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WO2021101622A1 - Systèmes et procédés de pose pour dispositifs d'assistance cardiaque implantables - Google Patents

Systèmes et procédés de pose pour dispositifs d'assistance cardiaque implantables Download PDF

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Publication number
WO2021101622A1
WO2021101622A1 PCT/US2020/051841 US2020051841W WO2021101622A1 WO 2021101622 A1 WO2021101622 A1 WO 2021101622A1 US 2020051841 W US2020051841 W US 2020051841W WO 2021101622 A1 WO2021101622 A1 WO 2021101622A1
Authority
WO
WIPO (PCT)
Prior art keywords
conduit
pump
delivery sheath
flanges
delivery
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.)
Ceased
Application number
PCT/US2020/051841
Other languages
English (en)
Inventor
Joshua D. Cross
Robert M. DEPUE
Paul D. Goodman
Brett J. Wham
Dustin C. Burkart
Zachary A. CRANNELL
Richard D. STRONES
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
WL Gore and Associates Inc
Original Assignee
WL Gore and Associates Inc
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by WL Gore and Associates Inc filed Critical WL Gore and Associates Inc
Publication of WO2021101622A1 publication Critical patent/WO2021101622A1/fr
Anticipated expiration legal-status Critical
Ceased 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
    • A61M60/20—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
    • A61M60/10—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
    • A61M60/139—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting inside the aorta, e.g. intra-aortic balloon pumps
    • 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
    • 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
    • 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
    • A61M60/226—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 radial components
    • A61M60/232—Centrifugal 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
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—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
    • 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
    • A61M60/859—Connections therefor
    • 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
    • A61M60/861—Connections or anchorings for connecting or anchoring pumps or pumping devices to parts of the patient's body
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00234—Surgical instruments, devices or methods for minimally invasive surgery
    • A61B2017/00238—Type of minimally invasive operation
    • A61B2017/00243—Type of minimally invasive operation cardiac
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/11—Surgical instruments, devices or methods for performing anastomosis; Buttons for anastomosis
    • A61B2017/1107—Surgical instruments, devices or methods for performing anastomosis; Buttons for anastomosis for blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/11—Surgical instruments, devices or methods for performing anastomosis; Buttons for anastomosis
    • A61B2017/1139—Side-to-side connections, e.g. shunt or X-connections

