CA2178541C - Implantable medical device - Google Patents
Implantable medical device Download PDFInfo
- Publication number
- CA2178541C CA2178541C CA002178541A CA2178541A CA2178541C CA 2178541 C CA2178541 C CA 2178541C CA 002178541 A CA002178541 A CA 002178541A CA 2178541 A CA2178541 A CA 2178541A CA 2178541 C CA2178541 C CA 2178541C
- Authority
- CA
- Canada
- Prior art keywords
- another
- bioactive material
- bioactive
- layer
- agent
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K51/00—Preparations containing radioactive substances for use in therapy or testing in vivo
- A61K51/12—Preparations containing radioactive substances for use in therapy or testing in vivo characterised by a special physical form, e.g. emulsion, microcapsules, liposomes, characterized by a special physical form, e.g. emulsions, dispersions, microcapsules
- A61K51/1282—Devices used in vivo and carrying the radioactive therapeutic or diagnostic agent, therapeutic or in vivo diagnostic kits, stents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
- A61L27/306—Other specific inorganic materials not covered by A61L27/303 - A61L27/32
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/54—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/08—Materials for coatings
- A61L29/085—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/08—Materials for coatings
- A61L29/10—Inorganic materials
- A61L29/106—Inorganic materials other than carbon
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
- A61L29/16—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/082—Inorganic materials
- A61L31/088—Other specific inorganic materials not covered by A61L31/084 or A61L31/086
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/10—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L31/146—Porous materials, e.g. foams or sponges
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L31/16—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L33/00—Antithrombogenic treatment of surgical articles, e.g. sutures, catheters, prostheses, or of articles for the manipulation or conditioning of blood; Materials for such treatment
- A61L33/02—Use of inorganic materials
- A61L33/022—Metal or alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
- A61F2250/0068—Means for introducing or releasing pharmaceutical products into the body the pharmaceutical product being in a reservoir
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
- A61L2300/602—Type of release, e.g. controlled, sustained, slow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
- A61L2300/606—Coatings
- A61L2300/608—Coatings having two or more layers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2420/00—Materials or methods for coatings medical devices
- A61L2420/08—Coatings comprising two or more layers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1002—Intraluminal radiation therapy
Abstract
A coated implantable medical device 10 includes a structure 12 adapted for introduction into the vascular system, esophagus, trachea, colon, biliary tract, or urinary tract; at least one layer 18 of a bioactive material posited on one surface of structure 12; and at least one porous layer 20 posited over the bioactive material layer 18 posited on one surface of structure (12) and the bioactive-material-free surface. Preferably, the structure 12 is a coronary stent. The porous layer 20 is comprised of a polymer applied preferably by vapor or plasma deposition and provides a controlled release of the bioactive material. It is particularly preferred that the polymer is a polyamide, parylene or a parylene derivative, which is deposited without solvents, heat or catalysts, merely by condensation of a monomer vapor. The invention is also directed to the method of manufacture of the device 10, as well as a method of using it in medical treatments.
Description
IMPLANTABLE MEDICAL DEVICE
Technical Field This invention relates generally to medical devices.
Background of.the Invention It has become common to treat a variety of medical conditions by introducing an implantable medical device partly or completely into the esophagus, trachea, colon, biliary tract, urinary tract, vascular system or other location within a human or veterinary patient. For example, many treatments of the vascular system entail the introduction of a device such as a stent, a catheter, a balloon, a wire guide, a cannula, or the like. However, when such a device is introduced into and manipulated through the vascular system, the blood vessel walls can be disturbed or injured. Clot formation or thrombosis often results at the injured site, causing stenosis or occlusion of the blood vessel. Moreover, if the medical device is left within the patient for an extended period of time, thrombus often forms on the device itself, again causing stenosis or occlusion. As a result, the patient is placed at risk of a variety of complications, including heart attack, pulmonary embolism, and stroke. Thus, the use of such a medical device can entail the risk of precisely the problems that its use was intended to ameliorate.
Another way in which blood vessels undergo stenosis is through disease. Probably the most common disease causing stenosis of blood vessels is atherosclerosis. Atherosclerosis is a condition which commonly affects the coronary arteries, the aorta, the iliofemoral arteries and the carotid arteries.
Atherosclerotic plaques of lipids, fibroblasts, and fibrin proliferate and cause obstruction of an artery or arteries. As
Technical Field This invention relates generally to medical devices.
Background of.the Invention It has become common to treat a variety of medical conditions by introducing an implantable medical device partly or completely into the esophagus, trachea, colon, biliary tract, urinary tract, vascular system or other location within a human or veterinary patient. For example, many treatments of the vascular system entail the introduction of a device such as a stent, a catheter, a balloon, a wire guide, a cannula, or the like. However, when such a device is introduced into and manipulated through the vascular system, the blood vessel walls can be disturbed or injured. Clot formation or thrombosis often results at the injured site, causing stenosis or occlusion of the blood vessel. Moreover, if the medical device is left within the patient for an extended period of time, thrombus often forms on the device itself, again causing stenosis or occlusion. As a result, the patient is placed at risk of a variety of complications, including heart attack, pulmonary embolism, and stroke. Thus, the use of such a medical device can entail the risk of precisely the problems that its use was intended to ameliorate.
Another way in which blood vessels undergo stenosis is through disease. Probably the most common disease causing stenosis of blood vessels is atherosclerosis. Atherosclerosis is a condition which commonly affects the coronary arteries, the aorta, the iliofemoral arteries and the carotid arteries.
Atherosclerotic plaques of lipids, fibroblasts, and fibrin proliferate and cause obstruction of an artery or arteries. As
2 -the obstruction increases, a critical level of stenosis is reached, to the point where the flow of blood past the obstruction is insufficient to meet the metabolic needs of the tissue distal to (downstream of) the obstruction. The result is ischemia.
Many medical devices and therapeutic methods are known for the treatment of atherosclerotic disease. One particularly useful therapy for certain atherosclerotic lesions is percutaneous transluminal angioplasty (PTA). During PTA, a balloon-tipped catheter is inserted in a patient's artery, the balloon being deflated. The tip of the catheter is advanced to the site of the atherosclerotic plaque to be dilated. The balloon is placed within or across the stenotic segment of the artery, and then inflated. Inflation of the balloon "cracks" the atherosclerotic plaque and expands the vessel, thereby relieving the stenosis, at least in part.
While PTA presently enjoys wide use, it suffers from two major problems. First, the blood vessel may suffer acute occlusion immediately after or within the initial hours after the dilation procedure. Such occlusion is referred to as "abrupt closure." Abrupt closure occurs in perhaps five percent or so of the cases in which PTA is employed, and can result in myocardial infarction and death if blood flow is not restored promptly. The primary mechanisms of abrupt closures are believed to be elastic recoil, arterial dissection and/or thrombosis. It has been postulated that the delivery of an appropriate agent (such as an antithrombic) directly into the arterial wall at the time of angioplasty could reduce the incidence of thrombotic acute closure, but the results of attempts to do so have been mixed.
A second major problem encountered in PTA is the re-narrowing of an artery after an initially successful angioplasty.
This re-narrowing is referred to as "restenosis" and typically occurs within the first six months after angioplasty. Restenosis is believed to arise through the proliferation and migration of cellular components from the arterial wall, as well as through
Many medical devices and therapeutic methods are known for the treatment of atherosclerotic disease. One particularly useful therapy for certain atherosclerotic lesions is percutaneous transluminal angioplasty (PTA). During PTA, a balloon-tipped catheter is inserted in a patient's artery, the balloon being deflated. The tip of the catheter is advanced to the site of the atherosclerotic plaque to be dilated. The balloon is placed within or across the stenotic segment of the artery, and then inflated. Inflation of the balloon "cracks" the atherosclerotic plaque and expands the vessel, thereby relieving the stenosis, at least in part.
While PTA presently enjoys wide use, it suffers from two major problems. First, the blood vessel may suffer acute occlusion immediately after or within the initial hours after the dilation procedure. Such occlusion is referred to as "abrupt closure." Abrupt closure occurs in perhaps five percent or so of the cases in which PTA is employed, and can result in myocardial infarction and death if blood flow is not restored promptly. The primary mechanisms of abrupt closures are believed to be elastic recoil, arterial dissection and/or thrombosis. It has been postulated that the delivery of an appropriate agent (such as an antithrombic) directly into the arterial wall at the time of angioplasty could reduce the incidence of thrombotic acute closure, but the results of attempts to do so have been mixed.
A second major problem encountered in PTA is the re-narrowing of an artery after an initially successful angioplasty.
This re-narrowing is referred to as "restenosis" and typically occurs within the first six months after angioplasty. Restenosis is believed to arise through the proliferation and migration of cellular components from the arterial wall, as well as through
- 3 -geometric changes in the arterial wall referred to as "remodeling." It has similarly been postulated that the delivery of appropriate agents directly into the arterial wall could interrupt the cellular and/or remodeling events leading to restenosis. However, like the attempts to prevent thrombotic acute closure, the results of attempts to prevent restenosis in this manner have been mixed.
Non=atherosclerotic vascular stenosis may also be treated by PTA. For example, Takayasu arteritis or neurofibromatosis may cause stenosis by fibrotic thickening of the arterial wall.
Restenosis of these lesions occurs at a high rate following angioplasty, however, due to the fibrotic nature of the diseases.
Medical therapies to treat or obviate them have been similarly disappointing.
A device such as an intravascular stent can be a useful adjunct to PTA, particularly in the case of either acute or threatened closure after angioplasty. The stent is placed in the dilated segment of the artery to mechanically prevent abrupt closure and restenosis. Unfortunately, even when the implantation of the stent is accompanied by aggressive and precise antiplatelet and anticoagulation therapy (typically by systemic administration), the incidence of thrombotic vessel closure or other thrombotic complication remains significant, and the prevention of restenosis is not as successful as desired.
Furthermore, an undesirable side effect of the systemic antiplatelet and anticoagulation therapy is an increased incidence of bleeding complications, most often at the percutaneous entry site.
Other conditions and diseases are treatable with stents, catheters, cannulae and other devices inserted into the esophagus, trachea, colon, biliary tract, urinary tract and other locations in the body, or with orthopedic devices, implants, or replacements. It would be desirable to develop devices and methods for reliably delivering suitable agents, drugs or
Non=atherosclerotic vascular stenosis may also be treated by PTA. For example, Takayasu arteritis or neurofibromatosis may cause stenosis by fibrotic thickening of the arterial wall.
Restenosis of these lesions occurs at a high rate following angioplasty, however, due to the fibrotic nature of the diseases.
Medical therapies to treat or obviate them have been similarly disappointing.
A device such as an intravascular stent can be a useful adjunct to PTA, particularly in the case of either acute or threatened closure after angioplasty. The stent is placed in the dilated segment of the artery to mechanically prevent abrupt closure and restenosis. Unfortunately, even when the implantation of the stent is accompanied by aggressive and precise antiplatelet and anticoagulation therapy (typically by systemic administration), the incidence of thrombotic vessel closure or other thrombotic complication remains significant, and the prevention of restenosis is not as successful as desired.
Furthermore, an undesirable side effect of the systemic antiplatelet and anticoagulation therapy is an increased incidence of bleeding complications, most often at the percutaneous entry site.
Other conditions and diseases are treatable with stents, catheters, cannulae and other devices inserted into the esophagus, trachea, colon, biliary tract, urinary tract and other locations in the body, or with orthopedic devices, implants, or replacements. It would be desirable to develop devices and methods for reliably delivering suitable agents, drugs or
- 4 -bioactive materials directly into a body portion during or following a medical procedure, so as to treat or prevent such conditions and diseases, for example, to prevent abrupt closure and/or restenosis of a body portion such as a passage, lumen or blood vessel. As a particular example, it would be desirable to have devices and methods which can deliver an antithrombic or other medication to the region of a blood vessel which has been treated by PTA, or by another interventional technique such as atherectomy, laser ablation, or the like. It would also be desirable that such devices would deliver their agents over both the short term (that is, the initial hours and days after treatment) and the long term (the weeks and months after treatment) It would also be desirable to provide precise control over the delivery rate for the agents, drugs or bioactive materials, and to limit systemic exposure to them. This would be particularly advantageous in therapies involving the delivery of a chemotherapeutic agent to a particular organ or site through an intravenous catheter (which itself has the advantage of reducing the amount of agent needed for successful treatment), by preventing stenosis both along the catheter and at the catheter tip. A wide variety of other therapies could be similarly improved. Of course, it would also be desirable to avoid degradation of the agent, drug or bioactive material during its incorporation on or into any such device.
Summary of the Invention The foregoing problems are solved and a technical advance is achieved in an illustrative vascular stent or other implantable medical device that provides a controlled release of at least one bioactive material into the vascular or other system, or other location in the body, in which a stent or other device is positioned. The bioactive material such as an agent(s) or drug(s) applied to a device or at least to part of the device may
Summary of the Invention The foregoing problems are solved and a technical advance is achieved in an illustrative vascular stent or other implantable medical device that provides a controlled release of at least one bioactive material into the vascular or other system, or other location in the body, in which a stent or other device is positioned. The bioactive material such as an agent(s) or drug(s) applied to a device or at least to part of the device may
- 5 -be degraded during application of a covering layer. Applicants have discovered that the degradation of bioactive material(s) applied to such a device may be avoided by covering the bioactive material(s) with one or more biocompatible material or materials such a porous layer of at least one biocompatible polymer that is applied without the use of solvents, catalysts, heat or other chemicals or techniques, which would otherwise be likely to degrade or damage the bioactive material. Those biocompatible polymers may be applied preferably by vapor deposition or plasma deposition, and may polymerize and cure merely upon condensation from the vapor phase, or may be photolytically polymerizable and are expected to be useful for this purpose. However, it should be recognized that alternative methods of deposition, and alternative porous material(s) may be employed.
In a first aspect, then, the present invention is directed in its simplest form to an implantable medical device comprising a structure adapted for introduction into the esophagus, trachea, colon, biliary tract, urinary tract, vascular system or other location in a human or veterinary patient, the structure being composed of a base material; at least one bioactive material on at least one part of the structure such as in wells, holes, grooves, slots and the like or on the surface of the structure;
and at least one porous material over the bioactive material and any bioactive-material-free surface if present, the porous material(s) preferably being composed of at least one polymer and having a thickness adequate to provide a controlled release of the bioactive material(s) therethrough.
Preferably, when the device is intended for use in the vascular system, the bioactive material(s) in the at least one layer is heparin or another antiplatelet or antithrombotic agent, or dexamethasone, dexamethasone acetate, dexamethasone sodium phosphate, or another dexamethasone derivative or anti-inflammatory steroid. Furthermore, a wide range of other bioactive materials can be separately or simultaneously employed.
In a first aspect, then, the present invention is directed in its simplest form to an implantable medical device comprising a structure adapted for introduction into the esophagus, trachea, colon, biliary tract, urinary tract, vascular system or other location in a human or veterinary patient, the structure being composed of a base material; at least one bioactive material on at least one part of the structure such as in wells, holes, grooves, slots and the like or on the surface of the structure;
and at least one porous material over the bioactive material and any bioactive-material-free surface if present, the porous material(s) preferably being composed of at least one polymer and having a thickness adequate to provide a controlled release of the bioactive material(s) therethrough.
Preferably, when the device is intended for use in the vascular system, the bioactive material(s) in the at least one layer is heparin or another antiplatelet or antithrombotic agent, or dexamethasone, dexamethasone acetate, dexamethasone sodium phosphate, or another dexamethasone derivative or anti-inflammatory steroid. Furthermore, a wide range of other bioactive materials can be separately or simultaneously employed.
- 6 -The materials can be mixed and deposited on the structure, or can be applied separately but to different parts of the structure.
The structure can have only one bioactive material thereon if desired. The bioactive material can include but not limited to, the following categories of agents: thrombolytics, vasodilators, antihypertensive agents, antimicrobials or antibiotics, antimitotics, antiproliferatives, antisecretory agents, non-steroidal anti-inflammatory drugs, immunosuppressive agents, growth factors and growth factor antagonists, antitumor and/or chemotherapeutic agents, antipolymerases, antiviral agents, photodynamic therapy agents, antibody targeted therapy agents, prodrugs, sex hormones, free radical scavengers, antioxidants, biologic agents, radiotherapeutic agents, radiopaque agents and radiolabelled agents. The major restriction is that the bioactive material must be able to withstand the coating techniques, for example, the vacuum employed during vapor deposition or plasma deposition of the at least one porous material, preferably as a layer. In other words, the bioactive material must have a relatively low vapor pressure at the deposition temperature, typically, near or at room temperature.
The at least one porous layer is preferably composed of a polyamide, parylene or a parylene derivative applied by catalyst-free vapor deposition and is conveniently about 5,000 to 250,000 A thick, which is adequate to provide a controlled release of the bioactive material. "Parylene" is both a generic name for a known group of polymers based on p-xylylene and made by vapor phase polymerization, and a name for the unsubstituted form of the polymer; the latter usage is employed herein. More particularly, parylene or a parylene derivative is created by first heating p-xylene or a suitable derivative at an appropriate temperature (for example, at about 950 C) to produce the cyclic dimer di-p-xylylene (or a derivative thereof). The resultant solid can be separated in pure form, and then cracked and pyrolyzed at an appropriate temperature (for example, at about 680 C) to produce a monomer
The structure can have only one bioactive material thereon if desired. The bioactive material can include but not limited to, the following categories of agents: thrombolytics, vasodilators, antihypertensive agents, antimicrobials or antibiotics, antimitotics, antiproliferatives, antisecretory agents, non-steroidal anti-inflammatory drugs, immunosuppressive agents, growth factors and growth factor antagonists, antitumor and/or chemotherapeutic agents, antipolymerases, antiviral agents, photodynamic therapy agents, antibody targeted therapy agents, prodrugs, sex hormones, free radical scavengers, antioxidants, biologic agents, radiotherapeutic agents, radiopaque agents and radiolabelled agents. The major restriction is that the bioactive material must be able to withstand the coating techniques, for example, the vacuum employed during vapor deposition or plasma deposition of the at least one porous material, preferably as a layer. In other words, the bioactive material must have a relatively low vapor pressure at the deposition temperature, typically, near or at room temperature.
The at least one porous layer is preferably composed of a polyamide, parylene or a parylene derivative applied by catalyst-free vapor deposition and is conveniently about 5,000 to 250,000 A thick, which is adequate to provide a controlled release of the bioactive material. "Parylene" is both a generic name for a known group of polymers based on p-xylylene and made by vapor phase polymerization, and a name for the unsubstituted form of the polymer; the latter usage is employed herein. More particularly, parylene or a parylene derivative is created by first heating p-xylene or a suitable derivative at an appropriate temperature (for example, at about 950 C) to produce the cyclic dimer di-p-xylylene (or a derivative thereof). The resultant solid can be separated in pure form, and then cracked and pyrolyzed at an appropriate temperature (for example, at about 680 C) to produce a monomer
- 7 -vapor of p-xylylene (or derivative); the monomer vapor is cooled to a suitable temperature (for example, below 50 C) and allowed to condense on the desired object, for example, on the at least one layer of bioactive material. The resultant polymer has the repeating structure -(CH2C6H4CH2-)-n, with n equal to about 5,000, and a molecular weight in the range of 500,000.
As indicated, parylene and parylene derivative coatings applicable by vapor deposition are known for a variety of biomedical uses, and are commercially available from or through a variety of sources, including Specialty Coating Systems (100 Deposition Drive, Clear Lake, WI 54005), Para Tech Coating, Inc.
(35 Argonaut, Aliso Viejo, CA 92656) and Advanced Surface Technology, Inc. (9 Linnel Circle, Billerica, MA 01821-3902).
The at least one porous layer can alternatively be applied by plasma deposition. Plasma is an ionized gas maintained under vacuum and excited by electrical energy, typically in the radiofrequency range. Because the gas is maintained under vacuum, the plasma deposition process occurs at or near room temperature.
Plasma can be used to deposit polymers such as poly(ethylene oxide), poly(ethylene glycol), and poly(propylene oxide), as well as polymers of silicone, methane, tetrafluoroethylene (including TEFLON brand polymers), tetramethyldisiloxane, and others.
While the foregoing represents some preferred embodiments of the present invention, other polymer systems may also be employed, e.g., polymers derived from photopolymerizeable monomers. Also, other coating techniques may be utilized, e.g., dipping, spraying, and the like.
The device may include two or more layers of different bioactive materials atop the structure. However, for the purposes of the present invention, the same bioactive material will generally not be posited on the different surfaces of the device within the same layer. In other words, each surface of the device structure will carry a different bioactive material or materials except where the bioactive material is the innermost or outermost
As indicated, parylene and parylene derivative coatings applicable by vapor deposition are known for a variety of biomedical uses, and are commercially available from or through a variety of sources, including Specialty Coating Systems (100 Deposition Drive, Clear Lake, WI 54005), Para Tech Coating, Inc.
(35 Argonaut, Aliso Viejo, CA 92656) and Advanced Surface Technology, Inc. (9 Linnel Circle, Billerica, MA 01821-3902).
The at least one porous layer can alternatively be applied by plasma deposition. Plasma is an ionized gas maintained under vacuum and excited by electrical energy, typically in the radiofrequency range. Because the gas is maintained under vacuum, the plasma deposition process occurs at or near room temperature.
Plasma can be used to deposit polymers such as poly(ethylene oxide), poly(ethylene glycol), and poly(propylene oxide), as well as polymers of silicone, methane, tetrafluoroethylene (including TEFLON brand polymers), tetramethyldisiloxane, and others.
While the foregoing represents some preferred embodiments of the present invention, other polymer systems may also be employed, e.g., polymers derived from photopolymerizeable monomers. Also, other coating techniques may be utilized, e.g., dipping, spraying, and the like.
The device may include two or more layers of different bioactive materials atop the structure. However, for the purposes of the present invention, the same bioactive material will generally not be posited on the different surfaces of the device within the same layer. In other words, each surface of the device structure will carry a different bioactive material or materials except where the bioactive material is the innermost or outermost
- 8 -layer, e.g. heparin may form the innermost layer or the outermost layer or both. These additional layers may be placed directly atop one another or can be separated by additional porous polymer layers between each of them. Additionally, the layers of bioactive materials can comprise a mixture of different bioactive materials. The porous layers are also preferably composed of parylene or a parylene derivative. Advantageously, the two or more bioactive materials can have different solubilities, and the layer containing the less soluble bioactive material (for example, dexamethasone) is preferably posited above the layer containing the more soluble bioactive material (for example, heparin).
Unexpectedly, this has been found to increase the in vitro release rate of some relatively less soluble materials such as dexamethasone, while simultaneously decreasing the release rate of some relatively more soluble materials such as heparin.
While the structure included in the device may be configured in a variety of ways, the structure is preferably configured as a vascular stent composed of a biocompatible metal such as stainless steel, nickel, silver, platinum, gold, titanium, tantalum, iridium, tungsten, Nitinol, inconel, or the like. An additional substantially nonporous coating layer of parylene or a parylene derivative or other biocompatible polymer of about 50,000 to 500,000 A thick may be posited directly atop the vascular stent, beneath the at least one layer of bioactive material. The additional coating layer can merely be relatively less porous than the at least one porous layer, but preferably is substantially nonporous, that is, sufficiently nonporous to render the stent essentially impervious to blood during normal circumstances of use.
In a second aspect, the present invention is directed to a method of making an implantable medical device of the type disclosed above, in which the method comprises the steps of:
depositing at least one layer of a bioactive material on one surface of the structure; and depositing at least one porous layer
Unexpectedly, this has been found to increase the in vitro release rate of some relatively less soluble materials such as dexamethasone, while simultaneously decreasing the release rate of some relatively more soluble materials such as heparin.
While the structure included in the device may be configured in a variety of ways, the structure is preferably configured as a vascular stent composed of a biocompatible metal such as stainless steel, nickel, silver, platinum, gold, titanium, tantalum, iridium, tungsten, Nitinol, inconel, or the like. An additional substantially nonporous coating layer of parylene or a parylene derivative or other biocompatible polymer of about 50,000 to 500,000 A thick may be posited directly atop the vascular stent, beneath the at least one layer of bioactive material. The additional coating layer can merely be relatively less porous than the at least one porous layer, but preferably is substantially nonporous, that is, sufficiently nonporous to render the stent essentially impervious to blood during normal circumstances of use.
In a second aspect, the present invention is directed to a method of making an implantable medical device of the type disclosed above, in which the method comprises the steps of:
depositing at least one layer of a bioactive material on one surface of the structure; and depositing at least one porous layer
- 9 -over the at least one bioactive material layer and the bioactive-material-free surface, the at least one porous layer being composed of a polymer and being of a thickness adequate to provide a controlled release of the bioactive material. Conveniently and in a preferred embodiment, the at least one porous layer is polymerized from a monomer vapor which is free of any solvent or polymerization catalyst, and cures by itself upon condensation, without any additional heating or curing aid (for example, visible or ultraviolet light). The at least one layer of the bioactive material may be deposited on the one surface of the structure by any convenient method such as dipping, rolling, brushing, spraying, electrostatic deposition, or the like.
Lastly, in a third aspect, the present invention is directed to an improvement in a method of medically treating a human or veterinary patient by the step of inserting an implantable medical device into the body of the patient, the device comprising a structure adapted for introduction into an applicable system of or location in the patient, and the structure being composed of a base material, in which the procedure comprises the preliminary steps of: depositing at least one layer of a bioactive material on one surface of the structure; and depositing at least one porous layer over the at least one bioactive material layer and the bioactive-material-free surface, the at least one porous layer being composed of a polymer having a thickness adequate to provide a controlled release of the bioactive material.
The device and methods of the present invention are useful in a wide variety of locations within a human or veterinary patient, such as in the esophagus, trachea, colon, biliary tract, urinary tract and vascular system, as well as for subdural and orthopedic devices, implants or replacements. They are particularly advantageous for reliably delivering suitable bioactive materials during or following an intravascular procedure, and find particular use in preventing abrupt closure
Lastly, in a third aspect, the present invention is directed to an improvement in a method of medically treating a human or veterinary patient by the step of inserting an implantable medical device into the body of the patient, the device comprising a structure adapted for introduction into an applicable system of or location in the patient, and the structure being composed of a base material, in which the procedure comprises the preliminary steps of: depositing at least one layer of a bioactive material on one surface of the structure; and depositing at least one porous layer over the at least one bioactive material layer and the bioactive-material-free surface, the at least one porous layer being composed of a polymer having a thickness adequate to provide a controlled release of the bioactive material.
The device and methods of the present invention are useful in a wide variety of locations within a human or veterinary patient, such as in the esophagus, trachea, colon, biliary tract, urinary tract and vascular system, as well as for subdural and orthopedic devices, implants or replacements. They are particularly advantageous for reliably delivering suitable bioactive materials during or following an intravascular procedure, and find particular use in preventing abrupt closure
- 10 -and/or restenosis of a blood vessel. More particularly, they permit, for example, the delivery of an antithrombotic, an antiplatelet, an anti-inflammatory steroid, or another medication to the region of a blood vessel which has been opened by PTA.
Likewise, it allows for the delivery of one bioactive material to, for example, the lumen of a blood vessel and another bioactive material to the vessel wall. The use of a porous polymer layer permits the release rate of a bioactive material to be carefully controlled over both the short and long terms.
These and other aspects of the present invention will be appreciated by those skilled in the art upon the reading and understanding of the specification.
Brief Description of the Drawings A better understanding of the present invention will now be had upon reference to the following detailed description, when read in conjunction with the accompanying drawing, wherein like reference characters refer to like parts throughout the several views, and in which:
FIG. 1 is a cross-sectional view of a first preferred embodiment of the present invention;
FIG. 2 is a cross-sectional view of another preferred embodiment of the present invention;
FIG. 3 is a cross-sectional view of yet another preferred embodiment of the present invention;
FIG. 4 is a cross-sectional view of a further preferred embodiment of the present invention;
FIG. 5 is a cross-sectional view of an additional preferred embodiment of the present invention;
FIGs. 6A and 6B are cross-sectional views of an additional preferred embodiment of the present invention;
FIG. 7 is a cross-sectional view of an additional preferred embodiment of the present invention;
Likewise, it allows for the delivery of one bioactive material to, for example, the lumen of a blood vessel and another bioactive material to the vessel wall. The use of a porous polymer layer permits the release rate of a bioactive material to be carefully controlled over both the short and long terms.
These and other aspects of the present invention will be appreciated by those skilled in the art upon the reading and understanding of the specification.
Brief Description of the Drawings A better understanding of the present invention will now be had upon reference to the following detailed description, when read in conjunction with the accompanying drawing, wherein like reference characters refer to like parts throughout the several views, and in which:
FIG. 1 is a cross-sectional view of a first preferred embodiment of the present invention;
FIG. 2 is a cross-sectional view of another preferred embodiment of the present invention;
FIG. 3 is a cross-sectional view of yet another preferred embodiment of the present invention;
FIG. 4 is a cross-sectional view of a further preferred embodiment of the present invention;
FIG. 5 is a cross-sectional view of an additional preferred embodiment of the present invention;
FIGs. 6A and 6B are cross-sectional views of an additional preferred embodiment of the present invention;
FIG. 7 is a cross-sectional view of an additional preferred embodiment of the present invention;
- 11 -FIG. 8 is a partial, enlarged top view of FIG. 7;
FIG. 9 is an enlarged, sectional view along lines 9-9 of FIG. 8; and FIGs. 10A-10D are enlarged cross-sectional views along lines 10-10 of FIG. 8.
Detailed Description With reference now to FIG. 1, an implantable medical device 10 in accordance with the present invention is shown and first comprises a structure 12 adapted for introduction into a human or veterinary patient. "Adapted" means that the structure
FIG. 9 is an enlarged, sectional view along lines 9-9 of FIG. 8; and FIGs. 10A-10D are enlarged cross-sectional views along lines 10-10 of FIG. 8.
Detailed Description With reference now to FIG. 1, an implantable medical device 10 in accordance with the present invention is shown and first comprises a structure 12 adapted for introduction into a human or veterinary patient. "Adapted" means that the structure
12 is shaped and sized for such introduction. For clarity, only a portion of the structure 12 is shown in FIG. 1.
By way of example, the structure 12 is configured as a vascular stent particularly adapted for insertion into the vascular system of the patient. However, this stent structure can be used in other systems and sites such as the esophagus, trachea, colon, biliary ducts, urethra and ureters, subdural among others.
Indeed, the structure 12 can alternatively be configured as any conventional vascular or other medical device, and can include any of a variety of conventional stents or other adjuncts, such as helical wound strands, perforated cylinders, or the like.
Moreover, because the problems addressed by the present invention arise with respect to those portions of the device actually positioned within the patient, the inserted structure 12 need not be an entire device, but can merely be that portion of a vascular or other device which is intended to be introduced into the patient. Accordingly, the structure 12 can be configured as at least one of, or any portion of, a catheter, a wire guide, a cannula, a stent, a vascular or other graft, a cardiac pacemaker lead or lead tip, a cardiac defibrillator lead or lead tip, a heart valve, or an orthopedic device, appliance, implant, or replacement. The structure 12 can also be configured as a combination of portions of any of these.
Most preferably, however, the structure 12 is configured as a vascular stent such as the commercially available Gianturco-Roubin FLEX-STENTTM coronary stent from Cook Incorporated, Bloomington, Indiana. Such stents are typically about 10 to about 60 mm in length and designed to expand to a diameter of about 2 to about 6 mm when inserted into the vascular system of the patient. The Gianturco-Roubin stent in particular is typically about 12 to about 25 mm in length and designed to expand to a diameter of about 2 to about 4 mm when so inserted.
These stent dimensions are, of course, applicable to exemplary stents employed in the coronary arteries. Structures such as stents or catheter portions intended to be employed at other sites in the patient, such as in the aorta, esophagus, trachea, colon, biliary tract, or urinary tract will have different dimensions more suited to such use. For example, aortic, esophageal, tracheal and colonic stents may have diameters up to about 25 mm and lengths about 100 mm or longer.
The structure 12 is composed of a base material 14 suitable for the intended use of the structure 12. The base material 14 is preferably biocompatible, although cytotoxic or other poisonous base materials may be employed if they are adequately isolated from the patient. Such incompatible materials may be useful in, for example, radiation treatments in which a radioactive material is positioned by catheter in or close to the specific tissues to be treated. Under most circumstances, however, the base material 14 of the structure 12 should be biocompatible.
A variety of conventional materials can be employed as the base material 14. Some materials may be more useful for structures other than the coronary stent exemplifying the structure 12. The base material 14 may be either elastic or inelastic, depending upon the flexibility or elasticity of the
By way of example, the structure 12 is configured as a vascular stent particularly adapted for insertion into the vascular system of the patient. However, this stent structure can be used in other systems and sites such as the esophagus, trachea, colon, biliary ducts, urethra and ureters, subdural among others.
Indeed, the structure 12 can alternatively be configured as any conventional vascular or other medical device, and can include any of a variety of conventional stents or other adjuncts, such as helical wound strands, perforated cylinders, or the like.
Moreover, because the problems addressed by the present invention arise with respect to those portions of the device actually positioned within the patient, the inserted structure 12 need not be an entire device, but can merely be that portion of a vascular or other device which is intended to be introduced into the patient. Accordingly, the structure 12 can be configured as at least one of, or any portion of, a catheter, a wire guide, a cannula, a stent, a vascular or other graft, a cardiac pacemaker lead or lead tip, a cardiac defibrillator lead or lead tip, a heart valve, or an orthopedic device, appliance, implant, or replacement. The structure 12 can also be configured as a combination of portions of any of these.
Most preferably, however, the structure 12 is configured as a vascular stent such as the commercially available Gianturco-Roubin FLEX-STENTTM coronary stent from Cook Incorporated, Bloomington, Indiana. Such stents are typically about 10 to about 60 mm in length and designed to expand to a diameter of about 2 to about 6 mm when inserted into the vascular system of the patient. The Gianturco-Roubin stent in particular is typically about 12 to about 25 mm in length and designed to expand to a diameter of about 2 to about 4 mm when so inserted.
These stent dimensions are, of course, applicable to exemplary stents employed in the coronary arteries. Structures such as stents or catheter portions intended to be employed at other sites in the patient, such as in the aorta, esophagus, trachea, colon, biliary tract, or urinary tract will have different dimensions more suited to such use. For example, aortic, esophageal, tracheal and colonic stents may have diameters up to about 25 mm and lengths about 100 mm or longer.
The structure 12 is composed of a base material 14 suitable for the intended use of the structure 12. The base material 14 is preferably biocompatible, although cytotoxic or other poisonous base materials may be employed if they are adequately isolated from the patient. Such incompatible materials may be useful in, for example, radiation treatments in which a radioactive material is positioned by catheter in or close to the specific tissues to be treated. Under most circumstances, however, the base material 14 of the structure 12 should be biocompatible.
A variety of conventional materials can be employed as the base material 14. Some materials may be more useful for structures other than the coronary stent exemplifying the structure 12. The base material 14 may be either elastic or inelastic, depending upon the flexibility or elasticity of the
- 13 -polymer layers to be applied over it. The base material may be either biodegradable or non-biodegradable, and a variety of biodegradable polymers are known. Moreover, some biologic agents have sufficient strength to serve as the base material 14 of some useful structures 12, even if not especially useful in the exemplary coronary stent.
Accordingly, the base material 14 can include at least one of stainless steel, tantalum, titanium, nitinol, gold, platinum, inconel, iridium, silver, tungsten, or another biocompatible metal, or alloys of any of these; carbon or carbon fiber;
cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers of these; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxybutyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a suitable mixture of any of these. Stainless steel is particularly useful as the base material 14 when the structure 12 is configured as a vascular stent.
Of course, when the structure 12 is composed of a radiolucent material such as polypropylene, polyethylene, or others above, a conventional radiopaque coating may and preferably should be applied to it. The radiopaque coating provides a means for identifying the location of the structure 12 by X-ray or fluoroscopy during or after its introduction into the patient's vascular system.
With continued reference to FIG. 1, the vascular device 10 of the present invention next comprises at least one layer 18 of a bioactive material posited on one surface of the structure 12. For the purposes of the present invention, at least one
Accordingly, the base material 14 can include at least one of stainless steel, tantalum, titanium, nitinol, gold, platinum, inconel, iridium, silver, tungsten, or another biocompatible metal, or alloys of any of these; carbon or carbon fiber;
cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers of these; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxybutyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a suitable mixture of any of these. Stainless steel is particularly useful as the base material 14 when the structure 12 is configured as a vascular stent.
Of course, when the structure 12 is composed of a radiolucent material such as polypropylene, polyethylene, or others above, a conventional radiopaque coating may and preferably should be applied to it. The radiopaque coating provides a means for identifying the location of the structure 12 by X-ray or fluoroscopy during or after its introduction into the patient's vascular system.
With continued reference to FIG. 1, the vascular device 10 of the present invention next comprises at least one layer 18 of a bioactive material posited on one surface of the structure 12. For the purposes of the present invention, at least one
- 14 -bioactive material is posited on one surface of the structure 12, and the other surface will either contain no bioactive material or one or more different bioactive materials. In this manner, one or more bioactive materials or drugs may be delivered, for example, with a vascular stent, to the blood stream from the lumen surface of the stent, and a different treatment may be delivered on the vessel sur`face of the stent. A vast range of drugs, medicaments and materials may be employed as the bioactive material in the layer 18, so long as the selected material can survive exposure to the vacuum drawn during vapor deposition or plasma deposition. Particularly useful in the practice of the present invention are materials which prevent or ameliorate abrupt closure and restenosis of blood vessels previously opened by stenting surgery or other procedures. Thrombolytics (which dissolve, break up or disperse thrombi) and antithrombogenics (which interfere with or prevent the formation of thrombi) are especially useful bioactive materials when the structure 12 is a vascular stent. Particularly preferred thrombolytics are urokinase, streptokinase, and the tissue plasminogen activators.
Particularly preferred antithrombogenics are heparin, hirudin, and the antiplatelets.
Urokinase is a plasminogen activating enzyme typically obtained from human kidney cell cultures. Urokinase catalyzes the conversion of plasminogen into the fibrinolytic plasmin, which breaks down fibrin thrombi.
Heparin is a mucopolysaccharide anticoagulant typically obtained from porcine intestinal mucosa or bovine lung. Heparin acts as a thrombin inhibitor by greatly enhancing the effects of the blood's endogenous antithrombin III. Thrombin, a potent enzyme in the coagulation cascade, is key in catalyzing the formation of fibrin. Therefore, by inhibiting thrombin, heparin inhibits the formation of fibrin thrombi. Alternatively, heparin may be covalently bound to the outer layer of structure 12. Thus, heparin would form the outermost layer of structure 12 and would
Particularly preferred antithrombogenics are heparin, hirudin, and the antiplatelets.
Urokinase is a plasminogen activating enzyme typically obtained from human kidney cell cultures. Urokinase catalyzes the conversion of plasminogen into the fibrinolytic plasmin, which breaks down fibrin thrombi.
Heparin is a mucopolysaccharide anticoagulant typically obtained from porcine intestinal mucosa or bovine lung. Heparin acts as a thrombin inhibitor by greatly enhancing the effects of the blood's endogenous antithrombin III. Thrombin, a potent enzyme in the coagulation cascade, is key in catalyzing the formation of fibrin. Therefore, by inhibiting thrombin, heparin inhibits the formation of fibrin thrombi. Alternatively, heparin may be covalently bound to the outer layer of structure 12. Thus, heparin would form the outermost layer of structure 12 and would
- 15 -not be readily degraded enzymatically, and would remain active as a thrombin inhibitor.
Of course, bioactive materials having other functions can also be successfully delivered by the device 10 of the present invention. For example, an antiproliferative agent such as methotrexate will inhibit over-proliferation of smooth muscle cells and thus inhibit restenosis of the dilated segment of the blood vessel. The antiproliferative is desirably supplied for this purpose over a period of about four to six months.
Additionally, localized delivery of an antiproliferative agent is also useful for the treatment of a variety of malignant conditions characterized by highly vascular growth. In such cases, the device 10 of the present invention could be placed in the arterial supply of the tumor to provide a means of delivering a relatively high dose of the antiproliferative agent directly to the tumor.
A vasodilator such as a calcium channel blocker or a nitrate will suppress vasospasm, which is common following angioplasty procedures. Vasospasm occurs as a response to injury of a blood vessel, and the tendency toward vasospasm decreases as the vessel heals. Accordingly, the vasodilator is desirably supplied over a period of about two to three weeks. Of course, trauma from angioplasty is not the only vessel injury which can cause vasospasm, and the device 10 may be introduced into vessels other than the coronary arteries, such as the aorta, carotid arteries, renal arteries, iliac arteries or peripheral arteries for the prevention of vasospasm in them.
A variety of other bioactive materials are particularly suitable for use when the structure 12 is configured as something other than a coronary stent. For example, an anti-cancer chemotherapeutic agent can be delivered by the device 10 to a localized tumor. More particularly, the device 10 can be placed in an artery supplying blood to the tumor or elsewhere to deliver a relatively high and prolonged dose of the agent directly to the tumor, while limiting systemic exposure and toxicity. The agent
Of course, bioactive materials having other functions can also be successfully delivered by the device 10 of the present invention. For example, an antiproliferative agent such as methotrexate will inhibit over-proliferation of smooth muscle cells and thus inhibit restenosis of the dilated segment of the blood vessel. The antiproliferative is desirably supplied for this purpose over a period of about four to six months.
Additionally, localized delivery of an antiproliferative agent is also useful for the treatment of a variety of malignant conditions characterized by highly vascular growth. In such cases, the device 10 of the present invention could be placed in the arterial supply of the tumor to provide a means of delivering a relatively high dose of the antiproliferative agent directly to the tumor.
A vasodilator such as a calcium channel blocker or a nitrate will suppress vasospasm, which is common following angioplasty procedures. Vasospasm occurs as a response to injury of a blood vessel, and the tendency toward vasospasm decreases as the vessel heals. Accordingly, the vasodilator is desirably supplied over a period of about two to three weeks. Of course, trauma from angioplasty is not the only vessel injury which can cause vasospasm, and the device 10 may be introduced into vessels other than the coronary arteries, such as the aorta, carotid arteries, renal arteries, iliac arteries or peripheral arteries for the prevention of vasospasm in them.
