CA1240802A - High-capacity intravascular blood pump utilizing percutaneous access - Google Patents
High-capacity intravascular blood pump utilizing percutaneous accessInfo
- Publication number
- CA1240802A CA1240802A CA000463995A CA463995A CA1240802A CA 1240802 A CA1240802 A CA 1240802A CA 000463995 A CA000463995 A CA 000463995A CA 463995 A CA463995 A CA 463995A CA 1240802 A CA1240802 A CA 1240802A
- Authority
- CA
- Canada
- Prior art keywords
- pump
- blood
- pumping means
- housing
- order
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- 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
- A61M60/827—Sealings between moving parts
- A61M60/829—Sealings between moving parts having a purge fluid supply
-
- 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
- A61M60/13—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 by means of a catheter allowing explantation, e.g. catheter pumps temporarily introduced via the vascular system
-
- 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
- A61M60/205—Non-positive displacement blood pumps
- A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
- A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow pumps
-
- 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
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/405—Details relating to driving for non-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
- A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
- A61M60/804—Impellers
- A61M60/806—Vanes or blades
-
- 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
- A61M60/818—Bearings
- A61M60/825—Contact bearings, e.g. ball-and-cup or pivot bearings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/871—Energy supply devices; Converters therefor
- A61M60/88—Percutaneous cables
-
- 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
-
- 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
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
- A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
- A61M60/414—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted by a rotating cable, e.g. for blood pumps mounted on a catheter
-
- 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
- A61M60/818—Bearings
- A61M60/824—Hydrodynamic or fluid film bearings
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/03—Heart-lung
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S415/00—Rotary kinetic fluid motors or pumps
- Y10S415/90—Rotary blood pump
Abstract
ABSTRACT
Full-flow cardiac assist is provided for cardio-genic shock patients without major surgery by a minia-ture axial-flow pump which can be inserted into the heart through the femoral artery and driven via a flexible cable from an external power source. The cable is contained within the catheter attached to the pump. The catheter also provides a conduit to supply the pump bearings with a blood-compatible purge fluid at a rate and pressure sufficient to prevent thrombus formation and introduction of blood elements between rotating and stationary elements of the pump. Due to the very small diameter of the pump, rotational speeds on the order of 10,000 to 20,000 rpm can be used to produce a blood flow on the order of about four liters per minute without significant hemolysis.
Full-flow cardiac assist is provided for cardio-genic shock patients without major surgery by a minia-ture axial-flow pump which can be inserted into the heart through the femoral artery and driven via a flexible cable from an external power source. The cable is contained within the catheter attached to the pump. The catheter also provides a conduit to supply the pump bearings with a blood-compatible purge fluid at a rate and pressure sufficient to prevent thrombus formation and introduction of blood elements between rotating and stationary elements of the pump. Due to the very small diameter of the pump, rotational speeds on the order of 10,000 to 20,000 rpm can be used to produce a blood flow on the order of about four liters per minute without significant hemolysis.
Description
I . V ~ ~..L
1087 . C020CA
Z
E~IGH-CAPACITY INTRAVASCULAR BLOOD PUMP
UTILIZING PERCUTANEOUS ACCESS
_ .
This invention relates to blood pumps, and more particularly to a miniature blood pump capable o~ per-cutaneous insertion into the vascular system to provide full-flow right or left ventricular temporary cardiac assist without major surgery.
Background of tha Invention The medical profession is frequently confronted with cases of cardiogenic shock (i.e. a condition in which the heart still functions but is not pumping suficient blood to keep the patient alive). Emergencv treatment of this condition often requires some form of cardiac assist which maintains a blood flow sufficient for survival while other measures are initiated to restore the heart itself to more normal function.
At the present time, the only methods available for a cardiac assist of this nature are pump systems whose connection to the vascular system involves major surgery, or a balloon catheter inserted into an appropriate artery. Un-fortunately, major surgery may involve too much delay or risk for a patient in cardiogenic shock, and the balloon catheter may not provide sufficient improvement in cardiac output.
~Z4~
It has been proposed to provide left-sided circula-tory support by the use of nGn-thoracotomy vascular access.
In such systems, two simultaneous arterial sites would be employed to pump blood from the heart into the arterial system. However, this technique would necessitate the use of long, small-bore cannulae which would result in large pressure drops. Exposure of conduits with negative pressure could result in air embolism and serious complications. In addition, the subclavian ~rtery would need to be employed for the pump inlet because of its proximity to the heart.
Surgical access to this vessel is more difficuLt than for the femoral artery.
Use of an external pump for support oE the right heart would require access at two simultaneous venous sites. In this case the pump output would need to be returned by a long, small-bore cannula to the pulmonary artery. Similar complications oE lar~e pressure drops with negative pressures and possible air embolism could occur. The prior art has thus been unable to provide an easily-implemented low-risk circulatory-assist device capable of rapidly providiny full flow heart assist to critically ill patients.
8~
Summary of the Invention According to the present invention, there is provided a high speed miniature blood pump, preferably of the axial -type, which is small enough to directly access ei-ther the right or left heart for circulatory assistance by means of either the peripheral venous or arterial system. This device is intended for peripheral percutaneous insertion and is capable of providing as much as three to four liters of flow per minute.
Support of the right heart would involve an antegrade insertion through the tricuspid and pulmonary valve into -the pulmonary artery. Such a procedure would be possible from peripheral venous access through either the femoral, external jugular or cephalic vein.
Support of the lef-t heart would be achieved by retrograde insertion through the aortic valve into the left ventricle. This could be performed from ei-ther the subclavian or femoral artery.
In the event that peripheral access proves dif~icult, i-t would be possible to achieve vascular access by means of a mini-thoracotomy and introduction through the ventricular apex.
~4~8C~2 The pump of this invention is driven by a small power unit on the outside of the body, by way of a flexible cable or hydraulic line extending through a small diameter cannula at the site of systemic circulatory access.
In order to deliver the required blood flow~ the pump of this invention has to operate with a shaft speed of 10,000 to 20,000 rpm. Pumps of such high rotational speed have pre~iously been thought unsuitable for blood pumping applications because it was generally thought that the tips of the impeller blades passing close to the stationary wall of the impeller chamber would create shear forces so great as to cause severe hemolysis. The present invention arises out of the recognition that the linear velocity of the tips of the blades is dependent upon the diameter of the pump, and is therefore small enough in a miniature pump as contemplated by this invention to produce no significant hemolysis even at the speeds required for its operation.
Thrombus formation is avoided in the pump of this invention by the use of a purge seal between the rotating and stationary parts of the pump. In addition, bacterio-static effects may be achieved by using ethanol, or a similar bacteriostatic agent capable of acting as a bearing lubricant, as the purge fluid.
Brief Description of the Drawin__ Fig. la is a schematic sec-tion of a human heart generally in the plane of the aorta, illustrating a preferred positioning of the pump of this invention for cardiac assis-t purposes;
Fig. lb is a schematic view of a human being illustra-ting the insertion of the pump of this invention through the femoral artery;
Fig. 2 is a par-tially schematic axial cross sec-tion of the pump of this inven-tion;
Figs. 3a and 3b are fragmentary transverse sections of the pump of Fig. 2 along lines 3a-3a and 3b-3b in Fig. 2; and Fig. 4 is a fragmentary section of the pump of Fig. 2 along line 4-4 in Fig. 2.
/
/
.
