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US20180207334A1 - Intracardiac pumping device - Google Patents

Intracardiac pumping device Download PDF

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Publication number
US20180207334A1
US20180207334A1 US15/876,346 US201815876346A US2018207334A1 US 20180207334 A1 US20180207334 A1 US 20180207334A1 US 201815876346 A US201815876346 A US 201815876346A US 2018207334 A1 US2018207334 A1 US 2018207334A1
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United States
Prior art keywords
pumping device
pump
blood
cannula
heart
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.)
Abandoned
Application number
US15/876,346
Inventor
Thorsten Siess
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Abiomed Europe GmbH
Original Assignee
Abiomed Europe GmbH
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Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=32731194&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=US20180207334(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Abiomed Europe GmbH filed Critical Abiomed Europe GmbH
Priority to US15/876,346 priority Critical patent/US20180207334A1/en
Assigned to IMPELLA CARDIOSYSTEMS GMBH reassignment IMPELLA CARDIOSYSTEMS GMBH ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SIESS, THORSTEN
Assigned to ABIOMED EUROPE GMBH reassignment ABIOMED EUROPE GMBH CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: IMPELLA CARDIOSYSTEMS GMBH
Publication of US20180207334A1 publication Critical patent/US20180207334A1/en
Priority to US16/576,912 priority patent/US20200222603A1/en
Priority to US17/014,218 priority patent/US11491320B2/en
Priority to US17/960,988 priority patent/US12023477B2/en
Abandoned legal-status Critical Current

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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
    • A61M60/10—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
    • A61M1/101—
    • 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
    • A61M1/1074—
    • A61M1/125—
    • 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
    • A61M60/10—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
    • 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
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/17—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart inside a ventricle, e.g. intraventricular balloon 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
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood 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
    • A61M60/20—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
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/865—Devices for guiding or inserting pumps or pumping devices into the patient's body
    • A61M1/1008—
    • A61M1/122—
    • 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
    • A61M25/0021—Catheters; Hollow probes characterised by the form of the tubing
    • A61M25/0041—Catheters; Hollow probes characterised by the form of the tubing pre-formed, e.g. specially adapted to fit with the anatomy of body channels
    • 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
    • A61M25/0067—Catheters; Hollow probes characterised by the distal end, e.g. tips
    • A61M25/0068—Static characteristics of the catheter tip, e.g. shape, atraumatic tip, curved tip or tip structure
    • A61M25/0069—Tip not integral with tube

Definitions

  • the invention relates to an intracardiac pumping device adapted to be fully inserted into the heart via adjoining vessels to assist the natural cardiac pump function or to replace the same by a continuous pumping operation.
  • Intracardiac blood pumps inserted percutaneously into a patient's body are highly miniaturized. They comprise a cylindrical drive portion and a cylindrical pump portion. The intake end of the pump portion is provided with a flexible canula having a suction head with lateral inlet openings at the distal end.
  • a pumping device is described in EP 0 916 359 A1 (Impella).
  • Another pumping device conveying in the distal direction is described in WO 99/58170 (Impella).
  • the pumping portion is prolonged by a flexible canula adapted to be passed through a cardiac valve.
  • a catheter projects from the distal end of the canula, at which catheter a balloon is provided which is to be entrained by the blood flow in the body when the pumping device is inserted.
  • a pumping device that takes in blood through a canula and then feeds it proximally can be placed such that it leads through the aortic valve, the suction head at the end of the canula being situated in the left ventricle, while the pump outlet lies in the aorta.
  • the operation of the continually feeding pump is superposed on the pulsating activity of the heart so that the pump is subjected to heavily pulsating pressure variations.
  • the pump, together with the associated proximal catheter is subjected to substantial changes in position.
  • the catheter is pressed against the outer side of the aortic arch, whereas it is pressed against the inner side thereof during a diastole.
  • the position of the pump varies continuously, which may result in displacements of the canula passing through the aortic valve and even in an ejection of the canula which then slips from the cardiac valve into the aorta.
  • suction head may adhere to tissue parts inside the heart by suction. This entails the danger of irritations of the heart and, further, the pumping capacity is reduced by the obstruction of inlet openings. Finally, it may happen that the canula adheres to the mitral valve by suction and an additional damage to the blood is induced by suction.
  • the present pumping device has the features of claim 1 .
  • a flexible projection is provided at the canula distal of the inlet openings.
  • the projection forms a mechanical spacer maintaining a distance to neighboring walls, yet does not change the pumping device hydraulically.
  • the projection has other effects. It increases the mechanical length of the pumping device without increasing the hydraulic length. The increase in mechanical length has the consequence that the pumping device is less likely to slip out through the aortic valve. On the other hand, the hydraulic resistance of the canula is not increased so that the suction performance is not degraded. It is another effect that the projection essentially reduces the tendency of the pumping device to make pulsating motions caused by cardiac pulsation.
  • the pumping device including the pump and the catheter lies much calmer within the heart, whereby also the danger of an ejection is reduced.
  • the distal projection is preferably configured such that a new retrograde passage of the aortic valve is possible easily and reproducibly.
  • the flexible projection is a hollow tube whose lumen is in communication with that of the canula.
  • a pumping device is suited for use with a guide wire.
  • the guide wire may be included as a stiffening means. It is also possible to first place the guide wire and to then slip the pumping device over the same. Eventually, an angled tip of the guide wire may also be pushed out from the projection to serve as a pathfinder through the vascular system.
  • the lumen of the projection is in communication with the lumen of the canula, the pump does not suck through the projection.
  • the inlet openings at the suction head have a much larger cross section than the lumen of the projection so that due to the lower flow resistance the suction is affected for the much greater part through the inlet openings.
  • a certain suction effect caused by the lumen of the projection is so small that it is negligible and is not sufficient to cause adherence by suction to other parts.
  • the projection is unable to adhere by suction.
  • the lumen of the projection be obstructed for some reason, this has no effects on the hydraulic function of the pump.
  • the flexible projection may comprise a pigtail tip as known from catheters and stents.
  • the rounded pigtail tip allows for an atraumatical supporting at heart or vessel walls. Moreover, the tip is so soft and flexible that it adapts to any cavity topology by deforming.
  • the pigtail tip also facilitates the insertion and the placing of the pumping device. Specifically, it can be used in combination with a guide wire, the pigtail tip being stretched by the guide wire during insertion. When the pigtail tip is advanced without the guide wire, a simple and reproducible retrograde passage through the aortic valve is still possible. This is of particular importance since the guide wire is removed for the pump to operate and can not be advanced again without having to remove the pump for that purpose. Should the pump be ejected from the left heart due to the systolic cardiac functions, it may be repositioned even without the wire because of the configuration of the flexible projection as a pigtail.
  • FIG. 1 illustrates the pumping device operating in the heart
  • FIG. 2 illustrates the pumping device in an unused state
  • FIG. 3 shows a section through the suction head with the projection attached thereto
  • FIG. 4 illustrates an embodiment in which the suction head has a flow-shaping inflow funnel
  • FIG. 5 illustrates an embodiment in which the canula comprises a second set of inlet openings at the end of the projection.
  • FIG. 1 illustrates the heart H with the aorta AO branching therefrom.
  • the aorta Via the aortic arch 10 , the aorta passes into a vertical strand that branches into the femoral artery, among others.
  • the pumping device is percutaneously inserted into the femoral artery in the region of the groin and is advanced to the heart.
  • the intracardiac pumping device comprises a pump 11 with a proximal end 12 and a distal end 13 .
  • the pump 11 has a housing with an outer diameter of 4 mm at most and a length of approximately 15 mm so that the pump can be inserted percutaneously and be operated inside the heart. Larger pumps that can only be inserted surgically must not exceed an outer diameter of 6 mm because of the peripheral vessel diameters.
  • the proximal end 12 of the pump 11 is connected with a catheter 14 including the electric wires for the operation and the control of the pump 11 .
  • the distal end 13 is connected with a canula 15 which is an elongate flexible hose forming at its distal end a suction head 16 with lateral inlet openings 17 .
  • the pump 11 draws blood through the inlet openings 17 of the canula 15 and pumps the same through the outlet openings 18 provided in the sides of the pump.
  • the pump and the canula are generally designed as described in EP 0 916 369 A1 (Impella).
  • the canula 15 is a hose with a length of about 40 to 70 mm, whose wall is formed by a coiled wire provided with a polyurethane coating.
  • the canula 15 has a certain form stability, yet it is flexible.
  • the suction head 16 of the canula 15 is adjoined by a projection 20 that extends the canula 15 mechanically, but not hydraulically.
  • the projection 20 has a length of 10 to 30 mm. In the present case, it is provided with a pigtail tip 21 to allow for atraumatic support at body tissue.
  • FIG. 1 shows the extension of the pumping device in the heart H and the aorta AO.
  • the pumping device is placed such that the pump 11 is located in the aorta AO while the suction head 16 lies in the left ventricle LV.
  • the canula 15 extends through the aortic valve AK.
  • FIG. 1 shows the left atrium LA and the mitral valve MK.
  • the pump 11 pumps continuously at a delivery rate of 2 to 3 1/min.
  • the reaction force tends to pull the pump into the heart. This force is countered by the pumping force of the heart.
  • the heart has a fluctuating delivery rate of about 10 1/min. It has been found that the pump moves resulting in a systolic position 25 at the outer side of the aortic arch 10 during the ejection phase of the heart, while, during the filling phase, a diastolic position 26 on the inner side of the aortic arch 10 is obtained. With these movements, the position of the canula 15 and the suction head 16 also changes.
  • Adhering by suction is made more difficult by the projection 20 that is supported at the wall of the heart. Further, the projection 20 forms a mechanical extension of the canula to prevent ejection from the left ventricle and the aortic valve.
  • the pump 11 comprises a motor part 30 and a pump part 31 arranged axially one behind the other.
  • the pump part 31 includes a housing ring and an impeller driven by the motor and feeding the blood flow in the axial direction, the blood flow being deflected outward radially and exiting laterally from the housing of the pump 11 through the outlet openings 18 .
  • the pump part 31 is axially adjoined by the canula 15 having about the same outer diameter (4 mm) as the pump 11 .
  • the suction head 16 with the inlet opening 17 has a length of about 10 to 15 mm.
  • the outlet openings 18 have an area at least as large as the cross-section area of the canula lumen so that the suction head forms no constriction.
  • the projection 20 is designed as a hollow hose with a continuous lumen 32 .
  • the width of this lumen is much smaller than that of the canula lumen.
  • the lumen 32 serves to pass a guide wire 33 therethrough to facilitate the insertion of the pumping device into the body.
  • the guide wire 33 extends the projection 20 if the same has a preformed bend.
  • the guide wire may also have a soft flexible bent tip protruding from the distal end of the projection 20 and serving as a pathfinder through the vascular system.
  • the guide wire 33 leads into the pump 11 , through the pump part 31 and out from an outlet opening 18 . It is then guided along the outside of the catheter 14 . After the pumping device has been placed, the guide wire is withdrawn.
  • the canula 15 has a preformed bend 34 that also serves to better find the path.
  • FIG. 3 illustrates the distal end of the canula 15 with the suction head 16 .
  • the suction head 16 comprises the longitudinal inlet openings 17 .
  • a ball 36 is provided into which a hollow pin 37 is inserted and welded.
  • This pin 37 serves as a connecting element for the projection 20 , which in the present case is provided with a pigtail tip 21 .
  • the lumen 32 of the projection 20 extends through the pin 37 and the ball 36 into the suction head 16 .
  • the outer diameter of the projection 20 is smaller than that of the canula 15 .
  • FIG. 4 illustrates an embodiment in which the suction head 16 includes an inflow funnel 41 in an expansible suction basket 40 .
  • the suction basket 40 is made from a material able to restore itself, for example, or it is expanded by a balloon. In the expanded state, the suction basket 40 has an outer diameter larger than that of the canula 15 . Thus, the suction basket 40 is expanded from its initial 4 mm to a diameter of about 6 mm.
  • the inflow funnel 41 is spanned from a flexible polymer screen that allows for a smooth inflow and substantially increases the hydraulic capacity of the pump by reducing the hydraulic losses.
  • the canula 15 has a two-stage design. It is provided with first inlet openings 17 forming the main inlet. Distal of the inlet openings 17 , the projection 20 follows that, in the present case, has the same outer diameter and the same lumen diameter as the canula 15 . In the distal end portion of the projection 20 , further lateral auxiliary openings 44 are provided that serve as auxiliary openings. No suction head is provided here. The distal end of the canula is closed by a rounded end wall 45 with a passage for a guide wire 33 .
  • the pumping device of FIG. 5 is slipped over the guide wire 33 that passes through the impeller part 33 of the pump 11 and exits laterally from an outlet opening 18 .
  • the guide wire 33 is withdrawn in the proximal direction.
  • the operation of the pump 11 causes blood to be drawn through the inlet openings 17 .
  • Due to the higher flow resistance of the projection 20 and the auxiliary openings 44 only the inlet openings 17 exert a suction effect, while the projection 20 has practically no hydraulic effect. Only when the inlet openings 17 adhere by suction or are clogged in another way, will the auxiliary openings 44 become effective.
  • the projection 20 has an angled part 46 . Its lumen is in communication with that of the canula 15 .
  • the projection has a flexibility that is preferably higher than that of the canula 15 .