A variety of other bioactive materials are particularly suitable for use when the structure 12 is configured as something other than a coronary stent. For example, an anti-cancer chemotherapeutic agent can be delivered by the device 10 to a localized tumor. More particularly, the device 10 can be placed in an artery supplying blood to the tumor or elsewhere to deliver a relatively high and prolonged dose of the agent directly to the tumor, while limiting systemic exposure and toxicity. The agent
- 16 -may be a curative, a pre-operative debulker reducing the size of the tumor, or a palliative which eases the symptoms of the disease. It should be noted that the bioactive material in the present invention is delivered across the device 10, and not by passage from an outside source through any lumen defined in the device 10, such as through a catheter employed for conventional chemotherapy. The bioactive material of the present invention may, of course, be released from the device 10 into any lumen defined in the device, or to tissue in contact with the device and that the lumen may carry some other agent to be delivered through it. For example, tamoxifen citrate, Taxol or derivatives thereof Proscar , Hytrin@, or Eulexin may be applied to the tissue-exposed surface of the device for delivery to a tumor located, for example in breast tissue or the prostate.
Dopamine or a dopamine agonist such as bromocriptine mesylate or pergolide mesylate is useful for the treatment of neurological disorders such as Parkinson's disease. The device 10 could be placed in the vascular supply of the thalamic substantia nigra for this purpose, or elsewhere, localizing treatment in the thalamus.
A wide range of other bioactive materials can be delivered by the device 10. Accordingly, it is preferred that the bioactive material contained in the layer 18 includes at least one of heparin, covalent heparin, or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof;
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; Hytrin or other antihypertensive agents; an antimicrobial agent or antibiotic; aspirin, ticlopidine, a glycoprotein Iib/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine
Dopamine or a dopamine agonist such as bromocriptine mesylate or pergolide mesylate is useful for the treatment of neurological disorders such as Parkinson's disease. The device 10 could be placed in the vascular supply of the thalamic substantia nigra for this purpose, or elsewhere, localizing treatment in the thalamus.
A wide range of other bioactive materials can be delivered by the device 10. Accordingly, it is preferred that the bioactive material contained in the layer 18 includes at least one of heparin, covalent heparin, or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof;
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; Hytrin or other antihypertensive agents; an antimicrobial agent or antibiotic; aspirin, ticlopidine, a glycoprotein Iib/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine
- 17 -or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide (DMSO), a retinoid or another antisecretory agent;
cytochalasin or another actin inhibitor; or a remodelling inhibitor; deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, TaxolO or the derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal antiinflammatory agent; cyclosporin or another immunosuppressive agent; trapidal (a PDGF antagonist), angiopeptin (a growth hormone antagonist), angiogenin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co (5.3 year half life) , 192Ir (73.8 days) , 32P (14.3 days ), 111In (68 hours ), 90Y (64 hours ), 9911'TC (6 hours) or another radiotherapeutic agent; iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme (ACE) inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-aminosteroid (lasaroid) or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium, Norvir, Crixivan, or other antiviral agents; 5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431
cytochalasin or another actin inhibitor; or a remodelling inhibitor; deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, TaxolO or the derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal antiinflammatory agent; cyclosporin or another immunosuppressive agent; trapidal (a PDGF antagonist), angiopeptin (a growth hormone antagonist), angiogenin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co (5.3 year half life) , 192Ir (73.8 days) , 32P (14.3 days ), 111In (68 hours ), 90Y (64 hours ), 9911'TC (6 hours) or another radiotherapeutic agent; iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme (ACE) inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-aminosteroid (lasaroid) or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium, Norvir, Crixivan, or other antiviral agents; 5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431
- 18 -epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; gene therapy agents; and enalapril and other prodrugs; ProscarO, Hytrin or other agents for treating benign prostatic hyperplasia (BHP) or a mixture of any of these; and various forms of small intestine submucosa (SIS).
In a particularly preferred aspect, the layer of bioactive material contains preferably from about 0.01 mg to about 10 mg and more preferably from about 0.1 mg to about 4 mg of the bioactive material per cm2 of the gross surface area of the structure.
"Gross surface area" refers to the area calculated from the gross or overall extent of the structure, and not necessarily to the actual surface area of the particular shape or individual parts of the structure. In other terms, about 100 g to about 300 g of drug per 0.001 inch of coating thickness may be contained on the device surface.
When the structure 12 is configured as a vascular stent, however, particularly preferred materials for the bioactive material of the layer 18 are heparin, anti-inflammatory steroids including but not limited to dexamethasone and its derivatives, and mixtures of heparin and such steroids.
Still with reference to FIG. 1, the device 10 of the present invention also comprises at least one porous layer 20 posited over the layer 18 of bioactive material and the bioactive-material-free surface. The purpose of the porous layer 20 is to provide a controlled release of the bioactive material when the device 10 is positioned in the vascular system of a patient. The thickness of the porous layer 20 is chosen so as to provide such control.
More particularly, the porous layer 20 is composed of a polymer deposited on the bioactive material layer 18, preferably by vapor deposition. Plasma deposition may also be useful for this purpose. Preferably, the layer 20 is one that is polymerized
In a particularly preferred aspect, the layer of bioactive material contains preferably from about 0.01 mg to about 10 mg and more preferably from about 0.1 mg to about 4 mg of the bioactive material per cm2 of the gross surface area of the structure.
"Gross surface area" refers to the area calculated from the gross or overall extent of the structure, and not necessarily to the actual surface area of the particular shape or individual parts of the structure. In other terms, about 100 g to about 300 g of drug per 0.001 inch of coating thickness may be contained on the device surface.
When the structure 12 is configured as a vascular stent, however, particularly preferred materials for the bioactive material of the layer 18 are heparin, anti-inflammatory steroids including but not limited to dexamethasone and its derivatives, and mixtures of heparin and such steroids.
Still with reference to FIG. 1, the device 10 of the present invention also comprises at least one porous layer 20 posited over the layer 18 of bioactive material and the bioactive-material-free surface. The purpose of the porous layer 20 is to provide a controlled release of the bioactive material when the device 10 is positioned in the vascular system of a patient. The thickness of the porous layer 20 is chosen so as to provide such control.
More particularly, the porous layer 20 is composed of a polymer deposited on the bioactive material layer 18, preferably by vapor deposition. Plasma deposition may also be useful for this purpose. Preferably, the layer 20 is one that is polymerized
- 19 -from a vapor which is free of any solvent, catalysts or similar polymerization promoters. Also preferably, the polymer in the porous layer 20 is one which automatically polymerizes upon condensation from the vapor phase, without the action of any curative agent or activity such as heating, the application of visible or ultraviolet light, radiation, ultrasound, or the like.
Most preferably, the polymer in the porous layer 20 is polyimide, parylene or a parylene derivative.
When first deposited, the parylene or parylene derivative is thought to form a network resembling a fibrous mesh, with relatively large pores. As more is deposited, the porous layer not only becomes thicker, but it is believed that parylene or parylene derivative is also deposited in the previously formed pores, making the existing pores smaller. Careful and precise 15 control over the deposition of the parylene or parylene derivative therefore permits close control over the release rate of material from the at least one layer 18 of bioactive material. It is for this reason that the bioactive material lies under the at least one porous layer 20, rather than being dispersed within or
Most preferably, the polymer in the porous layer 20 is polyimide, parylene or a parylene derivative.
When first deposited, the parylene or parylene derivative is thought to form a network resembling a fibrous mesh, with relatively large pores. As more is deposited, the porous layer not only becomes thicker, but it is believed that parylene or parylene derivative is also deposited in the previously formed pores, making the existing pores smaller. Careful and precise 15 control over the deposition of the parylene or parylene derivative therefore permits close control over the release rate of material from the at least one layer 18 of bioactive material. It is for this reason that the bioactive material lies under the at least one porous layer 20, rather than being dispersed within or
20 throughout it. The porous layer 20, however, also protects the bioactive material layer 18 during deployment of the device 10, for example, during insertion of the device 10 through a catheter and into the vascular system or elsewhere in the patient.
As shown in FIG. 1, the device 10 of the present invention can further comprise at least one additional coating layer 16 posited between the structure 12 and the at least one layer 18 of bioactive material. While the additional coating layer 16 can simply be a medical grade primer, the additional coating layer 16 is preferably composed of the same polymer as the at least one porous layer 20. However, the additional coating layer 16 is also preferably less porous than the at least one porous layer 20, and is more preferably substantially nonporous. "Substantially nonporous" means that the additional coating layer 16 is sufficiently impervious to prevent any appreciable interaction between the base material 14 of the structure 12 and the blood to which the device 10 will be exposed during use. The use of an additional coating layer 16 which is substantially nonporous would permit the use of a toxic or poisonous base material 14, as mentioned above. Even if the base material 14 of the structure 12 is biocompatible, however, it may be advantageous to isolate it from the blood by use of a substantially nonporous coating layer 16.
Other polymer systems that may find application within the scope of the invention include polymers derived from photopolymerizable monomers such as liquid monomers preferably having at least two cross linkable C-C (Carbon to Carbon) double bonds and being a non-gaseous addition polymerizable ethylenically unsaturated compound, having a boiling point above 100 C, at atmospheric pressure, a molecular weight of about 100-1500 and being capable of forming high molecular weight addition polymers readily. More preferably, the monomer is preferably an addition photopolymerizable polyethylenically unsaturated acrylic or methacrylic acid ester containing two or more acrylate or methacrylate groups per molecule or mixtures thereof. A few illustrative examples of such multifunctional acrylates are ethylene glycol diacrylate, ethylene glycol dimethacrylate, trimethylopropane triacrylate, trimethylopropane trimethacrylate, pentaerythritol tetraacrylate or pentaerythritol tetramethacrylate, 1,6-hexanediol dimethacrylate, and diethyleneglycol dimethacrylate.
Also useful in some special instances are monoacrylates such as n-butyl-acrylate, n-butyl methacrylate, 2-ethylhexyl acrylate, lauryl-acrylate, and 2-hydroxy-propyl acrylate. Small quantities of amides of (meth)acrylic acid such as N-methylol methacrylamide butyl ether are also suitable, N-vinyl compounds such as N-vinyl pyrrolidone, vinyl esters of aliphatic monocarboxylic acids such as vinyl oleate, vinyl ethers of diols such as butanediol-1, 4-divinyl ether and allyl ether and allyl
As shown in FIG. 1, the device 10 of the present invention can further comprise at least one additional coating layer 16 posited between the structure 12 and the at least one layer 18 of bioactive material. While the additional coating layer 16 can simply be a medical grade primer, the additional coating layer 16 is preferably composed of the same polymer as the at least one porous layer 20. However, the additional coating layer 16 is also preferably less porous than the at least one porous layer 20, and is more preferably substantially nonporous. "Substantially nonporous" means that the additional coating layer 16 is sufficiently impervious to prevent any appreciable interaction between the base material 14 of the structure 12 and the blood to which the device 10 will be exposed during use. The use of an additional coating layer 16 which is substantially nonporous would permit the use of a toxic or poisonous base material 14, as mentioned above. Even if the base material 14 of the structure 12 is biocompatible, however, it may be advantageous to isolate it from the blood by use of a substantially nonporous coating layer 16.
Other polymer systems that may find application within the scope of the invention include polymers derived from photopolymerizable monomers such as liquid monomers preferably having at least two cross linkable C-C (Carbon to Carbon) double bonds and being a non-gaseous addition polymerizable ethylenically unsaturated compound, having a boiling point above 100 C, at atmospheric pressure, a molecular weight of about 100-1500 and being capable of forming high molecular weight addition polymers readily. More preferably, the monomer is preferably an addition photopolymerizable polyethylenically unsaturated acrylic or methacrylic acid ester containing two or more acrylate or methacrylate groups per molecule or mixtures thereof. A few illustrative examples of such multifunctional acrylates are ethylene glycol diacrylate, ethylene glycol dimethacrylate, trimethylopropane triacrylate, trimethylopropane trimethacrylate, pentaerythritol tetraacrylate or pentaerythritol tetramethacrylate, 1,6-hexanediol dimethacrylate, and diethyleneglycol dimethacrylate.
Also useful in some special instances are monoacrylates such as n-butyl-acrylate, n-butyl methacrylate, 2-ethylhexyl acrylate, lauryl-acrylate, and 2-hydroxy-propyl acrylate. Small quantities of amides of (meth)acrylic acid such as N-methylol methacrylamide butyl ether are also suitable, N-vinyl compounds such as N-vinyl pyrrolidone, vinyl esters of aliphatic monocarboxylic acids such as vinyl oleate, vinyl ethers of diols such as butanediol-1, 4-divinyl ether and allyl ether and allyl
- 21 -ester are also suitable. Also included would be other monomers such as the reaction products of di- or polyepoxides such as butanediol-1, 4-diglycidyl ether or bisphenol A diglycidyl ether with (meth)acrylic acid. The characteristics of the photopolymerizable liquid dispersing medium can be modified for the specific purpose by a suitable selection of monomers or mixtures thereof.
Other useful polymer systems include a polymer that is biocompatible and minimizes irritation to the vessel wall when the stent is implanted. The polymer may be either a biostable or a bioabsorbable polymer depending on the desired rate of release or the desired degree of polymer stability, but a bioabsorbable polymer is preferred for this embodiment since, unlike a biostable polymer, it will not be present long after implantation to cause any adverse, chronic local response. Bioabsorbable polymers that could be used include poly(L-lactic acid), polycaprolactone, poly(lactide-co-glycolide), poly(hydroxybutyrate), poly(hydroxybutyrate-co-valerate), polydioxanone, polyorthoester, polyanhydride, poly(glycolic acid), poly(D,L-lactic acid), poly(glycolic acid-co-trimethylene carbonate), polyphosphoester, polyphosphoester urethane, poly(amino acids), cyanoacrylates, poly(trimethylene carbonate), poly(iminocarbonate), copoly(ether-esters) (e.g., PEO/PLA), polyalkylene oxalates, polyphosphazenes and biomolecules such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid. Also, biostable polymers with a relatively low chronic tissue response such as polyurethanes, silicones, and polyesters could be used and other polymers could also be used if they can be dissolved and cured or polymerized on the stent such as polyolefins, polyisobutylene and ethylene-alphaolefin copolymers; acrylic polymers and copolymers, vinyl halide polymers and copolymers, such as polyvinyl chloride;
polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile, polyvinyl ketones; polyvinyl
Other useful polymer systems include a polymer that is biocompatible and minimizes irritation to the vessel wall when the stent is implanted. The polymer may be either a biostable or a bioabsorbable polymer depending on the desired rate of release or the desired degree of polymer stability, but a bioabsorbable polymer is preferred for this embodiment since, unlike a biostable polymer, it will not be present long after implantation to cause any adverse, chronic local response. Bioabsorbable polymers that could be used include poly(L-lactic acid), polycaprolactone, poly(lactide-co-glycolide), poly(hydroxybutyrate), poly(hydroxybutyrate-co-valerate), polydioxanone, polyorthoester, polyanhydride, poly(glycolic acid), poly(D,L-lactic acid), poly(glycolic acid-co-trimethylene carbonate), polyphosphoester, polyphosphoester urethane, poly(amino acids), cyanoacrylates, poly(trimethylene carbonate), poly(iminocarbonate), copoly(ether-esters) (e.g., PEO/PLA), polyalkylene oxalates, polyphosphazenes and biomolecules such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid. Also, biostable polymers with a relatively low chronic tissue response such as polyurethanes, silicones, and polyesters could be used and other polymers could also be used if they can be dissolved and cured or polymerized on the stent such as polyolefins, polyisobutylene and ethylene-alphaolefin copolymers; acrylic polymers and copolymers, vinyl halide polymers and copolymers, such as polyvinyl chloride;
polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile, polyvinyl ketones; polyvinyl
- 22 -aromatics, such as polystyrene, polyvinyl esters, such as polyvinyl acetate; copolymers of vinyl monomers with each other and olef ins, such as ethylene-methyl methacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins, and ethylene-vinyl acetate copolymers; polyamides, such as Nylon 66 and polycaprolactam; alkyd resins, polycarbonates; polyoxymethylenes;
polyimides; polyethers; epoxy resins, polyurethanes; rayon; rayon-triacetate; cellulose, cellulose acetate, cellulose butyrate;
cellulose acetate butyrate; cellophane; cellulose nitrate;
cellulose propionate; cellulose ethers; and carboxymethyl cellulose.
While plasma deposition and vapor phase deposition may be a preferred method for applying the various coatings on the stent surfaces, other techniques may be employed. For example, a polymer solution may be applied to the stent and the solvent allowed to evaporate, thereby leaving on the stent surface a coating of the polymer and the therapeutic substance. Typically, the solution can be applied to the stent by either spraying the solution onto the stent or immersing the stent in the solution.
Whether one chooses application by immersion or application by spraying depends principally on the viscosity and surface tension of the solution, however, it has been found that spraying in a fine spray such as that available from an airbrush will provide a coating with the greatest uniformity and will provide the greatest control over the amount of coating material to be applied to the stent. In either a coating applied by spraying or by immersion, multiple application steps are generally desirable to provide improved coating uniformity and improved control over the amount of therapeutic substance to be applied to the stent.
When the layer 18 of bioactive material contains a relatively soluble material such as heparin, and when the at least one porous layer 20 is composed of parylene or a parylene derivative, the at least one porous layer 20 is at least 5,000 A thick, preferably about 5,000 to 250,000 A
thick, more preferably about 5,000 to 100,000
polyimides; polyethers; epoxy resins, polyurethanes; rayon; rayon-triacetate; cellulose, cellulose acetate, cellulose butyrate;
cellulose acetate butyrate; cellophane; cellulose nitrate;
cellulose propionate; cellulose ethers; and carboxymethyl cellulose.
While plasma deposition and vapor phase deposition may be a preferred method for applying the various coatings on the stent surfaces, other techniques may be employed. For example, a polymer solution may be applied to the stent and the solvent allowed to evaporate, thereby leaving on the stent surface a coating of the polymer and the therapeutic substance. Typically, the solution can be applied to the stent by either spraying the solution onto the stent or immersing the stent in the solution.
Whether one chooses application by immersion or application by spraying depends principally on the viscosity and surface tension of the solution, however, it has been found that spraying in a fine spray such as that available from an airbrush will provide a coating with the greatest uniformity and will provide the greatest control over the amount of coating material to be applied to the stent. In either a coating applied by spraying or by immersion, multiple application steps are generally desirable to provide improved coating uniformity and improved control over the amount of therapeutic substance to be applied to the stent.
When the layer 18 of bioactive material contains a relatively soluble material such as heparin, and when the at least one porous layer 20 is composed of parylene or a parylene derivative, the at least one porous layer 20 is at least 5,000 A thick, preferably about 5,000 to 250,000 A
thick, more preferably about 5,000 to 100,000
- 23 -A thick, and optimally about 50,000 A thick. When the at least one additional coating layer 16 is composed of parylene or a parylene derivative, the at least one additional coating is preferably about 50,000 to 500,000 A thick, more preferably about 100,000 to 500,000 A thick, and optimally about 200,000 A thick.
When the at least one layer 18 of bioactive material contains a relatively soluble material such as heparin, the at least one layer 18 preferably contains a total of about 0.1 to 4 mg of bioactive material per cm2 of the gross surface area of the structure 12. This provides a release rate for the heparin (measured in vitro) which is desirably in the range of 0.1 to 0.5 mg/cmz per day, and preferably about 0.25 mg/cmz per day, under typical blood flows through vascular stents. It should be noted that the solubility of dexamethasone can be adjusted as desired, with or without the inclusion of heparin, by mixing it with one or more of its relatively more soluble derivatives, such as dexamethasone sodium phosphate.
As shown in FIG. 2, the device 10 of the present invention is not limited to the inclusion of a single layer 18 of bioactive material. The device 10 can, for example, comprise a second layer 22 of a bioactive material posited over the structure 12. The bioactive material of the second layer 22 can be, but need not necessarily be, different from the bioactive material of the first bioactive material layer 18, only that they not be posited on the same surface of the device 10 without the intermediate porous layer 24. The use of different materials in the layers 18 and 22 allows the device 10 to perform more than a single therapeutic function.
The device 10 of the present invention can further comprise an additional porous layer 24 of the polymer posited between each of the layers 18 and 22 of bioactive material. it is reiterated that bioactive material 18 is on one surface of structure 12. The other surface may be free of bioactive material or may comprise one or more different bioactive materials. The ~178541
When the at least one layer 18 of bioactive material contains a relatively soluble material such as heparin, the at least one layer 18 preferably contains a total of about 0.1 to 4 mg of bioactive material per cm2 of the gross surface area of the structure 12. This provides a release rate for the heparin (measured in vitro) which is desirably in the range of 0.1 to 0.5 mg/cmz per day, and preferably about 0.25 mg/cmz per day, under typical blood flows through vascular stents. It should be noted that the solubility of dexamethasone can be adjusted as desired, with or without the inclusion of heparin, by mixing it with one or more of its relatively more soluble derivatives, such as dexamethasone sodium phosphate.
As shown in FIG. 2, the device 10 of the present invention is not limited to the inclusion of a single layer 18 of bioactive material. The device 10 can, for example, comprise a second layer 22 of a bioactive material posited over the structure 12. The bioactive material of the second layer 22 can be, but need not necessarily be, different from the bioactive material of the first bioactive material layer 18, only that they not be posited on the same surface of the device 10 without the intermediate porous layer 24. The use of different materials in the layers 18 and 22 allows the device 10 to perform more than a single therapeutic function.
The device 10 of the present invention can further comprise an additional porous layer 24 of the polymer posited between each of the layers 18 and 22 of bioactive material. it is reiterated that bioactive material 18 is on one surface of structure 12. The other surface may be free of bioactive material or may comprise one or more different bioactive materials. The ~178541
- 24 -additional porous layer 24 can give the bioactive materials in the layers 18 and 22 different release rates. Simultaneously, or alternatively, the device 10 may employ bioactive materials in the two layers 18 and 22 which are different from one another and have different solubilities. In such a case, it is advantageous and preferred to position the layer 22 containing the less soluble bioactive material above the layer 18 containing the more soluble bioactive material. Alternatively, the bioactive material 18 may be contained in holes, wells, slots and the like occurring within the stent surface as illustrated in FIGs. 8-10 and will further be discussed in greater detail.
For example, when the structure 12 of the device 10 is configured as a vascular stent, it is advantageous for the at least one layer 18 to contain relatively soluble heparin, and the second layer 22 to contain relatively less soluble dexamethasone.
Unexpectedly, the heparin promotes the release of the dexamethasone, increasing its release rate many times over the release rate of dexamethasone in the absence of heparin. The release rate of the heparin is also lowered, somewhat less dramatically than the increase of the dexamethasone release rate.
More particularly, when dexamethasone is disposed by itself beneath a porous parylene layer 20 dimensioned as disclosed above, its release rate is negligible; an adequate release rate is obtained only when the thickness of the porous layer 20 is reduced by a factor of ten or more. In contrast, when a layer 22 of dexamethasone is disposed over a layer 18 of heparin, and beneath a porous parylene layer 20 dimensioned as above, the dexamethasone may be released at a desirable rate of about 1 to 10 /.cg/cm2 per day. Moreover, and even more unexpectedly, this increased release rate for the dexamethasone is thought to be maintained even after all of the heparin has been released from the layer 18.
The bioactive material layers 18 and/or 22 are applied to the device 10 independent of the application of the porous polymer layers 20 and/or 24. Any mixing of a bioactive material from the
For example, when the structure 12 of the device 10 is configured as a vascular stent, it is advantageous for the at least one layer 18 to contain relatively soluble heparin, and the second layer 22 to contain relatively less soluble dexamethasone.
Unexpectedly, the heparin promotes the release of the dexamethasone, increasing its release rate many times over the release rate of dexamethasone in the absence of heparin. The release rate of the heparin is also lowered, somewhat less dramatically than the increase of the dexamethasone release rate.
More particularly, when dexamethasone is disposed by itself beneath a porous parylene layer 20 dimensioned as disclosed above, its release rate is negligible; an adequate release rate is obtained only when the thickness of the porous layer 20 is reduced by a factor of ten or more. In contrast, when a layer 22 of dexamethasone is disposed over a layer 18 of heparin, and beneath a porous parylene layer 20 dimensioned as above, the dexamethasone may be released at a desirable rate of about 1 to 10 /.cg/cm2 per day. Moreover, and even more unexpectedly, this increased release rate for the dexamethasone is thought to be maintained even after all of the heparin has been released from the layer 18.
The bioactive material layers 18 and/or 22 are applied to the device 10 independent of the application of the porous polymer layers 20 and/or 24. Any mixing of a bioactive material from the
- 25 -layers 18 and/or 22 into the porous layers 20 and/or 24, prior to introducing the device 10 into the vascular system of the patient, is unintentional and merely incidental. This gives significantly more control over the release rate of the bioactive material than the simple dispersal of a bioactive material in a polymeric layer.
The device 10 need not include the additional porous layer 24 when two or more layers 18 and 22 of bioactive material are present. As shown in FIG. 3, the layers 18 and 22 do not have to be separated by a porous layer, but can instead lie directly against one another. It is still advantageous in this embodiment to position the layer 22 containing the relatively less soluble bioactive material above the layer 18 containing the relatively more soluble bioactive material.
Whether or not the additional porous layer 24 is present, it is preferred that the layers 18 and 22 contain about 0.05 to 2.0 mg of each of heparin and dexamethasone, respectively, per 1 cmz of the gross surface area of the structure 12. The total amount of bioactive material posited in the layers 18 and 22 over the structure 12 is thus preferably in the range of about 0.1 to 10 mg/cm2.
Some dexamethasone derivatives, such as dexamethasone sodium phosphate, are substantially more soluble than dexamethasone itself. If a more soluble dexamethasone derivative is used as the bioactive material in the device 10 of the present invention, the thickness of the at least one porous layer 20 (and of the additional porous layer 24) should be adjusted accordingly.
The particular structure of the device 10 as disclosed may be adapted to specific uses in a variety of ways. For example, the device 10 may include further layers of the same or different bioactive materials. These additional layers of bioactive material may or may not be separated by additional porous layers, as convenient or desired. Alternatively, additional porous layers may separate only some of the additional layers of bioactive material. Moreover, one bioactive material may be placed on one
The device 10 need not include the additional porous layer 24 when two or more layers 18 and 22 of bioactive material are present. As shown in FIG. 3, the layers 18 and 22 do not have to be separated by a porous layer, but can instead lie directly against one another. It is still advantageous in this embodiment to position the layer 22 containing the relatively less soluble bioactive material above the layer 18 containing the relatively more soluble bioactive material.
Whether or not the additional porous layer 24 is present, it is preferred that the layers 18 and 22 contain about 0.05 to 2.0 mg of each of heparin and dexamethasone, respectively, per 1 cmz of the gross surface area of the structure 12. The total amount of bioactive material posited in the layers 18 and 22 over the structure 12 is thus preferably in the range of about 0.1 to 10 mg/cm2.
Some dexamethasone derivatives, such as dexamethasone sodium phosphate, are substantially more soluble than dexamethasone itself. If a more soluble dexamethasone derivative is used as the bioactive material in the device 10 of the present invention, the thickness of the at least one porous layer 20 (and of the additional porous layer 24) should be adjusted accordingly.
The particular structure of the device 10 as disclosed may be adapted to specific uses in a variety of ways. For example, the device 10 may include further layers of the same or different bioactive materials. These additional layers of bioactive material may or may not be separated by additional porous layers, as convenient or desired. Alternatively, additional porous layers may separate only some of the additional layers of bioactive material. Moreover, one bioactive material may be placed on one
- 26 -portion of the structure 12 of the device 10, and another bioactive material placed on a different portion of the structure 12 of the device 10.
Alternatively, the device 10 need not include the additional coating layer 16 at all. Such a configuration is shown in FIG. 4, in which the bioactive material layer 18 is posited directly atop the base material 14 of the structure 12. In such a case, it may be highly advantageous to surface process or surface activate the base material 14, to promote the deposition or adhesion of the bioactive material on the base material 14, especially before the depositing of the at least one porous layer 20. Surface processing and surface activation can also selectively alter the release rate of the bioactive material.
Such processing can also be used to promote the deposition or adhesion of the additional coating layer 16, if present, on the base material 14. The additional coating layer 16 itself, or any second or additional porous layer 24 itself, can similarly be processed to promote the deposition or adhesion of the bioactive material layer 18, or to further control the release rate of the bioactive material.
Useful methods of surface processing can include any of a variety of such procedures, including: cleaning; physical modifications such as etching, drilling, cutting, or abrasion; and chemical modifications such as solvent treatment, the application of primer coatings, the application of surfactants, plasma treatment, ion bombardment and covalent bonding.
It has been found particularly advantageous to plasma treat the additional coating layer 16 (for example, of parylene) before depositing the bioactive material layer 18 atop it. The plasma treatment improves the adhesion of the bioactive material, increases the amount of bioactive material that can be deposited, and allows the bioactive material to be deposited in a more uniform layer. Indeed, it is very difficult to deposit a hygroscopic agent such as heparin on an unmodified parylene
Alternatively, the device 10 need not include the additional coating layer 16 at all. Such a configuration is shown in FIG. 4, in which the bioactive material layer 18 is posited directly atop the base material 14 of the structure 12. In such a case, it may be highly advantageous to surface process or surface activate the base material 14, to promote the deposition or adhesion of the bioactive material on the base material 14, especially before the depositing of the at least one porous layer 20. Surface processing and surface activation can also selectively alter the release rate of the bioactive material.
Such processing can also be used to promote the deposition or adhesion of the additional coating layer 16, if present, on the base material 14. The additional coating layer 16 itself, or any second or additional porous layer 24 itself, can similarly be processed to promote the deposition or adhesion of the bioactive material layer 18, or to further control the release rate of the bioactive material.
Useful methods of surface processing can include any of a variety of such procedures, including: cleaning; physical modifications such as etching, drilling, cutting, or abrasion; and chemical modifications such as solvent treatment, the application of primer coatings, the application of surfactants, plasma treatment, ion bombardment and covalent bonding.
It has been found particularly advantageous to plasma treat the additional coating layer 16 (for example, of parylene) before depositing the bioactive material layer 18 atop it. The plasma treatment improves the adhesion of the bioactive material, increases the amount of bioactive material that can be deposited, and allows the bioactive material to be deposited in a more uniform layer. Indeed, it is very difficult to deposit a hygroscopic agent such as heparin on an unmodified parylene
- 27 -surf ace, which is hydrophobic and poorly wettable. However, plasma treatment renders the parylene surface wettable, allowing heparin to be easily deposited on it.
Any of the porous polymer layers 20 and 24 may also be surface processed by any of the methods mentioned above to alter the release rate of the bioactive material or materials, and/or otherwise improve the biocompatibility of the surface of the layers. For example, the application of an overcoat of polyethylene oxide, phosphatidylcholine or a covalently bound bioactive material, e.g., covalently attached heparin to the layers 20 and/or 24 could render the surface of the layers more blood compatible. Similarly, the plasma treatment or application of a hydrogel coating to the layers 20 and/or 24 could alter their surface energies, preferably providing surface energies in the range of 20 to 30 dyne/cm, thereby rendering their surfaces more biocompatible.
Referring now to FIG. 5, an embodiment of the device 10 is there shown in which a mechanical bond or connector 26 is provided between (a) any one of the porous layers 20 and 24, and (b) any or all of the other of the porous layers 20 and 24, the additional coating layer 16 and the base material 14. The connector 26 reliably secures the layers 16, 20 and/or 24 to each other, and or to the base material 14. The connector 26 lends structural integrity to the device 10, particularly after the bioactive material layer or layers 18 and/or 20 have been fully released into the patient.
For simplicity, the connector 26 is shown in FIG. 5 as a plurality of projections of the base material 14 securing a single porous layer 20 to the base material 14. The connector 26 may alternatively extend from the porous layer 20, through the bioactive material layer 18, and to the base material 14. In either case, a single layer 18 of bioactive material, divided into several segments by the connector 26, is posited between the porous layer 20 and the base material 14. The connectors can also
Any of the porous polymer layers 20 and 24 may also be surface processed by any of the methods mentioned above to alter the release rate of the bioactive material or materials, and/or otherwise improve the biocompatibility of the surface of the layers. For example, the application of an overcoat of polyethylene oxide, phosphatidylcholine or a covalently bound bioactive material, e.g., covalently attached heparin to the layers 20 and/or 24 could render the surface of the layers more blood compatible. Similarly, the plasma treatment or application of a hydrogel coating to the layers 20 and/or 24 could alter their surface energies, preferably providing surface energies in the range of 20 to 30 dyne/cm, thereby rendering their surfaces more biocompatible.
Referring now to FIG. 5, an embodiment of the device 10 is there shown in which a mechanical bond or connector 26 is provided between (a) any one of the porous layers 20 and 24, and (b) any or all of the other of the porous layers 20 and 24, the additional coating layer 16 and the base material 14. The connector 26 reliably secures the layers 16, 20 and/or 24 to each other, and or to the base material 14. The connector 26 lends structural integrity to the device 10, particularly after the bioactive material layer or layers 18 and/or 20 have been fully released into the patient.
For simplicity, the connector 26 is shown in FIG. 5 as a plurality of projections of the base material 14 securing a single porous layer 20 to the base material 14. The connector 26 may alternatively extend from the porous layer 20, through the bioactive material layer 18, and to the base material 14. In either case, a single layer 18 of bioactive material, divided into several segments by the connector 26, is posited between the porous layer 20 and the base material 14. The connectors can also
28 -function to partition the different bioactive agents into different regions of the device's surface.
The connector 26 may be provided in a variety of ways.
For example, the connector 26 can be formed as a single piece with the base material 14 during its initial fabrication or molding into the structure 12. The connector 26 can instead be formed as a distinct element, such as a bridge, strut, pin or stud added to an existing structure 12. The connector 26 can also be formed as a built-up land, shoulder, plateau, pod or pan on the base material 14. Alternatively, a portion of the base material 14 between the desired locations of plural connectors 26 may be removed by etching, mechanical abrasion, or the like, and the bioactive material layer 18 deposited between them. The connector 26 can also be formed so as to extend downwards towards the base material 14, by wiping or etching away a portion of a previously applied bioactive material layer 18, and allowing the porous layer to deposit by vapor deposition or plasma deposition directly on the bare portions of the base material 14. Other ways to expose a portion of the base material 14 to direct connection to 20 the porous layer 20 will be evident to those skilled in this area.
In another preferred embodiment, as illustrated in FIGs.
6A, 6B and 7, a bioactive material 18 is posited on the one surface of base material 14 making up structure 12 in FIG. 6A.
FIG. 7 shows a stent 10 in its flat or planar state prior to being coiled and showing porous layer 20 applied to its outermost surface. FIGs. 6A and 6B are section views along line 6-6 of FIG.
7. The bioactive material 18 posited on the one surface of base material 14 in FIG. 6A may be a number of different therapeutic and/or diagnostic agents. For example, the device 10 may be a stent which is placed in the body of a patient near a tumor to deliver a chemotherapeutic agent, such as tamoxifen citrate or Taxol , directly to the tumor. A porous layer 20 is posited over the bioactive material 18 to provide a smoother surface as well as a more controlled release of the bioactive material 18. As
The connector 26 may be provided in a variety of ways.
For example, the connector 26 can be formed as a single piece with the base material 14 during its initial fabrication or molding into the structure 12. The connector 26 can instead be formed as a distinct element, such as a bridge, strut, pin or stud added to an existing structure 12. The connector 26 can also be formed as a built-up land, shoulder, plateau, pod or pan on the base material 14. Alternatively, a portion of the base material 14 between the desired locations of plural connectors 26 may be removed by etching, mechanical abrasion, or the like, and the bioactive material layer 18 deposited between them. The connector 26 can also be formed so as to extend downwards towards the base material 14, by wiping or etching away a portion of a previously applied bioactive material layer 18, and allowing the porous layer to deposit by vapor deposition or plasma deposition directly on the bare portions of the base material 14. Other ways to expose a portion of the base material 14 to direct connection to 20 the porous layer 20 will be evident to those skilled in this area.
In another preferred embodiment, as illustrated in FIGs.
6A, 6B and 7, a bioactive material 18 is posited on the one surface of base material 14 making up structure 12 in FIG. 6A.
FIG. 7 shows a stent 10 in its flat or planar state prior to being coiled and showing porous layer 20 applied to its outermost surface. FIGs. 6A and 6B are section views along line 6-6 of FIG.
7. The bioactive material 18 posited on the one surface of base material 14 in FIG. 6A may be a number of different therapeutic and/or diagnostic agents. For example, the device 10 may be a stent which is placed in the body of a patient near a tumor to deliver a chemotherapeutic agent, such as tamoxifen citrate or Taxol , directly to the tumor. A porous layer 20 is posited over the bioactive material 18 to provide a smoother surface as well as a more controlled release of the bioactive material 18. As
- 29 -further illustrated in FIG. 6A, the opposite surface of the device may have, for example, heparin 18' covalently bonded to porous layer 20, particularly where this surface faces, for example, the lumen of a blood vessel, to provide antithrombotic effect and blood compatibility. It is pointed out, as has been discussed herein, a third but different bioactive material may be posited (not shown) on the opposite surface of base material 14 from the first bioactive material 18 and on the same side of base material 14 as the covalently bound heparin or any other bioactive material including other covalently bound bioactive materials and separated by porous layer 20.
A variation of the embodiment shown in FIG. 6A is illustrated in FIG 63, where two bioactive materials 18 and 18' are posited on the same surface of base material 14 of structure 12. A porous layer 20 may be deposited over the bioactive materials 18 and 18' as well as the bioactive-material-free surface of based material 14. This embodiment illustrates a situation where it may be desirable to deliver two agents to the tissue to which the particular surface of device 10 is exposed, e.g., an antiinflammatory agent and an antiviral agent. Moreover, the opposite surface of the device free of bioactive material is available for positing one or more bioactive materials or therapeutic agents, e.g., an antithrombotic agent.
As has been previously discussed, multiple layers of bioactive materials and porous layers may be applied to the device 10 where the limiting factors become the total thickness of the device, the adhesion of multiple layers and the like.
In still another embodiment of the present invention, the device of the present invention includes apertures within the device for containing the bioactive material. This embodiment is illustrated in FIGs. 8, 9, 10A, 10B, lOC and 10D. FIG. 8 shows an arm of the stent of FIG. 7 wherein the arm includes holes 28 into which a bioactive material is contained. FIG. 9 shows a section of the arm of the stent along lines 9-9 of FIG. 8.
A variation of the embodiment shown in FIG. 6A is illustrated in FIG 63, where two bioactive materials 18 and 18' are posited on the same surface of base material 14 of structure 12. A porous layer 20 may be deposited over the bioactive materials 18 and 18' as well as the bioactive-material-free surface of based material 14. This embodiment illustrates a situation where it may be desirable to deliver two agents to the tissue to which the particular surface of device 10 is exposed, e.g., an antiinflammatory agent and an antiviral agent. Moreover, the opposite surface of the device free of bioactive material is available for positing one or more bioactive materials or therapeutic agents, e.g., an antithrombotic agent.
As has been previously discussed, multiple layers of bioactive materials and porous layers may be applied to the device 10 where the limiting factors become the total thickness of the device, the adhesion of multiple layers and the like.
In still another embodiment of the present invention, the device of the present invention includes apertures within the device for containing the bioactive material. This embodiment is illustrated in FIGs. 8, 9, 10A, 10B, lOC and 10D. FIG. 8 shows an arm of the stent of FIG. 7 wherein the arm includes holes 28 into which a bioactive material is contained. FIG. 9 shows a section of the arm of the stent along lines 9-9 of FIG. 8.
- 30 -Bioactive material 18 is contained within the hole 28 where the base material 14 contains coating 16 and further where porous layer 20 forms the outer most layer for the bioactive material 18 to diffuse through. In an alternative embodiment, wells 28' may be cut, etched or stamped into the base material 14 of the device in which a bioactive material 18 may be contained. This embodiment is illustrated in FIGs. 10A, lOB, lOC and lOD which are sectional FIGs. taken along line 10-10 of FIG. 8. The wells 28' may also be in the form of slots or grooves in the surface of the base material 14 of the medical device. This aspect of the invention provides the advantage of better controlling the total amount of the bioactive material 18 to be released as well as the rate at which it is released. For example, a V-shape well 28', as illustrated in FIG. lOD, will contain less quantity of bioactive material 18 and release the material at geometric rate as compared to a square shaped well 28', as illustrated in FIG.
10B, which will have a more uniform, linear release rate.
The holes, wells, slots, grooves and the like, described above, may be formed in the surface of the device 10 by a variety of techniques. For example, such techniques include drilling or cutting by utilizing lasers, electron-beam machining and the like or employing photoresist procedures and etching the desired apertures.
All the bioactive materials discussed above that may be coated on the surface of the device 10 may be used to be contained within the apertures of this aspect of the invention. Likewise, layers of bioactive materials and porous layers may be applied and built up on the exterior surfaces of the device as described previously with regard to other aspects of the invention, e.g., heparin, may be covalently bound to one surface of the device illustrated in FIG. 9.
The method of making the device 10 according to the present invention may now be understood. In its simplest form, = the method comprises the steps of depositing the at least one
10B, which will have a more uniform, linear release rate.
The holes, wells, slots, grooves and the like, described above, may be formed in the surface of the device 10 by a variety of techniques. For example, such techniques include drilling or cutting by utilizing lasers, electron-beam machining and the like or employing photoresist procedures and etching the desired apertures.
All the bioactive materials discussed above that may be coated on the surface of the device 10 may be used to be contained within the apertures of this aspect of the invention. Likewise, layers of bioactive materials and porous layers may be applied and built up on the exterior surfaces of the device as described previously with regard to other aspects of the invention, e.g., heparin, may be covalently bound to one surface of the device illustrated in FIG. 9.