~, . ~, ~2~ 2 Description of the Preferred Embodiment The intravascular blood pump 10 of this invention may access the left ventricle 12 (Fig. la) of the heart 11 by retrograde insertion of an appropriate shor-t, flexible inlet cannula 14 through the aortic valve 15. The cannula 14 is guided through the aorta 16 from the femoral artery 17 ~Fig. lb), into which it can advantageously be inserted in the thigh 18. In the operation of the pump 10, blood is pumped in the direction of~the arrows (FigO la) from the left ventricle 12 through the inlet element 19 of cannula 14 and the interior of cannula 14 into the pump 10. At the outlet of pump 10, the pumped blood is discharged through outlet ele~ent 20 into the aorta 16.
Although the pump of this invention is discussed herein in terms of a left ventricle assist by retrograde insertion through the femoral artery, it will be understood that it, could also be used without significant modification as a left or right heart assist through other insertion techniques if desired, as discussed above.
The pump 10 is preferably driven by a flexible shaft 24 extending through a catheter 26 placed into the femoral artery 17 and aorta 16. The catheter 26 also serves as a conduit for a purge fluid whose purpose and function will be described below. Instead of the shaft 24, a hydraulic system using the catheter 26 may equally well be used to provide motive power to the pump 10.
In the arrangement of Fig. la and b, an appropriate support unit 28 located outside the patient's body provides the drive power for the shaft 24, and also provides the purge fluid to the pump 10 through the catheter 26. The catheter 26 is sufficiently small in diameter to allow rela-tively unobstructed blood flow around it when it is inserted into an artery.
Turning now to Fig. 2, the pump 10 has a housing 30 which is generally cylindrical along the body of the pump 10. The outlet element 14 and outlet element 20 are tapered to facilitate insertion and withdrawal of the pump 10 through the vascular system of the patient. The housing 30 carries stator blades 36. Support struts 38 (which also act as stator blades) connect the housina 30 to the stator support bearing 40 and tube attachment cone 42 n The cylindrical stator hub 40 supports the rotor 44 for rotational movement as driven by cable 24. ~xial move-ment of the rotor 44 is prevented by bearing flange 46. The rotor 44 carries a series of rotor blades 48 whose curved cross section (best shown in Fig. 4 ) is similar to that of the stator blades 36. However, the number of rotor blades in each ring of blades is different from the number of stator blades in each ring (there may be, for example, seven rotor blades per ring and eleven stator blades per ring), as best illustrated in Fig. 3~
~Z4~)80Z
The journal bearinys 41 are lubricated by a continuous flow of purge fluid 50 which is introduced into -the pump 10 under pressure through the catheter 26. The purge fluid 50 flows through the face seal 52 and is eventually discharged into the blood stream 54 at interface 56. As described in -the copending Canadian application Serial No. 463,668 filed Sep-tember 20, 1984 and entitled ANTI-THROMBOGENIC BLOOD PUMP, thrombus formation in pump 10 is prevented by maintaining a sufficient outflow of purge fluid 50 along the annular interface 56 to prevent blood elements from contacting the rotor and stator surfaces at -the interface 56.
The pump of this invention mus-t of necessity be ex-tremely small. Its outer diameter should ideally not exceed 7 to 9 mm. In order to provide the required blood flow on -the order of four liters per minute, the pump of -this invention needs to operate a-t speeds on the order of 10,000 to 20,000 rpm. In the operation of the pump, annular areas of blade tip shear occur at 58 and 60 in Fig. 2 where the tips of the blades 38 and 48 continuously sweep close to the rotor 44 and housing 30, respectively. However, in the worst case, which occurs in the area 58, the extremely small dimension of the pump causes the relative motion of the tip of blade / -/ _ Z
48 with respect to housing 30 to remain below 5 m/sec.
This relative velocity is low enough in combination with adequate tip clearance (on the order of O.lmm) t~ main-tain the shear forces in space 58 at a level sufficiently low to create no undue hemolysis. There is even less damage to the red cell membranes in space 60, as the relative velocity between the stator blade 38 and the rotor 44 is smaller because-space 60 is closer to the axis of pump 10 than space 58.
It will be seen that the present invention provides an efficient, intravascular cardiac assist method and apparatus which can be rapidly applied and removed without surgery and with minimal risk to the patient.
////
1087 . C020CA
Z
E~IGH-CAPACITY INTRAVASCULAR BLOOD PUMP
UTILIZING PERCUTANEOUS ACCESS
_ .
This invention relates to blood pumps, and more particularly to a miniature blood pump capable o~ per-cutaneous insertion into the vascular system to provide full-flow right or left ventricular temporary cardiac assist without major surgery.
Background of tha Invention The medical profession is frequently confronted with cases of cardiogenic shock (i.e. a condition in which the heart still functions but is not pumping suficient blood to keep the patient alive). Emergencv treatment of this condition often requires some form of cardiac assist which maintains a blood flow sufficient for survival while other measures are initiated to restore the heart itself to more normal function.
At the present time, the only methods available for a cardiac assist of this nature are pump systems whose connection to the vascular system involves major surgery, or a balloon catheter inserted into an appropriate artery. Un-fortunately, major surgery may involve too much delay or risk for a patient in cardiogenic shock, and the balloon catheter may not provide sufficient improvement in cardiac output.
~Z4~
It has been proposed to provide left-sided circula-tory support by the use of nGn-thoracotomy vascular access.
In such systems, two simultaneous arterial sites would be employed to pump blood from the heart into the arterial system. However, this technique would necessitate the use of long, small-bore cannulae which would result in large pressure drops. Exposure of conduits with negative pressure could result in air embolism and serious complications. In addition, the subclavian ~rtery would need to be employed for the pump inlet because of its proximity to the heart.
Surgical access to this vessel is more difficuLt than for the femoral artery.
Use of an external pump for support oE the right heart would require access at two simultaneous venous sites. In this case the pump output would need to be returned by a long, small-bore cannula to the pulmonary artery. Similar complications oE lar~e pressure drops with negative pressures and possible air embolism could occur. The prior art has thus been unable to provide an easily-implemented low-risk circulatory-assist device capable of rapidly providiny full flow heart assist to critically ill patients.
8~
Summary of the Invention According to the present invention, there is provided a high speed miniature blood pump, preferably of the axial -type, which is small enough to directly access ei-ther the right or left heart for circulatory assistance by means of either the peripheral venous or arterial system. This device is intended for peripheral percutaneous insertion and is capable of providing as much as three to four liters of flow per minute.
Support of the right heart would involve an antegrade insertion through the tricuspid and pulmonary valve into -the pulmonary artery. Such a procedure would be possible from peripheral venous access through either the femoral, external jugular or cephalic vein.
Support of the lef-t heart would be achieved by retrograde insertion through the aortic valve into the left ventricle. This could be performed from ei-ther the subclavian or femoral artery.
In the event that peripheral access proves dif~icult, i-t would be possible to achieve vascular access by means of a mini-thoracotomy and introduction through the ventricular apex.
~4~8C~2 The pump of this invention is driven by a small power unit on the outside of the body, by way of a flexible cable or hydraulic line extending through a small diameter cannula at the site of systemic circulatory access.
In order to deliver the required blood flow~ the pump of this invention has to operate with a shaft speed of 10,000 to 20,000 rpm. Pumps of such high rotational speed have pre~iously been thought unsuitable for blood pumping applications because it was generally thought that the tips of the impeller blades passing close to the stationary wall of the impeller chamber would create shear forces so great as to cause severe hemolysis. The present invention arises out of the recognition that the linear velocity of the tips of the blades is dependent upon the diameter of the pump, and is therefore small enough in a miniature pump as contemplated by this invention to produce no significant hemolysis even at the speeds required for its operation.
Thrombus formation is avoided in the pump of this invention by the use of a purge seal between the rotating and stationary parts of the pump. In addition, bacterio-static effects may be achieved by using ethanol, or a similar bacteriostatic agent capable of acting as a bearing lubricant, as the purge fluid.