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Mechanical Engineering (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Vascular Medicine (AREA)
  • Transplantation (AREA)
  • External Artificial Organs (AREA)

Abstract

The invention relates to an intercardiac pump device comprising a pump (11) whose distal end (13) is connected to a cannula (15) which is provided with a suction head (16) for sucking blood. Said strainer is provided with a non-sucking extension (20) for stabilising the position of said pump device in the heart and mechanically prolonging the cannula (15) without deteriorating hydraulic conditions. Said extension is also used in the form of a spacer in order to avoid that the suction head (16) adheres to a cardiac wall.

Description

  • The invention relates to an intracardiac pumping device adapted to be fully inserted into the heart via adjoining vessels to assist the natural cardiac pump function or to replace the same by a continuous pumping operation.
  • Intracardiac blood pumps inserted percutaneously into a patient's body are highly miniaturized. They comprise a cylindrical drive portion and a cylindrical pump portion. The intake end of the pump portion is provided with a flexible canula having a suction head with lateral inlet openings at the distal end. Such a pumping device is described in EP 0 916 359 A1 (Impella). Another pumping device conveying in the distal direction is described in WO 99/58170 (Impella). In this pumping device, the pumping portion is prolonged by a flexible canula adapted to be passed through a cardiac valve. A catheter projects from the distal end of the canula, at which catheter a balloon is provided which is to be entrained by the blood flow in the body when the pumping device is inserted.
  • A pumping device that takes in blood through a canula and then feeds it proximally can be placed such that it leads through the aortic valve, the suction head at the end of the canula being situated in the left ventricle, while the pump outlet lies in the aorta. The operation of the continually feeding pump is superposed on the pulsating activity of the heart so that the pump is subjected to heavily pulsating pressure variations. In this context it may happen that the pump, together with the associated proximal catheter is subjected to substantial changes in position. During a systole, the catheter is pressed against the outer side of the aortic arch, whereas it is pressed against the inner side thereof during a diastole. Further, the position of the pump varies continuously, which may result in displacements of the canula passing through the aortic valve and even in an ejection of the canula which then slips from the cardiac valve into the aorta.
  • It is another difficulty with such blood pumps that the suction head may adhere to tissue parts inside the heart by suction. This entails the danger of irritations of the heart and, further, the pumping capacity is reduced by the obstruction of inlet openings. Finally, it may happen that the canula adheres to the mitral valve by suction and an additional damage to the blood is induced by suction.
  • It is an object of the present invention to provide an intracardiac pumping device for percutaneous insertion that substantially avoids the risk of adhering by suction.
  • The present pumping device has the features of claim 1. According thereto, a flexible projection is provided at the canula distal of the inlet openings. The projection forms a mechanical spacer maintaining a distance to neighboring walls, yet does not change the pumping device hydraulically.
  • Beside the spacing function, the projection has other effects. It increases the mechanical length of the pumping device without increasing the hydraulic length. The increase in mechanical length has the consequence that the pumping device is less likely to slip out through the aortic valve. On the other hand, the hydraulic resistance of the canula is not increased so that the suction performance is not degraded. It is another effect that the projection essentially reduces the tendency of the pumping device to make pulsating motions caused by cardiac pulsation. The pumping device including the pump and the catheter lies much calmer within the heart, whereby also the danger of an ejection is reduced. In the event that a new insertion is to be allowed after an ejection, the distal projection is preferably configured such that a new retrograde passage of the aortic valve is possible easily and reproducibly.
  • In a preferred embodiment of the invention, the flexible projection is a hollow tube whose lumen is in communication with that of the canula. Such a pumping device is suited for use with a guide wire. When inserting the pumping device, the guide wire may be included as a stiffening means. It is also possible to first place the guide wire and to then slip the pumping device over the same. Eventually, an angled tip of the guide wire may also be pushed out from the projection to serve as a pathfinder through the vascular system. Although the lumen of the projection is in communication with the lumen of the canula, the pump does not suck through the projection. This is because the inlet openings at the suction head have a much larger cross section than the lumen of the projection so that due to the lower flow resistance the suction is affected for the much greater part through the inlet openings. A certain suction effect caused by the lumen of the projection is so small that it is negligible and is not sufficient to cause adherence by suction to other parts. Thus, other than the suction head, the projection is unable to adhere by suction. However, should the lumen of the projection be obstructed for some reason, this has no effects on the hydraulic function of the pump.
  • The flexible projection may comprise a pigtail tip as known from catheters and stents. The rounded pigtail tip allows for an atraumatical supporting at heart or vessel walls. Moreover, the tip is so soft and flexible that it adapts to any cavity topology by deforming. The pigtail tip also facilitates the insertion and the placing of the pumping device. Specifically, it can be used in combination with a guide wire, the pigtail tip being stretched by the guide wire during insertion. When the pigtail tip is advanced without the guide wire, a simple and reproducible retrograde passage through the aortic valve is still possible. This is of particular importance since the guide wire is removed for the pump to operate and can not be advanced again without having to remove the pump for that purpose. Should the pump be ejected from the left heart due to the systolic cardiac functions, it may be repositioned even without the wire because of the configuration of the flexible projection as a pigtail.
  • The following is a detailed description of embodiments of the invention with reference to the drawing. The features mentioned in the context of the embodiments do not limit the scope of the invention. The same is defined by the claims.
  • In the Figures:
  • FIG. 1 illustrates the pumping device operating in the heart;
  • FIG. 2 illustrates the pumping device in an unused state;
  • FIG. 3 shows a section through the suction head with the projection attached thereto;
  • FIG. 4 illustrates an embodiment in which the suction head has a flow-shaping inflow funnel; and
  • FIG. 5 illustrates an embodiment in which the canula comprises a second set of inlet openings at the end of the projection.
    •
  • FIG. 1 illustrates the heart H with the aorta AO branching therefrom. Via the aortic arch 10, the aorta passes into a vertical strand that branches into the femoral artery, among others. The pumping device is percutaneously inserted into the femoral artery in the region of the groin and is advanced to the heart.
  • The intracardiac pumping device comprises a pump 11 with a proximal end 12 and a distal end 13. The pump 11 has a housing with an outer diameter of 4 mm at most and a length of approximately 15 mm so that the pump can be inserted percutaneously and be operated inside the heart. Larger pumps that can only be inserted surgically must not exceed an outer diameter of 6 mm because of the peripheral vessel diameters.
  • The proximal end 12 of the pump 11 is connected with a catheter 14 including the electric wires for the operation and the control of the pump 11. The distal end 13 is connected with a canula 15 which is an elongate flexible hose forming at its distal end a suction head 16 with lateral inlet openings 17. The pump 11 draws blood through the inlet openings 17 of the canula 15 and pumps the same through the outlet openings 18 provided in the sides of the pump. The pump and the canula are generally designed as described in EP 0 916 369 A1 (Impella). The canula 15 is a hose with a length of about 40 to 70 mm, whose wall is formed by a coiled wire provided with a polyurethane coating. The canula 15 has a certain form stability, yet it is flexible.
  • According to the invention, the suction head 16 of the canula 15 is adjoined by a projection 20 that extends the canula 15 mechanically, but not hydraulically. The projection 20 has a length of 10 to 30 mm. In the present case, it is provided with a pigtail tip 21 to allow for atraumatic support at body tissue.
  • The solid lines in FIG. 1 represent the extension of the pumping device in the heart H and the aorta AO. The pumping device is placed such that the pump 11 is located in the aorta AO while the suction head 16 lies in the left ventricle LV. The canula 15 extends through the aortic valve AK. Thus, the pump draws blood from the left ventricle LV and feeds into the aorta AO. Moreover, FIG. 1 shows the left atrium LA and the mitral valve MK.
