|Publication number||US3771174 A|
|Publication date||Nov 13, 1973|
|Filing date||Apr 28, 1972|
|Priority date||Apr 28, 1972|
|Publication number||US 3771174 A, US 3771174A, US-A-3771174, US3771174 A, US3771174A|
|Original Assignee||D Wortman|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (2), Referenced by (16), Classifications (15)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent Wortman Nov. 13, 1973 ARTIFICIAL HEART UTILIZING BLOOD PULSING FLUID OSCILLATORS Donald E. Wortman, 609 Muriel St., Rockville, Md. 20852 Inventor:
Filed: Apr. 28, 1972 Appl. No.: 248,460
U.S. Cl 3/1, 3/DIG. 2, 128/1 D, 128/D1G. 3, l28/DIG. 10,417/350, l37/81.5 Int. Cl. A611 1/24 Field of Search 3/1, DIG. 2; 128/1 R, 1 D, 214 R, DIG. 3, DIG. 10; 137/815; 417/350 References Cited UNITED STATES PATENTS 8/1971 Wortman 3/1 9/1965 Woodward 128/] R ill 'Primary Examiner-Richard A. Gaudet Assistant Examiner-Ronald L. Frinks Attorney-Edward J. Kelly et a1.
 ABSTRACT I the pressure sensitive fluid oscillators increase their frequency in accordance with the flow of blood therethrough.
' 6 Claims, 5 Drawing Figures 50 LUNGS TO BODY P.
FLUlD OSGLLMOFZ 5 FROM 4 LUNGS Hum oscmnotz FROM BODY PAIENTEDNUY13 1915 3771.174
- SHEET 2 OF 2 ARTIFICIAL HEART UTILIZING BLOOD PULSING FLUID OSCILLATORS RIGHTS OF GOVERNMENT The invention described herein may be manufactured, used, and licensed by or for the United States Government for. governmental purposes without the payment to me of any royalty thereon.
BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates generally to an artificial heart and more particularly to an electromechanical system that incorporates the principles of fluidics to provide a device for use as a total replacement for or as an aid to the heart in circulating blood throughout the body.
2. DESCRIPTION OF THE PRIOR ART Devices heretofore developed and intended for use as artificial hearts have fallen far short of their expectations, one reason being their inherent complexity. Earlier embodiments of artificial hearts, while attempting to simulate as closely as possible the action of the human heart, were dependent for their operation upon a multitude of moving parts such as valves, flexible chambers, and displacement-type pumps, plus sophisticated synchronous control systems and sensors for either speeding up or slowing down the pumping action or heartbeat. Such devices have been found to require relatively large power supplies and to occupy large volumes in addition to being prohibitively expen sive, thus detracting from their usefulness as a total replacement organ. Additionally, such devices have not been suited for prolonged service: valves tend to wear out, leak, lose their efficiency and promote blood clots; pumps and collapsible chambers tend to exert large compressive forces upon the blood to the point where the blood would become damaged; and many other moving parts wear out or become inefficient.
It is therefore an object of the present invention to provide an artificial heart that is capable of replacing or aiding the natural heart by completely or partially taking over the operation of pumping blood through the circulatory system.
It is another object of the present invention to provide an artificial heart that is inherently pressure sensitive and thus does not require any external regulating mechanism for long term use.
It is an additional object of the present invention to provide an artificial heart whichwill be chemically inert and which will not destroy or be destroyed by the blood which it pumps. I
A further object of the present invention is to provide a greatly simplified artificial heart that simulates the action of the natural heart to a high degree and yet is valveless and contains no collapsible chambers.
A still further object of the present invention is to provide an artificial heart that is economical to manufacture, has very few moving parts, and does not damage the blood in operation.
An additional object is to provide various embodiments of the artificial heart of the present invention which permits optimum matching of the components controlling the blood flow through the heart with the circulatory system so as to permit the present invention to be adaptable to the individualized requirement of the users.