Brief Description of the Drawin__ Fig. la is a schematic sec-tion of a human heart generally in the plane of the aorta, illustrating a preferred positioning of the pump of this invention for cardiac assis-t purposes;
Fig. lb is a schematic view of a human being illustra-ting the insertion of the pump of this invention through the femoral artery;
Fig. 2 is a par-tially schematic axial cross sec-tion of the pump of this inven-tion;
Figs. 3a and 3b are fragmentary transverse sections of the pump of Fig. 2 along lines 3a-3a and 3b-3b in Fig. 2; and Fig. 4 is a fragmentary section of the pump of Fig. 2 along line 4-4 in Fig. 2.
/
/
.
~, . ~, ~2~ 2 Description of the Preferred Embodiment The intravascular blood pump 10 of this invention may access the left ventricle 12 (Fig. la) of the heart 11 by retrograde insertion of an appropriate shor-t, flexible inlet cannula 14 through the aortic valve 15. The cannula 14 is guided through the aorta 16 from the femoral artery 17 ~Fig. lb), into which it can advantageously be inserted in the thigh 18. In the operation of the pump 10, blood is pumped in the direction of~the arrows (FigO la) from the left ventricle 12 through the inlet element 19 of cannula 14 and the interior of cannula 14 into the pump 10. At the outlet of pump 10, the pumped blood is discharged through outlet ele~ent 20 into the aorta 16.
Although the pump of this invention is discussed herein in terms of a left ventricle assist by retrograde insertion through the femoral artery, it will be understood that it, could also be used without significant modification as a left or right heart assist through other insertion techniques if desired, as discussed above.
The pump 10 is preferably driven by a flexible shaft 24 extending through a catheter 26 placed into the femoral artery 17 and aorta 16. The catheter 26 also serves as a conduit for a purge fluid whose purpose and function will be described below. Instead of the shaft 24, a hydraulic system using the catheter 26 may equally well be used to provide motive power to the pump 10.
In the arrangement of Fig. la and b, an appropriate support unit 28 located outside the patient's body provides the drive power for the shaft 24, and also provides the purge fluid to the pump 10 through the catheter 26. The catheter 26 is sufficiently small in diameter to allow rela-tively unobstructed blood flow around it when it is inserted into an artery.
Turning now to Fig. 2, the pump 10 has a housing 30 which is generally cylindrical along the body of the pump 10. The outlet element 14 and outlet element 20 are tapered to facilitate insertion and withdrawal of the pump 10 through the vascular system of the patient. The housing 30 carries stator blades 36. Support struts 38 (which also act as stator blades) connect the housina 30 to the stator support bearing 40 and tube attachment cone 42 n The cylindrical stator hub 40 supports the rotor 44 for rotational movement as driven by cable 24. ~xial move-ment of the rotor 44 is prevented by bearing flange 46. The rotor 44 carries a series of rotor blades 48 whose curved cross section (best shown in Fig. 4 ) is similar to that of the stator blades 36. However, the number of rotor blades in each ring of blades is different from the number of stator blades in each ring (there may be, for example, seven rotor blades per ring and eleven stator blades per ring), as best illustrated in Fig. 3~
~Z4~)80Z
The journal bearinys 41 are lubricated by a continuous flow of purge fluid 50 which is introduced into -the pump 10 under pressure through the catheter 26. The purge fluid 50 flows through the face seal 52 and is eventually discharged into the blood stream 54 at interface 56. As described in -the copending Canadian application Serial No. 463,668 filed Sep-tember 20, 1984 and entitled ANTI-THROMBOGENIC BLOOD PUMP, thrombus formation in pump 10 is prevented by maintaining a sufficient outflow of purge fluid 50 along the annular interface 56 to prevent blood elements from contacting the rotor and stator surfaces at -the interface 56.
The pump of this invention mus-t of necessity be ex-tremely small. Its outer diameter should ideally not exceed 7 to 9 mm. In order to provide the required blood flow on -the order of four liters per minute, the pump of -this invention needs to operate a-t speeds on the order of 10,000 to 20,000 rpm. In the operation of the pump, annular areas of blade tip shear occur at 58 and 60 in Fig. 2 where the tips of the blades 38 and 48 continuously sweep close to the rotor 44 and housing 30, respectively. However, in the worst case, which occurs in the area 58, the extremely small dimension of the pump causes the relative motion of the tip of blade / -/ _ Z
48 with respect to housing 30 to remain below 5 m/sec.
This relative velocity is low enough in combination with adequate tip clearance (on the order of O.lmm) t~ main-tain the shear forces in space 58 at a level sufficiently low to create no undue hemolysis. There is even less damage to the red cell membranes in space 60, as the relative velocity between the stator blade 38 and the rotor 44 is smaller because-space 60 is closer to the axis of pump 10 than space 58.
It will be seen that the present invention provides an efficient, intravascular cardiac assist method and apparatus which can be rapidly applied and removed without surgery and with minimal risk to the patient.
////
Claims (5)
OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. An intravascular blood pump, comprising:
a) an elongated housing open at each end, said housing having a shape and size allowing it to be passed through a human blood vessel;
b) non-hemolytic rotary pumping means within said housing for pumping blood in a living patient longitudinally through said housing;
c) conduit means extending from said housing and adapted to lie within said blood vessel without blocking it;
d) power means located remotely from said pumping means for powering said pumping means; and e) drive means including a flexible cable extending from said power means to said pumping means through said conduit means for transferring drive power from said power means to said pumping means.
a) an elongated housing open at each end, said housing having a shape and size allowing it to be passed through a human blood vessel;
b) non-hemolytic rotary pumping means within said housing for pumping blood in a living patient longitudinally through said housing;
c) conduit means extending from said housing and adapted to lie within said blood vessel without blocking it;
d) power means located remotely from said pumping means for powering said pumping means; and e) drive means including a flexible cable extending from said power means to said pumping means through said conduit means for transferring drive power from said power means to said pumping means.
2. The pump of claim 1, in which said rotary pumping means is an axial flow pump operating at a rotational speed on the order of 10,000 - 20,000 rpm.
3. The pump of claim 1, in which said rotary pumping means has a blood flow rate on the order of four liters per minute.
4. The pump of claim 1, in which said rotary pumping means is an axial flow pump in which the relationship between speed of rotation and blade size is such that no point on any blade has a linear velocity high enough to cause significant hemolysis.
