CA2096025A1 - Muscle powered cardiac assist system - Google Patents
Muscle powered cardiac assist systemInfo
- Publication number
- CA2096025A1 CA2096025A1 CA002096025A CA2096025A CA2096025A1 CA 2096025 A1 CA2096025 A1 CA 2096025A1 CA 002096025 A CA002096025 A CA 002096025A CA 2096025 A CA2096025 A CA 2096025A CA 2096025 A1 CA2096025 A1 CA 2096025A1
- Authority
- CA
- Canada
- Prior art keywords
- skeletal muscle
- muscle mass
- heart
- muscle
- contraction
- 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.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36042—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of grafted tissue, e.g. skeletal muscle
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
- A61M60/191—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart mechanically acting upon the outside of the patient's native heart, e.g. compressive structures placed around the heart
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/289—Devices for mechanical circulatory actuation assisting the residual heart function by means mechanically acting upon the patient's native heart or blood vessel structure, e.g. direct cardiac compression [DCC] devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/515—Regulation using real-time patient data
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/562—Electronic control means, e.g. for feedback regulation for making blood flow pulsatile in blood pumps that do not intrinsically create pulsatile flow
- A61M60/569—Electronic control means, e.g. for feedback regulation for making blood flow pulsatile in blood pumps that do not intrinsically create pulsatile flow synchronous with the native heart beat
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/871—Energy supply devices; Converters therefor
- A61M60/878—Electrical connections within the patient's body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/871—Energy supply devices; Converters therefor
- A61M60/882—Devices powered by the patient, e.g. skeletal muscle powered devices
Abstract
A method and apparatus for providing assistance to a patient's heart using a surgically prepared skeletal muscle. A skeletal muscle, such as the latissimus dorsi, is carefully separated from the skeletal structure leaving innervation and vascularization intact. The muscle tissue is then separated into two independent contractile masses. Alternatively, two separate skeletal muscles may be used. The first of these is wrapped about the atria. The second is wrapped about the ventricles. Each muscle mass is individually stimulated using an implantable pulse generator. Stimulation to the muscle mass is synchronized to the naturally or artificially paced contractions of the heart to provide the maximum in assistance. During each complete heart cycle, the muscle mass assisting the ventricles is stimulated at the same time as contraction of the ventricular myocardium. The muscle mass assisting the atria is then stimulated at the same time as contraction of the atrial myocardium. Various sensing and stimulating modes may be used to optimize cardiac assistance.
Description
WO 92/06738 PCr/l,lS91/06800 209602~ ~ -MUSCLE POWERED CARDIAC ASSIST SYSTEM
CROSS REFERENCE TO CO-PENDING APPLICATIONS
'` ~5 ' '.
This application is related to U.S. Serial No. 07/446,594, filed December 6, 1989, entitled "Steroid Eluting Intramuscular Lead"; U.S. Serial No.07/446,593, filed December 6, 1989, entitled "Muscle Fitness Detection by Colorimetry"; U.S. Serial No. 07/446,592, filed December 5, 1989, entitled "Muscle Work Output Monitor by Intramuscular Temperature Variation Measurement~'; and U.S. Serial No.
07f446,811, filed December ~. 1989, entitled "Muscle Contraction Control by Intramuscular Pressure Monitorin3~
- :
BACKGROUND OF THE INVENTION
,. 15 1. ~Field of the Invention--The present invention relates generally to ":
implantable cardiac assist systems, and more particularly, relates to implantable -cardiac assist systems which are powered by a skeletal muscle of the patient. -2. Descriotion of the Prior Art--The earliest cardiac assist systems were 2~ mechanical devices which move blood using an artificially powered pump. The two - ~ ' greatest disadvantages of such mechanical pumps relate to materiàls and energy sources. Material problems arise when artificial materials which are foreign to the ~ ~
body cause thrombosis after coming in contact with the blood. Much research is ~ ~ .
currently ongoing in an attempt to find materials which are more compatible with :;~
the blood. Yet the use of thrombogenic materials remains a major disadvanta~e of cardiac assist systems using mechanical pumps.
,~ A second major disadvantage of mechanical pumps resides in the energy systems. Current energy storage systems in the form of batteries are simply not practical. With present day technology, the energy density and the capacity of . 30 implantable batteries limits the useful life of the battery. With percutaneous or radio frequency recharge, the energy stored corresponds to a few hours up to a day.