SUMMARY OF THE INVENTION Briefly, in accordance with this invention, an artificial heart is provided for use as either a total replacement for the natural heart to be implanted in the chest of the user or as an external supplement during surgery or the like. The device is characterized by a pair of valveless, non-pulsitive fluid pumps each connected to a pressure sensitive fluid oscillator. One set of oscillator and pump receives oxygenated blood from the lungs and directs a pulsed flow to the remainder of the circulatory system of the body. The other set of pump and fluid oscillator receives deoxygenated blood from the general circulatory system and directs a pulsed flow of same to the lungs of the body. The fluid oscillators may be either independent or interdependent, depending on the individualized needs of the user. The pumps are run continuously at a preselected speed and have pressurevolume flow responses which simulate the natural heart. The present invention provides great improvement over the prior art in that it simulates the action of the natural heart and yet has no valves to clog the blood and no collapsible chambers to squeeze or crush the blood, thus minimizing deterioration and wear of the device itself while allowing more efiicient and dependable operation.
BRIEF DESCRIPTION OF THE DRAWINGS The specific nature of the invention as well as other objects, aspects, uses, and advantages thereof will clearly appear from the following description and from the accompanying drawing, in which:
FIG. 1 is a schematic illustration of a preferred embodiment of an artificial heart in accordance with the present invention;
FIG. 2 is a schematic illustriative of another embodiment of an artificial heart in accordance with the present invention;
FIG. 3 shows a fluid oscillator that may be utilized in accordance with the present invention;
FIG. 4 is a schematic illustration of a dual fluid oscillator that may be utilized in the present invention; and
FIG. 5 is a schematic representation of another possible dual oscillator arrangement in accordance with the present invention.
DESCRIPTION OF THE PREFERRED EMBODIMENT A brief review of the natural hearts pumping action will facilitate understanding of the efficiency with which the present invention simulates the actions of the natural heart.
The heart is a muscular organ divided into four chambers. The upper chamber on each side of the heart is called an auricle and below each auricle is another chamber called the ventricle. Deoxygenated blood from the body enters the right auricle of the heart through two large veins. The blood-filled right auricle then contracts, sending the blood into the right ventricle through the tricuspid valve. The right ventricle then contracts, which simultaneously closes the tricuspid valve and opens the semilunar valve leading to the lungs via the pulmonary artery. From the lungs, oxygen-enriched blood flows into the left auricle through the pulmonary vein. The filled left auricle contracts, forcing blood through the mitral valve into the left ventricle which in turn will contract and force the flood through another semilunar valve into the aorta which is the main artery to the body.
It is evident that an artificial heart built to the above specifications to operate over an extended period of time would encounter many mechanical difficulties due to inevitable deteriorations of its numerous valves, chambers and contraction apparatus. The present invention, while efficiently carrying out the functions of the natural heart, does not attempt to duplicate its actions. Rather it employs well-known fluidic principles in pressure-sensitive fluid oscillators that provide alternate pulsing to a pair of fluid pumps that respond to pressure input variations as would be the natural heart.
FIG. 1 illustrates in schematic form a preferred embodiment of the artificial heart of the present invention. The system of FIG. 1 is seen to be comprised of two fluid oscillators 50 and 52 which provide a pulsed flow of blood to two fluid pumps 12 and 14, respectively, by way of the conduits 26 and 28, respectively. The input to oscillators 50 and 52 is received from conduits 54 and 56, respectively, which deliver blood from the lungs and from the remainder of the circulatory system, respectively. The oscillators 50 and 52 oscillate at a frequency that varies directly as the flow of blood through the body varies. When the body is at rest, there exists a low blood flow and the frequency of oscillation will automatically lower. When the body is at work and more blood flows in the system, the oscillation will increase in frequency to pump more blood. In other words, the operation of the system is based on the dynamic properties of blood flow. The operation of fluid oscillators 50 and 52 is explained more fully below, but essentially they accept a stream of blood and emit a pulsed flow towards pumps 12 and 14. Pumps 12 and 14 have the characteristics that their outputs are directly related to their input pressure and inversely related to the pressure head against which they are pumping. The pumps thus respond to pressure variations at their inlets 26 and 28 and outlets 38 and 42 in a fashion analogous to the natural heart. One embodiment of a pump possessing such characteristics that could be utilized in the present invention is known in the art as a centrifugal pump. Centrifugal pumps have been shown to pump blood in a highly efficient and non-destructive manner, as evidenced by the F. Dorman et al paper in Volume XV of the TRANSACTIONS OF THE AME- RICAN SOCIETY OF ARTIFICIAL INTERNAL OR- GANS I969 entitled Progress in the Design of a Centn'fugal Cardiac Assist Pump with Trans-cutaneous Energy Transmission by Magnetic Coupling. Pumps 12 and 14 are powered by a motor 30 which drives shafts 34 and 36, and a power supply 32. Much efiort has been directed towards perfecting implantable motors and power supplies for the use as directed herein, whereas external equivalents are also well known in the art. It is noted in the embodiment presented in FIG. 1 that each fluid oscillator and its respective fluid pump is independent of the other pair. This allows considerable leeway to the engineer and physician in designing and providing the proper flow and pulse in the pulmonary and systemic circulatory systems for the particular user. Since there are an infinite number of selections of pulse rates and phase relations between the pulmonary and systemic circulatory systems and obviously only one such combination would be the optimum for any particular user, such design considerations are of extreme importance. FIG. 2 illustrates another embodiment of the present invention in which there is a single fluid oscillator system 16 that may comprise a pair of fluid oscillators that are coupled in some fashion to interrelate their frequencies and phase to provide a more tightly controlled system which may be desirable in some cases. FIG. 2 is essentially the same system as FIG. 1 with the exception of the interdependence of the fluid oscillators.