5. The pump of claim 1, in which said speed of rotation exceeds 10,000 rpm.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US537,244 | 1983-09-28 | ||
US06/537,244 US4625712A (en) | 1983-09-28 | 1983-09-28 | High-capacity intravascular blood pump utilizing percutaneous access |
Publications (1)
Publication Number | Publication Date |
---|---|
CA1240802A true CA1240802A (en) | 1988-08-23 |
Family
ID=24141837
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000463995A Expired CA1240802A (en) | 1983-09-28 | 1984-09-25 | High-capacity intravascular blood pump utilizing percutaneous access |
Country Status (7)
Country | Link |
---|---|
US (1) | US4625712A (en) |
EP (1) | EP0157871B1 (en) |
JP (1) | JPS61500059A (en) |
BR (1) | BR8407086A (en) |
CA (1) | CA1240802A (en) |
DE (1) | DE3482656D1 (en) |
WO (1) | WO1985001432A1 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6123725A (en) | 1997-07-11 | 2000-09-26 | A-Med Systems, Inc. | Single port cardiac support apparatus |
Families Citing this family (229)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4753221A (en) * | 1986-10-22 | 1988-06-28 | Intravascular Surgical Instruments, Inc. | Blood pumping catheter and method of use |
US4779614A (en) * | 1987-04-09 | 1988-10-25 | Nimbus Medical, Inc. | Magnetically suspended rotor axial flow blood pump |
US4834707A (en) * | 1987-09-16 | 1989-05-30 | Evans Phillip H | Venting apparatus and method for cardiovascular pumping application |
US6210395B1 (en) | 1987-09-30 | 2001-04-03 | Lake Region Mfg., Inc. | Hollow lumen cable apparatus |
US5154705A (en) * | 1987-09-30 | 1992-10-13 | Lake Region Manufacturing Co., Inc. | Hollow lumen cable apparatus |
US6685696B2 (en) | 1987-09-30 | 2004-02-03 | Lake Region Manufacturing, Inc. | Hollow lumen cable apparatus |
US4846152A (en) * | 1987-11-24 | 1989-07-11 | Nimbus Medical, Inc. | Single-stage axial flow blood pump |
US4817586A (en) * | 1987-11-24 | 1989-04-04 | Nimbus Medical, Inc. | Percutaneous bloom pump with mixed-flow output |
AU2807389A (en) * | 1987-12-07 | 1989-07-05 | Nimbus Medical, Inc. | Inflow cannula for intravascular blood pumps |
US4895557A (en) * | 1987-12-07 | 1990-01-23 | Nimbus Medical, Inc. | Drive mechanism for powering intravascular blood pumps |
US5061256A (en) * | 1987-12-07 | 1991-10-29 | Johnson & Johnson | Inflow cannula for intravascular blood pumps |
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 |
US4895560A (en) * | 1988-03-31 | 1990-01-23 | Papantonakos Apostolos C | Angioplasty apparatus |
US4906229A (en) * | 1988-05-03 | 1990-03-06 | Nimbus Medical, Inc. | High-frequency transvalvular axisymmetric blood pump |
US4908012A (en) * | 1988-08-08 | 1990-03-13 | Nimbus Medical, Inc. | Chronic ventricular assist system |
US4964864A (en) * | 1988-09-27 | 1990-10-23 | American Biomed, Inc. | Heart assist pump |
JPH0653161B2 (en) * | 1988-09-28 | 1994-07-20 | 東洋紡績株式会社 | Circulator |
US4919647A (en) * | 1988-10-13 | 1990-04-24 | Kensey Nash Corporation | Aortically located blood pumping catheter and method of use |
US5112292A (en) * | 1989-01-09 | 1992-05-12 | American Biomed, Inc. | Helifoil pump |
US4969865A (en) * | 1989-01-09 | 1990-11-13 | American Biomed, Inc. | Helifoil pump |
US4944722A (en) * | 1989-02-23 | 1990-07-31 | Nimbus Medical, Inc. | Percutaneous axial flow blood pump |
US4995857A (en) * | 1989-04-07 | 1991-02-26 | Arnold John R | Left ventricular assist device and method for temporary and permanent procedures |
US5049134A (en) * | 1989-05-08 | 1991-09-17 | The Cleveland Clinic Foundation | Sealless heart pump |
US5324177A (en) * | 1989-05-08 | 1994-06-28 | The Cleveland Clinic Foundation | Sealless rotodynamic pump with radially offset rotor |
US4927407A (en) * | 1989-06-19 | 1990-05-22 | Regents Of The University Of Minnesota | Cardiac assist pump with steady rate supply of fluid lubricant |
US5040944A (en) * | 1989-09-11 | 1991-08-20 | Cook Einar P | Pump having impeller rotational about convoluted stationary member |
US5098256A (en) * | 1989-11-21 | 1992-03-24 | The Cleveland Clinic Foundation | Viscous seal blood pump |
US5308319A (en) * | 1989-12-28 | 1994-05-03 | Sumitmo Bakelite Company Limited | Cardio assist system and insertion device therefor |
US5118264A (en) * | 1990-01-11 | 1992-06-02 | The Cleveland Clinic Foundation | Purge flow control in rotary blood pumps |
US5145333A (en) * | 1990-03-01 | 1992-09-08 | The Cleveland Clinic Foundation | Fluid motor driven blood pump |
JPH0636821B2 (en) * | 1990-03-08 | 1994-05-18 | 健二 山崎 | Implantable auxiliary artificial heart |
US5092844A (en) * | 1990-04-10 | 1992-03-03 | Mayo Foundation For Medical Education And Research | Intracatheter perfusion pump apparatus and method |
US5112200A (en) * | 1990-05-29 | 1992-05-12 | Nu-Tech Industries, Inc. | Hydrodynamically suspended rotor axial flow blood pump |
US5211546A (en) * | 1990-05-29 | 1993-05-18 | Nu-Tech Industries, Inc. | Axial flow blood pump with hydrodynamically suspended rotor |
IT1243345B (en) * | 1990-07-16 | 1994-06-10 | Dideco Spa | CENTRIFUGAL PUMP FOR LIQUID, IN PARTICULAR BLOOD IN EXTRA-BODY CIRCULATION |
US5205721A (en) * | 1991-02-13 | 1993-04-27 | Nu-Tech Industries, Inc. | Split stator for motor/blood pump |
US5295958A (en) * | 1991-04-04 | 1994-03-22 | Shturman Cardiology Systems, Inc. | Method and apparatus for in vivo heart valve decalcification |
US5300112A (en) * | 1992-07-14 | 1994-04-05 | Aai Corporation | Articulated heart pump |
US5344443A (en) * | 1992-09-17 | 1994-09-06 | Rem Technologies, Inc. | Heart pump |
DE69229964T2 (en) * | 1992-10-19 | 2000-01-27 | Cleveland Clinic Foundation Cl | UNLOCKED ROTODYNAMIC PUMP |
US5376114A (en) * | 1992-10-30 | 1994-12-27 | Jarvik; Robert | Cannula pumps for temporary cardiac support and methods of their application and use |
JPH06346917A (en) * | 1993-06-03 | 1994-12-20 | Shicoh Eng Co Ltd | Pressure-proof water-proof sealing system using unidirectional dynamic pressure bearing |
US5368438A (en) * | 1993-06-28 | 1994-11-29 | Baxter International Inc. | Blood pump |
US5957672A (en) * | 1993-11-10 | 1999-09-28 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Blood pump bearing system |
US5947892A (en) * | 1993-11-10 | 1999-09-07 | Micromed Technology, Inc. | Rotary blood pump |
US5527159A (en) * | 1993-11-10 | 1996-06-18 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Rotary blood pump |
US5613935A (en) * | 1994-12-16 | 1997-03-25 | Jarvik; Robert | High reliability cardiac assist system |
