US3692018A - Cardiac assistance device - Google Patents
Cardiac assistance device Download PDFInfo
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- US3692018A US3692018A US10452A US3692018DA US3692018A US 3692018 A US3692018 A US 3692018A US 10452 A US10452 A US 10452A US 3692018D A US3692018D A US 3692018DA US 3692018 A US3692018 A US 3692018A
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- blood
- occluding
- chamber
- pumping
- assistance device
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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
- A61M60/894—Passive valves, i.e. valves actuated by the blood
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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
- A61M60/10—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
- A61M60/135—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 inside a blood vessel, e.g. using grafting
- A61M60/139—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 inside a blood vessel, e.g. using grafting inside the aorta, e.g. intra-aortic balloon pumps
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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
- A61M60/20—Type thereof
- A61M60/295—Balloon pumps for circulatory assistance
-
- 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
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M2025/1043—Balloon catheters with special features or adapted for special applications
- A61M2025/1052—Balloon catheters with special features or adapted for special applications for temporarily occluding a vessel for isolating a sector
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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
- A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
- A61M60/833—Occluders for preventing backflow
-
- 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
- A61M60/857—Implantable blood tubes
Definitions
- ABSTRACT Truluck Attorney-Pennie, Edmonds, Morton, Taylor and Adams [5 7 ABSTRACT A cardiac assistance device is disclosed which produces a uni-directional pumping action assisting the heart when the device is activated after it has been introduced into a blood vessel by conventional surgical procedures.
- Heart failure is medically defined, in its broadest sense, as the inability of the heart to pump blood throughout the body.
- a failing heart is defined as one that is not sufficiently healthy to pump blood at the rate needed to maintain adequate blood flow and continued well-being of its owner but which is nevertheless, capable of pumping some blood.
- a cardiac assistance device is one that aids a failing heart.
- One presently known device .used for this purpose comprises a single inflatable balloon which is adapted to be inserted into an appropriate blood vessel, as for example, the aorta. When such a device is inflated and deflated, a pumpingaction within theblood vessel occurs and when the inflation and deflation cycle is appropriately timed to the heartbeat, the device acts to assist the failing heart.
- a cardiac assistance device which is constructed to create an artificially induced unidirectional pumping action, within a blood vessel of the patient to aid the failing heart.
- the device includes an inflatable occluding chamber and one or more inflatable pumping chambers disposed on one side of the occluding chamber in communicating relationship therewith.
- the occluding and pumping chambers are adapted to be inserted into the blood vessel of the patient and both are inflated and deflated on a cyclical basis out of phase with the beat of the failing heart but sequentially with respect to each other by a pneumatic power source positioned externally of the patient.
- the occluding chamber has a diameter greater than the diameter of the blood vessel within which it lies so that when inflated it occludes the blood vessel. Since the occluding chamber is inflated before the pumping chamber, the pressure created in the blood vessel when the pumping chamber is later inflated causes the blood to flow in a single direction away from point of occlusion between the inflated occluding chamber and the wall of the blood vessel.
- the cardiac assistance device of the present invention acts as a uni-directional pump and when properly positioned the direction of blood flow created by the device can be effectively controlled according to the dictates of sound medical practice to be most beneficial to the patient.
- FIG. 1 is a cross-sectional view of the cardiac assistance device of this invention disposed within a blood vessel.
- FIG. 2 is a cross-sectional view of the cardiac assistance device of this invention disposed within a blood vessel showing an alternative embodiment of the structure within the occluding chamber.
- FIGS. 3 and 4 are elevation views of the cardiac assistance device of this invention showing progressive stages of the operation of the device.
- FIG. 5 is a diagrammatic illustration of a human heart showing the placement of thecardiac assistance device within the aorta.
- the cardiac assistance device includes a pumping structure indicated generally by reference numeral 10 which is adapted to be inserted within a blood vessel 2 of the patient by conventional surgical procedures.
- the pumping structure is specially constructed to produce auni-directional flow of blood within the blood vessel.
- the pumping structure operates to first occlude the blood vessel and then to create pressure within the blood vessel on one side of the point of occlusion to thereby cause the blood within the vessel to flow in one direction away from the point of occlusion.
- the pumping structure includes expansion means for internally occluding the blood vessel and blood moving means positioned on one side of the expansion means for displacing blood onthat side of the expansion means.
- the expansion means comprises an inflatable occluding chamber 3 and the blood moving means comprises one or more inflatable pumping chambers 4 which communicate in series with the occluding chamber.
- the occluding chamber 3 and the pumping chamber 4 are defined by a balloon structure which consists of a balloon member 5 mounted on a tubular conduit 6 extending longitudinally through the balloon member 5.
- Each end of the balloon is disposed in fluidgas tight relationship about the tubular conduit by suitable sealing means as for example, silk threads 7 tied tightly about the terminal ends of the balloon member.
- suitable sealing means as for example, silk threads 7 tied tightly about the terminal ends of the balloon member.
- an intermediate portion of the balloon member 5 is held against expansion in fluid-gas tight relationship to the tubular conduit 6 by silk threads 7' similar to the ones used for sealing each end of the balloon member.
- a metallic pellet 13 seals the end of the tubular conduit at a point located near the end of the pumping chamber 4 remote from the occluding chamber.
- the use of a metallic pellet for this pur pose advantageously permits the position of the pumping structure within the blood vessel to be visually monitored by the use of standard X-ray techniques after it has been introduced into the patient.
- the balloon member 5 and the tubular conduit are made of nonthrombogenic material so that the danger of blood clotting is eliminated.
- the silk sealing threads are coated with a nonthrombogenic material and the assembled pumping structure is dipped into a bath of molten nonthrombogenic material.