The method of making the device 10 according to the present invention may now be understood. In its simplest form, = the method comprises the steps of depositing the at least one
- 31 -layer 18 of bioactive material over the structure 12, followed by depositing the at least one porous layer 20, preferably by vapor deposition or plasma deposition, over the at least one bioactive material layer 18 on the one surface of structure 12. The at least one porous layer 20 being composed of a biocompatible polymer and being of a thickness adequate to provide a controlled release of the bioactive material. Preferably, the at least one additional coating layer 16 is first posited by vapor deposition directly on the base material 14 of the structure 12. Such deposition is carried out by preparing or obtaining di-p-xylylene or a derivative thereof, sublimating and cracking the di-p-xylylene or derivative to yield monomeric p-xylylene or a monomeric derivative, and allowing the monomer to simultaneously condense on and polymerize over the base material 14. The deposition step is carried out under vacuum, and the base material 14 maintained at or near room temperature during the deposition step. The deposition is carried out in the absence of any solvent or catalyst for the polymer, and in the absence of any other action to aid polymerization. One preferred derivative for carrying out the deposition step is dichloro-di-p-xylylene. The parylene or parylene derivative is preferably applied at the thickness disclosed above, to yield a coating layer 16 which is substantially nonporous, but in any event less porous than the at least one porous layer 20 to be applied. If required by the composition of the coating layer 16, the layer 16 is then surface processed in an appropriate manner, for example, by plasma treatment as disclosed above.
The at least one layer 18 of the desired bioactive material or materials is then applied to the one surface of the structure 12, and in particular, onto the additional coating layer 16. This application step can be carried out,in any of a variety of convenient ways, such as by dipping, rolling, brushing or spraying a fluid mixture of the bioactive material onto the additional coating layer 16, or by electrostatic deposition of
The at least one layer 18 of the desired bioactive material or materials is then applied to the one surface of the structure 12, and in particular, onto the additional coating layer 16. This application step can be carried out,in any of a variety of convenient ways, such as by dipping, rolling, brushing or spraying a fluid mixture of the bioactive material onto the additional coating layer 16, or by electrostatic deposition of
- 32 -either a fluid mixture or dry powder of the bioactive material, or by any other appropriate method. Different bioactive agents may be applied to different sections or surfaces of the device.
It can be particularly convenient to apply a mixture of the bioactive material or materials and a volatile fluid over the structure, and then remove the fluid in any suitable way, for example, by allowing it to evaporate. When heparin and/or dexamethasone or its derivatives serve as the bioactive material(s), the fluid is preferably ethyl alcohol. The bioactive material is preferably applied in an amount as disclosed above.
Other methods of depositing the bioactive material layer 18 over the structure 12 would be equally useful. Without regard to the method of application, however, what is important is that the bioactive material need only be physically held in place until the porous layer 20 is deposited over it. This can avoid the use of carriers, surfactants, chemical binding and other such methods often employed to hold a bioactive agent on other devices. The additives used in such methods may be toxic, or the additives or methods may alter or degrade the bioactive agent, rendering it less effective, or even toxic itself. Nonetheless, if desired these other methods may also be employed to deposit the bioactive material layer 18 of the present invention.
The bioactive material may, of course, be deposited on the one surface of the structure 12 as a smooth film or as a layer of particles. Moreover, multiple but different bioactive materials may be deposited in a manner that different surfaces of the device contain the different bioactive agents. In the latter case, the particle size may affect the properties or characteristics of the device 10, such as the smoothness of the uppermost porous coating 20, the profile of the device 10, the surface area over which the bioactive material layer 18 is disposed, the release rate of the bioactive material, the formation of bumps or irregularities in the bioactive material layer 18, the uniformity and strength of adhesion of the bioactive material layer 18, and other properties
It can be particularly convenient to apply a mixture of the bioactive material or materials and a volatile fluid over the structure, and then remove the fluid in any suitable way, for example, by allowing it to evaporate. When heparin and/or dexamethasone or its derivatives serve as the bioactive material(s), the fluid is preferably ethyl alcohol. The bioactive material is preferably applied in an amount as disclosed above.
Other methods of depositing the bioactive material layer 18 over the structure 12 would be equally useful. Without regard to the method of application, however, what is important is that the bioactive material need only be physically held in place until the porous layer 20 is deposited over it. This can avoid the use of carriers, surfactants, chemical binding and other such methods often employed to hold a bioactive agent on other devices. The additives used in such methods may be toxic, or the additives or methods may alter or degrade the bioactive agent, rendering it less effective, or even toxic itself. Nonetheless, if desired these other methods may also be employed to deposit the bioactive material layer 18 of the present invention.
The bioactive material may, of course, be deposited on the one surface of the structure 12 as a smooth film or as a layer of particles. Moreover, multiple but different bioactive materials may be deposited in a manner that different surfaces of the device contain the different bioactive agents. In the latter case, the particle size may affect the properties or characteristics of the device 10, such as the smoothness of the uppermost porous coating 20, the profile of the device 10, the surface area over which the bioactive material layer 18 is disposed, the release rate of the bioactive material, the formation of bumps or irregularities in the bioactive material layer 18, the uniformity and strength of adhesion of the bioactive material layer 18, and other properties
- 33 -or characteristics. For example, it has been useful to employ micronized bioactive materials, that is, materials which have been processed to a small particle size, typically less than 104m in diameter. However, the bioactive material may also be deposited as microencapsulated particles, dispersed in liposomes, adsorbed onto or absorbed into small carrier particles, or the like.
In still another embodiment according to the present invention, the bioactive material may be posited on the one surface of structure 12 in a specific geometric pattern. For example, the tips or arms of a stent may be free of bioactive material, or the bioactive material may be applied in parallel lines, particularly where two or more bioactive materials are applied to the same surface.
In any event, once the bioactive material layer 18 is in place, the at least one porous layer 20 is then applied over the at least one bioactive material layer 18 in the same manner as for the application of the at least one additional coating 16. A
polymer such as parylene or a parylene derivative is applied at the lesser thickness disclosed above, however, so as to yield the at least one porous layer 20.
Any other layers, such as the second bioactive material layer 22 or the additional porous layer 24, are applied in the appropriate order and in the same manner as disclosed above. The steps of the method are preferably carried out with any of the bioactive materials, structures, and base materials disclosed above.
Of course, polyimide may be deposited as any or all of the porous and additional coating layers 20, 24 and/or 16 by vapor deposition in a manner similar to that disclosed above for parylene and its derivatives. Techniques for the plasma deposition of polymers such as poly(ethylene oxide), poly(ethylene glycol), poly(propylene oxide), silicone, or a polymer of methane, tetrafluoroethylene or tetramethyl-disiloxane on other objects are
In still another embodiment according to the present invention, the bioactive material may be posited on the one surface of structure 12 in a specific geometric pattern. For example, the tips or arms of a stent may be free of bioactive material, or the bioactive material may be applied in parallel lines, particularly where two or more bioactive materials are applied to the same surface.
In any event, once the bioactive material layer 18 is in place, the at least one porous layer 20 is then applied over the at least one bioactive material layer 18 in the same manner as for the application of the at least one additional coating 16. A
polymer such as parylene or a parylene derivative is applied at the lesser thickness disclosed above, however, so as to yield the at least one porous layer 20.
Any other layers, such as the second bioactive material layer 22 or the additional porous layer 24, are applied in the appropriate order and in the same manner as disclosed above. The steps of the method are preferably carried out with any of the bioactive materials, structures, and base materials disclosed above.
Of course, polyimide may be deposited as any or all of the porous and additional coating layers 20, 24 and/or 16 by vapor deposition in a manner similar to that disclosed above for parylene and its derivatives. Techniques for the plasma deposition of polymers such as poly(ethylene oxide), poly(ethylene glycol), poly(propylene oxide), silicone, or a polymer of methane, tetrafluoroethylene or tetramethyl-disiloxane on other objects are
- 34 -well-known, and these techniques may be useful in the practice of the present invention.
Another technique for controlling the release of the bioactive material may include depositing monodispersed polymeric particles, i.e., referred to as porogens, on the surface of the device 10 comprising one or more bioactive materials prior to deposition of porous layer 20. After the porous layer 20 is deposited and cured, the porogens may be dissolved away with the appropriate solvent, leaving a cavity or pore in the outer coating to facilitate the passage of the underlying bioactive materials.
The method of using the device 10 of the present invention in medically treating a human or veterinary patient can now be easily understood as well. The method of the present invention is an improvement over previous methods which include the step of inserting into a patient an implantable vascular device 10, the device 10 comprising a structure 12 adapted for introduction into the vascular system of a patient, and the structure 12 being composed of a base material 14. The method according to the present invention comprises the preliminary steps of depositing at least one layer 18 of a bioactive material on one surface of the structure 12, followed by depositing at least one porous layer 20 over the at least one bioactive material layer 18, the porous layer 20 being composed of a polymer and having a thickness adequate to provide a controlled release of the bioactive material when the device 10 is positioned in the patient's vascular system.
The method can further entail carrying out the two depositing steps with the various embodiments of the device 10 disclosed above, in accordance with the method of making the device 10 disclosed above. More particularly, the step of depositing the at least one porous layer 20 can comprise polymerizing the at least one layer 20 from a monomer vapor, preferably a vapor of parylene or a parylene derivative, free of any solvent or catalyst. The method can also comprise the step
Another technique for controlling the release of the bioactive material may include depositing monodispersed polymeric particles, i.e., referred to as porogens, on the surface of the device 10 comprising one or more bioactive materials prior to deposition of porous layer 20. After the porous layer 20 is deposited and cured, the porogens may be dissolved away with the appropriate solvent, leaving a cavity or pore in the outer coating to facilitate the passage of the underlying bioactive materials.
The method of using the device 10 of the present invention in medically treating a human or veterinary patient can now be easily understood as well. The method of the present invention is an improvement over previous methods which include the step of inserting into a patient an implantable vascular device 10, the device 10 comprising a structure 12 adapted for introduction into the vascular system of a patient, and the structure 12 being composed of a base material 14. The method according to the present invention comprises the preliminary steps of depositing at least one layer 18 of a bioactive material on one surface of the structure 12, followed by depositing at least one porous layer 20 over the at least one bioactive material layer 18, the porous layer 20 being composed of a polymer and having a thickness adequate to provide a controlled release of the bioactive material when the device 10 is positioned in the patient's vascular system.
The method can further entail carrying out the two depositing steps with the various embodiments of the device 10 disclosed above, in accordance with the method of making the device 10 disclosed above. More particularly, the step of depositing the at least one porous layer 20 can comprise polymerizing the at least one layer 20 from a monomer vapor, preferably a vapor of parylene or a parylene derivative, free of any solvent or catalyst. The method can also comprise the step
- 35 -of depositing the at least one additional coating layer 16 between the structure 12 and the at least one bioactive material layer 18.
The method of treatment according to the present invention is completed by inserting the device 10 into the vascular system of the patient. The at least one porous layer 20 and any additional porous layers 24 automatically release the bioactive material or materials in a controlled fashion into the patient.
A different and third bioactive material is posited on the bioactive-material-free side of structure and further having porous layer posited over the first and third bioactive materials; and wherein the second bioactive material forming the outermost layer is covalent heparin bound to porous layer.
The stent structure comprises either a single bioactive material on one surface of said structure or different bioactive materials on the different surfaces of the stent structure with the porous layer over said bioactive material or materials and said second bioactive material forms the outermost layer over the porous layer.
The bioactive material layer is deposited by a process selected from the group consisting of adsorption, absorption, vapor phase deposition, plasma deposition, chemically binding to the surface of the device, utilizing surfactants as an adhesion medium, electrode position, and combinations thereof.
The structure is biocompatible and is configured as at least one of a stent, a vascular graft, another graft, a vascular graft in combination with a stent, heart valve, an orthopedic device, appliance, implant, replacement, or portion thereof; or a portion of any of these.
- 35a -The remaining details of the method of medical treatment are the same as those disclosed with respect to the method of making the device 10 of the present invention; for the sake of brevity, they need not be repeated here.
In view of the disclosure above, it is clear that the present invention provides an implantable medical device which achieves precise control over the release of one or more bioactive materials contained in the device. Moreover, the polyimide, parylene, parylene derivative or other polymeric layers 16, 20 and/or 24 can be remarkably thin, in comparison to the thicknesses required for other polymer layers. The bulk or substantial majority of the overall coating on the structure 12 can therefore consist of bioactive material.
This allows the supply of relatively large quantities of bioactive material to the patient, much greater than the amounts supplied by prior devices. These quantities of bioactive material can be supplied to any of a wide variety of locations within a patient during or after the performance of a medical procedure, but are especially useful for preventing abrupt closure and/or restenosis of a blood vessel by the delivery of an antithrombic or other medication to the region of it which has been opened by PTA. The invention permits the release rate of a bioactive material to be carefully controlled over both the short and long terms. Most importantly, any degradation of the bioactive material which might otherwise occur by other polymer coating techniques is avoided.
The other details of the construction or composition of the various elements of the disclosed embodiment of the present ..... 2178541
The method of treatment according to the present invention is completed by inserting the device 10 into the vascular system of the patient. The at least one porous layer 20 and any additional porous layers 24 automatically release the bioactive material or materials in a controlled fashion into the patient.
A different and third bioactive material is posited on the bioactive-material-free side of structure and further having porous layer posited over the first and third bioactive materials; and wherein the second bioactive material forming the outermost layer is covalent heparin bound to porous layer.
The stent structure comprises either a single bioactive material on one surface of said structure or different bioactive materials on the different surfaces of the stent structure with the porous layer over said bioactive material or materials and said second bioactive material forms the outermost layer over the porous layer.
The bioactive material layer is deposited by a process selected from the group consisting of adsorption, absorption, vapor phase deposition, plasma deposition, chemically binding to the surface of the device, utilizing surfactants as an adhesion medium, electrode position, and combinations thereof.
The structure is biocompatible and is configured as at least one of a stent, a vascular graft, another graft, a vascular graft in combination with a stent, heart valve, an orthopedic device, appliance, implant, replacement, or portion thereof; or a portion of any of these.
- 35a -The remaining details of the method of medical treatment are the same as those disclosed with respect to the method of making the device 10 of the present invention; for the sake of brevity, they need not be repeated here.
In view of the disclosure above, it is clear that the present invention provides an implantable medical device which achieves precise control over the release of one or more bioactive materials contained in the device. Moreover, the polyimide, parylene, parylene derivative or other polymeric layers 16, 20 and/or 24 can be remarkably thin, in comparison to the thicknesses required for other polymer layers. The bulk or substantial majority of the overall coating on the structure 12 can therefore consist of bioactive material.
This allows the supply of relatively large quantities of bioactive material to the patient, much greater than the amounts supplied by prior devices. These quantities of bioactive material can be supplied to any of a wide variety of locations within a patient during or after the performance of a medical procedure, but are especially useful for preventing abrupt closure and/or restenosis of a blood vessel by the delivery of an antithrombic or other medication to the region of it which has been opened by PTA. The invention permits the release rate of a bioactive material to be carefully controlled over both the short and long terms. Most importantly, any degradation of the bioactive material which might otherwise occur by other polymer coating techniques is avoided.
The other details of the construction or composition of the various elements of the disclosed embodiment of the present ..... 2178541
- 36 -invention are not believed to be critical to the achievement of the advantages of the present invention, so long as the elements possess the strength or flexibility needed for them to perform as disclosed. The selection of these and other details of construction are believed to be well within the ability of one of ordinary skills in this area, in view of the present disclosure.
Industrial Applicability The present invention is useful in the performance of vascular surgical procedures, and therefore finds applicability in human and veterinary medicine.
It is to be understood, however, that the above-described device is merely an illustrative embodiment of the principles of this invention, and that other devices and methods for using them may be devised by those skilled in the art, without departing from the spirit and scope of the invention. It is also to be understood that the invention is directed to embodiments both comprising and consisting of the disclosed parts. It is contemplated that only part of a device need be coated.
Furthermore, different parts of the device can be coated with different bioactive materials or coating layers. It is also contemplated that different sides or regions of the same part of a device can be coated with different bioactive materials or coating layers.
$ioactive Material It is intended that the term bioactive material include any material that is molecularly interactive with the fluids, cells, proteins or tissues of an animal including humans to augment the diagnosis, treatment or prevention of any physiologic or pathologic condition. It is further intended that this term includes therapeutic and diagnostic agents such as, for example,
Industrial Applicability The present invention is useful in the performance of vascular surgical procedures, and therefore finds applicability in human and veterinary medicine.
It is to be understood, however, that the above-described device is merely an illustrative embodiment of the principles of this invention, and that other devices and methods for using them may be devised by those skilled in the art, without departing from the spirit and scope of the invention. It is also to be understood that the invention is directed to embodiments both comprising and consisting of the disclosed parts. It is contemplated that only part of a device need be coated.
Furthermore, different parts of the device can be coated with different bioactive materials or coating layers. It is also contemplated that different sides or regions of the same part of a device can be coated with different bioactive materials or coating layers.
$ioactive Material It is intended that the term bioactive material include any material that is molecularly interactive with the fluids, cells, proteins or tissues of an animal including humans to augment the diagnosis, treatment or prevention of any physiologic or pathologic condition. It is further intended that this term includes therapeutic and diagnostic agents such as, for example,
- 37 -drugs, vaccines, hormones, steroids, proteins, previously described agents, complexing agents, salts, chemical compounds, polymers, and the like.
Claims (125)
1. An implantable medical device, comprising:
a structure configured for introduction into a patient, the structure being composed of a base material;
at least one coating layer between the structure and at least one layer of a bioactive material;
at least one layer comprising a bioactive material posited on at least a portion of the coating layer; and at least one porous layer posited over the at least one layer comprising the bioactive material layer, composed of a polymer and being of a thickness adequate to provide a controlled release of the bioactive material, the at least one coating layer being less porous than, but composed of the same or different polymer as, the at least one porous layer.
a structure configured for introduction into a patient, the structure being composed of a base material;
at least one coating layer between the structure and at least one layer of a bioactive material;
at least one layer comprising a bioactive material posited on at least a portion of the coating layer; and at least one porous layer posited over the at least one layer comprising the bioactive material layer, composed of a polymer and being of a thickness adequate to provide a controlled release of the bioactive material, the at least one coating layer being less porous than, but composed of the same or different polymer as, the at least one porous layer.
2. The device according to claim 1, wherein the at least one porous layer is one polymerized from a catalyst-free monomer vapor.
3. The device according to claim 1, wherein the polymer is selected from the group consisting of a polyamide, polymers of parylene or derivatives thereof, poly(ethylene oxide), poly(ethylene glycol), poly(propylene oxide), silicone based polymers, polytetrafluoroethylene, polytetramethyldisiloxane, and a polymer derived from photopolymerizeable monomers.
4. The device according to claim 3, wherein the thickness of the at least one porous layer is about 5,000 to 250,000 .ANG..
5. The device according to claim 1, wherein the at least one coating layer consisting of parylene or a parylene derivative.
6. The device according to claim 1, wherein the at least one coating layer is less porous than, but composed of the same or different polymer as the at least one porous layer.
7. The device according to claim 6, wherein the polymer of the at least one porous layer and the polymer of coating layer are selected from the group consisting of polyamide, polymers of parylene or derivatives thereof, and a polymer derived from photopolymerizable monomers of bisphenol A diglycidyl ether and acrylic acid or methacrylic acid, and the at least one coating layer is about 50,000 to 500,000 .ANG. thick.
8. The device according to claim 1, wherein the structure is configured as a vascular stent.
9. The device according to claim 1, wherein the structure is configured as at least one of: a stent, a vascular or other graft, a vascular or other graft in combination with a stent, heart valve, an orthopedic device, appliance, implant or replacement, or portion thereof; or a portion of any of these.
10. The device according to claim 1, wherein the base material is biocompatible.
11. The device according to claim 10, wherein the base material of the structure comprises at least one of:
stainless steel, tantalum, titanium, Nitinol.TM., gold, platinum, inconel, iridium, silver, tungsten, or another biocompatible metal, or alloys of any of these; carbon or carbon fiber;
cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers thereof; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxy-butyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a mixture thereof.
stainless steel, tantalum, titanium, Nitinol.TM., gold, platinum, inconel, iridium, silver, tungsten, or another biocompatible metal, or alloys of any of these; carbon or carbon fiber;
cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers thereof; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxy-butyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a mixture thereof.
12. The device according to claim 1, wherein the bioactive material comprises at least one of: heparin, covalent heparin, or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof; urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof;
a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiogenin, angiopeptin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P-, or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; gene therapy agents; and enalapril and other prodrugs, or a mixture of any of these.
a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiogenin, angiopeptin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P-, or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; gene therapy agents; and enalapril and other prodrugs, or a mixture of any of these.
13. The device according to claim 1, wherein the at least one layer comprising the bioactive material contains about 0.01 to 4 mg of the bioactive material per cm2 of the gross surface area of the structure.
14. The device according to claim 1, wherein different bioactive materials are posited on the different surfaces of the structure.
15. The device according to claim 1, wherein a bioactive material is posited on one surface of structure, a porous layer is posited over the bioactive material on the one surface of structure and over the bioactive-material-free surface of structure, and a second bioactive material is posited on the porous layer and forms the outermost layer for structure.
16. The device according to claim 15, wherein a different and third bioactive material is posited on the bioactive-material-free side of structure and further having porous layer posited over the first and third bioactive materials; and wherein the second bioactive material forming the outermost layer is covalent heparin bound to porous layer.
17. The device according to claim 15, wherein the structure comprises either a single bioactive material on one surface of said structure or different bioactive materials on the different surfaces of structure with the porous layer over said bioactive material or materials and said second bioactive material forms the outermost layer over the porous layer.
18. The device according to claim 1, wherein plural but different bioactive materials are posited on the different surfaces of structure with the proviso that the same bioactive material is not posited on the different surfaces of the structure within the same layer and that the outermost layer comprises either a porous layer or a bioactive material layer.
19. The device according to claim 1, wherein said bioactive material is posited on said one surface of structure in a geometric pattern.
20. The device according to claim 19, wherein said device is a stent and said bioactive material is posited on one surface of the stent in a discontinuous geometric pattern.
21. The device according to claim 20, wherein bioactive material is posited on one surface of the stent in a pattern of parallel lines or wherein the bioactive material is not posited on the tips of the stent.
22. The device according to claim 1, wherein two or more different bioactive materials are posited on one surface of the structure.
23. The device according to claim 22, wherein the two or more bioactive materials are posited on adjacent areas of the one surface of structure.
24. The device according to claim 1, further comprising a connector securing the at least one porous layer to the base material of the structure.
25. An implantable vascular device, comprising:
A. a stent structure configured for introduction into a vascular system of a patient, the stent structure comprising a biocompatible metal;
B. at least one bioactive material posited on one surface of the structure of the stent; and C. a porous layer posited over the bioactive material and the bioactive-material-free stent surface, wherein said porous layer being at least 5,000 .ANG.
thick adequate to provide a controlled release of the bioactive material.
A. a stent structure configured for introduction into a vascular system of a patient, the stent structure comprising a biocompatible metal;
B. at least one bioactive material posited on one surface of the structure of the stent; and C. a porous layer posited over the bioactive material and the bioactive-material-free stent surface, wherein said porous layer being at least 5,000 .ANG.
thick adequate to provide a controlled release of the bioactive material.
26. The device according to claim 25, wherein the stent surface is coated with a substantially non-porous coating layer having a thickness of about 50,000 .ANG. to about 500,000 .ANG.
wherein the coating layer comprises a polymer selected from the group consisting of polyamide, a polymer derived from parylene or derivatives thereof, polyalkylene oxides, polyalkylene glycols, silicon based polymers, polytetrafluoro-ethylene, polytetramethyldisiloxane, and polymers derived from photopolymerizeable monomers or mixtures of such polymers and copolymers thereof.
wherein the coating layer comprises a polymer selected from the group consisting of polyamide, a polymer derived from parylene or derivatives thereof, polyalkylene oxides, polyalkylene glycols, silicon based polymers, polytetrafluoro-ethylene, polytetramethyldisiloxane, and polymers derived from photopolymerizeable monomers or mixtures of such polymers and copolymers thereof.
27. The device according to claim 25, wherein the bioactive material comprises at least one of: heparin, covalent heparin or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof;
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiopeptin, angiogenin, or other growth factors, or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; enalapril or other prodrugs; gene therapy agents, or a mixture of any of these; and various forms of small intestine submucosa.
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiopeptin, angiogenin, or other growth factors, or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; enalapril or other prodrugs; gene therapy agents, or a mixture of any of these; and various forms of small intestine submucosa.
28. The device according to claim 25, wherein the at least one layer of bioactive material contains about 1 to 4 mg of the bioactive material per cm2 of the gross surface area of the structure.
29. The device according to claim 25, wherein different bioactive materials are posited on the different surfaces of the stent structure.
30. The device according to claim 25, wherein the bioactive material is posited on one surface of the stent structure, the porous layer is posited over the bioactive material on the one surface of the stent structure and over the bioactive-material-free surface of the stent structure, and a second bioactive material is posited on the porous layer and forms the outermost layer for the stent structure.
31. The device according to claim 30, wherein a different and third bioactive material is posited on the bioactive-material-free surface of the stent structure further having a porous layer posited over the bioactive materials and wherein the second bioactive material forming the outermost layer is covalent heparin bound to the porous layer.
32. The device according to claim 31, wherein the stent structure comprises either a single bioactive material on one surface of said structure or different bioactive materials on the different surfaces of the stent structure with the porous layer over said bioactive material or materials and said second bioactive material forms the outermost layer over the porous layer.
33. The device according to claim 25, wherein multiple layers comprise the stent surfaces wherein such layers comprise alternating porous layers and at least one bioactive material layer and wherein different bioactive materials are posited on the different surfaces of the stent structure with the proviso that the same bioactive material is not posited on the different surfaces of the stent structure within the same layer and that a porous layer is posited over each bioactive material layer and the outermost layer comprises either a porous layer or a bioactive material layer.
34. The device according to claim 25, wherein said bioactive material is posited on said one surface of stent structure in a geometric pattern.
35. The device according to claim 34, wherein the bioactive material is posited on one surface of the stent structure in a pattern of parallel lines or a pattern wherein the bioactive material is not posited on the tips of the stent.
36. The device according to claim 25, wherein two or more different bioactive materials are posited on one surface of the stent structure.
37. The device according to claim 36, wherein the two or more bioactive materials are posited on adjacent areas of the one surface of the stent structure.
38. A method of manufacturing an implantable medical device, the device comprising a structure configured for introduction into the patient, and the structure being composed of a base material, the method comprising:
depositing at least one coating layer on at least one surface of structure;
depositing at least one bioactive material layer on at least a portion of the coating layer, on at least one surface of the structure, or on the coating layer and the surface of the structure; and depositing at least one porous layer over the at least one bioactive material layer and a bioactive-material-free surface of structure, the at least one porous layer being composed of a polymer and having a thickness adequate to provide a controlled release of the bioactive material.
depositing at least one coating layer on at least one surface of structure;
depositing at least one bioactive material layer on at least a portion of the coating layer, on at least one surface of the structure, or on the coating layer and the surface of the structure; and depositing at least one porous layer over the at least one bioactive material layer and a bioactive-material-free surface of structure, the at least one porous layer being composed of a polymer and having a thickness adequate to provide a controlled release of the bioactive material.
39. The method according to claim 38, wherein the at least one porous layer is deposited on the one surface of structure by polymerizing the at least one layer from a catalyst-free monomer vapor.
40. The method according to claim 38, wherein the at least one porous layer comprises a polymer selected from the group consisting of polyamide, polymers of parylene or derivative thereof, poly(ethylene oxide), poly(ethylene glycol), poly(propylene oxide), silicone based polymers, polytetrafluoroethylene, polytetramethyldisiloxane and polymers of photopolymerizable monomers.
41. The method according to claim 40, wherein the at least one porous layer is applied to thickness of about 5,000 to 250,000 .ANG..
42. The method according to claim 38, wherein the at least one coating layer consists of parylene or a parylene derivative.
43. The method according to claim 38, wherein the step of depositing the at least one coating layer is carried out so that the at least one coating layer is less porous than, but composed of the same or different polymer as the at least one porous layer.
44. The method according to claim 43, wherein the at least one coating layer comprises a polymer selected from the group consisting of polyimides, polymers derived from parylene and a parylene derivative, and the at least one coating layer is applied to a thickness of about 50,000 to 500,000 .ANG..
45. The method according to claim 38, wherein the method is carried out with the structure configured as a vascular stent.
46. The method according to claim 38, wherein the base material is biocompatible.
47. The method according to claim 46, wherein the method is carried out with the structure whose base material comprises at least one of: stainless steel, tantalum, titanium, Nitinol.TM., gold, platinum, inconel, iridium, silver, tungsten, or another biocompatible metal, or alloys of any of these;
carbon or carbon fiber; cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers of these; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxy-butyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a mixture of any of these.
carbon or carbon fiber; cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers of these; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxy-butyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a mixture of any of these.
48. The method according to claim 38, wherein the step of depositing the at least one bioactive material layer is carried out with the bioactive material which comprises at least one of: heparin, covalent heparin or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof;
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; GP IIb/IIIa, GP Ib-IX or another inhibitor or surface glycoprotein receptor; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiopeptin, angiogenin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody target therapy agents; enalapril or other prodrugs; gene therapy agents, or a mixture of any of these; and various forms of small intestine submucosa.
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; GP IIb/IIIa, GP Ib-IX or another inhibitor or surface glycoprotein receptor; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiopeptin, angiogenin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody target therapy agents; enalapril or other prodrugs; gene therapy agents, or a mixture of any of these; and various forms of small intestine submucosa.
49. The method according to claim 38, wherein the step of depositing the at least one layer of bioactive material is carried out so that the at least one layer contains about 1 to 4 mg of the bioactive material per cm2 of the gross surface area of the structure.
50. The method according to claim 38, wherein different bioactive materials are deposited on the different surfaces of the structure.
51. The method according to claim 38, wherein the bioactive material is deposited on one surface of the structure, the porous layer is posited over the bioactive material on one surface of structure and over the bioactive-material-free surface of structure, and a second bioactive material is posited on porous layer and forms the outermost layer for structure.
52. The method according to claim 51, wherein a different and third bioactive material is deposited on a bioactive-material-free side of structure further having porous layer deposited over the different bioactive materials and wherein the second bioactive material forming the outermost layer is covalent heparin bound to porous layer.
53. The method according to claim 38, wherein the structure comprises either a single bioactive material on one side of said structure or different bioactive materials on the different sides of structure with the porous layer over said bioactive material or materials and a second bioactive material forms the outermost layer over porous layer.
54. The method according to claim 38, wherein multiple layers comprise stent surfaces wherein such layers comprise alternating porous layers and at least one bioactive material and wherein different bioactive materials are posited on the different surfaces of structure with the proviso that the same bioactive material is not posited on both surfaces of the structure within the same layer and that the outermost layer comprises either the porous layer or the bioactive material.
55. The method according to claim 38, wherein said bioactive material is deposited on one surface of structure in a geometric pattern.
56. The method according to claim 55, wherein said device is a stent and said bioactive material is deposited on one surface of the stent in a discontinuous geometric pattern.
57. The method according to claim 56, wherein bioactive material is deposited on one surface of the stent in a pattern of parallel lines or a pattern wherein the bioactive material is not posited on the tips of the stent.
58. The method according to claim 38, wherein two or more different bioactive materials are deposited on one side of the structure.
59. The method according to claim 58, wherein the two or more bioactive materials are deposited on adjacent areas of the one surface of structure.
60. The method according to claim 38, wherein the method is carried out with a device further comprising a connector securing the at least one porous layer to the base material of the structure.
61. A method of making an implantable medical device, the device including a structure configured for introduction into a patient, and the structure being composed of a base material; wherein the method comprises the steps of:
A. depositing a coating layer on one surface of the structure;
B. depositing at least one bioactive material on at least a portion of the coating layer, on the one surface of the structure, or on the coating layer and the surface of the structure; and C. depositing at least one porous layer over the at least one bioactive material, the at least one porous layer being composed of a polymer and being of a thickness adequate to provide a controlled release of the bioactive material.
A. depositing a coating layer on one surface of the structure;
B. depositing at least one bioactive material on at least a portion of the coating layer, on the one surface of the structure, or on the coating layer and the surface of the structure; and C. depositing at least one porous layer over the at least one bioactive material, the at least one porous layer being composed of a polymer and being of a thickness adequate to provide a controlled release of the bioactive material.
62. The method according to claim 61, wherein the step of depositing the at least one porous layer comprises polymerizing the at least one layer from a catalyst-free monomer vapor.
63. The method according to claim 61, wherein the at least one porous layer comprises a polymer selected from the group consisting of polyimides, polymers derived from parylene or derivatives thereof, poly(ethylene oxide), poly(ethylene glycol), poly(propylene oxide), silicone based polymer, polytetrafluoroethylene, polytetramethyldisiloxane and polymers derived from photopolymerizeable monomers.
64. The method according to claim 61, wherein the bioactive material is deposited by a process selected from the group consisting of adsorption, absorption, vapor phase deposition, plasma deposition, chemically binding to the surface of the device, utilizing surfactants as an adhesion medium, electrode position, and combinations thereof.
65. The method according to claim 64, wherein the bioactive material is applied by vapor phase deposition, plasma deposition or by chemically binding to the substrate structure and the bioactive material is in the form of a powder, microencapsulated particles or a matrix incorporated material.
66. The method according to claim 61, wherein different bioactive materials are deposited on the different surfaces of the structure.
67. The method according to claim 61, wherein a first bioactive material is deposited on one surface of structure, the porous layer is deposited over the bioactive material on one surface of the structure and over the bioactive-material-free surface of structure and a second bioactive material is deposited on the porous layer and forms the outermost layer for structure.
68. The method according to claim 67, wherein a different and third bioactive material is deposited on the bioactive-material-free surface of structure prior to the deposition of the porous layer and the subsequent deposition of the second bioactive material on porous layer forming the outermost layer for structure.
69. The method according to claim 61, wherein multiple layers are deposited on the surfaces of structure wherein such layers comprise alternating porous layers and at least one bioactive material and wherein different bioactive materials are deposited on the different surfaces of structure with the proviso that the same bioactive material is not deposited on both surfaces of structure within the same layer and that the porous layer is deposited over each layer of the bioactive material wherein the outermost layer of structure comprises either the porous layer or a layer of the bioactive material.
70. The method according to claim 61, wherein the bioactive material is deposited on one surface of structure in a geometric pattern.
71. The method according to claim 70, wherein the device is a stent and the bioactive material is deposited on one surface of the stent in a discontinuous geometric pattern.
72. The method according to claim 71, wherein the bioactive material is deposited on one surface of the stent in a pattern of parallel lines or in a pattern wherein the bioactive material is not deposited on the tips of the stent.
73. The method according to claim 61, wherein two or more bioactive materials are deposited on one side or surface of the structure.
74. The method according to claim 73, wherein the two or more bioactive materials are deposited on adjacent areas of the one surface of structure.
75. The method according to claim 61, wherein the at least one porous layer is applied to thickness of about 5,000 to 250,000 .ANG..
76. The method according to claim 61, wherein at least one porous layer is carried out by sublimating and cracking di-p-xylylene or a derivative thereof to yield monomeric p-xylylene or a derivative thereof, and allowing the monomer so formed to simultaneously condense and polymerize over the bioactive material layer.
77. The method according to claim 76, wherein the sublimating and cracking step is carried out with dichloro-di-p-xylylene.
78. The method according to claim 61, wherein the step of depositing the at least one porous layer is carried out in the absence of a solvent or catalyst for the polymer.
79. The method according to claim 61, wherein the step of depositing the at least one bioactive material is carried out by applying over the structure a mixture of the bioactive material and a fluid, and removing the fluid prior to the step of depositing the at least one porous layer.
80. The method according to claim 79, wherein the fluid is volatile, and the fluid removing step is carried out by allowing the fluid to evaporate from the structure and bioactive material before the step of depositing the at least one porous layer.
81. The method according to claim 61, wherein the coating layer comprises a polymer selected from the group consisting of polyamide, parylene and a parylene derivative, and the coating layer is applied to a thickness of about 50,000 to 500,000 .ANG..
82. The method according to claim 61, wherein the method is carried out with the structure configured as a vascular stent.
83. The method according to claim 61, wherein the step of depositing the at least one bioactive material is carried out with the bioactive material which comprises at least one of: heparin, covalent heparin or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof;
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; tripodal, angiopeptin, angiogenin or other growth factors, or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody target therapy agents; enalapril or other prodrugs; and gene therapy agents, or a mixture of any of these.
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; tripodal, angiopeptin, angiogenin or other growth factors, or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody target therapy agents; enalapril or other prodrugs; and gene therapy agents, or a mixture of any of these.
84. The method according to claim 61, wherein the step of depositing the at least one bioactive material is carried out so that at least one layer of the bioactive material contains about 1 to 4 mg of the bioactive material per cm2 of the gross surface area of the structure.
85. The method according to claim 61, comprising the further step of surface processing the base material before depositing the at least one bioactive material layer over the structure.
86. An implantable medical device, comprising:
a structure configured for introduction into a patient, the structure being comprised of a base material; wherein the base material comprises apertures within the surface of the base material and containing at least one bioactive material within said apertures wherein at least one porous layer is posited over said base material and said bioactive material contained within said apertures and wherein said porous layer is comprised of a polymer and having a thickness sufficient to provide a controlled release of the bioactive material.
a structure configured for introduction into a patient, the structure being comprised of a base material; wherein the base material comprises apertures within the surface of the base material and containing at least one bioactive material within said apertures wherein at least one porous layer is posited over said base material and said bioactive material contained within said apertures and wherein said porous layer is comprised of a polymer and having a thickness sufficient to provide a controlled release of the bioactive material.
87. The medical device according to claim 86, wherein said apertures are holes, slots, grooves or wells and have the sectional shape of a half circle, of the letter V or of a truncated square.
88. The medical device according to claim 87, wherein said hole, slot, groove or well are formed by etching using a photo resist pattern; by cutting with laser or EBM; or by stamping.
89. The medical device according to claim 88, wherein the same or different bioactive materials are contained within the holes, grooves, slots or wells.
90. The medical device according to claim 89, wherein the at least one bioactive material is selected from the group consisting of heparin, covalent heparin or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof;
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethylsulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; tripodal, angiopeptin, angiogenin or other growth factors, or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecaflouoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody target therapy agents; enalapril or other prodrugs; and gene therapy agents, and a mixture of any of these.
urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethylsulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; tripodal, angiopeptin, angiogenin or other growth factors, or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecaflouoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody target therapy agents; enalapril or other prodrugs; and gene therapy agents, and a mixture of any of these.
91. The medical device according to claim 87, wherein the base material further comprises a substantially non-porous coating and a porous layer overlies the holes, grooves, slots or wells containing the at least one bioactive layer.
92. The medical device according to claim 91, wherein said device comprises further layers of bioactive materials and porous layer coatings.
93. An implantable medical device, comprising:
a structure for introduction into a patient, the structure being composed of base material;
a coating layer comprising a polymer posited on at least one part of the structure;
at least one bioactive material posited on at least one part of the structure; and a porous material posited over the bioactive material, said porous material comprising a porous polymeric material and being of a thickness and having properties to enable controlled release of the bioactive material.
a structure for introduction into a patient, the structure being composed of base material;
a coating layer comprising a polymer posited on at least one part of the structure;
at least one bioactive material posited on at least one part of the structure; and a porous material posited over the bioactive material, said porous material comprising a porous polymeric material and being of a thickness and having properties to enable controlled release of the bioactive material.
94. The device according to claim 93, wherein said porous material is polymeric and formed as one or more porous layers, each polymerized from a catalyst-free monomer vapor, and is formed over the bioactive material and any part of the structure surface not covered by the bioactive material.
95. The device according to claim 94, wherein the polymer is selected from a polyamide, polymers of parylene or derivatives thereof, polyalkylene oxide, polyalkylene glycol, polypropylene oxide, silicone based polymers, polytetrafluoroethylene, polytetramethyldisiloxane and a polymer derived from photopolymerizeable monomers.
96. The device according to claim 94, wherein the base material of the structure comprises at least one of: stainless steel, tantalum, titanium, Nitinol.Tm., gold, platinum, inconel, iridium, silver, tungsten, or another biocompatible metal, or alloys of any of these; carbon or carbon fiber; cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers thereof; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxy-butyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; and a mixture thereof.
97. The device according to claim 94, wherein the bioactive material comprises at least one of: heparin, covalent heparin, or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof; urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof;
a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiogenin, angiopeptin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; gene therapy agents; and enalapril and other prodrugs, and a mixture of any of these.
a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; an antimicrobial agent or antibiotic;
aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide, a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodeling inhibitor;
deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol® or derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal anti-inflammatory agent; cyclosporin or another immunosuppressive agent; trapidal, angiogenin, angiopeptin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; 60Co, 192Ir, 32P, 111In, 90Y, 99m Tc or another radiotherapeutic agent;
iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-amino steroid or another free radical scavenger, iron chelator or antioxidant; a 14C-, 3H-, 131I-, 32P- or 36S-radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium or other antiviral agents;
5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; gene therapy agents; and enalapril and other prodrugs, and a mixture of any of these.
98. The device according to any one of claims 94 to 97, wherein the thickness of the at least one porous layer is about 5,000 to 250,000 .ANG., and the bioactive material(s) are present in about 1 to 4 mg per cm2.
99. The device according to claim 93, wherein the coating layer comprises a polymer selected from polyamide, polymers of parylene or derivatives thereof, a polymer derived from photopolymerizable monomers of bisphenol A diglycidyl ether and acrylic acid or methacrylic acid, and the coating layer is about 50,000 to 500,000 .ANG. thick.
100. The device according to claim 93, wherein the structure is biocompatible and is configured as at least one of a stent, a vascular graft, another graft, a vascular graft in combination with a stent, heart valve, an orthopedic device, appliance, implant, replacement, or portion thereof; or a portion of any of these.