US5643215A (en) * | 1995-02-24 | 1997-07-01 | The Research Foundation Of State University Of New York | Gas exchange apparatus and method |
US5707218A (en) * | 1995-04-19 | 1998-01-13 | Nimbus, Inc. | Implantable electric axial-flow blood pump with blood cooled bearing |
US5588812A (en) * | 1995-04-19 | 1996-12-31 | Nimbus, Inc. | Implantable electric axial-flow blood pump |
DE19535781C2 (en) | 1995-09-26 | 1999-11-11 | Fraunhofer Ges Forschung | Device for active flow support of body fluids |
US5824070A (en) * | 1995-10-30 | 1998-10-20 | Jarvik; Robert | Hybrid flow blood pump |
US5695471A (en) * | 1996-02-20 | 1997-12-09 | Kriton Medical, Inc. | Sealless rotary blood pump with passive magnetic radial bearings and blood immersed axial bearings |
US5840070A (en) | 1996-02-20 | 1998-11-24 | Kriton Medical, Inc. | Sealless rotary blood pump |
DE19613565C1 (en) * | 1996-04-04 | 1997-07-24 | Guenter Prof Dr Rau | Intravasal blood pump with drive motor |
US5911685A (en) * | 1996-04-03 | 1999-06-15 | Guidant Corporation | Method and apparatus for cardiac blood flow assistance |
DE19613564C1 (en) | 1996-04-04 | 1998-01-08 | Guenter Prof Dr Rau | Intravascular blood pump |
US5814011A (en) * | 1996-04-25 | 1998-09-29 | Medtronic, Inc. | Active intravascular lung |
US5746709A (en) * | 1996-04-25 | 1998-05-05 | Medtronic, Inc. | Intravascular pump and bypass assembly and method for using the same |
US6015272A (en) | 1996-06-26 | 2000-01-18 | University Of Pittsburgh | Magnetically suspended miniature fluid pump and method of designing the same |
US6244835B1 (en) | 1996-06-26 | 2001-06-12 | James F. Antaki | Blood pump having a magnetically suspended rotor |
US5851174A (en) * | 1996-09-17 | 1998-12-22 | Robert Jarvik | Cardiac support device |
WO1998014225A2 (en) | 1996-10-04 | 1998-04-09 | United States Surgical Corporation | Circulatory support system |
US5964694A (en) * | 1997-04-02 | 1999-10-12 | Guidant Corporation | Method and apparatus for cardiac blood flow assistance |
US7027869B2 (en) | 1998-01-07 | 2006-04-11 | Asthmatx, Inc. | Method for treating an asthma attack |
US6634363B1 (en) | 1997-04-07 | 2003-10-21 | Broncus Technologies, Inc. | Methods of treating lungs having reversible obstructive pulmonary disease |
US6273907B1 (en) | 1997-04-07 | 2001-08-14 | Broncus Technologies, Inc. | Bronchial stenter |
US6283988B1 (en) | 1997-04-07 | 2001-09-04 | Broncus Technologies, Inc. | Bronchial stenter having expandable electrodes |
US6488673B1 (en) | 1997-04-07 | 2002-12-03 | Broncus Technologies, Inc. | Method of increasing gas exchange of a lung |
US7992572B2 (en) | 1998-06-10 | 2011-08-09 | Asthmatx, Inc. | Methods of evaluating individuals having reversible obstructive pulmonary disease |
US6200333B1 (en) | 1997-04-07 | 2001-03-13 | Broncus Technologies, Inc. | Bronchial stenter |
US5972026A (en) | 1997-04-07 | 1999-10-26 | Broncus Technologies, Inc. | Bronchial stenter having diametrically adjustable electrodes |
AUPO902797A0 (en) * | 1997-09-05 | 1997-10-02 | Cortronix Pty Ltd | A rotary blood pump with hydrodynamically suspended impeller |
US6048363A (en) * | 1997-05-13 | 2000-04-11 | Nagyszalanczy; Lorant | Centrifugal blood pump apparatus |
US6395026B1 (en) | 1998-05-15 | 2002-05-28 | A-Med Systems, Inc. | Apparatus and methods for beating heart bypass surgery |
US6532964B2 (en) * | 1997-07-11 | 2003-03-18 | A-Med Systems, Inc. | Pulmonary and circulatory blood flow support devices and methods for heart surgery procedures |
US7182727B2 (en) | 1997-07-11 | 2007-02-27 | A—Med Systems Inc. | Single port cardiac support apparatus |
US6250880B1 (en) * | 1997-09-05 | 2001-06-26 | Ventrassist Pty. Ltd | Rotary pump with exclusively hydrodynamically suspended impeller |
US6889082B2 (en) | 1997-10-09 | 2005-05-03 | Orqis Medical Corporation | Implantable heart assist system and method of applying same |
UA56262C2 (en) | 1997-10-09 | 2003-05-15 | Орквіс Медікел Корпорейшн | Extracardiac pumping system for supplementing blood circulation |
US6390969B1 (en) | 1997-10-09 | 2002-05-21 | Orqis Medical Corporation | Implantable heart assist system and method of applying same |
US6387037B1 (en) | 1997-10-09 | 2002-05-14 | Orqis Medical Corporation | 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 |
US6120537A (en) * | 1997-12-23 | 2000-09-19 | Kriton Medical, Inc. | Sealless blood pump with means for avoiding thrombus formation |
US7921855B2 (en) | 1998-01-07 | 2011-04-12 | Asthmatx, Inc. | Method for treating an asthma attack |
US7371254B2 (en) | 1998-01-23 | 2008-05-13 | Innercool Therapies, Inc. | Medical procedure |
US6491039B1 (en) | 1998-01-23 | 2002-12-10 | Innercool Therapies, Inc. | Medical procedure |
US7198635B2 (en) | 2000-10-17 | 2007-04-03 | Asthmatx, Inc. | Modification of airways by application of energy |
US8181656B2 (en) | 1998-06-10 | 2012-05-22 | Asthmatx, Inc. | Methods for treating airways |
AU4690699A (en) | 1998-06-19 | 2000-01-05 | A-Med Systems, Inc. | Apparatus and methods for entering cavities of the body |
US6050987A (en) * | 1998-09-21 | 2000-04-18 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Tubular coupling |
US6152704A (en) * | 1998-09-30 | 2000-11-28 | A-Med Systems, Inc. | Blood pump with turbine drive |
US6210133B1 (en) | 1998-09-30 | 2001-04-03 | A-Med Systems, Inc. | Blood pump with sterile motor housing |
US6217541B1 (en) | 1999-01-19 | 2001-04-17 | Kriton Medical, Inc. | Blood pump using cross-flow principles |
US20020128587A1 (en) * | 1999-01-13 | 2002-09-12 | A-Med Systems, Inc. | Pulmonary and circulatory blood flow support devices and methods for heart surgery procedures |
US6018208A (en) * | 1999-01-26 | 2000-01-25 | Nimbus, Inc. | Articulated motor stator assembly for a pump |
US6245007B1 (en) | 1999-01-28 | 2001-06-12 | Terumo Cardiovascular Systems Corporation | Blood pump |
DE20007581U1 (en) * | 1999-04-20 | 2000-10-19 | Mediport Kardiotechnik Gmbh | Device for the axial conveyance of fluid media |
AUPP995999A0 (en) | 1999-04-23 | 1999-05-20 | University Of Technology, Sydney | Non-contact estimation and control system |
US6234772B1 (en) | 1999-04-28 | 2001-05-22 | Kriton Medical, Inc. | Rotary blood pump |
US7022100B1 (en) | 1999-09-03 | 2006-04-04 | A-Med Systems, Inc. | Guidable intravascular blood pump and related methods |
JP4159781B2 (en) * | 1999-09-03 | 2008-10-01 | エイ−メド システムズ, インコーポレイテッド | Guideable intravascular blood pump and related methods |
US8251070B2 (en) | 2000-03-27 | 2012-08-28 | Asthmatx, Inc. | Methods for treating airways |