Definitions

  • the present disclosure relates generally to medical devices and more specifically to implantable cardiac assist devices and supporting structures configured to operate within a patient’s vasculature and that can be minimally invasively delivered via a catheter.
  • Cardiac assist devices generally relate to systems that include a pump that assists heart function without replacing the heart in order to improve hemodynamics.
  • the pump may be placed outside the patient's body (extra- or para-corporeal devices), or within the patient’s abdomen such as in the pericardial cavity beneath or above the diaphragm (intracorporeal device). Attempts have also been made to place such pumps within the patient’s vasculature, including within the heart itself.
  • a device for cardiac assistance includes a barrel portion including a lumen for fluid flow; a first flange at a first end of the barrel portion and configured to expand from a reduced diameter to engage a first tissue wall side; a second flange at a second end of the barrel portion and configured to expand from a reduced diameter to engage a second tissue wall side; and one or more anchor elements arranged within the barrel portion and configured to releasably engage and a pump arranged within the barrel portion.
  • Example 2 further to the device of Example 1 , the barrel portion, and the first flange, the second flange, and form a unitary structure that is a conduit.
  • Example 3 further to the device of Example 2, the one or more anchor elements are arranged within the barrel portion and extend within the lumen.
  • the first flange, the second flange, and the barrel portion are formed by struts having one or more of differing widths or differing depths within the barrel portion and at least one of the first flange and the second flange.
  • the struts include a curvature that extends portions of the flanges toward a center of the barrel portion.
  • a portion of the struts within at least one of the first flange and the second flange include a width less than a portion of the struts within the barrel portion.
  • a portion of the struts within the barrel portion include a depth less than a portion of the struts within at least one of the first flange and the second flange.
  • Example 8 further to the device of any one of Examples 2-7, the one or more anchor elements are spaced about a circumference of the barrel portion.
  • the one or more anchor elements are configured to move inwardly into the lumen and move outwardly relative to the lumen to engage the pump.
  • a method of deploying the device of any one of Examples 1-9 includes deploying the first flange against a tissue wall of an aorta, deploying and the second flange against a tissue wall of a left atrium.
  • Example 11 further to the method of Example 10, the method also includes deploying the pump concurrently with deploying the first flange and the second flange
  • Example 12 further to the method of Example 10, the method includes deploying the pump after deploying the first flange and the second flange.
  • a system includes a pump configured to transfer fluid flow therethrough; a barrel portion including a lumen for the fluid flow; a first flange arranged at a first end of the barrel portion and configured to expand from a reduced diameter to engage a first side of a structure; a second flange arranged at a second end of the barrel portion and configured to expand from a reduced diameter to engage a second side of a structure, and one or more anchor elements arranged with the barrel portion and configured to releasably engage and the pump arranged within the barrel portion.
  • Example 14 further to the system of Example 13, the system also includes a drive line coupled to the pump and a controller coupled to the pump and configured to configured to control the operation of the pump.
  • Example 15 further to the system of Example 14, the first side of the structure is an implantable medical device and the second side of a structure is a tissue wall.
  • an apparatus include: a conduit having a conduit outer surface, a conduit first end and a conduit second end defining a conduit length, and a lumen extending therethrough; a first flange coupled to the conduit outer surface adjacent the conduit first end and configured to expand from a reduced diameter to a larger diameter operable to engage a first tissue surface; and a second flange coupled to the conduit outer surface adjacent the conduit second end and configured to expand from a reduced diameter to a larger diameter operable to engage a second tissue surface, and at least one of the first flange and the second flange is configured to be positioned to a location along the conduit length.
  • Example 17 further to the apparatus of Example 17, the first flange movably coupled to the conduit outer surface and the second flange movably coupled to the conduit outer surface
  • the apparatus also includes a pump arranged within the conduit and defining a fluid passage for the transfer of fluid from the conduit first end to the conduit second end.
  • the conduit includes corrugations, and at least one of the first flange and the second flange are moveable along a length of the conduit.
  • At least one of the first flange and the second flange include one or more tabs configured to interface with corrugations on the conduit.
  • an apparatus includes a conduit having a conduit outer surface, a conduit first end and a conduit second end defining a conduit length, and a lumen extending therethrough; a first flange coupled to the conduit outer surface adjacent the conduit first end and configured to expand from a reduced diameter to a larger diameter operable to engage a first tissue surface; and a second flange coupled to the conduit outer surface adjacent the conduit second end and configured to expand from a reduced diameter to a larger diameter operable to engage a second tissue surface, and the first flange and the second flange include gaps to allow fluid flow into the conduit for the pump to transfer fluid through the conduit.
  • a delivery system for a device for cardiac assistance includes a first delivery sheath; a second delivery sheath; and a control device configured to pass through the first delivery sheath and the second delivery sheath to releasably connect with a pump and allow force to be applied to the pump to move the pump into engagement with a conduit.
  • Example 23 further to the system of Example 22, the first delivery sheath is configured for arterial access and the second delivery sheath is configured for venous access.
  • Example 24 further to the system of Example 22, the first delivery sheath is configured for carotid access and the second delivery sheath is configured for femoral access.
  • control device is configured to interface with the pump external to the venous access.
  • control device is configured to pull the pump through the venous access to engage with the conduit.
  • control device is a wire that is configured to interface with the pump.
  • the pump includes an eyelet configured to interface with the wire.
  • Example 29 further to the system of Example 28, the wire is configured to pass through the first delivery sheath, pass through the eyelet, and pass back through the first delivery sheath.
  • Example 30 further to the system of Example 27, the further including a nose cone arranged at an end of the wire configured to interface with the pump.
  • control device is a catheter configured to interface with the pump.
  • the conduit or the pump includes one or more anchor elements configured to releasably engage with one or more recesses arranged the other of the conduit or the pump.
  • the conduit includes the one or more anchor elements and the pump includes the one or more recesses.
  • the pump includes the one or more anchor elements and the conduit includes the one or more recesses.
  • Example 35 further to the system of any one of Examples 22-34, where in the conduit is configured to couple a patient’s heart to a vessel.
  • a method of delivering a pump for cardiac assistance includes arranging a first delivery sheath through arterial access; arranging a second delivery sheath through a venous access; passing a control device pass through the first delivery sheath and the second delivery sheath to interface with a pump; and applying force to the control device by way of the arterial access to engage the pump with a conduit configured to releasably engage and the pump arranged within the conduit.
  • the arterial access is a carotid access and the venous access is a femoral access.
  • control device is configured to interface with the pump external to the venous access.
  • a delivery system for a device for cardiac assistance includes a collet configured to engage a pump; and a control device configured to force the pump from engagement with the collet.
  • a method of delivering a device for cardiac assistance includes engaging a collet with a pump; and using a control device force the pump from engagement with the collet.
  • a method of treating heart failure includes arranging a first delivery sheath through arterial access; arranging a second delivery sheath through a venous access; passing a control device pass through the first delivery sheath and the second delivery sheath to interface with a pump; and applying force to the control device by way of the arterial access to engage the pump with a conduit.
  • the arterial access is a carotid access and the venous access is a femoral access.
  • control device is configured to interface with the pump external to the venous access.