101. The device according to claim 93, wherein different bioactive materials are posited at different locations on one surface or side of the structure, and are formed either directly on or in the structure, or partly on or in the structure at one location and partly on the porous layer, at another location.
102. The device according to claim 101, wherein a third or different bioactive material is posited on or in another side of the structure, wherein the porous layer is positioned over the said third or different material and is also posited over one of the bioactive materials on the one side of the structure, and wherein another bioactive material is bonded to the outer surface of the porous layer.
103. The device according to any one of claims 93 to 102, wherein the at least one bioactive material is posited on said at least one part in one of a geometric pattern, a discontinuous geometric pattern when the structure is a stent, a pattern of parallel lines, a pattern of parallel lines but not on the tips of the structure, and adjacent parts of the same surface of the structure.
104. The device according to any one of claims 93 to 103, further comprising a connector securing the at least one porous layer to the base material of the structure.
105. The device according to any one of claims 102 to 104, wherein the structure is surface coated with a substantially non-porous coating layer having a thickness of about 50,000 .ANG.
to about 500,000 .ANG. wherein the coating layer comprises a polymer selected from polyamide, a polymer derived from parylene or derivatives thereof, polyalkylene oxides, polyalkylene glycols, silicon based polymers, polytetrafluoroethylene, polytetramethyldisiloxane and polymers derived from photopolymerizeable monomers mixtures of such polymers or copolymers thereof.
to about 500,000 .ANG. wherein the coating layer comprises a polymer selected from polyamide, a polymer derived from parylene or derivatives thereof, polyalkylene oxides, polyalkylene glycols, silicon based polymers, polytetrafluoroethylene, polytetramethyldisiloxane and polymers derived from photopolymerizeable monomers mixtures of such polymers or copolymers thereof.
106. The device according to any one of claims 101 or 102, wherein multiple layers comprise stent surfaces, such layers comprising alternating porous layers and at least one bioactive material layer and wherein different bioactive materials are posited on the different surfaces of the stent structure with the proviso that the same bioactive material is not posited on the different surfaces of the stent structure within the same layer and that the porous layer is posited over each bioactive material layer and the outermost layer comprises either the porous layer or the bioactive material layer.
107. A method of making the device according to any one of claims 93 to 106, wherein the bioactive material is posited by a process of adsorption, absorption, vapor phase deposition, plasma deposition, chemically binding to the surface of the device, utilizing surfactants as an adhesion medium, electrode position, and combinations thereof, the coating layer is posited on the structure by a process of vapor deposition and mechanical application, and the porous material is posited on the bioactive material by a process of vapor phase deposition, plasma deposition, mechanical application of a polymer solution and curing the polymer solution by condensation, and combinations thereof.
108. The method according to claim 107, wherein the bioactive material layer has been applied by vapor phase deposition, plasma deposition or by chemically binding to the substrate structure and the bioactive material is in the form of a powder, microencapsulated particles or a matrix incorporated material.
109. A method of making the device according to any one of claims 93 to 106, wherein at least one porous layer has been formed by sublimating and cracking di-p-xylylene or a derivative thereof to yield monomeric p-xylylene or a derivative thereof, and allowing the monomer so formed to simultaneously condense and polymerize over the bioactive material, the sublimation and cracking step being carried out with dichloro-di-p-xylylene, and the bioactive material is posited by a process of adsorption, absorption, vapor phase deposition, plasma deposition, chemically binding to the surface of the device, utilizing surfactants as an adhesion medium, electrode position, and combinations thereof, the coating layer is posited on the structure by a process of vapor deposition and mechanical application.
110. The method according to any one of claims 107 to 109, wherein the step of depositing the at least one bioactive material is carried out by applying over the structure a mixture of the bioactive material and a fluid, and removing the fluid prior to the step of depositing the at least one porous layer.
111. The method according to claim 110, wherein the fluid is volatile, and the fluid removing step is carried out by allowing the fluid to evaporate from the structure and bioactive material before the step of depositing the at least one porous layer.
112. A device according to any one of claims 93 to 106, wherein the base material comprises apertures within the surface of the base material and the bioactive material are positioned within the apertures, said apertures being in the form of holes, slots, grooves or wells having etched or stamped sectional shapes of a half circle, a letter V or of a truncated square, same or different bioactive materials being contained within the holes, grooves, slots or wells.
113. An implantable medical device, comprising:
a structure for introduction into a patient, the structure being composed of base material;
a coating layer comprising a polymer posited on at least one part of the structure;
at least one bioactive material posited on the coating layer; the coating layer comprising a polymeric material and controlling the release of the bioactive material; and a porous layer posited on the at least one bioactive material at a thickness adequate to provide controlled release of the at least one bioactive material.
a structure for introduction into a patient, the structure being composed of base material;
a coating layer comprising a polymer posited on at least one part of the structure;
at least one bioactive material posited on the coating layer; the coating layer comprising a polymeric material and controlling the release of the bioactive material; and a porous layer posited on the at least one bioactive material at a thickness adequate to provide controlled release of the at least one bioactive material.
114. The implantable medical device of claim 113, wherein the coating layer consists of parylene or a parylene derivative.
115. An implantable medical device, comprising:
a structure configured for introduction into a patient, the structure being composed of a base material;
at least one coating layer comprising a first polymer posited on at least one surface of the structure;
at least one bioactive material posited on the coating layer; and at least one porous layer posited over the bioactive material, the porous layer comprising a second polymer, the at least one porous layer being of a thickness adequate to provide controlled release of the at least one bioactive material.
a structure configured for introduction into a patient, the structure being composed of a base material;
at least one coating layer comprising a first polymer posited on at least one surface of the structure;
at least one bioactive material posited on the coating layer; and at least one porous layer posited over the bioactive material, the porous layer comprising a second polymer, the at least one porous layer being of a thickness adequate to provide controlled release of the at least one bioactive material.
116. The implantable medical device of claim 115, wherein the coating layer comprises parylene or a parylene derivative.
117. The implantable medical device of claim 115, wherein the bioactive material is an immunosuppressive agent.
118. The implantable medical device of any one of claims 115 to 117, wherein the first polymer is different from the second polymer.
119. The implantable medical device of any one of claims 115 to 118, wherein the first polymer and the second polymer are selected from: parylene, a parylene derivative, poly(n-butyl methacrylate), poly(ethyl vinyl acetate), copolymers thereof and mixtures thereof.
120. The implantable medical device of any one of claims 1, 93 and 113 to 119, wherein the total amount of bioactive material posited over the implantable medical device is 0.01 to 10 mg of the bioactive material per cm2 of gross surface area of the structure.
121. The implantable medical device of claim 120, wherein the implantable medical device contains a total of 0.1 to 4 mg of the bioactive material per cm2 of gross surface area of the structure.
122. The implantable medical device of any one of claims 1, 93 and 113 to 121, wherein the implantable medical device provides a release rate of the bioactive material in the range of 0.1 to 0.5 mg/cm 2 per day upon implantation.
123. The implantable medical device of any one of claims 113 to 122, wherein the coating layer is 50,000 to 500,000 Angstroms thick.
124. The implantable medical device of any one of claims 115 to 120, wherein the first polymer is parylene or a parylene derivative, and the second polymer is a copolymer of poly(n-butyl methacrylate) and poly(ethyl vinyl acetate).
125. The implantable medical device of any one of claims 1 to 37, 85 to 106 and 112 to 124, wherein the medical device contains 100 micrograms to 300 micrograms of the bioactive material per 0.001 inch of coating thickness.
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US484,532 | 1995-06-07 | ||
US08/484,532 US5609629A (en) | 1995-06-07 | 1995-06-07 | Coated implantable medical device |
US645,646 | 1996-05-16 | ||
US08/645,646 US6096070A (en) | 1995-06-07 | 1996-05-16 | Coated implantable medical device |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2178541A1 CA2178541A1 (en) | 1996-12-08 |
CA2178541C true CA2178541C (en) | 2009-11-24 |
Family
ID=27048040
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002178541A Expired - Lifetime CA2178541C (en) | 1995-06-07 | 1996-06-07 | Implantable medical device |
Country Status (3)
Country | Link |
---|---|
US (3) | US5824049A (en) |
AU (1) | AU716005B2 (en) |
CA (1) | CA2178541C (en) |
Cited By (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US7942926B2 (en) | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7976915B2 (en) | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US7981150B2 (en) | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
US8002823B2 (en) | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8029554B2 (en) | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
US8066763B2 (en) | 1998-04-11 | 2011-11-29 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US8067054B2 (en) | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US8071156B2 (en) | 2009-03-04 | 2011-12-06 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US8187620B2 (en) | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
US8216632B2 (en) | 2007-11-02 | 2012-07-10 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8221822B2 (en) | 2007-07-31 | 2012-07-17 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
US8231980B2 (en) | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
US8287937B2 (en) | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
US8353949B2 (en) | 2006-09-14 | 2013-01-15 | Boston Scientific Scimed, Inc. | Medical devices with drug-eluting coating |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
US8449603B2 (en) | 2008-06-18 | 2013-05-28 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8574615B2 (en) | 2006-03-24 | 2013-11-05 | Boston Scientific Scimed, Inc. | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8771343B2 (en) | 2006-06-29 | 2014-07-08 | Boston Scientific Scimed, Inc. | Medical devices with selective titanium oxide coatings |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
US8815273B2 (en) | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
US8900292B2 (en) | 2007-08-03 | 2014-12-02 | Boston Scientific Scimed, Inc. | Coating for medical device having increased surface area |
US8920491B2 (en) | 2008-04-22 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical devices having a coating of inorganic material |
US8932346B2 (en) | 2008-04-24 | 2015-01-13 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
US9284409B2 (en) | 2007-07-19 | 2016-03-15 | Boston Scientific Scimed, Inc. | Endoprosthesis having a non-fouling surface |
Families Citing this family (1042)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5843089A (en) * | 1990-12-28 | 1998-12-01 | Boston Scientific Corporation | Stent lining |
US6515009B1 (en) | 1991-09-27 | 2003-02-04 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US5811447A (en) | 1993-01-28 | 1998-09-22 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US5981568A (en) | 1993-01-28 | 1999-11-09 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US6491938B2 (en) | 1993-05-13 | 2002-12-10 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US6663881B2 (en) | 1993-01-28 | 2003-12-16 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
EP1304085A3 (en) * | 1994-09-16 | 2004-01-21 | Ethicon Endo-Surgery, Inc. | Biodegradable tissue marking device |
US20030083733A1 (en) * | 1997-10-10 | 2003-05-01 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US6099562A (en) * | 1996-06-13 | 2000-08-08 | Schneider (Usa) Inc. | Drug coating with topcoat |
US20020091433A1 (en) * | 1995-04-19 | 2002-07-11 | Ni Ding | Drug release coated stent |
US5837313A (en) * | 1995-04-19 | 1998-11-17 | Schneider (Usa) Inc | Drug release stent coating process |
US20020193828A1 (en) * | 2001-06-14 | 2002-12-19 | Cook Incorporated | Endovascular filter |
US7896914B2 (en) | 1995-06-07 | 2011-03-01 | Cook Incorporated | Coated implantable medical device |
US7611533B2 (en) * | 1995-06-07 | 2009-11-03 | Cook Incorporated | Coated implantable medical device |
US7867275B2 (en) | 1995-06-07 | 2011-01-11 | Cook Incorporated | Coated implantable medical device method |
US20070203520A1 (en) * | 1995-06-07 | 2007-08-30 | Dennis Griffin | Endovascular filter |
US7846202B2 (en) | 1995-06-07 | 2010-12-07 | Cook Incorporated | Coated implantable medical device |
US6774278B1 (en) | 1995-06-07 | 2004-08-10 | Cook Incorporated | Coated implantable medical device |
US7550005B2 (en) | 1995-06-07 | 2009-06-23 | Cook Incorporated | Coated implantable medical device |
US7266725B2 (en) * | 2001-09-03 | 2007-09-04 | Pact Xpp Technologies Ag | Method for debugging reconfigurable architectures |
US6428571B1 (en) | 1996-01-22 | 2002-08-06 | Scimed Life Systems, Inc. | Self-sealing PTFE vascular graft and manufacturing methods |
US5800512A (en) * | 1996-01-22 | 1998-09-01 | Meadox Medicals, Inc. | PTFE vascular graft |
ATE314843T1 (en) | 1996-03-12 | 2006-02-15 | Pg Txl Co Lp | WATER SOLUBLE PACLITAXEL PRODRUGS |
US6441025B2 (en) * | 1996-03-12 | 2002-08-27 | Pg-Txl Company, L.P. | Water soluble paclitaxel derivatives |
EP0909148A1 (en) * | 1996-05-31 | 1999-04-21 | The University Of Western Ontario | Expansible bioprosthetic valve stent |
US20060025726A1 (en) * | 1996-06-04 | 2006-02-02 | Vance Products Incorporated, D/B/A Cook Urological Incorporated | Implantable medical device with pharmacologically active layer |
US20060030826A1 (en) * | 1996-06-04 | 2006-02-09 | Vance Products Incorporated,d/b/a Cook Urological Incorporated | Implantable medical device with anti-neoplastic drug |
US20060052757A1 (en) * | 1996-06-04 | 2006-03-09 | Vance Products Incorporated, D/B/A Cook Urological Incorporated | Implantable medical device with analgesic or anesthetic |
US6666883B1 (en) | 1996-06-06 | 2003-12-23 | Jacques Seguin | Endoprosthesis for vascular bifurcation |
US8728143B2 (en) * | 1996-06-06 | 2014-05-20 | Biosensors International Group, Ltd. | Endoprosthesis deployment system for treating vascular bifurcations |
US7238197B2 (en) * | 2000-05-30 | 2007-07-03 | Devax, Inc. | Endoprosthesis deployment system for treating vascular bifurcations |
US7686846B2 (en) * | 1996-06-06 | 2010-03-30 | Devax, Inc. | Bifurcation stent and method of positioning in a body lumen |
US7070590B1 (en) | 1996-07-02 | 2006-07-04 | Massachusetts Institute Of Technology | Microchip drug delivery devices |
US6530951B1 (en) * | 1996-10-24 | 2003-03-11 | Cook Incorporated | Silver implantable medical device |
US6515016B2 (en) | 1996-12-02 | 2003-02-04 | Angiotech Pharmaceuticals, Inc. | Composition and methods of paclitaxel for treating psoriasis |
US20030157187A1 (en) * | 1996-12-02 | 2003-08-21 | Angiotech Pharmaceuticals, Inc. | Compositions and methods for treating or preventing inflammatory diseases |
US6495579B1 (en) | 1996-12-02 | 2002-12-17 | Angiotech Pharmaceuticals, Inc. | Method for treating multiple sclerosis |
JP4084420B2 (en) * | 1996-12-10 | 2008-04-30 | パーデュー・リサーチ・ファウンデーション | Tubular submucosa graft composition |
IT1289815B1 (en) * | 1996-12-30 | 1998-10-16 | Sorin Biomedica Cardio Spa | ANGIOPLASTIC STENT AND RELATED PRODUCTION PROCESS |
US10028851B2 (en) | 1997-04-15 | 2018-07-24 | Advanced Cardiovascular Systems, Inc. | Coatings for controlling erosion of a substrate of an implantable medical device |
US5843172A (en) | 1997-04-15 | 1998-12-01 | Advanced Cardiovascular Systems, Inc. | Porous medicated stent |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US8172897B2 (en) | 1997-04-15 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Polymer and metal composite implantable medical devices |
US6273913B1 (en) | 1997-04-18 | 2001-08-14 | Cordis Corporation | Modified stent useful for delivery of drugs along stent strut |
TW586934B (en) * | 1997-05-19 | 2004-05-11 | Sumitomo Pharma | Immunopotentiating composition |
US6245760B1 (en) * | 1997-05-28 | 2001-06-12 | Aventis Pharmaceuticals Products, Inc | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6159978A (en) | 1997-05-28 | 2000-12-12 | Aventis Pharmaceuticals Product, Inc. | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6180632B1 (en) | 1997-05-28 | 2001-01-30 | Aventis Pharmaceuticals Products Inc. | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US20030199425A1 (en) * | 1997-06-27 | 2003-10-23 | Desai Neil P. | Compositions and methods for treatment of hyperplasia |
US6156061A (en) * | 1997-08-29 | 2000-12-05 | Target Therapeutics, Inc. | Fast-detaching electrically insulated implant |
US6890546B2 (en) | 1998-09-24 | 2005-05-10 | Abbott Laboratories | Medical devices containing rapamycin analogs |
US20030129215A1 (en) * | 1998-09-24 | 2003-07-10 | T-Ram, Inc. | Medical devices containing rapamycin analogs |
US8057816B2 (en) * | 1997-09-26 | 2011-11-15 | Abbott Laboratories | Compositions and methods of administering paclitaxel with other drugs using medical devices |
US8257726B2 (en) * | 1997-09-26 | 2012-09-04 | Abbott Laboratories | Compositions, systems, kits, and methods of administering rapamycin analogs with paclitaxel using medical devices |
DE69828963T2 (en) * | 1997-10-01 | 2006-01-26 | Medtronic AVE, Inc., Santa Rosa | Drug delivery and gene therapy delivery system |
US6151525A (en) * | 1997-11-07 | 2000-11-21 | Medtronic, Inc. | Method and system for myocardial identifier repair |
US6775574B1 (en) * | 1997-11-07 | 2004-08-10 | Medtronic, Inc. | Method and system for myocardial infarction repair |
US6270464B1 (en) * | 1998-06-22 | 2001-08-07 | Artemis Medical, Inc. | Biopsy localization method and device |
DE69829653T2 (en) * | 1997-11-14 | 2005-09-08 | Sumitomo Osaka Cement Co., Ltd. | METHOD FOR PRODUCING ANTIMICROBIAL METAL PARTS AND METAL PARTS MANUFACTURED THEREFOR |
US6254642B1 (en) * | 1997-12-09 | 2001-07-03 | Thomas V. Taylor | Perorally insertable gastroesophageal anti-reflux valve prosthesis and tool for implantation thereof |
US5976169A (en) * | 1997-12-16 | 1999-11-02 | Cardiovasc, Inc. | Stent with silver coating and method |
US20030036746A1 (en) * | 2001-08-16 | 2003-02-20 | Avi Penner | Devices for intrabody delivery of molecules and systems and methods utilizing same |
WO1999044538A1 (en) * | 1998-01-27 | 1999-09-10 | The Regents Of The University Of California | Biodegradable polymer/protein based coils for intralumenal implants |
US20070093889A1 (en) * | 1999-01-27 | 2007-04-26 | Wu Benjamin M | Non-Fragmenting Low Friction Bioactive Absorbable Coils for Brain Aneurysm Therapy |
US6541116B2 (en) * | 1998-01-30 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Superoxide dismutase or superoxide dismutase mimic coating for an intracorporeal medical device |
US6221425B1 (en) | 1998-01-30 | 2001-04-24 | Advanced Cardiovascular Systems, Inc. | Lubricious hydrophilic coating for an intracorporeal medical device |
US7208011B2 (en) * | 2001-08-20 | 2007-04-24 | Conor Medsystems, Inc. | Implantable medical device with drug filled holes |
US20040254635A1 (en) * | 1998-03-30 | 2004-12-16 | Shanley John F. | Expandable medical device for delivery of beneficial agent |
US7208010B2 (en) | 2000-10-16 | 2007-04-24 | Conor Medsystems, Inc. | Expandable medical device for delivery of beneficial agent |
US6241762B1 (en) | 1998-03-30 | 2001-06-05 | Conor Medsystems, Inc. | Expandable medical device with ductile hinges |
US7179289B2 (en) | 1998-03-30 | 2007-02-20 | Conor Medsystems, Inc. | Expandable medical device for delivery of beneficial agent |
US5980566A (en) * | 1998-04-11 | 1999-11-09 | Alt; Eckhard | Vascular and endoluminal stents with iridium oxide coating |
US20020099438A1 (en) * | 1998-04-15 | 2002-07-25 | Furst Joseph G. | Irradiated stent coating |
US20030040790A1 (en) | 1998-04-15 | 2003-02-27 | Furst Joseph G. | Stent coating |
US8029561B1 (en) | 2000-05-12 | 2011-10-04 | Cordis Corporation | Drug combination useful for prevention of restenosis |
US20070087028A1 (en) * | 1998-04-16 | 2007-04-19 | Robert Falotico | Intraluminal devices for the prevention and treatment of vascular disease |
WO1999055396A1 (en) | 1998-04-27 | 1999-11-04 | Surmodics, Inc. | Bioactive agent release coating |
JP4583597B2 (en) * | 1998-05-05 | 2010-11-17 | ボストン サイエンティフィック リミテッド | Smooth end stent |
US20020058882A1 (en) * | 1998-06-22 | 2002-05-16 | Artemis Medical, Incorporated | Biopsy localization method and device |
US6096175A (en) | 1998-07-17 | 2000-08-01 | Micro Therapeutics, Inc. | Thin film stent |
US7967855B2 (en) | 1998-07-27 | 2011-06-28 | Icon Interventional Systems, Inc. | Coated medical device |
US8070796B2 (en) * | 1998-07-27 | 2011-12-06 | Icon Interventional Systems, Inc. | Thrombosis inhibiting graft |
US20020038146A1 (en) * | 1998-07-29 | 2002-03-28 | Ulf Harry | Expandable stent with relief cuts for carrying medicines and other materials |
JP4898991B2 (en) | 1998-08-20 | 2012-03-21 | クック メディカル テクノロジーズ エルエルシー | Sheathed medical device |
US6689121B1 (en) | 1998-09-24 | 2004-02-10 | C. R. Bard, Inc. | Systems and methods for treating ischemia |
US7960405B2 (en) * | 1998-09-24 | 2011-06-14 | Abbott Laboratories | Compounds and methods for treatment and prevention of diseases |
US7455853B2 (en) * | 1998-09-24 | 2008-11-25 | Abbott Cardiovascular Systems Inc. | Medical devices containing rapamycin analogs |
EP1115389B1 (en) * | 1998-09-25 | 2014-03-12 | PhilERA New Zealand Limited | Fructosamine oxidase: antagonists and inhibitors |
US20040043068A1 (en) * | 1998-09-29 | 2004-03-04 | Eugene Tedeschi | Uses for medical devices having a lubricious, nitric oxide-releasing coating |
US6248112B1 (en) | 1998-09-30 | 2001-06-19 | C. R. Bard, Inc. | Implant delivery system |
US6458092B1 (en) | 1998-09-30 | 2002-10-01 | C. R. Bard, Inc. | Vascular inducing implants |
US6432126B1 (en) * | 1998-09-30 | 2002-08-13 | C.R. Bard, Inc. | Flexible vascular inducing implants |
US6364902B1 (en) * | 1998-10-05 | 2002-04-02 | Noble-Met, Ltd. | Metal composite tube for biomedical applications |
US6494879B2 (en) | 1998-10-15 | 2002-12-17 | Scimed Life Systems, Inc. | Treating urinary retention |
US6475234B1 (en) * | 1998-10-26 | 2002-11-05 | Medinol, Ltd. | Balloon expandable covered stents |
US6293967B1 (en) | 1998-10-29 | 2001-09-25 | Conor Medsystems, Inc. | Expandable medical device with ductile hinges |
US6187024B1 (en) | 1998-11-10 | 2001-02-13 | Target Therapeutics, Inc. | Bioactive coating for vaso-occlusive devices |
US6723112B2 (en) | 1998-11-10 | 2004-04-20 | Scimed Life Systems, Inc. | Bioactive three loop coil |
US6569179B2 (en) | 1998-11-10 | 2003-05-27 | Scimed Life Systems, Inc. | Bioactive three loop coil |
US8016852B2 (en) * | 1998-11-10 | 2011-09-13 | Stryker Corporation | Bioactive components for incorporation with vaso-occlusive members |
US6692520B1 (en) | 1998-12-15 | 2004-02-17 | C. R. Bard, Inc. | Systems and methods for imbedded intramuscular implants |
US9669113B1 (en) | 1998-12-24 | 2017-06-06 | Devicor Medical Products, Inc. | Device and method for safe location and marking of a biopsy cavity |
US6356782B1 (en) * | 1998-12-24 | 2002-03-12 | Vivant Medical, Inc. | Subcutaneous cavity marking device and method |
US6371904B1 (en) * | 1998-12-24 | 2002-04-16 | Vivant Medical, Inc. | Subcutaneous cavity marking device and method |
US6258117B1 (en) | 1999-04-15 | 2001-07-10 | Mayo Foundation For Medical Education And Research | Multi-section stent |
US6620170B1 (en) | 1999-04-26 | 2003-09-16 | C. R. Bard, Inc. | Devices and methods for treating ischemia by creating a fibrin plug |
US6679824B1 (en) * | 1999-04-28 | 2004-01-20 | Medi-Physics, Inc. | Products and methods for brachytherapy |
US6986784B1 (en) | 1999-05-14 | 2006-01-17 | C. R. Bard, Inc. | Implant anchor systems |
US6290673B1 (en) * | 1999-05-20 | 2001-09-18 | Conor Medsystems, Inc. | Expandable medical device delivery system and method |
US20040110722A1 (en) * | 1999-05-27 | 2004-06-10 | Ornberg Richard L. | Modified hyaluronic acid polymers |
EP1185312B1 (en) * | 1999-05-27 | 2005-03-23 | Monsanto Company | Biomaterials modified with superoxide dismutase mimics |
US6719805B1 (en) * | 1999-06-09 | 2004-04-13 | C. R. Bard, Inc. | Devices and methods for treating tissue |
US20040073155A1 (en) * | 2000-01-14 | 2004-04-15 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in tissue |
US20050060044A1 (en) * | 1999-08-05 | 2005-03-17 | Ed Roschak | Methods and devices for maintaining patency of surgically created channels in a body organ |
US6692494B1 (en) * | 1999-08-05 | 2004-02-17 | Broncus Technologies, Inc. | Methods and devices for creating collateral channels in the lungs |
US20030070676A1 (en) * | 1999-08-05 | 2003-04-17 | Cooper Joel D. | Conduits having distal cage structure for maintaining collateral channels in tissue and related methods |
US20030130657A1 (en) * | 1999-08-05 | 2003-07-10 | Tom Curtis P. | Devices for applying energy to tissue |
US20050137715A1 (en) * | 1999-08-05 | 2005-06-23 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in a body organ |
US7815590B2 (en) * | 1999-08-05 | 2010-10-19 | Broncus Technologies, Inc. | Devices for maintaining patency of surgically created channels in tissue |
US6485735B1 (en) * | 1999-08-31 | 2002-11-26 | Phelps Dodge High Performance Conductors Of Sc & Ga, Inc. | Multilayer thermoset polymer matrix and structures made therefrom |
US6503556B2 (en) | 2000-12-28 | 2003-01-07 | Advanced Cardiovascular Systems, Inc. | Methods of forming a coating for a prosthesis |
US20040029952A1 (en) * | 1999-09-03 | 2004-02-12 | Yung-Ming Chen | Ethylene vinyl alcohol composition and coating |
US6749626B1 (en) | 2000-03-31 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Actinomycin D for the treatment of vascular disease |
US6503954B1 (en) | 2000-03-31 | 2003-01-07 | Advanced Cardiovascular Systems, Inc. | Biocompatible carrier containing actinomycin D and a method of forming the same |
US20070032853A1 (en) * | 2002-03-27 | 2007-02-08 | Hossainy Syed F | 40-O-(2-hydroxy)ethyl-rapamycin coated stent |
US6759054B2 (en) | 1999-09-03 | 2004-07-06 | Advanced Cardiovascular Systems, Inc. | Ethylene vinyl alcohol composition and coating |
US7682647B2 (en) | 1999-09-03 | 2010-03-23 | Advanced Cardiovascular Systems, Inc. | Thermal treatment of a drug eluting implantable medical device |
US6713119B2 (en) | 1999-09-03 | 2004-03-30 | Advanced Cardiovascular Systems, Inc. | Biocompatible coating for a prosthesis and a method of forming the same |
US6790228B2 (en) * | 1999-12-23 | 2004-09-14 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US7807211B2 (en) * | 1999-09-03 | 2010-10-05 | Advanced Cardiovascular Systems, Inc. | Thermal treatment of an implantable medical device |
US6379381B1 (en) | 1999-09-03 | 2002-04-30 | Advanced Cardiovascular Systems, Inc. | Porous prosthesis and a method of depositing substances into the pores |
US6287628B1 (en) * | 1999-09-03 | 2001-09-11 | Advanced Cardiovascular Systems, Inc. | Porous prosthesis and a method of depositing substances into the pores |
US20040229856A1 (en) * | 1999-09-21 | 2004-11-18 | Baskaran Chandrasekar | Local delivery of 17-beta estradiol for preventing vascular intimal hyperplasia and for improving vascular endothelium function after vascular injury |
MXPA02003009A (en) * | 1999-09-21 | 2005-02-17 | Inst Cardiologie Montreal | Local delivery of 17-beta estradiol for preventing vascular intima hyperplasia and for improving vascular endothelium function after vascular injury. |
US6334868B1 (en) | 1999-10-08 | 2002-01-01 | Advanced Cardiovascular Systems, Inc. | Stent cover |
US6733513B2 (en) | 1999-11-04 | 2004-05-11 | Advanced Bioprosthetic Surfaces, Ltd. | Balloon catheter having metal balloon and method of making same |
US6491666B1 (en) * | 1999-11-17 | 2002-12-10 | Microchips, Inc. | Microfabricated devices for the delivery of molecules into a carrier fluid |
US7300457B2 (en) | 1999-11-19 | 2007-11-27 | Advanced Bio Prosthetic Surfaces, Ltd. | Self-supporting metallic implantable grafts, compliant implantable medical devices and methods of making same |
US7235092B2 (en) | 1999-11-19 | 2007-06-26 | Advanced Bio Prosthetic Surfaces, Ltd. | Guidewires and thin film catheter-sheaths and method of making same |
US6849085B2 (en) | 1999-11-19 | 2005-02-01 | Advanced Bio Prosthetic Surfaces, Ltd. | Self-supporting laminated films, structural materials and medical devices manufactured therefrom and method of making same |
US6936066B2 (en) | 1999-11-19 | 2005-08-30 | Advanced Bio Prosthetic Surfaces, Ltd. | Complaint implantable medical devices and methods of making same |
US7736687B2 (en) | 2006-01-31 | 2010-06-15 | Advance Bio Prosthetic Surfaces, Ltd. | Methods of making medical devices |
US6379383B1 (en) * | 1999-11-19 | 2002-04-30 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal device exhibiting improved endothelialization and method of manufacture thereof |
US7195641B2 (en) | 1999-11-19 | 2007-03-27 | Advanced Bio Prosthetic Surfaces, Ltd. | Valvular prostheses having metal or pseudometallic construction and methods of manufacture |
US10172730B2 (en) | 1999-11-19 | 2019-01-08 | Vactronix Scientific, Llc | Stents with metallic covers and methods of making same |
US8458879B2 (en) | 2001-07-03 | 2013-06-11 | Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. | Method of fabricating an implantable medical device |
US6537310B1 (en) | 1999-11-19 | 2003-03-25 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal implantable devices and method of making same |
US20060052865A1 (en) * | 2004-09-09 | 2006-03-09 | Banas Christopher E | Stents with metallic covers and methods of making same |
AU782639B2 (en) * | 1999-12-10 | 2005-08-18 | Massachusetts Institute Of Technology | Microchip devices for delivery of molecules and methods of fabrication thereof |
US6702849B1 (en) * | 1999-12-13 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Method of processing open-celled microcellular polymeric foams with controlled porosity for use as vascular grafts and stent covers |
US6613432B2 (en) * | 1999-12-22 | 2003-09-02 | Biosurface Engineering Technologies, Inc. | Plasma-deposited coatings, devices and methods |
US7169187B2 (en) * | 1999-12-22 | 2007-01-30 | Ethicon, Inc. | Biodegradable stent |
US6338739B1 (en) * | 1999-12-22 | 2002-01-15 | Ethicon, Inc. | Biodegradable stent |
US6494908B1 (en) | 1999-12-22 | 2002-12-17 | Ethicon, Inc. | Removable stent for body lumens |
US6981987B2 (en) | 1999-12-22 | 2006-01-03 | Ethicon, Inc. | Removable stent for body lumens |
US6908624B2 (en) * | 1999-12-23 | 2005-06-21 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US20050238686A1 (en) * | 1999-12-23 | 2005-10-27 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
AU2599501A (en) * | 1999-12-29 | 2001-07-09 | Advanced Cardiovascular Systems Inc. | Device and active component for inhibiting formation of thrombus-inflammatory cell matrix |
AU2609401A (en) * | 1999-12-29 | 2001-07-09 | Nicholas Kipshidze | Apparatus and method for delivering compounds to a living organism |
JP2003520830A (en) | 2000-01-25 | 2003-07-08 | エドワーズ ライフサイエンシーズ コーポレイション | Delivery system for treatment of restenosis and anastomotic intimal hyperplasia |
WO2001064344A2 (en) | 2000-03-02 | 2001-09-07 | Microchips, Inc. | Microfabricated devices for the storage and selective exposure of chemicals and devices |
US6613082B2 (en) | 2000-03-13 | 2003-09-02 | Jun Yang | Stent having cover with drug delivery capability |
US6379382B1 (en) | 2000-03-13 | 2002-04-30 | Jun Yang | Stent having cover with drug delivery capability |
US6558315B1 (en) | 2000-03-15 | 2003-05-06 | Ams Research Corporation | Parylene-coated components for inflatable penile prosthesis |
US7011622B2 (en) * | 2000-03-15 | 2006-03-14 | Ams Research Corporation | Parylene coated components for artificial sphincters |
US8088060B2 (en) | 2000-03-15 | 2012-01-03 | Orbusneich Medical, Inc. | Progenitor endothelial cell capturing with a drug eluting implantable medical device |
US20050271701A1 (en) * | 2000-03-15 | 2005-12-08 | Orbus Medical Technologies, Inc. | Progenitor endothelial cell capturing with a drug eluting implantable medical device |
US9522217B2 (en) | 2000-03-15 | 2016-12-20 | Orbusneich Medical, Inc. | Medical device with coating for capturing genetically-altered cells and methods for using same |
US20020077290A1 (en) * | 2000-03-17 | 2002-06-20 | Rama Bhatt | Polyglutamic acid-camptothecin conjugates and methods of preparation |
ES2222352T3 (en) * | 2000-03-18 | 2005-02-01 | Polyzenix Gmbh | USE OF POLYPHOSPHACENE DERIVATIVES FOR ANTIBACTERIAL COATINGS. |
US6695865B2 (en) | 2000-03-20 | 2004-02-24 | Advanced Bio Prosthetic Surfaces, Ltd. | Embolic protection device |
US6818247B1 (en) | 2000-03-31 | 2004-11-16 | Advanced Cardiovascular Systems, Inc. | Ethylene vinyl alcohol-dimethyl acetamide composition and a method of coating a stent |
US7265199B2 (en) * | 2000-04-11 | 2007-09-04 | Celonova Biosciences Germany Gmbh | Poly-tri-fluoro-ethoxypolyphosphazene coverings and films |
US8109994B2 (en) | 2003-01-10 | 2012-02-07 | Abbott Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US6527801B1 (en) | 2000-04-13 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US7875283B2 (en) | 2000-04-13 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Biodegradable polymers for use with implantable medical devices |
US20010049422A1 (en) * | 2000-04-14 | 2001-12-06 | Phaneuf Matthew D. | Methods of applying antibiotic compounds to polyurethane biomaterials using textile dyeing technology |
US6270779B1 (en) * | 2000-05-10 | 2001-08-07 | United States Of America | Nitric oxide-releasing metallic medical devices |
US20050002986A1 (en) * | 2000-05-12 | 2005-01-06 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US8236048B2 (en) | 2000-05-12 | 2012-08-07 | Cordis Corporation | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US8845713B2 (en) | 2000-05-12 | 2014-09-30 | Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. | Self-supporting laminated films, structural materials and medical devices manufactured therefrom and methods of making same |
US20040243097A1 (en) * | 2000-05-12 | 2004-12-02 | Robert Falotico | Antiproliferative drug and delivery device |
US6776796B2 (en) | 2000-05-12 | 2004-08-17 | Cordis Corportation | Antiinflammatory drug and delivery device |
US8252044B1 (en) * | 2000-11-17 | 2012-08-28 | Advanced Bio Prosthestic Surfaces, Ltd. | Device for in vivo delivery of bioactive agents and method of manufacture thereof |
US20030139803A1 (en) * | 2000-05-30 | 2003-07-24 | Jacques Sequin | Method of stenting a vessel with stent lumenal diameter increasing distally |
US6395326B1 (en) | 2000-05-31 | 2002-05-28 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for depositing a coating onto a surface of a prosthesis |
US7682648B1 (en) | 2000-05-31 | 2010-03-23 | Advanced Cardiovascular Systems, Inc. | Methods for forming polymeric coatings on stents |
US20040211362A1 (en) * | 2000-05-31 | 2004-10-28 | Daniel Castro | System for coating a stent |
EP1289429B1 (en) | 2000-06-05 | 2006-03-15 | Boston Scientific Limited | devices for the treatment of urinary incontinence |
CA2410632A1 (en) | 2000-06-22 | 2001-12-27 | David S. Garvey | Nitrosated and nitrosylated taxanes, compositions and methods of use |
AU2001266727A1 (en) * | 2000-06-29 | 2002-01-14 | Johnson & Johnson Consumer Companies, Inc | Electrostatic impregnation of powders on substrates |
US6585765B1 (en) * | 2000-06-29 | 2003-07-01 | Advanced Cardiovascular Systems, Inc. | Implantable device having substances impregnated therein and a method of impregnating the same |
US6540775B1 (en) | 2000-06-30 | 2003-04-01 | Cordis Corporation | Ultraflexible open cell stent |
US6974473B2 (en) | 2000-06-30 | 2005-12-13 | Vascular Architects, Inc. | Function-enhanced thrombolytic AV fistula and method |
US6506408B1 (en) * | 2000-07-13 | 2003-01-14 | Scimed Life Systems, Inc. | Implantable or insertable therapeutic agent delivery device |
US6709451B1 (en) * | 2000-07-14 | 2004-03-23 | Norman Noble, Inc. | Channeled vascular stent apparatus and method |
US6451373B1 (en) | 2000-08-04 | 2002-09-17 | Advanced Cardiovascular Systems, Inc. | Method of forming a therapeutic coating onto a surface of an implantable prosthesis |
US20090004240A1 (en) * | 2000-08-11 | 2009-01-01 | Celonova Biosciences, Inc. | Implants with a phosphazene-containing coating |
