Source: https://patents.google.com/patent/EP3434227A1/en
Timestamp: 2019-09-16 11:37:00
Document Index: 613594853

Matched Legal Cases: ['Application No. 12', 'Application No. 61', 'Application No. 11', 'art.\n23', 'art,\n25', 'art.\n26', 'art.\n28', 'art.\n29', 'art.\n30']

EP3434227A1 - Ventricular assist device for intraventricular placement - Google Patents
EP3434227A1
EP3434227A1 EP18192906.8A EP18192906A EP3434227A1 EP 3434227 A1 EP3434227 A1 EP 3434227A1 EP 18192906 A EP18192906 A EP 18192906A EP 3434227 A1 EP3434227 A1 EP 3434227A1
EP18192906.8A
Jeffrey A Larose
Charles R Shambaugh
Steve A WHITE
2008-02-08 Priority to US6514008P priority Critical
2008-11-07 Priority to US19868208P priority
2009-02-06 Application filed by HeartWare Inc filed Critical HeartWare Inc
2009-02-06 Priority to PCT/US2009/000762 priority patent/WO2009099644A1/en
2009-02-06 Priority to EP09707311.8A priority patent/EP2249746B1/en
2019-01-30 Publication of EP3434227A1 publication Critical patent/EP3434227A1/en
There is provided a blood pump for intraventricular placement inside a heart of a mammalian subject comprising. The blood pump comprises a pump that defines a pump axis that is and positionable within the heart. The pump includes an inlet and an outlet, the inlet and outlet being positioned along the pump axis, a rotor and at least one electric drive coil for magnetically driving the rotor. The blood pump further comprises wiring extending along a defined pathway offset from the pump axis extending from outside of the pump and into the at least one electric drive coil.
In certain disease states, the heart lacks sufficient pumping capacity to meet the needs of the body. This inadequacy can be alleviated by providing a mechanical pumping device referred to as a ventricular assist device ("VAD") to supplement the pumping action of the heart. Considerable effort has been devoted to providing a VAD which can be implanted and which can remain in operation for months or years to keep the patient alive while the heart heals, or which can remain in operation permanently or until a suitable donor heart becomes available if the heart does not heal.
As described, for example, in U.S. Patent Nos 5,376,114 and 6,217,541 , certain VADs having pumps are arranged so that at least a portion of the pump is disposed within the heart when the VAD is implanted within the patient. These VADs incorporate pumps which are connected to separate electric motors by elongated driveshafts. Such shaft-driven pumps suffer from significant drawbacks. Commonly assigned, copending U.S. Patent Application 12/072,471 , the disclosure of which is hereby incorporated by reference herein, discloses a VAD having a unitary pump and motor adapted for positioning within the arterial system as, for example, within the aorta.
The words "proximal" and "distal" are used herein to denote directions and ends of the device and components. As used herein, when referring the ventricular assist device or components, the term "proximal" refers to the direction toward the surgeon or other operating room personnel during installation of the device and the term "distal" has the opposite meaning.
One aspect of the present invention provides a ventricular assist device for intraventricular placement inside a heart of a mammalian subject. The device preferably includes an anchor element such as a ring configured to be mounted adjacent an apex of the subject's heart, and also desirably includes an elongate member having proximal and distal ends. The device according to this aspect of the invention desirably also includes a pump having a housing, an inlet and an outlet, a rotor within the housing and electric drive coils carried on the housing for magnetically driving the rotor. Preferably, when the device is implanted in the heart, the anchor element and the pump are fixed to the rigid elongate member remote from one another so that the rigid elongate member maintains the pump in position relative to the anchor element and hence with respect to the heart.
Fig. 1 is a diagrammatic perspective view of a ventricular assist device according to one embodiment of the present invention.
Figs 3 and 4 are perspective views of certain components used in the device of Fig. 1.
Figs 5 and 6 are perspective interior views depicting certain portions of the device shown in Fig. 1.
Figs 7a, 7b and 7c are fragmentary views depicting a portion of a component used in the device of Fig. 1.
Figs 8a and 8b are diagrammatic perspective views depicting portions of devices according to further embodiments of the invention.
Figs 9 and 10 are diagrammatic views of the ventricular assist device of Fig. 1 in an installed condition, in conjunction with the certain structures of the heart.
