US3641591A - Soft shell mushroom shaped heart - Google Patents
Soft shell mushroom shaped heart Download PDFInfo
- Publication number
- US3641591A US3641591A US9307A US3641591DA US3641591A US 3641591 A US3641591 A US 3641591A US 9307 A US9307 A US 9307A US 3641591D A US3641591D A US 3641591DA US 3641591 A US3641591 A US 3641591A
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- Prior art keywords
- blood
- pumping
- heart
- pumping chamber
- valve head
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- Expired - Lifetime
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Classifications
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- 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
- A61M60/89—Valves
- A61M60/898—Valves the blood pump being a membrane blood pump and the membrane acting as inlet valve
-
- 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
- A61M60/196—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body replacing the entire heart, e.g. total artificial hearts [TAH]
-
- 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
- A61M60/40—Details relating to driving
- A61M60/424—Details relating to driving for positive displacement blood pumps
- A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
-
- 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
- A61M60/89—Valves
- A61M60/892—Active valves, i.e. actuated by an external force
-
- 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
- A61M60/89—Valves
- A61M60/894—Passive valves, i.e. valves actuated by the blood
-
- 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
- A61M60/20—Type thereof
- A61M60/247—Positive displacement blood pumps
- A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
- A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
Definitions
- the external configuration is usually grossly dissimilar to that of a natural heart. They are also generally constructed of a rigid material which causes considerable damage to surrounding tissue when the artificial heart is placed in the same general vicinity as that usually occupied by a natural heart.
- the blood pumping chamber is defined as the area between a flexible external wall of the artificial heart and an inflatable pumping member inside the heart. Blood is forced from the pumping chamber by the inflation of the pumping member. The direction of flow of the blood is appropriately controlled by valves in inlet and outlet conduits.
- the inlet valve to the pumping chamber is formed as an integral part of the pumping member thus giving rise to the name "Mushroom Heart” since the valve comprises the head or button of the mushroom and the pumping member is the stem.
- the inlet blocking member or valve head acts in a manner similar to a ball valve since the valve head is formed as an extension of the pumping member and is comprised of an inflatable membrane having a surface which contacts the periphery of the inlet opening to the pumping chamber to occlude the inlet when the valve is inflated. Inflation of the valve is accomplished either simultaneously with the inflation of the pumping member or separately as desired to achieve optimal pumping efficiency.
- the flexible external wall is restrained from flexing beyond certain limits by a nonelastic but flexible restraining surface such as a netting material either incorporated into the external wall or located exteriorily thereto.
- a nonelastic but flexible restraining surface such as a netting material either incorporated into the external wall or located exteriorily thereto.
- FIG. I is a cross-sectional schematic of the soft shell mushroom heart during the inlet phase of blood into the pumping chamber of the artificial heart;
- FIG. 2 is a cross-sectional schematic of the soft shell mushroom heart during the pumping phase
- FIGS. 3A, 3B, 3C, and 30 are cross-sectional schematic views of one modification of the soft shell mushroom heart during different stages of the pumping cycle.
- the artificial heart as shown in schematic comprises a blood pumping chamber I0 enclosed within a flexible, and (to a limited extent) elastic, external wall II which is restrained from distending beyond certain limits by a nonelastic, flexible net I2.
- Pumping member 13 is periodically inflated by a working fluid, which in the presently preferred embodiment is air.
- a valve head 14 is formed as an integral part of pumping member 13.
- blood enters the pumping chamber I0 through an opening between a valve seat 15 and valve head 14.
- the volume of pumping chamber 10 is responsive to the atrial filling pressure in response to Starlings Law. Flexibility of external wall 11 of pumping chamber 10 allows blood to flow into the pumping chamber 10 of the heart from the atrial filling chamber without undue negative pressure being exerted upon the blood when the working fluid or air is withdrawn from pumping member 13.
- a valve 16 prevents the reverse flow of blood from the arterial system during the filling phase of the artificial heart.
- the artificial heart is shown in schematic during the pumping stage in which air is forced into pumping member 13 and simultaneously forces valve head I4 against valve seat 15.
- the inlet to the pumping chamber is thus closed and the back flow of blood through the inlet is prevented.
- Blood is pumped out of pumping chamber I0 through valve 16 as shown by solid arrows in the diagram.