EP1179353A1 (en) * | 2000-08-11 | 2002-02-13 | B. Braun Melsungen Ag | Antithrombogenic implants with coating of polyphosphazenes and a pharmacologically active agent |
US20020072792A1 (en) | 2000-09-22 | 2002-06-13 | Robert Burgermeister | Stent with optimal strength and radiopacity characteristics |
US6695833B1 (en) * | 2000-09-27 | 2004-02-24 | Nellix, Inc. | Vascular stent-graft apparatus and forming method |
US6953560B1 (en) | 2000-09-28 | 2005-10-11 | Advanced Cardiovascular Systems, Inc. | Barriers for polymer-coated implantable medical devices and methods for making the same |
US6805898B1 (en) * | 2000-09-28 | 2004-10-19 | Advanced Cardiovascular Systems, Inc. | Surface features of an implantable medical device |
US6716444B1 (en) * | 2000-09-28 | 2004-04-06 | Advanced Cardiovascular Systems, Inc. | Barriers for polymer-coated implantable medical devices and methods for making the same |
US6254632B1 (en) * | 2000-09-28 | 2001-07-03 | Advanced Cardiovascular Systems, Inc. | Implantable medical device having protruding surface structures for drug delivery and cover attachment |
US20020051730A1 (en) * | 2000-09-29 | 2002-05-02 | Stanko Bodnar | Coated medical devices and sterilization thereof |
US7261735B2 (en) * | 2001-05-07 | 2007-08-28 | Cordis Corporation | Local drug delivery devices and methods for maintaining the drug coatings thereon |
AU2001294861A1 (en) | 2000-09-29 | 2002-04-08 | Endovasc Ltd., Inc. | Resorbable prosthesis for medical treatment |
US20020111590A1 (en) * | 2000-09-29 | 2002-08-15 | Davila Luis A. | Medical devices, drug coatings and methods for maintaining the drug coatings thereon |
DE60124285T3 (en) | 2000-09-29 | 2011-03-17 | Cordis Corp., Miami Lakes | COATED MEDICAL EQUIPMENT |
US6746773B2 (en) | 2000-09-29 | 2004-06-08 | Ethicon, Inc. | Coatings for medical devices |
US6764507B2 (en) | 2000-10-16 | 2004-07-20 | Conor Medsystems, Inc. | Expandable medical device with improved spatial distribution |
US7024248B2 (en) * | 2000-10-16 | 2006-04-04 | Remon Medical Technologies Ltd | Systems and methods for communicating with implantable devices |
AU9463401A (en) * | 2000-10-16 | 2002-04-29 | Conor Medsystems Inc | Expandable medical device for delivery of beneficial agent |
US6506437B1 (en) | 2000-10-17 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Methods of coating an implantable device having depots formed in a surface thereof |
US6551267B1 (en) * | 2000-10-18 | 2003-04-22 | Becton, Dickinson And Company | Medical article having blood-contacting surface |
US6979347B1 (en) | 2000-10-23 | 2005-12-27 | Advanced Cardiovascular Systems, Inc. | Implantable drug delivery prosthesis |
US6558733B1 (en) | 2000-10-26 | 2003-05-06 | Advanced Cardiovascular Systems, Inc. | Method for etching a micropatterned microdepot prosthesis |
US6783793B1 (en) * | 2000-10-26 | 2004-08-31 | Advanced Cardiovascular Systems, Inc. | Selective coating of medical devices |
US6758859B1 (en) * | 2000-10-30 | 2004-07-06 | Kenny L. Dang | Increased drug-loading and reduced stress drug delivery device |
US6761708B1 (en) * | 2000-10-31 | 2004-07-13 | Advanced Cardiovascular Systems, Inc. | Radiopaque marker for a catheter and method of making |
US7803149B2 (en) | 2002-07-12 | 2010-09-28 | Cook Incorporated | Coated medical device |
US6833153B1 (en) | 2000-10-31 | 2004-12-21 | Advanced Cardiovascular Systems, Inc. | Hemocompatible coatings on hydrophobic porous polymers |
US7807210B1 (en) * | 2000-10-31 | 2010-10-05 | Advanced Cardiovascular Systems, Inc. | Hemocompatible polymers on hydrophobic porous polymers |
JP4583756B2 (en) * | 2000-10-31 | 2010-11-17 | クック インコーポレイテッド | Medical instruments |
WO2002038080A2 (en) | 2000-11-07 | 2002-05-16 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent, self-fupporting endoluminal graft and methods of making same |
US10398830B2 (en) * | 2000-11-17 | 2019-09-03 | Vactronix Scientific, Llc | Device for in vivo delivery of bioactive agents and method of manufacture thereof |
US6638205B1 (en) * | 2000-11-17 | 2003-10-28 | Mds (Canada) Inc. | Radioactive medical device for radiation therapy |
WO2002055136A2 (en) * | 2000-12-01 | 2002-07-18 | Nephros Therapeutics Inc | Intrasvascular drug delivery device and use therefor |
US7244272B2 (en) | 2000-12-19 | 2007-07-17 | Nicast Ltd. | Vascular prosthesis and method for production thereof |
US20040030377A1 (en) * | 2001-10-19 | 2004-02-12 | Alexander Dubson | Medicated polymer-coated stent assembly |
WO2002049544A1 (en) * | 2000-12-19 | 2002-06-27 | Vascular Architects, Inc. | Biologically active agent delivery apparatus and method |
US20020084178A1 (en) * | 2000-12-19 | 2002-07-04 | Nicast Corporation Ltd. | Method and apparatus for manufacturing polymer fiber shells via electrospinning |
US7077859B2 (en) | 2000-12-22 | 2006-07-18 | Avantec Vascular Corporation | Apparatus and methods for variably controlled substance delivery from implanted prostheses |
US20020082679A1 (en) * | 2000-12-22 | 2002-06-27 | Avantec Vascular Corporation | Delivery or therapeutic capable agents |
US20030033007A1 (en) * | 2000-12-22 | 2003-02-13 | Avantec Vascular Corporation | Methods and devices for delivery of therapeutic capable agents with variable release profile |
US7018405B2 (en) | 2000-12-22 | 2006-03-28 | Avantec Vascular Corporation | Intravascular delivery of methylprednisolone |
US6824559B2 (en) | 2000-12-22 | 2004-11-30 | Advanced Cardiovascular Systems, Inc. | Ethylene-carboxyl copolymers as drug delivery matrices |
US20030050692A1 (en) * | 2000-12-22 | 2003-03-13 | Avantec Vascular Corporation | Delivery of therapeutic capable agents |
US7083642B2 (en) * | 2000-12-22 | 2006-08-01 | Avantec Vascular Corporation | Delivery of therapeutic capable agents |
US6471980B2 (en) | 2000-12-22 | 2002-10-29 | Avantec Vascular Corporation | Intravascular delivery of mycophenolic acid |
US6939375B2 (en) | 2000-12-22 | 2005-09-06 | Avantac Vascular Corporation | Apparatus and methods for controlled substance delivery from implanted prostheses |
US20020082678A1 (en) * | 2000-12-22 | 2002-06-27 | Motasim Sirhan | Intravascular delivery of mizoribine |
US6663662B2 (en) * | 2000-12-28 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Diffusion barrier layer for implantable devices |
US8632845B2 (en) * | 2000-12-28 | 2014-01-21 | Abbott Cardiovascular Systems Inc. | Method of drying bioabsorbable coating over stents |
US7504125B1 (en) | 2001-04-27 | 2009-03-17 | Advanced Cardiovascular Systems, Inc. | System and method for coating implantable devices |
US6540776B2 (en) | 2000-12-28 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Sheath for a prosthesis and methods of forming the same |
US6547812B1 (en) | 2000-12-29 | 2003-04-15 | Advanced Cardiovascular Systems, Inc. | Radiation therapy using a radioactive implantable device and a radiosensitizer agent |
US6641607B1 (en) | 2000-12-29 | 2003-11-04 | Advanced Cardiovascular Systems, Inc. | Double tube stent |
US6635082B1 (en) | 2000-12-29 | 2003-10-21 | Advanced Cardiovascular Systems Inc. | Radiopaque stent |
US6544582B1 (en) * | 2001-01-05 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for coating an implantable device |
GB0100761D0 (en) | 2001-01-11 | 2001-02-21 | Biocompatibles Ltd | Drug delivery from stents |
DE10100961B4 (en) * | 2001-01-11 | 2005-08-04 | Polyzenix Gmbh | Body-compatible material and substrate coated with this material for the cultivation of cells and artificial organic implants constructed or grown from cells |
US9080146B2 (en) * | 2001-01-11 | 2015-07-14 | Celonova Biosciences, Inc. | Substrates containing polyphosphazene as matrices and substrates containing polyphosphazene with a micro-structured surface |
AP2003002828A0 (en) | 2001-01-16 | 2003-09-30 | Vascular Therapies Llc | Implantable device containing resorbable matrix material and anti-proliferative drugs for preventing or treating failure of hemodialysis vascular access and other vascular grafts. |
US6866656B2 (en) * | 2001-01-24 | 2005-03-15 | Becton, Dickinson And Company | Lubricious coating for a medical device |
US20020120333A1 (en) * | 2001-01-31 | 2002-08-29 | Keogh James R. | Method for coating medical device surfaces |
US20040220660A1 (en) * | 2001-02-05 | 2004-11-04 | Shanley John F. | Bioresorbable stent with beneficial agent reservoirs |
US6964680B2 (en) * | 2001-02-05 | 2005-11-15 | Conor Medsystems, Inc. | Expandable medical device with tapered hinge |
US20040073294A1 (en) * | 2002-09-20 | 2004-04-15 | Conor Medsystems, Inc. | Method and apparatus for loading a beneficial agent into an expandable medical device |
US8038708B2 (en) | 2001-02-05 | 2011-10-18 | Cook Medical Technologies Llc | Implantable device with remodelable material and covering material |
US20040204756A1 (en) * | 2004-02-11 | 2004-10-14 | Diaz Stephen Hunter | Absorbent article with improved liquid acquisition capacity |
DE10105592A1 (en) * | 2001-02-06 | 2002-08-08 | Achim Goepferich | Placeholder for drug release in the frontal sinus |
CA2435306C (en) * | 2001-02-16 | 2010-12-21 | Stephan Wnendt | Implants with fk506 |
GB0104383D0 (en) * | 2001-02-22 | 2001-04-11 | Psimedica Ltd | Cancer Treatment |
WO2002069848A2 (en) * | 2001-03-06 | 2002-09-12 | Board Of Regents, The University Of Texas System | Apparatus for stent deployment with delivery of bioactive agents |
EP1365679B1 (en) | 2001-03-09 | 2007-11-14 | Boston Scientific Limited | Medical slings |
US9149261B2 (en) | 2001-03-09 | 2015-10-06 | Boston Scientific Scimed, Inc. | Systems, methods and devices relating to delivery of medical implants |
US8033983B2 (en) | 2001-03-09 | 2011-10-11 | Boston Scientific Scimed, Inc. | Medical implant |
US8915927B2 (en) | 2001-03-09 | 2014-12-23 | Boston Scientific Scimed, Inc. | Systems, methods and devices relating to delivery of medical implants |
DE60239188D1 (en) * | 2001-03-09 | 2011-03-31 | Boston Scient Ltd | SYSTEM FOR INSERTING A SLING |
US7771468B2 (en) * | 2001-03-16 | 2010-08-10 | Angiotech Biocoatings Corp. | Medicated stent having multi-layer polymer coating |
WO2002074194A2 (en) * | 2001-03-16 | 2002-09-26 | Sts Biopolymers, Inc. | Stent with medicated multi-layer hydrid polymer coating |
ATE473082T1 (en) * | 2001-03-20 | 2010-07-15 | Nicast Ltd | PORTABLE ELECTROSPINNER DEVICE |
DE10115740A1 (en) * | 2001-03-26 | 2002-10-02 | Ulrich Speck | Preparation for restenosis prophylaxis |
US6780424B2 (en) * | 2001-03-30 | 2004-08-24 | Charles David Claude | Controlled morphologies in polymer drug for release of drugs from polymer films |
US6764505B1 (en) | 2001-04-12 | 2004-07-20 | Advanced Cardiovascular Systems, Inc. | Variable surface area stent |
US6712845B2 (en) | 2001-04-24 | 2004-03-30 | Advanced Cardiovascular Systems, Inc. | Coating for a stent and a method of forming the same |
US6913762B2 (en) * | 2001-04-25 | 2005-07-05 | Mayo Foundation For Medical Education And Research | Stent having non-woven framework containing cells |
US6887857B2 (en) * | 2001-04-27 | 2005-05-03 | Scimed Life Systems, Inc. | Microparticle protection of therapeutic agents |
US6613083B2 (en) * | 2001-05-02 | 2003-09-02 | Eckhard Alt | Stent device and method |
US20020165601A1 (en) * | 2001-05-04 | 2002-11-07 | Clerc Claude O. | Bioabsorbable stent-graft and covered stent |
US8182527B2 (en) | 2001-05-07 | 2012-05-22 | Cordis Corporation | Heparin barrier coating for controlled drug release |
ITMO20010086A1 (en) * | 2001-05-08 | 2002-11-08 | Worgas Bruciatori Srl | METHOD AND APPARATUS TO REDUCE NITROGEN DIOXIDE (NO2) EMISSIONS IN A CHIMNEY-FREE HEATING APPLIANCE |
US6656506B1 (en) | 2001-05-09 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Microparticle coated medical device |
US20030166197A1 (en) * | 2001-05-10 | 2003-09-04 | Ecker Joseph R. | Ethylene insensitive plants |
US6685745B2 (en) | 2001-05-15 | 2004-02-03 | Scimed Life Systems, Inc. | Delivering an agent to a patient's body |
US7651695B2 (en) | 2001-05-18 | 2010-01-26 | Advanced Cardiovascular Systems, Inc. | Medicated stents for the treatment of vascular disease |
ATE287269T1 (en) * | 2001-05-25 | 2005-02-15 | Gorm Danscher | METHOD FOR IMPLANTING HEAVY METAL, SUCH AS A PRECIOUS METAL, E.G. GOLD, AND METAL FOR USE IN IMPLANTATION |
US6973718B2 (en) * | 2001-05-30 | 2005-12-13 | Microchips, Inc. | Methods for conformal coating and sealing microchip reservoir devices |
US6743462B1 (en) * | 2001-05-31 | 2004-06-01 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating implantable devices |
AU2002326304A1 (en) * | 2001-05-31 | 2002-12-16 | Massachusetts Institute Of Technology | Microchip devices with improved reservoir opening |
US7862495B2 (en) | 2001-05-31 | 2011-01-04 | Advanced Cardiovascular Systems, Inc. | Radiation or drug delivery source with activity gradient to minimize edge effects |
US7201940B1 (en) * | 2001-06-12 | 2007-04-10 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for thermal spray processing of medical devices |
US7247313B2 (en) * | 2001-06-27 | 2007-07-24 | Advanced Cardiovascular Systems, Inc. | Polyacrylates coatings for implantable medical devices |
US7727221B2 (en) * | 2001-06-27 | 2010-06-01 | Cardiac Pacemakers Inc. | Method and device for electrochemical formation of therapeutic species in vivo |
US7175873B1 (en) | 2001-06-27 | 2007-02-13 | Advanced Cardiovascular Systems, Inc. | Rate limiting barriers for implantable devices and methods for fabrication thereof |
US8741378B1 (en) | 2001-06-27 | 2014-06-03 | Advanced Cardiovascular Systems, Inc. | Methods of coating an implantable device |
US6695920B1 (en) * | 2001-06-27 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Mandrel for supporting a stent and a method of using the mandrel to coat a stent |
EP1399135B1 (en) | 2001-06-28 | 2004-12-29 | Microchips, Inc. | Methods for hermetically sealing microchip reservoir devices |
US6656216B1 (en) | 2001-06-29 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Composite stent with regioselective material |
EP1273314A1 (en) * | 2001-07-06 | 2003-01-08 | Terumo Kabushiki Kaisha | Stent |
US7246321B2 (en) * | 2001-07-13 | 2007-07-17 | Anoto Ab | Editing data |
US7286877B2 (en) * | 2001-07-13 | 2007-10-23 | Cardiac Pacemakers, Inc. | Device programmer with enclosed imaging capability |
US6704600B2 (en) | 2001-07-13 | 2004-03-09 | Cardiac Pacemakers, Inc. | Device programmer with enclosed imaging capability |
ATE330564T1 (en) * | 2001-07-20 | 2006-07-15 | Sorin Biomedica Cardio Srl | STENT |
US7547321B2 (en) * | 2001-07-26 | 2009-06-16 | Alveolus Inc. | Removable stent and method of using the same |
WO2003009778A2 (en) | 2001-07-26 | 2003-02-06 | Avantec Vascular Corporation | Methods and devices for delivery of therapeutic capable agents with variable release profile |
US7682669B1 (en) | 2001-07-30 | 2010-03-23 | Advanced Cardiovascular Systems, Inc. | Methods for covalently immobilizing anti-thrombogenic material into a coating on a medical device |
PT1432380E (en) * | 2001-08-17 | 2007-01-31 | Polyzenix Gmbh | Device based on nitinol with a polyphosphazene coating |
US7842083B2 (en) | 2001-08-20 | 2010-11-30 | Innovational Holdings, Llc. | Expandable medical device with improved spatial distribution |
US7056338B2 (en) * | 2003-03-28 | 2006-06-06 | Conor Medsystems, Inc. | Therapeutic agent delivery device with controlled therapeutic agent release rates |
US20040249443A1 (en) * | 2001-08-20 | 2004-12-09 | Shanley John F. | Expandable medical device for treating cardiac arrhythmias |
US7708712B2 (en) | 2001-09-04 | 2010-05-04 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in a body organ |
US20050060042A1 (en) * | 2001-09-04 | 2005-03-17 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
US20050137611A1 (en) * | 2001-09-04 | 2005-06-23 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
US8303651B1 (en) | 2001-09-07 | 2012-11-06 | Advanced Cardiovascular Systems, Inc. | Polymeric coating for reducing the rate of release of a therapeutic substance from a stent |
US20080145402A1 (en) * | 2001-09-10 | 2008-06-19 | Abbott Cardiovascular Systems Inc. | Medical Devices Containing Rapamycin Analogs |
US7989018B2 (en) | 2001-09-17 | 2011-08-02 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US7285304B1 (en) | 2003-06-25 | 2007-10-23 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US20030060873A1 (en) * | 2001-09-19 | 2003-03-27 | Nanomedical Technologies, Inc. | Metallic structures incorporating bioactive materials and methods for creating the same |
US7776379B2 (en) * | 2001-09-19 | 2010-08-17 | Medlogics Device Corporation | Metallic structures incorporating bioactive materials and methods for creating the same |
US6863683B2 (en) | 2001-09-19 | 2005-03-08 | Abbott Laboratoris Vascular Entities Limited | Cold-molding process for loading a stent onto a stent delivery system |
EP1429819B1 (en) * | 2001-09-24 | 2010-11-24 | Boston Scientific Limited | Optimized dosing for paclitaxel coated stents |
WO2003028590A1 (en) * | 2001-09-24 | 2003-04-10 | Medtronic Ave Inc. | Rational drug therapy device and methods |
US6827737B2 (en) * | 2001-09-25 | 2004-12-07 | Scimed Life Systems, Inc. | EPTFE covering for endovascular prostheses and method of manufacture |
US7195640B2 (en) * | 2001-09-25 | 2007-03-27 | Cordis Corporation | Coated medical devices for the treatment of vulnerable plaque |
US20030059520A1 (en) | 2001-09-27 | 2003-03-27 | Yung-Ming Chen | Apparatus for regulating temperature of a composition and a method of coating implantable devices |
US6753071B1 (en) * | 2001-09-27 | 2004-06-22 | Advanced Cardiovascular Systems, Inc. | Rate-reducing membrane for release of an agent |
US7223282B1 (en) * | 2001-09-27 | 2007-05-29 | Advanced Cardiovascular Systems, Inc. | Remote activation of an implantable device |
US7108701B2 (en) * | 2001-09-28 | 2006-09-19 | Ethicon, Inc. | Drug releasing anastomosis devices and methods for treating anastomotic sites |
US20030065377A1 (en) * | 2001-09-28 | 2003-04-03 | Davila Luis A. | Coated medical devices |
US20030065382A1 (en) * | 2001-10-02 | 2003-04-03 | Fischell Robert E. | Means and method for the treatment of coronary artery obstructions |
WO2003030964A2 (en) * | 2001-10-06 | 2003-04-17 | Walid Aboul-Hosn | Systems and methods for overcoming or preventing vascular flow restrictions |
US20030077310A1 (en) | 2001-10-22 | 2003-04-24 | Chandrashekhar Pathak | Stent coatings containing HMG-CoA reductase inhibitors |
US8740973B2 (en) | 2001-10-26 | 2014-06-03 | Icon Medical Corp. | Polymer biodegradable medical device |
US7179283B2 (en) * | 2001-11-02 | 2007-02-20 | Scimed Life Systems, Inc. | Vapor deposition process for producing a stent-graft and a stent-graft produced therefrom |
US20030088307A1 (en) * | 2001-11-05 | 2003-05-08 | Shulze John E. | Potent coatings for stents |
US6939376B2 (en) | 2001-11-05 | 2005-09-06 | Sun Biomedical, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
US7682387B2 (en) | 2002-04-24 | 2010-03-23 | Biosensors International Group, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
US7585516B2 (en) | 2001-11-12 | 2009-09-08 | Advanced Cardiovascular Systems, Inc. | Coatings for drug delivery devices |
EP1310242A1 (en) * | 2001-11-13 | 2003-05-14 | SORIN BIOMEDICA CARDIO S.p.A. | Carrier and kit for endoluminal delivery of active principles |
US20030206906A1 (en) * | 2001-11-26 | 2003-11-06 | Genentech, Inc. | Catheter composition and uses thereof |
US6663880B1 (en) | 2001-11-30 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Permeabilizing reagents to increase drug delivery and a method of local delivery |
US7175874B1 (en) | 2001-11-30 | 2007-02-13 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating implantable devices |
AUPR951501A0 (en) * | 2001-12-14 | 2002-01-24 | Smart Drug Systems Inc | Modified sustained release pharmaceutical system |
US20030216758A1 (en) * | 2001-12-28 | 2003-11-20 | Angiotech Pharmaceuticals, Inc. | Coated surgical patches |
US6709514B1 (en) | 2001-12-28 | 2004-03-23 | Advanced Cardiovascular Systems, Inc. | Rotary coating apparatus for coating implantable medical devices |
DE10200387B4 (en) * | 2002-01-08 | 2009-11-26 | Translumina Gmbh | stent |
WO2003061634A1 (en) * | 2002-01-24 | 2003-07-31 | Smart Drug Systems Inc | Sustained release pharmaceutical composition |
US7326245B2 (en) * | 2002-01-31 | 2008-02-05 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US7291165B2 (en) | 2002-01-31 | 2007-11-06 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US7445629B2 (en) * | 2002-01-31 | 2008-11-04 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US20030220297A1 (en) | 2002-02-01 | 2003-11-27 | Berstein David L. | Phosphorus-containing compounds and uses thereof |
US8685427B2 (en) * | 2002-07-31 | 2014-04-01 | Boston Scientific Scimed, Inc. | Controlled drug delivery |
US8133501B2 (en) | 2002-02-08 | 2012-03-13 | Boston Scientific Scimed, Inc. | Implantable or insertable medical devices for controlled drug delivery |
US7008397B2 (en) | 2002-02-13 | 2006-03-07 | Percardia, Inc. | Cardiac implant and methods |
US20030153971A1 (en) * | 2002-02-14 | 2003-08-14 | Chandru Chandrasekaran | Metal reinforced biodegradable intraluminal stents |
JP3993773B2 (en) * | 2002-02-20 | 2007-10-17 | 株式会社日立製作所 | Storage subsystem, storage control device, and data copy method |
US20030157269A1 (en) * | 2002-02-20 | 2003-08-21 | University Of Washington | Method and apparatus for precision coating of molecules on the surfaces of materials and devices |
US20110306997A9 (en) * | 2002-02-21 | 2011-12-15 | Roschak Edmund J | Devices for creating passages and sensing for blood vessels |
CN1649577A (en) * | 2002-03-08 | 2005-08-03 | 普罗特米克斯公司 | Preventing and/or treating cardiovascular disease and/or associated heart failure |
US7919075B1 (en) | 2002-03-20 | 2011-04-05 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices |
US7022334B1 (en) * | 2002-03-20 | 2006-04-04 | Advanced Cardiovascular Systems, Inc. | Therapeutic composition and a method of coating implantable medical devices |
US20030181973A1 (en) * | 2002-03-20 | 2003-09-25 | Harvinder Sahota | Reduced restenosis drug containing stents |
US7288111B1 (en) * | 2002-03-26 | 2007-10-30 | Thoratec Corporation | Flexible stent and method of making the same |
AU2003221744A1 (en) * | 2002-04-19 | 2003-11-03 | Broncus Technologies, Inc. | Devices for maintaining surgically created openings |
US20030199887A1 (en) * | 2002-04-23 | 2003-10-23 | David Ferrera | Filamentous embolization device and method of use |
US20030236457A1 (en) * | 2002-04-24 | 2003-12-25 | Mericle Robert A. | Method of endovascular brain mapping |
US20040024450A1 (en) * | 2002-04-24 | 2004-02-05 | Sun Biomedical, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
US7083822B2 (en) * | 2002-04-26 | 2006-08-01 | Medtronic Vascular, Inc. | Overlapping coated stents |
US7008979B2 (en) * | 2002-04-30 | 2006-03-07 | Hydromer, Inc. | Coating composition for multiple hydrophilic applications |
AU2003231229A1 (en) * | 2002-04-30 | 2003-11-17 | Cook Biotech Incorporated | Sling for supporting tissue |
US20030208258A1 (en) * | 2002-05-02 | 2003-11-06 | Tom Reilly | Vascular grafts surrounding an expanded stent for transplantation |
US8313760B2 (en) | 2002-05-24 | 2012-11-20 | Angiotech International Ag | Compositions and methods for coating medical implants |
EP1509256B1 (en) * | 2002-05-24 | 2009-07-22 | Angiotech International Ag | Compositions and methods for coating medical implants |
US7160272B1 (en) | 2002-05-31 | 2007-01-09 | Elcam Plastic | Y-site medical valve |
US20040234703A1 (en) * | 2002-06-04 | 2004-11-25 | Frautschi Jack R. | Method of forming a polymer layer on a metal surface |
AU2003243465A1 (en) * | 2002-06-07 | 2003-12-22 | Broncus Technologies, Inc. | Method and devices for maintaining patency of surgically created channels in tissue |
US6835387B2 (en) | 2002-06-11 | 2004-12-28 | Scimed Life Systems, Inc. | Sustained release of superoxide dismutase mimics from implantable or insertable medical devices |
US7097850B2 (en) | 2002-06-18 | 2006-08-29 | Surmodics, Inc. | Bioactive agent release coating and controlled humidity method |
US7105175B2 (en) * | 2002-06-19 | 2006-09-12 | Boston Scientific Scimed, Inc. | Implantable or insertable medical devices for controlled delivery of a therapeutic agent |
US7396539B1 (en) * | 2002-06-21 | 2008-07-08 | Advanced Cardiovascular Systems, Inc. | Stent coatings with engineered drug release rate |
US7033602B1 (en) * | 2002-06-21 | 2006-04-25 | Advanced Cardiovascular Systems, Inc. | Polycationic peptide coatings and methods of coating implantable medical devices |
US7217426B1 (en) | 2002-06-21 | 2007-05-15 | Advanced Cardiovascular Systems, Inc. | Coatings containing polycationic peptides for cardiovascular therapy |
US6994867B1 (en) | 2002-06-21 | 2006-02-07 | Advanced Cardiovascular Systems, Inc. | Biocompatible carrier containing L-arginine |
US7070798B1 (en) | 2002-06-21 | 2006-07-04 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices incorporating chemically-bound polymers and oligomers of L-arginine |
US7011842B1 (en) | 2002-06-21 | 2006-03-14 | Advanced Cardiovascular Systems, Inc. | Polycationic peptide coatings and methods of making the same |
US7794743B2 (en) | 2002-06-21 | 2010-09-14 | Advanced Cardiovascular Systems, Inc. | Polycationic peptide coatings and methods of making the same |
US7056523B1 (en) | 2002-06-21 | 2006-06-06 | Advanced Cardiovascular Systems, Inc. | Implantable medical devices incorporating chemically conjugated polymers and oligomers of L-arginine |
US8506617B1 (en) | 2002-06-21 | 2013-08-13 | Advanced Cardiovascular Systems, Inc. | Micronized peptide coated stent |
US20080138377A1 (en) * | 2002-07-05 | 2008-06-12 | Celonova Biosciences, Inc. | Vasodilator Eluting Luminal Stent Devices With A Specific Polyphosphazene Coating and Methods for Their Manufacture and Use |
US20080138433A1 (en) * | 2002-07-05 | 2008-06-12 | Celonova Biosciences, Inc. | Vasodilator eluting blood storage and administration devices with a specific polyphosphazene coating and methods for their manufacture and use |
AU2003250913A1 (en) * | 2002-07-08 | 2004-01-23 | Abbott Laboratories Vascular Enterprises Limited | Drug eluting stent and methods of manufacture |
US7622146B2 (en) * | 2002-07-18 | 2009-11-24 | Advanced Cardiovascular Systems, Inc. | Rate limiting barriers for implantable devices and methods for fabrication thereof |
US7294329B1 (en) * | 2002-07-18 | 2007-11-13 | Advanced Cardiovascular Systems, Inc. | Poly(vinyl acetal) coatings for implantable medical devices |
US20040034275A1 (en) * | 2002-07-29 | 2004-02-19 | Peter Forsell | Multi-material incontinence treatment constriction device |
US20040133219A1 (en) * | 2002-07-29 | 2004-07-08 | Peter Forsell | Multi-material constriction device for forming stoma opening |
DE60330359D1 (en) * | 2002-07-29 | 2010-01-14 | Potentica Ag | PENIS CONSTRUCTION DEVICE MADE FROM SEVERAL MATERIALS |
EP1539262A1 (en) * | 2002-07-29 | 2005-06-15 | Potencia Medical AG | Durable implant |
US8920826B2 (en) * | 2002-07-31 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical imaging reference devices |
US8016881B2 (en) | 2002-07-31 | 2011-09-13 | Icon Interventional Systems, Inc. | Sutures and surgical staples for anastamoses, wound closures, and surgical closures |
US20040024448A1 (en) | 2002-08-05 | 2004-02-05 | Chang James W. | Thermoplastic fluoropolymer-coated medical devices |
CA2705609C (en) | 2002-08-14 | 2016-10-25 | Boston Scientific Limited | Systems, methods and devices relating to delivery of medical implants |
EP1391184A1 (en) * | 2002-08-16 | 2004-02-25 | Endosense Sàrl | Extensible multilayer tubular structure and production method therefor |
US7951392B2 (en) * | 2002-08-16 | 2011-05-31 | Boston Scientific Scimed, Inc. | Microarray drug delivery coatings |
WO2004017956A1 (en) | 2002-08-20 | 2004-03-04 | Protemix Corporation Limited | Dosage forms and related therapies |
US7363074B1 (en) * | 2002-08-20 | 2008-04-22 | Advanced Cardiovascular Systems, Inc. | Coatings comprising self-assembled molecular structures and a method of delivering a drug using the same |
US7438925B2 (en) * | 2002-08-26 | 2008-10-21 | Biovention Holdings Ltd. | Drug eluting coatings for medical implants |
US7732535B2 (en) * | 2002-09-05 | 2010-06-08 | Advanced Cardiovascular Systems, Inc. | Coating for controlled release of drugs from implantable medical devices |
US20040054104A1 (en) * | 2002-09-05 | 2004-03-18 | Pacetti Stephen D. | Coatings for drug delivery devices comprising modified poly(ethylene-co-vinyl alcohol) |
US7201935B1 (en) | 2002-09-17 | 2007-04-10 | Advanced Cardiovascular Systems, Inc. | Plasma-generated coatings for medical devices and methods for fabricating thereof |
DE10243132B4 (en) | 2002-09-17 | 2006-09-14 | Biocer Entwicklungs Gmbh | Anti-infective, biocompatible titanium oxide coatings for implants and methods of making them |
US20040063805A1 (en) * | 2002-09-19 | 2004-04-01 | Pacetti Stephen D. | Coatings for implantable medical devices and methods for fabrication thereof |
US7438722B1 (en) | 2002-09-20 | 2008-10-21 | Advanced Cardiovascular Systems, Inc. | Method for treatment of restenosis |
US20040127976A1 (en) * | 2002-09-20 | 2004-07-01 | Conor Medsystems, Inc. | Method and apparatus for loading a beneficial agent into an expandable medical device |
US7758636B2 (en) | 2002-09-20 | 2010-07-20 | Innovational Holdings Llc | Expandable medical device with openings for delivery of multiple beneficial agents |
EP2668933A1 (en) * | 2002-09-20 | 2013-12-04 | Innovational Holdings, LLC | Expandable medical device with openings for delivery of multiple beneficial agents |
DE10244847A1 (en) | 2002-09-20 | 2004-04-01 | Ulrich Prof. Dr. Speck | Medical device for drug delivery |
US20040116997A1 (en) | 2002-09-20 | 2004-06-17 | Taylor Charles S. | Stent-graft with positioning anchor |
US20040059409A1 (en) * | 2002-09-24 | 2004-03-25 | Stenzel Eric B. | Method of applying coatings to a medical device |
JP2006500996A (en) * | 2002-09-26 | 2006-01-12 | エンドバスキュラー デバイセス インコーポレイテッド | Apparatus and method for delivering mitomycin via an eluting biocompatible implantable medical device |
EP1549248A4 (en) | 2002-09-26 | 2015-11-25 | Advanced Bio Prosthetic Surfac | High strength vacuum deposited nitionol alloy films, medical thin film graft materials and method of making same |
US7232573B1 (en) * | 2002-09-26 | 2007-06-19 | Advanced Cardiovascular Systems, Inc. | Stent coatings containing self-assembled monolayers |
US8202530B2 (en) * | 2002-09-27 | 2012-06-19 | Advanced Cardiovascular Systems, Inc. | Biocompatible coatings for stents |
US20060100695A1 (en) * | 2002-09-27 | 2006-05-11 | Peacock James C Iii | Implantable stent with modified ends |
US8337937B2 (en) * | 2002-09-30 | 2012-12-25 | Abbott Cardiovascular Systems Inc. | Stent spin coating method |
US7404979B1 (en) | 2002-09-30 | 2008-07-29 | Advanced Cardiovascular Systems Inc. | Spin coating apparatus and a method for coating implantable devices |
US7135038B1 (en) * | 2002-09-30 | 2006-11-14 | Advanced Cardiovascular Systems, Inc. | Drug eluting stent |
US6638301B1 (en) * | 2002-10-02 | 2003-10-28 | Scimed Life Systems, Inc. | Medical device with radiopacity |
US7087263B2 (en) | 2002-10-09 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Rare limiting barriers for implantable medical devices |
WO2004037443A1 (en) * | 2002-10-22 | 2004-05-06 | Medtronic Vascular Inc. | Stent with intermittent coating |
US20040093056A1 (en) * | 2002-10-26 | 2004-05-13 | Johnson Lianw M. | Medical appliance delivery apparatus and method of use |
US20040088038A1 (en) * | 2002-10-30 | 2004-05-06 | Houdin Dehnad | Porous metal for drug-loaded stents |
US20060271168A1 (en) * | 2002-10-30 | 2006-11-30 | Klaus Kleine | Degradable medical device |
US7959671B2 (en) * | 2002-11-05 | 2011-06-14 | Merit Medical Systems, Inc. | Differential covering and coating methods |
US7875068B2 (en) | 2002-11-05 | 2011-01-25 | Merit Medical Systems, Inc. | Removable biliary stent |
US7637942B2 (en) | 2002-11-05 | 2009-12-29 | Merit Medical Systems, Inc. | Coated stent with geometry determinated functionality and method of making the same |
US7527644B2 (en) * | 2002-11-05 | 2009-05-05 | Alveolus Inc. | Stent with geometry determinated functionality and method of making the same |
US8221495B2 (en) | 2002-11-07 | 2012-07-17 | Abbott Laboratories | Integration of therapeutic agent into a bioerodible medical device |
US8524148B2 (en) * | 2002-11-07 | 2013-09-03 | Abbott Laboratories | Method of integrating therapeutic agent into a bioerodible medical device |
DE60331854D1 (en) * | 2002-11-07 | 2010-05-06 | Abbott Lab | METHOD FOR ATTACHING A MEDICAMENT TO A PROSTHESIS BY MEANS OF A LIQUID AMOUNT |
KR20130032407A (en) * | 2002-11-08 | 2013-04-01 | 코너 메드시스템즈, 엘엘씨 | Method and apparatus for reducing tissue damage after ischemic injury |
JP2006505364A (en) * | 2002-11-08 | 2006-02-16 | コナー メドシステムズ, インコーポレイテッド | Expandable medical device and method for treating chronic total infarction using a local supply of angiogenic factors |
US20040142014A1 (en) * | 2002-11-08 | 2004-07-22 | Conor Medsystems, Inc. | Method and apparatus for reducing tissue damage after ischemic injury |
DE60231843D1 (en) * | 2002-11-08 | 2009-05-14 | Jacques Seguin | ENDOPROTHESIS FOR VESSEL FORKING |
US8034361B2 (en) * | 2002-11-12 | 2011-10-11 | Advanced Cardiovascular Systems, Inc. | Stent coatings incorporating nanoparticles |
US7169178B1 (en) | 2002-11-12 | 2007-01-30 | Advanced Cardiovascular Systems, Inc. | Stent with drug coating |
US7022372B1 (en) | 2002-11-12 | 2006-04-04 | Advanced Cardiovascular Systems, Inc. | Compositions for coating implantable medical devices |
US6896965B1 (en) | 2002-11-12 | 2005-05-24 | Advanced Cardiovascular Systems, Inc. | Rate limiting barriers for implantable devices |
EP2336318B1 (en) | 2002-11-13 | 2013-04-24 | Genzyme Corporation | Antisense modulation of apolipoprotein b expression |
ES2420914T3 (en) | 2002-11-13 | 2013-08-27 | Genzyme Corporation | Antisense modulation of apolipoprotein B expression |
US20040098106A1 (en) * | 2002-11-14 | 2004-05-20 | Williams Michael S. | Intraluminal prostheses and carbon dioxide-assisted methods of impregnating same with pharmacological agents |
US20040098090A1 (en) * | 2002-11-14 | 2004-05-20 | Williams Michael S. | Polymeric endoprosthesis and method of manufacture |
US7285287B2 (en) * | 2002-11-14 | 2007-10-23 | Synecor, Llc | Carbon dioxide-assisted methods of providing biocompatible intraluminal prostheses |
US20040102855A1 (en) * | 2002-11-21 | 2004-05-27 | Scimed Life Systems, Inc. | Anti-reflux stent |
US6992127B2 (en) | 2002-11-25 | 2006-01-31 | Ast Products, Inc. | Polymeric coatings containing a pH buffer agent |
US6982004B1 (en) | 2002-11-26 | 2006-01-03 | Advanced Cardiovascular Systems, Inc. | Electrostatic loading of drugs on implantable medical devices |
US20040158289A1 (en) * | 2002-11-30 | 2004-08-12 | Girouard Steven D. | Method and apparatus for cell and electrical therapy of living tissue |
US7627373B2 (en) * | 2002-11-30 | 2009-12-01 | Cardiac Pacemakers, Inc. | Method and apparatus for cell and electrical therapy of living tissue |
US6918869B2 (en) * | 2002-12-02 | 2005-07-19 | Scimed Life Systems | System for administering a combination of therapies to a body lumen |
US7211150B1 (en) | 2002-12-09 | 2007-05-01 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating and drying multiple stents |
US7776926B1 (en) | 2002-12-11 | 2010-08-17 | Advanced Cardiovascular Systems, Inc. | Biocompatible coating for implantable medical devices |
US7758880B2 (en) | 2002-12-11 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Biocompatible polyacrylate compositions for medical applications |
US7074276B1 (en) * | 2002-12-12 | 2006-07-11 | Advanced Cardiovascular Systems, Inc. | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US7758881B2 (en) | 2004-06-30 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US8435550B2 (en) | 2002-12-16 | 2013-05-07 | Abbot Cardiovascular Systems Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US7094256B1 (en) | 2002-12-16 | 2006-08-22 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical device containing polycationic peptides |
US20060002968A1 (en) | 2004-06-30 | 2006-01-05 | Gordon Stewart | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders |
AU2003259834A1 (en) | 2002-12-17 | 2004-07-29 | Boston Scientific Limited | Spacer for sling delivery system |
US7338557B1 (en) * | 2002-12-17 | 2008-03-04 | Advanced Cardiovascular Systems, Inc. | Nozzle for use in coating a stent |
US20040236415A1 (en) * | 2003-01-02 | 2004-11-25 | Richard Thomas | Medical devices having drug releasing polymer reservoirs |
US7087115B1 (en) * | 2003-02-13 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Nozzle and method for use in coating a stent |
US20050079199A1 (en) * | 2003-02-18 | 2005-04-14 | Medtronic, Inc. | Porous coatings for drug release from medical devices |
US7255891B1 (en) * | 2003-02-26 | 2007-08-14 | Advanced Cardiovascular Systems, Inc. | Method for coating implantable medical devices |
US6926919B1 (en) | 2003-02-26 | 2005-08-09 | Advanced Cardiovascular Systems, Inc. | Method for fabricating a coating for a medical device |
US8715771B2 (en) * | 2003-02-26 | 2014-05-06 | Abbott Cardiovascular Systems Inc. | Coated stent and method of making the same |
US7063884B2 (en) | 2003-02-26 | 2006-06-20 | Advanced Cardiovascular Systems, Inc. | Stent coating |
US7563483B2 (en) | 2003-02-26 | 2009-07-21 | Advanced Cardiovascular Systems Inc. | Methods for fabricating a coating for implantable medical devices |
US7001421B2 (en) * | 2003-02-28 | 2006-02-21 | Medtronic Vascular, Inc. | Stent with phenoxy primer coating |
US7288609B1 (en) * | 2003-03-04 | 2007-10-30 | Advanced Cardiovascular Systems, Inc. | Coatings for drug delivery devices based on poly (orthoesters) |
US6932930B2 (en) * | 2003-03-10 | 2005-08-23 | Synecor, Llc | Intraluminal prostheses having polymeric material with selectively modified crystallinity and methods of making same |
AU2004226327A1 (en) | 2003-03-28 | 2004-10-14 | Innovational Holdings, Llc | Implantable medical device with beneficial agent concentration gradient |
US20040202692A1 (en) * | 2003-03-28 | 2004-10-14 | Conor Medsystems, Inc. | Implantable medical device and method for in situ selective modulation of agent delivery |