However, this ordinarily leads to undue risk of infection. ~, .
:
~,.~.', , ., ~ ,.............. . ..
wo 92/06738 PC~/US91/06800 209~025 . --2~
The most promising solution to the energy aspect is to use a biochemical power source such as a muscle. Wrapping the skeletal muscle around the heart seems to resolve the issues around the materials problems. Because the blood touches only naturally endothelialized tissue, thrombogenic problems are eliminated. Because the vascularization of the skeletal muscle is preserved, power is derived from normal biological oxidation reactions.
United States Patent No. 4,411,268 issued to Cox and United States Patent No. 4,81~,952 issued to Khalafalla, both of which are incorporated herein by reference, teach skeletal muscle powere~ cardiac assist systems. Even though such cardiac assist systems are known in the art, the prior art systems do not specifically provide atrio-ventricular synchrony (i.e., either natural or stimulated synchrony with a skeletal muscle boost).
SUMMARY OF THE INVENTION
The present invention provides a skeletal muscle powered cardiac assist system which can provide assistance to the right, as well as the leR, side of the heart. !t also ensures that the hemodynamic benefits of atrial filling are similarly assisted.
Right heart boost is important to ensure adequate pulmonary function in a ~ patient experiencing atrial myocardial disease. Sufficient pulmonary pressure is necessary to provide the efficient oxygenation required by a patient previously weakened by hemodynamic deficiency.
Similarly, skeletal muscle assistance to the atria ensures that even with very ineffective myocardial tissue, suflicient atrial kick is present to ofler the hemodynamic improvement associated with optimal ventricular filling.
The present invention provides these advantages by surgically dividing the harvested skeletal muscle into two separately stimulatable contractile components, or two separate skeletal muscles. The first issued to assist the atria, and the second assists the ventricles. Stimulation of the ventricular component is 3û synchronized with contractions of the ventricles whether naturally or artificially ,.,.. . . - . ~ ................... . .
: ... - . . ....................... .
~. ' ~'. ,: - . .. . : .
wo 92/06738 Pcr/US9l/o68oo 203~6~2~
paced. Similarly, the atrial component is stimulated to contract in proper synchrony with naturally or artificially paced atrial contractions.
BRIEF DESCRIPTION OF THE DRAWINGS
Further objects and advantages of the present invention will be apparent as the same becomes better known from the detailed specification and accompanying drawings in which like reference numerals refer to like components and wherein:
FIG. 1A is a lef~ side view of a patient showin3 the location of skeletal .-muscle to be ~sed for cardiac assist: -FIG. lB is a vie.v~ simila~ to FIG. 1A wlth the skeletal muscle severed posteriorly;
FIG. lC is a front view of a patient's thorax after completion of the implant, !, but before closure;
FIG. lD is a view similar to FIG. 1C of an alternative embodiment;
FIG. 2A is a block diagram for the implantable pulse generator of the .`
: present invention; .
. FIG. 2B is a block diagram of an alternative embodiment of the implantable pulse generator; and, FIG. 3 is a timing diagram for the pulses produced by the implantable pulse ~ .
generator of the present invention.
DETA~ED DES~ÇR!PTIQN OF THE PREFERRED EMBODIMENTS
FIG. lA is a left side view of a patient 10 showing the initial location of the skeletal muscle 11 to be used to power the cardiac assist system of the present : ~:
invention. Use of the left latissimus dorsi is shown by way of example only and is not intended to limit the present invention. Other skeletal muscles may also be . used. ~ -,.. ,...... ~ .- ... . . .
,. . . .
,.,,, ~ ;, . : ' ' ; ~ ' .. , , ~ . , . . ,; ~.
WO 92/06?38 PCr/US91/06800 . 209~02~
Shown schematicall~ is t~e line of incision 12 for severing skeletal muscle 11 from its initial position. Notiee that skeletal muscle 11 is severed posteriorly and : inferiorally to preserve maximum innervation and vascularization.FIG. 1 B is a similar view of patient 10 with skeletal muscle 11 severed at lineof incision 12 (see also FIG. 1A). After being severed, skeletal muscle 11 is carefully elevated in the direction of arrow 14. At this time, skeletal muscle 11 is separated into an upper compone.~ 15 and a lower component 16. It is important to separate skele~al muscle F ', wh~ slili p!eservin9 the maximum innervation and vascularization . . ...