Fig. 12 is a diagrammatic sectional view along line A-A in Fig. 11.
Figs 13-19 are diagrammatic perspective views depicting portions of device according to still further embodiments.
Referring to the drawings, wherein like reference numerals refer to like elements, there is shown in Figs 1-2, an embodiment of the ventricular assist device of the present invention designated generally by reference numeral 10. As shown in those figures, device 10 has four distinct sections including a pump 20, an outflow cannula 40, a rigid elongate member 60, and a ring 80.
Pump 20 is shown in Figs 2-5. Pump 20 is an axial flow pump having an inlet 21 and an outlet 23 arranged on an axis 19 referred to herein as the pump axis. The pump has an axial bore 29 defined by a tubular housing 22 which extends between the inlet and the outlet. Housing 22 is formed from biocompatible materials such as ceramics and metals such as titanium. The materials used for those portions of the housing disposed inside the motor stator discussed below desirably are non-magnetic dielectric materials such as ceramics.
The features of the rotor and stator may be generally as shown in the aforementioned copending, commonly assigned U.S. Patent Application No. 12/072,471 . However, the pump of this embodiment typically is larger than a pump intended for positioning within an artery. For example, the pump used in this embodiment may be about 21 mm outside diameter and about 34 mm long, and may have a rotor about 10 mm in outside diameter. The pump desirably is arranged to deliver about 4 to 6 L/min flow rate against a pressure head of about 100 mm Hg. As an alternative to the unitary magnetic rotor discussed above, a conventional rotor design involving placement of magnets sealed within a rotor formed from non-magnetic material may be used.
The pump also includes diffuser blades 28 are mounted within housing 22 downstream from rotor 26, between the rotor and the outlet 23. As best seen in Figs 3, 5, and 6, each diffuser blade is generally in the form of a plate-like vane secured to the housing and projecting radially into the bore from the wall of the housing. As best seen in Fig. 3, the upstream ends of the diffuser blades 28, closest to rotor 26, curve in a circumferential direction around the axis 19. The direction of curvature of the diffuser blades is opposite to the direction of curvature of the rotor blades. Preferably, the number of diffuser blades is unequal to the number of rotor blades, and the number of diffuser blades is not an integral multiple or divisor of the number of pump blades. Thus, where the rotor has an even number of blades, the pump desirably has an odd number of diffuser blades, such as three or five diffuser blades 28. This arrangement helps to maximize the stability of the rotor and minimize vibration in operation of the pump. However, it should be understood that two, four, or more than five diffuser blades 28 may be utilized. During operation, the blood passing downstream from the rotor has rotational momentum imparted by the rotor. As the blood encounters the diffuser blades, this rotational momentum is converted to axial momentum and pressure head. Thus, the diffuser blades serve to reclaim the energy used to create the rotational motion and convert that energy to useful pumping work. In this embodiment, the diffuser blades are not attached to one another at the axis. This arrangement conserves space within the bore, and thus maximizes axial flow.
The distal end 63 of member 60 is received in recess 38 of first attachment portion 30 of the pump 20. Preferably, the distal end of member 60 is joined to the attachment portion of the pump by a permanent, fluid-tight connection as, for example, by welding member 60 to the pump shroud. Electrical power wiring 67 extends from the stator 24 of the motor through bore 62 of member 60 and out of the member through a fitting 100 at the proximal end of the member. Preferably, there is a fluid-tight feedthrough (not shown) at fitting 100, at the connection between the distal end 63 and the attachment portion of the pump, or both. The electrical wiring extends out of the fitting 100 to a source of electrical power (not shown) external to the body of the patient or implanted within the body of the patient. Preferably, the power source is a transcutaneous energy transfer or "TET" device. Such a device includes an implantable unit which has a battery and an induction coil. The implantable unit typically is mounted remote from the heart, near the patient's skin. Energy is supplied to the induction coil of the implantable unit by an induction coil incorporated in an external unit worn by the patient. The internal battery provides continued operation during intervals when the patient is not wearing the external unit.
An outflow cannula 40 of extends distally from distal end 27 of pump 20. Outflow cannula 40 is generally in the form of a hollow tube having a proximal end attached to pump 20 and communicating with the outlet 23 (Fig. 3) of the pump. The outflow cannula has a tip 70 at its distal end.