FIG. 3 illustrates at 60 a typical fluid oscillator that may be utilized in the embodiment depicted in FIG. 1. Oscillator 60 is comprised of an input 62, a resistance path 70, a capacitance chamber 68, a flexible diaphragm 66, a resistance conduit 74, an interaction region 72, and an outlet 64. In normal operation, fluid will enter input 62 and be biased by interaction region 72 to flow through resistance conduit 70. The fluid will come to rest in capacitance chamber 68. As chamber 68 is filling with fluid, diaphragm 66 will flex outwardly to accommodate a larger portion of fluid. When a certain predetermined volume of fluid is attained in capacitance chamber 68, diaphragm 66 will flex inwardly forcing the fluid in chamber 68 to exit along resistance conduit 74. The fluid exiting along resistance conduit 74 will impact with the stream entering input 62 and deflect said stream to output conduit 64 in the well knowm manner. The frequency of oscillation of oscillator 60 is dependent upon the rate of flow of fluid into the oscillator, the resistance of conduits and 74, and the spring constant of the flexible diaphragm 66 which can obviously be varied for each patients needs. It is understood that in adapting oscillator 60 to the system of FIG. 1, inlet 54 that receives blood from the lungs would be connected to input 62 and output 64 would be connected to conduit 26 that delivers the pulsed flow of blood to pump 12. A similar arrangement would exist for fluid oscillator 52. Individualized design of oscillator 60 to be adapted to fluid oscillators 50 and 52 presents distinct advantages in providing slight alterations between the frequency and phase of the dual circulatory system.
FIG. 4 represents my unique dual fluid oscillator that was first disclosed in my US. Pat. No. 3,599,244. The two back-to-back RCR fluid oscillators 10 and 40 are intended for use in the system depicted in FIG. 2. The oscillators are interdependent by means of the common diaphragm 92 encased in an inclosed chamber 99. Fluid oscillators l0 and 40 each basically operate in a manner similar to the fluid oscillator 60 of FIG. 3. Chamber 99 defines the two capacitance chambers 98 and 100 that are separated by diaphragm 92. In operation, consider the fluid to be entering oscillator 40 through input 82. The flow is initially biased to exit along conduit and fill capacitance chamber 100. The initial emptiness of capacitance chamber implies that capacitance chamber 98 of oscillator 10 is nearly full and diaphragm 92 is bulging to the right. As chamber 100 becomes filled with fluid, diaphragm 92 moves from the right to the left. The increased pressure on diaphragm 92 from the fluid in chamber 100 will help to force the fluid in nearly full chamber 98 to exit through resistance conduit 96 which acts as a control jet for fluid subsequently entering conduit 80. The control jet issuing from conduit 96 will impinge upon the fluid entering conduit 80 and divert it to conduit 86 to exit the system. In actuality, with reference to FIG. 2, conduit 80 will receive oxygen-rich blood from the lungs from conduit 24 and will deliver this blood in a pulsed fashion from conduit 86 to conduit of FIG. 2 to pump 12. This emptying action of capacitance chamber 98 continues until chamber 98 is nearly empty and chamber 100 is nearly full. Once diaphragm 92 is fully expanded to the left of chamber 99 no force will be exerted on the fluid remaining in chamber 98 and thus the control jet will cease to issue from conduit 96. Part of the fluid'entering conduit 80 will then reattach to resistance conduit 88 and begin to fill chamber 98 once more. As chamber 98 fills with fluid, diaphragm 92 will move to the right in chamber 99 and exert pressure on the fluid in nearly filled tank 100 forcing the fluid to exit through resistance conduit 94 which now acts as a control jet to impinge upon the main stream of fluid entering conduit 82. Again referring to FIG. 2, it is immediately apparent that conduit 82 is connected to conduit 22 that receives deoxygenated blood from the body and conduit 84 sends this deoxygenated blood out conduit 18 to pump 14. The stream of blood entering conduit 82 will thus be deflected and attached to conduit 84. Once the fluid has been nearly emptied from chamber 100 and diaphragm 92 is fully expanded to the right, the control jet from conduit 94 will slow to a trickle and eventually cease. Part of the blood subsequently entering conduit 82 will reattach along conduit 90 and the above cycle will repeat itself. The foregoing description encompasses one cycle in the operation of this embodiment of the artificial heart; i.e. one pulse has issued from each oscillator to each pump. The duration of a single cycle is controlled in part by the dimensions of the resistance conduits and the capacitance chambers which can be varied for each patient's needs. It is apparent that the outputs from conduits 84 and 86 are approximately 180 degrees out of phase with one another.