FIG. lC is a front vie~ patie~ showing upper component 15 wrapped about both ri~ht and le~. a~ri- Gl neart ~, 7. z.~d Iower component 16 wrapped about both right and le'-. ventricles c' heart 17. Tne free ends of upper component 15 ~, and lower component 16 are fixedly attached in the manner known in the art.
. Implantable pulse generator 40 is implanted in a convenient place, such as 1~ the lower abdomen.
As shown, both components may be harvested from the latissimus dorsi, - although other skeletal muscles may be used. Each is prepared and conditioned in accordance with the teach,ny o' United S,ates Patent Number 4,411,268 issued to Cox. Upper componen' 1a is stimulated to contract by electrode 32 which is coupled to be implantable pu!se generat3, 40 via insulated lead 34. Similarly, , ~ electrode 28, which is coupled to the imp!antable pulse generator 4û by insulated .! lead 30, stimulates contractions in lower component 16. Heart 17 may be artificially paced transvenously through superior vena cava 26 in accordance with . one or more of the accepted pacing modalities, or epicardially in accordance with one or more accepted pacing modalities. Atrial and ventricular sensing and stimulation are accomplished using epicardial leads 42 and 44, respectively.
FIG. 1D is a view similar to that of Fl~i. 1C. However, in this embodiment, upper component 15 is taken from the right latissimus dorsi and lower component 16 is taken from the left latissimus dorsi. All other elements are as previously` 30 described.
.
wo 92/06738 Pcr/l~S91/o68oo 5 209~2~
FIG. 2A is a block diagram of the preferred mode of implementing implantable pulse generator 40. In the preferred mode, the circuitry is microprogrammable, although hardwired embodiments are also useful (see also FIG. 2B). The microprogrammed architecture is the most flexible in that it can be programmed to operate in any of the ICHD modes and others not yet defined.
Preferably, implantable pulse gene, ator 40 operates in the DDD mode as described in U.S. Patent No. 4,312,355, issued to Funke, herein incorporated by reference.In the DDD mode, the pacer senses the ven~ricle for naturally occurring ventricular contractions. If such a contraction is nGt sensed within the predetermined (and programmable) escape interval, an artificial pacing pulse is supplied to the right ventricle. If a natural contraction is sensed, the artificial pacing pulse to the ventricle is inhibited. In either case, the atrium is next sensed.
Again, an artificial pacing pulse is supplied to the atrium if a natural contraction is not sensed within the escape imerval.
Controller 58 is a microprocessor which is microprogrammed to provide the desired timing and logic to implement the chosen modality. As described above, the DDD mode is preferred. Atrial pacing lead 42 supplies electrical coupling between the at,.um and sense amplifier 55 and atrial output amplifier 59 via wired or circuit 61. Similarly, ventricle pacing lead 44 supplies electrical coupling between the ventricles and ventricular output amplifier 6û and sense amplifier 56 via wired or circuit 62. The skeletal muscle masses are stimulated by muscle output amplifier 48 and muscle output amplifier 50 via leads 34 and 30, respectively.
FIG. 2B is a block diagram of an alternative embodiment of implantable pulse generator 140 which supplies the stimulation pulses to the upper component15 and the lower component 16. This embodiment employs hardwired rather than microprogrammed circuitry. In the alternative mode, and not to be construed as limiting of the present invention, implantable pulse generator 40 artificially paces heart 17 in the DVI mode according to the ICHD code.
1,,, ,,,~ ~ , ; ' !
' ' .. ,', ' ' ' ,' ' . ' ' i ,. . ;' ' ' ' ' ' ' . ' ' ~ `' ' ,.~. . . ' '' . .
wo 92/06738 Pcr/US9l/o68oo ._ .
2 0 9 6 0 2 ~-6-In the DVI mode the pacer senses the ventricle for naturally occurring ventricular contractions. If such a contraction is not sensed within the predetermined escape interval, an artificial pacing pulse is supplied to the ventricle.
If a natural contraction is sensed, the artificial pacing pulse to the ventricle is inhibited. In either case, an artificial pacing pulse is supplied to the atrium after a suitable delay from contraction of the ventricle. United States Patent No. 3,595,242 issued to Berkovits, herein incorparated by re.erences, teaches this artificial pacing mode in greater detail.
