US3568214A - Artificial heart system and method of pumping blood by electromagnetically pulsed fluid - Google Patents

Abstract

AN ARTIFICIAL HEART SYSTEM INCLUDING METHOD AND APPARATUS, THE APPARATUS COMPRISING, PREFERABLY, TWO INTERCONNECTED VENTRICLES, EACH INTERNALLY PROVIDED WITH AN ACCUMULATOR DIAPHRAGM WHICH IS, ACCORDING TO THE METHOD, SERIALLY FLEXED IN RESPONSE TO PULSATILE DISPLACEMENT OF ELECTRICALLY CONDUCTIVE FLUID OTHER THAN BLOOD, THE DISPLACEMENT BEING DEVELOPED BY AN ELECTROMAGNETIC FLUID DRIVING DEVICE POWERED BY THERMOELECTRICALLY DERIVED ELECTRICAL ENERGY.

Description

Mardl 1 971 F. R. GOLDSCHMIED 3,

ARTIFICIAL HEART SYSTEM AND METHOD OF PUMPING BLOOD BY. ELECTROMAGNETICALLY PULSED FLUID- Filed July '24, 1968 2 Sheets-Sheet l o 35 1 It HI 'I'I a 1 low I I 1 MIM INVENTOR. FABIO R. GOLDSCHMIED ATTORN M rch 9. 1 71 F. R. GOLDSCHMIED 3,553,214 I ARTIFICIAL HEART SYSTEM AND METHOD OF PUMPING BLOOD BY ELECTROMAGNETICALLY PULSED FLUID '2 Sheets-Sheet 2 Filed July 24, 1968 INVENTOR. FABIO R. GOLDSCHMIED ATTORNEY United States Patent 3,568,214 ARTIFICIAL HEART SYSTEM AND METHOD OF PUMPING BLUOD BY ELECTROMAG- NETI'CALLY PULSED FLUID Fabio R. Goldschmied, Salt Lake City, Utah, assignor to University of Utah Filed July 24, 1968, Ser. No. 747,394 Int. Cl. A61f 1/24 US. Cl. 3-1 8 Claims ABSTRACT OF THE DISCLOSURE An artificial heart system including method and apparatus, the apparatus comprising, preferably, two interconnected ventricles, each internally provided with an accumulator diaphragm which is, according to the method, serially flexed in response to pulsatile displacement of electrically conductive fluid other than blood, the displacement being developed by an electromagnetic fluid driving device powered by thermoelectrically derived electrical energy.

The present invention relates to electromagnetic pumping systems and more particularly to electromagnetic pumping systems cooperating with ventricular structure for replacing or assisting a heart in its function of pumping blood through a living body.

In recent years considerable experimentation has been conducted to construct workable artificial heart pumps for replacing or assisting damaged or diseased hearts of living beings. Transplants of artificial hearts in animals have met with limited success, however, a self-contained, fully successful arificial heart has not, until this present invention, been devised.

Pumping devices utilizing moving parts have generated undesirable heat and have been susceptible to wear and deterioration. Electromagnetic pumps, with no mechanical moving parts, have not previously been generally accepted because the use thereof has depended largely upon passing electric current through the blood. See US. Pat. 3,206,768 in this regard. The passing of current through the blood generates undesirable amounts of heat within the blood because of the poor conductivity of the blood. Moreover, the low conductivity of the blood requires the use of high current densities which cause electrolysis of the blood. Difliculty has also occurred in developing suitable power sources which may be implanted within the body for long-term use without servicing or recharging. Many conventional artificial heart devices are powered by external sources of energy, such as compressed air, which greatly restrict the mobility of the user.

It is, therefore, a primary object of the present invention to provide an artificial heart system which alleviates or overcomes problems of the mentioned type.