- the flexible net 12 lies closely adjacent the external wall 11 and prevents the further distention of the latter beyond certain limits when the pumping member 13 is inflated. Even when the atrial filling pressure is insufficient to completely fill the pumping chamber 10, the pumping member 13 is still inflated to its full extent and forces external wall 11 against net 12. The only change resulting from a partial filling of the pumping chamber 10 is a reduction in the output volume of the artificial heart.
- valve head 14 and pumping member 13 are inflated simultaneously.
- that material comprising the elastic portions of valve head 14 be constructed of a material which stretches under less pressure than the material comprising the pumping member 13. In this manner, the more elastic material of valve 14 would preferentially distend to cause valve head 14 to occlude the blood inlet before pumping member 13 starts to distend.
- FIGS. 3A-3D another embodiment of an artificial heart is shown in four stages of pumping.
- the stages of filled pumping chamber, closed inlet valve, inflated pumping member, and deflated pumping member and valve are shown in FIGS. 3A, 3B, 3C, and 3D, respectively.
- valve head 14 is shown in a relaxed state and enveloping a support member 17. Blood is free to flow under normal atrial filling pressure between valve head 14 and valve seat 15 into pumping chamber 10.
- the support member 17 is in turn supported by an inflation conduit 18 that passes interiorily through the pumping member 13.
- the inflation medium for valve head 14 passes through inflation conduit 18 and into the confines of valve 14 through passageways or holes 19 in the support member 17. In this particular embodiment there is no communication of the valve inflation medium with the interior of pumping member 13.
- the inflation control system for the valve head 14 operates separately from the inflation control system for pumping member 13. However, it is envisioned that the same inflation medium for valve head 14 could also be used to inflate pumping member 13 after a suitable delay in passage from valve head l4 into pumping member 13. The delay in passage of the inflation medium would create the necessary sequencing between inlet valve closure and pumping member 13 inflation for optimal pumping efl'iciency. In either manner, it is possible to achieve the sequential inflation of the valve and pumping member for the optimal pumping efficiency of the artificial heart.
- valve head 14 is shown in its fully inflated state wherein it contacts the valve seat 15 to occlude the blood inlet into the pumping chamber.
- Base 21 serves as an attachment point between inflation member 13 and external wall 11 and as a means for segregating the inflation medium of valve head 14 and pumping member l3 from the area immediately surrounding the artificial heart.
- Inflation medium for pumping member [3 passes through conduit which serves both as an inflation port and as a deflation'port through base 21.
- the inflation medium is either returned to a control device (not shown) located either interiorly or exteriorily of the body, or in the case of air, allowed to escape to the atmosphere.
- pumping member 13 is shown in its fully inflated state wherein it almost completely fills pumping chamber 10 and thus expels almost all the blood from pumping chamber 10 through valve 16.
- valve head 14 and pumping member [3 are depicted in their deflated states to allow for the filling of pumping chamber 10.
- External wall 11 is drawn inwardly by the negative pressure created by the deflation of pumping member 13.
- Blood enters pumping chamber 10 under the force of the atrial filling pressure through the opening between valve head 14 and valve seat 15. The quantity of blood in pumping chamber 10 will thus depend upon the atrial filling pressure of the blood and in this manner make the artificial heart of this invention highly responsive to Starling: Law.
- Valve [6 in all drawings may be any one of a number of appropriate valves used in blood flow systems.
- a single pumping chamber may be used in heart bypass operations to replace or asist the pumping function of a ventrical of the natural heart for any period of time required for healing of the diseased natural heart.
- a blood pumping device to replace or temporarily assist the natural heart comprising:
- an inflatable blood displacement member of elastic wall construction located within said pumping chamber and operable upon periodic inflation to forcibly eject blood from said pumping chamber through said outlet means, an inflatable valve head for periodically blocking said inlet means, said valve head being affixed to said dis lacement member and operable as a valvmg means, sa valve head including means for operating said valve head separately from said inflation of said inflatable blood displacement member to thereby achieve optimum pumping efficiency of said blood pumping device.