Preferably, outflow cannula 40 is a single molded polymer piece made of thermoplastic polyurethanes (segmented and/or copolymerized with silicone, polycarbonate-urethanes, polyether-urethanes, aliphatic polycarbonate, or other additives), silicone, polycarbonate-urethanes, polyether-urethanes, aliphatic polycarbonate, silicone material with or without catalyst metals and possibly sulfonated styrenic polymers. Preferably, outflow cannula 40 may be cast with or without titanium wire structures for bend enhancement properties and non- invasive visualization of a catheter typically under x-ray or fluoroscopy. The outflow cannula 40 may contain barium sulfate or other minerals, or metallic marker bands to provide landmark location visualization by fluoroscopic, CAT or other radiological techniques during or after implantation in the patient.
Outflow cannula 40 may be straight or bent and desirably has an appropriate stiffness and hardness to accommodate the native heart and aortic root geometry and also to have non-traumatic contact with tissues. The diameter of the cannula can be tapered from pump body 20 to a smaller diameter near the distal end of the cannula. As further described below, the distal end of the cannula will project through the aortic valve when the apparatus is implanted in a patient. A cannula which tapers in diameter towards its distal end provides relatively low flow resistance due to its large diameter at the proximal end, but also provides a desirable small diameter portion at the aortic valve. The small-diameter portion at the aortic valve helps to minimize aortic valve insufficiency, i.e. retrograde flow through the valve due to poor sealing of the tri-leaflets around the cannula. Desirably, the cannula is round in cross-section, at least in the region near tip 70 which will extend through the aortic valve when implanted. A round cross-sectional shape also minimizes aortic valve insufficiency. Merely by way of example, a cannula for carrying about 5 1/min of blood may have a mean interior diameter of about 6 mm.
As best seen in Figs 7A-7C, tip 70 has a circumferential surface which tapers inwardly toward the axis of the cannula in the distal direction, and thus converges toward the distal extremity 74 of the cannula. In the embodiment illustrated, the distal surface of the tip defines a smooth, dome- like shape at the distal extremity of the tip. A plurality of openings 72 extend through the circumferential surface of the tip. Openings 72 communicate with the interior bore of the cannula. When blood is discharged through openings 72, the flow has a radial component, and will provide a hydrodynamic self centering force for cannula 40. The centering action is believed to further minimize aortic valve insufficiency. Moreover, even if the cannula tip is resting against an arterial wall, the plural openings spaced around the circumference of the tip will still provide good blood flow. The tip 70 geometry is described in more detail in U.S. Provisional Patent Application No. 61/135,004, filed July 16, 2008 , and entitled "CANNULA TIP FOR USE WITH A VAD" which application is hereby incorporated by reference in its entirety in the present application.
A family of outflow cannula 40 sizes may be developed to better accommodate the variety of patent native heart sizes. It is preferred that the outflow cannula is preattached to pump 20; however, various cannula sizes may be supplied with the device for attachment in the operating room prior to implantation. The attachment between the outflow cannula and the pump may be of any configuration suitable for maintaining the proximal end in place. The proximal end of the cannula may extend over the distal end of pump housing 22, and may be secured in place by an adhesive bond. Alternatively, a crimp ring may surround the proximal end of the cannula, so that the wall of the cannula is held between the crimp ring and the pump housing.
In this embodiment, the device 10 also includes an anchoring element in the form of a ring 80. Preferably, ring 80 is adapted for mounting adjacent the apex of the patient's heart by sewing around a perimeter of ring 80 to tissue along a wall of the patient's heart. For example, ring 80 may be a metallic structure having a peripheral flange with numerous holes for sewing or stapling the ring to the heart wall. The periphery of ring 80 may be covered with a fabric material such as for example polyester material, expanded polytetrafluoroethylene, felt or the like for promoting tissue growth over the ring to further secure the ring in place. U.S. Patent Application No. 11/289,410 , entitled "IMPLANT CONNECTOR," teaches such a ring component and is herein incorporated by reference in its entirety in the present application.