- An example of nonthrombogenic material is polyurethane.
- the balloon member is also inelastic or nonstretchable so that the danger of fatigue failure due to stretching when the balloon member is repeatedly inflated and deflated is avoided. In other words, no stretching of the balloon member occurs when it is inflated. Rather the balloon merely expands upon inflation to its natural but relaxed inflated state.
- the tubular conduit serves a dual purpose. First, it acts to hold the pumping chamber on one side of the occluding chamber as the balloon structure is introduced into the patient thus preventing the balloon structure from folding back on itself. Secondly, the tubular conduit provides a convenient means for introducing gas or fluid into the balloon structure to inflate the occluding and pumping chambers. For the latter purpose those portions of the tubular conduit which extend through the occluding and pumping chambers are provided with a series of perforations 8 which permit air flow into and out of the occluding and pumping chambers. In the presently preferred embodiment of this invention, the tubular conduit has a diameter of approximately 2-3 millimeters and the perforations are approximately 1 millimeter in diameter.
- the occluding chamber of the balloon has a size such as when inflated the blood vessel is internally occluded.
- the blood vessel is occluded by the inflated occluding chamber in the sense that a complete occlusion of the blood vessel is produced causing stoppage of the blood stream and accumulation of the pressure within the blood vessel.
- the pumping chamber on the other hand is slightly smaller in size than the occluding chamber and when inflated the pumping chamber acts only to increase the pressure within the blood vessel. In other words, flow of blood past the inflated pumping chamber is not prevented but blood flow past the inflated occluding chamber is prevented.
- the occluding chamber is substantially spherical in shape while the single pumping chamber shown is substantially cylindrical in shape. Since the construction shown in the drawing is intended for insertion within the aorta of the patient which for the average patient has an inside diameter of approximately 18-22 millimeters, it is preferred that the spherical occluding chamber be slightly greater than 22 millimeters in diameter in its inflated state and that the pumping chamber have an inflated size of approximately 16 millimeters in diameter.
- the occluding and pumping chamber of the balloon are alternately inflated and deflated at a cycle which is out of phase with the heartbeat of the patient. That is, when the heart is relaxed, the chambers of the balloon are inflated and when the heart is pumping these chambers are deflated.
- a pneumatic power source indicated diagrammatically by reference numeral 11 in FIG. is provided.
- the pneumatic power source is of conventional construction having the capability of creating alternating positive and negative pressure as triggered by the electrocardiogram of the patient.
- the pumping machine is connected to the balloon structure via the tubular conduit 6.
- a suitable pumping machine for practicing the teachings of the present invention is the pneumatic pumping machine produced by the Datascope Company of New Jersey.
- the occluding chamber of the balloon structure is inflated prior to inflation of the pumping chamber.
- an obstruction member 9 is provided.
- the obstruction member acts to divert the flow of gas within the balloon structure in a manner which produces sequential inflation of the occluding and pumping chambers.
- the obstruction member is disposed within that portion of the tubular conduit extending through the occluding chamber 3 at a point located between two adjacent perforations 8' and 8". With this arrangement, gas supplied from the pneumatic power source is temporarily diverted from the tubular conduit into the occluding chamber through the perforations 8" disposed upstream of the obstruction member.
- the path of exit from the pumping chamber leads into the conduit 6 through the perforations disposed in the portion of the conduit 6 located within the pumping chamber and then into the occluding chamber via the perforations 8 and finally back into the tubular conduit through the perforations 8" and out of the balloon structure.
- the occluding and pumping chambers may advantageously be deflated substantially simultaneously by replacing the solid obstruction member with a oneway valve such as the ball valve 12 shown in FIG. 2.
- the ball valve is closed during the inflation cycle thereby producing the same pattern of air flow as is produced with the solid obstruction member shown in FIG. 1.
- the ball valve is opened thus permitting air to be withdrawn from the occluding and pumping chambers through all the perforations in those portions of the tubular conduit disposed within these chambers at substantially the same time.
- Simultaneous deflation of the occluding and pumping chambers is advantageous since very little time is consumed between successive beats of the heart. Thus the possibility that the pumping structure will pulsate in appropriate coordination with the heartbeat is thereby greatly enhanced.
- FIG. 5 One application for the cardiac assistance device of the present invention is sown in FIG. 5.
- the pumping structure section of the device is inserted into the femoral artery at a point below the bifurcation in the aorta and pushed upward into the aorta to the position shown.
- the device acts to direct a flow of blood toward the heart into the coronary artery which supplies blood to the heart muscles and also into the carotid arteries which supply blood to the brain. Blood pumped by the cardiac assistance device is prevented from reentering the heart chamber by the aortic valve. It will be recognized that this particular use of the device is particularly beneficial since an adequate supply of blood to these critical organs is insured.
- a cardiac assistance device comprising: a. a pump structure adapted to be inserted into a blood vessel of a patient, said blood structure having an elongated support means with an insertable end;
- the expansion means comprises an inflatable occluding chamber
- the blood moving means comprises at least one inflatable pumping chamber communicating with the occluding chamber.
- the occluding chamber and pumping chamber are troduced into the patient.
- the holding means comprises a tubular conduit extending through the balloon member, said balloon member being held in sealed relationship about said conduit at each end thereof and at said intermediate point along its length;
- the means for sequentially inflating the occluding and pumping chambers comprises means for temporarily diverting the flow of air through the tubu lar conduit into the occluding chamber prior to entrance into the pumping chamber.
- the means for diverting the flow of air through the tubular conduit comprises an obstruction member disposed within the portion of the tubular conduit extending through the occluding chamber at a point located between two adjacent perforations of said conduit portion.