The present invention utilizes an electromagnetic pump with no moving parts to pulse a conducting fluid other than blood. Preferably, the fluid is in simultaneous communication with two ventricles and is displaced by the electromagnetic pump alternately toward one or the other of the two ventricles. Volume changes in the ventricles are accommodated by flexing diaphragms or accumulators which control the volume of blood allowed within each ventricle and maintain a constant uniform blood volume in a natural body circulatory system. A long-life radioisotope thermoelectric power source adapted to be implanted within the chest cavit is used to supply energy to the electromagnetic pump.

Using the presently preferred apparatus and method of the invention, desirable pulsatile flow is achieved with complete compensation for blood volume changes. Un-

desirable heat and wear of moving mechanical parts is Patented Mar. 9, 1971 eliminated. The problem of electrolysis and heat absorption in the blood are absent and complete mobility of the user is possible for long periods of time.

Accordingly, it is another primary object of the present invention to utilize an electrically conductive and heat conductive fluid, other than blood, for electromagnetic pumping in an improved artificial heart system.

It is another important object of the present invention to provide a novel system for pulsatilely pumping blood using an electromagnetic pumping device Without moving parts.

Another and no less important object of the present invention is to provide a unique system for pulsatilely pumping blood using a biventricular system to compensate for blood volume changes.

A further and no less important object of the present invention is to provide a novel electromagnetic pumping device which is powered by a radioisotope thermoelectric source.

Another significant object of the present invention is to provide an improved artificial heart pump system capable of being implanted within the body,

These and other objects and features of the present invention will become more fully apparent from the following description and appended claims taken in conjunction with the accompanying drawings wherein:

FIG. 1 is a schematic representation of one presently preferred biventricular embodiment of the present inven-- tion; and

FIGS. 2-5 schematically illustrate other presently preferred embodiments of the ventricles illustrated in FIG. 1.

In the presently preferred embodiment of the invention, a biventricular system is illustrated. Although a monoventricular system could be used, the biventricular system is preferred because pulsatile pumping of blood normally requires a way of compensating for blood volume changes within the system. Pulsatile, rather than steady state, blood flow is desirable to enhance capillary perfusion, to prevent visco-elastic creep of the vessels and to operate the physiological baroreceptors.

Reference is now made to FIG. 1 wherein the biventricular artificial heart system generally designated 20 comprisesventricles 22 and 24. Each of theventricles 22 and 24 is substantially identical to the other, respectively comprising arigid chamber 26, 27 which is provided with anentrance port 28, 29 and anexit port 30, 31. Eachentrance port 28 and 29 is provided with a one-way valve 32 and 33 such as a Gott check valve. Similarly, eachexit port 30 and 31 is provided with a one-way valve 34 and 35 which open in a direction opposite thevalve 32. Although Gott valves are shown in the illustrated embodiment, clearly any suitable one-way valve, such as a ball check valve could be used. I An accumulator diaphragm orresilient partition 36, 37 is peripherally attached to the interior of therespective ventricles 22 and 24, essentially central thereof, to divide each ventricle into twoseparate chambers 38, 40 and 39, 41. Eachaccumulator 36, 37 is preferably made of an inert, flexible material, such as silastic, a commercially available silicone rubber made by Dow-Coming Corporation.

Eachentrance port 28, 29 and eachexit port 30, 31 have exclusive communication with therespective chambers 38, 39. Thechambers 40 and 41 in theventricles 22 and 24 open into respectiveupper portions 42 and 44 of a generallyU-shaped tube 46. Thetube 46, thus, accommodates communication of therespective chambers 40 and 41 in theventricles 22 and 24.

An electricallyconductive fluid 48, such as mercury in the preferred embodiment, is confined, in part, by thetube 46. If desired, asecond fluid 50 may be located in thechambers 40 and 41 and theupper portion 42 and 44 of the U-shaped tube above themercury 48. Thefluid 50 is preferably a biologically acceptable fluid, such as, for example, sterile isotonic saline solution. The purpose for the isotonic saline St is to prevent contamination ofblood 52 located inchambers 38 and' 39 in the event the accumulator I36 should rupture, develop a puncture or the like. Clearly, thesaline solution 50 is merely a safety feature and is not essential to the apparatus or'method comprising the present invention.