US20050010170A1 (en) * | 2004-02-11 | 2005-01-13 | Shanley John F | Implantable medical device with beneficial agent concentration gradient |
US7637934B2 (en) | 2003-03-31 | 2009-12-29 | Merit Medical Systems, Inc. | Medical appliance optical delivery and deployment apparatus and method |
US20040243224A1 (en) * | 2003-04-03 | 2004-12-02 | Medtronic Vascular, Inc. | Methods and compositions for inhibiting narrowing in mammalian vascular pathways |
US8109987B2 (en) | 2003-04-14 | 2012-02-07 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US20040236399A1 (en) * | 2003-04-22 | 2004-11-25 | Medtronic Vascular, Inc. | Stent with improved surface adhesion |
US7563454B1 (en) * | 2003-05-01 | 2009-07-21 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices |
US8791171B2 (en) | 2003-05-01 | 2014-07-29 | Abbott Cardiovascular Systems Inc. | Biodegradable coatings for implantable medical devices |
ATE447904T1 (en) * | 2003-05-07 | 2009-11-15 | Advanced Bio Prosthetic Surfac | METAL IMPLANTABLE PROSTHESES AND PRODUCTION METHOD THEREOF |
US7279174B2 (en) | 2003-05-08 | 2007-10-09 | Advanced Cardiovascular Systems, Inc. | Stent coatings comprising hydrophilic additives |
US7618434B2 (en) * | 2003-05-12 | 2009-11-17 | University Of Florida Research Foundation, Inc. | Devices and methods for disruption and removal of luminal occlusions |
DE10323676A1 (en) * | 2003-05-15 | 2004-12-02 | Aesculap Ag & Co. Kg | Implant with long-term antibiotic effect |
US7323209B1 (en) | 2003-05-15 | 2008-01-29 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating stents |
US20050112273A1 (en) * | 2003-05-19 | 2005-05-26 | Stenzel Eric B. | Method of improving the quality and performance of a coating on a coated medical device using a solvent to reflow the coating |
US7731757B2 (en) * | 2003-06-01 | 2010-06-08 | Reflux Corporation | Obesity treatment |
US7169179B2 (en) * | 2003-06-05 | 2007-01-30 | Conor Medsystems, Inc. | Drug delivery device and method for bi-directional drug delivery |
US7186789B2 (en) | 2003-06-11 | 2007-03-06 | Advanced Cardiovascular Systems, Inc. | Bioabsorbable, biobeneficial polyester polymers for use in drug eluting stent coatings |
US20050118344A1 (en) | 2003-12-01 | 2005-06-02 | Pacetti Stephen D. | Temperature controlled crimping |
US7341630B1 (en) * | 2003-06-26 | 2008-03-11 | Advanced Cardiovascular Systems, Inc. | Stent coating system |
US7645504B1 (en) | 2003-06-26 | 2010-01-12 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices comprising hydrophobic and hydrophilic polymers |
US7875285B1 (en) | 2003-07-15 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Medicated coatings for implantable medical devices having controlled rate of release |
US8308682B2 (en) | 2003-07-18 | 2012-11-13 | Broncus Medical Inc. | Devices for maintaining patency of surgically created channels in tissue |
US8002740B2 (en) * | 2003-07-18 | 2011-08-23 | Broncus Technologies, Inc. | Devices for maintaining patency of surgically created channels in tissue |
US20050021127A1 (en) * | 2003-07-21 | 2005-01-27 | Kawula Paul John | Porous glass fused onto stent for drug retention |
US20050021133A1 (en) * | 2003-07-22 | 2005-01-27 | Dong Li | Tubular stents sandwiched inside of a composite membrane and methods of making and using thereof |
US7056591B1 (en) | 2003-07-30 | 2006-06-06 | Advanced Cardiovascular Systems, Inc. | Hydrophobic biologically absorbable coatings for drug delivery devices and methods for fabricating the same |
US7169404B2 (en) | 2003-07-30 | 2007-01-30 | Advanced Cardiovasular Systems, Inc. | Biologically absorbable coatings for implantable devices and methods for fabricating the same |
US7645474B1 (en) | 2003-07-31 | 2010-01-12 | Advanced Cardiovascular Systems, Inc. | Method and system of purifying polymers for use with implantable medical devices |
US7431959B1 (en) | 2003-07-31 | 2008-10-07 | Advanced Cardiovascular Systems Inc. | Method and system for irradiation of a drug eluting implantable medical device |
US7785512B1 (en) | 2003-07-31 | 2010-08-31 | Advanced Cardiovascular Systems, Inc. | Method and system of controlled temperature mixing and molding of polymers with active agents for implantable medical devices |
CA2539110A1 (en) * | 2003-09-02 | 2005-03-24 | University Of Florida | Polymeric reconstrainable, repositionable, detachable, percutaneous endovascular stentgraft |
US7488343B2 (en) * | 2003-09-16 | 2009-02-10 | Boston Scientific Scimed, Inc. | Medical devices |
US7785653B2 (en) | 2003-09-22 | 2010-08-31 | Innovational Holdings Llc | Method and apparatus for loading a beneficial agent into an expandable medical device |
US7020947B2 (en) * | 2003-09-23 | 2006-04-04 | Fort Wayne Metals Research Products Corporation | Metal wire with filaments for biomedical applications |
US7789891B2 (en) * | 2003-09-23 | 2010-09-07 | Boston Scientific Scimed, Inc. | External activation of vaso-occlusive implants |
US7441513B1 (en) | 2003-09-26 | 2008-10-28 | Advanced Cardiovascular Systems, Inc. | Plasma-generated coating apparatus for medical devices and a method of coating deposition |
US7198675B2 (en) | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US7318932B2 (en) * | 2003-09-30 | 2008-01-15 | Advanced Cardiovascular Systems, Inc. | Coatings for drug delivery devices comprising hydrolitically stable adducts of poly(ethylene-co-vinyl alcohol) and methods for fabricating the same |
US7704544B2 (en) * | 2003-10-07 | 2010-04-27 | Advanced Cardiovascular Systems, Inc. | System and method for coating a tubular implantable medical device |
US7208172B2 (en) * | 2003-11-03 | 2007-04-24 | Medlogics Device Corporation | Metallic composite coating for delivery of therapeutic agents from the surface of implantable devices |
US7435256B2 (en) * | 2003-11-06 | 2008-10-14 | Boston Scientific Scimed, Inc. | Method and apparatus for controlled delivery of active substance |
US7329413B1 (en) | 2003-11-06 | 2008-02-12 | Advanced Cardiovascular Systems, Inc. | Coatings for drug delivery devices having gradient of hydration and methods for fabricating thereof |
US20050100577A1 (en) * | 2003-11-10 | 2005-05-12 | Parker Theodore L. | Expandable medical device with beneficial agent matrix formed by a multi solvent system |
CA2448995A1 (en) * | 2003-11-12 | 2005-05-12 | James Keenan | Device and method for attracting diseased cells and foreign substances |
US7261946B2 (en) * | 2003-11-14 | 2007-08-28 | Advanced Cardiovascular Systems, Inc. | Block copolymers of acrylates and methacrylates with fluoroalkenes |
US9114198B2 (en) | 2003-11-19 | 2015-08-25 | Advanced Cardiovascular Systems, Inc. | Biologically beneficial coatings for implantable devices containing fluorinated polymers and methods for fabricating the same |
AU2004293463A1 (en) * | 2003-11-20 | 2005-06-09 | Angiotech International Ag | Implantable sensors and implantable pumps and anti-scarring agents |
US8192752B2 (en) | 2003-11-21 | 2012-06-05 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable devices including biologically erodable polyesters and methods for fabricating the same |
US20050113904A1 (en) * | 2003-11-25 | 2005-05-26 | Shank Peter J. | Composite stent with inner and outer stent elements and method of using the same |
US8435285B2 (en) * | 2003-11-25 | 2013-05-07 | Boston Scientific Scimed, Inc. | Composite stent with inner and outer stent elements and method of using the same |
US7560492B1 (en) | 2003-11-25 | 2009-07-14 | Advanced Cardiovascular Systems, Inc. | Polysulfone block copolymers as drug-eluting coating material |
US7807722B2 (en) | 2003-11-26 | 2010-10-05 | Advanced Cardiovascular Systems, Inc. | Biobeneficial coating compositions and methods of making and using thereof |
US20060085062A1 (en) * | 2003-11-28 | 2006-04-20 | Medlogics Device Corporation | Implantable stent with endothelialization factor |
US20050119723A1 (en) * | 2003-11-28 | 2005-06-02 | Medlogics Device Corporation | Medical device with porous surface containing bioerodable bioactive composites and related methods |
ATE531419T1 (en) * | 2003-12-15 | 2011-11-15 | Nitricare Hb | DEVICE FOR ADMINISTRATION OF THERAPEUTIC AGENTS |
US7220816B2 (en) | 2003-12-16 | 2007-05-22 | Advanced Cardiovascular Systems, Inc. | Biologically absorbable coatings for implantable devices based on poly(ester amides) and methods for fabricating the same |
US20050149174A1 (en) * | 2003-12-18 | 2005-07-07 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US20050154455A1 (en) * | 2003-12-18 | 2005-07-14 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US20050154451A1 (en) * | 2003-12-18 | 2005-07-14 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US7435788B2 (en) | 2003-12-19 | 2008-10-14 | Advanced Cardiovascular Systems, Inc. | Biobeneficial polyamide/polyethylene glycol polymers for use with drug eluting stents |
US20050137683A1 (en) * | 2003-12-19 | 2005-06-23 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US20050152943A1 (en) * | 2003-12-23 | 2005-07-14 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US20050152942A1 (en) * | 2003-12-23 | 2005-07-14 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US20050152940A1 (en) * | 2003-12-23 | 2005-07-14 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US20050154452A1 (en) * | 2003-12-23 | 2005-07-14 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US8309112B2 (en) | 2003-12-24 | 2012-11-13 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices comprising hydrophilic substances and methods for fabricating the same |
US20050159809A1 (en) * | 2004-01-21 | 2005-07-21 | Medtronic Vascular, Inc. | Implantable medical devices for treating or preventing restenosis |
US7211108B2 (en) | 2004-01-23 | 2007-05-01 | Icon Medical Corp. | Vascular grafts with amphiphilic block copolymer coatings |
US7349971B2 (en) * | 2004-02-05 | 2008-03-25 | Scenera Technologies, Llc | System for transmitting data utilizing multiple communication applications simultaneously in response to user request without specifying recipient's communication information |
DE102004029611A1 (en) * | 2004-02-06 | 2005-08-25 | Restate Patent Ag | Implant for e.g. releasing active substances into a vessel through which body fluids flow, comprises a base consisting of a biodegradable material as the carrier of the active substances |
CA2556212C (en) * | 2004-02-13 | 2013-05-28 | Conor Medsystems, Inc. | Implantable drug delivery device including wire filaments |
US8137397B2 (en) * | 2004-02-26 | 2012-03-20 | Boston Scientific Scimed, Inc. | Medical devices |
US7840263B2 (en) | 2004-02-27 | 2010-11-23 | Cardiac Pacemakers, Inc. | Method and apparatus for device controlled gene expression |
US8632580B2 (en) | 2004-12-29 | 2014-01-21 | Boston Scientific Scimed, Inc. | Flexible medical devices including metallic films |
US7901447B2 (en) | 2004-12-29 | 2011-03-08 | Boston Scientific Scimed, Inc. | Medical devices including a metallic film and at least one filament |
US8992592B2 (en) | 2004-12-29 | 2015-03-31 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US8591568B2 (en) | 2004-03-02 | 2013-11-26 | Boston Scientific Scimed, Inc. | Medical devices including metallic films and methods for making same |
US8998973B2 (en) | 2004-03-02 | 2015-04-07 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US8685431B2 (en) | 2004-03-16 | 2014-04-01 | Advanced Cardiovascular Systems, Inc. | Biologically absorbable coatings for implantable devices based on copolymers having ester bonds and methods for fabricating the same |
US8551512B2 (en) | 2004-03-22 | 2013-10-08 | Advanced Cardiovascular Systems, Inc. | Polyethylene glycol/poly(butylene terephthalate) copolymer coated devices including EVEROLIMUS |
US20050208093A1 (en) * | 2004-03-22 | 2005-09-22 | Thierry Glauser | Phosphoryl choline coating compositions |
US20050214339A1 (en) | 2004-03-29 | 2005-09-29 | Yiwen Tang | Biologically degradable compositions for medical applications |
US8778014B1 (en) | 2004-03-31 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Coatings for preventing balloon damage to polymer coated stents |
US20050220853A1 (en) * | 2004-04-02 | 2005-10-06 | Kinh-Luan Dao | Controlled delivery of therapeutic agents from medical articles |
CN1964748A (en) | 2004-04-06 | 2007-05-16 | 苏莫迪克斯公司 | Coating compositions for bioactive agents |
US20050228490A1 (en) * | 2004-04-09 | 2005-10-13 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US7553377B1 (en) * | 2004-04-27 | 2009-06-30 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for electrostatic coating of an abluminal stent surface |
US20050265960A1 (en) * | 2004-05-26 | 2005-12-01 | Pacetti Stephen D | Polymers containing poly(ester amides) and agents for use with medical articles and methods of fabricating the same |
US8293890B2 (en) | 2004-04-30 | 2012-10-23 | Advanced Cardiovascular Systems, Inc. | Hyaluronic acid based copolymers |
US7820732B2 (en) | 2004-04-30 | 2010-10-26 | Advanced Cardiovascular Systems, Inc. | Methods for modulating thermal and mechanical properties of coatings on implantable devices |
US20050255230A1 (en) * | 2004-05-17 | 2005-11-17 | Clerc Claude O | Method of manufacturing a covered stent |
US7390524B1 (en) | 2004-05-20 | 2008-06-24 | Advanced Cardiovascular Systems, Inc. | Method for electrostatic spraying of an abluminal stent surface |
US20050261762A1 (en) * | 2004-05-21 | 2005-11-24 | Medtronic Vascular, Inc. | Medical devices to prevent or inhibit restenosis |
US20050266039A1 (en) * | 2004-05-27 | 2005-12-01 | Jan Weber | Coated medical device and method for making the same |
US9561309B2 (en) | 2004-05-27 | 2017-02-07 | Advanced Cardiovascular Systems, Inc. | Antifouling heparin coatings |
US7764995B2 (en) | 2004-06-07 | 2010-07-27 | Cardiac Pacemakers, Inc. | Method and apparatus to modulate cellular regeneration post myocardial infarct |
KR100596218B1 (en) * | 2004-06-10 | 2006-07-03 | (주)액세스 플러스 | Tube conntecting artery to vein for hemodialysis |
US7563780B1 (en) | 2004-06-18 | 2009-07-21 | Advanced Cardiovascular Systems, Inc. | Heparin prodrugs and drug delivery stents formed therefrom |
WO2006002112A1 (en) * | 2004-06-18 | 2006-01-05 | Surmodics, Inc. | Devices, articles, coatings, and methods for controlled active agent release |
US7794490B2 (en) * | 2004-06-22 | 2010-09-14 | Boston Scientific Scimed, Inc. | Implantable medical devices with antimicrobial and biodegradable matrices |
US20050287287A1 (en) * | 2004-06-24 | 2005-12-29 | Parker Theodore L | Methods and systems for loading an implantable medical device with beneficial agent |
US8568469B1 (en) | 2004-06-28 | 2013-10-29 | Advanced Cardiovascular Systems, Inc. | Stent locking element and a method of securing a stent on a delivery system |
US8241554B1 (en) | 2004-06-29 | 2012-08-14 | Advanced Cardiovascular Systems, Inc. | Method of forming a stent pattern on a tube |
US20050287184A1 (en) | 2004-06-29 | 2005-12-29 | Hossainy Syed F A | Drug-delivery stent formulations for restenosis and vulnerable plaque |
US20060009839A1 (en) * | 2004-07-12 | 2006-01-12 | Scimed Life Systems, Inc. | Composite vascular graft including bioactive agent coating and biodegradable sheath |
WO2006017275A1 (en) | 2004-07-13 | 2006-02-16 | The University Of Tennessee Research Foundation | Adhesive composition for carrying therapeutic agents as delivery vehicle on coatings applied to vascular grafts |
EP1786499A2 (en) * | 2004-07-19 | 2007-05-23 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in a body organ |
CA2577634C (en) * | 2004-07-19 | 2015-07-07 | Protemix Corporation Limited | Synthesis of triethylenetetramines |
US8409167B2 (en) | 2004-07-19 | 2013-04-02 | Broncus Medical Inc | Devices for delivering substances through an extra-anatomic opening created in an airway |
US8048145B2 (en) | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
US7971333B2 (en) | 2006-05-30 | 2011-07-05 | Advanced Cardiovascular Systems, Inc. | Manufacturing process for polymetric stents |
US20060020330A1 (en) * | 2004-07-26 | 2006-01-26 | Bin Huang | Method of fabricating an implantable medical device with biaxially oriented polymers |
US8747878B2 (en) | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device by controlling crystalline structure |
US8747879B2 (en) | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device to reduce chance of late inflammatory response |
US7731890B2 (en) | 2006-06-15 | 2010-06-08 | Advanced Cardiovascular Systems, Inc. | Methods of fabricating stents with enhanced fracture toughness |
US8778256B1 (en) | 2004-09-30 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Deformation of a polymer tube in the fabrication of a medical article |
US7494665B1 (en) | 2004-07-30 | 2009-02-24 | Advanced Cardiovascular Systems, Inc. | Polymers containing siloxane monomers |
US8357391B2 (en) | 2004-07-30 | 2013-01-22 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable devices comprising poly (hydroxy-alkanoates) and diacid linkages |
US20060025852A1 (en) * | 2004-08-02 | 2006-02-02 | Armstrong Joseph R | Bioabsorbable self-expanding endolumenal devices |
US7311980B1 (en) | 2004-08-02 | 2007-12-25 | Advanced Cardiovascular Systems, Inc. | Polyactive/polylactic acid coatings for an implantable device |
US8980300B2 (en) | 2004-08-05 | 2015-03-17 | Advanced Cardiovascular Systems, Inc. | Plasticizers for coating compositions |
US7601382B2 (en) * | 2004-08-05 | 2009-10-13 | Boston Scientific Scimed, Inc. | Method of making a coated medical device |
US20060041102A1 (en) * | 2004-08-23 | 2006-02-23 | Advanced Cardiovascular Systems, Inc. | Implantable devices comprising biologically absorbable polymers having constant rate of degradation and methods for fabricating the same |
US9283099B2 (en) | 2004-08-25 | 2016-03-15 | Advanced Cardiovascular Systems, Inc. | Stent-catheter assembly with a releasable connection for stent retention |
US7648727B2 (en) | 2004-08-26 | 2010-01-19 | Advanced Cardiovascular Systems, Inc. | Methods for manufacturing a coated stent-balloon assembly |
US7244443B2 (en) * | 2004-08-31 | 2007-07-17 | Advanced Cardiovascular Systems, Inc. | Polymers of fluorinated monomers and hydrophilic monomers |
US7507433B2 (en) * | 2004-09-03 | 2009-03-24 | Boston Scientific Scimed, Inc. | Method of coating a medical device using an electrowetting process |
US7229471B2 (en) * | 2004-09-10 | 2007-06-12 | Advanced Cardiovascular Systems, Inc. | Compositions containing fast-leaching plasticizers for improved performance of medical devices |
US20060054604A1 (en) * | 2004-09-10 | 2006-03-16 | Saunders Richard J | Laser process to produce drug delivery channel in metal stents |
US7063720B2 (en) * | 2004-09-14 | 2006-06-20 | The Wallace Enterprises, Inc. | Covered stent with controlled therapeutic agent diffusion |
US20060064133A1 (en) | 2004-09-17 | 2006-03-23 | Cardiac Pacemakers, Inc. | System and method for deriving relative physiologic measurements using an external computing device |
US20060062822A1 (en) * | 2004-09-21 | 2006-03-23 | Medtronic Vascular, Inc. | Medical devices to treat or inhibit restenosis |
US8110211B2 (en) | 2004-09-22 | 2012-02-07 | Advanced Cardiovascular Systems, Inc. | Medicated coatings for implantable medical devices including polyacrylates |
US7901451B2 (en) | 2004-09-24 | 2011-03-08 | Biosensors International Group, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
CA2581855C (en) * | 2004-09-28 | 2012-11-27 | Cordis Corporation | Thin film medical device and delivery system |
US7875233B2 (en) | 2004-09-30 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a biaxially oriented implantable medical device |
US9011831B2 (en) * | 2004-09-30 | 2015-04-21 | Advanced Cardiovascular Systems, Inc. | Methacrylate copolymers for medical devices |
US8173062B1 (en) | 2004-09-30 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube in fabricating a medical article |
US8043553B1 (en) | 2004-09-30 | 2011-10-25 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube with a restraining surface in fabricating a medical article |
EP1814490A2 (en) * | 2004-10-06 | 2007-08-08 | Cook Incorporated | Medical device with bioactive agent |
US7166680B2 (en) | 2004-10-06 | 2007-01-23 | Advanced Cardiovascular Systems, Inc. | Blends of poly(ester amide) polymers |
US20070197538A1 (en) * | 2004-10-07 | 2007-08-23 | Mark Nesbit | Anti-vascular and anti-proliferation methods, therapies, and combinations employing specific tyrosine kinase inhibitors |
US20060085065A1 (en) * | 2004-10-15 | 2006-04-20 | Krause Arthur A | Stent with auxiliary treatment structure |
US20060083770A1 (en) * | 2004-10-15 | 2006-04-20 | Specialty Coating Systems, Inc. | Medical devices and methods of preparation and use |
US20060083859A1 (en) | 2004-10-20 | 2006-04-20 | Todd Robida | Magnetic levitation system for coating a device, a method of using the system, and device made by the system |
US20060088571A1 (en) * | 2004-10-21 | 2006-04-27 | Medtronic Vascular, Inc. | Biocompatible and hemocompatible polymer compositions |
US9114162B2 (en) | 2004-10-25 | 2015-08-25 | Celonova Biosciences, Inc. | Loadable polymeric particles for enhanced imaging in clinical applications and methods of preparing and using the same |
US9107850B2 (en) | 2004-10-25 | 2015-08-18 | Celonova Biosciences, Inc. | Color-coded and sized loadable polymeric particles for therapeutic and/or diagnostic applications and methods of preparing and using the same |
US20210299056A9 (en) | 2004-10-25 | 2021-09-30 | Varian Medical Systems, Inc. | Color-Coded Polymeric Particles of Predetermined Size for Therapeutic and/or Diagnostic Applications and Related Methods |
US20060089485A1 (en) * | 2004-10-27 | 2006-04-27 | Desnoyer Jessica R | End-capped poly(ester amide) copolymers |
US8603634B2 (en) | 2004-10-27 | 2013-12-10 | Abbott Cardiovascular Systems Inc. | End-capped poly(ester amide) copolymers |
US7390497B2 (en) | 2004-10-29 | 2008-06-24 | Advanced Cardiovascular Systems, Inc. | Poly(ester amide) filler blends for modulation of coating properties |
US20060095122A1 (en) * | 2004-10-29 | 2006-05-04 | Advanced Cardiovascular Systems, Inc. | Implantable devices comprising biologically absorbable star polymers and methods for fabricating the same |
US7481835B1 (en) | 2004-10-29 | 2009-01-27 | Advanced Cardiovascular Systems, Inc. | Encapsulated covered stent |
US20060093642A1 (en) * | 2004-11-03 | 2006-05-04 | Ranade Shrirang V | Method of incorporating carbon nanotubes in a medical appliance, a carbon nanotube medical appliance, and a medical appliance coated using carbon nanotube technology |
US7214759B2 (en) | 2004-11-24 | 2007-05-08 | Advanced Cardiovascular Systems, Inc. | Biologically absorbable coatings for implantable devices based on polyesters and methods for fabricating the same |
US7813808B1 (en) | 2004-11-24 | 2010-10-12 | Remon Medical Technologies Ltd | Implanted sensor system with optimized operational and sensing parameters |
US7588642B1 (en) | 2004-11-29 | 2009-09-15 | Advanced Cardiovascular Systems, Inc. | Abluminal stent coating apparatus and method using a brush assembly |
US8609123B2 (en) | 2004-11-29 | 2013-12-17 | Advanced Cardiovascular Systems, Inc. | Derivatized poly(ester amide) as a biobeneficial coating |
US20060115449A1 (en) * | 2004-11-30 | 2006-06-01 | Advanced Cardiovascular Systems, Inc. | Bioabsorbable, biobeneficial, tyrosine-based polymers for use in drug eluting stent coatings |
US7892592B1 (en) * | 2004-11-30 | 2011-02-22 | Advanced Cardiovascular Systems, Inc. | Coating abluminal surfaces of stents and other implantable medical devices |
JP2008522747A (en) * | 2004-12-08 | 2008-07-03 | クック・インコーポレイテッド | Medical devices coated with contrast media |
US20060127443A1 (en) * | 2004-12-09 | 2006-06-15 | Helmus Michael N | Medical devices having vapor deposited nanoporous coatings for controlled therapeutic agent delivery |
US7632307B2 (en) * | 2004-12-16 | 2009-12-15 | Advanced Cardiovascular Systems, Inc. | Abluminal, multilayer coating constructs for drug-delivery stents |
US8874204B2 (en) | 2004-12-20 | 2014-10-28 | Cardiac Pacemakers, Inc. | Implantable medical devices comprising isolated extracellular matrix |
US8060219B2 (en) * | 2004-12-20 | 2011-11-15 | Cardiac Pacemakers, Inc. | Epicardial patch including isolated extracellular matrix with pacing electrodes |
WO2006068516A1 (en) * | 2004-12-20 | 2006-06-29 | Protemix Corporation Limited | Implantable medical devices coated with or containing copper chelating compounds |
US7981065B2 (en) | 2004-12-20 | 2011-07-19 | Cardiac Pacemakers, Inc. | Lead electrode incorporating extracellular matrix |
US7604818B2 (en) | 2004-12-22 | 2009-10-20 | Advanced Cardiovascular Systems, Inc. | Polymers of fluorinated monomers and hydrocarbon monomers |
US7419504B2 (en) | 2004-12-27 | 2008-09-02 | Advanced Cardiovascular Systems, Inc. | Poly(ester amide) block copolymers |
US8007775B2 (en) | 2004-12-30 | 2011-08-30 | Advanced Cardiovascular Systems, Inc. | Polymers containing poly(hydroxyalkanoates) and agents for use with medical articles and methods of fabricating the same |
US7344601B2 (en) * | 2005-01-05 | 2008-03-18 | Boston Scientific Scimed, Inc. | Integrated cross-wire fixture for coating a device, a method of using the fixture, and a device made using the fixture |
US8287583B2 (en) | 2005-01-10 | 2012-10-16 | Taheri Laduca Llc | Apparatus and method for deploying an implantable device within the body |
US7202325B2 (en) | 2005-01-14 | 2007-04-10 | Advanced Cardiovascular Systems, Inc. | Poly(hydroxyalkanoate-co-ester amides) and agents for use with medical articles |
US7161076B2 (en) * | 2005-02-16 | 2007-01-09 | Chia-Chun Hsu | Button structure of saxophone |
US7491225B2 (en) | 2005-02-16 | 2009-02-17 | Boston Scientific Scimed, Inc. | System and method for deploying a drug-eluting external body and tissue scaffold |
US8735394B2 (en) * | 2005-02-18 | 2014-05-27 | Abraxis Bioscience, Llc | Combinations and modes of administration of therapeutic agents and combination therapy |
MX339142B (en) * | 2005-02-18 | 2016-05-13 | Abraxis Bioscience Llc | Combinations and modes of administration of therapeutic agents and combination therapy. |
US9452001B2 (en) * | 2005-02-22 | 2016-09-27 | Tecres S.P.A. | Disposable device for treatment of infections of human limbs |
US20060193891A1 (en) * | 2005-02-25 | 2006-08-31 | Robert Richard | Medical devices and therapeutic delivery devices composed of bioabsorbable polymers produced at room temperature, method of making the devices, and a system for making the devices |
AU2005100176A4 (en) * | 2005-03-01 | 2005-04-07 | Gym Tv Pty Ltd | Garbage bin clip |
US20060201601A1 (en) * | 2005-03-03 | 2006-09-14 | Icon Interventional Systems, Inc. | Flexible markers |
US20060200048A1 (en) * | 2005-03-03 | 2006-09-07 | Icon Medical Corp. | Removable sheath for device protection |
US20060264914A1 (en) * | 2005-03-03 | 2006-11-23 | Icon Medical Corp. | Metal alloys for medical devices |
US8323333B2 (en) | 2005-03-03 | 2012-12-04 | Icon Medical Corp. | Fragile structure protective coating |
US9107899B2 (en) | 2005-03-03 | 2015-08-18 | Icon Medical Corporation | Metal alloys for medical devices |
WO2006110197A2 (en) | 2005-03-03 | 2006-10-19 | Icon Medical Corp. | Polymer biodegradable medical device |
JP5335244B2 (en) | 2005-03-03 | 2013-11-06 | アイコン メディカル コーポレーション | Medical member using improved metal alloy |
US7540995B2 (en) | 2005-03-03 | 2009-06-02 | Icon Medical Corp. | Process for forming an improved metal alloy stent |
ATE538833T1 (en) * | 2005-03-18 | 2012-01-15 | Cook Medical Technologies Llc | WIRE GUIDES WITH NEW OUTER LAYER AREAS AND CHAMBERS TO IMPROVE HYDROPHILIC PROPERTIES AND RELEASE OF THERAPEUTIC ACTIVE INGREDIENTS |
US7700659B2 (en) | 2005-03-24 | 2010-04-20 | Advanced Cardiovascular Systems, Inc. | Implantable devices formed of non-fouling methacrylate or acrylate polymers |
US9381279B2 (en) | 2005-03-24 | 2016-07-05 | Abbott Cardiovascular Systems Inc. | Implantable devices formed on non-fouling methacrylate or acrylate polymers |
US20060224226A1 (en) * | 2005-03-31 | 2006-10-05 | Bin Huang | In-vivo radial orientation of a polymeric implantable medical device |
CA2604419C (en) | 2005-04-05 | 2015-03-24 | Elixir Medical Corporation | Degradable implantable medical devices |
US7381048B2 (en) | 2005-04-12 | 2008-06-03 | Advanced Cardiovascular Systems, Inc. | Stents with profiles for gripping a balloon catheter and molds for fabricating stents |
US7795467B1 (en) | 2005-04-26 | 2010-09-14 | Advanced Cardiovascular Systems, Inc. | Bioabsorbable, biobeneficial polyurethanes for use in medical devices |
US20060246210A1 (en) * | 2005-04-29 | 2006-11-02 | Vascular Architects Inc., A Delaware Corporation | Method for making a covered drug-eluting stent |
US8778375B2 (en) | 2005-04-29 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Amorphous poly(D,L-lactide) coating |
US7637941B1 (en) | 2005-05-11 | 2009-12-29 | Advanced Cardiovascular Systems, Inc. | Endothelial cell binding coatings for rapid encapsulation of bioerodable stents |
US7854760B2 (en) | 2005-05-16 | 2010-12-21 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US7291166B2 (en) * | 2005-05-18 | 2007-11-06 | Advanced Cardiovascular Systems, Inc. | Polymeric stent patterns |
WO2006130873A2 (en) * | 2005-06-01 | 2006-12-07 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
WO2006130836A2 (en) | 2005-06-02 | 2006-12-07 | Cordis Corporation | Patent foramen ovale closure device |
US7622070B2 (en) * | 2005-06-20 | 2009-11-24 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing an implantable polymeric medical device |
US20070009564A1 (en) * | 2005-06-22 | 2007-01-11 | Mcclain James B | Drug/polymer composite materials and methods of making the same |
US7823533B2 (en) | 2005-06-30 | 2010-11-02 | Advanced Cardiovascular Systems, Inc. | Stent fixture and method for reducing coating defects |
US20070038176A1 (en) * | 2005-07-05 | 2007-02-15 | Jan Weber | Medical devices with machined layers for controlled communications with underlying regions |
AU2006269419A1 (en) | 2005-07-07 | 2007-01-18 | Nellix, Inc. | Systems and methods for endovascular aneurysm treatment |
US8021676B2 (en) | 2005-07-08 | 2011-09-20 | Advanced Cardiovascular Systems, Inc. | Functionalized chemically inert polymers for coatings |
CA2615452C (en) | 2005-07-15 | 2015-03-31 | Micell Technologies, Inc. | Polymer coatings containing drug powder of controlled morphology |
US20090062909A1 (en) * | 2005-07-15 | 2009-03-05 | Micell Technologies, Inc. | Stent with polymer coating containing amorphous rapamycin |
US20070020312A1 (en) * | 2005-07-20 | 2007-01-25 | Desnoyer Jessica R | Method of fabricating a bioactive agent-releasing implantable medical device |
US7785647B2 (en) | 2005-07-25 | 2010-08-31 | Advanced Cardiovascular Systems, Inc. | Methods of providing antioxidants to a drug containing product |
US20070027530A1 (en) * | 2005-07-26 | 2007-02-01 | Medtronic Vascular, Inc. | Intraluminal device, catheter assembly, and method of use thereof |
WO2007016251A2 (en) * | 2005-07-28 | 2007-02-08 | Cook Incorporated | Implantable thromboresistant valve |
US7735449B1 (en) | 2005-07-28 | 2010-06-15 | Advanced Cardiovascular Systems, Inc. | Stent fixture having rounded support structures and method for use thereof |
US7658880B2 (en) | 2005-07-29 | 2010-02-09 | Advanced Cardiovascular Systems, Inc. | Polymeric stent polishing method and apparatus |
US7297758B2 (en) * | 2005-08-02 | 2007-11-20 | Advanced Cardiovascular Systems, Inc. | Method for extending shelf-life of constructs of semi-crystallizable polymers |
US20070038290A1 (en) * | 2005-08-15 | 2007-02-15 | Bin Huang | Fiber reinforced composite stents |
US7476245B2 (en) * | 2005-08-16 | 2009-01-13 | Advanced Cardiovascular Systems, Inc. | Polymeric stent patterns |
US9248034B2 (en) | 2005-08-23 | 2016-02-02 | Advanced Cardiovascular Systems, Inc. | Controlled disintegrating implantable medical devices |
US20070045255A1 (en) * | 2005-08-23 | 2007-03-01 | Klaus Kleine | Laser induced plasma machining with an optimized process gas |
US20070045252A1 (en) * | 2005-08-23 | 2007-03-01 | Klaus Kleine | Laser induced plasma machining with a process gas |
WO2007028092A1 (en) | 2005-09-01 | 2007-03-08 | Cordis Corporation | Patent foramen ovale closure method |
DE102005042372B3 (en) * | 2005-09-07 | 2007-01-18 | Dräger Medical AG & Co. KG | Artificial respiration and/or anesthetic device comprises hydrophilic polymer material surface that contains silver particle and mineral filler such as zeolite, silicon dioxide, titanium dioxide, alumina, and zircon oxide |
US20070061006A1 (en) * | 2005-09-14 | 2007-03-15 | Nathan Desatnik | Methods of making shape memory films by chemical vapor deposition and shape memory devices made thereby |
US8663308B2 (en) * | 2005-09-19 | 2014-03-04 | Cook Medical Technologies Llc | Graft with bioabsorbable support frame |
US20070067020A1 (en) * | 2005-09-22 | 2007-03-22 | Medtronic Vasular, Inc. | Intraluminal stent, delivery system, and a method of treating a vascular condition |
US20070077435A1 (en) * | 2005-10-05 | 2007-04-05 | Schachter Deborah M | Process for coating a medical device |
US7838023B2 (en) * | 2005-11-16 | 2010-11-23 | Nitromed, Inc. | Furoxan compounds, compositions and methods of use |
US20070128342A1 (en) * | 2005-12-02 | 2007-06-07 | Stenzel Eric B | Method and system for coating a medical device |
US20070128246A1 (en) * | 2005-12-06 | 2007-06-07 | Hossainy Syed F A | Solventless method for forming a coating |
US20070135909A1 (en) * | 2005-12-08 | 2007-06-14 | Desnoyer Jessica R | Adhesion polymers to improve stent retention |
US10029034B2 (en) * | 2005-12-15 | 2018-07-24 | CARDINAL HEALTH SWITZERLAND 515 GmbH | Drug-eluting articles with improved drug release profiles |
US7591841B2 (en) | 2005-12-16 | 2009-09-22 | Advanced Cardiovascular Systems, Inc. | Implantable devices for accelerated healing |
US7976891B1 (en) | 2005-12-16 | 2011-07-12 | Advanced Cardiovascular Systems, Inc. | Abluminal stent coating apparatus and method of using focused acoustic energy |
US7638156B1 (en) | 2005-12-19 | 2009-12-29 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for selectively coating a medical article |
US7867547B2 (en) | 2005-12-19 | 2011-01-11 | Advanced Cardiovascular Systems, Inc. | Selectively coating luminal surfaces of stents |
US8647654B2 (en) * | 2005-12-22 | 2014-02-11 | The Penn State Research Foundation | Method and systems for forming and using nanoengineered sculptured thin films |
US20070148390A1 (en) * | 2005-12-27 | 2007-06-28 | Specialty Coating Systems, Inc. | Fluorinated coatings |
US20070151961A1 (en) * | 2006-01-03 | 2007-07-05 | Klaus Kleine | Fabrication of an implantable medical device with a modified laser beam |
US20070156230A1 (en) * | 2006-01-04 | 2007-07-05 | Dugan Stephen R | Stents with radiopaque markers |
US8840660B2 (en) | 2006-01-05 | 2014-09-23 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US20080286325A1 (en) * | 2006-01-05 | 2008-11-20 | Med Institute, Inc. | Cyclodextrin elution media for medical device coatings comprising a taxane therapeutic agent |
US7919108B2 (en) * | 2006-03-10 | 2011-04-05 | Cook Incorporated | Taxane coatings for implantable medical devices |
US7951185B1 (en) | 2006-01-06 | 2011-05-31 | Advanced Cardiovascular Systems, Inc. | Delivery of a stent at an elevated temperature |
US20070179219A1 (en) * | 2006-01-31 | 2007-08-02 | Bin Huang | Method of fabricating an implantable medical device using gel extrusion and charge induced orientation |
US8089029B2 (en) | 2006-02-01 | 2012-01-03 | Boston Scientific Scimed, Inc. | Bioabsorbable metal medical device and method of manufacture |
WO2007092735A2 (en) | 2006-02-02 | 2007-08-16 | Innovative Bio Therapies | An extracorporeal cell-based therapeutic device and delivery system |
US20070190104A1 (en) * | 2006-02-13 | 2007-08-16 | Kamath Kalpana R | Coating comprising an adhesive polymeric material for a medical device and method of preparing the same |
US20070196428A1 (en) | 2006-02-17 | 2007-08-23 | Thierry Glauser | Nitric oxide generating medical devices |
US7601383B2 (en) | 2006-02-28 | 2009-10-13 | Advanced Cardiovascular Systems, Inc. | Coating construct containing poly (vinyl alcohol) |
US7713637B2 (en) | 2006-03-03 | 2010-05-11 | Advanced Cardiovascular Systems, Inc. | Coating containing PEGylated hyaluronic acid and a PEGylated non-hyaluronic acid polymer |
US7875284B2 (en) * | 2006-03-10 | 2011-01-25 | Cook Incorporated | Methods of manufacturing and modifying taxane coatings for implantable medical devices |
US20070231361A1 (en) * | 2006-03-28 | 2007-10-04 | Medtronic Vascular, Inc. | Use of Fatty Acids to Inhibit the Growth of Aneurysms |
US20070231363A1 (en) * | 2006-03-29 | 2007-10-04 | Yung-Ming Chen | Coatings formed from stimulus-sensitive material |
US7964210B2 (en) | 2006-03-31 | 2011-06-21 | Abbott Cardiovascular Systems Inc. | Degradable polymeric implantable medical devices with a continuous phase and discrete phase |
US8048150B2 (en) | 2006-04-12 | 2011-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis having a fiber meshwork disposed thereon |
US8303648B2 (en) * | 2006-04-25 | 2012-11-06 | Cook Medical Technologies Llc | Artificial venous valve containing therapeutic agent |
CA2996768C (en) | 2006-04-26 | 2020-12-08 | Micell Technologies, Inc. | Coatings containing multiple drugs |
US20070254012A1 (en) * | 2006-04-28 | 2007-11-01 | Ludwig Florian N | Controlled degradation and drug release in stents |
US20070259101A1 (en) * | 2006-05-02 | 2007-11-08 | Kleiner Lothar W | Microporous coating on medical devices |
US8304012B2 (en) | 2006-05-04 | 2012-11-06 | Advanced Cardiovascular Systems, Inc. | Method for drying a stent |
US7985441B1 (en) | 2006-05-04 | 2011-07-26 | Yiwen Tang | Purification of polymers for coating applications |
US8003156B2 (en) | 2006-05-04 | 2011-08-23 | Advanced Cardiovascular Systems, Inc. | Rotatable support elements for stents |
WO2007133479A2 (en) * | 2006-05-10 | 2007-11-22 | Cook Incorporated | Delivery of elastin-stabilizing compound within a body lumen |
US20070264303A1 (en) * | 2006-05-12 | 2007-11-15 | Liliana Atanasoska | Coating for medical devices comprising an inorganic or ceramic oxide and a therapeutic agent |
US20070275035A1 (en) * | 2006-05-24 | 2007-11-29 | Microchips, Inc. | Minimally Invasive Medical Implant Devices for Controlled Drug Delivery |
US7761968B2 (en) | 2006-05-25 | 2010-07-27 | Advanced Cardiovascular Systems, Inc. | Method of crimping a polymeric stent |