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- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Cardiology (AREA)
- Biomedical Technology (AREA)
- Anesthesiology (AREA)
- Mechanical Engineering (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- External Artificial Organs (AREA)
- Prostheses (AREA)
Abstract
The output volume of the artificial heart of this invention is highly responsive and directly proportional, within limits, to the atrial filling pressure of the blood flowing into the pumping chamber of the artificial heart. Flexible wall construction is responsible for the output volume being a function of the inlet pressure and also serves to reduce tissue damage to the surrounding body organs when the artificial heart is placed in the same general locality as that usually occupied by the natural heart. An integral valve means operable in conjunction with an inflatable blood displacement member occludes the inlet to the heart during the pumping phase of the heart.
Description
United States Patent Kolff Feb. 15, 1972 [$4] SOFT SHELL MUSHROOM SHAPED FOREIGN PATEN'I'SORAPHJCA'IIONS HEART 1,538,644 7/l968 France .JIDIG. 2 [72] Inventor: Willem .I. Kolfl, Salt Lake City, Utah Primary Examiner-Dalton L. Truluck [73, Amsnee' Unlnnuy UM Attorney-Clarence W. Martin [22] Filed: Feb. 6, I970 (21] Appl. No.: 9,307 AISIIACT The output volume of the artificial heart of this invention is [52] use. ..3/1, l28/l R a y mpqnflve and directly w 5 Int gum/14 theatrial filling pressure ofthebloodflovnng mtothepunpin; '[58] FieldolSearch ..l28ll R,2l4, DIG. 3;3/l, chamber ofthe artificial heart. Flexible \vall oomtruetion SIDlG. 2 responsible for the output volume being a function of the inlet pressureandalsoservestoreducetiluedamqetotheaut- 1 Mm CM rounding body organs when u artificial heart it placed in m samegenerallocalityathatumallyoocupiedbythemunl UNITED STATES PATENTS heart. An integral valve means operable in conjunction with 3,504,662 4/ I970 Jones I 28/1 R an inflatablg blood digplaccment member occlude: the ink! to 9 8/1962 NOflOnM the heart during the pumping phase ofthe heat. 3,491,377 l/l970 Bolie 3,518,702 7/l970 LaRussa ..3/l 4Chlm60rawlngflpru PATENTEUFEH 15 m2 SHEET 1 OF 2 INVENTOR. WILLEM J1 KOLFF AGENT 'mzmsnreewswn 3.641.591
Further restrictions to the usefulness of prior modifications of an artificial heart are in the external design and materials of construction. The external configuration is usually grossly dissimilar to that of a natural heart. They are also generally constructed of a rigid material which causes considerable damage to surrounding tissue when the artificial heart is placed in the same general vicinity as that usually occupied by a natural heart.
In the present embodiment of the natural heart, the blood pumping chamber is defined as the area between a flexible external wall of the artificial heart and an inflatable pumping member inside the heart. Blood is forced from the pumping chamber by the inflation of the pumping member. The direction of flow of the blood is appropriately controlled by valves in inlet and outlet conduits. The inlet valve to the pumping chamber is formed as an integral part of the pumping member thus giving rise to the name "Mushroom Heart" since the valve comprises the head or button of the mushroom and the pumping member is the stem. The inlet blocking member or valve head acts in a manner similar to a ball valve since the valve head is formed as an extension of the pumping member and is comprised of an inflatable membrane having a surface which contacts the periphery of the inlet opening to the pumping chamber to occlude the inlet when the valve is inflated. Inflation of the valve is accomplished either simultaneously with the inflation of the pumping member or separately as desired to achieve optimal pumping efficiency.
The flexible external wall is restrained from flexing beyond certain limits by a nonelastic but flexible restraining surface such as a netting material either incorporated into the external wall or located exteriorily thereto. In circumstances where the restaining surface hinders the necessary flexibility of the external wall, it is suggested that the two surfaces not be joined but operate independently of each other.
Therefore, it is an object of this invention to provide an artificial heart which is similar in size and external shape to a natural heart.
It is a further object of this invention to provide an artificial heart of flexible external construction.
It is a still further object of this invention to provide an artificial heart which is responsive in its pumping output to the filling pressure of the artificial heart.
It is a still further object of this invention to provide an artificial heart with an integral valve means closely connected with the pumping member to provide a means for occluding the inlet to the heart pumping chamber during the pumping phase for the prevention of the reverse flow of blood.
These and other objects of this invention will become obvious when viewed in conjunction with the following description and drawings in which:
FIG. I is a cross-sectional schematic of the soft shell mushroom heart during the inlet phase of blood into the pumping chamber of the artificial heart;
FIG. 2 is a cross-sectional schematic of the soft shell mushroom heart during the pumping phase; and
FIGS. 3A, 3B, 3C, and 30 are cross-sectional schematic views of one modification of the soft shell mushroom heart during different stages of the pumping cycle.