The lower portion '54 of thetube 46 carries anelectromagnetic pump 56. It is presently preferred that a lightweight, easily portable or man-mobile Faraday type electromagnetic pump be used. In the illustrated embodiment, themercury 48 is disposed in a thinwalled duct 58 within thepump 56. Direct current is passed through a winding on a magnetic core (not shown) comprising part of the pump. The magnetic core is oriented so as to develop a magnetic field having one axis perpendicular to the direction of flow of themercury 48 as shown byarrows 60 and 62. A voltage is impressed across themercury 48 in a direction mutually perpendicular to the direction of flow of the mercury and the magnetic field. As a result, the mercury is caused to move axially in the direction ofarrows 60 and 62 while the direct ourent is being conducted to theelectromagnetic pump 56.

The direct current, needed by thepump 56, is generated by athermoelectric power source 64. Energy for thethermoelectric power source 64 is preferably derived from radioisotope material such as, for example, promethium 147, made commercially available by Isochem, 'Inc., of Richland, Wash. Promethium 147 has a half-life of 2.62 years and a low energy decay requiring very little shielding and which provides the high current, low voltage output required by the electromagnetic pump. Although promethium 147 is presently preferred, any suitable radioisotope material having a relatively long half-life and low energy decay, including strontium 90, could be used. Moreover, other long-term electrical energy sources, such as chemical power supplies, biological fuel cells, muscle-power generators and the like are within the scope of this invention.

The direct current provided by the thermoelectric source is pulsed by acontrol device 66 which comprises capacitive elements and a standard conventional pacemaker system for pulsing the direct current to the thermoelectric source.

In the operation of the artificial heart system illustrated in FIG. 1, when the system has been implanted Within a living being, direct current from thepower source 64 is pulsed by thecontrol device 66. The resulting pulsatile current is conducted to the electromagnetic driving mechanism 56-. Themercury 48 is then moved in a direction mutually perpendicular to the flows of both the current and the electromagnetic field in thepumping mechanism 56, according to Faradays Law. The accumulators and 41 within theventricles 22 and 24 are both caused to flex in the direction of flow of themercury 48. Thechamber 38 inventricle 22 expands to receiveblood 52 from the cardiovascular system of the living being, thevalve 32 admitting the blood into thechamber 38. Thechamber 39 decreases in size andblood 52 is forced out of thechamber 39 through theexit port 31, thevalve 35 accommodating one-way movement of the blood out of theventricle 24. Between pulses themercury 48 will move in a direction opposite thearows 60 and 62 toward an equilibrium point due to the memory of theelastomeric accumulators 36 and 37 and the force of gravity upon themercury 48. Movement of themercury 48 in a direction oppositearrows 60 and 62 will cause the reverse effect, i.e. blood will flow intocompartment 39 through the valve 3-3 and out ofcompartment 38 through thevalve 34 until the next pulse is received by thepump 56. v

Alternatively, the same pump or an adjacent substantially substantially identical pump could be used to forcibly 4- move themercury 48 in the opposite direction, thereby cyclically forcing themercury 48 alternately toward theventricles 24 and 22. The interval of alternation would be determined by the pacemaker (not shown) within the control device. 66.

If desired, the ventricle illustrated in FIG. 2 can be used in place of theventricles 22 or 24 illustrated in FIG. 1. With reference to FIG. 2, a cylindrically-shaped rigid element 70- is provided with aninlet port 72 and anoutlet port 74. Each of theports 72 and 74 is provided with one-way valves 32 and 34 which are substantially identical tovalves 32 and 34 in FIG. 1.Inlet port 72 andoutlet port 74 are connected by tube 76 sealed in fluid-tight relation at theends 78 and 80 to theinterior surface 82 of theelement 70. The fluid 50, moved by themercury 48 as described in FIG. 1, causes the tube 76 to collapse and squeezes theblood 52 contained therein through theoutlet port 74. When the tube 76 returns to its normal cylindrical configuration,blood 52 is allowed to pass through theinlet port 72 into the tube 76.