FIG. 5 illustrates another possible configuration of two fluid oscillators 130 and 140 which are arranged so that their outputs from conduits 104 and 132, respectively, are approximately in phase. This occurs by virtue of the weak coupling between oscillators 130 and 140 accomplished by means of conduits 118 and 120. In basic operation, oscillators 130 and 140 are identical to oscillator 60 of FIG. 3, each having an input conduit 102 and 116, a resistance conduit 106 and 124, a capacitance chamber 110 and 126, a flexible diaphragm 114 and 128, a resistance conduit 108 and 122, and an output conduit 104 and 132. In operation, we can assume that both capacitance chambers 110 and 126 are nearly filled with fluid and thus diaphragms 114 and 128 are flexed to the right. When the diaphragms reach their elastic limit and begin to flex to the left forcing fluid through resistance conduits 108 and 122, the streams of fluid entering conduits 102 and 116 will be deflected through output conduits 104 and 134, respectively. As this action commences, a small portion of the fluid exiting along conduit 134 will enter feedback conduit 118 that leads to chamber 1 12. Feedback conduit 118 is a high resistance (small diameter) conduit that provides weak coupling between the two oscillators. The larger portion of fluid flowing through conduit 134 exits through output conduit 132 that will lead to a fluid pump as depicted in FIG. 2. The partial filling of chamber 112 by fluid from feedback conduit 118 will reinforce the emptying action of diaphragm 114 by exerting pressure on its right side. When capacitance chamber 110 is nearly empty, the fluid exiting along with resistance conduit 108 will cease and fluid entering input conduit 102 will reattach to resistance conduit 106 and begin to fill capacitance chamber once again forcing diaphragm 1 14 to the right. This will cause any fluid that has gathered in chamber 112 to exit along feedback conduit 120. This flow from conduit 120 will impinge upon the fluid entering conduit 116 and re-enforce its natural shift to resistance conduit 124 such that capacitance chamber 126 begins to fill again. It is seen by the foregoing action that fluid will fill chamber 110 and 126 at approximately the same time and will subsequently exit along conduits 104 and 132 in phase. This is but one other example of two interdependent fluid oscillators that are adaptable within the system of FIG. 2.
During the alternate pulsing of the oscillators in the system of FIG. 1 or 2, pumps 12 and 14 will run continuously at the same speed. The pumps will pump only that blood that is present at their inlet. Thus if the blood pressure increases or decreases and forces the frequency of oscillation to do likewise, the pumps would automatically adjust to the change in pulsatile flow. The entire heart can be constructed of a material that is noncorrosive, has nonoccluding surfaces, and does not damage the blood in any way.
From the foregoing it is apparent that I have provided a greatly improved artificial heart capable of assisting the natural heart by complete implantation within the body or for use as an external aid to circulation. The device heretofore described is simple and uncomplicated, relying on the dynamic flow properties of the blood for its operation. No valves or collapsible chambers are used, which makes the device less susceptible to wear and tear while ensuring further that the blood remains undamaged.
I wish it to be understood that I do not desire to be limited to the exact details of construction shown and described, for obvious modifications will occur to a person skilled in the art. For example, the positions of pumps and oscillators could be interchanged if greater compliance with the circulatory system could be attained.