  • The pump 11 pumps continuously at a delivery rate of 2 to 3 1/min. The reaction force tends to pull the pump into the heart. This force is countered by the pumping force of the heart. During the systole, the heart has a fluctuating delivery rate of about 10 1/min. It has been found that the pump moves resulting in a systolic position 25 at the outer side of the aortic arch 10 during the ejection phase of the heart, while, during the filling phase, a diastolic position 26 on the inner side of the aortic arch 10 is obtained. With these movements, the position of the canula 15 and the suction head 16 also changes. When the suction head 16 comes close to the trabecula structures situated at the wall of the heart, there is a danger of these structures being caught by suction, of an occlusion of the suction head, of an increased damage to the blood and the risk of a hematoma being formed in the cardiac structure.
  • Adhering by suction is made more difficult by the projection 20 that is supported at the wall of the heart. Further, the projection 20 forms a mechanical extension of the canula to prevent ejection from the left ventricle and the aortic valve.
  • As is evident from FIG. 2, the pump 11 comprises a motor part 30 and a pump part 31 arranged axially one behind the other. The pump part 31 includes a housing ring and an impeller driven by the motor and feeding the blood flow in the axial direction, the blood flow being deflected outward radially and exiting laterally from the housing of the pump 11 through the outlet openings 18. The pump part 31 is axially adjoined by the canula 15 having about the same outer diameter (4 mm) as the pump 11. The suction head 16 with the inlet opening 17 has a length of about 10 to 15 mm. The outlet openings 18 have an area at least as large as the cross-section area of the canula lumen so that the suction head forms no constriction.
  • In FIG. 2, the projection 20 is designed as a hollow hose with a continuous lumen 32. The width of this lumen is much smaller than that of the canula lumen. The lumen 32 serves to pass a guide wire 33 therethrough to facilitate the insertion of the pumping device into the body. The guide wire 33 extends the projection 20 if the same has a preformed bend. The guide wire may also have a soft flexible bent tip protruding from the distal end of the projection 20 and serving as a pathfinder through the vascular system. The guide wire 33 leads into the pump 11, through the pump part 31 and out from an outlet opening 18. It is then guided along the outside of the catheter 14. After the pumping device has been placed, the guide wire is withdrawn.
  • As illustrated in FIG. 2, the canula 15 has a preformed bend 34 that also serves to better find the path.
  • FIG. 3 illustrates the distal end of the canula 15 with the suction head 16. The suction head 16 comprises the longitudinal inlet openings 17. At its end, a ball 36 is provided into which a hollow pin 37 is inserted and welded. This pin 37 serves as a connecting element for the projection 20, which in the present case is provided with a pigtail tip 21. The lumen 32 of the projection 20 extends through the pin 37 and the ball 36 into the suction head 16. Here, the outer diameter of the projection 20 is smaller than that of the canula 15.
  • FIG. 4 illustrates an embodiment in which the suction head 16 includes an inflow funnel 41 in an expansible suction basket 40. The suction basket 40 is made from a material able to restore itself, for example, or it is expanded by a balloon. In the expanded state, the suction basket 40 has an outer diameter larger than that of the canula 15. Thus, the suction basket 40 is expanded from its initial 4 mm to a diameter of about 6 mm. Here, the inflow funnel 41 is spanned from a flexible polymer screen that allows for a smooth inflow and substantially increases the hydraulic capacity of the pump by reducing the hydraulic losses.
  • In the embodiment of FIG. 5, the canula 15 has a two-stage design. It is provided with first inlet openings 17 forming the main inlet. Distal of the inlet openings 17, the projection 20 follows that, in the present case, has the same outer diameter and the same lumen diameter as the canula 15. In the distal end portion of the projection 20, further lateral auxiliary openings 44 are provided that serve as auxiliary openings. No suction head is provided here. The distal end of the canula is closed by a rounded end wall 45 with a passage for a guide wire 33.
  • The pumping device of FIG. 5 is slipped over the guide wire 33 that passes through the impeller part 33 of the pump 11 and exits laterally from an outlet opening 18. After the pumping device has been positioned, the guide wire 33 is withdrawn in the proximal direction. The operation of the pump 11 causes blood to be drawn through the inlet openings 17. Due to the higher flow resistance of the projection 20 and the auxiliary openings 44, only the inlet openings 17 exert a suction effect, while the projection 20 has practically no hydraulic effect. Only when the inlet openings 17 adhere by suction or are clogged in another way, will the auxiliary openings 44 become effective. The projection 20 has an angled part 46. Its lumen is in communication with that of the canula 15. The projection has a flexibility that is preferably higher than that of the canula 15.

Claims (21)

1-9. (canceled)
10. An intracardiac pumping device for percutaneous insertion comprising:
a pump configured to be positioned within the vasculature of a patient, the pump comprising:
a motor, and
a pump housing and impeller positioned distal of the motor and mechanically coupled to the motor;
a cannula positioned distal of the pump housing, the cannula comprising a distal suction head having inlet openings;
a catheter having a distal end that operably extends to the motor and permits an electrical lead to pass into contact with the motor so that the impeller is rotatably driven by the motor, and a proximal end configured to extend the electrical lead to a controller located outside the patient; and
a flexible atraumatic projection extending distally from a distal end of the suction head.
11. The pumping device of claim 10, wherein the catheter is configured so it can bend to extend over an aortic arch.
12. The pumping device of claim 10, wherein the controller is configured to operate the impeller to pump blood at a rate of 2 to 3 liters per minute.
13. The pumping device of claim 10, wherein the cannula is configured to extend across an aortic valve in a heart.
14. The pumping device of claim 13, wherein the inlet openings of the suction head are configured to be positioned in a left ventricle of the heart.
15. The pumping device of claim 14, wherein during systole the pump is configured to change position within the heart with respect to a position during diastole.
16. The pumping device of claim 15, wherein the flexible atraumatic projection is configured to space the pump from a wall of the heart.
17. The pumping device of claim 16, wherein the flexible atraumatic projection is configured as a pigtail.
18. The pumping device of claim 17, further comprising blood outlets positioned proximal of the impeller.
19. The pumping device of claim 18, wherein the blood outlets are distal of the motor part.
20. The pumping device of claim 19, wherein the blood outlets are formed in the pump housing.
21. The pumping device of claim 20, wherein the impeller is configured to pull the blood into the cannula through the blood inlets and out the blood outlets.
22. The pumping device of claim 21, wherein the impeller is configured to deflect the blood out through the blood outlets, wherein the blood exits the pump with a radial component.
23. The pumping device of claim 22, wherein the outlet openings are configured to be positioned in the aorta.
24. The pumping device of claim 10, wherein a cross-sectional area of the inlet openings is the same as a cross-sectional area of the cannula.
25. The pumping device of claim 24, wherein the cannula is formed from a metal coil having a polymer coating.
26. The pumping device of claim 25, wherein the polymer coating is a polyurethane coating.
27. The pumping device of claim 26, wherein the cannula has a length of less than 70 mm.
28. The pumping device of claim 27, wherein the cannula is configured to be flexible.
29. The pumping device of claim 10, wherein the pump housing has an outer diameter of 4 mm.
US15/876,346 2003-08-08 2018-01-22 Intracardiac pumping device Abandoned US20180207334A1 (en)

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US15/876,346 US20180207334A1 (en) 2003-08-08 2018-01-22 Intracardiac pumping device
US16/576,912 US20200222603A1 (en) 2003-08-08 2019-09-20 Intracardiac pumping device
US17/014,218 US11491320B2 (en) 2003-08-08 2020-09-08 Intracardiac pumping device
US17/960,988 US12023477B2 (en) 2003-08-08 2022-10-06 Intracardiac pumping device

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DE10336902.3 2003-08-08
DE10336902.3A DE10336902C5 (en) 2003-08-08 2003-08-08 Intracardiac pumping device
US10/566,423 US9872948B2 (en) 2003-08-08 2004-07-24 Intracardiac pumping device
PCT/EP2004/008321 WO2005016416A1 (en) 2003-08-08 2004-07-24 Intracardiac pump device
US15/876,346 US20180207334A1 (en) 2003-08-08 2018-01-22 Intracardiac pumping device

