WO2023283751A1 - Dispositif d'assistance cardiaque en cas d'insuffisance cardiaque - Google Patents

Dispositif d'assistance cardiaque en cas d'insuffisance cardiaque Download PDF

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Publication number
WO2023283751A1
WO2023283751A1 PCT/CN2021/105656 CN2021105656W WO2023283751A1 WO 2023283751 A1 WO2023283751 A1 WO 2023283751A1 CN 2021105656 W CN2021105656 W CN 2021105656W WO 2023283751 A1 WO2023283751 A1 WO 2023283751A1
Authority
WO
WIPO (PCT)
Prior art keywords
bushing
bush
magnet
receiving
channel
Prior art date
Application number
PCT/CN2021/105656
Other languages
English (en)
Chinese (zh)
Inventor
齐献山
徐嘉颢
罗根·托马斯·乔治
张磊
张家良
付建新
Original Assignee
苏州心擎医疗技术有限公司
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 苏州心擎医疗技术有限公司 filed Critical 苏州心擎医疗技术有限公司
Priority to PCT/CN2021/105656 priority Critical patent/WO2023283751A1/fr
Priority to CN202220733003.6U priority patent/CN218572654U/zh
Priority to CN202210383880.XA priority patent/CN115430038A/zh
Priority to CN202210383884.8A priority patent/CN115463338B/zh
Priority to CN202210382380.4A priority patent/CN115463337B/zh
Priority to CN202210382379.1A priority patent/CN115591107B/zh
Priority to PCT/CN2022/086472 priority patent/WO2023284339A1/fr
Priority to CN202210795839.3A priority patent/CN115382093A/zh
Publication of WO2023283751A1 publication Critical patent/WO2023283751A1/fr
Priority to CN202310248247.4A priority patent/CN116236683A/zh

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/17—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart inside a ventricle, e.g. intraventricular balloon pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—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
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for 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
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/419—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being permanent magnetic, e.g. from a rotating magnetic coupling between driving and driven magnets
    • 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
    • A61M60/50—Details relating to control
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/804—Impellers
    • 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
    • A61M60/90—Details not provided for in groups A61M60/40, A61M60/50 or A61M60/80

Definitions

  • the invention relates to a device for assisting the heart when its function fails, and belongs to the technical field of medical devices.
  • Heart failure is a life-threatening disease, and once it progresses to an advanced stage, the one-year mortality rate is about 75%.
  • ventricular assist device technology Given the limited number of heart donors in advanced heart failure, ventricular assist device technology has emerged as a viable therapeutic or alternative treatment option between erected subjects and transplant surgery.
  • adverse events caused by current technology still limit the use of ventricular assist devices in the treatment of critically ill subjects.
  • the existing ventricular assist devices have problems such as low transmission efficiency.
  • the existing ventricular assist devices have problems such as low transmission efficiency.
  • the purpose of the present invention is to provide a device for assisting the heart in failure, which can significantly improve the performance of the device.
  • the device of the first aspect of the present invention comprises:
  • the drive shaft is passed through the catheter
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered in the subject's vasculature at a first outer diameter size, and, in a corresponding operative configuration of the pump is deployed such that the pump is at a second outer diameter size greater than the first outer diameter size.
  • the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades are configured to: in the corresponding intervention configuration of the pump Wrapped on the outer wall of the hub and at least partially in contact with the inner wall of the pump casing, and extending radially outward from the hub and spaced from the inner wall of the pump casing when the pump is in a corresponding working configuration ;
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft connected passive magnets;
  • connection assembly is configured to: correspond to when the socket is not connected to the coupler, the motor end bush is separated from the intervening end bush; and, corresponding to the connection of the socket to the coupler , the motor end bushing is connected to the intervening end bushing, the active magnet and the passive magnet are at least partially coincident along the axial projection of the drive shaft, and the active magnet and the passive magnet are spaced apart along the axial direction ;
  • connection assembly is further configured to: corresponding to the unconnected state of the socket and the coupler, the magnetic coupling force between the active magnet and the passive magnet is smaller than that corresponding to the connected state of the socket and the coupler
  • the magnetic coupling force between the active magnet and the passive magnet is described below.
  • the device of the second aspect of the present invention comprises:
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered in the subject's vasculature at a first outer diameter size, and, in a corresponding operative configuration of the pump is deployed such that the pump is at a second outer diameter size greater than the first outer diameter size.
  • the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades are configured to: in the corresponding intervention configuration of the pump Wrapped on the outer wall of the hub and at least partially in contact with the inner wall of the pump casing, and extending radially outward from the hub and spaced from the inner wall of the pump when the pump is in a corresponding working configuration;
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft a connected passive magnet;
  • the connecting assembly is configured to transmit the rotation of the motor to the drive shaft by means of the coupling between the active magnet and the passive magnet, thereby driving the impeller to rotate;
  • the device further includes: a perfusion channel that runs through the pump, the drive shaft and the coupler; the proximal inlet of the perfusion channel is provided at the proximal end of the intervention end bushing and connects the The cavity in which the passive magnet is housed.
  • the device of the third aspect of the present invention comprises:
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered in the subject's vasculature at a first outer diameter size, and, in a corresponding operative configuration of the pump is deployed such that the pump is at a second outer diameter size greater than the first outer diameter size.
  • the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades are configured to: in the corresponding intervention configuration of the pump Wrapped on the outer wall of the hub and at least partially in contact with the inner wall of the pump casing, and extending radially outward from the hub and spaced from the inner wall of the pump when the pump is in a corresponding working configuration;
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft a connected passive magnet;
  • the connecting assembly is configured to transmit the rotation of the motor to the drive shaft by means of the coupling between the active magnet and the passive magnet, thereby driving the impeller to rotate;
  • the device further includes a guide channel passing through the pump, the drive shaft and the coupler, and the guide channel includes a bypass outlet located on the side of the inserting end bushing.
  • the device of the fourth aspect of the present invention comprises:
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered in the subject's vasculature at a first outer diameter size, and, in a corresponding operative configuration of the pump is deployed such that the pump is at a second outer diameter size greater than the first outer diameter size.
  • the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades are configured to: in the corresponding intervention configuration of the pump Wrapped on the outer wall of the hub and at least partially in contact with the inner wall of the pump casing, and extending radially outward from the hub and spaced from the inner wall of the pump when the pump is in a corresponding working configuration;
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft a connected passive magnet;
  • the connecting assembly is configured to transmit the rotation of the motor to the drive shaft by means of the coupling between the active magnet and the passive magnet, thereby driving the impeller to rotate;
  • the bushing at the motor end is mated with the bushing at the intervening end, one of them is configured as a plug, and the other of the two includes a slot for receiving the plug;
  • a bushing is defined as an inserting bushing and a bushing defining said slot is defined as a receiving bushing;
  • the device further includes a locking mechanism for engaging and fixing the inserting bush and the receiving bush, and the locking mechanism includes: an engagement formed on one of the outer wall of the inserting bush and the inner wall of the receiving bushing portion and a locking member operatively embedded in the engaging portion.
  • the device of the fifth aspect of the present invention comprises:
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered in the subject's vasculature at a first outer diameter size, and, in a corresponding operative configuration of the pump is deployed such that the pump is at a second outer diameter size greater than the first outer diameter size.
  • the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades are configured to: in the corresponding intervention configuration of the pump Wrapped on the outer wall of the hub and at least partially in contact with the inner wall of the pump casing, and extending radially outward from the hub and spaced from the inner wall of the pump when the pump is in a corresponding working configuration;
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft a connected passive magnet;
  • the connecting assembly is configured to transmit the rotation of the motor to the drive shaft by means of the coupling between the active magnet and the passive magnet, thereby driving the impeller to rotate;
  • the bushing at the motor end is mated with the bushing at the intervening end, one of them is configured as a plug, and the other of the two includes a slot for receiving the plug;
  • a bushing is defined as an inserting bushing and a bushing defining said slot is defined as a receiving bushing;
  • the device further includes a locking mechanism for engaging and fixing the inserting bush and the receiving bush, and the locking mechanism is configured to realize the axial fixing of the inserting bush and the receiving bush by increasing friction .