In a method of implantation according to one embodiment of the invention, the apparatus discussed above, including the ring 80, member 60, pump 20 and outflow cannula 40 is provided as a pre-assembled unit. The surgeon gains access to the heart, preferably using a left subcostal or left thoracotomy incision exposing the left ventricular apex. A pledgeted purse string suture is then applied to the epicardium circumferentially over the pump insertion site. A slit incision or an incision in the form of a cross or X, commonly referred to as a "crux" incision, is made through the apex of the heart into the interior of the left ventricle using a cutting instrument such as a scalpel. Pump 20, member 60 and outflow cannula 40 are then inserted through the crux incision or slit incision and positioned within the left ventricle so that cannula 40 extends through the aortic valve into the aorta. Ring 80 is positioned on the outside of the heart as depicted in Figs 9 and 10. Proper placement of the components can be verified by fluoroscope or other imaging technique. After placement, the pump can be started by applying electrical power from the external or implantable power source, and proper outflow may be verified using echocardiography. After outflow is verified, crux incision is closed around member 60, as by suturing, and ring 80 is secured to the exterior of the cardiac wall.
As shown in Figs 9 and 10, in the implanted condition, ring 80 is mounted adjacent the apex of the subject's heart. Ring 80 and pump body 20 are connected to elongate member 60 remote from one another so that rigid elongate member 60 maintains pump 20 in position relative to ring 80. This maintains the pump and outflow cannula 40 in position relative to the heart.
In the implanted condition, the axis 19 of the pump extends near the apex of the heart, and the inlet 21 of the pump 20 is aimed generally in the direction toward the apex of the heart. The length of elongate member 60 is such that the inlet 21 of pump 20 is remote from the aortic valve. This position and orientation provide certain advantages. Fibrous structures of the aortic valve, just proximal to the opening of the valve, do not get sucked into the inlet of pump 20. Moreover, the inlet of the pump will not be occluded by the ventricular wall or the interventricular septum of the heart.
The ventricular assist device according to the embodiment discussed above thus provides an intra-ventricular, full output, wearless blood pump that is sized for thoracotomy, sub-costal or other implantation method not requiring a sternotomy. The majority of the device sits within the left ventricle and pumps blood distal to the aortic valve to provide cardiac assistance. The patient population which is typically suited for implantation of this device is similar to the biventricular pacing population; congestive heart failure patients who are failing medical therapy and are willing to undergo a 4 to 6-hour procedure requiring a maximum hospital stay of approximately five days. These patients are very sick and will need 4 to 6 L/min of support initially and may only need 2 to 3 L/min for long term.
In a further variant, the spherical ball 90 used in the arrangement of Fig. 1 is fixed within the spherical socket of the ring or other anchoring element. In yet another variant, the spherical ball and socket may be replaced by a pivotable joint which allows pivoting movement of the anchoring element about just one axis of rotation. In further embodiments, the position of the anchoring element may be adjustable along the length of the elongated element. For example, the anchoring element or ring may include a gripper arranged so that the gripper may be tightened around the elongated member by rotating or otherwise moving one portion of the anchoring element relative to another portion, and so that the gripper may be locked in a tightened condition. For example, the anchor element may incorporate a collet and collet chuck similar to those used to hold machinist's tools. In yet another variant, the elongated member may be threadedly engaged with the anchoring element so that the position of the anchoring element may be adjusted towards and away. from the pump by rotating the anchoring element, and then locked in position using a lock nut or other device to prevent further rotation. In still further variants, the elongated member 60 may have appreciable flexibility while still having enough rigidity to maintain the pump and outflow cannula in position. For example, the elongated member 60 may be formed as an elongated coil spring of relatively stiff wire. The electrical wiring extending within the elongated member may be coiled or otherwise convoluted to provide increase resistance to fatigue in flexing.
Figs 8a and 8b show two alternative configurations of the elongate member and anchoring element. As seen in Fig. 8a, the elongate member 160 has a ring or anchoring element 102 disposed near the proximal end thereof. Anchoring element 102 has a tapered distal surface 103 and a proximal surface 105 which extends substantially perpendicular to the axis of elongation of member 160. In the implantation procedure, anchoring element 102 is advanced into the interior of the ventricle through the crux incision. The incision is closed around the portion of member 160 lying proximal to surface 105, leaving surface 105 of the anchoring element engaged with the interior surface of the myocardium. Purse string sutures may be used on the external myocardium surface Anchoring element 102 acts in a similar manner to the anchoring element or ring 80 discussed above, to prevent axial translation of the elongated member, pump and outflow cannula relative to the heart. When implanted in this manner, the myocardium is closed around that portion of elongate member 160 proximal to anchoring element 102. At this region, rigid member 60 optionally may be provided with a roughened surface, as by sintering, to promote tissue ingrowth for hemostasis. Alternatively, this portion of the elongated member may be left smooth. An interior anchoring element such as member 102 may be used in lieu of, or in addition to, an exterior securement member such as the ring 80 discussed above.