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US10/566,423 Continuation US9872948B2 (en) 2003-08-08 2004-07-24 Intracardiac pumping device
PCT/EP2004/008321 Continuation WO2005016416A1 (en) 2003-08-08 2004-07-24 Intracardiac pump device
US11/566,423 Continuation US7670112B2 (en) 2005-12-05 2006-12-04 Turbine blade with cooling and with improved service life

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US20180207334A1 true US20180207334A1 (en) 2018-07-26

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US14/979,019 Expired - Lifetime US9833550B2 (en) 2003-08-08 2015-12-22 Intracardiac pumping device
US15/876,346 Abandoned US20180207334A1 (en) 2003-08-08 2018-01-22 Intracardiac pumping device
US16/576,912 Abandoned US20200222603A1 (en) 2003-08-08 2019-09-20 Intracardiac pumping device
US17/014,218 Active US11491320B2 (en) 2003-08-08 2020-09-08 Intracardiac pumping device
US17/960,988 Expired - Lifetime US12023477B2 (en) 2003-08-08 2022-10-06 Intracardiac pumping device

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US14/979,019 Expired - Lifetime US9833550B2 (en) 2003-08-08 2015-12-22 Intracardiac pumping device

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US17/014,218 Active US11491320B2 (en) 2003-08-08 2020-09-08 Intracardiac pumping device
US17/960,988 Expired - Lifetime US12023477B2 (en) 2003-08-08 2022-10-06 Intracardiac pumping device

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Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10722631B2 (en) 2018-02-01 2020-07-28 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US10881770B2 (en) 2018-01-10 2021-01-05 Magenta Medical Ltd. Impeller for blood pump
US11185677B2 (en) 2017-06-07 2021-11-30 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
US11191944B2 (en) 2019-01-24 2021-12-07 Magenta Medical Ltd. Distal tip element for a ventricular assist device
US11260212B2 (en) 2016-10-25 2022-03-01 Magenta Medical Ltd. Ventricular assist device
US11291826B2 (en) 2018-01-10 2022-04-05 Magenta Medical Ltd. Axially-elongatable frame and impeller
US11511103B2 (en) 2017-11-13 2022-11-29 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
US11654275B2 (en) 2019-07-22 2023-05-23 Shifamed Holdings, Llc Intravascular blood pumps with struts and methods of use and manufacture
US11724089B2 (en) 2019-09-25 2023-08-15 Shifamed Holdings, Llc Intravascular blood pump systems and methods of use and control thereof
US11964145B2 (en) 2019-07-12 2024-04-23 Shifamed Holdings, Llc Intravascular blood pumps and methods of manufacture and use
US12102815B2 (en) 2019-09-25 2024-10-01 Shifamed Holdings, Llc Catheter blood pumps and collapsible pump housings
US12121713B2 (en) 2019-09-25 2024-10-22 Shifamed Holdings, Llc Catheter blood pumps and collapsible blood conduits
US12128227B2 (en) 2020-04-07 2024-10-29 Magenta Medical Ltd. Manufacture of an impeller
US12161857B2 (en) 2018-07-31 2024-12-10 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US12220570B2 (en) 2018-10-05 2025-02-11 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US12403296B2 (en) 2018-05-30 2025-09-02 Kardion Gmbh Apparatus for anchoring a ventricular assist system in a blood vessel, operating method, production method for producing an apparatus and ventricular assist system
US12409310B2 (en) 2019-12-11 2025-09-09 Shifamed Holdings, Llc Descending aorta and vena cava blood pumps
US12440665B2 (en) 2021-11-22 2025-10-14 Magenta Medical Ltd. Magnetic phase detection