  • the device of the sixth aspect of the present invention comprises:
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered to the desired location in the subject's vasculature at a first outer diameter size, and the pump is deployed in a corresponding working configuration such that the pump is larger than the first outer diameter pump blood at the desired location; the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades being configured to: The pump is wrapped on the outer wall of the hub and is at least partially in contact with the inner wall of the pump casing when the pump is in the corresponding intervention configuration, and extends radially outward from the hub and is
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft a connected passive magnet;
  • the connecting assembly is configured to transmit the rotation of the motor to the drive shaft by means of the coupling between the active magnet and the passive magnet, thereby driving the impeller to rotate;
  • the device further includes a connecting shaft rotatably arranged in the first axial channel of the intervening end bush, the front end of the connecting shaft is connected with the driving shaft, and the rear end is connected with the passive magnet ; At least one bearing is arranged outside the connecting shaft, and a damping element is arranged between the outer ring of the bearing and the inner wall of the first axial passage.
  • the device of the sixth aspect of the present invention comprises:
  • a pump that can be delivered to a desired location in the heart through the catheter to pump blood, comprising a pump housing connected to the distal end of the catheter and having an inlet end and an outlet port, an impeller housed within the pump housing, the impeller being The drive shaft is driven in rotation to draw blood into the pump housing from the inlet end and out from the outlet end; the pump housing and impeller are configured to be compressed in a corresponding interventional configuration of the pump to The pump is delivered in the subject's vasculature at a first outer diameter size, and, in a corresponding operative configuration of the pump is deployed such that the pump is at a second outer diameter size greater than the first outer diameter size.
  • the impeller includes a hub connected to the distal end of the drive shaft and blades supported on the outer wall of the hub, the blades are configured to: in the corresponding intervention configuration of the pump Wrapped on the outer wall of the hub and at least partially in contact with the inner wall of the pump casing, and extending radially outward from the hub and spaced from the inner wall of the pump when the pump is in a corresponding working configuration;
  • a drive assembly comprising a motor housing and a motor accommodated in the motor housing and having a motor shaft;
  • a connection assembly for detachably connecting the drive assembly with the drive shaft including a socket and a coupler;
  • the socket includes a motor end bushing connected to the motor housing and housed in the motor housing An active magnet inside the end bushing and connected to the motor shaft,
  • the coupler includes an intervening end bushing connected to the proximal end of the catheter, and is received inside the intervening end bushing and connected to the proximal end of the drive shaft a connected passive magnet;
  • the connecting assembly is configured to transmit the rotation of the motor to the drive shaft by means of the coupling between the active magnet and the passive magnet, thereby driving the impeller to rotate;
  • the bushing at the motor end is mated with the bushing at the intervening end, one of them is configured as a plug, and the other of the two includes a slot for receiving the plug;
  • a bushing is defined as an inserting bushing and a bushing defining said slot is defined as a receiving bushing;
  • a drag reducing structure is provided between the inserting bush and the receiving bush, and the drag reducing structure is configured to reduce the impact of gas formation on the inserting bush when the inserting bush is inserted into the receiving bush. insertion resistance.
  • the active magnet and the passive magnet have approximately the same cross-sectional shape perpendicular to the axial direction.
  • the offset of the projection of the center of mass of the passive magnet relative to the center of mass of the active magnet does not exceed 20%.
  • the projection coincidence degree of the active magnet and the passive magnet along the axial direction is greater than or equal to 80%; preferably, the active magnet and the passive magnet are completely aligned along the axial direction.
  • the magnetic coupling force between the active magnet and the passive magnet is configured to be insufficient to transmit the rotational power of the motor to the drive shaft; or, the The magnetic coupling force is insufficient to overcome the rotation resistance of the drive shaft; or, the magnetic coupling force is zero.
  • the active magnet and the passive magnet have at least a state in which the coincidence degree along the axial projection is 0.
  • the active magnet and the passive magnet are circular magnets continuous in the circumferential direction; or, the active magnet and the passive magnet include a plurality of magnets arranged at intervals in the circumferential direction.
  • the magnetized surfaces of the active magnet and the passive magnet facing each other have the same shape.
  • the bushing at the motor end is mated with the bushing at the intervening end, one of them is configured as a plug, and the other of the two includes a slot for receiving the plug;
  • the plug will be configured as The bushing of is defined as an inserting bushing, and the bushing defining said slot is defined as a receiving bushing;
  • the device also includes a locking mechanism for engaging and fixing the inserting bush and the receiving bush, the locking mechanism comprising: an engaging portion formed on one of the outer wall of the inserting bush and the inner wall of the receiving bush; A locking member operably engages in the joint.
  • the engaging portion is a locking groove formed inwardly from the outer surface of the inserting bush, the side wall of the receiving bush is provided with an opening, and the locking member is configured as a radially movable pin ; the pin is operable to be inserted into or removed from the lock slot through the opening;
  • the pin is arranged in a supporting sleeve, and the supporting sleeve is sleeved outside the receiving bush and fixedly arranged relative to the receiving bush.
  • the pin has a locked state inserted into the lock slot to securely engage the motor end bush with the access end bush, and to move out of the lock slot to allow the motor end bush to engage with the access end bush. Release the unlocked state of the fixed engagement;
  • a first elastic member is biased between the pin and the support sleeve, and the reset force exerted by the first elastic member on the pin makes the pin have a tendency to maintain the locked state or move toward the locked state .
  • the locking mechanism further includes: a rotatable unlocking actuator provided outside the receiving bush, the unlocking actuator including a profiling part that cooperates with the pin; the profiling part is configured to When the unlocking actuator rotates in a first direction, a force opposite to that of the first elastic member is applied to the pin, and is released when the unlocking actuator rotates in a second direction opposite to the first direction. force applied to the pin.
  • a rotatable unlocking actuator provided outside the receiving bush, the unlocking actuator including a profiling part that cooperates with the pin; the profiling part is configured to When the unlocking actuator rotates in a first direction, a force opposite to that of the first elastic member is applied to the pin, and is released when the unlocking actuator rotates in a second direction opposite to the first direction. force applied to the pin.
  • the unlocking actuator is configured such that: when the pin is rotated to a first dead point along the first direction, the pin is in an unlocked state, and when the pin is rotated to a second dead point along the second direction, pin is locked;
  • a second elastic member is provided between the unlocking actuator and the supporting sleeve, and the reset force exerted by the second elastic member on the unlocking actuator makes it maintain at the second dead center position or toward The tendency of the movement of the second dead center position.
  • the support sleeve is provided with a generally arc-shaped track opening along the circumferential direction
  • the unlocking actuator includes a locking protrusion extending into the track opening
  • the locking protrusion has a direction The first stop surface in the first direction and the second stop surface pointing in the second direction
  • the second elastic member is arranged between the first stop surface and the inner wall of the track opening.
  • the unlocked state of the unlocking actuator corresponds to the state when the second stop surface is in contact with the inner wall of the track opening
  • the locked state corresponds to the state when the second elastic member is further compressed
  • the unlocking actuator is connected with an operating member located outside the support sleeve, and the operating member is configured to receive an external force to drive the unlocking actuator to rotate in the first direction.
  • the joint part is an opening penetrating through the side wall of the receiving bush or a groove only penetrating the inner wall of the receiving bush;
  • the outer surface of the insert bush is recessed inwardly to form a receiving groove
  • the locking member is configured as a pin or a ball that is at least partially accommodated in the receiving groove and can move radially; the pin or The radially outer end of the ball has an unlocked state that does not exceed the outer surface of the insertion bush to unlock the insertion bush and the receiving bush, and the radial outer end protrudes from the outer surface of the insertion bush to engage the
  • the engaging portion combines and fixes the inserting bush and the receiving bush in a locked state.