The apparatus shown in Fig. 8b is similar to the apparatus of Fig. 8a, except that the elongated member includes a larger diameter stem section 104 extending proximally from the anchoring element. The enlarged section 104 provides greater surface area for tissue ingrowth. The surface of section 104 may be treated to enhance tissue ingrowth as, for example, by sintering.
The elongate member may have various configurations. It should be understood that these alternative configurations are merely exemplary and different configurations may be used without departing from the scope of the present invention. As shown in Figs 11-12, an elongate member 160 has a proximal end 161, a distal end 163 and a bore 162 therethrough. In this embodiment, elongate member 160 has an axis along its direction of elongation which axis is parallel to the axis 119 of the pump body but offset from axis 119 in a direction transverse to both axes. Elongate member 160 includes a hydrodynamic outer surface 165, i.e. a streamlined surface as seen in cross-section in Fig. 12. The streamlined surface 165 facilitates fluid flow within the left ventricle in the direction across elongate member 160.
As shown in Fig. 15, an elongate member 360 is curved along the length of the member. Elongate member 360 preferably has a bore 362 structured to allow electrical power wiring to be housed and extend therethrough.
Outflow cannula 40 may be replaced by a graft lumen material fixed to pump 20 as described herein. The graft lumen may be homologous polyester with gel structure, or impregnated with heparin or thromboresistant materials, or augmented with targeted tissue ingrowth promotion factors such as collagen. Similar to the outflow cannula 40, the graft may be tapered, fitted with a polymer tip, or fashioned into a terminal tip. The tip of the graft may be arranged to provide hydrodynamic self centering as described above.
In still other embodiments, the outflow cannula may be non-circular and rather take the shape of other geometric configurations such as triangular, oval, elliptical, or the like. As shown in Figs 17-18, outflow cannula 140 is generally triangular in cross-section. Outflow cannula 140 may be straight or bent and desirably has an appropriate stiffness and hardness to accommodate the native heart and aortic root geometry and also to have non-traumatic contact with tissues. Here again, the cross- sectional dimensions of the cannula preferably taper to smaller dimensions in the distal direction, away from pump body 20. Here again, the outflow cannula preferably projects through the aortic valve when the apparatus is implanted in a patient. Here again, the use of a relatively small cross-section at the aortic valve helps to minimize aortic valve insufficiency, i.e. retrograde flow through the valve due to poor sealing of the tri-leaflets around the cannula.
In a further embodiment depicted schematically in Fig. 19, the diffuser blades 128 of the pump, may be connected to a common hub 131 extending along the axis 19 of the pump. The diffuser blades and hub may be fabricated as a separate unit, and this unit may be installed within the tubular housing 122 of the pump distal to the rotor 134. Although the invention herein has been described with reference to particular embodiments, it is to be understood that these embodiments are merely illustrative of the principles and applications of the present invention. It is therefore to be understood that numerous modifications may be made to the illustrative embodiments and that other arrangements may be devised without departing from the spirit and scope of the present invention as defined by the appended claims.
Certain aspects and embodiments of the invention are described in the clauses below:
an anchor element configured to be mounted to the subject's heart;
an elongate member having proximal and distal ends; and
a pump comprising a housing, an inlet and an outlet, a rotor within the housing and electric drive coils carried on the housing for magnetically driving the rotor,
wherein the anchor element and the pump are connected to the elongate member remote from one another.
2. The ventricular assist device of clause 1, wherein the anchor element is configured to be mounted to the subject's heart adjacent the apex thereof.
3. The ventricular assist device of clause 1, wherein the pump has an axis extending between the inlet and the outlet, and the elongate member has an axis offset from the axis of the pump.
4. The ventricular assist device of clause 3, wherein the axis of the elongate member is substantially parallel to the axis of the pump.
5. The ventricular assist device of clause 1, wherein the elongate member includes a bore extending in the proximal and distal directions thereof, the device further comprising wiring extending through the bore to the pump.