FIG. 3 illustrates another preferred embodiment of a ventricle which may be used in place of theventricles 22 and 24 of FIG. 1. In the embodiment of FIG. 3, inlet port 86 andoutlet port 88 are disposed in a substantially flat element 90. A bell-shapedmember 92 cooperates with the element to form a rigid ventricle. Anaccumulator 94 is peripherally attached at 95 between the element 90 and themember 92 in fluid-sealed relation, thus forming twoseparate accumulator chambers 96 and 98. Theaccumulator chamber 98 is in free communication withfluid 50 through the tube 97. When the fluid is forced into thechamber 98, the accumulator 9'4 collapses forcing blood'52 out through theoutlet port 88. When fluid 50 is withdrawn from thechamber 98, the chamber 96 is filled with blood through the inlet port 86.

FIG. 4 illustrates still another embodiment of a ventricle which may be used in place of theventricles 22 and 24 illustrated in FIG. 1. With reference to FIG. 4,inlet port 100 andoutlet port 102 are disposed in the essentially bell-shapedmember 104. The bell-shapedmember 104 cooperates with an essentially flat element 106 to form a rigid ventricle. The ventricle is internally provided with an accumulator 108 which is fluid-sealed at theperiphery 110 between themember 104 and the element 106. The acumulator108 formsaccumulator chambers 112 and 114. When accumulatorchamber 114 expands due to the influx offluid 50 through thetube 116,blood 52 is forced out of theoutlet port 102 and, conversely, when theaccumulator chamber 114 decreases in size due to the egress offluid 50 through thetube 116, blood will enter theaccumulator chamber 112 through theinlet port 100.

FIG. 5 schematically illustrates a differential piston pump which may be used in place of theventricles 22 and 24 of FIG. 1. In FIG. 5, a rigid casing is provided withoutlet port 122 andinlet port 124. A rollingdiaphragm 126 is fluid-sealed at oneend 128 to thecasing 120 and, likewise, fluid-sealed at theother end 130 toadifferential piston 132. The trailing end of the piston is in contact with a high-pressure rolling diaphragm 136 fluid-sealed at the exterior of thecasing 120. Thediaphragm 136 forms achamber 138 with afluidcarrying coupling 140 which is continuous withtube 142.

Fluid 50 entering thechamber 138 through thetube 142 forces thepiston 132 to advance toward'the inlet andoutlet ports 124 and 122, respectively. As thedifferential piston 132 moves, the rollingdiaphragm 126 rolls upon itself andblood 52 is forced out through theoutlet port 122. Conversely, when fluid 1'50 egresses throughtube 142, thedifferential piston 132 will move in the opposite direction causing thediaphragm 136 to roll upon itself and blood will move through theinlet port 124.

It should now be appreciated that the present invention provides a new and useful apparatus and technique for pumping blood in connection with or in place of the heart of a living being. Electromagnetic pumping of a conducting fluid other than blood reduces heat generation in the blood and substantially eliminates electrolysis thereof. The provision of a long-life radioisotope energy source used in connection with a lightweight thermoelectric generator makes implantation of the artificial heart system within the body of the living being practical.

The invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. The present embodiments are, therefore, to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore to be embraced therein.

What is claimed and desired to be secured by United States Letters Patent is:

1. An artificial heart pump apparatus comprising electrically conductive fluid other than blood and ventricle means having accumulator means disposed therein responsive to pulsatile displacement of the electrically conductive fluid, the accumulator means comprising at least one resilient partition defining two chambers the peripheral edge of the partition being joined to the ventricle means in fluid tight relation, one chamber and one surface of the partition adapted to be disposed in pressure communication and contact with circulated blood obtainable from the cardiovascular system of a living body, the

other chamber and a second opposed surface of the partition being in pressure communication with the electrically-conductive fluid, electromagnetic means for exposing said electrically-conductive fluid to a magnetic field caused by the electromagnetic means to exert a pulsating force on and cyclically displace the electricallyconductive fluid thereby causing the conductive fluid to cyclically exert pressure upon the second surface of the partition in the other chamber, and ingress and egress valve means adapted to be placed in fluid communication with the cardiovascular system for successively receiving and emitting substantially equal volumes of blood to and from the one chamber of the ventricle means in response to back and forth displacement of the partition.