  • an elastic reset member is biased between the pin or the ball and the receiving groove, and the reset force exerted by the elastic reset member on the pin makes it always move radially outward to maintain the A locked state or a tendency to move towards said locked state.
  • a drag reducing structure is provided between the inserting bush and the receiving bush, and the drag reducing structure is configured to reduce the impact of gas formation on the receiving bush when the inserting bush is inserted into the receiving bush. Insertion resistance of the insert bushing.
  • a gap is formed between the support sleeve and the receiving bush; the drag reducing structure includes a pressure relief hole penetrating the side wall of the receiving bush, and the pressure relief hole passes through the gap and The external space is connected.
  • the drag reducing structure includes a pressure relief groove formed on the inner wall of the receiving bush and/or the outer wall of the insertion bush and communicated with the external space.
  • the drag reducing structure includes a space formed between the inserting bush and the receiving bush when the inserting bush and the receiving bush are in an engaged state.
  • the space includes a groove formed in the insertion bush facing the receiving bush.
  • the locking groove is formed inwardly from the outer surface of the inserting bush, and the locking member is configured as a generally annular spring ring formed on the inner wall of the receiving bush, and the spring ring is radially Reversible deformation.
  • the recoverable deformation does not exceed 20%.
  • the spring coil is a canted coil spring.
  • a substantially annular receiving groove is formed on the inner wall of the receiving bush, and the spring ring is limited in the receiving groove; wherein, the depth of the receiving groove is smaller than the diameter of the spring ring.
  • the spring ring is configured to sink into the receiving groove when the inserting bush is engaged with the receiving bush, which is larger than when the inserting bush is not engaged with the receiving bush. depth.
  • the locking groove is formed by recessing outward from the inner surface of the receiving bush, and the locking piece is configured as a protrusion formed on the inner wall of the inserting bush;
  • the locking groove includes The first slot extending in the inserting direction of the sleeve and the second slot connected to the first slot, the extending direction of the second slot and the extending direction of the first slot form an angle not equal to 0°.
  • the inner wall of the second groove forms a stop surface on which the protrusion is hooked.
  • the included angle is 90°.
  • the bushing at the motor end is mated with the bushing at the intervening end, one of them is configured as a plug, and the other of the two includes a slot for receiving the plug;
  • the plug will be configured as The bushing of is defined as an inserting bushing, and the bushing defining said slot is defined as a receiving bushing;
  • the device also includes a locking mechanism for engaging and securing the male bush and the receiving bush, the locking mechanism being configured to achieve axial fixation of the male bush and the receiving bush by increasing friction.
  • the locking mechanism includes a hoop sleeved on the receiving bushing and a locking operating member operable to lock or release the hoop.
  • the locking mechanism includes a threaded hole penetrating through the side wall of the receiving bush, and a bolt screwed into the threaded hole; the inner end of the bolt can be rotated to compress or disengage from the threaded hole. Insert the outer surface of the bushing as described.
  • a passive magnet protection component is provided outside the passive magnet.
  • the passive magnet protection assembly includes a first protection layer at least partially covering the outer surface of the passive magnet, the first protection layer being configured to at least isolate liquid from contact with the passive magnet.
  • the first protective layer is a waterproof coating.
  • the first protection layer forms a first accommodation cavity for accommodating the passive magnet therein.
  • the first protective layer is non-magnetic and configured to rotate together with the passive magnet.
  • the passive magnet protection assembly further includes a second protection layer disposed in the intervening end bushing and physically separated from the passive magnet; the second protection layer is non-magnetic and non-conductive, and configured not to rotate with the passive magnet.
  • a first magnetic restraint located at the distal end of the passive magnet is provided in the inserting end bush, and the first magnetic restraint is magnetically conductive.
  • a connecting shaft is rotated inside the inserting end bush, the passive magnet is sleeved on the proximal end of the connecting shaft, and the driving shaft is connected to the distal end of the connecting shaft;
  • the first magnetic constraint is arranged at the proximal end of the connecting shaft, and the passive magnet is fixed on the proximal end surface of the first magnetic constraint.
  • an active magnet protection component is provided outside the active magnet.
  • the active magnet protection assembly includes a third protection layer covering at least the rear end face of the active magnet.
  • the third protection layer is configured to further cover the front face of the active magnet.
  • the front end of the active magnet is exposed.
  • a magnet fixing block is provided on the motor shaft, and the active magnet is sheathed on the magnet fixing block; the third protective layer forms with the magnet fixing block to at least partially store the active magnet Inside the second storage chamber.
  • the third protection layer is non-magnetic and configured to rotate together with the active magnet.
  • the active magnet protection assembly further includes a fourth protection layer disposed in the motor end bushing and physically separated from the active magnet; the fourth protection layer is non-magnetic and non-conductive, and configured not to rotate with the active magnet.
  • the motor end bushing is provided with a second magnetic restraint behind the active magnet, and the second magnetic restraint is magnetically permeable.
  • the second magnetic constraint is connected to the motor shaft, and the active magnet is fixed on the distal end surface of the second magnetic constraint.
  • the device further includes a connecting shaft rotatably arranged in the first axial channel of the intervening end bush, the front end of the connecting shaft is connected to the driving shaft, and the rear end is connected to the passive magnet Connection; at least one bearing is arranged outside the connecting shaft, and a damping element is arranged between the outer ring of the bearing and the inner wall of the first axial passage.
  • the drive shaft and the connecting shaft are circumferentially fixed and axially slidable.
  • the proximal end of the drive shaft is provided with or formed with a hollow connecting portion, and the cross-section of the connecting portion is in any shape other than a circle; the distal end of the connecting shaft is formed with a The connecting part is slidably inserted into the matching channel in the axial direction.
  • the damping element is flexible, approximately annular, and sleeved on the outer peripheral surface of the bearing.
  • the device further includes a perfusion channel that runs through the pump, the catheter, the drive shaft and the coupler; the proximal inlet of the perfusion channel is located at the proximal end of the intervention end bushing And the cavity in which the passive magnet is accommodated.
  • the inserting end bushing is provided with a perfusion input channel communicating with the cavity, and the outer end of the perfusion input channel passes through the connecting assembly and is used to communicate with a perfusion fluid source.
  • the perfusion channel includes in the coupler part: a second axial channel formed in the connecting shaft, a first gap formed between the connecting shaft and the first axial channel ;
  • the second axial passage, the first gap communicate with the cavity.
  • said mating channel is part of said second axial channel.
  • the perfusion channel includes a second gap formed between the drive shaft and the shaft lumen of the catheter at the part of the catheter and the driving shaft.
  • the drive shaft is axially penetrated, and the perfusion channel further includes a third axial channel formed in the drive shaft at the part of the drive shaft.
  • the sidewall of the drive shaft is liquid permeable; alternatively, the sidewall of the drive shaft is liquid impermeable.
  • said priming channel comprises, in said pump portion, a fourth axial channel formed in said hub and communicating with said third axial channel.
  • the distal outlet of the perfusion channel comprises the distal opening of the catheter, further comprising the distal opening of the hub.
  • the coupler further includes a positioning sleeve connected to the distal end of the intervention end bushing; the proximal end of the catheter is accommodated in the positioning sleeve, and the proximal end of the drive shaft is exposed from the positioning sleeve;
  • the second gap communicates with the first gap through the positioning sleeve, and the third axial passage communicates with the second axial passage.
  • the coupler also includes a housing connected to the distal end of the insertion end bushing and containing the positioning sleeve therein, the distal opening of the housing is provided with a retaining sleeve for the catheter to pass through .
  • the outer surface of the housing is configured to be flush with the outer surface of the receptacle when the coupler and the receptacle are in a connected state.