  • an apparatus includes a conduit having a conduit outer surface, a conduit first end and a conduit second end defining a conduit length, and a lumen extending therethrough; a first flange coupled to the conduit outer surface adjacent the conduit first end and configured to expand from a reduced diameter to a larger diameter operable to engage a first tissue surface; and a second flange coupled to the conduit outer surface adjacent the conduit second end and configured to expand from a reduced diameter to a larger diameter operable to engage a second tissue surface, wherein the conduit includes one or more recesses configured to interface with protrusions arranged with a secondary implantable medical device.
  • the secondary implantable medical device is a pump.
  • FIG. 1 is an illustration of a system including a conduit and a pump, according to some embodiments
  • FIG. 2A is an illustration of an implantable medical device for cardiac assistance and sheath in a first delivery configuration, according to some embodiments.
  • FIG. 2B is an illustration the implantable medical device for cardiac, shown in FIG. 2A, in a second delivery configuration, according to some embodiments.
  • FIG. 2C is a side view illustration the implantable medical device for cardiac assistance, shown in FIGS. 2A-B, in a deployed configuration, according to some embodiments.
  • FIG. 2D is an end view illustration a flange of the implantable medical device for cardiac assistance, shown in FIGS. 2A-C, in a deployed configuration, according to some embodiments.
  • FIG. 3A is a side view illustration of an example implantable medical device for cardiac assistance, according to some embodiments.
  • FIG. 3B is a perspective view illustration of the device shown in FIG. 3A, according to some embodiments.
  • FIG. 4A is an illustration of another implantable medical device for cardiac assistance in a first configuration, according to some embodiments.
  • FIG. 4B is an illustration of the implantable medical device for cardiac assistance, shown in FIG. 4A, in a second configuration, according to some embodiments.
  • FIG. 5A is a side view illustration of an example implantable medical device for cardiac assistance, according to some embodiments.
  • FIG. 5B is a perspective view illustration of the device shown in FIG.5A, according to some embodiments.
  • FIG. 6 is a perspective view illustration of an example implantable medical device for cardiac assistance in a delivery configuration, according to some embodiments.
  • FIG. 7 is a side view illustration of an example implantable medical device for cardiac assistance, according to some embodiments.
  • FIG. 8 is an illustration of an example conduit with flanges, according to some embodiments.
  • FIG. 9A is an illustration of an example delivery system and pump, according to some embodiments.
  • FIG. 9B is a close up view of the delivery system and an end of the pump, shown in FIG. 9A, according to some embodiments.
  • FIG. 10A is an illustration of an example delivery system and pump in a first configuration, according to some embodiments.
  • FIG. 10B is an illustration the delivery system, shown in FIG. 10A, in a second configuration, according to some embodiments.
  • FIG. 11 is an illustration of another example delivery system and pump in a first configuration, according to some embodiments.
  • FIG. 12 is an illustration of an example delivery system and pump in a first configuration, according to some embodiments.
  • FIG. 13A is an example implantable medical device, according to some embodiments.
  • FIG. 13B is an example secondary medical device configured to interface with the implantable medical device shown in FIG. 13A, according to some embodiments.
  • Various aspects of the present disclosure are directed to systems and methods for improving or assisting the cardiac function of the heart.
  • the disclosed systems and methods generally include an endoprosthesis having a pump within the patient’s vasculature.
  • the disclosed systems and methods also include a delivery system configured for transcatheter delivery of the pump and the conduit.
  • cardiac assist devices including aorta (also referred to herein as ventricular assist), although it should be readily appreciated that the various embodiments and examples discussed herein can be applied in association with any known uses of cardiac assist devices, including for use within other regions of the heart or vasculature, as well as percutaneous procedures ( e.g ., laparoscopic) and / or surgical procedures.
  • Cardiac assist devices including ventricular assist devices, may be beneficial for patients experiencing heart failure.
  • the cardiac assist devices may include an implantable pump that forces blood from chambers of the heart ⁇ e.g., the right ventricle or left ventricle) to the rest of the body ⁇ e.g., via the aorta).
  • a system 1000 includes a conduit 100 and a pump 200 disposed at least partially within the conduit 100, and a retention element 300 configured to help maintain a position of the pump 200 within the conduit 100.
  • the conduit 100 may surround at least a portion of the pump 200 or form a portion of the pump 200.
  • the conduit 100 may include a graft, a stent, or a combination of a stent and a graft.
  • the conduit 100 creates a fluidic connection between spaces or tissue structures such as the aorta and an atrium or ventricle or the conduit 100 may be arranged within the vasculature (e.g ., pulmonary vein).
  • the conduit 100 and pump 200 may act as a right ventricular assist device and increase blood flow into the pulmonary veins or arteries.
  • the conduit 100 may be placed in the pulmonary artery with blood being transferred or forced into the atrium or ventricle as discussed in detail herein.
  • the conduit 100 and the pump 200 may increase flow of other non-blood bodily fluids when placed in other areas of the body ⁇ e.g., urinary, biliary)
  • the stent portion of a conduit 100 is defined by a plurality of interconnected strut elements.
  • the stent portion of the conduit 100 may comprise, such as, but not limited to, elastically deformable metallic or polymeric biocompatible materials.
  • the stent portion of the conduit 100 may comprise a shape- memory material, such as nitinol, a nickel-titanium alloy.
  • stent portion of the conduit 100 include, but are not limited to, other titanium alloys, stainless steel, cobalt-nickel alloy, polypropylene, acetyl homopolymer, acetyl copolymer, other alloys or polymers, or any other biocompatible ⁇ e.g., bio-absorbable) material having adequate physical and mechanical properties to function as the stent portion of the conduit 100, as described herein.
  • the stent portion of the conduit 100 may be self-expanding and/or may be expandable using an expansion element, such as a balloon. That is, in various examples, the conduit 100 may be transitionable between a collapsed delivery configuration and an expanded deployed configuration.
  • the conduit 100 may be a stent that is partially covered with a graft material.
  • the graft material of the conduit 100 may further include a graft material disposed thereabout ⁇ e.g., such as about an interior of or an exterior of the conduit 100).
  • graft materials can include, for example, expanded polytetrafluoroethylene (ePTFE), polyester, polyurethane, fluoropolymers, such as perfluoroelastomers and the like, polytetrafluoroethylene, silicones, urethanes, ultra high molecular weight polyethylene, aramid fibers, and combinations thereof.
  • a graft member material can include high strength polymer fibers such as ultra-high molecular weight polyethylene fibers ⁇ e.g., Spectra®, Dyneema Purity®, etc.) or aramid fibers ⁇ e.g., Technora®, etc.). Some embodiments may comprise of a graft material only partially disposed about the conduit frame.
  • the system 1000 is configured such that the pump 200 can be removably coupled with the conduit 100.
  • the pump 200 is removably coupled with the conduit 100 after the conduit 100 has been delivered and deployed within the patient’s vasculature (e.g ., a conduit of an implantable medical device).
  • the pump 200 is removable from the patient’s vasculature without also requiring removal of the conduit 100 ⁇ e.g., such that the pump 200 may be replaced and/or such that removal of the system 1000 may be done minimally invasively).
  • the pump 200 is generally configured to drive or otherwise cause blood to flow across the pump 200 from an inflow side 1004 of the system 1000 to an outflow side 1002 of the system, such as along a direction of arrow 1006.
  • the pump mechanism (also referred to herein as a pump drive) of the pump 200 may be, for example, a centrifugal-action pump, an axial-action pump, or other similar device such as a worm-style drive mechanism, or impeller.
  • the pump housing is configured to interface and engage with the conduit 100.
  • the pump 200 is situated within the deployed conduit 100 such that the pump 200 is operable to pump or drive blood across the pump 200 and into the aorta and out into the vasculature of the body.
  • the pump 200 can be operated to draw blood from the left ventricle (or other heart chamber), blood across the pump 200, and into the aorta and out through the vasculature of the body.
  • system 1000 further includes a driveline 400.
  • the driveline 400 is a cable assembly that operates to electrically couple a controller 500 located external to the patient’s anatomy with the pump 200 or the drive line 400 can be a rotating driveshaft.
  • the driveline 400 may be routed through the patient’s vasculature ⁇ e.g., exiting the heart through the apex of the left ventricle) and then out through the skin to where it is coupled with the controller 500 or to a subcutaneously implanted controller 500.