US8752268B2 (en) | 2006-05-26 | 2014-06-17 | Abbott Cardiovascular Systems Inc. | Method of making stents with radiopaque markers |
US7775178B2 (en) * | 2006-05-26 | 2010-08-17 | Advanced Cardiovascular Systems, Inc. | Stent coating apparatus and method |
US7951194B2 (en) | 2006-05-26 | 2011-05-31 | Abbott Cardiovascular Sysetms Inc. | Bioabsorbable stent with radiopaque coating |
US7842737B2 (en) | 2006-09-29 | 2010-11-30 | Abbott Cardiovascular Systems Inc. | Polymer blend-bioceramic composite implantable medical devices |
US7959940B2 (en) | 2006-05-30 | 2011-06-14 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical devices |
US20070282434A1 (en) * | 2006-05-30 | 2007-12-06 | Yunbing Wang | Copolymer-bioceramic composite implantable medical devices |
US8343530B2 (en) | 2006-05-30 | 2013-01-01 | Abbott Cardiovascular Systems Inc. | Polymer-and polymer blend-bioceramic composite implantable medical devices |
US9561351B2 (en) | 2006-05-31 | 2017-02-07 | Advanced Cardiovascular Systems, Inc. | Drug delivery spiral coil construct |
US20080058916A1 (en) * | 2006-05-31 | 2008-03-06 | Bin Huang | Method of fabricating polymeric self-expandable stent |
US8568764B2 (en) | 2006-05-31 | 2013-10-29 | Advanced Cardiovascular Systems, Inc. | Methods of forming coating layers for medical devices utilizing flash vaporization |
US8486135B2 (en) | 2006-06-01 | 2013-07-16 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from branched polymers |
US20070281073A1 (en) * | 2006-06-01 | 2007-12-06 | Gale David C | Enhanced adhesion of drug delivery coatings on stents |
US8034287B2 (en) | 2006-06-01 | 2011-10-11 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US20070282433A1 (en) * | 2006-06-01 | 2007-12-06 | Limon Timothy A | Stent with retention protrusions formed during crimping |
US8703167B2 (en) | 2006-06-05 | 2014-04-22 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices for controlled release of a hydrophilic drug and a hydrophobic drug |
US20080124372A1 (en) * | 2006-06-06 | 2008-05-29 | Hossainy Syed F A | Morphology profiles for control of agent release rates from polymer matrices |
US20070286882A1 (en) * | 2006-06-09 | 2007-12-13 | Yiwen Tang | Solvent systems for coating medical devices |
US8778376B2 (en) | 2006-06-09 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Copolymer comprising elastin pentapeptide block and hydrophilic block, and medical device and method of treating |
US20070286941A1 (en) * | 2006-06-13 | 2007-12-13 | Bin Huang | Surface treatment of a polymeric stent |
US20080095918A1 (en) * | 2006-06-14 | 2008-04-24 | Kleiner Lothar W | Coating construct with enhanced interfacial compatibility |
US8114150B2 (en) | 2006-06-14 | 2012-02-14 | Advanced Cardiovascular Systems, Inc. | RGD peptide attached to bioabsorbable stents |
US8603530B2 (en) | 2006-06-14 | 2013-12-10 | Abbott Cardiovascular Systems Inc. | Nanoshell therapy |
US8048448B2 (en) | 2006-06-15 | 2011-11-01 | Abbott Cardiovascular Systems Inc. | Nanoshells for drug delivery |
US8535372B1 (en) | 2006-06-16 | 2013-09-17 | Abbott Cardiovascular Systems Inc. | Bioabsorbable stent with prohealing layer |
US20070290412A1 (en) * | 2006-06-19 | 2007-12-20 | John Capek | Fabricating a stent with selected properties in the radial and axial directions |
US8333000B2 (en) | 2006-06-19 | 2012-12-18 | Advanced Cardiovascular Systems, Inc. | Methods for improving stent retention on a balloon catheter |
US8017237B2 (en) | 2006-06-23 | 2011-09-13 | Abbott Cardiovascular Systems, Inc. | Nanoshells on polymers |
US9072820B2 (en) | 2006-06-26 | 2015-07-07 | Advanced Cardiovascular Systems, Inc. | Polymer composite stent with polymer particles |
US8128688B2 (en) | 2006-06-27 | 2012-03-06 | Abbott Cardiovascular Systems Inc. | Carbon coating on an implantable device |
US20070299511A1 (en) * | 2006-06-27 | 2007-12-27 | Gale David C | Thin stent coating |
WO2008005297A2 (en) * | 2006-06-29 | 2008-01-10 | Massachusetts Institute Of Technology | Coating of devices with effector compounds |
US7794776B1 (en) | 2006-06-29 | 2010-09-14 | Abbott Cardiovascular Systems Inc. | Modification of polymer stents with radiation |
US8956640B2 (en) * | 2006-06-29 | 2015-02-17 | Advanced Cardiovascular Systems, Inc. | Block copolymers including a methoxyethyl methacrylate midblock |
US7740791B2 (en) | 2006-06-30 | 2010-06-22 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a stent with features by blow molding |
US20080008736A1 (en) * | 2006-07-06 | 2008-01-10 | Thierry Glauser | Random copolymers of methacrylates and acrylates |
US9028859B2 (en) | 2006-07-07 | 2015-05-12 | Advanced Cardiovascular Systems, Inc. | Phase-separated block copolymer coatings for implantable medical devices |
US20080009938A1 (en) * | 2006-07-07 | 2008-01-10 | Bin Huang | Stent with a radiopaque marker and method for making the same |
US7823263B2 (en) | 2006-07-11 | 2010-11-02 | Abbott Cardiovascular Systems Inc. | Method of removing stent islands from a stent |
US20080014244A1 (en) * | 2006-07-13 | 2008-01-17 | Gale David C | Implantable medical devices and coatings therefor comprising physically crosslinked block copolymers |
US7998404B2 (en) | 2006-07-13 | 2011-08-16 | Advanced Cardiovascular Systems, Inc. | Reduced temperature sterilization of stents |
US7757543B2 (en) | 2006-07-13 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Radio frequency identification monitoring of stents |
WO2008008291A2 (en) * | 2006-07-13 | 2008-01-17 | Icon Medical Corp. | Stent |
US8685430B1 (en) | 2006-07-14 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Tailored aliphatic polyesters for stent coatings |
US7794495B2 (en) | 2006-07-17 | 2010-09-14 | Advanced Cardiovascular Systems, Inc. | Controlled degradation of stents |
US7886419B2 (en) | 2006-07-18 | 2011-02-15 | Advanced Cardiovascular Systems, Inc. | Stent crimping apparatus and method |
US7955268B2 (en) * | 2006-07-21 | 2011-06-07 | Cardiac Pacemakers, Inc. | Multiple sensor deployment |
US20080091262A1 (en) * | 2006-10-17 | 2008-04-17 | Gale David C | Drug delivery after biodegradation of the stent scaffolding |
US8016879B2 (en) | 2006-08-01 | 2011-09-13 | Abbott Cardiovascular Systems Inc. | Drug delivery after biodegradation of the stent scaffolding |
US9265866B2 (en) * | 2006-08-01 | 2016-02-23 | Abbott Cardiovascular Systems Inc. | Composite polymeric and metallic stent with radiopacity |
JP2009545407A (en) * | 2006-08-02 | 2009-12-24 | ボストン サイエンティフィック サイムド,インコーポレイテッド | End prosthesis with 3D decomposition control |
US8703169B1 (en) | 2006-08-15 | 2014-04-22 | Abbott Cardiovascular Systems Inc. | Implantable device having a coating comprising carrageenan and a biostable polymer |
US9173733B1 (en) | 2006-08-21 | 2015-11-03 | Abbott Cardiovascular Systems Inc. | Tracheobronchial implantable medical device and methods of use |
EP2089072B1 (en) * | 2006-09-06 | 2014-06-04 | Boston Scientific Limited | Medical devices having a coating for promoting endothelial cell adhesion |
US7923022B2 (en) | 2006-09-13 | 2011-04-12 | Advanced Cardiovascular Systems, Inc. | Degradable polymeric implantable medical devices with continuous phase and discrete phase |
WO2008034013A2 (en) | 2006-09-15 | 2008-03-20 | Boston Scientific Limited | Medical devices and methods of making the same |
DE602007011114D1 (en) * | 2006-09-15 | 2011-01-20 | Boston Scient Scimed Inc | BIODEGRADABLE ENDOPROTHESIS WITH BIOSTABILES INORGANIC LAYERS |
JP2010503489A (en) | 2006-09-15 | 2010-02-04 | ボストン サイエンティフィック リミテッド | Biodegradable endoprosthesis and method for producing the same |
WO2008034066A1 (en) * | 2006-09-15 | 2008-03-20 | Boston Scientific Limited | Bioerodible endoprostheses and methods of making the same |
WO2008034047A2 (en) * | 2006-09-15 | 2008-03-20 | Boston Scientific Limited | Endoprosthesis with adjustable surface features |
WO2008036554A2 (en) * | 2006-09-18 | 2008-03-27 | Boston Scientific Limited | Endoprostheses |
WO2008036548A2 (en) | 2006-09-18 | 2008-03-27 | Boston Scientific Limited | Endoprostheses |
WO2008039749A2 (en) * | 2006-09-25 | 2008-04-03 | Surmodics, Inc. | Multi-layered coatings and methods for controlling elution of active agents |
US10188826B2 (en) * | 2006-09-29 | 2019-01-29 | Covidien Lp | Catheters including antimicrobial sleeve and methods of making catheters |
WO2008042909A2 (en) | 2006-10-02 | 2008-04-10 | Micell Technologies Inc. | Surgical sutures having increased strength |
WO2008045184A1 (en) * | 2006-10-05 | 2008-04-17 | Boston Scientific Limited | Polymer-free coatings for medical devices formed by plasma electrolytic deposition |
ES2378905T3 (en) * | 2006-10-10 | 2012-04-19 | Celonova Biosciences, Inc. | Bioprotics heart valve with polyphosphazene |
JP2010533505A (en) * | 2006-10-10 | 2010-10-28 | セロノバ バイオサイエンシーズ, インコーポレイテッド | Compositions and devices comprising silicone and certain polyphosphazenes |
US20080097591A1 (en) | 2006-10-20 | 2008-04-24 | Biosensors International Group | Drug-delivery endovascular stent and method of use |
US8067055B2 (en) * | 2006-10-20 | 2011-11-29 | Biosensors International Group, Ltd. | Drug-delivery endovascular stent and method of use |
US20080097577A1 (en) * | 2006-10-20 | 2008-04-24 | Boston Scientific Scimed, Inc. | Medical device hydrogen surface treatment by electrochemical reduction |
CA2667228C (en) | 2006-10-23 | 2015-07-14 | Micell Technologies, Inc. | Holder for electrically charging a substrate during coating |
US20080103584A1 (en) * | 2006-10-25 | 2008-05-01 | Biosensors International Group | Temporal Intraluminal Stent, Methods of Making and Using |
EP2086571A2 (en) | 2006-11-07 | 2009-08-12 | Genentech, Inc. | Tissue plasminogen activator variant uses |
US8414525B2 (en) * | 2006-11-20 | 2013-04-09 | Lutonix, Inc. | Drug releasing coatings for medical devices |
US8414910B2 (en) | 2006-11-20 | 2013-04-09 | Lutonix, Inc. | Drug releasing coatings for medical devices |
US8414526B2 (en) | 2006-11-20 | 2013-04-09 | Lutonix, Inc. | Medical device rapid drug releasing coatings comprising oils, fatty acids, and/or lipids |
US9737640B2 (en) | 2006-11-20 | 2017-08-22 | Lutonix, Inc. | Drug releasing coatings for medical devices |
US9700704B2 (en) | 2006-11-20 | 2017-07-11 | Lutonix, Inc. | Drug releasing coatings for balloon catheters |
US20080276935A1 (en) | 2006-11-20 | 2008-11-13 | Lixiao Wang | Treatment of asthma and chronic obstructive pulmonary disease with anti-proliferate and anti-inflammatory drugs |
US8430055B2 (en) | 2008-08-29 | 2013-04-30 | Lutonix, Inc. | Methods and apparatuses for coating balloon catheters |
US8998846B2 (en) | 2006-11-20 | 2015-04-07 | Lutonix, Inc. | Drug releasing coatings for balloon catheters |
US8425459B2 (en) | 2006-11-20 | 2013-04-23 | Lutonix, Inc. | Medical device rapid drug releasing coatings comprising a therapeutic agent and a contrast agent |
US20080175887A1 (en) | 2006-11-20 | 2008-07-24 | Lixiao Wang | Treatment of Asthma and Chronic Obstructive Pulmonary Disease With Anti-proliferate and Anti-inflammatory Drugs |
EP2097119A4 (en) * | 2006-11-21 | 2012-10-17 | Abbott Lab | Use of a terpolymer of tetrafluoroethylene, hexafluoropropylene, and vinylidene fluoride in drug eluting coatings |
US7713541B1 (en) | 2006-11-21 | 2010-05-11 | Abbott Cardiovascular Systems Inc. | Zwitterionic terpolymers, method of making and use on medical devices |
US20080118541A1 (en) * | 2006-11-21 | 2008-05-22 | Abbott Laboratories | Use of a terpolymer of tetrafluoroethylene, hexafluoropropylene, and vinylidene fluoride in drug eluting coatings on medical devices |
WO2008063935A2 (en) * | 2006-11-22 | 2008-05-29 | Broncus Technologies, Inc. | Devices for creating passages and sensing for blood vessels |
US8099849B2 (en) | 2006-12-13 | 2012-01-24 | Abbott Cardiovascular Systems Inc. | Optimizing fracture toughness of polymeric stent |
US8597673B2 (en) | 2006-12-13 | 2013-12-03 | Advanced Cardiovascular Systems, Inc. | Coating of fast absorption or dissolution |
US8017141B2 (en) * | 2006-12-15 | 2011-09-13 | Advanced Cardiovascular Systems, Inc. | Coatings of acrylamide-based copolymers |
ES2506144T3 (en) | 2006-12-28 | 2014-10-13 | Boston Scientific Limited | Bioerodible endoprosthesis and their manufacturing procedure |
US11426494B2 (en) | 2007-01-08 | 2022-08-30 | MT Acquisition Holdings LLC | Stents having biodegradable layers |
CA2679712C (en) | 2007-01-08 | 2016-11-15 | Micell Technologies, Inc. | Stents having biodegradable layers |
WO2008097511A2 (en) * | 2007-02-07 | 2008-08-14 | Cook Incorporated | Medical device coatings for releasing a therapeutic agent at multiple rates |
JP2010517703A (en) | 2007-02-09 | 2010-05-27 | タヘリ ラドュカ エルエルシー | Vascular graft and method for processing the same |
US8221505B2 (en) | 2007-02-22 | 2012-07-17 | Cook Medical Technologies Llc | Prosthesis having a sleeve valve |
ATE554819T1 (en) * | 2007-03-14 | 2012-05-15 | Terumo Corp | GUIDE WIRE |
US8646444B2 (en) * | 2007-03-27 | 2014-02-11 | Electrolux Home Products, Inc. | Glide rack |
US20080243228A1 (en) * | 2007-03-28 | 2008-10-02 | Yunbing Wang | Implantable medical devices fabricated from block copolymers |
US8262723B2 (en) | 2007-04-09 | 2012-09-11 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from polymer blends with star-block copolymers |
WO2008127966A1 (en) * | 2007-04-11 | 2008-10-23 | Boston Scientific Scimed, Inc. | Photoresist coating to apply a coating to select areas of a medical device |
CA2684482C (en) * | 2007-04-17 | 2014-08-12 | Micell Technologies, Inc. | Stents having biodegradable layers |
US20080286332A1 (en) | 2007-05-14 | 2008-11-20 | Pacetti Stephen D | Implantable medical devices with a topcoat layer of phosphoryl choline acrylate polymer for reduced thrombosis, and improved mechanical properties |
US8147769B1 (en) | 2007-05-16 | 2012-04-03 | Abbott Cardiovascular Systems Inc. | Stent and delivery system with reduced chemical degradation |
AU2008256684B2 (en) | 2007-05-25 | 2012-06-14 | Micell Technologies, Inc. | Polymer films for medical device coating |
US9056155B1 (en) | 2007-05-29 | 2015-06-16 | Abbott Cardiovascular Systems Inc. | Coatings having an elastic primer layer |
US7829008B2 (en) | 2007-05-30 | 2010-11-09 | Abbott Cardiovascular Systems Inc. | Fabricating a stent from a blow molded tube |
US7959857B2 (en) | 2007-06-01 | 2011-06-14 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8202528B2 (en) | 2007-06-05 | 2012-06-19 | Abbott Cardiovascular Systems Inc. | Implantable medical devices with elastomeric block copolymer coatings |
US20080306582A1 (en) * | 2007-06-05 | 2008-12-11 | Yunbing Wang | Implantable medical devices with elastomeric copolymer coatings |
US8293260B2 (en) | 2007-06-05 | 2012-10-23 | Abbott Cardiovascular Systems Inc. | Elastomeric copolymer coatings containing poly (tetramethyl carbonate) for implantable medical devices |
JP2008305262A (en) * | 2007-06-08 | 2008-12-18 | Konica Minolta Business Technologies Inc | Printer introduction method in server and thin client environment |
US8425591B1 (en) | 2007-06-11 | 2013-04-23 | Abbott Cardiovascular Systems Inc. | Methods of forming polymer-bioceramic composite medical devices with bioceramic particles |
JP2010530769A (en) * | 2007-06-14 | 2010-09-16 | カーディアック ペースメイカーズ, インコーポレイテッド | Body pressure measuring device and method |
US8048441B2 (en) | 2007-06-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Nanobead releasing medical devices |
US8109904B1 (en) | 2007-06-25 | 2012-02-07 | Abbott Cardiovascular Systems Inc. | Drug delivery medical devices |
US7901452B2 (en) | 2007-06-27 | 2011-03-08 | Abbott Cardiovascular Systems Inc. | Method to fabricate a stent having selected morphology to reduce restenosis |
US7955381B1 (en) | 2007-06-29 | 2011-06-07 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical device with different types of bioceramic particles |
WO2009011895A1 (en) * | 2007-07-17 | 2009-01-22 | Silverleaf Materials, Inc | Wound closure method apparatus and system |
DE102007034364A1 (en) * | 2007-07-24 | 2009-01-29 | Biotronik Vi Patent Ag | Degradable metal stent with active ingredient-containing coating |
DE102007034363A1 (en) * | 2007-07-24 | 2009-01-29 | Biotronik Vi Patent Ag | endoprosthesis |
US20090041845A1 (en) * | 2007-08-08 | 2009-02-12 | Lothar Walter Kleiner | Implantable medical devices having thin absorbable coatings |
US8271101B2 (en) * | 2007-08-29 | 2012-09-18 | Advanced Bionics | Modular drug delivery system for minimizing trauma during and after insertion of a cochlear lead |
WO2009029866A2 (en) * | 2007-08-29 | 2009-03-05 | Advanced Bionics, Llc | Minimizing trauma during and after insertion of a cochlear lead |
US8052745B2 (en) | 2007-09-13 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis |
JP2010539245A (en) | 2007-09-14 | 2010-12-16 | 日東電工株式会社 | Drug carrier |
KR100930167B1 (en) * | 2007-09-19 | 2009-12-07 | 삼성전기주식회사 | Ultra wide angle optical system |
WO2009051780A1 (en) * | 2007-10-19 | 2009-04-23 | Micell Technologies, Inc. | Drug coated stents |
US8142490B2 (en) | 2007-10-24 | 2012-03-27 | Cordis Corporation | Stent segments axially connected by thin film |
US20090110730A1 (en) * | 2007-10-30 | 2009-04-30 | Celonova Biosciences, Inc. | Loadable Polymeric Particles for Marking or Masking Individuals and Methods of Preparing and Using the Same |
US20090118809A1 (en) * | 2007-11-02 | 2009-05-07 | Torsten Scheuermann | Endoprosthesis with porous reservoir and non-polymer diffusion layer |
US20090118813A1 (en) * | 2007-11-02 | 2009-05-07 | Torsten Scheuermann | Nano-patterned implant surfaces |
US20090118818A1 (en) * | 2007-11-02 | 2009-05-07 | Boston Scientific Scimed, Inc. | Endoprosthesis with coating |
WO2009065087A1 (en) | 2007-11-14 | 2009-05-22 | Biosensors International Group, Ltd. | Automated coating apparatus and method |
US7828840B2 (en) * | 2007-11-15 | 2010-11-09 | Med Institute, Inc. | Medical devices and methods for local delivery of angiotensin II type 2 receptor antagonists |
US8257434B2 (en) | 2007-12-18 | 2012-09-04 | Cormatrix Cardiovascular, Inc. | Prosthetic tissue valve |
US8679176B2 (en) | 2007-12-18 | 2014-03-25 | Cormatrix Cardiovascular, Inc | Prosthetic tissue valve |
US8361538B2 (en) | 2007-12-19 | 2013-01-29 | Abbott Laboratories | Methods for applying an application material to an implantable device |
US8211489B2 (en) * | 2007-12-19 | 2012-07-03 | Abbott Cardiovascular Systems, Inc. | Methods for applying an application material to an implantable device |
US20090162417A1 (en) * | 2007-12-21 | 2009-06-25 | Cook Incorporated | Drug eluting ocular conformer |
US20090186068A1 (en) * | 2008-01-18 | 2009-07-23 | Chameleon Scientific Corporation | Atomic plasma deposited coatings for drug release |
US20090192580A1 (en) * | 2008-01-28 | 2009-07-30 | Shrojalkumar Desai | Medical electrical lead with biocompatible lead body coating |
US20090192577A1 (en) * | 2008-01-28 | 2009-07-30 | Shrojalkumar Desai | Medical electrical lead with coated conductor |
FR2928084A1 (en) * | 2008-02-28 | 2009-09-04 | Cie Euro Etude Rech Paroscopie | IMPLANTABLE DEVICE AND METHOD FOR MANUFACTURING THE SAME |
EP2271294B1 (en) | 2008-04-17 | 2018-03-28 | Micell Technologies, Inc. | Stents having bioabsorbable layers |
CA2721950A1 (en) | 2008-04-25 | 2009-10-29 | Nellix, Inc. | Stent graft delivery system |
US7998192B2 (en) | 2008-05-09 | 2011-08-16 | Boston Scientific Scimed, Inc. | Endoprostheses |
AU2009256084A1 (en) | 2008-06-04 | 2009-12-10 | Nellix, Inc. | Sealing apparatus and methods of use |
US8236046B2 (en) | 2008-06-10 | 2012-08-07 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US20090312832A1 (en) * | 2008-06-13 | 2009-12-17 | Cook Incorporated | Slip layer delivery catheter |
WO2010071692A2 (en) * | 2008-06-18 | 2010-06-24 | Innovative Biotherapies, Inc. | Methods for enhanced propagation of cells |
US20090319026A1 (en) * | 2008-06-20 | 2009-12-24 | Boston Scientific Scimed, Inc. | Composite Stent with Reservoirs for Drug Delivery and Methods of Manufacturing |
US10898620B2 (en) * | 2008-06-20 | 2021-01-26 | Razmodics Llc | Composite stent having multi-axial flexibility and method of manufacture thereof |
US8206635B2 (en) | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
US20100042202A1 (en) * | 2008-08-13 | 2010-02-18 | Kamal Ramzipoor | Composite stent having multi-axial flexibility |
JP2011528275A (en) | 2008-07-17 | 2011-11-17 | ミセル テクノロジーズ,インク. | Drug delivery medical device |
US7985252B2 (en) | 2008-07-30 | 2011-07-26 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
JP5393684B2 (en) * | 2008-08-11 | 2014-01-22 | テルモ株式会社 | Medical tools |
US9198968B2 (en) | 2008-09-15 | 2015-12-01 | The Spectranetics Corporation | Local delivery of water-soluble or water-insoluble therapeutic agents to the surface of body lumens |
US8114429B2 (en) | 2008-09-15 | 2012-02-14 | Cv Ingenuity Corp. | Local delivery of water-soluble or water-insoluble therapeutic agents to the surface of body lumens |
US8257722B2 (en) | 2008-09-15 | 2012-09-04 | Cv Ingenuity Corp. | Local delivery of water-soluble or water-insoluble therapeutic agents to the surface of body lumens |
US9220811B2 (en) * | 2008-09-22 | 2015-12-29 | Boston Scientific Scimed, Inc. | Implantable or insertable medical devices |
US8226603B2 (en) | 2008-09-25 | 2012-07-24 | Abbott Cardiovascular Systems Inc. | Expandable member having a covering formed of a fibrous matrix for intraluminal drug delivery |
US8049061B2 (en) | 2008-09-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Expandable member formed of a fibrous matrix having hydrogel polymer for intraluminal drug delivery |
US8076529B2 (en) | 2008-09-26 | 2011-12-13 | Abbott Cardiovascular Systems, Inc. | Expandable member formed of a fibrous matrix for intraluminal drug delivery |
US8382824B2 (en) | 2008-10-03 | 2013-02-26 | Boston Scientific Scimed, Inc. | Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides |
US20100106242A1 (en) * | 2008-10-23 | 2010-04-29 | Abbott Cardiovascular Systems Inc. | Stent and method for making a stent |
US20100137908A1 (en) * | 2008-12-01 | 2010-06-03 | Zimmer Spine, Inc. | Dynamic Stabilization System Components Including Readily Visualized Polymeric Compositions |
DE102008054920A1 (en) * | 2008-12-18 | 2010-07-01 | Biotronik Vi Patent Ag | Implant and method for producing a layer structure |
US8834913B2 (en) | 2008-12-26 | 2014-09-16 | Battelle Memorial Institute | Medical implants and methods of making medical implants |
WO2010091100A1 (en) | 2009-02-03 | 2010-08-12 | Abbott Cardiovascular Systems Inc. | Multiple beam laser system for forming stents |
US8872062B2 (en) * | 2009-02-03 | 2014-10-28 | Abbott Cardiovascular Systems Inc. | Laser cutting process for forming stents |
WO2010091106A1 (en) * | 2009-02-03 | 2010-08-12 | Abbott Cardiovascular Systems Inc. | Improved laser cutting system |
CA2752899A1 (en) * | 2009-02-18 | 2010-08-26 | Cormatrix Cardiovascular, Inc. | Compositions and methods for preventing cardiac arrhythmia |
EP2403546A2 (en) | 2009-03-02 | 2012-01-11 | Boston Scientific Scimed, Inc. | Self-buffering medical implants |
US8574612B2 (en) * | 2009-03-04 | 2013-11-05 | Boston Scientific Scimed, Inc. | Medical devices having a coating of biologic macromolecules |
CA2756307C (en) * | 2009-03-23 | 2017-08-08 | Micell Technologies, Inc. | Peripheral stents having layers and reinforcement fibers |
WO2010111238A2 (en) * | 2009-03-23 | 2010-09-30 | Micell Technologies, Inc. | Improved biodegradable polymers |
US20100239635A1 (en) * | 2009-03-23 | 2010-09-23 | Micell Technologies, Inc. | Drug delivery medical device |
US20100247600A1 (en) * | 2009-03-24 | 2010-09-30 | Warsaw Orthopedic, Inc. | Therapeutic drug eluting implant cover and method of making the same |
CN102481195B (en) | 2009-04-01 | 2015-03-25 | 米歇尔技术公司 | Drug delivery medical device |
US9414864B2 (en) | 2009-04-15 | 2016-08-16 | Warsaw Orthopedic, Inc. | Anterior spinal plate with preformed drug-eluting device affixed thereto |
US9078712B2 (en) | 2009-04-15 | 2015-07-14 | Warsaw Orthopedic, Inc. | Preformed drug-eluting device to be affixed to an anterior spinal plate |
WO2010121187A2 (en) | 2009-04-17 | 2010-10-21 | Micell Techologies, Inc. | Stents having controlled elution |
US20100274352A1 (en) * | 2009-04-24 | 2010-10-28 | Boston Scientific Scrimed, Inc. | Endoprosthesis with Selective Drug Coatings |
US9289540B2 (en) * | 2009-05-08 | 2016-03-22 | Greatbatch Ltd. | Surface modification for coating |
WO2010151269A1 (en) | 2009-06-26 | 2010-12-29 | Biotic Laboratories, Inc. | Para-xylylene based multilayer drug elution devices |
US8382818B2 (en) | 2009-07-02 | 2013-02-26 | Tryton Medical, Inc. | Ostium support for treating vascular bifurcations |
EP2453834A4 (en) | 2009-07-16 | 2014-04-16 | Micell Technologies Inc | Drug delivery medical device |
JP2011528608A (en) * | 2009-09-29 | 2011-11-24 | エム. アイ. テック カンパニー, インコーポレイテッド | Transplantation tube and coating method thereof |
BR112012007578B1 (en) * | 2009-09-30 | 2021-04-20 | Terumo Kabushiki Kaisha | stent |
US8016872B2 (en) * | 2009-12-22 | 2011-09-13 | Cook Medical Technologies Llc | Deployment and dilation with an expandable roll sock delivery system |
US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
US8568471B2 (en) | 2010-01-30 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds |
US8808353B2 (en) | 2010-01-30 | 2014-08-19 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds having a low crossing profile |
US11369498B2 (en) | 2010-02-02 | 2022-06-28 | MT Acquisition Holdings LLC | Stent and stent delivery system with improved deliverability |
US8398916B2 (en) | 2010-03-04 | 2013-03-19 | Icon Medical Corp. | Method for forming a tubular medical device |
WO2011119536A1 (en) | 2010-03-22 | 2011-09-29 | Abbott Cardiovascular Systems Inc. | Stent delivery system having a fibrous matrix covering with improved stent retention |
US8668732B2 (en) | 2010-03-23 | 2014-03-11 | Boston Scientific Scimed, Inc. | Surface treated bioerodible metal endoprostheses |
US8795762B2 (en) | 2010-03-26 | 2014-08-05 | Battelle Memorial Institute | System and method for enhanced electrostatic deposition and surface coatings |
NZ703047A (en) | 2010-03-29 | 2016-11-25 | Abraxis Bioscience Llc | Methods of enhancing drug delivery and effectiveness of therapeutic agents |
CA3087813A1 (en) | 2010-03-29 | 2011-10-06 | Abraxis Bioscience, Llc | Methods of treating cancer |
US8685433B2 (en) | 2010-03-31 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Absorbable coating for implantable device |
US9801738B2 (en) | 2010-04-14 | 2017-10-31 | Northwestern University | Liquid cast biodegradable arterial stent |
WO2011133655A1 (en) | 2010-04-22 | 2011-10-27 | Micell Technologies, Inc. | Stents and other devices having extracellular matrix coating |
NZ604031A (en) | 2010-06-04 | 2015-05-29 | Abraxis Bioscience Llc | Methods of treatment of pancreatic cancer |
US8389041B2 (en) | 2010-06-17 | 2013-03-05 | Abbott Cardiovascular Systems, Inc. | Systems and methods for rotating and coating an implantable device |
CA2805631C (en) | 2010-07-16 | 2018-07-31 | Micell Technologies, Inc. | Drug delivery medical device |
US8556511B2 (en) | 2010-09-08 | 2013-10-15 | Abbott Cardiovascular Systems, Inc. | Fluid bearing to support stent tubing during laser cutting |
WO2012034079A2 (en) | 2010-09-09 | 2012-03-15 | Micell Technologies, Inc. | Macrolide dosage forms |
SG188636A1 (en) | 2010-10-01 | 2013-05-31 | Univ Tennessee Res Foundation | Multigraft copolymers as superelastomers |
US8833402B2 (en) * | 2010-12-30 | 2014-09-16 | Cook Medical Technologies Llc | Woven fabric having composite yarns for endoluminal devices |
US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
US8936827B2 (en) | 2011-02-25 | 2015-01-20 | Abbott Cardiovascular Systems Inc. | Methods of loading a hollow stent with a drug or drug formulation |
US20120216908A1 (en) | 2011-02-25 | 2012-08-30 | Abbott Cardiovascular Systems Inc. | Methods Of Drug Loading A Hollow Stent By Immersion |
US9238514B2 (en) | 2011-02-25 | 2016-01-19 | Abbott Cardiovascular Systems Inc. | Vacuum chamber and apparatus for loading material into a stent strut |
US8757219B2 (en) | 2011-02-25 | 2014-06-24 | Abbott Cardiovascular Systems Inc. | Suction pump and apparatus for loading material into a stent strut |
US9585780B2 (en) | 2011-02-25 | 2017-03-07 | Abbott Cardiovascular Systems Inc. | Pressure chamber and apparatus for loading material into a stent strut |
US8733408B2 (en) | 2011-02-25 | 2014-05-27 | Abbott Cardiovascular Systems Inc. | Cover sleeve and apparatus for loading material into a stent strut |
US8927047B2 (en) | 2011-02-25 | 2015-01-06 | Abbott Cardiovascular Systems Inc. | Methods of drug loading a hollow stent with a high viscosity formulation |
JP5976777B2 (en) | 2011-04-06 | 2016-08-24 | エンドーロジックス インコーポレイテッド | Methods and systems for the treatment of intravascular aneurysms |
JP2014521381A (en) | 2011-05-13 | 2014-08-28 | ブロンカス テクノロジーズ, インコーポレイテッド | Methods and devices for tissue ablation |
US8709034B2 (en) | 2011-05-13 | 2014-04-29 | Broncus Medical Inc. | Methods and devices for diagnosing, monitoring, or treating medical conditions through an opening through an airway wall |
AU2012262549B2 (en) | 2011-05-27 | 2016-02-11 | Cormatrix Cardiovascular, Inc. | Extracellular matrix material valve conduit and methods of making thereof |
WO2012166819A1 (en) | 2011-05-31 | 2012-12-06 | Micell Technologies, Inc. | System and process for formation of a time-released, drug-eluting transferable coating |
CA2841360A1 (en) | 2011-07-15 | 2013-01-24 | Micell Technologies, Inc. | Drug delivery medical device |
US8726483B2 (en) | 2011-07-29 | 2014-05-20 | Abbott Cardiovascular Systems Inc. | Methods for uniform crimping and deployment of a polymer scaffold |
US20130046375A1 (en) | 2011-08-17 | 2013-02-21 | Meng Chen | Plasma modified medical devices and methods |
US10188772B2 (en) | 2011-10-18 | 2019-01-29 | Micell Technologies, Inc. | Drug delivery medical device |
ITMI20112121A1 (en) * | 2011-11-22 | 2013-05-23 | Getters Spa | SYSTEM FOR THE PRODUCTION OF HOT WATER AND AUTOMATIC DRINK OF DRINKS THAT USES IT |
WO2013078235A1 (en) | 2011-11-23 | 2013-05-30 | Broncus Medical Inc | Methods and devices for diagnosing, monitoring, or treating medical conditions through an opening through an airway wall |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
US8998977B2 (en) * | 2012-04-13 | 2015-04-07 | Medtronic Vascular, Inc. | Hollow drug-filled stent and method of forming hollow drug-filled stent |
KR101362446B1 (en) * | 2012-05-10 | 2014-02-11 | 이훈범 | Filler for wrinkle removing |
US9956385B2 (en) | 2012-06-28 | 2018-05-01 | The Spectranetics Corporation | Post-processing of a medical device to control morphology and mechanical properties |
EP2912121B1 (en) | 2012-10-29 | 2019-09-25 | Ariste Medical, LLC | Polymer coating compositions and coated products |
US8847412B2 (en) * | 2012-11-09 | 2014-09-30 | Invensas Corporation | Microelectronic assembly with thermally and electrically conductive underfill |
AU2014214700B2 (en) | 2013-02-11 | 2018-01-18 | Cook Medical Technologies Llc | Expandable support frame and medical device |
KR20150143476A (en) | 2013-03-12 | 2015-12-23 | 미셀 테크놀로지즈, 인코포레이티드 | Bioabsorbable biomedical implants |
US9289536B2 (en) | 2013-03-14 | 2016-03-22 | Endologix, Inc. | Method for forming materials in situ within a medical device |
US9545301B2 (en) | 2013-03-15 | 2017-01-17 | Covidien Lp | Coated medical devices and methods of making and using same |
US9320592B2 (en) | 2013-03-15 | 2016-04-26 | Covidien Lp | Coated medical devices and methods of making and using same |
WO2014182542A1 (en) | 2013-05-06 | 2014-11-13 | Abbott Cardiovascular Systems Inc. | A hollow stent filled with a therapeutic agent formulation |
KR102079613B1 (en) | 2013-05-15 | 2020-02-20 | 미셀 테크놀로지즈, 인코포레이티드 | Bioabsorbable biomedical implants |
EP3498239B1 (en) | 2013-08-01 | 2021-04-21 | Cook Medical Technologies LLC | Tissue adjustment implant |
US9433763B2 (en) | 2013-09-27 | 2016-09-06 | Acclarent, Inc. | Sinus wall implant |
US9668890B2 (en) | 2013-11-22 | 2017-06-06 | Covidien Lp | Anti-thrombogenic medical devices and methods |
US10525171B2 (en) | 2014-01-24 | 2020-01-07 | The Spectranetics Corporation | Coatings for medical devices |
EP2994175A1 (en) | 2014-02-04 | 2016-03-16 | Abbott Cardiovascular Systems, Inc. | Drug delivery scaffold or stent with a novolimus and lactide based coating such that novolimus has a minimum amount of bonding to the coating |
GB2537770B (en) | 2014-04-22 | 2017-09-13 | Ariste Medical Llc | Methods and processes for application of drug delivery polymeric coatings |
US9163122B1 (en) | 2014-05-30 | 2015-10-20 | Pall Corporation | Self-assembling polymers—II |
US9441078B2 (en) | 2014-05-30 | 2016-09-13 | Pall Corporation | Self-assembling polymers—I |
US9593219B2 (en) | 2014-05-30 | 2017-03-14 | Pall Corporation | Membrane comprising self-assembled block copolymer and process for producing the same by spin coating (IIa) |
US9604181B2 (en) | 2014-05-30 | 2017-03-28 | Pall Corporation | Membrane comprising self-assembled block copolymer and process for producing the same by spray coating (IIc) |
US9598543B2 (en) | 2014-05-30 | 2017-03-21 | Pall Corporation | Self-assembled structure and membrane comprising block copolymer and process for producing the same by spin coating (VIa) |
US9616395B2 (en) | 2014-05-30 | 2017-04-11 | Pall Corportaion | Membrane comprising self-assembled block copolymer and process for producing the same by spray coating (Ic) |
US9593217B2 (en) | 2014-05-30 | 2017-03-14 | Pall Corporation | Self-assembled structure and membrane comprising block copolymer and process for producing the same by spin coating (Va) |
US9193835B1 (en) | 2014-05-30 | 2015-11-24 | Pall Corporation | Self-assembling polymers—IV |
US9328206B2 (en) | 2014-05-30 | 2016-05-03 | Pall Corporation | Self-assembling polymers—III |
US9162189B1 (en) | 2014-05-30 | 2015-10-20 | Pall Corporation | Membrane comprising self-assembled block copolymer and process for producing the same by spin coating (Ia) |
US9765171B2 (en) | 2014-05-30 | 2017-09-19 | Pall Corporation | Self-assembling polymers—V |
US9593218B2 (en) | 2014-05-30 | 2017-03-14 | Pall Corporation | Self-assembled structure and membrane comprising block copolymer and process for producing the same by spin coating (IIIa) |
US9469733B2 (en) | 2014-05-30 | 2016-10-18 | Pall Corporation | Self-assembled structure and membrane comprising block copolymer and process for producing the same by spin coating (IVa) |
US9592476B2 (en) | 2014-05-30 | 2017-03-14 | Pall Corporation | Membrane comprising self-assembled block copolymer and process for producing the same by hybrid casting (IIb) |
US9592477B2 (en) | 2014-05-30 | 2017-03-14 | Pall Corporation | Membrane comprising self-assembled block copolymer and process for producing the same by hybrid casting (Ib) |
US9169361B1 (en) | 2014-05-30 | 2015-10-27 | Pall Corporation | Self-assembling polymers—VI |
DE112015002920T5 (en) | 2014-06-20 | 2017-03-02 | University Of Tennessee Research Foundation | Multiprop Copolymer Superelastomers by Emulsion Polymerization |
BR112016030273A8 (en) | 2014-06-24 | 2021-05-18 | Icon Medical Corp | medical device and method of forming said device |
US9254466B2 (en) | 2014-06-30 | 2016-02-09 | Pall Corporation | Crosslinked cellulosic membranes |
US9260569B2 (en) | 2014-06-30 | 2016-02-16 | Pall Corporation | Hydrophilic block copolymers and method of preparation thereof (III) |
US9718924B2 (en) | 2014-06-30 | 2017-08-01 | Pall Corporation | Hydrophilic block copolymers and membranes prepared therefrom (II) |
US9309367B2 (en) | 2014-06-30 | 2016-04-12 | Pall Corporation | Membranes comprising cellulosic material and hydrophilic block copolymer (V) |
US9394407B2 (en) | 2014-06-30 | 2016-07-19 | Pall Corporation | Hydrophilic block copolymers and membranes prepared therefrom (I) |
US9962662B2 (en) | 2014-06-30 | 2018-05-08 | Pall Corporation | Fluorinated polymer and use thereof in the preparation of hydrophilic membranes (vi) |
US9303133B2 (en) | 2014-06-30 | 2016-04-05 | Pall Corporation | Hydrophilic membranes and method of preparation thereof (IV) |
US9895243B2 (en) | 2014-07-17 | 2018-02-20 | W. L. Gore & Associates, Inc. | Stent having adjacent elements connected by narrow flexible webs |
WO2016033424A1 (en) | 2014-08-29 | 2016-03-03 | Genzyme Corporation | Methods for the prevention and treatment of major adverse cardiovascular events using compounds that modulate apolipoprotein b |
US9789228B2 (en) | 2014-12-11 | 2017-10-17 | Covidien Lp | Antimicrobial coatings for medical devices and processes for preparing such coatings |
US9801983B2 (en) | 2014-12-18 | 2017-10-31 | Cook Medical Technologies Llc | Medical devices for delivering a bioactive to a point of treatment and methods of making medical devices |
US9238090B1 (en) | 2014-12-24 | 2016-01-19 | Fettech, Llc | Tissue-based compositions |
US9999527B2 (en) | 2015-02-11 | 2018-06-19 | Abbott Cardiovascular Systems Inc. | Scaffolds having radiopaque markers |
US9700443B2 (en) | 2015-06-12 | 2017-07-11 | Abbott Cardiovascular Systems Inc. | Methods for attaching a radiopaque marker to a scaffold |
JP6426068B2 (en) * | 2015-08-10 | 2018-11-21 | 朝日インテック株式会社 | Catheter and balloon catheter |
US11766506B2 (en) | 2016-03-04 | 2023-09-26 | Mirus Llc | Stent device for spinal fusion |
CN109715224B (en) | 2016-09-19 | 2022-02-22 | 百多力股份公司 | Polymer-free drug-eluting vascular stent |
CN110267627B (en) | 2016-12-09 | 2023-07-11 | 真复灵公司 | Systems, devices, and methods for accurately deploying implants in the prostatic urethra |
EP3589243A1 (en) | 2017-02-28 | 2020-01-08 | University College Cork - National University of Ireland, Cork | An intravascular cell therapy device |
US11325991B2 (en) | 2017-04-25 | 2022-05-10 | University Of Tennessee Research Foundation | All-acrylic multigraft copolymer superelastomers |
CN107469156B (en) * | 2017-09-30 | 2020-04-14 | 郑州大学第一附属医院 | Laminated Y-shaped bile duct stent partially covered with chemotherapeutic drugs |
JP2023502997A (en) | 2019-11-19 | 2023-01-26 | ゼンフロー, インコーポレイテッド | Systems, devices and methods for accurate deployment and imaging of implants within the prostatic urethra |
Family Cites Families (257)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3240616A (en) * | 1962-08-27 | 1966-03-15 | Harasowski Jerzy | Method of activating bentonite clays |
US3699956A (en) * | 1970-10-01 | 1972-10-24 | Tecna Corp | Percutaneous lead device |