  • the device further includes a guide channel through the pump, the catheter, the drive shaft and the coupler, the guide channel includes a bypass outlet on the side of the inserting end bushing .
  • the guide channel further includes an end face outlet located on the proximal end face of the interventional end bushing, the guide channel is configured to guide a guide wire from the end face outlet and the bypass outlet One of them goes out.
  • the guide channel includes, at the pump and drive shaft parts: an axial hollow cavity formed in the hub and the drive shaft.
  • the connecting shaft is also hollow, and the proximal end of the drive shaft is inserted into the connecting shaft; a seal with a resealable channel is arranged in the outlet of the end face;
  • the resealable channel is in a closed sealing state
  • the resealable channel is open for passage of the guidewire when the seal is in the second state.
  • the seal is a flexible sealing plug that can move axially in the end face outlet, and the outer wall of the flexible sealing plug and/or the inner wall of the end face outlet are designed to be inclined so that the flexible sealing plug can move axially When moving in the first direction, it is squeezed to switch to the first state, and when moving in a second direction opposite to the first direction, it expands radially to switch to the second state.
  • the seal is a bladder structure
  • the first state corresponds to the state when the bladder structure is filled with fluid medium or elastic material
  • the second state corresponds to the fluid medium in the bladder structure being filled with at least The released state of the part.
  • the bypass outlet is in a sealed state.
  • the inserting end bushing is provided with a first bypass channel connecting the bypass outlet and the axial channel of the connecting shaft inside, and the side wall of the connecting shaft is provided with a second bypass channel connected with the internal channel. a bypass channel; the second bypass channel is selectively communicated with the first bypass channel.
  • the guide wire bypass cannula when the second bypass channel is in communication with the first bypass channel, the guide wire bypass cannula is operable to be inserted through the two bypass channels in sequence, and the inner end of the guide wire bypass is connected to the drive The proximal end of the shaft is butt-connected.
  • the guide wire bypass cannula when the guide wire bypass cannula is inserted, the passage of the guide wire passing through the outlet of the end face is blocked.
  • the end face outlet is in a sealed state.
  • a sealing plug is optionally provided in the bypass outlet; the sealing plug is configured to be removed from the bypass outlet when the device is in the state of passing through the guide wire when the guide wire needs to pass through the bypass outlet. It is removed from the bypass outlet, and is inserted into the bypass outlet when it is in any other working state except the state of removing the guide wire.
  • the present invention has the following beneficial effects: the device for assisting the heart in the event of functional failure can obviously improve the performance of the device.
  • Fig. 1 and Fig. 2 are three-dimensional schematic diagrams of different angles of the device provided by the present invention.
  • Fig. 3 is a three-dimensional schematic diagram of the separation of the drive assembly and the working assembly of the device shown in Fig. 1;
  • Fig. 4 is an axial sectional view of the device shown in Fig. 1;
  • Fig. 5 is a partial three-dimensional exploded schematic diagram of the device shown in Fig. 1;
  • Fig. 6 is a sectional view of the device shown in Fig. 1 along a plane perpendicular to the axial direction;
  • Fig. 7 is the partial structure of the drive assembly of the device shown in Fig. 1 along the sectional view of a plane of axial aspect;
  • Fig. 8 is the sectional view of another plane along the axial aspect of the partial structure of the working assembly of the device shown in Fig. 1;
  • FIG. 9 and 10 are partial cross-sectional views of the proximal end of the working assembly of the device shown in FIG. 1.
  • the sealing member closes the end face opening at the proximal end; in FIG. Connected to the outside world.
  • Fig. 11 shows a schematic structural view of a locking mechanism provided by another embodiment of the present invention.
  • Fig. 14 shows a schematic structural diagram of a locking mechanism provided by another embodiment of the present invention.
  • proximity refers to the clinician who manipulates the device (hereinafter referred to as the device) for assisting the heart when its function fails.
  • proximal and posterior refer to the part relatively close to the clinician
  • distal refers to the part relatively far away from the clinician.
  • the driving component is at the proximal end and the rear end
  • the working component is at the distal end and the front end; for another example, the proximal end of a certain part/component means the end relatively close to the driving component, and the far end means the end relatively close to the working component.
  • the device of the present invention defines "axial direction” or “axial extension direction” by the extension direction of the motor shaft, connecting shaft, and drive shaft.
  • the driving shaft is a flexible shaft, and the axial direction of the driving shaft refers to the axial direction when the driving shaft is adjusted to extend in a straight line.
  • the terms “inner” and “outer” used in the present invention are relative to the axially extending centerline, the direction relatively close to the centerline is “inner”, and the direction relatively far away from the centerline is “outer”.
  • orientations of “near”, “far”, “rear”, “front”, “inner” and “outer” are definitions for convenience of description.
  • the device can be used in many orientations and positions, and thus these terms expressing relative positional relationships are not intended to be limiting and absolute.
  • the above definition of each direction is only for the convenience of explaining the technical solution of the present invention, and does not limit the auxiliary device of the present invention when it includes but is not limited to product testing, transportation and manufacturing, etc., which may lead to its inversion or position
  • the orientation in the scene where the transformation occurs In the present invention, if the above definitions are otherwise clearly defined and limited, they shall follow the above clearly specified and limited.
  • connection and “connected” should be interpreted in a broad sense unless otherwise specified and limited. For example, it can be a fixed connection, a detachable connection, a movable connection, or an integral body; it can be directly connected or indirectly connected through an intermediary, and it can be the internal communication of two components or two components. interaction relationship. Those of ordinary skill in the art can understand the specific meanings of the above terms in the present invention according to specific situations.
  • the device 100 can at least partially assist the pumping function of the heart, and at least partially reduce the burden on the heart.
  • the device 100 can be used as a left ventricular assist, and its working part (specifically referred to as the pump below) can be inserted into the left ventricle, and the pump can pump the blood in the left ventricle when it is running into the ascending aorta.
  • the pump can pump the blood in the left ventricle when it is running into the ascending aorta.
  • the device 100 is used as left ventricular assistance, which is only a possible application scenario of the device 100 .
  • the device 100 can also be used as a right ventricular assist, the working part can be inserted into the right ventricle, and the pump pumps the blood in the vein to the right and left ventricle during operation.
  • the device 100 can also be adapted to pump blood from the vena cava and/or right atrium into the right ventricle, from the vena cava and/or right atrium into the pulmonary artery, and/or from the renal vein into the vena cava, and can also be configured as Placed within the subclavian or jugular vein at the junction of the vein with the lymphatic duct and used to increase the flow of lymphatic fluid from the lymphatic vessel to the vein.
  • the following will mainly use the device 100 as left ventricular assistance as the main scenario for illustration. However, based on the above description, it can be seen that the protection scope of the embodiments of the present invention is not limited thereby.
  • the device 100 includes a driving assembly 10 and a working assembly 30 .
  • the drive assembly 10 includes a motor housing 12 and a motor 14 accommodated in the motor housing 12 and having a motor shaft 16 .
  • the working assembly 30 includes a conduit 32 , a drive shaft 34 passing through the conduit 32 , and a pump 36 driven by the drive shaft 34 .
  • the driving assembly 10 provides power for the working assembly 30 to drive the working assembly 30 to realize the function of pumping blood.
  • the pump 36 and part of the catheter 32 (specifically, the front end of the catheter 32 ) are sent into and kept in the body of the subject, and it is desirable that the size of the pump 36 and the catheter 32 be as small as possible. Therefore, the axially projected areas of the pump 36 and the conduit 32 are smaller than the axially projected areas of other components of the working assembly 30 and also smaller than the axially projected area of the driving assembly 10 .
  • the pump 36 and the catheter 32 with a smaller size can enter the human body through a smaller intervention size, which reduces the pain caused to the subject during the intervention process and reduces complications caused by an oversized intervention size.
  • Other parts of the working assembly 30 may have relatively large dimensions, so as to meet the requirements of structural design.