Pacing lead 44 is implanted in hean~ 17 as taught in United States Patent No. 3,902,501 issued to Citron, et al. It is electrically coupled to sense amplifier 156 for detection of naturally occurring ventricular contractions. The output ofsense amplifier 158 is coupled to inhibit logic 15.. If sense amplifier 156 senses ~` a naturally occurring ventricular contraction before the end of the escape inteNal, as determined by escape interval timer 158, the artificial pacing pul-~e is inhibited by inhibit logic 154. Ventricular output amplifier 160 amplifies the artificial pacing 1: ~ pulse and couples it to pacing lead 44 via wired or'circuit 162.
A ventricular contraction, whether naturally occurring or artificially paced, results in the generation of a stimulation burst to lower component 16 by muscle . output amplifier i50 after a time period determined by delay circuit 149. This stimulation burst is coupled to the lower component 16 by insulated lead 30 and electrode 28 (see also FIG. lC).
Similarly, the electrical representation of the ventricular contraction is delayed by v-a delay 152 for the generation of an atrial pacing pulse by atrial 3 ~ output amplifier 146. This atrial stimulation pulse is delivered to the atrium by ~: 25 pacing lead 42. The suitable v-a delay is well documented in the prior art. It is on the order of 300-700 milliseconds for the normal heart.
;~ ARer the same v-a delay and the delay of delay circuit 147, muscle output amplifier 148 generates a burst of pulses to stimulate the upper component 15.
, ~ This burst is transferred to upper component 15 by insulated lead 34 and electrode 30 - 32 (see also FIG. 1C).
i~
wo 92/06738 Pcr/~S91/o68oo 7 2~96~2~
FIG. 3 is a graphical representation of the output of implantable pulse generator 40 for one typical cardiac cyclL. Graph 70 shows the presence of a .
ventricular contraction as pulse 72. In this case the ventricular contraction isartificially stimulated by pulse 72 as produced by ventricular output amplifier 60.
This pulse is as measurable on pacing lead 44.
Graph 74 shows the resulting output of muscle output amplifier 50. In the preferred mode, stimulation of the lower component 16 is accomplished by a burst .
of four pulses comprising pulses 76a, 76b, 76c, and 76d.
Graph 80 shows the atrial stimula:ion pulse 82 generated by atrial output -~
amplifier 59 or 146 following the end of the atrial escape period because a naturally occurring atrial contraction is not sensed. As explained above, this v-a delay can be measured from the sensed or artificially stimulated ventricular event.
Graph 84 shows the burst of pulses generated by muscle output amplifier 48 or 148. This burst consists of the four pulses B6a, 86b, 86c, and 86d. J -. 15 Having thus described the preferred mode of the present invention, those of skill in the art will be readily able to apply the teaching found herein to various ; other skeletal muscle powered cardiac assist systems without deviating from the scope of the claims hereto attached.
What is claimed is:
?
' .
.
~, , . , , ,. : ,,, ~ ,: , , ' , , ' ' ' ', . ' - ` .
CROSS REFERENCE TO CO-PENDING APPLICATIONS
'` ~5 ' '.
This application is related to U.S. Serial No. 07/446,594, filed December 6, 1989, entitled "Steroid Eluting Intramuscular Lead"; U.S. Serial No.07/446,593, filed December 6, 1989, entitled "Muscle Fitness Detection by Colorimetry"; U.S. Serial No. 07/446,592, filed December 5, 1989, entitled "Muscle Work Output Monitor by Intramuscular Temperature Variation Measurement~'; and U.S. Serial No.
07f446,811, filed December ~. 1989, entitled "Muscle Contraction Control by Intramuscular Pressure Monitorin3~
- :
BACKGROUND OF THE INVENTION
,. 15 1. ~Field of the Invention--The present invention relates generally to ":
implantable cardiac assist systems, and more particularly, relates to implantable -cardiac assist systems which are powered by a skeletal muscle of the patient. -2. Descriotion of the Prior Art--The earliest cardiac assist systems were 2~ mechanical devices which move blood using an artificially powered pump. The two - ~ ' greatest disadvantages of such mechanical pumps relate to materiàls and energy sources. Material problems arise when artificial materials which are foreign to the ~ ~
body cause thrombosis after coming in contact with the blood. Much research is ~ ~ .
currently ongoing in an attempt to find materials which are more compatible with :;~
the blood. Yet the use of thrombogenic materials remains a major disadvanta~e of cardiac assist systems using mechanical pumps.