1. An artificial heart comprising:
a. first means for pumping oxygenated blood from the lungs of a body to the remainder of the circulatory system of said body;
b. second means for pumping deoxygenated blood from said remainder of said circulatory system to said lungs; I 4
c. a first independent fluid oscillator for receiving oxygenated blood from said lungs and emitting said oxygenated blood in a pulsed fashion to said remainder of said circulatory system; and
d. a second independent fluid oscillator for receiving deoxygenated blood from said remainder of said circulatory system and emitting said deoxygenated blood in a pulsed fashion to said lungs;
e. said first pumping means connected in series with said first fluid oscillator and said second pumping means connected in series with said second fluid oscillator.
2. The artificial heart of claim 1, wherein each of said fluid oscillators comprises:
a. an input conduit for receiving a mainstream of blood;
b. a capacitance chamber to store the blood received from said input conduit until a certain volume therein is attained;
c. a control conduit for transmitting the blood from said capacitance chamber to deflect said mainstream of blood; and
d. an output conduit for receiving said mainstream of blood after its deflection by the blood issuing from said control conduit;
c. said mainstream of blood re-entering said input conduit upon the cessation of flow of blood through said control conduit.
3. The artificial heart of claim 2 wherein each of said fluid oscillators further comprises a flexible diaphragm adjacent to said capacitance chamber, said diaphragm expanding as blood fills said capacitance chamber, said diaphragm contracting upon the attainment of said certain volume of blood in said capacitance chamber to help force blood through said control conduit, said ex- .panding and contracting of said diaphragm tending to pumping means comprises a centrifugal pump.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3208448 *||Feb 2, 1962||Sep 28, 1965||Kenneth E Woodward||Artificial heart pump circulation system|
|US3599244 *||Nov 20, 1969||Aug 17, 1971||Donald E Wortman||Dynamic action valveless artificial heart utilizing dual fluid oscillator|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4369530 *||May 19, 1981||Jan 25, 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis and method of actuation|
|US4376312 *||May 19, 1981||Mar 15, 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis|
|US4381567 *||Sep 15, 1981||May 3, 1983||Foxcroft Associates||Hydraulically actuated total cardiac prosthesis with reversible pump and three-way ventricular valving|
|US4389737 *||Sep 15, 1981||Jun 28, 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis with three-way ventricular valving|
|US4397049 *||Sep 15, 1981||Aug 9, 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis with three-way ventricular valving|
|US4427470||Sep 1, 1981||Jan 24, 1984||University Of Utah||Vacuum molding technique for manufacturing a ventricular assist device|
|US4473423 *||Sep 16, 1983||Sep 25, 1984||University Of Utah||Artificial heart valve made by vacuum forming technique|
|US4479760 *||Dec 28, 1982||Oct 30, 1984||Baxter Travenol Laboratories, Inc.||Actuator apparatus for a prepackaged fluid processing module having pump and valve elements operable in response to applied pressures|
|US4479761 *||Dec 28, 1982||Oct 30, 1984||Baxter Travenol Laboratories, Inc.||Actuator apparatus for a prepackaged fluid processing module having pump and valve elements operable in response to externally applied pressures|
|US4479762 *||Dec 28, 1982||Oct 30, 1984||Baxter Travenol Laboratories, Inc.||Prepackaged fluid processing module having pump and valve elements operable in response to applied pressures|
|US4662355 *||Aug 6, 1984||May 5, 1987||Alain Pieronne||Pump regulation device|
|US4838889 *||Jul 23, 1986||Jun 13, 1989||University Of Utah Research Foundation||Ventricular assist device and method of manufacture|
|US5109832 *||Dec 7, 1990||May 5, 1992||Proctor Richard D J||Method of and apparatus for producing alternating pressure in a therapeutic device|
|US6527698||Oct 12, 2000||Mar 4, 2003||Abiomed, Inc.||Active left-right flow control in a two chamber cardiac prosthesis|
|US6540658||Oct 12, 2000||Apr 1, 2003||Abiomed, Inc.||Left-right flow control algorithm in a two chamber cardiac prosthesis|
|US20100043718 *||Aug 22, 2008||Feb 25, 2010||Chi-Der Chen||Submerged motor for aquarium|
|U.S. Classification||623/3.13, 417/350, 137/826, 128/899, 623/3.16, 128/DIG.100, 128/DIG.300|
|International Classification||A61M1/12, A61M1/10|
|Cooperative Classification||Y10S128/10, A61M1/101, A61M2001/1005, Y10S128/03, A61M1/12|