  • the relatively large size of the drive assembly 10 can meet the needs of structural design and provide sufficient power for the drive shaft 34 and the pump 36 to meet the power requirements of the drive shaft 34 and the pump 36 .
  • the driving assembly 10 is detachably connected with the working assembly 30 .
  • the driving assembly 10 and the working assembly 30 can be disassembled to prevent the larger and heavier driving assembly 10 from affecting the pump 36 and the front end of the catheter 32
  • the operation in which part is sent into the subject's body is easier to operate.
  • the driving assembly 10 drives the working assembly 30 through magnetic coupling, specifically:
  • the driving assembly 10 includes a socket, and the working assembly 30 includes a coupler.
  • the socket includes a motor end bushing 20 connected to the motor housing 12 and an active magnet 22 housed inside the motor end bushing 20 and connected to the motor shaft 16 .
  • the coupler includes an intervening end bushing 40 disposed at the proximal end of the working component 30 and a passive magnet 42 accommodated inside the intervening end bushing 40 and connected to the proximal end of the driving shaft 34 .
  • the transmission chain of the driving assembly 10 includes a motor shaft 16 and an active magnet 22 connected to the motor shaft 16 .
  • the transmission link of the working assembly 30 includes a passive magnet 42 , a connecting shaft 44 on which the passive magnet 42 is installed, a driving shaft 34 connected to the distal end of the connecting shaft 44 , and a pump 36 connected to the distal end of the driving shaft 34 .
  • a protective head 38 is provided at the distal end of the pump 36, which is configured to be soft so as not to damage the tissue of the subject, and the protective head 38 can exhibit flexibility from any macro material.
  • the protective head 38 is a flexible protrusion (Pigtail or Tip member) with an arc-shaped or coiled end, and the flexible end is supported on the inner wall of the ventricle in a non-invasive or non-damaging manner, and the pump 36
  • the suction port of the pump is separated from the inner wall of the ventricle, so as to prevent the suction port of the pump 36 from adhering to the inner wall of the ventricle due to the reaction force of the fluid (blood) during the working process, so as to ensure the effective area of pumping.
  • the driving shaft 34 is a flexible shaft that can be deformed visible to the naked eye.
  • the passive magnet 42 is installed on the connecting shaft 44, and the connecting shaft 44 is a hard shaft, which cannot be deformed by naked eyes, so that the installation of the driving magnet can be made more stable.
  • the motor shaft 16 drives the active magnet 22 to rotate
  • the passive magnet 42 is magnetically coupled with the active magnet 22
  • the passive magnet 42 is driven to rotate by the active magnet 22
  • the passive magnet 42 rotates to drive the connecting shaft 44 and the drive shaft 34 to rotate in turn.
  • the drive shaft 34 rotates to drive the pump 36 to pump blood.
  • connection assembly the combination of the connector and the coupler.
  • the connecting assembly is configured as follows: when the corresponding socket is not connected to the coupler, the motor end bush 20 is separated from the intervening end bush 40; The bushing 40 is connected, the active magnet 22 and the passive magnet 42 are at least partially coincident along the axial projection of the drive shaft 34 , and the active magnet 22 and the passive magnet 42 are spaced apart along the axial direction.
  • the active magnet 22 can drive the passive magnet 42 more efficiently, improving transmission efficiency.
  • the active magnet 22 and the passive magnet 42 are spaced apart in the axial direction, and the non-contact power transmission can be realized through the magnetic coupling between the two magnets, which is beneficial to realize the sealing of the fluid and prevent the fluid from entering the motor.
  • the liquid referred to above is the purge liquid that needs to be poured into the human body during the operation of the device 100.
  • the purge liquid is a physiological fluid that can partially maintain the functions of the human body, such as physiological saline, glucose solution, anticoagulant, or any combination of the above .
  • connection assembly is further configured such that: the magnetic coupling force between the active magnet 22 and the passive magnet 42 when the corresponding socket and the coupler are in an unconnected state is smaller than that between the active magnet 22 and the passive magnet 42 when the corresponding socket and the coupler are in a connected state. Magnetic coupling force between magnets 42 .
  • the driving assembly 10 and the working assembly 30 are in an unconnected state, the magnetic coupling force between the active magnet 22 and the passive magnet 42 is small, and the driving assembly 10 is not enough to drive the working assembly. 30. Avoid misuse.
  • the driving assembly 10 and the working assembly 30 are in the connected state, the magnetic coupling force between the active magnet 22 and the passive magnet 42 is strong enough, and the driving assembly 10 can drive the working assembly 30 smoothly.
  • the magnetic coupling force between the active magnet 22 and the passive magnet 42 is configured to be insufficient to transmit the rotational power of the motor 14 to the drive shaft 34; or, the magnetic coupling force is insufficient to overcome The rotation resistance of the drive shaft 34; or, the magnetic coupling force is zero. Therefore, when the socket and the coupler are not connected, the driving assembly 10 cannot drive the working assembly 30, so as to avoid misoperation.
  • the active magnet 22 and the passive magnet 42 have at least a state in which the axial projection coincidence degree is 0. That is to say, when the connector and the coupler are not connected, the active magnet 22 and the passive magnet 42 are completely staggered, the drive assembly 10 is far away from the working assembly 30, and the catheter 32 and the pump 36 of the working assembly 30 can be easily sent into the subject. In the body; and the active magnet 22 cannot drive the passive magnet 42, and the driving assembly 10 cannot drive the working assembly 30, so as to avoid misoperation.
  • the cross-sectional shapes of the active magnet 22 and the passive magnet 42 along a direction perpendicular to the axial direction are substantially the same.
  • the active magnet 22 and the passive magnet 42 may be cylindrical or conical. In this way, the cross-sectional shapes of the active magnet 22 and the passive magnet 42 are both circular.
  • the surfaces of the two magnets facing each other have the same shape, which is beneficial to achieve better magnetic coupling. Therefore, in some embodiments, the overall shape of the active magnet 22 and the passive magnet 42 may be different, but the magnetization surfaces of the two are the same, which is also feasible. For example, one of the magnets is cylindrical and the other is conical.
  • the axial alignment of the two magnets will affect the two coupling efficiencies, and will also affect the positional stability of the magnets in the axial direction and possible vibrations during the transmission process after coupling. Therefore, it is desirable that the two magnets be fully aligned in the axial direction.
  • the two magnets After considering factors such as magnet manufacturing precision and assembly tolerance, it is acceptable for the two magnets to appear within a predetermined range in the axial direction. For example, along the axial direction, the offset of the projection of the center of mass of the passive magnet 42 relative to the center of mass of the active magnet 22 does not exceed 20%, or the projection coincidence degree of the active magnet 22 and the passive magnet 42 along the axial direction is greater than or equal to 80%. %; More preferably, the active magnet 22 is completely aligned with the passive magnet 42 along the axial direction.
  • the center of mass of the magnet can be its center of circle.
  • the offset value of the centers of mass of the two magnets may be a radial offset value based on the axis center of the connecting shaft. Then the offset between the two can be the ratio of the difference between the offset between the two and the offset of any one magnet.
  • the offset between the two is less than 20%, which can realize magnetic coupling and power transmission. Further, the offset between the two is less than 15%, 10%, 5% or even 1%. When the offset of the two is 0, the two magnets are fully aligned along the axial direction.
  • the overlapping degree of the axial projections of the two magnets may be the ratio of the overlapping area of the axial projections of the two magnets to the axial projection area of any one magnet. Likewise, the coincidence degree is greater than or equal to 80%, further, greater than 85%, 90%, 95% or even 100%.
  • the active magnet 22 can drive the passive magnet 42 more efficiently, the transmission efficiency is higher, and the driving assembly 10 can drive the working assembly 30 more efficiently, so that the working assembly 30 can be better realized as The subject's heart provides assistance in pumping blood.