Families Citing this family (163)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10336902C5 (en) 2003-08-08 2019-04-25 Abiomed Europe Gmbh Intracardiac pumping device
EP2151257B1 (en) 2004-08-13 2013-04-17 Delgado, Reynolds M., III Apparatus for long-term assisting a left ventricle to pump blood
US7393181B2 (en) 2004-09-17 2008-07-01 The Penn State Research Foundation Expandable impeller pump
CN102380135A (en) 2006-03-23 2012-03-21 宾州研究基金会 Heart assist device with expandable impeller pump
AT504990B1 (en) * 2007-02-27 2008-12-15 Miracor Medizintechnik Handels CATHETER FOR SUPPORTING THE PERFORMANCE OF A HEART
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
JP5473085B2 (en) * 2008-06-23 2014-04-16 カーディオブリッジ ゲーエムベーハー Catheter pump for circulatory assistance
EP2341956B1 (en) 2008-10-06 2015-12-23 Indiana University Research and Technology Corporation Methods and apparatus for active or passive assistance in the circulatory system
EP2194278A1 (en) 2008-12-05 2010-06-09 ECP Entwicklungsgesellschaft mbH Fluid pump with a rotor
DE102009007216A1 (en) 2009-02-03 2010-08-12 Siemens Aktiengesellschaft Blood pump e.g. right ventricular impella blood pump, for insertion into heart of patient, has position sensor for determining position and/or location of pump in patient's body, where pump is connected to catheter at proximal end
EP2216059A1 (en) 2009-02-04 2010-08-11 ECP Entwicklungsgesellschaft mbH Catheter device with a catheter and an actuation device
DE102009011726A1 (en) 2009-03-04 2010-09-09 Siemens Aktiengesellschaft Medical device for controlling location of e.g. left-ventricular, minimally invasive catheter-based cardiac assist device-blood pump in heart of patient, has reference position sensor arranged at surface of heart of patient
EP2229965A1 (en) 2009-03-18 2010-09-22 ECP Entwicklungsgesellschaft mbH Fluid pump with particular form of a rotor blade
DE102009014462B4 (en) 2009-03-23 2019-01-17 Siemens Healthcare Gmbh A blood pump, medical device, comprising a blood pump and methods for assisting the placement of a blood pump
EP2246078A1 (en) 2009-04-29 2010-11-03 ECP Entwicklungsgesellschaft mbH Shaft assembly with a shaft which moves within a fluid-filled casing
EP2248544A1 (en) 2009-05-05 2010-11-10 ECP Entwicklungsgesellschaft mbH Fluid pump with variable circumference, particularly for medical use
US8617239B2 (en) 2009-05-18 2013-12-31 Cardiobridge Gmbh Catheter pump
EP2266640A1 (en) 2009-06-25 2010-12-29 ECP Entwicklungsgesellschaft mbH Compressible and expandable turbine blade for a fluid pump
EP2282070B1 (en) 2009-08-06 2012-10-17 ECP Entwicklungsgesellschaft mbH Catheter device with a coupling device for a drive device
EP2298373A1 (en) 2009-09-22 2011-03-23 ECP Entwicklungsgesellschaft mbH Fluid pump with at least one turbine blade and a seating device
EP2298371A1 (en) 2009-09-22 2011-03-23 ECP Entwicklungsgesellschaft mbH Function element, in particular fluid pump with a housing and a transport element
EP2299119B1 (en) 2009-09-22 2018-11-07 ECP Entwicklungsgesellschaft mbH Inflatable rotor for a fluid pump
EP2298372A1 (en) 2009-09-22 2011-03-23 ECP Entwicklungsgesellschaft mbH Rotor for an axial pump for transporting a fluid
EP2314331B1 (en) 2009-10-23 2013-12-11 ECP Entwicklungsgesellschaft mbH Catheter pump arrangement and flexible shaft arrangement with a cable core
EP2314330A1 (en) 2009-10-23 2011-04-27 ECP Entwicklungsgesellschaft mbH Flexible shaft arrangement
EP2338541A1 (en) 2009-12-23 2011-06-29 ECP Entwicklungsgesellschaft mbH Radial compressible and expandable rotor for a fluid pump
EP2338540A1 (en) 2009-12-23 2011-06-29 ECP Entwicklungsgesellschaft mbH Delivery blade for a compressible rotor
EP2338539A1 (en) 2009-12-23 2011-06-29 ECP Entwicklungsgesellschaft mbH Pump device with a detection device
EP2347778A1 (en) 2010-01-25 2011-07-27 ECP Entwicklungsgesellschaft mbH Fluid pump with a radially compressible rotor
EP2363157A1 (en) 2010-03-05 2011-09-07 ECP Entwicklungsgesellschaft mbH Device for exerting mechanical force on a medium, in particular fluid pump
EP2560722A2 (en) 2010-04-21 2013-02-27 The Regents of the University of Michigan Fluoroscopy-independent, endovascular aortic occlusion system
EP2388029A1 (en) 2010-05-17 2011-11-23 ECP Entwicklungsgesellschaft mbH Pump array
EP2399639A1 (en) 2010-06-25 2011-12-28 ECP Entwicklungsgesellschaft mbH System for introducing a pump
EP2407187A3 (en) 2010-07-15 2012-06-20 ECP Entwicklungsgesellschaft mbH Blood pump for invasive application within the body of a patient
EP2407186A1 (en) 2010-07-15 2012-01-18 ECP Entwicklungsgesellschaft mbH Rotor for a pump, produced with an initial elastic material
EP2407185A1 (en) 2010-07-15 2012-01-18 ECP Entwicklungsgesellschaft mbH Radial compressible and expandable rotor for a pump with a turbine blade
EP2422735A1 (en) 2010-08-27 2012-02-29 ECP Entwicklungsgesellschaft mbH Implantable blood transportation device, manipulation device and coupling device
EP2646099B1 (en) 2010-12-01 2015-04-08 Abiomed, Inc. Radiopaque cannula marker
ES2786754T3 (en) 2010-12-01 2020-10-13 Abiomed Inc Loading guide lumen
US8485961B2 (en) 2011-01-05 2013-07-16 Thoratec Corporation Impeller housing for percutaneous heart pump
WO2012094641A2 (en) 2011-01-06 2012-07-12 Thoratec Corporation Percutaneous heart pump
EP2497521A1 (en) 2011-03-10 2012-09-12 ECP Entwicklungsgesellschaft mbH Push device for axial insertion of a string-shaped, flexible body
KR102062132B1 (en) * 2011-08-17 2020-01-03 플로우 포워드 메디컬, 인크. Blood pump systems and methods
EP2564771A1 (en) 2011-09-05 2013-03-06 ECP Entwicklungsgesellschaft mbH Medicinal product with a functional element for invasive use in the body of a patient
US8926492B2 (en) 2011-10-11 2015-01-06 Ecp Entwicklungsgesellschaft Mbh Housing for a functional element
EP2606919A1 (en) 2011-12-22 2013-06-26 ECP Entwicklungsgesellschaft mbH Sluice device for inserting a catheter
EP2606920A1 (en) 2011-12-22 2013-06-26 ECP Entwicklungsgesellschaft mbH Sluice device for inserting a catheter
US9327067B2 (en) 2012-05-14 2016-05-03 Thoratec Corporation Impeller for catheter pump
US8721517B2 (en) 2012-05-14 2014-05-13 Thoratec Corporation Impeller for catheter pump
EP4218887A1 (en) 2012-05-14 2023-08-02 Tc1 Llc Mechanical circulatory support device for stabilizing a patient after cardiogenic shock
US9872947B2 (en) 2012-05-14 2018-01-23 Tc1 Llc Sheath system for catheter pump
US9446179B2 (en) 2012-05-14 2016-09-20 Thoratec Corporation Distal bearing support
CN108742951B (en) 2012-06-06 2021-05-25 洋红医疗有限公司 Artificial kidney valve
US9358329B2 (en) 2012-07-03 2016-06-07 Thoratec Corporation Catheter pump
US9421311B2 (en) 2012-07-03 2016-08-23 Thoratec Corporation Motor assembly for catheter pump
EP4186557A1 (en) 2012-07-03 2023-05-31 Tc1 Llc Motor assembly for catheter pump
US12151092B2 (en) 2012-11-06 2024-11-26 Procardia Llc Mechanical circulatory support device with centrifugal impeller designed for implantation in the descending aorta
US10857274B2 (en) 2012-11-06 2020-12-08 Queen Mary University Of London Mechanical circulatory support device with centrifugal impeller designed for implantation in the descending aorta
EP2745869A1 (en) 2012-12-21 2014-06-25 ECP Entwicklungsgesellschaft mbH Sluice assembly for the introduction of a cord-like body, in particular of a catheter, into a patient
EP4233702A3 (en) 2013-03-13 2023-12-20 Magenta Medical Ltd. Manufacture of an impeller
US11077294B2 (en) 2013-03-13 2021-08-03 Tc1 Llc Sheath assembly for catheter pump
WO2014164136A1 (en) 2013-03-13 2014-10-09 Thoratec Corporation Fluid handling system
US11033728B2 (en) 2013-03-13 2021-06-15 Tc1 Llc Fluid handling system
US10583231B2 (en) 2013-03-13 2020-03-10 Magenta Medical Ltd. Blood pump
US9308302B2 (en) 2013-03-15 2016-04-12 Thoratec Corporation Catheter pump assembly including a stator
EP4190376A1 (en) 2013-03-15 2023-06-07 Tc1 Llc Catheter pump assembly including a stator
US9968719B2 (en) 2013-07-30 2018-05-15 Heartware, Inc. Wire scaffold device for ventricular assist device
US10569062B2 (en) 2013-09-09 2020-02-25 Prytime Medical Devices, Inc. Low profile occlusion catheter
DE102014012850A1 (en) * 2014-09-03 2016-03-03 Novapump Gmbh catheter
US11583670B2 (en) * 2014-03-03 2023-02-21 Novapump Gmbh Catheter for the directional conveyance of a fluid, particularly a body fluid
US10583232B2 (en) 2014-04-15 2020-03-10 Tc1 Llc Catheter pump with off-set motor position
WO2015160943A1 (en) 2014-04-15 2015-10-22 Thoratec Corporation Sensors for catheter pumps
EP3131597B1 (en) 2014-04-15 2020-12-02 Tc1 Llc Catheter pump introducer systems
EP3131599B1 (en) * 2014-04-15 2019-02-20 Tc1 Llc Catheter pump with access ports
EP4046678B1 (en) * 2014-05-13 2025-10-01 Abiomed, Inc. Cannula assembly
WO2015175711A1 (en) * 2014-05-13 2015-11-19 Abiomed, Inc. Blood pump housing component
US10232142B2 (en) 2014-06-10 2019-03-19 Prytime Medical Devices, Inc. Conduit guiding tip
EP3583973A1 (en) 2014-08-18 2019-12-25 Tc1 Llc Guide features for percutaneous catheter pump
US9675738B2 (en) 2015-01-22 2017-06-13 Tc1 Llc Attachment mechanisms for motor of catheter pump
US9770543B2 (en) 2015-01-22 2017-09-26 Tc1 Llc Reduced rotational mass motor assembly for catheter pump
WO2016118781A2 (en) 2015-01-22 2016-07-28 Thoratec Corporation Motor assembly with heat exchanger for catheter pump
CA2980018C (en) 2015-03-19 2018-02-20 Prytime Medical Devices, Inc. System and method for low-profile occlusion balloon catheter
US9855143B2 (en) * 2015-03-30 2018-01-02 Hocor Cardiovascular Technologies Llc Percutaneuous temporary aortic valve
US9907890B2 (en) 2015-04-16 2018-03-06 Tc1 Llc Catheter pump with positioning brace
DE102015005002A1 (en) 2015-04-21 2016-10-27 Xenios Ag cannula