,~ A second major disadvantage of mechanical pumps resides in the energy systems. Current energy storage systems in the form of batteries are simply not practical. With present day technology, the energy density and the capacity of . 30 implantable batteries limits the useful life of the battery. With percutaneous or radio frequency recharge, the energy stored corresponds to a few hours up to a day.
However, this ordinarily leads to undue risk of infection. ~, .
:
~,.~.', , ., ~ ,.............. . ..
wo 92/06738 PC~/US91/06800 209~025 . --2~
The most promising solution to the energy aspect is to use a biochemical power source such as a muscle. Wrapping the skeletal muscle around the heart seems to resolve the issues around the materials problems. Because the blood touches only naturally endothelialized tissue, thrombogenic problems are eliminated. Because the vascularization of the skeletal muscle is preserved, power is derived from normal biological oxidation reactions.
United States Patent No. 4,411,268 issued to Cox and United States Patent No. 4,81~,952 issued to Khalafalla, both of which are incorporated herein by reference, teach skeletal muscle powere~ cardiac assist systems. Even though such cardiac assist systems are known in the art, the prior art systems do not specifically provide atrio-ventricular synchrony (i.e., either natural or stimulated synchrony with a skeletal muscle boost).
SUMMARY OF THE INVENTION
The present invention provides a skeletal muscle powered cardiac assist system which can provide assistance to the right, as well as the leR, side of the heart. !t also ensures that the hemodynamic benefits of atrial filling are similarly assisted.
Right heart boost is important to ensure adequate pulmonary function in a ~ patient experiencing atrial myocardial disease. Sufficient pulmonary pressure is necessary to provide the efficient oxygenation required by a patient previously weakened by hemodynamic deficiency.
Similarly, skeletal muscle assistance to the atria ensures that even with very ineffective myocardial tissue, suflicient atrial kick is present to ofler the hemodynamic improvement associated with optimal ventricular filling.
The present invention provides these advantages by surgically dividing the harvested skeletal muscle into two separately stimulatable contractile components, or two separate skeletal muscles. The first issued to assist the atria, and the second assists the ventricles. Stimulation of the ventricular component is 3û synchronized with contractions of the ventricles whether naturally or artificially ,.,.. . . - . ~ ................... . .
: ... - . . ....................... .
~. ' ~'. ,: - . .. . : .
wo 92/06738 Pcr/US9l/o68oo 203~6~2~
paced. Similarly, the atrial component is stimulated to contract in proper synchrony with naturally or artificially paced atrial contractions.
BRIEF DESCRIPTION OF THE DRAWINGS
Further objects and advantages of the present invention will be apparent as the same becomes better known from the detailed specification and accompanying drawings in which like reference numerals refer to like components and wherein:
FIG. 1A is a lef~ side view of a patient showin3 the location of skeletal .-muscle to be ~sed for cardiac assist: -FIG. lB is a vie.v~ simila~ to FIG. 1A wlth the skeletal muscle severed posteriorly;
FIG. lC is a front view of a patient's thorax after completion of the implant, !, but before closure;
FIG. lD is a view similar to FIG. 1C of an alternative embodiment;
FIG. 2A is a block diagram for the implantable pulse generator of the .`
: present invention; .
. FIG. 2B is a block diagram of an alternative embodiment of the implantable pulse generator; and, FIG. 3 is a timing diagram for the pulses produced by the implantable pulse ~ .
generator of the present invention.
DETA~ED DES~ÇR!PTIQN OF THE PREFERRED EMBODIMENTS
FIG. lA is a left side view of a patient 10 showing the initial location of the skeletal muscle 11 to be used to power the cardiac assist system of the present : ~:
invention. Use of the left latissimus dorsi is shown by way of example only and is not intended to limit the present invention. Other skeletal muscles may also be . used. ~ -,.. ,...... ~ .- ... . . .
,. . . .
,.,,, ~ ;, . : ' ' ; ~ ' .. , , ~ . , . . ,; ~.