  • the active magnet 22 and the passive magnet 42 are circular magnets continuous in the circumferential direction, or the active magnet 22 and the passive magnet 42 include a plurality of magnets arranged at intervals in the circumferential direction.
  • the motor shaft 16 rotates to drive the active magnet 22 to rotate, and the active magnet 22 rotates to drive the passive magnet 42 to rotate.
  • the active magnet 22 and the passive magnet 42 are annular magnets, or include a plurality of magnets arranged at intervals along the circumferential direction.
  • the magnet 22 and the passive magnet 42 are still ring-shaped during the rotation process, thus, the rotational power of the motor 14 can be transmitted to the working assembly 30 continuously and stably, and the working assembly 30 can realize the blood pumping function stably and reliably.
  • Passive magnet 42 is provided with passive magnet protection assembly 46 outside, and this protection assembly 46 can protect passive magnet 42 from mechanical or chemical damage on the one hand, on the other hand, can provide orientation to the magnetic force of passive magnet 42, restrict its magnetic field range, avoid An undesired spread of magnetic force occurs, allowing the passive magnet 42 to work reliably.
  • the passive magnet protection assembly 46 includes a first protection layer at least partially covering the outer surface of the passive magnet 42 , and the first protection layer is configured to at least isolate liquid from contacting the passive magnet 42 .
  • This liquid is the purge liquid mentioned above.
  • the first protective layer isolates the liquid from being in contact with the passive magnet 42, which can prevent the liquid from corroding the passive magnet 42, prevent the magnet 42 from being corroded by the liquid and cause the magnetic force to weaken, and prolong the life of the magnet 42 providing magnetic force as much as possible.
  • the first protective layer may be a waterproof coating.
  • the waterproof coating can be light and thin but effectively isolate the contact between the liquid and the passive magnet 42 .
  • the first protective layer formed by the waterproof coating has the advantages of thin thickness, light weight, easy forming and high bonding strength, and these advantages will provide beneficial promotion for coupling efficiency, assembly, production cost and service life.
  • the advantage of thin thickness can reduce the setting space for the rear end face of the passive magnet 42, and then shorten the axial distance between the passive magnet 42 and the active magnet, which can improve the coupling efficiency between the two magnets and ensure the transmission effect of rotational power. , is extremely beneficial.
  • the advantages of thin thickness and light weight can also reduce the size and gravity of the magnet, which is conducive to reducing the gravity of the working components and has high adaptability to the assembly space.
  • the waterproof coating can be realized by using existing mature solutions such as spraying, evaporation, and PVD, which have lower requirements on the manufacturing process and the corresponding manufacturing costs can also be reduced.
  • the high bonding strength can significantly improve the anti-peeling performance of the waterproof coating, continuously provide waterproof protection for the magnet 42, and prolong the life of the magnet 42.
  • the first protective layer may be a mechanical structure that wraps or wraps the passive magnet 42 to form a first storage cavity for storing the passive magnet 42 therein. Similar to the above embodiment of the waterproof coating, the first storage chamber can reliably protect the passive magnet 42 and reliably isolate the passive magnet 42 from being corroded by liquid.
  • the passive magnet 42 is arranged at the proximal end of the connecting shaft 44 .
  • the connecting shaft 44 is of variable diameter structure, and its proximal end has a larger diameter, forming a mounting portion 441 , and the passive magnet 42 is sheathed outside the mounting portion 441 .
  • the first protective layer includes a first proximal protection member 451 covering the proximal end surface of the passive magnet 42, a first distal protection member 452 sleeved outside the connecting shaft 44 and covering the distal end surface of the passive magnet 42, and a first distal protection member 452 connected to the first
  • the first peripheral protection member 453 between the proximal protection member 451 and the first distal protection member 452 and covers the peripheral surface of the passive magnet 42 .
  • the first proximal protection part 451 , the first distal protection part 452 , the first peripheral surface protection part 453 and the connecting shaft 44 jointly define the first receiving cavity.
  • the first proximal protection member 451 is in the shape of a thin plate or sheet, and fits on the proximal end surface of the passive magnet 41 , and is connected to the proximal end of the connecting shaft 44 , and the connection is preferably a fixed connection.
  • the first proximal protection member 451 is integrated with the connecting shaft 44 . That is, the first proximal protection member 451 is formed by extending radially outward from the proximal end of the connecting shaft 44 .
  • the first proximal protection member 451 of this structure can fix and limit the passive magnet 42 .
  • the two magnets have a tendency to move towards each other under the action of magnetic force. Therefore, adopt the mode that the first proximal protection part 451 is fixedly connected with the proximal end of the connecting shaft 44, the first proximal protection part 451 acts as a stopper for the passive magnet 42 or restricts its movement toward the proximal end, and maintains the passive magnet 42. The position is fixed.
  • the first distal protection member 452 is in the shape of a circular thin plate or sheet, and is sleeved on the outside of the connecting shaft 44 . In this way, the proximal and distal protection pieces 451 , 452 can clamp the passive magnet 42 in the axial direction, keeping the position of the passive magnet 42 fixed.
  • a step is formed at the distal end of the mounting portion 441 .
  • the first distal protection member 452 can lean against the step, and the step can form a limit on the first distal protection member 452 to ensure that its axial position is fixed.
  • the shape of the first peripheral surface protector 453 is adapted to the trend of the outer peripheral surface of the passive magnet 42, such as a hollow cylinder, a conical thin plate or a sheet, and is attached to the outer peripheral surface of the passive magnet 42.
  • the front and rear ends are respectively connected to the near and far ends.
  • the protection pieces 451, 452 are connected.
  • the first protective layer configured as a waterproof coating or the first protective layer configured as the first storage cavity
  • the first protective layer is non-magnetic and configured to rotate with the passive magnet 42 . That is, the first protective layer and the passive magnet 42 are fixedly arranged, and the two remain relatively stationary.
  • the non-magnetic first protective layer can prevent the passive magnet 42 from magnetically absorbing some impurities and affect the normal operation of the passive magnet 42; in addition, it can also constrain the orientation of the magnetic force of the passive magnet 42 to avoid the undesired diffusion of the magnetic force of the passive magnet 42 Furthermore, on the one hand, the magnetic coupling force and coupling efficiency are improved, and on the other hand, other parts of the working assembly 30 can be avoided from being magnetized by the passive magnet 42, causing unnecessary troubles. For example, other components of the working assembly 30 are prevented from being magnetized to magnetically attract some impurities to affect the normal operation of the working assembly 30 .
  • Passive magnet protection assembly 46 also includes a second protection layer disposed within intervening end bushing 40 and physically spaced from passive magnet 42 ; the second protection layer is configured not to rotate with passive magnet 42 .
  • the second protection layer is arranged radially on the periphery of the passive magnet 42 and fixed in the inner cavity of the intervening bush 40 , and the second protection layer is arranged at a distance from the passive magnet 42 . Since the passive magnet 42 is rotatable, the second protective layer is fixed. Therefore, during the rotation process of the magnetic passive magnet 42 , the second protective layer moves relative to it due to the fixation. If the second protective layer is made of conductive material, eddy current may be generated in the second protective layer.
  • the non-conductive configuration of the second protective layer can avoid the generation of eddy current in the second protective layer, ensure that the equipment shell is not charged, and avoid the risk of electric shock.
  • the second protective layer is further configured with non-magnetic conduction, which can restrict the direction of the magnetic force. For details, please refer to the above description, and will not repeat them here.
  • a first magnetic force constraining member is provided inside the inserting end bush 40 .
  • the first magnetic constraining member is roughly disc-shaped, installed on the connecting shaft 44 , and located at the distal end of the passive magnet 42 .
  • the first magnetic constraining component is disposed at the distal end of the connecting shaft 44, and the passive magnet 42 is fixed on the proximal end surface of the first magnetic constraining component.