  • the controller 500 is a module that is configured to control the operation of the pump 200.
  • the controller 500 may include a battery to control operation of the pump 200.
  • the driveline 400 may be routed through one of the left or right subclavian arteries, veins, or the left common carotid artery to a subclavian or other associated access. Alternatively, the driveline 400 may be routed through the descending aorta to a femoral or other associated access. In certain instances, the driveline 400 is associated with the retention element 300, for example being routed through the retention element 300 or integral to the retention element 300. In some examples where the driveline 400 is integral with the retention element 300, the retention element 300 includes one or more connectors such that when the retention element 300 is coupled to the conduit 100, the driveline 400 is electrically coupled with the pump 200.
  • the system 1000 may be configured to operate without the need for the driveline 400, or the driveline 400 need not extend extracorporeally. That is, in some examples, an extracorporeal control system may be configured to both control the operation of the pump, and to power the pump wirelessly ( e.g through a transcutaneous energy transmission system). In some examples, transcutaneous energy transmission may be accomplished through known means of transcutaneous energy transmission, such as those described in U.S. Patent No. 6,400,991. Such a configuration eliminates the need to route the driveline 400 through the vasculature and out through a percutaneous access site, which can help minimize a risk for infection.
  • the driveline 400 may not exit the patient through the thoracic cavity.
  • the driveline 400 may be configured to be unplugged or decoupled from the pump 200 at its junction with the pump 200.
  • decoupling the driveline 400 from the pump 200 includes decoupling or removing the retention element 300.
  • the system 1000 may include an “antenna” (or internal coil) that is configured for transcutaneous energy transfer (“TET”).
  • an extracorporeal TET component maybe worn around the torso similar to a standard heart rate monitor, and additionally coupled to a power source (wall unit or high capacity battery) such that the extracorporeal TET component is operable to transmit energy transcutaneously to the antenna.
  • FIG. 2A is an illustration of an implantable medical device for cardiac assistance and sheath 416 in a first delivery configuration, according to some embodiments.
  • an access sheath 416 is arranged at a target location of delivery of an implantable medical device (not shown).
  • the implantable medical device is arranged within a delivery sheath 314.
  • the access sheath 416 is arranged to deliver the implantable medical device between the aorta and the left atrium.
  • the delivery sheath 314 may include a dilator 550 to facilitate delivery.
  • FIG. 2B is an illustration the implantable medical device for cardiac, shown in FIG. 2A, in a second delivery configuration, according to some embodiments.
  • a pump 200 is arranged within the access sheath 416.
  • flanges 520a, 520b may be directly coupled to the pump 200, or the flanges 520a, 520b may form a portion of a conduit 100, which is also arranged and collapsed within the access sheath 416 (and as is shown in further detail with reference to FIGS. 3A-B and in FIG. 6).
  • the pump 200 may be removable from the flanges 520a, 520b. In other instances, the flanges 520a, 520b form a part of and extend from a circumference of the pump 200.
  • a driveline 400 be coupled to the pump 200 to power the pump and communicate with a controller 500 as discussed in detail above.
  • FIG. 2C is a side view illustration the implantable medical device for cardiac assistance, shown in FIGS. 2A-B, in a deployed configuration, according to some embodiments.
  • the flanges 520a, 520b have been deployed, and the pump 200 is arranged between the aorta and left atrium.
  • the flanges 520a, 520b may be deployed within a vessel ( e.g ., pulmonary vein), or between the left or right ventricle and the aorta.
  • the pump 200 (and conduit 100) may have been expanded from the delivery configuration.
  • the pump 200 (and conduit 100) may be configured to collapse within the sheath 416.
  • the flanges 520a, 520b are configured to expand outwardly from a reduced diameter to engage tissue walls ⁇ e.g., of the aorta and left atrium).
  • the flanges 520a, 520b may seal against the tissue walls and stabilize the pump 200 between the aorta and left atrium.
  • the flanges 520a, 520b and pump 200 may be arranged between and connect other areas of patients’ anatomy ⁇ e.g., vessel-vessel communication such as percutaneous fistula creation).
  • the flanges 520a, 520b may be a first flange 520a arranged at a first end of the conduit 100 and configured to expand from a reduced diameter to engage a first tissue wall ⁇ e.g., of the aorta, first vessel), and a second flange 520b is arranged at a second end of the conduit 100 and configured to expand from a reduced diameter to engage a second tissue wall ⁇ e.g., of the left atrium, right atrium, left ventricle, right ventricle, second vessel) the first and second flanges 520a, 520b are used to connect two areas within a patient with the conduit 100 being a fluid pathway between the two areas of the patient.
  • the pump 200 When the pump 200 is engaged with the conduit 100, the pump 200 is configured to increase fluid between the areas of the patient. As noted above, the pump 200 may be for cardiac assistance and increase blood flow of the patient’s heart through the patient by supplementing blood flow into the aorta from the heart ( e.g left atrium or ventricle).
  • the pump 200 may be for cardiac assistance and increase blood flow of the patient’s heart through the patient by supplementing blood flow into the aorta from the heart (e.g left atrium or ventricle).
  • the driveline 400 may exit the left atrium (or other area of the heart).
  • the pump 200 may be arranged within a conduit 100 as described in detail above.
  • the conduit 100 and the pump 200 may be separately delivered.
  • the flanges 520a, 520b may be coupled to the conduit 100.
  • the pump 200 or the conduit 100 may have anchor features such that the pump 200 is removeable and/or replaceable. As the pump 200 may be removable from the flanges 520a, 520b (and conduit 100).
  • FIG. 2D is an end view illustration a flange 520a of the implantable medical device for cardiac assistance, shown in FIGS. 2A-C, in a deployed configuration, according to some embodiments.
  • the flange 520a and flange 520b may be substantially similar structures. As shown, the flange 520a extends circumferentially outwardly relative to the pump 200. In addition, the pump 200 may dock within the flange 520a (and flange 520b).
  • the flanges 520a, 520b (and conduit 100) and pump 200 may be deployed together, as shown in FIGS. 2A-C, or deployed separately (with the flanges 520a, 520b and conduit 100 being deployed and the pump 200 arranged and secured within the flanges 520a, 520b).
  • the flanges 520a, 520b may include a plurality of lobes 524 (with one highlighted for ease of illustration).
  • the lobes 524 may be configured to rest against a tissue surface without puncturing or damaging the tissue.
  • the lobes 524 may conform to the tissue surface.
  • the lobes 524 stabilize against the tissue to lessen movement of the pump 200.
  • the flanges 520a, 520b and/or the barrel portion 272 may be covered or partially covered with a graft component.
  • the graft portion arranged with the flanges may be configured to facilitate tissue in-growth.
  • the graft portion for example, can have a microporous structure that provides a tissue ingrowth scaffold for durable occlusion and supplemental anchoring strength.
  • the graft portion can lessen leakage from about the flanges 520a, 520b.
  • FIG. 3A is a side view illustration of an example implantable medical device for cardiac assistance, according to some embodiments.
  • a conduit 100 is shown in FIGS. 3A-B that includes flanges 520a, 520b that extend outwardly relative to a barrel portion 272.
  • the flanges 520a, 520b may be collapsed inwardly relative in a delivery configuration ⁇ e.g., as shown in FIG. 6)
  • the barrel portion 272 may also be collapsed further to facilitate delivery to a target location.
  • the barrel portion 272 may include one or more anchor elements 570a, 570b configured to interface with a pump 200.
  • anchor elements 570a, 570b is highlighted for east of illustration.
  • the pump 200 may include similar anchor elements 570a, 570b (with the barrel portion 272 including recesses rather than the anchor elements 570a, 570b).
  • the anchor elements 560 may friction or interference couple to the pump 200 to secure the pump 200 within the conduit 100.
  • the anchor elements 570a, 570b may be spaced about a circumference of the barrel portion 272.
  • both the pump 200 and the conduit 100 include anchor elements 570a, 570b.
  • the anchor elements 570a, 570b of each may interface to secure the pump 200 to the conduit 100.
  • a conduit 100 as described in detail above, may include similar anchor elements 570a, 570b to interface with a pump 200 having the anchor elements 570a, 570b.
  • the anchor elements 570a, 570b may be moveable relative to a lumen 46 of the conduit 100.
  • the anchor elements 570a, 570b may extend into the lumen 46, and may be moved outwardly relative to the lumen 46 during engagement and when engaged with the pump 200.
  • the pump 200 may include receiving structures (e.g ., similar to receiving structure 620) that receive the anchor elements 570a, 570b.