JP2003530185A (en) | 2000-03-31 | 2003-10-14 | インナークール セラピーズ, インコーポレイテッド | Medical law |
US6592612B1 (en) * | 2000-05-04 | 2003-07-15 | Cardeon Corporation | Method and apparatus for providing heat exchange within a catheter body |
US7104987B2 (en) | 2000-10-17 | 2006-09-12 | Asthmatx, Inc. | Control system and process for application of energy to airway walls and other mediums |
US7366754B2 (en) * | 2001-06-29 | 2008-04-29 | Thomson Licensing | Multi-media jitter removal in an asynchronous digital home network |
EP1412022B1 (en) | 2001-07-27 | 2005-04-13 | Impella Cardiotechnik AG | Neurostimulation unit for immobilizing the heart during cardiosurgical operations |
DE10155011B4 (en) * | 2001-11-02 | 2005-11-24 | Impella Cardiosystems Ag | Intra-aortic pump |
CA2374989A1 (en) * | 2002-03-08 | 2003-09-08 | Andre Garon | Ventricular assist device comprising a dual inlet hybrid flow blood pump |
US6936222B2 (en) * | 2002-09-13 | 2005-08-30 | Kenneth L. Franco | Methods, apparatuses, and applications for compliant membrane blood gas exchangers |
CA2428741A1 (en) * | 2003-05-13 | 2004-11-13 | Cardianove Inc. | Dual inlet mixed-flow blood pump |
US20040226556A1 (en) | 2003-05-13 | 2004-11-18 | Deem Mark E. | Apparatus for treating asthma using neurotoxin |
US7416525B2 (en) | 2003-09-18 | 2008-08-26 | Myrakelle, Llc | Rotary blood pump |
US7070398B2 (en) * | 2003-09-25 | 2006-07-04 | Medforte Research Foundation | Axial-flow blood pump with magnetically suspended, radially and axially stabilized impeller |
US7229258B2 (en) * | 2003-09-25 | 2007-06-12 | Medforte Research Foundation | Streamlined unobstructed one-pass axial-flow pump |
US7445592B2 (en) | 2004-06-10 | 2008-11-04 | Orqis Medical Corporation | Cannulae having reduced flow resistance |
DE602005023886D1 (en) | 2004-08-13 | 2010-11-11 | Delgado Reynolds M | IKELS WHILE PUMPING BLOOD |
US7393181B2 (en) | 2004-09-17 | 2008-07-01 | The Penn State Research Foundation | Expandable impeller pump |
US8419609B2 (en) | 2005-10-05 | 2013-04-16 | Heartware Inc. | Impeller for a rotary ventricular assist device |
US7699586B2 (en) * | 2004-12-03 | 2010-04-20 | Heartware, Inc. | Wide blade, axial flow pump |
US7972122B2 (en) * | 2005-04-29 | 2011-07-05 | Heartware, Inc. | Multiple rotor, wide blade, axial flow pump |
US7479102B2 (en) * | 2005-02-28 | 2009-01-20 | Robert Jarvik | Minimally invasive transvalvular ventricular assist device |
CA2611313A1 (en) | 2005-06-06 | 2006-12-14 | The Cleveland Clinic Foundation | Blood pump |
JP4209412B2 (en) * | 2005-09-13 | 2009-01-14 | 三菱重工業株式会社 | Artificial heart pump |
US8672611B2 (en) | 2006-01-13 | 2014-03-18 | Heartware, Inc. | Stabilizing drive for contactless rotary blood pump impeller |
EP1977110B8 (en) | 2006-01-13 | 2018-12-26 | HeartWare, Inc. | Rotary blood pump |
AU2007230945B2 (en) | 2006-03-23 | 2013-05-02 | The Penn State Research Foundation | Heart assist device with expandable impeller pump |
WO2007115222A2 (en) | 2006-03-31 | 2007-10-11 | Orqis Medical Corporation | Rotary blood pump |
WO2007140481A2 (en) * | 2006-05-31 | 2007-12-06 | Richard Wampler | Heart assist device |
US7914436B1 (en) | 2006-06-12 | 2011-03-29 | Abiomed, Inc. | Method and apparatus for pumping blood |
US9028392B2 (en) * | 2006-12-01 | 2015-05-12 | NuCardia, Inc. | Medical device |
US7828710B2 (en) * | 2007-06-05 | 2010-11-09 | Medical Value Partners, Llc | Apparatus comprising a drive cable for a medical device |
US8079948B2 (en) * | 2007-08-29 | 2011-12-20 | NuCardia, Inc. | Article comprising an impeller |
DE502007005015C5 (en) * | 2007-10-08 | 2020-02-20 | Ais Gmbh Aachen Innovative Solutions | Catheter device |
US8489190B2 (en) | 2007-10-08 | 2013-07-16 | Ais Gmbh Aachen Innovative Solutions | Catheter device |
US8439859B2 (en) | 2007-10-08 | 2013-05-14 | Ais Gmbh Aachen Innovative Solutions | Catheter device |
JP4523962B2 (en) * | 2007-11-26 | 2010-08-11 | 三菱重工業株式会社 | Artificial heart pump |
JP4611365B2 (en) * | 2007-11-26 | 2011-01-12 | 三菱重工業株式会社 | Artificial heart pump |
US20110106115A1 (en) * | 2008-01-18 | 2011-05-05 | Med Institute, Inc. | Intravascular device attachment system having struts |
WO2009100336A1 (en) * | 2008-02-07 | 2009-08-13 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Intracorporeal gas exchange devices, systems and methods |
EP2249746B1 (en) * | 2008-02-08 | 2018-10-03 | Heartware, Inc. | Ventricular assist device for intraventricular placement |
US8483831B1 (en) | 2008-02-15 | 2013-07-09 | Holaira, Inc. | System and method for bronchial dilation |
EP2662046B1 (en) | 2008-05-09 | 2023-03-15 | Nuvaira, Inc. | Systems and assemblies for treating a bronchial tree |
US9180235B2 (en) * | 2008-10-10 | 2015-11-10 | Peter Forsell | Heart help pump, system and method |
EP2248544A1 (en) * | 2009-05-05 | 2010-11-10 | ECP Entwicklungsgesellschaft mbH | Fluid pump with variable circumference, particularly for medical use |
US8535211B2 (en) | 2009-07-01 | 2013-09-17 | Thoratec Corporation | Blood pump with expandable cannula |
EP2314330A1 (en) * | 2009-10-23 | 2011-04-27 | ECP Entwicklungsgesellschaft mbH | Flexible shaft arrangement |
CN107049479B (en) | 2009-10-27 | 2020-10-16 | 努瓦拉公司 | Delivery device with coolable energy emitting assembly |
US8690749B1 (en) | 2009-11-02 | 2014-04-08 | Anthony Nunez | Wireless compressible heart pump |
EP2496281A2 (en) * | 2009-11-04 | 2012-09-12 | Richard Wampler | Methods and devices for treating heart failure |
KR101820542B1 (en) | 2009-11-11 | 2018-01-19 | 호라이라 인코포레이티드 | Systems, apparatuses, and methods for treating tissue and controlling stenosis |
US8911439B2 (en) | 2009-11-11 | 2014-12-16 | Holaira, Inc. | Non-invasive and minimally invasive denervation methods and systems for performing the same |
EP2627366B1 (en) | 2010-10-13 | 2016-08-31 | Thoratec Corporation | Blood pump |
WO2012054490A1 (en) * | 2010-10-18 | 2012-04-26 | World Heart Corporation | Blood pump with splitter impeller blades and splitter stator vanes and methods of manufacturing |
US8485961B2 (en) | 2011-01-05 | 2013-07-16 | Thoratec Corporation | Impeller housing for percutaneous heart pump |
US8597170B2 (en) | 2011-01-05 | 2013-12-03 | Thoratec Corporation | Catheter pump |
US8591393B2 (en) | 2011-01-06 | 2013-11-26 | Thoratec Corporation | Catheter pump |
US9138518B2 (en) | 2011-01-06 | 2015-09-22 | Thoratec Corporation | Percutaneous heart pump |
DE112012004282T5 (en) | 2011-10-13 | 2014-07-03 | Thoratec Corporation | PUMP AND METHOD FOR THE HYDRAULIC PUMPING OF BLOOD |