Referring to FIG. I, the artificial heart as shown in schematic comprises a blood pumping chamber I0 enclosed within a flexible, and (to a limited extent) elastic, external wall II which is restrained from distending beyond certain limits by a nonelastic, flexible net I2. Pumping member 13 is periodically inflated by a working fluid, which in the presently preferred embodiment is air. A valve head 14 is formed as an integral part of pumping member 13. As indicated by dashed arrows in the drawings, blood enters the pumping chamber I0 through an opening between a valve seat 15 and valve head 14. As indicated by the collapsed state of the external wall 11, the volume of pumping chamber 10 is responsive to the atrial filling pressure in response to Starlings Law. Flexibility of external wall 11 of pumping chamber 10 allows blood to flow into the pumping chamber 10 of the heart from the atrial filling chamber without undue negative pressure being exerted upon the blood when the working fluid or air is withdrawn from pumping member 13.
A valve 16 prevents the reverse flow of blood from the arterial system during the filling phase of the artificial heart.
Referring to FIG. 2, the artificial heart is shown in schematic during the pumping stage in which air is forced into pumping member 13 and simultaneously forces valve head I4 against valve seat 15. The inlet to the pumping chamber is thus closed and the back flow of blood through the inlet is prevented. Blood is pumped out of pumping chamber I0 through valve 16 as shown by solid arrows in the diagram. The flexible net 12 lies closely adjacent the external wall 11 and prevents the further distention of the latter beyond certain limits when the pumping member 13 is inflated. Even when the atrial filling pressure is insufficient to completely fill the pumping chamber 10, the pumping member 13 is still inflated to its full extent and forces external wall 11 against net 12. The only change resulting from a partial filling of the pumping chamber 10 is a reduction in the output volume of the artificial heart.
As illustrated in the drawing, valve head 14 and pumping member 13 are inflated simultaneously. However, this could result in a reverse flow of some of the blood from the pumping chamber 10 at the onset of inflation of pumping member 13. Therefore it is suggested that that material comprising the elastic portions of valve head 14 be constructed of a material which stretches under less pressure than the material comprising the pumping member 13. In this manner, the more elastic material of valve 14 would preferentially distend to cause valve head 14 to occlude the blood inlet before pumping member 13 starts to distend.
Referring to FIGS. 3A-3D, another embodiment of an artificial heart is shown in four stages of pumping. The stages of filled pumping chamber, closed inlet valve, inflated pumping member, and deflated pumping member and valve are shown in FIGS. 3A, 3B, 3C, and 3D, respectively.
Referring to FIG. 3A, the elastic material of valve head 14 is shown in a relaxed state and enveloping a support member 17. Blood is free to flow under normal atrial filling pressure between valve head 14 and valve seat 15 into pumping chamber 10. The support member 17 is in turn supported by an inflation conduit 18 that passes interiorily through the pumping member 13. The inflation medium for valve head 14 passes through inflation conduit 18 and into the confines of valve 14 through passageways or holes 19 in the support member 17. In this particular embodiment there is no communication of the valve inflation medium with the interior of pumping member 13.
The inflation control system for the valve head 14 operates separately from the inflation control system for pumping member 13. However, it is envisioned that the same inflation medium for valve head 14 could also be used to inflate pumping member 13 after a suitable delay in passage from valve head l4 into pumping member 13. The delay in passage of the inflation medium would create the necessary sequencing between inlet valve closure and pumping member 13 inflation for optimal pumping efl'iciency. In either manner, it is possible to achieve the sequential inflation of the valve and pumping member for the optimal pumping efficiency of the artificial heart.
Referring to FIG. 3B, the valve head 14 is shown in its fully inflated state wherein it contacts the valve seat 15 to occlude the blood inlet into the pumping chamber.
Referring to FIG. 3C, pumping member 13 is shown in its fully inflated state wherein it almost completely fills pumping chamber 10 and thus expels almost all the blood from pumping chamber 10 through valve 16.