WO 92/06?38 PCr/US91/06800 . 209~02~
Shown schematicall~ is t~e line of incision 12 for severing skeletal muscle 11 from its initial position. Notiee that skeletal muscle 11 is severed posteriorly and : inferiorally to preserve maximum innervation and vascularization.FIG. 1 B is a similar view of patient 10 with skeletal muscle 11 severed at lineof incision 12 (see also FIG. 1A). After being severed, skeletal muscle 11 is carefully elevated in the direction of arrow 14. At this time, skeletal muscle 11 is separated into an upper compone.~ 15 and a lower component 16. It is important to separate skele~al muscle F ', wh~ slili p!eservin9 the maximum innervation and vascularization . . ...
FIG. lC is a front vie~ patie~ showing upper component 15 wrapped about both ri~ht and le~. a~ri- Gl neart ~, 7. z.~d Iower component 16 wrapped about both right and le'-. ventricles c' heart 17. Tne free ends of upper component 15 ~, and lower component 16 are fixedly attached in the manner known in the art.
. Implantable pulse generator 40 is implanted in a convenient place, such as 1~ the lower abdomen.
As shown, both components may be harvested from the latissimus dorsi, - although other skeletal muscles may be used. Each is prepared and conditioned in accordance with the teach,ny o' United S,ates Patent Number 4,411,268 issued to Cox. Upper componen' 1a is stimulated to contract by electrode 32 which is coupled to be implantable pu!se generat3, 40 via insulated lead 34. Similarly, , ~ electrode 28, which is coupled to the imp!antable pulse generator 4û by insulated .! lead 30, stimulates contractions in lower component 16. Heart 17 may be artificially paced transvenously through superior vena cava 26 in accordance with . one or more of the accepted pacing modalities, or epicardially in accordance with one or more accepted pacing modalities. Atrial and ventricular sensing and stimulation are accomplished using epicardial leads 42 and 44, respectively.
FIG. 1D is a view similar to that of Fl~i. 1C. However, in this embodiment, upper component 15 is taken from the right latissimus dorsi and lower component 16 is taken from the left latissimus dorsi. All other elements are as previously` 30 described.
.
wo 92/06738 Pcr/l~S91/o68oo 5 209~2~
FIG. 2A is a block diagram of the preferred mode of implementing implantable pulse generator 40. In the preferred mode, the circuitry is microprogrammable, although hardwired embodiments are also useful (see also FIG. 2B). The microprogrammed architecture is the most flexible in that it can be programmed to operate in any of the ICHD modes and others not yet defined.
Preferably, implantable pulse gene, ator 40 operates in the DDD mode as described in U.S. Patent No. 4,312,355, issued to Funke, herein incorporated by reference.In the DDD mode, the pacer senses the ven~ricle for naturally occurring ventricular contractions. If such a contraction is nGt sensed within the predetermined (and programmable) escape interval, an artificial pacing pulse is supplied to the right ventricle. If a natural contraction is sensed, the artificial pacing pulse to the ventricle is inhibited. In either case, the atrium is next sensed.
Again, an artificial pacing pulse is supplied to the atrium if a natural contraction is not sensed within the escape imerval.
Controller 58 is a microprocessor which is microprogrammed to provide the desired timing and logic to implement the chosen modality. As described above, the DDD mode is preferred. Atrial pacing lead 42 supplies electrical coupling between the at,.um and sense amplifier 55 and atrial output amplifier 59 via wired or circuit 61. Similarly, ventricle pacing lead 44 supplies electrical coupling between the ventricles and ventricular output amplifier 6û and sense amplifier 56 via wired or circuit 62. The skeletal muscle masses are stimulated by muscle output amplifier 48 and muscle output amplifier 50 via leads 34 and 30, respectively.
FIG. 2B is a block diagram of an alternative embodiment of implantable pulse generator 140 which supplies the stimulation pulses to the upper component15 and the lower component 16. This embodiment employs hardwired rather than microprogrammed circuitry. In the alternative mode, and not to be construed as limiting of the present invention, implantable pulse generator 40 artificially paces heart 17 in the DVI mode according to the ICHD code.
1,,, ,,,~ ~ , ; ' !
' ' .. ,', ' ' ' ,' ' . ' ' i ,. . ;' ' ' ' ' ' ' . ' ' ~ `' ' ,.~. . . ' '' . .
wo 92/06738 Pcr/US9l/o68oo ._ .