Abstract
A cardiac assistance device is disclosed which produces a unidirectional pumping action assisting the heart when the device is activated after it has been introduced into a blood vessel by conventional surgical procedures.
Description
United States Patent Goetz et al.
[541 CARDIAC ASSISTANCE DEVICE [72] Inventors: Robert H. Goetz; Lionel J. Goetz, both of 80 Vernon Drive, Scarsdale, NY. 10583 22 Filed: Feb.ll,1970
21 App1.No.: 10,452
I Coronary Artery Aortic I Volve I ll 1 I l ';-i 7 l 74 :1 1 I [151 3,692,018 51 Sept. 19, 1972 3,505,987 4/l970 Heilman 128/1 R FOREIGN PATENTS OR APPLICATIONS 15,864 7/1912 France ..l28/344 OTHER PUBLICATIONS Laird et al. Trans. Amer. Soc. Artif. Int. Organs. Vol. XIV, 1968 pp. 338- 342 Primary Examiner-Dalton L. Truluck Attorney-Pennie, Edmonds, Morton, Taylor and Adams [5 7 ABSTRACT A cardiac assistance device is disclosed which produces a uni-directional pumping action assisting the heart when the device is activated after it has been introduced into a blood vessel by conventional surgical procedures.
8 Claims, 5 Drawing Figures PATENTED SEP 19 I 3 6 92.018
A cardiac assistance device is one that aids a failing heart. One presently known device .used for this purpose comprises a single inflatable balloon which is adapted to be inserted into an appropriate blood vessel, as for example, the aorta. When such a device is inflated and deflated, a pumpingaction within theblood vessel occurs and when the inflation and deflation cycle is appropriately timed to the heartbeat, the device acts to assist the failing heart.
While this type of cardiac assistance device has significantly contributed to the progress of medical science, it is inherently inefficient. This is due to the fact that the balloon acts as an omni-directional pump thus making it impossible to direct its force in a single direction so that blood is pumped only to those regions of h the body where adequate blood flow is most critical as for example, to the brain and the muscles of the heart itself.
SUMMARY OF THE INVENTION In accordance with the teachings of the present invention a cardiac assistance device is provided which is constructed to create an artificially induced unidirectional pumping action, within a blood vessel of the patient to aid the failing heart. In construction, the device includes an inflatable occluding chamber and one or more inflatable pumping chambers disposed on one side of the occluding chamber in communicating relationship therewith. The occluding and pumping chambers are adapted to be inserted into the blood vessel of the patient and both are inflated and deflated on a cyclical basis out of phase with the beat of the failing heart but sequentially with respect to each other by a pneumatic power source positioned externally of the patient.
The occluding chamber has a diameter greater than the diameter of the blood vessel within which it lies so that when inflated it occludes the blood vessel. Since the occluding chamber is inflated before the pumping chamber, the pressure created in the blood vessel when the pumping chamber is later inflated causes the blood to flow in a single direction away from point of occlusion between the inflated occluding chamber and the wall of the blood vessel. Thus the cardiac assistance device of the present invention acts as a uni-directional pump and when properly positioned the direction of blood flow created by the device can be effectively controlled according to the dictates of sound medical practice to be most beneficial to the patient.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a cross-sectional view of the cardiac assistance device of this invention disposed within a blood vessel.
FIG. 2 is a cross-sectional view of the cardiac assistance device of this invention disposed within a blood vessel showing an alternative embodiment of the structure within the occluding chamber.
FIGS. 3 and 4 are elevation views of the cardiac assistance device of this invention showing progressive stages of the operation of the device.
FIG. 5 is a diagrammatic illustration of a human heart showing the placement of thecardiac assistance device within the aorta.
DETAILED DESCRIPTION OF THE INVENTION As shown in FIG. 1, the cardiac assistance device includes a pumping structure indicated generally by reference numeral 10 which is adapted to be inserted within a blood vessel 2 of the patient by conventional surgical procedures. The pumping structure is specially constructed to produce auni-directional flow of blood within the blood vessel. For this purpose the pumping structure operates to first occlude the blood vessel and then to create pressure within the blood vessel on one side of the point of occlusion to thereby cause the blood within the vessel to flow in one direction away from the point of occlusion. In construction, the pumping structure includes expansion means for internally occluding the blood vessel and blood moving means positioned on one side of the expansion means for displacing blood onthat side of the expansion means. As shown, the expansion means comprises an inflatable occluding chamber 3 and the blood moving means comprises one or more inflatable pumping chambers 4 which communicate in series with the occluding chamber. The occluding chamber 3 and the pumping chamber 4 are defined by a balloon structure which consists of a balloon member 5 mounted on a tubular conduit 6 extending longitudinally through the balloon member 5. Each end of the balloon is disposed in fluidgas tight relationship about the tubular conduit by suitable sealing means as for example, silk threads 7 tied tightly about the terminal ends of the balloon member. As shown, an intermediate portion of the balloon member 5 is held against expansion in fluid-gas tight relationship to the tubular conduit 6 by silk threads 7' similar to the ones used for sealing each end of the balloon member. A metallic pellet 13 seals the end of the tubular conduit at a point located near the end of the pumping chamber 4 remote from the occluding chamber. The use of a metallic pellet for this pur pose advantageously permits the position of the pumping structure within the blood vessel to be visually monitored by the use of standard X-ray techniques after it has been introduced into the patient.