  • the anchor elements 570a, 570b may reside within the receiving structure on the pump 200 to secure the pump 200 to the conduit 100.
  • the pump 200 may be arranged within the conduit 100 starting on either of the sides of the flanges 520a, 520b, and forced within the barrel portion 272.
  • the anchor elements 570a, 570b may be forced outwardly by an outer surface of the pump 200 or by an outer surface of a delivery sheath that the pump is arranged ⁇ e.g., collapsed) within.
  • the anchor elements 570a, 570b may then deploy or extend inwardly relative to the lumen 46 to engage the pump 200.
  • the anchor elements 570a, 570b are arranged within the barrel portion 272 at a common location ⁇ e.g., relative to the x-axis shown on FIG. 3A) about a circumference the barrel portion 272.
  • the anchor elements 570a, 570b may be staggered relative to the length of the barrel portion 272 such that multiple anchor elements 570a, 570b are arranged at differing locations within the barrel portion 272 relative to the length of the barrel portion 272.
  • the barrel portion 272 includes the anchor elements 570a, 570b at multiple length locations and multiple anchor elements 570a, 570b arranged about the circumference of the barrel portion 272 at the multiple length locations.
  • the first row of anchor elements 570a may be configured to engage the pump 200 and the second row of anchor elements 570b are configured to engage the delivery sheath 314.
  • the barrel portion 272 and the flanges 520a, 520b are a unitary structure ( e.g formed from a cut-tube) formed by struts 555a, 555b or stent- elements.
  • the flanges 520a, 520b and barrel portion 272 may be self-expanding and/or balloon expandable.
  • the flanges 520a, 520b and barrel portion 272 are formed of Nitinol or stainless steel.
  • the barrel portion 272 may be substantially cylindrical and the flanges 520a, 520b may extend from the barrel portion 272 ⁇ e.g., as shown in FIG. 7). In other instances and is shown, the barrel portion 272 may increase in circumference or diameter between the flanges 520a, 520b. The barrel portion 272 increasing or tapering in diameter may facilitate arrangement of the pump 200 to engage the anchor elements 570a.
  • the flanges 520a, 520b may extend circumferentially outward relative to the barrel portion 272 as is shown in particular in FIG. 3B. Struts 555b are arranged to extend the flanges 520a, 520 relative to the barrel portion 272. In certain instances, flanges 520a, 520b may be of different diameters, circumferences, shapes, and/or sizes.
  • the struts 555b may include a curvature as shown.
  • the curvature of the struts 555b may extend portions of the flanges 520a, 520b downward (relative to a center) of the barrel portion 272.
  • perimeters 520c, 520d of the flanges 520a, 520b are arranged lower or downward toward the barrel portion 272 (relative to an apex of the curvature of struts 555b).
  • the curvature of the struts 555b may be a constant curve or a s-shaped curve with multiple stages.
  • the curvature of the struts 555b may be different for each of the flanges 520a, 520b as shown in FIG. 3A.
  • the perimeters 520c, 520d may be different. As shown, the perimeter 520c has a greater circumference than a circumference of perimeter 520d.
  • the flanges 520a, 520b may be configured in this manner to lessen the pump 200 from shifting or otherwise damaging the tissue wall that the flanges 520a, 520b engage.
  • the pump 200 may be arranged to force blood through the conduit 100 from the flange 520b side to the flange 520a side. The force of the pump 200 may apply greater force on the flange 520b side.
  • the flange 520b may be greater than the flange 520a to lessen movement of the pump 200.
  • the greater perimeter 520c may increase a surface area of engagement of the flange 520b.
  • the struts 555a, 555b may include different widths within the barrel portion 272 and within the flanges 520a, 520b.
  • a portion of the struts 555b include a less width (e.g ., relative to the z-axis) than a portion of the struts 555a.
  • the thinner width of the struts 555b may facilitate collapsing of the flanges 520a, 520b to a reduced diameter ⁇ e.g., toward the barrel portion 272, which may also reduce in diameter (as shown in FIG. 2A-C).
  • the thinner width of the struts 555b may enhance flexibility of the flanges 520a, 520b and facilitate conformability of the flanges 520a, 520b to the tissue walls.
  • a depth ⁇ e.g., relative to the y-axis) of the struts 555a, 555b may differ.
  • the depth of the struts 555a, 555b may be different in addition to or in alternative to the widths of the struts 555a, 555b being different.
  • the depth of the struts 555a may be less than the depth of the struts 555b.
  • the differences in width and depth may be cut into a cut-tube or cut-sheet pattern or laser removed.
  • the flanges 520a, 520b may include a plurality of lobes 524 (with one highlighted for ease of illustration).
  • the lobes 524 may be configured to rest against a tissue surface without puncturing or damaging the tissue. In certain instances, the lobes 524 may conform to the tissue surface.
  • one of the flanges 520a, 520b may be configured to engage a tissue wall and another of the flanges 520a, 520b may be arranged within a main body portion that is implanted in a patient’s aorta.
  • the struts 555b have a width that is greater than the depth.
  • the struts 555b having this arrangement may facilitate conformability and fatigue resistance.
  • the width is aligned with the bend axis of the struts 555b, which may facilitate flexibility.
  • the struts 555a may have a depth that it is greater than the width.
  • the depth of the struts 555b is aligned where forces act on the barrel portion 272 when implanted.
  • the depth of the struts 555b is configured to lessen potential radial contraction of the barrel portion 272.
  • one or both of the anchor elements 570a, 570b may be include a different shape or form than those shown.
  • the anchor elements 570a, 570b may be hooks, j-shape hooks, protrusions, or other elements that may interface with a corresponding recess or opening.
  • U.S. Patent Application Ser. No. 16/577,565 (“ Bryson et a/.”).
  • FIG. 4A is an illustration of another implantable medical device for cardiac assistance in a first configuration, according to some embodiments.
  • the device is a conduit 100 having flanges 520a, 520b.
  • the flanges 520a, 520b are formed of a metallic material (e.g Nitinol) and the conduit 100 is formed a graft material the conduit 100 may also include stent-components.
  • FIG. 3A and FIG. 3B for further discussion of the arrangement and aspects of the flanges 520a, 520b.
  • the flanges 520a, 520b when arranged with the conduit 100, may include a barrel portion 754 that facilitates connection to the conduit 100.
  • the conduit 100 as shown, includes a conduit outer surface, a conduit first end and a conduit second end defining a conduit length, and a lumen 46 extending therethrough.
  • one or both of the flanges 520a, 520b may be moveable along a length of the conduit 100.
  • One or both of the flanges 520a, 520b may be positioned to a location along the conduit 100. As shown in comparing FIG. 4A and FIG. 4B, flange 520b is moved from the configuration shown in FIG. 4A to an opposite end of the conduit 100.
  • the conduit 100 may be a pump 200, the conduit 100 may be similar to the conduit 100 and be configured to securely anchor a pump 200 therein.
  • the conduit 100 may include one or more anchor or attachment features as described in detail above.
  • the flange 520a is fixed to the conduit 100 and is not moveable along the length of the conduit 100.
  • the conduit 100 may be corrugated such that the moveable flange 520b may stop at a number of locations along the conduit 100.
  • One of both of the flanges 520a, 520b may include one or more tabs 752 that are configured to interface with corrugations on the conduit 100.
  • the tabs 752 may be spaced about a circumference of the flanges 520a, 520b in instances where the flanges 520a, 520b include more than one tab 752.
  • the conduit 100 includes one, two, three, four, or any additional corrugations.
  • the flanges 520a, 520b and conduit 100 may be arranged within a sheath ⁇ e.g., as described above with reference to FIGS. 2A-C).
  • the following describes the solution for use in a ventricular assistance procedure.
  • the flanges 520a, 520b are attached to the conduit 100 (which may be the pump 200 as noted above) are constrained within the sheath.
  • the sheath is placed across a pathway from the left atrium to the aorta, for example, and pulled back while holding a delivery catheter (not shown) stationary.
  • the flange 520a deploys first to engage the tissue wall of, for example, the aorta.
  • the delivery catheter is pulled proximally, abutting the underside of the flange 520a to the aortic wall.
  • the sheath is further pulled back exposing the flange 520b, for example, to engage the tissue wall of the left atrium.
  • the sheath may then advance distally to move the flange 520b along the conduit 100.
  • the flange 520b may be moved closer to flange 520 until the flanges 520a, 520b abut, as shown in FIG. 4A, or until the tissue provides sufficient resistance against further movement.
  • the conduit 100 includes a lumen 46 for fluid flow.
  • FIG. 5A is a side view illustration of an example implantable medical device for cardiac assistance, according to some embodiments.
  • the device is a conduit 100 and includes flanges 520a, 520b, and a barrel portion 272.
  • the flanges 520a, 520b are formed of a metallic material (e.g ., Nitinol) and the conduit 100 is formed a graft material the conduit 100 may also include stent-components.