US4101984A (en) * | 1975-05-09 | 1978-07-25 | Macgregor David C | Cardiovascular prosthetic devices and implants with porous systems |
US4225647B1 (en) * | 1977-12-02 | 1995-05-09 | Richard A Parent | Articles having thin, continuous, impervious coatings |
US5108424A (en) * | 1984-01-30 | 1992-04-28 | Meadox Medicals, Inc. | Collagen-impregnated dacron graft |
US5197977A (en) * | 1984-01-30 | 1993-03-30 | Meadox Medicals, Inc. | Drug delivery collagen-impregnated synthetic vascular graft |
WO1986007541A1 (en) * | 1985-06-19 | 1986-12-31 | Yasushi Zyo | Composition which can impart antithrombotic ability and medical apparatus to be in contact with blood |
US4795475A (en) | 1985-08-09 | 1989-01-03 | Walker Michael M | Prosthesis utilizing salt-forming oxyacids for bone fixation |
IL76079A (en) | 1985-08-13 | 1991-03-10 | Univ Ramot | Collagen implants |
FR2601675B1 (en) | 1986-07-17 | 1988-09-23 | Rhone Poulenc Sante | TAXOL DERIVATIVES, THEIR PREPARATION AND THE PHARMACEUTICAL COMPOSITIONS CONTAINING THEM |
FR2601676B1 (en) | 1986-07-17 | 1988-09-23 | Rhone Poulenc Sante | PROCESS FOR THE PREPARATION OF TAXOL AND DESACETYL-10 TAXOL |
US5019096A (en) * | 1988-02-11 | 1991-05-28 | Trustees Of Columbia University In The City Of New York | Infection-resistant compositions, medical devices and surfaces and methods for preparing and using same |
US4942184A (en) | 1988-03-07 | 1990-07-17 | The United States Of America As Represented By The Department Of Health And Human Services | Water soluble, antineoplastic derivatives of taxol |
WO1989011500A1 (en) * | 1988-05-17 | 1989-11-30 | Commonwealth Scientific And Industrial Research Or | Hydrophilic non-swelling multilayer polymeric materials and process for their manufacture |
US5213580A (en) | 1988-08-24 | 1993-05-25 | Endoluminal Therapeutics, Inc. | Biodegradable polymeric endoluminal sealing process |
DE68922497T2 (en) | 1988-08-24 | 1995-09-14 | Marvin J Slepian | ENDOLUMINAL SEAL WITH BISDEGRADABLE POLYMERS. |
US5053048A (en) * | 1988-09-22 | 1991-10-01 | Cordis Corporation | Thromboresistant coating |
US5298255A (en) * | 1988-10-28 | 1994-03-29 | Terumo Kabushiki Kaisha | Antithrombic medical material, artificial internal organ, and method for production of antithrombic medical material |
US5067491A (en) * | 1989-12-08 | 1991-11-26 | Becton, Dickinson And Company | Barrier coating on blood contacting devices |
US5059166A (en) * | 1989-12-11 | 1991-10-22 | Medical Innovative Technologies R & D Limited Partnership | Intra-arterial stent with the capability to inhibit intimal hyperplasia |
US5304121A (en) * | 1990-12-28 | 1994-04-19 | Boston Scientific Corporation | Drug delivery system making use of a hydrogel polymer coating |
AU7998091A (en) * | 1990-05-17 | 1991-12-10 | Harbor Medical Devices, Inc. | Medical device polymer |
US5112457A (en) * | 1990-07-23 | 1992-05-12 | Case Western Reserve University | Process for producing hydroxylated plasma-polymerized films and the use of the films for enhancing the compatiblity of biomedical implants |
US5455040A (en) * | 1990-07-26 | 1995-10-03 | Case Western Reserve University | Anticoagulant plasma polymer-modified substrate |
US5278324A (en) | 1990-08-28 | 1994-01-11 | Virginia Tech Intellectual Properties, Inc. | Water soluble derivatives of taxol |
US5059699A (en) | 1990-08-28 | 1991-10-22 | Virginia Tech Intellectual Properties, Inc. | Water soluble derivatives of taxol |
US5344411A (en) * | 1991-02-27 | 1994-09-06 | Leonard Bloom | Method and device for inhibiting HIV, hepatitis B and other viruses and germs when using a catheter in a medical environment |
TW197439B (en) | 1991-04-04 | 1993-01-01 | Ueno Pharmaceutics Applic Res Co Ltd | |
NL9101159A (en) * | 1991-07-03 | 1993-02-01 | Industrial Res Bv | FORMATTABLE EXPANDABLE RING, CYLINDER OR SLEEVE. |
CA2071160A1 (en) | 1991-07-31 | 1993-02-01 | Vittorio Farina | Asymmetric synthesis of taxol side chain |
US5356433A (en) * | 1991-08-13 | 1994-10-18 | Cordis Corporation | Biocompatible metal surfaces |
SG46582A1 (en) | 1991-09-23 | 1998-02-20 | Univ Florida State | 10-Desacetoxytaxol derivatives |
US5283253A (en) | 1991-09-23 | 1994-02-01 | Florida State University | Furyl or thienyl carbonyl substituted taxanes and pharmaceutical compositions containing them |
US5811447A (en) | 1993-01-28 | 1998-09-22 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US5464450A (en) * | 1991-10-04 | 1995-11-07 | Scimed Lifesystems Inc. | Biodegradable drug delivery vascular stent |
JP3093375B2 (en) * | 1991-11-01 | 2000-10-03 | 株式会社東海メディカルプロダクツ | Immobilization method of antithrombotic substance |
US5270047A (en) * | 1991-11-21 | 1993-12-14 | Kauffman Raymond F | Local delivery of dipyridamole for the treatment of proliferative diseases |
WO1993010076A1 (en) | 1991-11-22 | 1993-05-27 | The University Of Mississippi | Synthesis and optical resolution of the taxol side chain and related compounds |
US5272171A (en) | 1992-02-13 | 1993-12-21 | Bristol-Myers Squibb Company | Phosphonooxy and carbonate derivatives of taxol |
US5200534A (en) | 1992-03-13 | 1993-04-06 | University Of Florida | Process for the preparation of taxol and 10-deacetyltaxol |
US5282823A (en) * | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
US5599352A (en) | 1992-03-19 | 1997-02-04 | Medtronic, Inc. | Method of making a drug eluting stent |
US5440056A (en) | 1992-04-17 | 1995-08-08 | Abbott Laboratories | 9-deoxotaxane compounds |
US5288711A (en) | 1992-04-28 | 1994-02-22 | American Home Products Corporation | Method of treating hyperproliferative vascular disease |
US5383927A (en) * | 1992-05-07 | 1995-01-24 | Intervascular Inc. | Non-thromogenic vascular prosthesis |
CA2136213A1 (en) | 1992-05-21 | 1993-11-25 | Richard N. Arteca | Cultured taxu tissues as a source of taxol, related taxanes and other novel anti-tumor/anti-viral compounds |
AU4406793A (en) | 1992-06-04 | 1993-12-30 | Clover Consolidated, Limited | Water-soluble polymeric carriers for drug delivery |
US5383928A (en) * | 1992-06-10 | 1995-01-24 | Emory University | Stent sheath for local drug delivery |
US5248796A (en) | 1992-06-18 | 1993-09-28 | Bristol-Myers Squibb Company | Taxol derivatives |
GB9213077D0 (en) | 1992-06-19 | 1992-08-05 | Erba Carlo Spa | Polymerbound taxol derivatives |
US5274137A (en) | 1992-06-23 | 1993-12-28 | Nicolaou K C | Intermediates for preparation of taxols |
US5254580A (en) | 1993-01-19 | 1993-10-19 | Bristol-Myers Squibb Company | 7,8-cyclopropataxanes |
US5294637A (en) | 1992-07-01 | 1994-03-15 | Bristol-Myers Squibb Company | Fluoro taxols |
US5202448A (en) | 1992-08-14 | 1993-04-13 | Napro Biotherapeutics, Inc. | Processes of converting taxanes into baccatin III |
WO1994005282A1 (en) | 1992-09-04 | 1994-03-17 | The Scripps Research Institute | Water soluble taxol derivatives |
US5274132A (en) | 1992-09-30 | 1993-12-28 | Transitions Optical, Inc. | Photochromic naphthopyran compounds |
CA2100808A1 (en) | 1992-10-01 | 1994-04-02 | Vittorio Farina | Deoxy paclitaxels |
FR2696464B1 (en) | 1992-10-05 | 1994-11-10 | Rhone Poulenc Rorer Sa | New esterification process for baccatin III and 10-deacetyl baccatin III. |
FR2696462B1 (en) | 1992-10-05 | 1994-11-25 | Rhone Poulenc Rorer Sa | Process for obtaining 10-deacetyl baccatin III. |
FR2696463B1 (en) | 1992-10-05 | 1994-11-25 | Rhone Poulenc Rorer Sa | Process for obtaining 10-deacetyl baccatin III. |
US5411984A (en) | 1992-10-16 | 1995-05-02 | Virginia Tech Intellectual Properties, Inc. | Water soluble analogs and prodrugs of taxol |
US5449382A (en) * | 1992-11-04 | 1995-09-12 | Dayton; Michael P. | Minimally invasive bioactivated endoprosthesis for vessel repair |
US5578075B1 (en) * | 1992-11-04 | 2000-02-08 | Daynke Res Inc | Minimally invasive bioactivated endoprosthesis for vessel repair |
US5342348A (en) * | 1992-12-04 | 1994-08-30 | Kaplan Aaron V | Method and device for treating and enlarging body lumens |
US5380751A (en) | 1992-12-04 | 1995-01-10 | Bristol-Myers Squibb Company | 6,7-modified paclitaxels |
US5279949A (en) | 1992-12-07 | 1994-01-18 | Board Of Trustees Operating Michigan State University | Process for the isolation and purification of taxol and taxanes from Taxus spp |
US5443458A (en) * | 1992-12-22 | 1995-08-22 | Advanced Cardiovascular Systems, Inc. | Multilayered biodegradable stent and method of manufacture |
US5419760A (en) * | 1993-01-08 | 1995-05-30 | Pdt Systems, Inc. | Medicament dispensing stent for prevention of restenosis of a blood vessel |
US5595722A (en) * | 1993-01-28 | 1997-01-21 | Neorx Corporation | Method for identifying an agent which increases TGF-beta levels |
WO1994020089A1 (en) | 1993-03-09 | 1994-09-15 | Enzon, Inc. | Taxol-based compositions with enhanced bioactivity |
US5412092A (en) | 1993-04-23 | 1995-05-02 | Bristol-Myers Squibb Company | N-substituted 2-azetidinones |
US5464650A (en) * | 1993-04-26 | 1995-11-07 | Medtronic, Inc. | Intravascular stent and method |
US5824048A (en) | 1993-04-26 | 1998-10-20 | Medtronic, Inc. | Method for delivering a therapeutic substance to a body lumen |
US5849035A (en) | 1993-04-28 | 1998-12-15 | Focal, Inc. | Methods for intraluminal photothermoforming |
US5994341A (en) * | 1993-07-19 | 1999-11-30 | Angiogenesis Technologies, Inc. | Anti-angiogenic Compositions and methods for the treatment of arthritis |
EP0711158B2 (en) * | 1993-07-29 | 2008-07-23 | THE GOVERNMENT OF THE UNITED STATES OF AMERICA, as represented by THE SECRETARY, DEPARTMENT OF HEALTH AND HUMAN SERVICES | Method of treating atherosclerosis or restenosis using microtubule stabilizing agent |
US5380299A (en) * | 1993-08-30 | 1995-01-10 | Med Institute, Inc. | Thrombolytic treated intravascular medical device |
US5457113A (en) * | 1993-10-15 | 1995-10-10 | Eli Lilly And Company | Methods for inhibiting vascular smooth muscle cell proliferation and restinosis |
US5759205A (en) | 1994-01-21 | 1998-06-02 | Brown University Research Foundation | Negatively charged polymeric electret implant |
US5395850A (en) | 1994-03-10 | 1995-03-07 | Bristol-Myers Squibb Company | 6,7-epoxy paclitaxels |
CA2147813A1 (en) | 1994-04-28 | 1995-10-29 | Richard Dixon | Intravascular prosthesis with anti-thrombogenic coating |
US5554181A (en) * | 1994-05-04 | 1996-09-10 | Regents Of The University Of Minnesota | Stent |
US5629077A (en) | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
DE69534405T2 (en) * | 1994-07-01 | 2006-03-09 | Edwards Lifesciences Corp., Irvine | APPARATUS FOR OBTAINING AUTOMATED, MICROVASCULAR ENDOTHELIAL CELLS CONTAINING FAT TISSUE |
US5788979A (en) | 1994-07-22 | 1998-08-04 | Inflow Dynamics Inc. | Biodegradable coating with inhibitory properties for application to biocompatible materials |
US5649977A (en) | 1994-09-22 | 1997-07-22 | Advanced Cardiovascular Systems, Inc. | Metal reinforced polymer stent |
US5637113A (en) * | 1994-12-13 | 1997-06-10 | Advanced Cardiovascular Systems, Inc. | Polymer film for wrapping a stent structure |
US5876743A (en) | 1995-03-21 | 1999-03-02 | Den-Mat Corporation | Biocompatible adhesion in tissue repair |
US5605696A (en) * | 1995-03-30 | 1997-02-25 | Advanced Cardiovascular Systems, Inc. | Drug loaded polymeric material and method of manufacture |
WO1996037165A1 (en) | 1995-05-26 | 1996-11-28 | Bsi Corporation | Method and implantable article for promoting endothelialization |
US5674242A (en) | 1995-06-06 | 1997-10-07 | Quanam Medical Corporation | Endoprosthetic device with therapeutic compound |
US5609629A (en) * | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
US5773019A (en) | 1995-09-27 | 1998-06-30 | The University Of Kentucky Research Foundation | Implantable controlled release device to deliver drugs directly to an internal portion of the body |
US5968972A (en) * | 1995-10-26 | 1999-10-19 | Baker Norton Pharmaceuticals, Inc. | Method for increasing the oral bioactivity of pharmaceutical agents |
US20040106985A1 (en) | 1996-04-26 | 2004-06-03 | Jang G. David | Intravascular stent |
EP1616563A3 (en) | 1996-05-24 | 2006-01-25 | Angiotech Pharmaceuticals, Inc. | Perivascular administration of anti-angiogenic factors for treating or preventing vascular diseases |
US5797887A (en) | 1996-08-27 | 1998-08-25 | Novovasc Llc | Medical device with a surface adapted for exposure to a blood stream which is coated with a polymer containing a nitrosyl-containing organo-metallic compound which releases nitric oxide from the coating to mediate platelet aggregation |
US7351421B2 (en) | 1996-11-05 | 2008-04-01 | Hsing-Wen Sung | Drug-eluting stent having collagen drug carrier chemically treated with genipin |
US20020111603A1 (en) | 1996-12-02 | 2002-08-15 | Societe De Conseils De Recherches Et D'application | Device for local administration of solid or semi-solid formulations and delayed-release formulations for proposal parental administration and preparation process |
US6495579B1 (en) | 1996-12-02 | 2002-12-17 | Angiotech Pharmaceuticals, Inc. | Method for treating multiple sclerosis |
US6515016B2 (en) | 1996-12-02 | 2003-02-04 | Angiotech Pharmaceuticals, Inc. | Composition and methods of paclitaxel for treating psoriasis |
US20030157187A1 (en) | 1996-12-02 | 2003-08-21 | Angiotech Pharmaceuticals, Inc. | Compositions and methods for treating or preventing inflammatory diseases |
US5980551A (en) | 1997-02-07 | 1999-11-09 | Endovasc Ltd., Inc. | Composition and method for making a biodegradable drug delivery stent |
US8172897B2 (en) | 1997-04-15 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Polymer and metal composite implantable medical devices |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US6818016B1 (en) | 1997-06-27 | 2004-11-16 | The Regents Of The University Of Michigan | Methods for coating stents with DNA and expression of recombinant genes from DNA coated stents in vivo |
FR2766092B1 (en) | 1997-07-16 | 1999-10-08 | Centre Nat Rech Scient | IMPLANTABLE DEVICE COATED WITH A POLYMER CAPABLE OF RELEASING BIOLOGICALLY ACTIVE SUBSTANCES |
US6306426B1 (en) | 1997-08-11 | 2001-10-23 | Allergan Sales, Inc. | Implant device with a retinoid for improved biocompatibility |
US6485514B1 (en) | 1997-12-12 | 2002-11-26 | Supergen, Inc. | Local delivery of therapeutic agents |
US5957975A (en) | 1997-12-15 | 1999-09-28 | The Cleveland Clinic Foundation | Stent having a programmed pattern of in vivo degradation |
US20040254635A1 (en) | 1998-03-30 | 2004-12-16 | Shanley John F. | Expandable medical device for delivery of beneficial agent |
US6153252A (en) * | 1998-06-30 | 2000-11-28 | Ethicon, Inc. | Process for coating stents |
US6652581B1 (en) | 1998-07-07 | 2003-11-25 | Boston Scientific Scimed, Inc. | Medical device with porous surface for controlled drug release and method of making the same |
JP4898991B2 (en) * | 1998-08-20 | 2012-03-21 | クック メディカル テクノロジーズ エルエルシー | Sheathed medical device |
US7662409B2 (en) | 1998-09-25 | 2010-02-16 | Gel-Del Technologies, Inc. | Protein matrix materials, devices and methods of making and using thereof |
US20050033399A1 (en) | 1998-12-03 | 2005-02-10 | Jacob Richter | Hybrid stent |
US6333347B1 (en) | 1999-01-29 | 2001-12-25 | Angiotech Pharmaceuticals & Advanced Research Tech | Intrapericardial delivery of anti-microtubule agents |
US6903244B1 (en) | 1999-02-26 | 2005-06-07 | University Of Utah Research Foundation | Mice which are +/− or −/− for the elastin gene as models for vascular disease |
EP2305324B1 (en) | 1999-03-25 | 2014-09-17 | Metabolix, Inc. | Medical devices and applications of polyhydroxyalkanoate polymers |
US6716445B2 (en) | 1999-04-12 | 2004-04-06 | Cornell Research Foundation, Inc. | Hydrogel entrapping therapeutic agent and stent with coating comprising this |
US6258121B1 (en) | 1999-07-02 | 2001-07-10 | Scimed Life Systems, Inc. | Stent coating |
US20050060044A1 (en) | 1999-08-05 | 2005-03-17 | Ed Roschak | Methods and devices for maintaining patency of surgically created channels in a body organ |
US6709427B1 (en) | 1999-08-05 | 2004-03-23 | Kensey Nash Corporation | Systems and methods for delivering agents into targeted tissue of a living being |
US20050137715A1 (en) | 1999-08-05 | 2005-06-23 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in a body organ |
US7462162B2 (en) | 2001-09-04 | 2008-12-09 | Broncus Technologies, Inc. | Antiproliferative devices for maintaining patency of surgically created channels in a body organ |
US7682647B2 (en) | 1999-09-03 | 2010-03-23 | Advanced Cardiovascular Systems, Inc. | Thermal treatment of a drug eluting implantable medical device |
US7807211B2 (en) | 1999-09-03 | 2010-10-05 | Advanced Cardiovascular Systems, Inc. | Thermal treatment of an implantable medical device |
US20070032853A1 (en) * | 2002-03-27 | 2007-02-08 | Hossainy Syed F | 40-O-(2-hydroxy)ethyl-rapamycin coated stent |
US6790228B2 (en) | 1999-12-23 | 2004-09-14 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US20030144570A1 (en) | 1999-11-12 | 2003-07-31 | Angiotech Pharmaceuticals, Inc. | Compositions and methods for treating disease utilizing a combination of radioactive therapy and cell-cycle inhibitors |
AU1374601A (en) | 1999-11-12 | 2001-05-30 | Angiotech International Ag | Compositions and methods for treating disease utilizing a combination of radioactive therapy and cell-cycle inhibitors |
US6491666B1 (en) | 1999-11-17 | 2002-12-10 | Microchips, Inc. | Microfabricated devices for the delivery of molecules into a carrier fluid |
US6702849B1 (en) | 1999-12-13 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Method of processing open-celled microcellular polymeric foams with controlled porosity for use as vascular grafts and stent covers |
US20040127475A1 (en) | 1999-12-29 | 2004-07-01 | Estrogen Vascular Technology, Llc | Apparatus and method for delivering compounds to a living organism |
US6471979B2 (en) | 1999-12-29 | 2002-10-29 | Estrogen Vascular Technology, Llc | Apparatus and method for delivering compounds to a living organism |
JP2003520830A (en) | 2000-01-25 | 2003-07-08 | エドワーズ ライフサイエンシーズ コーポレイション | Delivery system for treatment of restenosis and anastomotic intimal hyperplasia |
SE0000363L (en) | 2000-02-04 | 2001-08-05 | Zoucas Kirurgkonsult Ab | Coated medical device |
US20030229393A1 (en) | 2001-03-15 | 2003-12-11 | Kutryk Michael J. B. | Medical device with coating that promotes cell adherence and differentiation |
EP1263484B1 (en) | 2000-03-15 | 2007-05-16 | OrbusNeich Medical, Inc. | Coating which promotes endothelial cell adherence |
US7875283B2 (en) | 2000-04-13 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Biodegradable polymers for use with implantable medical devices |
US6585765B1 (en) | 2000-06-29 | 2003-07-01 | Advanced Cardiovascular Systems, Inc. | Implantable device having substances impregnated therein and a method of impregnating the same |
US6555157B1 (en) | 2000-07-25 | 2003-04-29 | Advanced Cardiovascular Systems, Inc. | Method for coating an implantable device and system for performing the method |
US6451373B1 (en) | 2000-08-04 | 2002-09-17 | Advanced Cardiovascular Systems, Inc. | Method of forming a therapeutic coating onto a surface of an implantable prosthesis |
US7766956B2 (en) | 2000-09-22 | 2010-08-03 | Boston Scientific Scimed, Inc. | Intravascular stent and assembly |
US6506437B1 (en) | 2000-10-17 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Methods of coating an implantable device having depots formed in a surface thereof |
US20020161168A1 (en) | 2000-10-27 | 2002-10-31 | Shalaby Shalaby W. | Amorphous polymeric polyaxial initiators and compliant crystalline copolymers therefrom |
US6794485B2 (en) | 2000-10-27 | 2004-09-21 | Poly-Med, Inc. | Amorphous polymeric polyaxial initiators and compliant crystalline copolymers therefrom |
US20050123583A1 (en) | 2000-12-18 | 2005-06-09 | Hsing-Wen Sung | Medical use of reuterin |
US6939375B2 (en) | 2000-12-22 | 2005-09-06 | Avantac Vascular Corporation | Apparatus and methods for controlled substance delivery from implanted prostheses |
US20020082679A1 (en) | 2000-12-22 | 2002-06-27 | Avantec Vascular Corporation | Delivery or therapeutic capable agents |
US6752829B2 (en) | 2001-01-30 | 2004-06-22 | Scimed Life Systems, Inc. | Stent with channel(s) for containing and delivering a biologically active material and method for manufacturing the same |
WO2002072167A1 (en) | 2001-03-13 | 2002-09-19 | Implant Sciences Corporation. | Drug eluting encapsulated stent |
EP1379197A4 (en) | 2001-03-23 | 2009-06-03 | Durect Corp | Delivery of drugs from sustained release devices implanted in myocardial tissue or in the pericardial space |
US7048939B2 (en) | 2001-04-20 | 2006-05-23 | The Board Of Trustees Of The Leland Stanford Junior University | Methods for the inhibition of neointima formation |
US7056339B2 (en) | 2001-04-20 | 2006-06-06 | The Board Of Trustees Of The Leland Stanford Junior University | Drug delivery platform |
WO2002089865A2 (en) | 2001-05-04 | 2002-11-14 | Concentric Medical | Coated combination vaso-occlusive device |
US7128755B2 (en) | 2001-06-01 | 2006-10-31 | Texas Stent Technologies, Inc. | Expandable biodegradable polymeric stents for combined mechanical support and pharmacological or radiation therapy |
US6585755B2 (en) | 2001-06-29 | 2003-07-01 | Advanced Cardiovascular | Polymeric stent suitable for imaging by MRI and fluoroscopy |
EP1275442A1 (en) | 2001-07-13 | 2003-01-15 | Stichting voor de Technische Wetenschappen | Electrostatic spray deposition (ESD) of biocompatible coatings on metallic substrates |
SE523216C2 (en) | 2001-07-27 | 2004-04-06 | Zoucas Kirurgkonsult Ab | heparin stent |
US20040249443A1 (en) | 2001-08-20 | 2004-12-09 | Shanley John F. | Expandable medical device for treating cardiac arrhythmias |
US7056338B2 (en) | 2003-03-28 | 2006-06-06 | Conor Medsystems, Inc. | Therapeutic agent delivery device with controlled therapeutic agent release rates |
KR100455343B1 (en) | 2001-08-29 | 2004-11-12 | 학교법인 인하학원 | Covering composition for drug releasing stent and drug releasing stent manufactured using same |
US20050060041A1 (en) | 2001-09-04 | 2005-03-17 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
US7708712B2 (en) | 2001-09-04 | 2010-05-04 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in a body organ |
US20050060042A1 (en) | 2001-09-04 | 2005-03-17 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
US20050137611A1 (en) | 2001-09-04 | 2005-06-23 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
IN2014DN10834A (en) | 2001-09-17 | 2015-09-04 | Psivida Inc | |
US20030158598A1 (en) | 2001-09-17 | 2003-08-21 | Control Delivery Systems, Inc. | System for sustained-release delivery of anti-inflammatory agents from a coated medical device |
US6753071B1 (en) * | 2001-09-27 | 2004-06-22 | Advanced Cardiovascular Systems, Inc. | Rate-reducing membrane for release of an agent |
US20030077310A1 (en) | 2001-10-22 | 2003-04-24 | Chandrashekhar Pathak | Stent coatings containing HMG-CoA reductase inhibitors |
US7572287B2 (en) | 2001-10-25 | 2009-08-11 | Boston Scientific Scimed, Inc. | Balloon expandable polymer stent with reduced elastic recoil |
US6939376B2 (en) | 2001-11-05 | 2005-09-06 | Sun Biomedical, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
US20030088307A1 (en) | 2001-11-05 | 2003-05-08 | Shulze John E. | Potent coatings for stents |
US7682387B2 (en) | 2002-04-24 | 2010-03-23 | Biosensors International Group, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
US7473273B2 (en) | 2002-01-22 | 2009-01-06 | Medtronic Vascular, Inc. | Stent assembly with therapeutic agent exterior banding |
US7326245B2 (en) | 2002-01-31 | 2008-02-05 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US7993390B2 (en) | 2002-02-08 | 2011-08-09 | Boston Scientific Scimed, Inc. | Implantable or insertable medical device resistant to microbial growth and biofilm formation |
US20030153972A1 (en) | 2002-02-14 | 2003-08-14 | Michael Helmus | Biodegradable implantable or insertable medical devices with controlled change of physical properties leading to biomechanical compatibility |
US20030153971A1 (en) | 2002-02-14 | 2003-08-14 | Chandru Chandrasekaran | Metal reinforced biodegradable intraluminal stents |
KR20040097126A (en) | 2002-02-15 | 2004-11-17 | 씨브이 쎄러퓨틱스, 인코포레이티드 | Polymer coating for medical devices |
US7264822B2 (en) | 2002-04-03 | 2007-09-04 | Poly-Med, Inc. | Conjugated drug-polymer coated stent |
US20030195611A1 (en) | 2002-04-11 | 2003-10-16 | Greenhalgh Skott E. | Covering and method using electrospinning of very small fibers |
US20050187605A1 (en) | 2002-04-11 | 2005-08-25 | Greenhalgh Skott E. | Electrospun skin capable of controlling drug release rates and method |
US7261734B2 (en) * | 2002-04-23 | 2007-08-28 | Boston Scientific Scimed, Inc. | Resorption-controllable medical implants |
US20040024450A1 (en) | 2002-04-24 | 2004-02-05 | Sun Biomedical, Ltd. | Drug-delivery endovascular stent and method for treating restenosis |
AU2003228858A1 (en) * | 2002-05-02 | 2003-11-17 | Scimed Life Systems, Inc. | Energetically-controlled delivery of biologically active material from an implanted medical device |
ATE466281T1 (en) | 2002-05-07 | 2010-05-15 | Univ New York State Res Found | ßHIGH THROUGPUTß METHOD TO LABEL BIOMOLECULE DELIVERY FORMULATIONS |
CN1655738A (en) | 2002-05-20 | 2005-08-17 | 奥勃斯医学技术股份有限公司 | Drug eluting implantable medical device |
US7005137B1 (en) | 2002-06-21 | 2006-02-28 | Advanceed Cardiovascular Systems, Inc. | Coating for implantable medical devices |
EP1516597A4 (en) | 2002-06-27 | 2010-11-10 | Microport Medical Shanghai Co | Drug eluting stent |
US20040002755A1 (en) | 2002-06-28 | 2004-01-01 | Fischell David R. | Method and apparatus for treating vulnerable coronary plaques using drug-eluting stents |
AU2003250913A1 (en) | 2002-07-08 | 2004-01-23 | Abbott Laboratories Vascular Enterprises Limited | Drug eluting stent and methods of manufacture |
US7332160B2 (en) | 2002-07-12 | 2008-02-19 | Boston Scientific Scimed, Inc. | Medical device and method for tissue removal and repair |
JP4723244B2 (en) | 2002-07-19 | 2011-07-13 | オメロス コーポレイション | Biodegradable triblock copolymers, methods for their synthesis, and hydrogels and biomaterials made therefrom |
US7025777B2 (en) | 2002-07-31 | 2006-04-11 | Unison Therapeutics, Inc. | Flexible and conformable stent and method of forming same |
US7951392B2 (en) | 2002-08-16 | 2011-05-31 | Boston Scientific Scimed, Inc. | Microarray drug delivery coatings |
US6702850B1 (en) | 2002-09-30 | 2004-03-09 | Mediplex Corporation Korea | Multi-coated drug-eluting stent for antithrombosis and antirestenosis |
DE60336158D1 (en) | 2002-10-11 | 2011-04-07 | Univ Connecticut | ON SEMICRISTALLINE THERMOPLASTIC POLYURETHANES BASED FOR NANOSTRUCTURED HARD SEGMENTS BASED FORM MEMORY PILARMERS |
US7794494B2 (en) | 2002-10-11 | 2010-09-14 | Boston Scientific Scimed, Inc. | Implantable medical devices |
US20060121080A1 (en) | 2002-11-13 | 2006-06-08 | Lye Whye K | Medical devices having nanoporous layers and methods for making the same |
US7285287B2 (en) | 2002-11-14 | 2007-10-23 | Synecor, Llc | Carbon dioxide-assisted methods of providing biocompatible intraluminal prostheses |
US20040098106A1 (en) | 2002-11-14 | 2004-05-20 | Williams Michael S. | Intraluminal prostheses and carbon dioxide-assisted methods of impregnating same with pharmacological agents |
US20040098090A1 (en) | 2002-11-14 | 2004-05-20 | Williams Michael S. | Polymeric endoprosthesis and method of manufacture |
US7491234B2 (en) | 2002-12-03 | 2009-02-17 | Boston Scientific Scimed, Inc. | Medical devices for delivery of therapeutic agents |
US20040172127A1 (en) | 2002-12-09 | 2004-09-02 | John Kantor | Modular stent having polymer bridges at modular unit contact sites |
AU2003300022A1 (en) | 2002-12-30 | 2004-07-29 | Angiotech International Ag | Silk-containing stent graft |
US20040236415A1 (en) | 2003-01-02 | 2004-11-25 | Richard Thomas | Medical devices having drug releasing polymer reservoirs |
US20040260386A1 (en) | 2003-01-31 | 2004-12-23 | Shalaby Shalaby W. | Absorbable / biodegradable tubular stent and methods of making the same |
US6932930B2 (en) | 2003-03-10 | 2005-08-23 | Synecor, Llc | Intraluminal prostheses having polymeric material with selectively modified crystallinity and methods of making same |
US20050010170A1 (en) | 2004-02-11 | 2005-01-13 | Shanley John F | Implantable medical device with beneficial agent concentration gradient |
DE602004018908D1 (en) | 2003-03-31 | 2009-02-26 | Memry Corp | MEDICAL DEVICES WITH MEDICAMENT ELUTION PROPERTIES AND METHOD OF PREPARATION THEREOF |
US7163555B2 (en) | 2003-04-08 | 2007-01-16 | Medtronic Vascular, Inc. | Drug-eluting stent for controlled drug delivery |
US20050107870A1 (en) | 2003-04-08 | 2005-05-19 | Xingwu Wang | Medical device with multiple coating layers |
US20050070996A1 (en) | 2003-04-08 | 2005-03-31 | Dinh Thomas Q. | Drug-eluting stent for controlled drug delivery |
US20040215315A1 (en) | 2003-04-25 | 2004-10-28 | Jones Ryan A. | Drug-eluting stent with sheath and balloon deployment assembly |
US20040215335A1 (en) | 2003-04-25 | 2004-10-28 | Brin David S. | Methods and apparatus for treatment of aneurysmal tissue |
US20060025713A1 (en) | 2003-05-12 | 2006-02-02 | Alex Rosengart | Magnetic particle-based therapy |
WO2004101017A2 (en) | 2003-05-16 | 2004-11-25 | Blue Membranes Gmbh | Medical implants comprising biocompatible coatings |
WO2005018683A2 (en) | 2003-05-23 | 2005-03-03 | Angiotech International Ag | Anastomotic connector devices |
US20030216803A1 (en) | 2003-05-28 | 2003-11-20 | Ledergerber Walter J. | Textured and drug eluting stent-grafts |
US7041127B2 (en) | 2003-05-28 | 2006-05-09 | Ledergerber Walter J | Textured and drug eluting coronary artery stent |
US6979348B2 (en) | 2003-06-04 | 2005-12-27 | Medtronic Vascular, Inc. | Reflowed drug-polymer coated stent and method thereof |
US7186789B2 (en) | 2003-06-11 | 2007-03-06 | Advanced Cardiovascular Systems, Inc. | Bioabsorbable, biobeneficial polyester polymers for use in drug eluting stent coatings |
US20050118344A1 (en) | 2003-12-01 | 2005-06-02 | Pacetti Stephen D. | Temperature controlled crimping |
US7169404B2 (en) | 2003-07-30 | 2007-01-30 | Advanced Cardiovasular Systems, Inc. | Biologically absorbable coatings for implantable devices and methods for fabricating the same |
US20050055078A1 (en) | 2003-09-04 | 2005-03-10 | Medtronic Vascular, Inc. | Stent with outer slough coating |
US7055237B2 (en) | 2003-09-29 | 2006-06-06 | Medtronic Vascular, Inc. | Method of forming a drug eluting stent |
US7232461B2 (en) | 2003-10-29 | 2007-06-19 | Cordis Neurovascular, Inc. | Neck covering device for an aneurysm |
US20050100577A1 (en) | 2003-11-10 | 2005-05-12 | Parker Theodore L. | Expandable medical device with beneficial agent matrix formed by a multi solvent system |
CA2536041A1 (en) | 2003-11-10 | 2005-05-26 | Angiotech International Ag | Medical implants and fibrosis-inducing agents |
US20050112170A1 (en) | 2003-11-20 | 2005-05-26 | Hossainy Syed F. | Coatings for implantable devices comprising polymers of lactic acid and methods for fabricating the same |
US7807722B2 (en) | 2003-11-26 | 2010-10-05 | Advanced Cardiovascular Systems, Inc. | Biobeneficial coating compositions and methods of making and using thereof |
US7435788B2 (en) | 2003-12-19 | 2008-10-14 | Advanced Cardiovascular Systems, Inc. | Biobeneficial polyamide/polyethylene glycol polymers for use with drug eluting stents |
US20050187607A1 (en) | 2004-02-20 | 2005-08-25 | Akhtar Adil J. | Drug delivery device |
US8685431B2 (en) | 2004-03-16 | 2014-04-01 | Advanced Cardiovascular Systems, Inc. | Biologically absorbable coatings for implantable devices based on copolymers having ester bonds and methods for fabricating the same |
ATE534424T1 (en) | 2004-03-19 | 2011-12-15 | Abbott Lab | MULTIPLE MEDICINAL DELIVERY FROM A BALLOON AND A PROSTHESIS |
US7820732B2 (en) | 2004-04-30 | 2010-10-26 | Advanced Cardiovascular Systems, Inc. | Methods for modulating thermal and mechanical properties of coatings on implantable devices |
US8293890B2 (en) | 2004-04-30 | 2012-10-23 | Advanced Cardiovascular Systems, Inc. | Hyaluronic acid based copolymers |
US20060246109A1 (en) | 2005-04-29 | 2006-11-02 | Hossainy Syed F | Concentration gradient profiles for control of agent release rates from polymer matrices |
US7758892B1 (en) | 2004-05-20 | 2010-07-20 | Boston Scientific Scimed, Inc. | Medical devices having multiple layers |
US9561309B2 (en) | 2004-05-27 | 2017-02-07 | Advanced Cardiovascular Systems, Inc. | Antifouling heparin coatings |
US8357391B2 (en) | 2004-07-30 | 2013-01-22 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable devices comprising poly (hydroxy-alkanoates) and diacid linkages |
US20060041102A1 (en) | 2004-08-23 | 2006-02-23 | Advanced Cardiovascular Systems, Inc. | Implantable devices comprising biologically absorbable polymers having constant rate of degradation and methods for fabricating the same |
US7244443B2 (en) | 2004-08-31 | 2007-07-17 | Advanced Cardiovascular Systems, Inc. | Polymers of fluorinated monomers and hydrophilic monomers |
US7229471B2 (en) | 2004-09-10 | 2007-06-12 | Advanced Cardiovascular Systems, Inc. | Compositions containing fast-leaching plasticizers for improved performance of medical devices |
US9011831B2 (en) | 2004-09-30 | 2015-04-21 | Advanced Cardiovascular Systems, Inc. | Methacrylate copolymers for medical devices |
US20060095122A1 (en) | 2004-10-29 | 2006-05-04 | Advanced Cardiovascular Systems, Inc. | Implantable devices comprising biologically absorbable star polymers and methods for fabricating the same |
US8609123B2 (en) | 2004-11-29 | 2013-12-17 | Advanced Cardiovascular Systems, Inc. | Derivatized poly(ester amide) as a biobeneficial coating |
US20060115449A1 (en) | 2004-11-30 | 2006-06-01 | Advanced Cardiovascular Systems, Inc. | Bioabsorbable, biobeneficial, tyrosine-based polymers for use in drug eluting stent coatings |
US7604818B2 (en) | 2004-12-22 | 2009-10-20 | Advanced Cardiovascular Systems, Inc. | Polymers of fluorinated monomers and hydrocarbon monomers |
US7419504B2 (en) | 2004-12-27 | 2008-09-02 | Advanced Cardiovascular Systems, Inc. | Poly(ester amide) block copolymers |
US8007775B2 (en) | 2004-12-30 | 2011-08-30 | Advanced Cardiovascular Systems, Inc. | Polymers containing poly(hydroxyalkanoates) and agents for use with medical articles and methods of fabricating the same |
US20060147491A1 (en) * | 2005-01-05 | 2006-07-06 | Dewitt David M | Biodegradable coating compositions including multiple layers |
US7202325B2 (en) | 2005-01-14 | 2007-04-10 | Advanced Cardiovascular Systems, Inc. | Poly(hydroxyalkanoate-co-ester amides) and agents for use with medical articles |
US8778375B2 (en) | 2005-04-29 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Amorphous poly(D,L-lactide) coating |
US20070005130A1 (en) | 2005-06-29 | 2007-01-04 | Thierry Glauser | Biodegradable polymer for coating |
-
1996
- 1996-06-07 AU AU55888/96A patent/AU716005B2/en not_active Expired
- 1996-06-07 CA CA002178541A patent/CA2178541C/en not_active Expired - Lifetime
- 1996-10-31 US US08/741,565 patent/US5824049A/en not_active Expired - Lifetime
-
1997
- 1997-02-24 US US08/803,843 patent/US5873904A/en not_active Expired - Lifetime
-
2006
- 2006-11-15 US US11/599,859 patent/US8313521B2/en not_active Expired - Lifetime
Cited By (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8066763B2 (en) | 1998-04-11 | 2011-11-29 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US8574615B2 (en) | 2006-03-24 | 2013-11-05 | Boston Scientific Scimed, Inc. | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8187620B2 (en) | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
US8771343B2 (en) | 2006-06-29 | 2014-07-08 | Boston Scientific Scimed, Inc. | Medical devices with selective titanium oxide coatings |
US8353949B2 (en) | 2006-09-14 | 2013-01-15 | Boston Scientific Scimed, Inc. | Medical devices with drug-eluting coating |
US7981150B2 (en) | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
US8067054B2 (en) | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US7976915B2 (en) | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US8002823B2 (en) | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7942926B2 (en) | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US9284409B2 (en) | 2007-07-19 | 2016-03-15 | Boston Scientific Scimed, Inc. | Endoprosthesis having a non-fouling surface |
US8815273B2 (en) | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US8221822B2 (en) | 2007-07-31 | 2012-07-17 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
US8900292B2 (en) | 2007-08-03 | 2014-12-02 | Boston Scientific Scimed, Inc. | Coating for medical device having increased surface area |
US8216632B2 (en) | 2007-11-02 | 2012-07-10 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8029554B2 (en) | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US8920491B2 (en) | 2008-04-22 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical devices having a coating of inorganic material |
US8932346B2 (en) | 2008-04-24 | 2015-01-13 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
US8449603B2 (en) | 2008-06-18 | 2013-05-28 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8231980B2 (en) | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
US8071156B2 (en) | 2009-03-04 | 2011-12-06 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8287937B2 (en) | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
Also Published As
Publication number | Publication date |
---|---|
US5824049A (en) | 1998-10-20 |
US8313521B2 (en) | 2012-11-20 |
US20070150047A1 (en) | 2007-06-28 |
AU716005B2 (en) | 2000-02-17 |
AU5588896A (en) | 1996-12-19 |
CA2178541A1 (en) | 1996-12-08 |
US5873904A (en) | 1999-02-23 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2178541C (en) | Implantable medical device | |
US6096070A (en) | Coated implantable medical device | |
US7611532B2 (en) | Coated implantable medical device | |
CA2278586C (en) | Coated implantable medical device | |
US8758428B2 (en) | Coated implantable medical device | |
US6730064B2 (en) | Coated implantable medical device | |
US6530951B1 (en) | Silver implantable medical device | |
WO1998017331A1 (en) | Silver implantable medical device | |
US7896914B2 (en) | Coated implantable medical device | |
US20150150696A1 (en) | Coated implantable medical device |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
MKEX | Expiry |
Effective date: 20160607 |