The balloon member 5 and the tubular conduit are made of nonthrombogenic material so that the danger of blood clotting is eliminated. Also the silk sealing threads are coated with a nonthrombogenic material and the assembled pumping structure is dipped into a bath of molten nonthrombogenic material. An example of nonthrombogenic material is polyurethane. In addition to being nonthrombogenic, the balloon member is also inelastic or nonstretchable so that the danger of fatigue failure due to stretching when the balloon member is repeatedly inflated and deflated is avoided. In other words, no stretching of the balloon member occurs when it is inflated. Rather the balloon merely expands upon inflation to its natural but relaxed inflated state.
The tubular conduit serves a dual purpose. First, it acts to hold the pumping chamber on one side of the occluding chamber as the balloon structure is introduced into the patient thus preventing the balloon structure from folding back on itself. Secondly, the tubular conduit provides a convenient means for introducing gas or fluid into the balloon structure to inflate the occluding and pumping chambers. For the latter purpose those portions of the tubular conduit which extend through the occluding and pumping chambers are provided with a series of perforations 8 which permit air flow into and out of the occluding and pumping chambers. In the presently preferred embodiment of this invention, the tubular conduit has a diameter of approximately 2-3 millimeters and the perforations are approximately 1 millimeter in diameter.
The occluding chamber of the balloon has a size such as when inflated the blood vessel is internally occluded. The blood vessel is occluded by the inflated occluding chamber in the sense that a complete occlusion of the blood vessel is produced causing stoppage of the blood stream and accumulation of the pressure within the blood vessel. The pumping chamber on the other hand is slightly smaller in size than the occluding chamber and when inflated the pumping chamber acts only to increase the pressure within the blood vessel. In other words, flow of blood past the inflated pumping chamber is not prevented but blood flow past the inflated occluding chamber is prevented. In the construction shown in the drawing, the occluding chamber is substantially spherical in shape while the single pumping chamber shown is substantially cylindrical in shape. Since the construction shown in the drawing is intended for insertion within the aorta of the patient which for the average patient has an inside diameter of approximately 18-22 millimeters, it is preferred that the spherical occluding chamber be slightly greater than 22 millimeters in diameter in its inflated state and that the pumping chamber have an inflated size of approximately 16 millimeters in diameter.
The occluding and pumping chamber of the balloon are alternately inflated and deflated at a cycle which is out of phase with the heartbeat of the patient. That is, when the heart is relaxed, the chambers of the balloon are inflated and when the heart is pumping these chambers are deflated. For this purpose a pneumatic power source indicated diagrammatically by reference numeral 11 in FIG. is provided. The pneumatic power source is of conventional construction having the capability of creating alternating positive and negative pressure as triggered by the electrocardiogram of the patient. As shown, the pumping machine is connected to the balloon structure via the tubular conduit 6. A suitable pumping machine for practicing the teachings of the present invention is the pneumatic pumping machine produced by the Datascope Company of New Jersey.
In order to provide uni-directional pumping action, the occluding chamber of the balloon structure is inflated prior to inflation of the pumping chamber. For this purpose an obstruction member 9 is provided. The obstruction member acts to divert the flow of gas within the balloon structure in a manner which produces sequential inflation of the occluding and pumping chambers. As shown the obstruction member is disposed within that portion of the tubular conduit extending through the occluding chamber 3 at a point located between two adjacent perforations 8' and 8". With this arrangement, gas supplied from the pneumatic power source is temporarily diverted from the tubular conduit into the occluding chamber through the perforations 8" disposed upstream of the obstruction member. This diversion is due to the presence of the obstruction member which prevents uninterrupted flow of gas through the tubular conduit. When the occluding chamber has reached a fully inflated configuration as shown in FIG. 4, the gas reenters the tubular conduit through the perforations 8' disposed downstream of the obstruction member. From this point the gas flows into the pumping chamber through the perforations disposed in the portion of the tubular conduit extending within the pumping chamber. Thereby the pumping chamber is brought to a fully inflated condition as shown in FIG. 1. Thus it will be seen that the occluding chamber and pumping chambers are repeatedly cycled in a sequential fashion from the configuration shown in FIG. 3 where both chambers are collapsed to the configuration shown in FIG. 4 where the occluding chamber is inflated and the pumping chamber deflated and finally to the configuration shown in FIG. 1 wherein both chambers are inflated causing blood within the vessel to flow in the direction of arrows 14 away from the point of occlusion in the vessel created by the inflated occluding chamber. With the solid obstruction member it will be recognized that deflation of the occluding chamber also occurs in a sequential manner. In other words, during the deflation phase a reverse flow of air out of the balloon is created first from the occluding chamber through the perforations 8' and then from the pumping chamber. The path of exit from the pumping chamber leads into the conduit 6 through the perforations disposed in the portion of the conduit 6 located within the pumping chamber and then into the occluding chamber via the perforations 8 and finally back into the tubular conduit through the perforations 8" and out of the balloon structure.
The occluding and pumping chambers may advantageously be deflated substantially simultaneously by replacing the solid obstruction member with a oneway valve such as the ball valve 12 shown in FIG. 2. With this arrangement, the ball valve is closed during the inflation cycle thereby producing the same pattern of air flow as is produced with the solid obstruction member shown in FIG. 1. However, on the deflation cycle, the ball valve is opened thus permitting air to be withdrawn from the occluding and pumping chambers through all the perforations in those portions of the tubular conduit disposed within these chambers at substantially the same time. Simultaneous deflation of the occluding and pumping chambers is advantageous since very little time is consumed between successive beats of the heart. Thus the possibility that the pumping structure will pulsate in appropriate coordination with the heartbeat is thereby greatly enhanced.