2. In an apparatus as defined in claim 1 wherein said ventricle means comprise interconnected biventricular structure, the two parts of said biventricular structure being in simultaneous communication one with the other linked by the electrically-conductive fluid, each of the two parts of the biventricular structure being provided with separate accumulator structure each defining the two chambers, adapted to serially exert increased pressure on the blood to respectively simultaneously expel and draw equal volumes of blood from and to the one chambers of the accumulator structure, thereby maintaining a uniform blood level for use within the cardiovascular system.

3. An artificial heart pump comprising in combination: thermoelectric power source means for generating electrical energy, means for pulsing the flow of electrical energy from the source means, confined electrically conductive fluid, electromagnetic driving means responsive to the pulsed flow of electrical energy for pulsatilely pumping the confined electrically-conductive fluid by magnetic energy without the use of mechanically moving parts, dual ventricles each comprising accumulator means adapted to separate blood on one side from at least one other fluid subject to pressure caused by the action of the electrical energy confined within fluid communication means and disposed on the other side of the accumulator means, said accumulator means responding to changes in pressure exerted by the confined electrically-conductive fluid when influenced by electrical energy, and one-way valve means for selectively controlling the flow of the blood in and out of the ventricles.

4. In a heart pump as defined in claim 3 where in the thermoelectric power source means comprises a manmobile, long-term radioisotope thermoelectric power source.

5. In a heart pump as defined in claim 3 further con1- prising an isotonic, biologically compatible liquid interposed between the electromagnetic driving means and the accumulator means.

6. In a method of pumping blood within a living body by cyclically exposing an electrically-conductive fluid to an electromagnetic field, thereby pulsing the electricallyconductive fluid which is in pressure-communication with one side of a deformable accumulator partition of sheet material, flexing the central interior of the sheet accumulator partition in response to the pulsatile pressure exerted by the electrically-conductive fluid, imposing the pulsatile pressure on the blood across the sheet partition which blood is in communication with the other side of the deformable sheet accumulator partition and displacing the blood in response to the fluid pressure in a direction pre-defined by check valves.

7. A method of pumping blood through a ventricular artificial heart apparatus used by a living body comprising the steps of: providing a source of electrical current, pulsatilely exposing electrically conductive liquid to the electrical current to pulsatilely pump the electrically conductive liquid to impose a series of pressure pulses upon one side of an accumulator diaphragm comprising part of the artificial heart apparatus, flexing the accumulator diaphragm responsive to the pressure pulses of the electrically-conductive liquid, and cyclically receiving and emitting blood adjacent the other side of the accumulator diaphragm, maintaining an essentially constant uniform blood volume within the cardiovascular system of the living body according to the motion of the flexing accumulator.

8. A method as defined in claim 7 wherein the pulsatilely exposing step is responsive to a conversion of ther-' mal energy emitted by a radioisotope source to electrical energy.

References Cited UNITED STATES PATENTS 2,812,716 11/1957 Gray 103-44X(D) 3,007,416 11/ 1961 Childs 10344 (D) 3,277,827 10/ 1966 Roes 1031(M) 3,379,191 4/1968 Harvey 31X OTHER REFERENCES Air-Driven Artificial Hearts Inside The Chest, by W. Seidel et al. transactions of the American Society of Artificial Internal Organs, vol. VII, 1961, pp. 378-385.

Prolonged Mechanical Circulatory Support: Analysis of Certain Physical and Physiologic Considerations, by E. Bernstein et al., Surgery, vol. 57, No. 1, pp. 103-122.

RICHARD A GAUDET, Primary Examiner R. L. FRINKS, Assistant Examiner U.S.Cl.X.R.

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