US20130138205A1 (en) | 2011-11-28 | 2013-05-30 | MI-VAD, Inc. | Ventricular assist device and method |
EP2822614B1 (en) | 2012-03-05 | 2016-12-28 | Thoratec Corporation | Modular implantable medical pump |
US9572915B2 (en) | 2012-03-26 | 2017-02-21 | Procyrion, Inc. | Systems and methods for fluid flows and/or pressures for circulation and perfusion enhancement |
US9327067B2 (en) | 2012-05-14 | 2016-05-03 | Thoratec Corporation | Impeller for catheter pump |
GB2504176A (en) | 2012-05-14 | 2014-01-22 | Thoratec Corp | Collapsible impeller for catheter pump |
US9446179B2 (en) | 2012-05-14 | 2016-09-20 | Thoratec Corporation | Distal bearing support |
US8721517B2 (en) | 2012-05-14 | 2014-05-13 | Thoratec Corporation | Impeller for catheter pump |
US9872947B2 (en) | 2012-05-14 | 2018-01-23 | Tc1 Llc | Sheath system for catheter pump |
WO2013184319A1 (en) | 2012-06-04 | 2013-12-12 | Boston Scientific Scimed, Inc. | Systems and methods for treating tissue of a passageway within a body |
EP4186557A1 (en) | 2012-07-03 | 2023-05-31 | Tc1 Llc | Motor assembly for catheter pump |
US9421311B2 (en) | 2012-07-03 | 2016-08-23 | Thoratec Corporation | Motor assembly for catheter pump |
US9358329B2 (en) | 2012-07-03 | 2016-06-07 | Thoratec Corporation | Catheter pump |
WO2014018153A1 (en) | 2012-07-24 | 2014-01-30 | Boston Scientific Scimed, Inc. | Electrodes for tissue treatment |
US9272132B2 (en) | 2012-11-02 | 2016-03-01 | Boston Scientific Scimed, Inc. | Medical device for treating airways and related methods of use |
WO2014071372A1 (en) | 2012-11-05 | 2014-05-08 | Boston Scientific Scimed, Inc. | Devices for delivering energy to body lumens |
US9398933B2 (en) | 2012-12-27 | 2016-07-26 | Holaira, Inc. | Methods for improving drug efficacy including a combination of drug administration and nerve modulation |
US11033728B2 (en) | 2013-03-13 | 2021-06-15 | Tc1 Llc | Fluid handling system |
WO2014164136A1 (en) | 2013-03-13 | 2014-10-09 | Thoratec Corporation | Fluid handling system |
US9144638B2 (en) | 2013-03-14 | 2015-09-29 | Thoratec Corporation | Blood pump rotor bearings |
EP2968742B1 (en) * | 2013-03-15 | 2020-12-02 | Tc1 Llc | Catheter pump assembly including a stator |
US9308302B2 (en) | 2013-03-15 | 2016-04-12 | Thoratec Corporation | Catheter pump assembly including a stator |
US10111994B2 (en) * | 2013-05-14 | 2018-10-30 | Heartware, Inc. | Blood pump with separate mixed-flow and axial-flow impeller stages and multi-stage stators |
CA2913220A1 (en) | 2013-08-09 | 2015-02-12 | Boston Scientific Scimed, Inc. | Expandable catheter and related methods of manufacture and use |
AU2015223169B2 (en) | 2014-02-25 | 2019-08-29 | Zain KHALPEY | Ventricular assist device and method |
WO2015160943A1 (en) | 2014-04-15 | 2015-10-22 | Thoratec Corporation | Sensors for catheter pumps |
WO2015160942A1 (en) | 2014-04-15 | 2015-10-22 | Thoratec Corporation | Catheter pump with off-set motor position |
WO2015160990A1 (en) | 2014-04-15 | 2015-10-22 | Thoratec Corporation | Catheter pump introducer systems and methods |
WO2015160979A1 (en) | 2014-04-15 | 2015-10-22 | Thoratec Corporation | Catheter pump with access ports |
US10293090B2 (en) | 2014-04-25 | 2019-05-21 | Yale University | Percutaneous device and method for promoting movement of a bodily fluid |
EP3583973A1 (en) | 2014-08-18 | 2019-12-25 | Tc1 Llc | Guide features for percutaneous catheter pump |
WO2016086137A1 (en) | 2014-11-26 | 2016-06-02 | Thoratec Corporation | Pump and method for mixed flow blood pumping |
WO2016118777A1 (en) | 2015-01-22 | 2016-07-28 | Thoratec Corporation | Reduced rotational mass motor assembly for catheter pump |
EP3804797A1 (en) | 2015-01-22 | 2021-04-14 | Tc1 Llc | Motor assembly with heat exchanger for catheter pump |
US9675738B2 (en) | 2015-01-22 | 2017-06-13 | Tc1 Llc | Attachment mechanisms for motor of catheter pump |
US9907890B2 (en) | 2015-04-16 | 2018-03-06 | Tc1 Llc | Catheter pump with positioning brace |
FR3040304B1 (en) * | 2015-08-25 | 2020-11-13 | Fineheart | BLOOD FLOW PUMP FOR VENTRICULAR ASSISTANCE |
AU2016325720B2 (en) | 2015-09-25 | 2021-06-24 | Procyrion, Inc. | Non-occluding intravascular blood pump providing reduced hemolysis |
EP3153191A1 (en) | 2015-10-09 | 2017-04-12 | ECP Entwicklungsgesellschaft mbH | Blood pump |
US11160970B2 (en) | 2016-07-21 | 2021-11-02 | Tc1 Llc | Fluid seals for catheter pump motor assembly |
US10857273B2 (en) | 2016-07-21 | 2020-12-08 | Tc1 Llc | Rotary seal for cantilevered rotor pump and methods for axial flow blood pumping |
EP3808402A1 (en) | 2016-07-21 | 2021-04-21 | Tc1 Llc | Gas-filled chamber for catheter pump motor assembly |
WO2018031741A1 (en) | 2016-08-12 | 2018-02-15 | Tc1 Llc | Devices and methods for monitoring bearing and seal performance |
WO2018067410A1 (en) | 2016-10-03 | 2018-04-12 | Queen Mary University Of London | Mechanical circulatory support device with axial flow turbomachine optimized for heart failure and cardio-renal syndrome |
EP3532120A1 (en) | 2016-10-25 | 2019-09-04 | Magenta Medical Ltd. | Ventricular assist device |
EP3606575B1 (en) * | 2017-04-07 | 2022-09-14 | ECP Entwicklungsgesellschaft mbH | External drive unit for an implantable heart assist pump |
WO2018223060A1 (en) | 2017-06-01 | 2018-12-06 | Queen Mary University Of London | Mechanical circulatory support device with centrifugal impeller designed for implantation in the descending aorta |
EP3634528B1 (en) | 2017-06-07 | 2023-06-07 | Shifamed Holdings, LLC | Intravascular fluid movement devices, systems, and methods of use |
EP3710076B1 (en) | 2017-11-13 | 2023-12-27 | Shifamed Holdings, LLC | Intravascular fluid movement devices, systems, and methods of use |
US10905808B2 (en) | 2018-01-10 | 2021-02-02 | Magenta Medical Ltd. | Drive cable for use with a blood pump |
CN115040777A (en) | 2018-01-10 | 2022-09-13 | 马真塔医药有限公司 | Ventricular assist device |
DE102018201030A1 (en) | 2018-01-24 | 2019-07-25 | Kardion Gmbh | Magnetic coupling element with magnetic bearing function |
EP3746149A4 (en) | 2018-02-01 | 2021-10-27 | Shifamed Holdings, LLC | Intravascular blood pumps and methods of use and manufacture |
US11116959B2 (en) | 2018-04-04 | 2021-09-14 | Theodosios Alexander | Removable mechanical circulatory support for short term use |
US11020582B2 (en) | 2018-04-20 | 2021-06-01 | Cardiovascular Systems, Inc. | Intravascular pump with expandable region |