One application for the cardiac assistance device of the present invention is sown in FIG. 5. For this application the pumping structure section of the device is inserted into the femoral artery at a point below the bifurcation in the aorta and pushed upward into the aorta to the position shown. In this position the device acts to direct a flow of blood toward the heart into the coronary artery which supplies blood to the heart muscles and also into the carotid arteries which supply blood to the brain. Blood pumped by the cardiac assistance device is prevented from reentering the heart chamber by the aortic valve. It will be recognized that this particular use of the device is particularly beneficial since an adequate supply of blood to these critical organs is insured.
We claim: 1. A cardiac assistance device comprising: a. a pump structure adapted to be inserted into a blood vessel of a patient, said blood structure having an elongated support means with an insertable end;
1. expansion means on said support means for occluding the blood vessel;
2. blood moving means positioned on one side of the expansion means on said support means adjacent said insertable end for displacing blood within the vessel on said one side;
3. means for sequentially activating the expansion means and blood moving means in that order to produce a uni-directional flow of blood within the blood vessel away from the point of occlusion and toward the heart, and
b. means for alternately activating and deactivating the expansion means and to produce moving means on a cycle out of phase with the pumping action of the heart.
2. The cardiac assistance device according to claim 1 wherein:
a. the expansion means comprises an inflatable occluding chamber; and
b. the blood moving means comprises at least one inflatable pumping chamber communicating with the occluding chamber.
3. The cardiac assistance device according to claim 2 wherein:
a. the occluding chamber and pumping chamber are troduced into the patient.
4. The cardiac assistance device according to claim 3 wherein:
a. the holding means comprises a tubular conduit extending through the balloon member, said balloon member being held in sealed relationship about said conduit at each end thereof and at said intermediate point along its length; and
b. the means for activating the occluding and pumping chambers comprises a pneumatic power source operatively connected to the: tubular conduit for alternately pressurizing and depressurizing the balloon member to inflate and deflate it respectively;
c. 33: portion of the tubular conduit extending through the balloon member has a series of perforations permitting flow of air into and out of the balloon member during the inflation and deflation I phases respectively.
5. The cardiac assistance device according to claim 4 wherein:
a. the means for sequentially inflating the occluding and pumping chambers comprises means for temporarily diverting the flow of air through the tubu lar conduit into the occluding chamber prior to entrance into the pumping chamber.
6. The cardiac assistance device according to claim 5 wherein:
a. the means for diverting the flow of air through the tubular conduit comprises an obstruction member disposed within the portion of the tubular conduit extending through the occluding chamber at a point located between two adjacent perforations of said conduit portion.
7. The cardiac assistance device according to claim 5 wherein:
a. the means for diverting the flow of air through the
Claims (11)
1. A cardiac assistance device comprising: a. a pump structure adapted to be inserted into a blood vessel of a patient, said blood structure having an elongated support means with an insertable end; 1. expansion means on said support means for occluding the blood vessel; 2. blood moving means positioned on one side of the expansion means on said support means adjacent said insertable end for displacing blood within the vessel on said one side; 3. means for sequentially activating the expansion means and blood moving means in that order to produce a uni-directional flow of blood within the blood vessel away from the point of occlusion and toward the heart, and b. means for alternately activating and deactivating the expansion means and to produce moving means on a cycle out of phase with the pumping action of the heart.
2. blood moving means positioned on one side of the expansion means on said support means adjacent said insertable end for displacing blood within the vessel on said one side;
2. The cardiac assistance device according to claim 1 wherein: a. the expansion means comprises an inflatable occluding chamber; and b. the blood moving means comprises at least one inflatable pumping chamber communicating with the occluding chamber.
2. holding means attached to the balloon member for maintaining the relative position of the occluding chamber and pumping as they are introduced into the patient.
3. The cardiac assistance device according to claim 2 wherein: a. the occluding chamber and Pumping chamber are defined by a balloon structure comprising:
3. means for sequentially activating the expansion means and blood moving means in that order to produce a uni-directional flow of blood within the blood vessel away from the point of occlusion and toward the heart, and b. means for alternately activating and deactivating the expansion means and to produce moving means on a cycle out of phase with the pumping action of the heart.
4. The cardiac assistance device according to claim 3 wherein: a. the holding means comprises a tubular conduit extending through the balloon member, said balloon member being held in sealed relationship about said conduit at each end thereof and at said intermediate point along its length; and b. the means for activating the occluding and pumping chambers comprises a pneumatic power source operatively connected to the tubular conduit for alternately pressurizing and depressurizing the balloon member to inflate and deflate it respectively; and c. the portion of the tubular conduit extending through the balloon member has a series of perforations permitting flow of air into and out of the balloon member during the inflation and deflation phases respectively.
5. The cardiac assistance device according to claim 4 wherein: a. the means for sequentially inflating the occluding and pumping chambers comprises means for temporarily diverting the flow of air through the tubular conduit into the occluding chamber prior to entrance into the pumping chamber.
6. The cardiac assistance device according to claim 5 wherein: a. the means for diverting the flow of air through the tubular conduit comprises an obstruction member disposed within the portion of the tubular conduit extending through the occluding chamber at a point located between two adjacent perforations of said conduit portion.
7. The cardiac assistance device according to claim 5 wherein: a. the means for diverting the flow of air through the tubular conduit comprises a one-way valve disposed within the portion of the tubular conduit extending through the occluding chamber at a point located between two adjacent perforations of said conduit portion, said valve precluding the flow of air therethrough during the inflation phase and permitting flow of air therethrough during the deflation phase.