WO2016185473A1 (en) 2015-05-18 2016-11-24 Magenta Medical Ltd. Blood pump
EP4290081A3 (en) 2015-09-25 2024-02-21 Procyrion, Inc. Non-occluding intravascular blood pump providing reduced hemolysis
IL300148B2 (en) 2016-01-29 2024-01-01 Abiomed Inc Percutaneous pump system and cannula for a percutaneous pump
EP3205359B1 (en) * 2016-02-11 2018-08-29 Abiomed Europe GmbH Blood pump system
EP3205360B1 (en) * 2016-02-11 2018-08-29 Abiomed Europe GmbH Blood pump
US11986602B2 (en) * 2016-05-31 2024-05-21 Abiomed, Inc. Catheter of a heart pump shaped for anatomic fit
US10368872B2 (en) 2016-06-02 2019-08-06 Prytime Medical Devices, Inc. System and method for low profile occlusion balloon catheter
EP3808401A1 (en) 2016-07-21 2021-04-21 Tc1 Llc Gas-filled chamber for catheter pump motor assembly
US11160970B2 (en) 2016-07-21 2021-11-02 Tc1 Llc Fluid seals for catheter pump motor assembly
US11206992B2 (en) 2016-08-11 2021-12-28 Foundry Innovation & Research 1, Ltd. Wireless resonant circuit and variable inductance vascular monitoring implants and anchoring structures therefore
EP3496606A1 (en) 2016-08-11 2019-06-19 Foundry Innovation & Research 1, Ltd. Systems and methods for patient fluid management
US11701018B2 (en) 2016-08-11 2023-07-18 Foundry Innovation & Research 1, Ltd. Wireless resonant circuit and variable inductance vascular monitoring implants and anchoring structures therefore
EP3506960B1 (en) * 2016-09-01 2025-04-23 Abiomed, Inc. Anti-suction blood pump inlet
US11524153B2 (en) 2016-10-03 2022-12-13 Queen Mary University Of London Mechanical circulatory support device with axial flow turbomachine optimized for heart failure and cardio-renal syndrome by implantation in the descending aorta
US12090310B2 (en) 2016-10-03 2024-09-17 Procardia Llc Mechanical circulatory support device with axial flow turbomachine optimized for heart failure and cardio-renal syndrome by implantation in the descending aorta
JP7094279B2 (en) 2016-11-23 2022-07-01 マジェンタ・メディカル・リミテッド Blood pump
EP4327732A3 (en) 2017-01-12 2024-04-24 The Regents of The University of California Endovascular perfusion augmentation for critical care
CA3060519A1 (en) 2017-04-21 2018-10-25 The Regents Of The University Of California Aortic flow meter and pump for partial-aortic occlusion
EP3398624A1 (en) * 2017-05-04 2018-11-07 Abiomed Europe GmbH Blood pump with reinforced catheter
US11944495B2 (en) 2017-05-31 2024-04-02 Foundry Innovation & Research 1, Ltd. Implantable ultrasonic vascular sensor
EP3629921B1 (en) 2017-05-31 2025-04-02 Foundry Innovation & Research 1, Ltd. Implantable sensors for vascular monitoring
DE102018201030B4 (en) 2018-01-24 2025-10-16 Kardion Gmbh Magnetic dome element with magnetic bearing function
JP7566724B2 (en) 2018-04-04 2024-10-15 セオドシオス・アレクサンダー Removable mechanical circulatory support units for short-term use
DE102018207611A1 (en) 2018-05-16 2019-11-21 Kardion Gmbh Rotor bearing system
DE102018207575A1 (en) 2018-05-16 2019-11-21 Kardion Gmbh Magnetic face turning coupling for the transmission of torques
DE102018208539A1 (en) 2018-05-30 2019-12-05 Kardion Gmbh A motor housing module for sealing an engine compartment of a motor of a cardiac assist system and cardiac assistance system and method for mounting a cardiac assist system
DE102018208538A1 (en) 2018-05-30 2019-12-05 Kardion Gmbh Intravascular blood pump and process for the production of electrical conductors
DE102018208550A1 (en) 2018-05-30 2019-12-05 Kardion Gmbh A lead device for directing blood flow to a cardiac assist system, cardiac assist system, and method of making a lead device
DE102018208536A1 (en) * 2018-05-30 2019-12-05 Kardion Gmbh A lead apparatus for directing blood flow to a cardiac assist system, method of making a lead apparatus, and method of assembling a cardiac assist system
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
US10668195B2 (en) 2018-06-01 2020-06-02 Fbr Medical, Inc. Catheter pump with fixed-diameter impeller
DE102018208929A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh A method of determining a flow rate of fluid flowing through an implanted vascular support system
DE102018208899A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh A method for determining the speed of sound in a fluid in the region of an implanted vascular support system
DE102018208913A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh A method of operating an implanted ventricular assist device
DE102018208862A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh Implantable vascular support system
DE102018208936A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh Determining device and method for determining a viscosity of a fluid
DE102018208933A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh A method of determining a flow rate of fluid flowing through an implanted vascular support system
DE102018208945A1 (en) 2018-06-06 2019-12-12 Kardion Gmbh An analysis device and method for analyzing a viscosity of a fluid
DE102018208879A1 (en) 2018-06-06 2020-01-30 Kardion Gmbh Method for determining a total fluid volume flow in the area of an implanted, vascular support system
DE102018210076A1 (en) 2018-06-21 2019-12-24 Kardion Gmbh Method and device for detecting a state of wear of a cardiac support system, method and device for operating a cardiac support system and cardiac support system
DE102018210058A1 (en) 2018-06-21 2019-12-24 Kardion Gmbh Stator blade device for guiding the flow of a fluid flowing out of an outlet opening of a heart support system, heart support system with stator blade device, method for operating a stator blade device and manufacturing method
DE102018211327A1 (en) 2018-07-10 2020-01-16 Kardion Gmbh Impeller for an implantable vascular support system
DE102018212153A1 (en) 2018-07-20 2020-01-23 Kardion Gmbh Inlet line for a pump unit of a cardiac support system, cardiac support system and method for producing an inlet line for a pump unit of a cardiac support system
US11219753B2 (en) * 2018-07-30 2022-01-11 Cardiovascular Systems, Inc. Intravascular pump with expandable and collapsible inlet region and methods thereof
EP3833273A4 (en) 2018-08-06 2022-06-29 Prytime Medical Devices, Inc. System and method for low profile occlusion balloon catheter
CN112654389A (en) 2018-08-07 2021-04-13 开迪恩有限公司 Bearing device for a cardiac support system and method for flushing an intermediate space in a bearing device for a cardiac support system
US11135421B2 (en) * 2019-02-07 2021-10-05 Synecor Llc Conduit for transseptal passage of devices to the aorta
US11717652B2 (en) * 2019-02-26 2023-08-08 White Swell Medical Ltd Devices and methods for treating edema
JP7729779B2 (en) 2019-03-26 2025-08-26 パズル メディカル デバイシズ インコーポレイテッド Modular mammalian body implantable fluid flow affecting device and related methods
SG11202111114TA (en) 2019-04-18 2021-11-29 Abiomed Inc Variable-stiffness distal extension for a blood pump system
EP3972661B1 (en) 2019-05-23 2024-09-11 Magenta Medical Ltd. Blood pumps
EP3990095A4 (en) 2019-06-28 2023-07-12 Theodosios Alexander DETACHABLE MECHANICAL CIRCULATION SUPPORT FOR SHORT-TERM USE
US12383723B2 (en) 2019-10-05 2025-08-12 Puzzle Medical Devices Inc. Mammalian body implantable fluid flow influencing device
IL293625A (en) 2019-12-03 2022-08-01 Procyrion Inc blood pumps
WO2021119413A1 (en) 2019-12-13 2021-06-17 Procyrion, Inc. Support structures for intravascular blood pumps
CA3162782A1 (en) 2020-01-10 2021-07-15 Soumen Das Blood pump with improved leakage control
DE102020102474A1 (en) 2020-01-31 2021-08-05 Kardion Gmbh Pump for conveying a fluid and method for manufacturing a pump
IL294964A (en) 2020-02-04 2022-09-01 Abiomed Inc Intravascular blood pump with inlet filter
EP4121159A2 (en) 2020-03-16 2023-01-25 Certus Critical Care, Inc. Blood flow control devices, systems, and methods and error detection thereof
WO2022197895A1 (en) 2021-03-18 2022-09-22 Prytime Medical Devices, Inc. Vascular occlusion catheter
EP4291287A1 (en) 2021-04-14 2023-12-20 Boston Scientific Scimed Inc. Flexible tip for transvalvular circulatory support device
NL2028130B1 (en) 2021-05-03 2022-11-10 Cardiacbooster B V Cardiac assist device with high frequency operation
CN115591105B (en) 2021-07-07 2023-08-15 上海焕擎医疗科技有限公司 Impeller of heart assist device and heart assist device
AU2022390146B2 (en) 2021-11-17 2025-04-03 Boston Scientific Scimed Inc. Device housing features to facilitate damage free guidewire translations
CN114796845B (en) * 2021-12-03 2024-08-27 深圳核心医疗科技股份有限公司 Blood pump and its driving device
US20230338726A1 (en) * 2022-04-25 2023-10-26 Boston Scientific Scimed Inc. Percutaneous circulatory support device including curved proximal catheter
CN118286586A (en) * 2022-06-15 2024-07-05 心擎医疗（苏州）股份有限公司 Ventricular assist device
USD1029236S1 (en) 2022-08-12 2024-05-28 Luminoah, Inc. Fluid pouch assembly
USD1033628S1 (en) 2022-08-12 2024-07-02 Luminoah, Inc. Fluid delivery module
USD1029235S1 (en) 2022-08-12 2024-05-28 Luminoah, Inc. Fluid delivery system
EP4568636A2 (en) 2022-08-12 2025-06-18 Luminoah, Inc. Wearable fluid delivery system
WO2024092349A1 (en) 2022-11-01 2024-05-10 Puzzle Medical Devices Inc. Implantable medical devices and related methods thereof
EP4630101A2 (en) * 2022-12-07 2025-10-15 Procyrion, Inc. Percutaneous mechanical circulatory support device
DE102023103518A1 (en) 2023-02-14 2024-08-14 Enmodes Gmbh Cardiac catheter pump
WO2024206305A1 (en) * 2023-03-30 2024-10-03 Boston Scientific Scimed, Inc. Percutaneous circulatory support device including proximal guidewire lumen
WO2025034714A1 (en) * 2023-08-08 2025-02-13 Fbr Medical, Inc. Catheter blood pumps with a distal flexible tube providing a circular spacer
WO2025171909A1 (en) 2024-02-14 2025-08-21 Christopher Wall Implantable pump