6. The ventricular assist device of clause 1, further comprising a spherical ball mounted to the rigid elongate member.
7. The ventricular assist device of clause 5, wherein the anchor element includes a spherical socket adapted to engage the spherical ball such that the anchor element is pivotally mounted to the rigid elongate member.
8. The ventricular assist device of clause 1, wherein the anchor element is fixed to the elongate member.
9. The ventricular assist device of clause 1, wherein the anchor element is a ring adapted for fixation on the exterior surface of the heart wall.
10. The ventricular assist device of clause 1, wherein the elongate member has a hydrodynamic outer surface.
11. The ventricular assist device of clause 1, wherein the elongate member is curved.
12. The ventricular assist device of clause 1, wherein the elongate member is channel shaped.
13. The ventricular assist device of clause 1 having a plurality of anchor elements and elongate members.
14. The ventricular assist device of clause 1, wherein the anchor element is non-circular in cross-section.
15. The ventricular assist device of clause 1 wherein the anchor element is adapted to bear on the interior of surface of the heart wall.
16. The ventricular assist device of clause 1, further comprising a tubular outflow cannula defining a bore, the bore having an inlet at a proximal end thereof connected to the outlet of the pump.
17. The ventricular assist device of clause 16, wherein the outflow cannula includes a tip at the distal end thereof, the tip having a plurality of openings.
18. The ventricular assist device of clause 17, wherein the tip of the outflow cannula projects through an aortic valve but terminates short of an arch of the aorta.
19. The ventricular assist device of clause 16, wherein the outflow cannula is tapered in the distal direction.
20. The ventricular assist device of clause 16, wherein the outflow cannula has a generally triangular cross-section at a region proximal to the tip.
21. The ventricular assist device of clause 16, wherein the outflow cannula includes a plurality of side holes extending between the bore of the cannula and an exterior surface of the cannula proximal to the tip of the cannula.
22. The ventricular assist device of clause 1, wherein the anchor element is a ring adapted for mounting adjacent the apex of the patient's heart by sewing ring to tissue along a wall of the patient's heart.
23. The ventricular assist device of clause 1, wherein the position of the anchor element in the lengthwise direction of the elongate member is adjustable.
24. A ventricular assist device for intraventricular placement inside a heart of a mammalian subject comprising:
a rigid elongate member having a proximal and distal end; and
a housing, an outflow cannula having a tip, the tip having a distal end projecting through an aortic valve of the subject's heart,
25. The ventricular assist device of clause 24, wherein the tip terminates short of an arch of the aorta of the subject's heart.
26. A method of installing a ventricular assist device in a mammalian subject comprising:
(a) mounting a pump to the subject so that an inlet of the pump communicates with the left ventricle of the heart; and
(b) positioning an outflow cannula of the pump so that the outflow cannula extends from within the left ventricle through the aortic valve but terminates short of the arch of the aorta.
27. A method of clause 26 wherein the step of mounting a pump to the subject includes mounting the pump within the left ventricle of the heart.
28. A method of clause 27 further including engaging an anchor element with the wall of the heart near the apex of the heart so that the anchor element maintains the pump and outflow cannula in position within the heart.
29. A method of placing a ventricular assist device at a location inside a heart of a mammalian subject comprising:
providing an anchor element and a pump connected to a rigid elongate member remote from one another advancing the pump through a wall in an apex of the subject's heart and into an intraventricular region of the subject's heart; and mounting the anchor element to an apex of the subject's heart.
30. The method of clause 29, wherein the pump comprises a housing, an inlet and an outlet, a rotor within the housing and electric drive coils carried on the housing for magnetically driving the rotor.
31. The method of clause 30, wherein the pump further comprises a tubular outflow cannula defining a bore, the bore having an inlet at a proximal end thereof connected to the outlet of the pump, wherein the outflow cannula includes a tip at the distal end thereof, the tip having a plurality of openings, wherein the tip of the outflow cannula projects through an aortic valve.
32. The method of clause 29 wherein an inlet of the pump is positioned so that the inlet is remote from the aortic valve and faces generally in a direction toward the apex of the heart.