  • the first magnetic constraint is magnetically permeable. The first magnetic constraint can constrain the magnetic field lines of the passive magnet 42 on the proximal surface of the first magnetic constraint, preventing the magnetic force of the passive magnet 42 from spreading forward, that is, away from the active magnet 22 .
  • the active magnet 22 is also provided with an active magnet protection assembly 24, which can protect the active magnet 22 from mechanical or chemical damage on the one hand, and on the other hand, can provide orientation to the magnetic force of the active magnet 22, and constrain it.
  • the range of the magnetic field avoids the undesired diffusion of the magnetic force, so that the active magnet 22 can work reliably.
  • the active magnet protection assembly 24 includes a third protection layer at least partially covering the outer surface of the active magnet 22 .
  • the third protective layer can be a mechanical structure that wraps or wraps the active magnet 22 to form a second storage cavity for storing the active magnet 22 therein.
  • the second storage cavity can reliably protect the active magnet 22 .
  • the active magnet 22 is disposed at the distal end of the motor shaft 16 .
  • a magnet fixing block 26 is formed or installed on the motor shaft 16 , and the active magnet 22 is sheathed outside the magnet fixing block 26 .
  • the third protective layer includes the second distal protection member 251 covering the distal end face of the active magnet 22, the second proximal protection member 252 sleeved outside the magnet fixing block 26 and covering the proximal end face of the active magnet 22, and connected to the second proximal end face of the active magnet 22.
  • the second peripheral protection part 253 is between the two distal protection parts 251 and the second proximal protection part 252 and covers the peripheral surface of the active magnet 22 .
  • the second distal protection part 251 , the second proximal protection part 252 , the second peripheral surface protection part 253 and the magnet fixing block 26 jointly define the second storage cavity.
  • the second distal protection member 251 is in the shape of a thin plate or sheet, and fits on the distal end surface of the active magnet 22, and is connected to the distal end of the magnet fixing block 26, and the connection is preferably a fixed connection.
  • the second distal end protection member 251 and the magnet fixing block 26 are integrally constructed. That is, the second distal end protection member 251 is formed by extending radially outward from the distal end of the magnet fixing block 26 .
  • the second distal protection member 251 of this structure can fix and limit the active magnet 22 .
  • two magnets have a tendency to move towards each other under the action of magnetic force. Therefore, the second distal protection member 251 is fixedly connected to the distal end of the connecting shaft 44, the second distal protection member 251 stops the active magnet 22 or restricts its tendency to move distally, and maintains the active magnet 22. The position is fixed.
  • the second proximal protection member 252 is in the shape of a circular thin plate or sheet, and is sheathed outside the magnet fixing block 26 . In this way, the distal and proximal protectors 251 and 252 can respectively clamp the active magnet 22 in the axial direction, keeping the position of the active magnet 22 fixed.
  • the shape of the second peripheral surface protector 253 is adapted to the trend of the outer peripheral surface of the active magnet 22, for example, it is in the shape of a hollow cylinder, a conical thin plate or a sheet, and is attached to the outer peripheral surface of the active magnet 22.
  • the front and rear ends are respectively connected to the far and near ends.
  • the protection pieces 251, 252 are connected.
  • the third protection layer is non-magnetic and configured to rotate with the active magnet 22 . That is, the third protection layer and the active magnet 22 are fixedly arranged, and the two keep relatively stationary.
  • the non-magnetic third protective layer can prevent the active magnet 22 from magnetically absorbing some impurities and affect the normal operation of the active magnet 22; in addition, it can also constrain the orientation of the magnetic force of the active magnet 22 to avoid undesired diffusion of the magnetic force of the active magnet 22 Furthermore, on the one hand, the magnetic coupling force and coupling efficiency are improved, and on the other hand, it is possible to prevent the active magnet 22 from magnetizing other components of the drive assembly 10, causing unnecessary troubles. For example, other components of the drive assembly 10 are prevented from being magnetized and some impurities are magnetically attracted to affect the normal operation of the drive assembly 10 .
  • the active magnet protection assembly 24 also includes a fourth protective layer disposed within the motor end bushing 20 and physically spaced from the active magnet 22 ; the fourth protective layer is configured not to rotate with the active magnet 22 .
  • the fourth protective layer is arranged radially on the periphery of the active magnet 22 and fixed in the inner cavity of the intervening bush 40 , and the fourth protective layer is arranged at a distance from the active magnet 22 . Since the active magnet 22 is rotatable, the fourth protective layer is fixed. Therefore, during the rotation of the magnetically charged active magnet 22 , the fourth protection layer moves relative to it due to the fixation. If the fourth protection layer is made of conductive material, eddy current may be generated in the fourth protection layer.
  • the non-conductive configuration of the fourth protective layer can avoid the generation of eddy current in the fourth protective layer, ensure that the equipment shell is not charged, and avoid the risk of electric shock.
  • the fourth protective layer is further configured with non-magnetic conduction, which can restrict the direction of the magnetic force. For details, please refer to the above description, and will not repeat them here.
  • a second magnetic force constraining member is provided inside the motor end bushing 20 .
  • the second magnetic constraining member is generally disc-shaped, installed on the motor shaft 16 or the magnet fixing member 26 , and located at the proximal end of the active magnet 22 .
  • the second magnetic constraining component is disposed at the proximal end of the motor shaft 16 or the magnet fixing component 26 , and the active magnet 22 is fixed at the distal end surface of the second magnetic constraining component.
  • the second magnetic constraint is magnetically permeable.
  • the second magnetic restraint can constrain the magnetic field lines of the active magnet 22 on the distal end surface of the second magnetic restraint, preventing the magnetic force of the active magnet 22 from spreading backward, that is, away from the active magnet 22 .
  • the front end of the active magnet 22 is exposed.
  • the second distal end protection member 251 can be eliminated, and the distal end of the motor end bushing 20 faces the part of the outer surface of the active magnet 22 in the radial direction to limit the position; or the active magnet 22 is directly fixed to the magnet holder 26 or The pair of motor shafts 16 prevents the active magnet 22 from moving axially upwards.
  • the active magnet 22 is located on the drive assembly 10, and the drive assembly 10 is located outside the subject's body when the device 100 is working, the front end of the active magnet 22 is exposed without additional components, which can make the structure of the drive assembly 10 more compact; and The distance between the active magnet 22 and the passive magnet 42 can be made closer to improve transmission efficiency.
  • the driving assembly 10 is detachably connected to the working assembly 30 .
  • the bushing 20 at the motor end is detachably connected to the bushing 40 at the intervention end, so as to realize the detachable connection between the driving assembly 10 and the working assembly 30 .
  • the motor end bushing 20 is mated with the intervening end bushing 40, one of the two is configured as a plug, and the other of the two includes a A socket configured to receive a plug; a bushing configured as a plug is defined as an inserting bushing, and a bushing defining a slot is defined as a receiving bushing; the device 100 also includes a lock for engaging and securing the inserting bush and the receiving bushing mechanism.
  • the locking mechanism includes an engaging portion formed in one of the outer wall of the inserting bush and the inner wall of the receiving bushing, and a locking member operatively embedded in the engaging portion.
  • the locking part is embedded in the joint part to realize locking, and the inserting bush and the receiving bush are relatively fixed; the locking part is disengaged from the joint part, and the inserting bush and the receiving bush can be disengaged.
  • FIG. 6 shows the first locking mechanism provided by the specific embodiment of the present invention.
  • the engaging portion is a lock groove 48 formed inwardly recessed from the outer surface of the inserting bush, and the side wall of the receiving bush is provided with an opening, and the locking member is configured as a radially movable pin 50; the pin 50 is operable to be inserted through the opening Or move out of the lock groove 48, thereby realizing locking or unlocking.
  • the pin 50 is arranged in the supporting sleeve 52, and the supporting sleeve 52 is sleeved outside the receiving bush and fixedly arranged relative to the receiving bush.