  • the flanges 520a, 520b may be collapsed inwardly relative in a delivery configuration and the barrel portion 272 may also be collapsed further to facilitate delivery to a target location.
  • the barrel portion 272 may include one or more anchor elements 570a, 570b configured to interface with a pump 200 as shown and discussed with reference to FIGS. 3A-B.
  • the conduit 100 is in a first configuration and the flanges 520a, 520b are shown in a transition between delivery configuration (where the conduit 100 is a substantially cylindrical shape as shown in FIG. 2A) and in a deployed configuration shown in FIG. 5B.
  • the flanges 520a, 520b are configured to expand in response to a contraction in length of the conduit.
  • the flanges 520a, 520b are configured to expand or spring open relative to the barrel portion 272 when released from the delivery or collapsed configuration.
  • the flanges 520a, 520b may be a first flange 520a arranged at a first end of the conduit 100 and configured to expand from a reduced diameter to engage a first tissue wall ⁇ e.g., of the aorta, first vessel), and a second flange 520b is arranged at a second end of the conduit 100 and configured to expand from a reduced diameter to engage a second tissue wall ⁇ e.g., of the left atrium, right atrium, left ventricle, right ventricle, second vessel) the first and second flanges 520a, 520b are used to connect two areas within a patient with the conduit 100 being a fluid pathway between the two areas of the patient.
  • the pump 200 When the pump 200 is engaged with the conduit 100, the pump 200 is configured to increase fluid between the areas of the patient. As noted above, the pump 200 may be for cardiac assistance and increase blood flow of the patient’s heart through the patient by supplementing blood flow into the aorta from the heart ( e.g left atrium or ventricle).
  • the pump 200 may be for cardiac assistance and increase blood flow of the patient’s heart through the patient by supplementing blood flow into the aorta from the heart (e.g left atrium or ventricle).
  • the flanges 520a, 520b may include a plurality of lobes 524 (with one highlighted for ease of illustration).
  • the lobes 524 may be configured to rest against a tissue surface without puncturing or damaging the tissue. In certain instances, the lobes 524 may conform to the tissue surface. In addition, the lobes 524 stabilize against the tissue to lessen movement of the pump 200.
  • the flanges 520a, 520b may include gaps 530 (one highlighted for ease of illustration) to allow blood flow into the conduit 100 for the pump to force through the conduit.
  • the gaps 530 may lessen collapsing of the flanges 520a, 520b against the tissue wall during operation of the pump.
  • FIG. 6 is a perspective view illustration of an example implantable medical device for cardiac assistance in a delivery configuration, according to some embodiments. As shown, the flanges 520a, 520b are collapsed inwardly relative in a delivery configuration. The flanges 520a, 520b and the barrel portion 272 are arranged in a substantially cylindrical configuration.
  • the flanges 520a, 520b and the barrel portion 272 may transition between the delivery configuration to in a deployed configuration shown in FIGS. 3A-B.
  • the flanges 520a, 520b are configured to expand to engage tissue, and may spring open relative to the barrel portion 272 when released from the delivery or collapsed configuration.
  • FIG. 7 is a side view illustration of an example implantable medical device for cardiac assistance, according to some embodiments.
  • a conduit 100 includes flanges 520a, 520b that extend outwardly relative to a barrel portion 272.
  • the barrel portion 272 and the flanges 520a, 520b are a unitary structure ⁇ e.g., formed from a cut-tube) formed by struts 555a, 555b or stent-elements.
  • the barrel portion 272 may be substantially cylindrical and the flanges 520a, 520b may extend from the barrel portion 272.
  • the flanges 520a, 520b may extend circumferentially outward relative to the barrel portion 272 as is shown.
  • Struts 555b are arranged to extend the flanges 520a, 520 outwardly relative to the barrel portion 272.
  • the struts 555b may include a curvature as shown. The curvature of the struts 555b may extend portions of the flanges 520a, 520b downward (relative to a center 590 or midline) of the barrel portion 272.
  • perimeters 520c, 520d of the flanges 520a, 520b are arranged lower or downward toward the barrel portion 272 (relative to an apex of the curvature of struts 555b).
  • the curvature of the struts 555b may be a constant curve or a s-shaped curve with multiple stages.
  • the struts 555a, 555b may include different widths within the barrel portion 272 and within the flanges 520a, 520b.
  • a portion of the struts 555b include a less width ( e.g ., relative to the z-axis) than a portion of the struts 555a.
  • the thinner width of the struts 555b may facilitate collapsing of the flanges 520a, 520b to a reduced diameter ⁇ e.g., as shown in FIG. 6).
  • a depth ⁇ e.g., relative to the y-axis) of the struts 555a, 555b may differ.
  • the depth of the struts 555a, 555b may be different in addition to or in alternative to the widths of the struts 555a, 555b being different.
  • the depth of the struts 555a may be less than the depth of the struts 555b.
  • the struts 555b have a width that is greater than the depth.
  • the struts 555b having this arrangement may facilitate conformability and fatigue resistance.
  • the struts 555b are configured to bend and fold relative to the barrel portion 272.
  • the width is aligned with the bend axis of the struts 555b, which may facilitate flexibility.
  • the struts 555a may have a depth that it is greater than the width.
  • the depth of the struts 555b is aligned where forces act on the barrel portion 272 when implanted.
  • the depth of the struts 555b is configured to lessen potential radial contraction of the barrel portion 272.
  • the barrel portion 272 may include anchor elements 570a, 570b.
  • the barrel portion 272 may be configured for friction or interference engagement with a pump 200.
  • the anchor elements 570a, 570b are aligned with the center 690 of the barrel portion 272.
  • the anchor elements 570a, 570b may be staggered and at multiple locations away from the center 690 ⁇ e.g., as shown in FIGS. 3A-B) to provide multiple docking locations for the pump 200.
  • FIG. 8 is an illustration of an example conduit 100 with flanges 520a, 520b, according to some embodiments.
  • the conduit 100 creates a fluidic connection between spaces or tissue structures such as the aorta and an atrium or ventricle.
  • the conduit 100 includes flanges 520a, 520b as discussed in detail above.
  • the flanges 520a, 520b may be arranged to seal the conduit 100 within tissue structures or within a main body 208 of an implantable medical device.
  • the main body 208 may be a stent, graft, or stent graft component that is configured to implant within a patient’s aorta.
  • the main body 208 includes a fenestration (either created after implantable or prior to implantation).
  • the conduit 100 includes a lumen 46 that extends longitudinally from a first end of the conduit 100 to a second end of the device 40.
  • the lumen 46 acts as a connection (e.g a shunt passageway) between the main body 208, implanted in the aorta, and the internal intestinal space of the heart ⁇ e.g., atrium or ventricle), such that the main body 208 is in fluid communication with the atrium or ventricle via the anastomosis conduit 100.
  • the flange 520b may be configured to engage a tissue wall 522 in a fluid tight fluid communication between the conduit 100 and atrium or ventricle into which the conduit 100 is arranged.
  • the flange 520 prevents leakage between the puncture made in the atrium or ventricle and the conduit 100.
  • FIG. 9A is an illustration of an example delivery system and pump 200, according to some embodiments.
  • FIG. 9B is a close up view of the delivery system and an end of the pump 200, shown in FIG. 9A, according to some embodiments.
  • the delivery system includes a delivery sheath (not shown) through which a catheter 964 and a control device 962 may be placed or passed through.
  • the control device 962 may include a lumen through which the catheter 964 may pass through.
  • a collet 960 may be integrally formed or attached to a distal end of the delivery catheter 964.
  • the collet 960 may interface with a portion of the pump 200.
  • the collet 960 may be configured to pass at least partially through an end portion of the pump 200 and engage the portion of the pump 200 to enable movement of the frame 200.
  • the collet 960 may be frictionally engaged with the portion of the pump 200 and release in response to a force applied to the control device 962.
  • the control device 962 forces the collet 960 from the pump 200 after the pump 200 is deployed at a desired location in certain instances. In other instances, the control device 962 may push the pump 200 through the delivery sheath (not shown) and to the anchors in the conduit 100 and into the anchors.
  • the collet 960 may be a screw, leur screw, a twisting mechanism, or other mechanical attachment mechanism that releasably interfaces with the pump 200.
  • attachment mechanisms of delivery catheters reference may be made to U.S. Patent No. 8,551,135 (“ Kladakis et al.”), which is incorporated herein by reference.
  • FIG. 10A is an illustration of an example delivery system and pump 200 in a first configuration, according to some embodiments.
  • the delivery system includes a first delivery sheath 750 and a second delivery sheath 756.
  • the delivery system also includes a control device 758.
  • the control device 758 e.g a wire, metal hypotube, braided wire, torque wire, or the like