8. The cardiac assistance device according to claim 5 wherein: a. the occluding chamber is substantially spherical in shape; and b. the pumping chamber is substantially cylindrical in shape.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
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US1045270A | 1970-02-11 | 1970-02-11 |
Publications (1)
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US3692018A true US3692018A (en) | 1972-09-19 |
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Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10452A Expired - Lifetime US3692018A (en) | 1970-02-11 | 1970-02-11 | Cardiac assistance device |
Country Status (1)
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US (1) | US3692018A (en) |
Cited By (59)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3877838A (en) * | 1973-08-09 | 1975-04-15 | Daniel S J Choy | Device for advancing material through a tube |
US3939820A (en) * | 1974-10-29 | 1976-02-24 | Datascope Corporation | Single-chamber, multi-section balloon for cardiac assistance |
US4015590A (en) * | 1976-04-12 | 1977-04-05 | Baylor College Of Medicine | Balloon activated blood pump |
US4034742A (en) * | 1973-01-31 | 1977-07-12 | Thoma Dipl Ing Dr Techn Herwig | Apparatus for mechanically assisting circulation of the blood in the human body |
US4077394A (en) * | 1976-08-25 | 1978-03-07 | Mccurdy Martin D | Integral pressure sensor probe for a cardiac assistance device |
US4154227A (en) * | 1977-10-11 | 1979-05-15 | Krause Horst E | Method and apparatus for pumping blood within a vessel |
DE2915089A1 (en) * | 1978-03-06 | 1980-10-30 | Datascope Corp | BALLOON CATHEDRAL |
WO1980002366A1 (en) * | 1979-05-07 | 1980-11-13 | H Krause | Method and apparatus for pumping blood within a vessel |
FR2455465A1 (en) * | 1979-05-03 | 1980-11-28 | Datascope Corp | Balloon catheter - with central support rod for twisting balloon before insertion |
US4276874A (en) * | 1978-11-15 | 1981-07-07 | Datascope Corp. | Elongatable balloon catheter |
WO1981002110A1 (en) * | 1980-01-30 | 1981-08-06 | T Fogarty | Dilatation catheter apparatus and method |
WO1982000409A1 (en) * | 1980-07-28 | 1982-02-18 | T Fogarty | Calibrating dilatation catheter method and apparatus |
US4327709A (en) * | 1978-03-06 | 1982-05-04 | Datascope Corp. | Apparatus and method for the percutaneous introduction of intra-aortic balloons into the human body |
US4522195A (en) * | 1981-05-25 | 1985-06-11 | Peter Schiff | Apparatus for left heart assist |
US4527549A (en) * | 1982-08-05 | 1985-07-09 | Shelhigh Inc. | Method of and means for intraaortic assist |
US4531936A (en) * | 1981-01-29 | 1985-07-30 | Gordon Robert T | Device and method for the selective delivery of drugs to the myocardium |
US4546759A (en) * | 1983-07-29 | 1985-10-15 | Mladen Solar | Method and apparatus for assisting human heart function |
FR2577423A1 (en) * | 1985-02-20 | 1986-08-22 | Gilles Karcher | CIRCULATORY AND CORONARY ASSISTANCE PUMP WITH INTRA-AORTIC BALLOONS |
EP0194338A2 (en) * | 1985-03-14 | 1986-09-17 | Shelhigh, Inc. | Method of and means for intraaortic assist |
EP0209070A2 (en) * | 1985-07-15 | 1987-01-21 | ABIOMED, INC. ( a Delaware Corporation) | High frequency intra-arterial cardiac support system |
US4733652A (en) * | 1985-12-31 | 1988-03-29 | Aisin Seiki Kabushiki Kaisha | Intra-aortic balloon |
US4861330A (en) * | 1987-03-12 | 1989-08-29 | Gene Voss | Cardiac assist device and method |
US4896670A (en) * | 1988-04-19 | 1990-01-30 | C. R. Bard, Inc. | Kissing balloon catheter |
US4902272A (en) * | 1987-06-17 | 1990-02-20 | Abiomed Cardiovascular, Inc. | Intra-arterial cardiac support system |
US4934996A (en) * | 1984-02-27 | 1990-06-19 | Boston Scientific Corporation | Pressure-controlled intermittent coronary sinus occlusion apparatus and method |
US4969470A (en) * | 1984-02-27 | 1990-11-13 | Boston Scientific Corporation | Heart analysis using pressure-controlled intermittent coronary sinus occlusion |
US5100382A (en) * | 1988-10-24 | 1992-03-31 | Valtchev Konstantin L | Single channel balloon uterine injector |
US5222980A (en) * | 1991-09-27 | 1993-06-29 | Medtronic, Inc. | Implantable heart-assist device |
US5395330A (en) * | 1990-06-13 | 1995-03-07 | Dlp, Inc. | Auto-inflating catheter cuff |
US5738652A (en) * | 1991-07-16 | 1998-04-14 | Heartport, Inc. | Retrograde delivery catheter and method for inducing cardioplegic arrest |
US5755687A (en) * | 1997-04-01 | 1998-05-26 | Heartport, Inc. | Methods and devices for occluding a patient's ascending aorta |
US5765568A (en) * | 1994-05-27 | 1998-06-16 | Heartport, Inc. | Catheter system and method for venting the left ventricle |
US5769812A (en) * | 1991-07-16 | 1998-06-23 | Heartport, Inc. | System for cardiac procedures |