A blood pump (10) for intraventricular placement inside a heart of a mammalian subject comprising:
a pump (20;120) defining a pump axis (19; 119) and positionable within the heart, the pump including an inlet (21; 121) and an outlet (23; 123), the inlet and outlet being positioned along the pump axis, a rotor (26; 126), and at least one electric drive coil for magnetically driving the rotor; and
wiring (67) extending along a defined pathway offset from the pump axis extending from outside of the pump and into the at least one electric drive coil.
The blood pump (10) of claim 1, wherein the defined pathway is in communication with the inlet of the pump without occluding blood flow into the inlet of the pump.
The blood pump (10) of claim 1, wherein the defined pathway includes an elongate member (260) including a bore (62; 162; 262; 362).
The blood pump (10) of claim 3, wherein the bore (62; 162; 262; 362) is in communication with the inlet (21; 121) of the pump (20; 120) without occluding blood flow into the inlet of the pump.
The blood pump (10) of claim 1, further comprising a tubular outflow cannula (40; 140) defining a bore, the bore having an inlet at a proximal end thereof connected to the outlet (23; 123) of the pump (20; 120).
The blood pump (10) of claim 1, wherein the outflow cannula (40) includes a tip (70) at the distal end thereof, the tip having a plurality of openings (72); preferably wherein the tip of the outflow cannula projects through an aortic valve but terminates short of an arch (110) of the aorta.
The blood pump (10) of claim 3, wherein the elongate member (260) has a hydrodynamic outer surface.
The blood pump (10) of Claim 3, wherein the elongate member (260) is curved.
The blood pump (10) of claim 3, wherein the elongate member (260) is channel shaped.
The blood pump (10) of claim 3, wherein the axis of the elongate member (260) is substantially parallel to the axis of the pump.
EP18192906.8A 2008-02-08 2009-02-06 Ventricular assist device for intraventricular placement Pending EP3434227A1 (en)
US6514008P true 2008-02-08 2008-02-08
US19868208P true 2008-11-07 2008-11-07
PCT/US2009/000762 WO2009099644A1 (en) 2008-02-08 2009-02-06 Ventricular assist device for intraventricular placement
EP09707311.8A EP2249746B1 (en) 2008-02-08 2009-02-06 Ventricular assist device for intraventricular placement
EP09707311.8A Division EP2249746B1 (en) 2008-02-08 2009-02-06 Ventricular assist device for intraventricular placement
EP3434227A1 true EP3434227A1 (en) 2019-01-30
EP18192906.8A Pending EP3434227A1 (en) 2008-02-08 2009-02-06 Ventricular assist device for intraventricular placement
EP09707311.8A Active EP2249746B1 (en) 2008-02-08 2009-02-06 Ventricular assist device for intraventricular placement
EP (2) EP3434227A1 (en)
AU (1) AU2009210744B2 (en)
IL (1) IL207355A (en)
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2009-02-06 EP EP18192906.8A patent/EP3434227A1/en active Pending
2009-02-06 CN CN 200980104189 patent/CN101969886B/en active IP Right Grant
2009-02-06 EP EP09707311.8A patent/EP2249746B1/en active Active
2009-02-06 WO PCT/US2009/000762 patent/WO2009099644A1/en active Application Filing
2009-02-06 US US12/322,746 patent/US8852072B2/en active Active
2009-02-06 AU AU2009210744A patent/AU2009210744B2/en not_active Ceased
2009-02-06 KR KR1020107019415A patent/KR101621486B1/en active IP Right Grant
2009-02-06 CA CA2713865A patent/CA2713865C/en active Active
2010-08-02 IL IL207355A patent/IL207355A/en active IP Right Grant
2014-08-28 US US14/471,783 patent/US9173984B2/en active Active
2015-09-28 US US14/867,696 patent/US9579437B2/en active Active
2017-01-26 US US15/416,404 patent/US9956333B2/en active Active
AU2009210744B2 (en) 2014-06-12
US20090203957A1 (en) 2009-08-13
EP2249746B1 (en) 2018-10-03
IL207355D0 (en) 2010-12-30
US20170165408A1 (en) 2017-06-15
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2019-02-20 RIN1 Information on inventor provided before grant (corrected)
Inventor name: WHITE, STEVE A
Inventor name: TAMEZ, DANIEL
Inventor name: LAROSE, JEFFREY A
Inventor name: SHAMBAUGH, CHARLES R