US11110264B2 (en) | 2018-04-20 | 2021-09-07 | Cardiovascular Systems, Inc. | Intravascular pump with expandable distal region |
US11167121B2 (en) | 2018-05-15 | 2021-11-09 | Cardiovascular Systems, Inc. | Intravascular pump with integrated isolated conductor(s) and methods thereof |
DE102018208541A1 (en) * | 2018-05-30 | 2019-12-05 | Kardion Gmbh | Axial pump for a cardiac assist system and method of making an axial pump for a cardiac assist system |
EP3810219A2 (en) | 2018-06-25 | 2021-04-28 | Ballout, Bashar | Percutaneous blood pump and introducer system |
DE102018211327A1 (en) | 2018-07-10 | 2020-01-16 | Kardion Gmbh | Impeller for an implantable vascular support system |
US11013904B2 (en) | 2018-07-30 | 2021-05-25 | Cardiovascular Systems, Inc. | Intravascular pump with proximal and distal pressure or flow sensors and distal sensor tracking |
US11202900B2 (en) | 2018-07-31 | 2021-12-21 | Cardiovascular Systems, Inc. | Intravascular pump with controls and display screen on handle |
EP3749383B1 (en) | 2019-01-24 | 2021-04-28 | Magenta Medical Ltd. | Ventricular assist device |
US11654275B2 (en) | 2019-07-22 | 2023-05-23 | Shifamed Holdings, Llc | Intravascular blood pumps with struts and methods of use and manufacture |
WO2021062265A1 (en) | 2019-09-25 | 2021-04-01 | Shifamed Holdings, Llc | Intravascular blood pump systems and methods of use and control thereof |
WO2021113389A1 (en) | 2019-12-03 | 2021-06-10 | Procyrion, Inc. | Blood pumps |
CA3160964A1 (en) | 2019-12-13 | 2021-06-17 | Procyrion, Inc. | Support structures for intravascular blood pumps |
DE102020102474A1 (en) | 2020-01-31 | 2021-08-05 | Kardion Gmbh | Pump for conveying a fluid and method for manufacturing a pump |
CN113476738B (en) * | 2021-06-07 | 2022-11-08 | 浙江迪远医疗器械有限公司 | Blood pump with detection device |
Family Cites Families (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US967512A (en) * | 1909-04-21 | 1910-08-16 | William B Gregory | Means for measuring water for irrigation purposes. |
US2328199A (en) * | 1942-04-28 | 1943-08-31 | Harry S Day | Embalming apparatus |
US2738920A (en) * | 1950-12-23 | 1956-03-20 | Gen Motors Corp | Gas turbine engine with thrust balancing coupling |
US3021793A (en) * | 1959-12-09 | 1962-02-20 | Honeywell Regulator Co | Fluid pump |
GB1235321A (en) * | 1968-01-30 | 1971-06-09 | Nat Res Dev | Improvements in or relating to drills for clearing obstructions |
US3667069A (en) * | 1970-03-27 | 1972-06-06 | Univ Minnesota | Jet pump cardiac replacement and assist device and method of at least partially replacing a disabled right heart |
US3720200A (en) * | 1971-10-28 | 1973-03-13 | Avco Corp | Intra-arterial blood pump |
US3877838A (en) * | 1973-08-09 | 1975-04-15 | Daniel S J Choy | Device for advancing material through a tube |
DE2423673A1 (en) * | 1974-05-15 | 1975-11-27 | Juan N Walterspiel | Peristaltic pump for heart - preventing damage to blood uses sequenced set of valves for oil surrounding tube |
JPS5944519B2 (en) * | 1975-09-12 | 1984-10-30 | 工業技術院長 | axial blower |
US4077394A (en) * | 1976-08-25 | 1978-03-07 | Mccurdy Martin D | Integral pressure sensor probe for a cardiac assistance device |
US4135253A (en) * | 1976-11-30 | 1979-01-23 | Medtronic, Inc. | Centrifugal blood pump for cardiac assist |
US4173796A (en) * | 1977-12-09 | 1979-11-13 | University Of Utah | Total artificial hearts and cardiac assist devices powered and controlled by reversible electrohydraulic energy converters |
US4310930A (en) * | 1979-11-28 | 1982-01-19 | U.S. Philips Corporation | Rigid-vane artifical heart |
US4382199A (en) * | 1980-11-06 | 1983-05-03 | Nu-Tech Industries, Inc. | Hydrodynamic bearing system for a brushless DC motor |
US4417850A (en) * | 1982-12-20 | 1983-11-29 | Allis-Chalmers Corporation | Vertical column pump |
-
1983
- 1983-09-28 US US06/537,244 patent/US4625712A/en not_active Expired - Lifetime
-
1984
- 1984-09-25 CA CA000463995A patent/CA1240802A/en not_active Expired
- 1984-09-28 DE DE8484903827T patent/DE3482656D1/en not_active Expired - Fee Related
- 1984-09-28 BR BR8407086A patent/BR8407086A/en not_active IP Right Cessation
- 1984-09-28 WO PCT/US1984/001559 patent/WO1985001432A1/en active IP Right Grant
- 1984-09-28 EP EP84903827A patent/EP0157871B1/en not_active Expired - Lifetime
- 1984-09-28 JP JP59503865A patent/JPS61500059A/en active Granted
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6123725A (en) | 1997-07-11 | 2000-09-26 | A-Med Systems, Inc. | Single port cardiac support apparatus |
Also Published As
Publication number | Publication date |
---|---|
DE3482656D1 (en) | 1990-08-09 |
JPS61500059A (en) | 1986-01-16 |
EP0157871B1 (en) | 1990-07-04 |
EP0157871A1 (en) | 1985-10-16 |
JPH0531423B2 (en) | 1993-05-12 |
BR8407086A (en) | 1985-08-13 |
WO1985001432A1 (en) | 1985-04-11 |
EP0157871A4 (en) | 1987-09-08 |
US4625712A (en) | 1986-12-02 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA1240802A (en) | High-capacity intravascular blood pump utilizing percutaneous access | |
Reul et al. | Blood pumps for circulatory support | |
US5964694A (en) | Method and apparatus for cardiac blood flow assistance | |
US5755784A (en) | Cannula pumps for temporary cardiac support and methods of their application and use | |
US5911685A (en) | Method and apparatus for cardiac blood flow assistance | |
US6176848B1 (en) | Intravascular blood pump | |
AU699959B2 (en) | Blood pump device and method of producing | |
US9616157B2 (en) | Blood pump | |
US6508787B2 (en) | System for actively supporting the flow of body fluids | |
US20100152526A1 (en) | Blood pump device and method of producing | |
CN114215792B (en) | Micropump with totally-enclosed cleaning fluid circulation system | |
Sieß et al. | Concept, realization, and first in vitro testing of an intraarterial microaxial blood pump | |
CN111097077B (en) | External magnetic drive liquid suspension axial-flow type blood pump | |
CN116966415A (en) | Ventricular assist device | |
JPH04176471A (en) | Circulation auxiliary pump | |
JP2004057817A (en) | Blood pump with impeller | |
US20120035645A1 (en) | Dynamic and static blood filters | |
CN214837904U (en) | Bearing seat structure | |
US20230201561A1 (en) | Re-sealable member of distal bearing support | |
WO2024037203A1 (en) | Interventional blood pump | |
Akdis et al. | Mechanical blood pumps for cardiac assistance | |
Aber et al. | Development of the NASA/Baylor VAD | |
Reul et al. | Rotary blood pumps in circulatory assist |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
MKEX | Expiry |