US5792094A (en) * | 1991-07-16 | 1998-08-11 | Heartport, Inc. | Method of delivering cardioplegic fluid to a patient's heart |
US5980448A (en) * | 1998-01-28 | 1999-11-09 | Vascor, Inc. | Single chamber blood pump |
US6159178A (en) * | 1998-01-23 | 2000-12-12 | Heartport, Inc. | Methods and devices for occluding the ascending aorta and maintaining circulation of oxygenated blood in the patient when the patient's heart is arrested |
US6190304B1 (en) | 1999-07-13 | 2001-02-20 | University Of North Texas Health Science Center At Fort Worth | Enhanced intra-aortic balloon assist device |
US6200260B1 (en) | 1997-10-09 | 2001-03-13 | Fore Flow Corporation | Implantable heart assist system |
US6387037B1 (en) | 1997-10-09 | 2002-05-14 | Orqis Medical Corporation | Implantable heart assist system and method of applying same |
US6390969B1 (en) | 1997-10-09 | 2002-05-21 | Orqis Medical Corporation | Implantable heart assist system and method of applying same |
US20020115982A1 (en) * | 1999-03-01 | 2002-08-22 | Coaxia, Inc. | Partial aortic occlusion devices and methods for cerebral perfusion augmentation |
US6468200B1 (en) * | 2000-03-06 | 2002-10-22 | Michael C. Fischi | Segmented peristaltic intra-aortic balloon pump |
US6482171B1 (en) | 1991-07-16 | 2002-11-19 | Heartport, Inc. | Multi-lumen catheter |
US20030069468A1 (en) * | 1997-10-09 | 2003-04-10 | Bolling Steven F. | Implantable heart assist system and method of applying same |
US6610004B2 (en) | 1997-10-09 | 2003-08-26 | Orqis Medical Corporation | Implantable heart assist system and method of applying same |
US6635046B1 (en) * | 1999-03-01 | 2003-10-21 | Coaxia, Inc. | Partial aortic occlusion devices and methods for cerebral perfusion augmentation |
US20060014999A1 (en) * | 2004-07-19 | 2006-01-19 | Heilman Marlin S | Devices, systems and methods for assisting blood flow |
WO2006048883A3 (en) * | 2004-11-07 | 2006-10-26 | Drops Ltd | Apparatus and method for direct organ perfusion |
US7445592B2 (en) | 2004-06-10 | 2008-11-04 | Orqis Medical Corporation | Cannulae having reduced flow resistance |
US7468050B1 (en) * | 2002-12-27 | 2008-12-23 | L. Vad Technology, Inc. | Long term ambulatory intra-aortic balloon pump |
DE102005004663B4 (en) * | 2005-02-02 | 2009-07-23 | Medicor Gmbh | Medical vascular lock with blocking function |
US20100211008A1 (en) * | 2006-02-07 | 2010-08-19 | Egon Wiest | Medical Vascular Lock With Blocking Function |
US7927268B1 (en) | 2003-09-02 | 2011-04-19 | Coaxia, Inc. | Counterpulsation device with increased volume-displacement efficiency and methods of use |
US8066628B1 (en) | 2010-10-22 | 2011-11-29 | Nupulse, Inc. | Intra-aortic balloon pump and driver |
US8876686B2 (en) | 2011-02-18 | 2014-11-04 | Vascor, Inc | Control of blood flow assist systems |
CN104174078A (en) * | 2014-09-15 | 2014-12-03 | 湖南埃普特医疗器械有限公司 | Left ventricle auxiliary device |
US9981078B2 (en) | 2014-09-15 | 2018-05-29 | Lijun Jin | Left ventricular assist device |
US11426563B2 (en) | 2018-12-03 | 2022-08-30 | Nxt Biomedical, Llc | Blood pump or balloon cycling and venous occlusion |
WO2023173127A1 (en) * | 2022-03-11 | 2023-09-14 | Phap Medical, Llc | Systems and methods for a peristalsis heart assist pump |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR15864E (en) * | 1912-02-02 | 1912-10-10 | Louis Marie Clement Charnaux | Expandable catheter for the diagnosis and treatment of bowel, esophagus and urethral disorders |
US3266487A (en) * | 1963-06-04 | 1966-08-16 | Sundstrand Corp | Heart pump augmentation system and apparatus |
US3504662A (en) * | 1967-05-16 | 1970-04-07 | Avco Corp | Intra-arterial blood pump |
US3505987A (en) * | 1967-03-17 | 1970-04-14 | Medrad Inc | Intra-aortic heart pump |
US3592183A (en) * | 1969-05-27 | 1971-07-13 | David H Watkins | Heart assist method and apparatus |
-
1970
- 1970-02-11 US US10452A patent/US3692018A/en not_active Expired - Lifetime
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR15864E (en) * | 1912-02-02 | 1912-10-10 | Louis Marie Clement Charnaux | Expandable catheter for the diagnosis and treatment of bowel, esophagus and urethral disorders |
US3266487A (en) * | 1963-06-04 | 1966-08-16 | Sundstrand Corp | Heart pump augmentation system and apparatus |
US3505987A (en) * | 1967-03-17 | 1970-04-14 | Medrad Inc | Intra-aortic heart pump |
US3504662A (en) * | 1967-05-16 | 1970-04-07 | Avco Corp | Intra-arterial blood pump |
US3592183A (en) * | 1969-05-27 | 1971-07-13 | David H Watkins | Heart assist method and apparatus |
Non-Patent Citations (1)
Title |
---|
Laird et al. Trans. Amer. Soc. Artif. Int. Organs. Vol. XIV, 1968 pp. 338 342 * |
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US4034742A (en) * | 1973-01-31 | 1977-07-12 | Thoma Dipl Ing Dr Techn Herwig | Apparatus for mechanically assisting circulation of the blood in the human body |