  • the first delivery sheath 750 is configured for arterial access and the second delivery sheath 756 is configured for venous access.
  • the first delivery sheath 750 may be configured for carotid access ⁇ e.g., arranged through a cut-down in the carotid artery) and the second delivery sheath 756 may be configured for femoral access.
  • the first delivery sheath 750 is arranged to target a location within a vessel such as an aorta 820 of a patient and the second delivery sheath 756 may be arranged to target a location within a chamber 822 of the patient’s heart such as an atrium or ventricle.
  • the second delivery sheath 756 is arranged through the inferior vena cava 824 and then into the chamber 822 of the patient’s heart.
  • a conduit 100 may be arranged to connect the chamber 822 and the aorta 820 (or other target organ and vessel).
  • the control device 758 may be arranged through the first delivery sheath 750, through the conduit 100, and through the second delivery sheath 756 to engage the pump 200.
  • the pump 200 may include an eyelet 780 through which the control device 758 may be arranged.
  • the control device 758 may be configured to interface with the pump 200 external to the venous access. After the control device 758 is arranged through the eyelet 780, the control device 758 may be arranged back through the second delivery sheath 756, the conduit 100, and the first delivery sheath 750. As shown in FIG. 10B, both ends of the control device 758 may be arranged through the arterial access.
  • the pump 200 being coupled to the control device 758 allows for a force to be applied to the control device 758 by a physician to force the pump 200 into engagement with the conduit 100.
  • the control device 758 is configured to pull the pump 200 through the venous access to engage with the conduit 100.
  • either the conduit 100, the pump 200, or both the conduit 100 and the pump 20 include anchor elements to couple the pump 200 to the conduit 100.
  • the control device 758 may facilitate maintaining connection to the pump 200 during engagement between the pump 200 and the conduit 100.
  • the second delivery sheath 756 is larger in diameter than the first delivery sheath 750.
  • the first delivery sheath 750 (or the second delivery sheath 756) may be used to deliver the conduit 100 as described in detail above with respect to the connection between anchor elements 570b and delivery sheath 314.
  • FIG. 11 is an illustration of another example delivery system and pump in a first configuration, according to some embodiments.
  • the delivery system includes a first delivery sheath 750 and a second delivery sheath 756.
  • the delivery system also includes a control device such as, for example, a catheter 770 configured to interface with the pump 200.
  • the catheter 770 (e.g control device) may be configured pass through the first delivery sheath 750 and the second delivery sheath 756 to interface with a pump 200.
  • the catheter 770 may use a collet mechanism, screw, or other mechanical fixation mechanism to couple to the pump 200.
  • the first delivery sheath 750 is configured for arterial access and the second delivery sheath 756 is configured for venous access.
  • the first delivery sheath 750 may be configured for carotid access ⁇ e.g., arranged through a cut-down in the carotid artery) and the second delivery sheath 756 may be configured for femoral access.
  • the first delivery sheath 750 is arranged a target location within a vessel such as an aorta 820 of a patient and the second delivery sheath 756 may be arranged with a chamber 822 of the patient’s heart such as an atrium or ventricle.
  • the second delivery sheath 756 is arranged through the inferior vena cava 824 and then into the chamber 822 of the patient’s heart.
  • a conduit 100 may be arranged to connect the chamber 822 and the aorta 820 (or other target organ and vessel).
  • the pump 200 being coupled to the catheter 770 allows for a force to be applied to the catheter 770 by a physician to force the pump 200 into engagement with the conduit 100.
  • the catheter 770 is configured to pull the pump 200 through the venous access to engage with the conduit 100.
  • either the conduit 100, the pump 200, or both the conduit 100 and the pump 20 include anchor elements to couple the pump 200 to the conduit 100.
  • the second delivery sheath 756 is larger in diameter than the first delivery sheath 750.
  • the first delivery sheath 750 (or the second delivery sheath 756) may be used to deliver the conduit 100 as described in detail above with respect to the connection between anchor elements 570b and delivery sheath 314.
  • the catheter 770 may include one or more curvatures to facilitate passing through the first delivery sheath 750 and the second delivery sheath 756.
  • the catheter 770 may include portions of varying flexibility (by way of varying high and low durometer materials).
  • FIG. 12 is an illustration of an example delivery system and pump in a first configuration, according to some embodiments.
  • the delivery system includes a first delivery sheath 750 and a second delivery sheath 756.
  • the delivery system also includes a control device 758 (e.g a wire, metal hypotube, braided wire, or the like).
  • the control device 758 may be configured pass through the first delivery sheath 750 and the second delivery sheath 756 to interface with a pump 200.
  • a nose cone 772 (or other feature for attachment) may be arranged at an end of the control device 758 configured to interface with the pump 200.
  • the nose cone 772 may include anchors or a friction fit with the pump 200 or the nose cone 722 may be adhered to the pump 200. Once the pump 200 is engaged with the conduit 100, the nose cone 772 may release from the pump 200 after further force is applied.
  • the nose cone 772 may be collapsible.
  • U.S. Patent No. 7,658,747 (“ Forde et al.”
  • the first delivery sheath 750 is configured for arterial access and the second delivery sheath 756 is configured for venous access.
  • the first delivery sheath 750 may be configured for carotid access ⁇ e.g., arranged through a cut-down in the carotid artery) and the second delivery sheath 756 may be configured for femoral access.
  • the first delivery sheath 750 is arranged to target a location within a vessel such as an aorta 820 of a patient and the second delivery sheath 756 may be arranged to target a chamber 822 of the patient’s heart such as an atrium or ventricle.
  • the second delivery sheath 756 is arranged to pass through the inferior vena cava 824 and then into the chamber 822 of the patient’s heart.
  • a conduit 100 may be arranged to connect the chamber 822 and the aorta 820 (or other target organ and vessel).
  • the pump 200 being coupled to the control device 758 allows for a force to be applied to the control device 758 by a physician to force the pump 200 into engagement with the conduit 100.
  • the control device 758 is configured to pull the pump 200 through the venous access to engage with the conduit 100.
  • either the conduit 100, the pump 200, or both the conduit 100 and the pump 20 include anchor elements to couple the pump 200 to the conduit 100.
  • the second delivery sheath 756 is larger in diameter than the first delivery sheath 750.
  • the first delivery sheath 750 (or the second delivery sheath 756) may be used to deliver the conduit 100 as described in detail above with respect to the connection between anchor elements 570b and delivery sheath 314.
  • FIG. 13A is an example implantable medical device, according to some embodiments.
  • the implantable medical device shown in FIG. 13A is a conduit 100.
  • the conduit 100 consistent with the description of the barrel portion 272 above, may be formed by struts 555.
  • the conduit 100 may include flanges 520a, 520b as discussed in detail above.
  • the struts 555 form a series of open cells 670.
  • the cells 670 may include a number of differing shapes such as hexagonal and hourglass shape as is shown.
  • the hour glass shaped cells 670 may be arranged between rows of hexagonal cells 670.
  • end portions of the conduit 100 may include recesses 594 that may interface with protrusions 592 on a secondary device 1300, such as pump 200 as shown in FIG. 13B, a sensor, an occluder, a filter, or other medical device.
  • the recesses 594 may allow entry of the protrusions 592 and trap the protrusions 592 therein.
  • the protrusions 592 may engage and stay within the cells 670.
  • the graft may include a fluoropolymer, such as a polytetrafluoroethylene (PTFE) polymer or an expanded polytetrafluoroethylene (ePTFE) polymer.
  • PTFE polytetrafluoroethylene
  • ePTFE expanded polytetrafluoroethylene
  • the graft may be formed of a polyester, a silicone, a urethane, a polyethylene terephthalate, or another biocompatible polymer, or combinations thereof.
  • bioresorbable or bioabsorbable materials may be used, for example a bioresorbable or bioabsorbable polymer.
  • the graft can include Dacron, polyolefins, carboxy methylcellulose fabrics, polyurethanes, or other woven or film elastomers.
  • NiTi nitinol
  • other materials such as stainless steel, L605 steel, polymers, MP35N steel, polymeric materials, Pyhnox, Elgiloy, or any other appropriate biocompatible material, and combinations thereof, can be used as the material of the frame.
  • the super-elastic properties and softness of NiTi may enhance the conformability of the stent.
  • NiTi can be shape-set into a desired shape. That is, NiTi can be shape-set so that the frame tends to self-expand into a desired shape when the frame is unconstrained, such as when the frame is deployed out from a delivery system.