Referring to FIG. 3D, both valve head 14 and pumping member [3 are depicted in their deflated states to allow for the filling of pumping chamber 10. External wall 11 is drawn inwardly by the negative pressure created by the deflation of pumping member 13. Blood enters pumping chamber 10 under the force of the atrial filling pressure through the opening between valve head 14 and valve seat 15. The quantity of blood in pumping chamber 10 will thus depend upon the atrial filling pressure of the blood and in this manner make the artificial heart of this invention highly responsive to Starling: Law.
Valve [6 in all drawings may be any one of a number of appropriate valves used in blood flow systems.
Although only one pumping chamber has been depicted in the drawings and accompanying description, a complete artificial heart would comprise two such chambers which would serve to completely replace and duplicate the functions of the natural heart.
A single pumping chamber may be used in heart bypass operations to replace or asist the pumping function of a ventrical of the natural heart for any period of time required for healing of the diseased natural heart.
All materials of construction in contact with blood and living tissue are compatible with and noninjurious to the blood and living tissue.
lclaim:
l. A blood pumping device to replace or temporarily assist the natural heart, said device comprising:
a. a blood pumping chamber of flexible wall construction,
and having separate blood inlet and outlet means; and an inflatable blood displacement member of elastic wall construction located within said pumping chamber and operable upon periodic inflation to forcibly eject blood from said pumping chamber through said outlet means, an inflatable valve head for periodically blocking said inlet means, said valve head being affixed to said dis lacement member and operable as a valvmg means, sa valve head including means for operating said valve head separately from said inflation of said inflatable blood displacement member to thereby achieve optimum pumping efficiency of said blood pumping device.
2. A blood pumping device as defined in claim I wherein the external configuration of the pumping device conforms substantially to that of a natural human heart.
3. A blood pumping device as defined in claim I wherein said flexible wall construction of the pumping chamber is restrained from expansion beyond predetermined limits by a UNITED STATES PATENT OFFICE CERTIFICATE OF CORRECTION Patent No. 3,6u1,591 f D t February 15. 1972 Inventor( Willem J. Kolff It is certified that error appears in the aboveidentified patent and that said Letters Patent are hereby corrected as shown below:
Signed and sealed this '7th day of November 1972.
(SEAL) Attest:
EDWARD M.FLETCHER,JR. ROILER'I GOTTSCHALK Attesting Officer Commissioner of Patents FORM PO-1050 (10-69) USCOMM-DC wave-ps9 0 U.S. GOVERNMENT PRINTING OFFICE: 09! O-S 6-!!A
Claims (4)
1. A blood pumping device to replace or temporarily assist the natural heart, said device comprising: a. a blood pumping chamber of flexible wall construction, and having separate blood inlet and outlet means; and b. an inflatable blood displacement member of elastic wall construction located within said pumping chamber and operable upon periodic inflation to forcibly eject blood from said pumping chamber through said outlet means, an inflatable valve head for periodically blocking said inlet means, said valve head being affixed to said displacement member and operable as a valving means, said valve head including means for operating said valve head separately from said inflation of said inflatable blood displacement member to thereby achieve optimum pumping efficiency of said blood pumping device.
2. A blood pumping device as defined in claim 1 wherein the external configuration of the pumping device conforms substantially to that of a natural human heart.
3. A blood pumping device as defined in claim 1 wherein said flexible wall construction of the pumping chamber is restrained from expansion beyond predetermined limits by a nonelastic but flexible restraining surface.