US3877838A (en) * | 1973-08-09 | 1975-04-15 | Daniel S J Choy | Device for advancing material through a tube |
US3939820A (en) * | 1974-10-29 | 1976-02-24 | Datascope Corporation | Single-chamber, multi-section balloon for cardiac assistance |
US4015590A (en) * | 1976-04-12 | 1977-04-05 | Baylor College Of Medicine | Balloon activated blood pump |
US4077394A (en) * | 1976-08-25 | 1978-03-07 | Mccurdy Martin D | Integral pressure sensor probe for a cardiac assistance device |
US4154227A (en) * | 1977-10-11 | 1979-05-15 | Krause Horst E | Method and apparatus for pumping blood within a vessel |
DE2915089A1 (en) * | 1978-03-06 | 1980-10-30 | Datascope Corp | BALLOON CATHEDRAL |
US4346698A (en) * | 1978-03-06 | 1982-08-31 | Datascope Corp. | Balloon catheter with rotatable support |
US4327709A (en) * | 1978-03-06 | 1982-05-04 | Datascope Corp. | Apparatus and method for the percutaneous introduction of intra-aortic balloons into the human body |
US4261339A (en) * | 1978-03-06 | 1981-04-14 | Datascope Corp. | Balloon catheter with rotatable support |
US4276874A (en) * | 1978-11-15 | 1981-07-07 | Datascope Corp. | Elongatable balloon catheter |
FR2455465A1 (en) * | 1979-05-03 | 1980-11-28 | Datascope Corp | Balloon catheter - with central support rod for twisting balloon before insertion |
WO1980002366A1 (en) * | 1979-05-07 | 1980-11-13 | H Krause | Method and apparatus for pumping blood within a vessel |
WO1981002110A1 (en) * | 1980-01-30 | 1981-08-06 | T Fogarty | Dilatation catheter apparatus and method |
US4292974A (en) * | 1980-01-30 | 1981-10-06 | Thomas J. Fogarty | Dilatation catheter apparatus and method |
WO1982000409A1 (en) * | 1980-07-28 | 1982-02-18 | T Fogarty | Calibrating dilatation catheter method and apparatus |
US4328811A (en) * | 1980-07-28 | 1982-05-11 | Fogarty Thomas J | Calibrating dilation catheter |
US4531936A (en) * | 1981-01-29 | 1985-07-30 | Gordon Robert T | Device and method for the selective delivery of drugs to the myocardium |
US4522195A (en) * | 1981-05-25 | 1985-06-11 | Peter Schiff | Apparatus for left heart assist |
US4527549A (en) * | 1982-08-05 | 1985-07-09 | Shelhigh Inc. | Method of and means for intraaortic assist |
US4546759A (en) * | 1983-07-29 | 1985-10-15 | Mladen Solar | Method and apparatus for assisting human heart function |
US4934996A (en) * | 1984-02-27 | 1990-06-19 | Boston Scientific Corporation | Pressure-controlled intermittent coronary sinus occlusion apparatus and method |
US4969470A (en) * | 1984-02-27 | 1990-11-13 | Boston Scientific Corporation | Heart analysis using pressure-controlled intermittent coronary sinus occlusion |
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US4697574A (en) * | 1985-02-20 | 1987-10-06 | Medicorp Research Laboratories Corp. | Pump for assistance in circulation |
FR2577423A1 (en) * | 1985-02-20 | 1986-08-22 | Gilles Karcher | CIRCULATORY AND CORONARY ASSISTANCE PUMP WITH INTRA-AORTIC BALLOONS |
EP0194338A2 (en) * | 1985-03-14 | 1986-09-17 | Shelhigh, Inc. | Method of and means for intraaortic assist |
EP0194338A3 (en) * | 1985-03-14 | 1987-11-04 | Shelhigh, Inc. | Method of and means for intraaortic assist |
EP0209070A2 (en) * | 1985-07-15 | 1987-01-21 | ABIOMED, INC. ( a Delaware Corporation) | High frequency intra-arterial cardiac support system |
EP0209070A3 (en) * | 1985-07-15 | 1988-07-20 | ABIOMED, INC. ( a Delaware Corporation) | High frequency intra-arterial cardiac support system |
US4733652A (en) * | 1985-12-31 | 1988-03-29 | Aisin Seiki Kabushiki Kaisha | Intra-aortic balloon |
US4861330A (en) * | 1987-03-12 | 1989-08-29 | Gene Voss | Cardiac assist device and method |
US4902272A (en) * | 1987-06-17 | 1990-02-20 | Abiomed Cardiovascular, Inc. | Intra-arterial cardiac support system |
US4896670A (en) * | 1988-04-19 | 1990-01-30 | C. R. Bard, Inc. | Kissing balloon catheter |
US5100382A (en) * | 1988-10-24 | 1992-03-31 | Valtchev Konstantin L | Single channel balloon uterine injector |
US5395330A (en) * | 1990-06-13 | 1995-03-07 | Dlp, Inc. | Auto-inflating catheter cuff |
US5738652A (en) * | 1991-07-16 | 1998-04-14 | Heartport, Inc. | Retrograde delivery catheter and method for inducing cardioplegic arrest |
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CN104174078A (en) * | 2014-09-15 | 2014-12-03 | 湖南埃普特医疗器械有限公司 | Left ventricle auxiliary device |
CN104174078B (en) * | 2014-09-15 | 2016-09-21 | 靳立军 | A kind of left ventricular assist device |
US9981078B2 (en) | 2014-09-15 | 2018-05-29 | Lijun Jin | Left ventricular assist device |
US11426563B2 (en) | 2018-12-03 | 2022-08-30 | Nxt Biomedical, Llc | Blood pump or balloon cycling and venous occlusion |
WO2023173127A1 (en) * | 2022-03-11 | 2023-09-14 | Phap Medical, Llc | Systems and methods for a peristalsis heart assist pump |
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