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4153048A (en) * 1977-09-14 1979-05-08 Cleveland Clinic Foundation Thermodilution catheter and method
US4747840A (en) * 1986-09-17 1988-05-31 Ladika Joseph E Selective pulmonary arteriograph catheter
US4777951A (en) * 1986-09-19 1988-10-18 Mansfield Scientific, Inc. Procedure and catheter instrument for treating patients for aortic stenosis
US6139487A (en) * 1997-04-02 2000-10-31 Impella Cardiotechnik Ag Intracardiac pump device
US20020095210A1 (en) * 2001-01-16 2002-07-18 Finnegan Michael T. Heart pump graft connector and system
US6544216B1 (en) * 1998-05-13 2003-04-08 Impella Cardiotechnik Aktiengesellschaft Intracardiac blood pump
US7022100B1 (en) * 1999-09-03 2006-04-04 A-Med Systems, Inc. Guidable intravascular blood pump and related methods

Family Cites Families (101)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2350534A (en) 1942-10-05 1944-06-06 Rosinger Arthur Magnetic stirrer
JPS4824967B1 (en) 1964-11-27 1973-07-25
US3333127A (en) 1965-12-27 1967-07-25 Bergstrom Mfg Company Magnetic drive or coupling
US3489145A (en) 1966-08-08 1970-01-13 Surgeon General Of The Public Method and apparatus for continuous separation of blood in vivo
GB1489055A (en) 1973-08-17 1977-10-19 Pont Res & Investment Services Magnetic coupling
US4065234A (en) 1975-12-22 1977-12-27 Nihon Kagaku Kizai Kabushiki Kaisha Magnetically driven rotary pumps
DE2624058C2 (en) 1976-05-28 1984-11-15 Franz Klaus-Union, 4630 Bochum Permanent magnet pump
US4135253A (en) 1976-11-30 1979-01-23 Medtronic, Inc. Centrifugal blood pump for cardiac assist
US4420851A (en) 1981-12-07 1983-12-20 Wiener Stanley M Mechanized tooth brush having movement in two planes
US4686982A (en) 1985-06-19 1987-08-18 John Nash Spiral wire bearing for rotating wire drive catheter
US4679558A (en) 1985-08-12 1987-07-14 Intravascular Surgical Instruments, Inc. Catheter based surgical methods and apparatus therefor
US4728319A (en) 1986-03-20 1988-03-01 Helmut Masch Intravascular catheter
US4747821A (en) 1986-10-22 1988-05-31 Intravascular Surgical Instruments, Inc. Catheter with high speed moving working head
US4753221A (en) 1986-10-22 1988-06-28 Intravascular Surgical Instruments, Inc. Blood pumping catheter and method of use
US4749376A (en) 1986-10-24 1988-06-07 Intravascular Surgical Instruments, Inc. Reciprocating working head catheter
US4846152A (en) 1987-11-24 1989-07-11 Nimbus Medical, Inc. Single-stage axial flow blood pump
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
US5372138A (en) 1988-03-21 1994-12-13 Boston Scientific Corporation Acousting imaging catheters and the like
US5011469A (en) * 1988-08-29 1991-04-30 Shiley, Inc. Peripheral cardiopulmonary bypass and coronary reperfusion system
US4919647A (en) 1988-10-13 1990-04-24 Kensey Nash Corporation Aortically located blood pumping catheter and method of use
US5017103A (en) 1989-03-06 1991-05-21 St. Jude Medical, Inc. Centrifugal blood pump and magnetic coupling
US5147186A (en) 1989-08-04 1992-09-15 Bio Medicus, Inc. Blood pump drive system
US5097849A (en) 1989-08-17 1992-03-24 Kensey Nash Corporation Method of use of catheter with working head having selectable impacting surfaces
US5042984A (en) 1989-08-17 1991-08-27 Kensey Nash Corporation Catheter with working head having selectable impacting surfaces and method of using the same
US4984972A (en) 1989-10-24 1991-01-15 Minnesota Mining And Manufacturing Co. Centrifugal blood pump
US5037403A (en) 1989-11-08 1991-08-06 Cordis Corporation Pigtail catheter with angled apertures
JPH0636821B2 (en) 1990-03-08 1994-05-18 健二 山崎 Implantable auxiliary artificial heart
NL9000833A (en) * 1990-04-09 1991-11-01 Cordis Europ ANGIOGRAPHY CATHETER.
ES2020787A6 (en) 1990-07-20 1991-09-16 Figuera Aymerich Diego Intra-ventricular expansible assist pump
US5158279A (en) 1991-09-30 1992-10-27 Xerox Corporation Magnetic clutch with adjustable slip torque
US5250059A (en) 1992-01-22 1993-10-05 Devices For Vascular Intervention, Inc. Atherectomy catheter having flexible nose cone
FR2688923B1 (en) 1992-03-23 1994-06-10 Sagem WATERPROOF MAGNETIC DRIVE DEVICE WITHOUT WALL CROSSING AND ULTRA-SOUND PROBE COMPRISING APPLICATION.
US5300112A (en) 1992-07-14 1994-04-05 Aai Corporation Articulated heart pump
SE501215C2 (en) 1992-09-02 1994-12-12 Oeyvind Reitan catheter Pump
US5376114A (en) 1992-10-30 1994-12-27 Jarvik; Robert Cannula pumps for temporary cardiac support and methods of their application and use
NL9300231A (en) * 1993-02-04 1994-09-01 Cordis Europ Angiography catheter.
DE4321260C1 (en) 1993-06-25 1995-03-09 Westphal Dieter Dipl Ing Dipl Blood pump as a centrifugal pump
WO1995010979A1 (en) 1993-10-19 1995-04-27 Ep Technologies, Inc. Locating accessory pathways in the heart
DE4414903A1 (en) 1994-04-28 1995-11-02 Aesculap Ag Surgical instrument with tubular shaft for arthroscopy
US5911685A (en) * 1996-04-03 1999-06-15 Guidant Corporation Method and apparatus for cardiac blood flow assistance
NL1003226C2 (en) 1996-05-29 1997-12-03 Cordis Europ Suction catheter with preformed end section.
US6015272A (en) 1996-06-26 2000-01-18 University Of Pittsburgh Magnetically suspended miniature fluid pump and method of designing the same
US5779721A (en) 1996-07-26 1998-07-14 Kensey Nash Corporation System and method of use for revascularizing stenotic bypass grafts and other blood vessels
US5827171A (en) 1996-10-31 1998-10-27 Momentum Medical, Inc. Intravascular circulatory assist device
US5954745A (en) 1997-05-16 1999-09-21 Gertler; Jonathan Catheter-filter set having a compliant seal
US6129704A (en) 1997-06-12 2000-10-10 Schneider (Usa) Inc. Perfusion balloon catheter having a magnetically driven impeller
US6123725A (en) 1997-07-11 2000-09-26 A-Med Systems, Inc. Single port cardiac support apparatus
US6007478A (en) * 1997-11-13 1999-12-28 Impella Cardiotechnik Aktiengesellschaft Cannula having constant wall thickness with increasing distal flexibility and method of making
JPH11244376A (en) 1998-02-27 1999-09-14 Kyocera Corp Blood pump
DE29804046U1 (en) 1998-03-07 1998-04-30 Günther, Rolf W., Prof. Dr.med., 52074 Aachen Percutaneously implantable, self-expanding axial pump for temporary heart support
US5928132A (en) 1998-03-31 1999-07-27 Datascope Investment Corp. Closed chest intra-aortic balloon based ventricular assist device
US6054788A (en) 1998-08-12 2000-04-25 Reliance Electric Industrial Company Magnetic power transmission coupling
WO2000019097A1 (en) 1998-09-30 2000-04-06 A-Med Systems, Inc. Blood pump system with magnetic cable drive
US6217541B1 (en) 1999-01-19 2001-04-17 Kriton Medical, Inc. Blood pump using cross-flow principles
US7780628B1 (en) 1999-01-11 2010-08-24 Angiodynamics, Inc. Apparatus and methods for treating congestive heart disease
FR2788223B1 (en) 1999-01-12 2001-09-21 Francis Bartolome MEDICO-SURGICAL DISCHARGE CANNULA
US6245007B1 (en) * 1999-01-28 2001-06-12 Terumo Cardiovascular Systems Corporation Blood pump
EP1034808A1 (en) 1999-03-09 2000-09-13 Paul Frederik Gründeman A device for transventricular mechanical circulatory support
US6186981B1 (en) * 1999-03-23 2001-02-13 Peter Cho Cavo-atrial cannula
US6295877B1 (en) 1999-03-30 2001-10-02 A-Med Systems, Inc. Pressure sensing cannula
US20050165269A9 (en) 1999-06-18 2005-07-28 Aboul-Hosn Walid N. Cannulation system and related methods
AU7354400A (en) 1999-09-03 2001-04-10 A-Med Systems, Inc. Guidable intravascular blood pump and related methods
US6517528B1 (en) 2000-04-13 2003-02-11 Scimed Life Systems, Inc. Magnetic catheter drive shaft clutch
US6413222B1 (en) 2000-04-13 2002-07-02 Boston Scientific Corporation Catheter drive shaft clutch
DE10040403A1 (en) * 2000-08-18 2002-02-28 Impella Cardiotech Ag Intracardiac blood pump
US6808508B1 (en) 2000-09-13 2004-10-26 Cardiacassist, Inc. Method and system for closed chest blood flow support
CN1157545C (en) 2000-10-25 2004-07-14 李国坤 Magnetic suspension bearing
DE10059714C1 (en) 2000-12-01 2002-05-08 Impella Cardiotech Ag Intravasal pump has pump stage fitted with flexible expandible sleeve contricted during insertion through blood vessel
DE10060275A1 (en) * 2000-12-05 2002-06-13 Impella Cardiotech Ag Method for calibrating a pressure sensor or a flow sensor on a rotary pump
US6537247B2 (en) 2001-06-04 2003-03-25 Donald T. Shannon Shrouded strain relief medical balloon device and method of use
US6952855B2 (en) 2001-06-29 2005-10-11 Homedics, Inc. Automatic electric toothbrush
US6981942B2 (en) 2001-11-19 2006-01-03 University Of Medicine And Dentristy Of New Jersey Temporary blood circulation assist device
AU2003236497A1 (en) 2002-06-11 2003-12-22 Walid Aboul-Hosn Expandable blood pump and related methods
US6841910B2 (en) 2002-10-02 2005-01-11 Quadrant Technology Corp. Magnetic coupling using halbach type magnet array
US7316678B2 (en) 2003-03-28 2008-01-08 Kensey Nash Corporation Catheter with associated extension lumen
US20040260237A1 (en) 2003-06-17 2004-12-23 Paul Squadrito Inflation adaptor with magnetically-assisted loading
DE10336902C5 (en) 2003-08-08 2019-04-25 Abiomed Europe Gmbh Intracardiac pumping device
US7229258B2 (en) 2003-09-25 2007-06-12 Medforte Research Foundation Streamlined unobstructed one-pass axial-flow pump
US7942804B2 (en) 2004-05-20 2011-05-17 Cor-Med Vascular, Inc. Replaceable expandable transmyocardial ventricular assist device
EP2151257B1 (en) 2004-08-13 2013-04-17 Delgado, Reynolds M., III Apparatus for long-term assisting a left ventricle to pump blood
US7524305B2 (en) 2004-09-07 2009-04-28 B. Braun Medical, Inc. Peel-away introducer and method for making the same
US7393181B2 (en) 2004-09-17 2008-07-01 The Penn State Research Foundation Expandable impeller pump
DE102004054714A1 (en) 2004-11-12 2006-05-24 Impella Cardiosystems Gmbh Foldable intravascular insertable blood pump
US7479102B2 (en) 2005-02-28 2009-01-20 Robert Jarvik Minimally invasive transvalvular ventricular assist device
DE102005035795A1 (en) 2005-05-03 2006-11-09 Rheinisch-Westfälisch Technische Hochschule Aachen Device for detecting physiological parameters inside the body
DE102005030472A1 (en) 2005-06-28 2007-01-04 Joachim-Georg Pfeffer Rod-shaped body
DE102005033950A1 (en) 2005-07-20 2007-01-25 E.E.P.D. Electronic Equipment Produktion & Distribution Gmbh Electronic device
DE102005039950A1 (en) 2005-08-24 2007-03-15 Wulfsberg, Jens Peter, Prof. Dr.-Ing. Electric drive for tissue ablation device, has drive motor, where drive is completely integrated in closed housing, and electrical energy required for drive motor is inductively transferred via housing by transformer
DE102006040301A1 (en) 2005-12-06 2008-03-06 Düring, Klaus, Dr. Device for splinting a cavity, organ path and / or vessel
CN102380135A (en) 2006-03-23 2012-03-21 宾州研究基金会 Heart assist device with expandable impeller pump
WO2007131516A1 (en) 2006-05-11 2007-11-22 Gabriele Krombach Catheter device for percutaneous interventions
US7681295B2 (en) 2006-06-29 2010-03-23 Skf Usa Inc. Method of making improved large diameter seals
US9028392B2 (en) 2006-12-01 2015-05-12 NuCardia, Inc. Medical device
US7722568B2 (en) 2007-01-29 2010-05-25 Onset Medical Corporation Expandable intra-aortic balloon pump sheath
US8079948B2 (en) 2007-08-29 2011-12-20 NuCardia, Inc. Article comprising an impeller
US8439859B2 (en) 2007-10-08 2013-05-14 Ais Gmbh Aachen Innovative Solutions Catheter device
US8489190B2 (en) 2007-10-08 2013-07-16 Ais Gmbh Aachen Innovative Solutions Catheter device
ATE480274T1 (en) 2007-10-08 2010-09-15 Ais Gmbh Aachen Innovative Sol CATHETER DEVICE
EP2194278A1 (en) 2008-12-05 2010-06-09 ECP Entwicklungsgesellschaft mbH Fluid pump with a rotor
EP2229965A1 (en) 2009-03-18 2010-09-22 ECP Entwicklungsgesellschaft mbH Fluid pump with particular form of a rotor blade