4. A blood pumping device as defined in claim 3 wherein the elastic wall construction of the pumping member is operable to completely distend the elastic walls of the pumping chamber to the restraining limits of the restraining surface even in the presence of a differential amounts of blood in the blood pumping chamber at any given time.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
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US930770A | 1970-02-06 | 1970-02-06 |
Publications (1)
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US3641591A true US3641591A (en) | 1972-02-15 |
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ID=21736851
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US9307A Expired - Lifetime US3641591A (en) | 1970-02-06 | 1970-02-06 | Soft shell mushroom shaped heart |
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US (1) | US3641591A (en) |
Cited By (15)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3827426A (en) * | 1971-07-16 | 1974-08-06 | P Sawyer | Prosthetic pump |
US4177523A (en) * | 1978-03-15 | 1979-12-11 | Lande Arnold J | Artificial heart |
US4369530A (en) * | 1981-05-19 | 1983-01-25 | Foxcroft Associates | Hydraulically actuated cardiac prosthesis and method of actuation |
US4376312A (en) * | 1981-05-19 | 1983-03-15 | Foxcroft Associates | Hydraulically actuated cardiac prosthesis |
US4381567A (en) * | 1981-09-15 | 1983-05-03 | Foxcroft Associates | Hydraulically actuated total cardiac prosthesis with reversible pump and three-way ventricular valving |
US4389737A (en) * | 1981-09-15 | 1983-06-28 | Foxcroft Associates | Hydraulically actuated cardiac prosthesis with three-way ventricular valving |
US4397049A (en) * | 1981-09-15 | 1983-08-09 | Foxcroft Associates | Hydraulically actuated cardiac prosthesis with three-way ventricular valving |
FR2603487A1 (en) * | 1986-09-09 | 1988-03-11 | Biomasys Sa | COUPLABLE HEART RATE MODULES |
US4938766A (en) * | 1987-08-28 | 1990-07-03 | Jarvik Robert K | Prosthetic compliance devices |
US4994078A (en) * | 1988-02-17 | 1991-02-19 | Jarvik Robert K | Intraventricular artificial hearts and methods of their surgical implantation and use |
US5092879A (en) * | 1988-02-17 | 1992-03-03 | Jarvik Robert K | Intraventricular artificial hearts and methods of their surgical implantation and use |
US6629950B1 (en) * | 1998-02-04 | 2003-10-07 | John M. Levin | Fluid delivery system |
US20090270981A1 (en) * | 2008-04-23 | 2009-10-29 | Syncardia Systems, Inc. | Apparatus and method for pneumatically driving an implantable medical device |
WO2011004400A1 (en) * | 2009-07-10 | 2011-01-13 | Sujoy Kumar Guha | Replaceable artificial heart implantable by keyhole surgery |
GB2483422A (en) * | 2009-07-10 | 2012-03-07 | Sujoy Kumar Guha | Replaceable artificial-heart implantable by keyhole surgery |
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US3048165A (en) * | 1959-04-17 | 1962-08-07 | Thompson Ramo Wooldridge Inc | Pump for an artificial heart |
FR1538644A (en) * | 1967-07-28 | 1968-09-06 | Rhone Poulenc Sa | Heart prosthesis |
US3491377A (en) * | 1967-12-20 | 1970-01-27 | Advanced Technology Corp | Self-triggering standby ventricle for heart assist |
US3504662A (en) * | 1967-05-16 | 1970-04-07 | Avco Corp | Intra-arterial blood pump |
US3518702A (en) * | 1967-01-23 | 1970-07-07 | Farrand Optical Co Inc | Implantable body actuated artificial heart system |
-
1970
- 1970-02-06 US US9307A patent/US3641591A/en not_active Expired - Lifetime
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3048165A (en) * | 1959-04-17 | 1962-08-07 | Thompson Ramo Wooldridge Inc | Pump for an artificial heart |
US3518702A (en) * | 1967-01-23 | 1970-07-07 | Farrand Optical Co Inc | Implantable body actuated artificial heart system |
US3504662A (en) * | 1967-05-16 | 1970-04-07 | Avco Corp | Intra-arterial blood pump |
FR1538644A (en) * | 1967-07-28 | 1968-09-06 | Rhone Poulenc Sa | Heart prosthesis |
US3491377A (en) * | 1967-12-20 | 1970-01-27 | Advanced Technology Corp | Self-triggering standby ventricle for heart assist |
Cited By (18)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3827426A (en) * | 1971-07-16 | 1974-08-06 | P Sawyer | Prosthetic pump |
US4177523A (en) * | 1978-03-15 | 1979-12-11 | Lande Arnold J | Artificial heart |
US4369530A (en) * | 1981-05-19 | 1983-01-25 | Foxcroft Associates | Hydraulically actuated cardiac prosthesis and method of actuation |
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US20090270981A1 (en) * | 2008-04-23 | 2009-10-29 | Syncardia Systems, Inc. | Apparatus and method for pneumatically driving an implantable medical device |
US7811318B2 (en) | 2008-04-23 | 2010-10-12 | Syncardia Systems, Inc. | Apparatus and method for pneumatically driving an implantable medical device |
WO2011004400A1 (en) * | 2009-07-10 | 2011-01-13 | Sujoy Kumar Guha | Replaceable artificial heart implantable by keyhole surgery |
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