2 0 9 6 0 2 ~-6-In the DVI mode the pacer senses the ventricle for naturally occurring ventricular contractions. If such a contraction is not sensed within the predetermined escape interval, an artificial pacing pulse is supplied to the ventricle.
If a natural contraction is sensed, the artificial pacing pulse to the ventricle is inhibited. In either case, an artificial pacing pulse is supplied to the atrium after a suitable delay from contraction of the ventricle. United States Patent No. 3,595,242 issued to Berkovits, herein incorparated by re.erences, teaches this artificial pacing mode in greater detail.
Pacing lead 44 is implanted in hean~ 17 as taught in United States Patent No. 3,902,501 issued to Citron, et al. It is electrically coupled to sense amplifier 156 for detection of naturally occurring ventricular contractions. The output ofsense amplifier 158 is coupled to inhibit logic 15.. If sense amplifier 156 senses ~` a naturally occurring ventricular contraction before the end of the escape inteNal, as determined by escape interval timer 158, the artificial pacing pul-~e is inhibited by inhibit logic 154. Ventricular output amplifier 160 amplifies the artificial pacing 1: ~ pulse and couples it to pacing lead 44 via wired or'circuit 162.
A ventricular contraction, whether naturally occurring or artificially paced, results in the generation of a stimulation burst to lower component 16 by muscle . output amplifier i50 after a time period determined by delay circuit 149. This stimulation burst is coupled to the lower component 16 by insulated lead 30 and electrode 28 (see also FIG. lC).
Similarly, the electrical representation of the ventricular contraction is delayed by v-a delay 152 for the generation of an atrial pacing pulse by atrial 3 ~ output amplifier 146. This atrial stimulation pulse is delivered to the atrium by ~: 25 pacing lead 42. The suitable v-a delay is well documented in the prior art. It is on the order of 300-700 milliseconds for the normal heart.
;~ ARer the same v-a delay and the delay of delay circuit 147, muscle output amplifier 148 generates a burst of pulses to stimulate the upper component 15.
, ~ This burst is transferred to upper component 15 by insulated lead 34 and electrode 30 - 32 (see also FIG. 1C).
i~
wo 92/06738 Pcr/~S91/o68oo 7 2~96~2~
FIG. 3 is a graphical representation of the output of implantable pulse generator 40 for one typical cardiac cyclL. Graph 70 shows the presence of a .
ventricular contraction as pulse 72. In this case the ventricular contraction isartificially stimulated by pulse 72 as produced by ventricular output amplifier 60.
This pulse is as measurable on pacing lead 44.
Graph 74 shows the resulting output of muscle output amplifier 50. In the preferred mode, stimulation of the lower component 16 is accomplished by a burst .
of four pulses comprising pulses 76a, 76b, 76c, and 76d.
Graph 80 shows the atrial stimula:ion pulse 82 generated by atrial output -~
amplifier 59 or 146 following the end of the atrial escape period because a naturally occurring atrial contraction is not sensed. As explained above, this v-a delay can be measured from the sensed or artificially stimulated ventricular event.
Graph 84 shows the burst of pulses generated by muscle output amplifier 48 or 148. This burst consists of the four pulses B6a, 86b, 86c, and 86d. J -. 15 Having thus described the preferred mode of the present invention, those of skill in the art will be readily able to apply the teaching found herein to various ; other skeletal muscle powered cardiac assist systems without deviating from the scope of the claims hereto attached.
What is claimed is:
?
' .
.
~, , . , , ,. : ,,, ~ ,: , , ' , , ' ' ' ', . ' - ` .
Claims (7)
1. A method of assisting cardiac function comprising:
a. surgically preparing a first skeletal muscle mass;
b. surgically preparing a second skeletal muscle mass;
c. wrapping said first skeletal muscle mass about the atria of a heart;
d. wrapping said second skeletal muscle mass about the ventricles of said heart;
e. stimulating said second skeletal muscle mass to contract upon contraction of said ventricles of said heart; and f. stimulating said first skeletal muscle mass to contract upon contraction of said atria of said heart.
a. surgically preparing a first skeletal muscle mass;
b. surgically preparing a second skeletal muscle mass;
c. wrapping said first skeletal muscle mass about the atria of a heart;
d. wrapping said second skeletal muscle mass about the ventricles of said heart;
e. stimulating said second skeletal muscle mass to contract upon contraction of said ventricles of said heart; and f. stimulating said first skeletal muscle mass to contract upon contraction of said atria of said heart.