Landscapes

  • 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)
  • Prostheses (AREA)
  • External Artificial Organs (AREA)

Abstract

Divers aspects de la présente invention concernent des dispositifs médicaux implantables, des systèmes et des procédés d'assistance cardiaque.
PCT/US2020/051841 2019-11-21 2020-09-21 Systèmes et procédés de pose pour dispositifs d'assistance cardiaque implantables Ceased WO2021101622A1 (fr)

Applications Claiming Priority (2)

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US201962938881P 2019-11-21 2019-11-21
US62/938,881 2019-11-21

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023086992A3 (fr) * 2021-11-12 2023-06-15 Myka Labs, Inc. Dispositifs expansifs pour interventions endoluminales
WO2023059791A3 (fr) * 2021-10-07 2023-06-29 W. L. Gore & Associates, Inc. Systèmes et procédés de distribution pour canules d'entrée/sortie

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US6400991B1 (en) 1999-05-03 2002-06-04 Abiomed, Inc. Electromagnetic field source method with detection of position of secondary coil in relation to multiple primary coils
US7658747B2 (en) 2003-03-12 2010-02-09 Nmt Medical, Inc. Medical device for manipulation of a medical implant
US20110130619A1 (en) * 2008-05-05 2011-06-02 Coherex Medical, Inc. Ventricular assist device and related methods
US20120059459A1 (en) * 2009-05-11 2012-03-08 Mayo Foundation For Medical Education And Research Treating congestive heart failure
US8551135B2 (en) 2006-03-31 2013-10-08 W.L. Gore & Associates, Inc. Screw catch mechanism for PFO occluder and method of use
US20150258260A1 (en) * 2014-03-17 2015-09-17 Daassist As Percutaneous system, devices and methods
US20170196565A1 (en) * 2016-01-08 2017-07-13 Nuheart As Method for coupling anatomical walls using a connector
US20180099078A1 (en) * 2016-10-07 2018-04-12 Nuheart As Transcatheter device and system for the delivery of intracorporeal devices
US20190015232A1 (en) * 2015-12-30 2019-01-17 Nuheart As Transcatheter insertion system
US20190321528A1 (en) * 2018-04-23 2019-10-24 W. L. Gore & Associates, Inc. Prosthetic pump and delivery system
WO2020091910A1 (fr) * 2018-11-02 2020-05-07 W. L. Gore & Associates, Inc. Dispositifs et procédés d'assistance ventriculaire implantables

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Publication number Priority date Publication date Assignee Title
US6400991B1 (en) 1999-05-03 2002-06-04 Abiomed, Inc. Electromagnetic field source method with detection of position of secondary coil in relation to multiple primary coils
US7658747B2 (en) 2003-03-12 2010-02-09 Nmt Medical, Inc. Medical device for manipulation of a medical implant
US8551135B2 (en) 2006-03-31 2013-10-08 W.L. Gore & Associates, Inc. Screw catch mechanism for PFO occluder and method of use
US20110130619A1 (en) * 2008-05-05 2011-06-02 Coherex Medical, Inc. Ventricular assist device and related methods
US20120059459A1 (en) * 2009-05-11 2012-03-08 Mayo Foundation For Medical Education And Research Treating congestive heart failure
US20150258260A1 (en) * 2014-03-17 2015-09-17 Daassist As Percutaneous system, devices and methods
US20190015232A1 (en) * 2015-12-30 2019-01-17 Nuheart As Transcatheter insertion system
US20170196565A1 (en) * 2016-01-08 2017-07-13 Nuheart As Method for coupling anatomical walls using a connector
US20180099078A1 (en) * 2016-10-07 2018-04-12 Nuheart As Transcatheter device and system for the delivery of intracorporeal devices
US20190321528A1 (en) * 2018-04-23 2019-10-24 W. L. Gore & Associates, Inc. Prosthetic pump and delivery system
WO2020091910A1 (fr) * 2018-11-02 2020-05-07 W. L. Gore & Associates, Inc. Dispositifs et procédés d'assistance ventriculaire implantables

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023059791A3 (fr) * 2021-10-07 2023-06-29 W. L. Gore & Associates, Inc. Systèmes et procédés de distribution pour canules d'entrée/sortie
WO2023086992A3 (fr) * 2021-11-12 2023-06-15 Myka Labs, Inc. Dispositifs expansifs pour interventions endoluminales
US12076254B2 (en) 2021-11-12 2024-09-03 Myka Labs, Inc. Expanding devices for endoluminal interventions

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