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4153048A (en) * 1977-09-14 1979-05-08 Cleveland Clinic Foundation Thermodilution catheter and method
US4747840A (en) * 1986-09-17 1988-05-31 Ladika Joseph E Selective pulmonary arteriograph catheter
US4777951A (en) * 1986-09-19 1988-10-18 Mansfield Scientific, Inc. Procedure and catheter instrument for treating patients for aortic stenosis
US6139487A (en) * 1997-04-02 2000-10-31 Impella Cardiotechnik Ag Intracardiac pump device
US6544216B1 (en) * 1998-05-13 2003-04-08 Impella Cardiotechnik Aktiengesellschaft Intracardiac blood pump
US7022100B1 (en) * 1999-09-03 2006-04-04 A-Med Systems, Inc. Guidable intravascular blood pump and related methods
US20020095210A1 (en) * 2001-01-16 2002-07-18 Finnegan Michael T. Heart pump graft connector and system

Cited By (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11260212B2 (en) 2016-10-25 2022-03-01 Magenta Medical Ltd. Ventricular assist device
US12090314B2 (en) 2016-10-25 2024-09-17 Magenta Medical Ltd. Ventricular assist device
US11839754B2 (en) 2016-10-25 2023-12-12 Magenta Medical Ltd Ventricular assist device
US11291825B2 (en) 2016-10-25 2022-04-05 Magenta Medical Ltd. Ventricular assist device
US11717670B2 (en) 2017-06-07 2023-08-08 Shifamed Holdings, LLP Intravascular fluid movement devices, systems, and methods of use
US11185677B2 (en) 2017-06-07 2021-11-30 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
US11511103B2 (en) 2017-11-13 2022-11-29 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
US11806116B2 (en) 2018-01-10 2023-11-07 Magenta Medical Ltd. Sensor for blood pump
US11185679B2 (en) 2018-01-10 2021-11-30 Magenta Medical Ltd. Blood-pressure-measurement tube
US11950889B2 (en) 2018-01-10 2024-04-09 Magenta Medical Ltd. Ventricular assist device
US12343518B2 (en) 2018-01-10 2025-07-01 Magenta Medical Ltd. Blood-pressure-measurement element
US11291826B2 (en) 2018-01-10 2022-04-05 Magenta Medical Ltd. Axially-elongatable frame and impeller
US11185680B2 (en) 2018-01-10 2021-11-30 Magenta Medical Ltd. Ventricular assist device
US11944413B2 (en) 2018-01-10 2024-04-02 Magenta Medical Ltd. Ventricular assist device
US12207906B2 (en) 2018-01-10 2025-01-28 Magenta Medical Ltd. Tube for ventricular assist device
US11844592B2 (en) 2018-01-10 2023-12-19 Magenta Medical Ltd. Impeller and frame for blood pump
US11806117B2 (en) 2018-01-10 2023-11-07 Magenta Medical Ltd. Drive cable for blood pump
US12127820B2 (en) 2018-01-10 2024-10-29 Magenta Medical Ltd. Ventricular assist device
US10905808B2 (en) 2018-01-10 2021-02-02 Magenta Medical Ltd. Drive cable for use with a blood pump
US11684275B2 (en) 2018-01-10 2023-06-27 Magenta Medical Ltd. Distal tip element for blood pump
US11690521B2 (en) 2018-01-10 2023-07-04 Magenta Medical Ltd. Impeller for blood pump
US10994120B2 (en) 2018-01-10 2021-05-04 Magenta Medical Ltd. Ventricular assist device
US10881770B2 (en) 2018-01-10 2021-01-05 Magenta Medical Ltd. Impeller for blood pump
US12059235B2 (en) 2018-01-10 2024-08-13 Magenta Medical Ltd. Blood pump catheter with dual-function continuous lumen
US10722631B2 (en) 2018-02-01 2020-07-28 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US11229784B2 (en) 2018-02-01 2022-01-25 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US12076545B2 (en) 2018-02-01 2024-09-03 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US12403296B2 (en) 2018-05-30 2025-09-02 Kardion Gmbh Apparatus for anchoring a ventricular assist system in a blood vessel, operating method, production method for producing an apparatus and ventricular assist system
US12161857B2 (en) 2018-07-31 2024-12-10 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US12220570B2 (en) 2018-10-05 2025-02-11 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US11666747B2 (en) 2019-01-24 2023-06-06 Magenta Medical Ltd. Manufacturing an impeller
US11471663B2 (en) 2019-01-24 2022-10-18 Magenta Medical Ltd. Frame for blood pump
US12023476B2 (en) 2019-01-24 2024-07-02 Magenta Medical Ltd. Duckbill valve for use with percutaneous medical devices
US11964143B2 (en) 2019-01-24 2024-04-23 Magenta Medical Ltd. Flexible drive cable with rigid axial shaft
US11944800B2 (en) 2019-01-24 2024-04-02 Magenta Medical Ltd. Atraumatic balloon for blood pump
US11191944B2 (en) 2019-01-24 2021-12-07 Magenta Medical Ltd. Distal tip element for a ventricular assist device
US11285309B2 (en) 2019-01-24 2022-03-29 Magenta Medical Ltd. Ventricular assist device with stabilized impeller
US12329957B2 (en) 2019-01-24 2025-06-17 Magenta Medical Ltd. Impeller housing
US11298523B2 (en) 2019-01-24 2022-04-12 Magenta Medical Ltd. Impeller housing
US11484699B2 (en) 2019-01-24 2022-11-01 Magenta Medical Ltd. Welding overtube
US12186545B2 (en) 2019-01-24 2025-01-07 Magenta Medical Ltd. Impleller and frame for a blood pump
US11964145B2 (en) 2019-07-12 2024-04-23 Shifamed Holdings, Llc Intravascular blood pumps and methods of manufacture and use
US11654275B2 (en) 2019-07-22 2023-05-23 Shifamed Holdings, Llc Intravascular blood pumps with struts and methods of use and manufacture
US12121713B2 (en) 2019-09-25 2024-10-22 Shifamed Holdings, Llc Catheter blood pumps and collapsible blood conduits
US12102815B2 (en) 2019-09-25 2024-10-01 Shifamed Holdings, Llc Catheter blood pumps and collapsible pump housings
US11724089B2 (en) 2019-09-25 2023-08-15 Shifamed Holdings, Llc Intravascular blood pump systems and methods of use and control thereof
US12409310B2 (en) 2019-12-11 2025-09-09 Shifamed Holdings, Llc Descending aorta and vena cava blood pumps
US12128227B2 (en) 2020-04-07 2024-10-29 Magenta Medical Ltd. Manufacture of an impeller
US12440665B2 (en) 2021-11-22 2025-10-14 Magenta Medical Ltd. Magnetic phase detection
US12440663B2 (en) 2022-04-18 2025-10-14 Magenta Medical Ltd. Curved tube for a ventricular assist device

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DE10336902B3 (en) 2004-08-19
AU2004264655B2 (en) 2010-06-10
US9833550B2 (en) 2017-12-05
EP1651290B1 (en) 2012-01-18
US20200222603A1 (en) 2020-07-16
AU2004264655A1 (en) 2005-02-24
JP2007501644A (en) 2007-02-01
US12023477B2 (en) 2024-07-02
US20210060222A1 (en) 2021-03-04
US20230099453A1 (en) 2023-03-30
DE10336902C5 (en) 2019-04-25
US20160129170A1 (en) 2016-05-12
US11491320B2 (en) 2022-11-08
US20100268017A1 (en) 2010-10-21
JP4806350B2 (en) 2011-11-02
US9872948B2 (en) 2018-01-23
EP1651290B2 (en) 2018-05-30
WO2005016416A1 (en) 2005-02-24
EP1651290A1 (en) 2006-05-03

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