2. A method according to claim 1 wherein said stimulating of said first skeletal muscle mass is at a predetermined interval after said stimulating of said second skeletal muscle mass.
3. A method according to claim 1 or claim 2 wherein said contraction of said ventricles of said heart is artificially stimulated.
4. In a cardiac assist system powered by a surgically prepared skeletal muscle including means for sensing the occurrence of ventricular contractions, the improvement comprising:
a. first means responsively coupled to said sensing means for causing a first portion of said surgically prepared skeletal muscle to contract synchronously with said occurrence of ventricular contractions; and b. second means responsively coupled to said sensing means and said first causing means for causing a second portion of said surgically prepared skeletal muscle to contract at a different time from said first portion of said surgically prepared skeletal muscle.
a. first means responsively coupled to said sensing means for causing a first portion of said surgically prepared skeletal muscle to contract synchronously with said occurrence of ventricular contractions; and b. second means responsively coupled to said sensing means and said first causing means for causing a second portion of said surgically prepared skeletal muscle to contract at a different time from said first portion of said surgically prepared skeletal muscle.
5. The improvement of claim 4 wherein said first portion of said surgically prepared skeletal muscle contracts about the ventricles of a heart of a patient and said second portion of said surgically prepared skeletal muscle contracts about the atria of said heart of said patient.
6. A cardiac assist system powered by a surgically prepared muscle including means for sensing the occurrence of ventricular contractions, the system comprising:
a. a irst muscle mass wrapped about the atria of the heart;
b. a second muscle mass wrapped about the ventricles of the heart;
c. means for stimulating said second muscle mass to contract upon contraction of the ventricles; and d. means for stimulating said first muscle mass to contract upon contraction of said atria.
a. a irst muscle mass wrapped about the atria of the heart;
b. a second muscle mass wrapped about the ventricles of the heart;
c. means for stimulating said second muscle mass to contract upon contraction of the ventricles; and d. means for stimulating said first muscle mass to contract upon contraction of said atria.
7. The system according to claim 6 wherein said means for stimulating said first muscle mass is activated at a predetermined interval after the activation of said means for stimulating said second muscle mass.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US597,316 | 1990-10-15 | ||
US07/597,316 US5205810A (en) | 1990-10-15 | 1990-10-15 | Muscle powered cardiac assist system |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2096025A1 true CA2096025A1 (en) | 1992-04-16 |
Family
ID=24391008
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002096025A Abandoned CA2096025A1 (en) | 1990-10-15 | 1991-09-19 | Muscle powered cardiac assist system |
Country Status (7)
Country | Link |
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US (2) | US5205810A (en) |
EP (1) | EP0553123B1 (en) |
JP (1) | JPH06504210A (en) |
AU (1) | AU660289B2 (en) |
CA (1) | CA2096025A1 (en) |
DE (1) | DE69108252T2 (en) |
WO (1) | WO1992006738A1 (en) |
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-
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- 1990-10-15 US US07/597,316 patent/US5205810A/en not_active Expired - Lifetime
-
1991
- 1991-09-19 AU AU85471/91A patent/AU660289B2/en not_active Ceased
- 1991-09-19 CA CA002096025A patent/CA2096025A1/en not_active Abandoned
- 1991-09-19 EP EP91917171A patent/EP0553123B1/en not_active Expired - Lifetime
- 1991-09-19 DE DE69108252T patent/DE69108252T2/en not_active Expired - Fee Related
- 1991-09-19 JP JP3516180A patent/JPH06504210A/en active Pending
- 1991-09-19 WO PCT/US1991/006800 patent/WO1992006738A1/en active IP Right Grant
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1993
- 1993-04-14 US US08/047,722 patent/US5364337A/en not_active Expired - Lifetime
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EP0553123B1 (en) | 1995-03-15 |
EP0553123A1 (en) | 1993-08-04 |
JPH06504210A (en) | 1994-05-19 |
WO1992006738A1 (en) | 1992-04-30 |
DE69108252D1 (en) | 1995-04-20 |
DE69108252T2 (en) | 1995-07-06 |
AU660289B2 (en) | 1995-06-22 |
US5364337A (en) | 1994-11-15 |
US5205810A (en) | 1993-04-27 |
AU8547191A (en) | 1992-05-20 |
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