  • the support sleeve 52 is provided with a radially extending guide groove 54
  • the guide groove 54 is formed by indenting outward from the inner wall of the support sleeve 52 , and the pin 50 slides in the guide groove 54 to realize locking or unlocking.
  • the pin 50 has a locked state in which it is inserted into the lock slot 48 to securely engage the motor end bush 20 with the access end bush 40 , and an unlocked state in which it is removed from the lock slot 48 to release the fixed engagement of the motor end bush 20 with the access end bush 40
  • the first elastic member 56 is biased between the pin 50 and the support sleeve 52, and the reset force exerted by the first elastic member 56 on the pin 50 makes the pin 50 have a tendency to maintain the locked state or move toward the locked state.
  • a compressed first elastic member 56 is provided between the side of the pin 50 away from the lock groove 48 and the closed end of the guide groove 54, and the first elastic member 56 exerts a radially inward force on the pin 50,
  • the pin 50 has a tendency to maintain the locked state or move towards the locked state.
  • the side of the pin 50 facing away from the locking groove 48 is provided with an elastic member receiving groove 58 recessed inward, and the first elastic member 56 is partially accommodated in the elastic member receiving groove 58 .
  • the first elastic member 56 can return to deformation more stably, so that the pin 50 has a tendency to maintain the locked state or move toward the locked state.
  • the pin 50 includes a connected outer section 60 and an inner section 62, the width (diameter) of the outer section 60 is greater than the width of the inner section 62, and the elastic member receiving groove 58 is arranged on the outer section 60 with a larger width.
  • the elastic member receiving groove 58 is formed inwardly from the end surface of the outer section 60 facing away from the locking groove 48 .
  • the locking mechanism further includes an unlocking actuator rotatably arranged outside the receiving bush, and the unlocking actuator includes an annular main body portion 64, which is rotatably sleeved on the receiving bush.
  • the unlocking actuator includes a profiling part 66 cooperating with the pin 50 , the profiling part 66 is connected with the annular main body part 64 , and the profiling part 66 protrudes radially outward from the annular main part 64 .
  • the profiling part 66 is configured to exert a force on the pin 50 opposite to the reset direction of the first elastic member 56 when the annular body portion 64 of the unlocking actuator rotates along the first direction, Rotation in a second, opposite direction removes the force on pin 50 .
  • the pin 50 includes an inner section 62 and an outer section 60 having unequal widths, and on the outer surface of the pin 50 , the junction of the inner section 62 and the outer section 60 forms a corner.
  • the annular body portion 64 of the unlocking actuator is rotated in a first direction (clockwise as shown in FIG. 6 )
  • the contoured member 66 abuts against the corner, exerting a radially outward force on the pin 50, By urging the pin 50 out of the lock slot 48, the insert and receiver bushings can be disengaged.
  • the annular body portion 64 of the unlocking actuator rotates in the second direction (counterclockwise as shown in FIG. 6 )
  • the profiling part 66 is away from the pin 50, and the pin 50 is inserted into the locking groove under the action of the first elastic member 56. 48.
  • the inserting bush and the receiving bush are relatively fixed.
  • the pin 50 is in the unlocked state when the unlocking actuator rotates to the first dead point along the first direction, and the pin 50 is in the locked state when the unlocking actuator rotates to the second dead point along the second direction. That is to say, during the rotation of the unlocking actuator in the first direction, the pin 50 moves radially outward and gradually unlocks. When the unlocking actuator rotates to the first dead point along the first direction, the pin 50 is completely disengaged from the locking groove 48, and the unlocking is successful.
  • the pin 50 moves radially inward under the action of the first elastic member 56 and gradually locks.
  • the profiling part 66 completely moves the overhead 50, and the pin 50 is inserted into the locking groove 48 to a certain depth to realize locking.
  • a second elastic member 70 is provided between the unlocking actuator and the support sleeve 52, and the reset force exerted by the second elastic member 70 on the unlocking actuator makes it maintain the position at the second dead point or move toward the second dead point. trend.
  • the reset force exerted by the first elastic member 56 on the pin 50 makes the pin 50 have a tendency to maintain the locked state or move toward the locked state, while the reset force exerted by the second elastic member 70 on the unlocking actuator makes it maintain the locking state.
  • the profiling component 66 lets the state of the overhead 50 or tends to move toward the state of the overhead 50 .
  • the first elastic member 56 and the second elastic member 70 have a synergistic effect. Only when the effects of the second elastic member 70 and the first elastic member 56 are overcome can the inserting bush be separated from the receiving bushing, and the pin 50 can be kept. The reliable locking of the inserting bush and the receiving bush prevents accidents during the working process of the device 100 .
  • the support sleeve 52 is provided with a track opening 72 that is generally arc-shaped along the circumference.
  • the unlocking actuator includes a locking protrusion 74 extending into the track opening 72.
  • the locking protrusion 74 is connected with the ring-shaped main body 64 and along the Radially protrudes from the annular body portion 64 .
  • the locking protrusion 74 has a first stop surface 76 pointing to the first direction and a second stop surface 78 pointing to the second direction, and the second elastic member 70 is arranged on the first stop surface 76 and the track opening 72 along the first between the inner walls of the direction.
  • the second elastic member 70 is compressed so that the locking projection 74 has a state of keeping the second stop surface 78 abutting against the inner wall of the track opening 72 along the second direction, or has a tendency to move toward the second direction and abut against the inner wall, thereby
  • the contoured part 66 of the unlocking actuator allows the overhead 50 to maintain the locked state.
  • the unlocked state of the unlocking actuator corresponds to the state in which the locking protrusion 74 pushes the second elastic member 70 to be further compressed, so that the first stop surface 76 rotates in the inner wall direction toward the first direction in the track opening 72 .
  • the profiling component 66 in the locked state, under the action of the second elastic member 70 , the profiling component 66 is away from the pin 50 , and the profiling component 66 cannot push the pin 50 .
  • the pin 50 maintains the state of being inserted into the lock slot 48 under the action of the first elastic member 56 .
  • overcome the active force of the second elastic member 70 overcome the active force of the second elastic member 70, and rotate the locking projection 74 along the first direction to drive the ring-shaped main body 64 to rotate.
  • the pushing pin 50 moves radially outward against the force of the first elastic member 56 to unlock the inserting bush and the receiving bush.
  • the unlocking actuator is connected with an operating member 80 located outside the support sleeve 52, and the operating member 80 is configured to receive an external force to drive the unlocking actuator to rotate in a first direction.
  • the operating part 80 is fixedly connected with the locking protrusion 74, and the operating part 80 drives the locking protrusion 74 to rotate, and then drives the ring-shaped main part 64 and the profiling part 66 to rotate to realize unlocking.
  • the operating member 80 includes an annular portion 82 sleeved on the support sleeve 52 .
  • a part of the inner wall of the annular portion 82 is connected to the locking protrusion 74 ; another part of the inner wall of the annular portion 82 at least covers the part where the second elastic member 70 is installed in the track opening 72 of the supporting sleeve 52 . That is to say, the annular portion 82 , the locking protrusion 74 , and the supporting sleeve 52 are arranged to form a relatively closed space for accommodating the second elastic member 70 , which can ensure the reliable operation of the second elastic member 70 .
  • the profiling part 66 extends radially outward relative to the annular body part 64 , to allow space for the movement of the profiling part 66 , the inner wall of the support sleeve 52 is recessed outwardly to form a clearance groove 84 .
  • the circumferential extension length of the slot 84 be approximately equal to the length of the circumferential movement track of the unlocking actuator from locking to unlocking.
  • the number of pins 50 is two, and the number of locking grooves 48 is also two.
  • the pins 50 and the locking grooves 48 correspond one-to-one, that is, one pin 50 corresponds to one locking groove 48, and the two pins 50 are in a circumferential direction. Set at intervals of 180 degrees, the insertion bush and the receiving bush can be locked relatively evenly.
  • the number of first elastic members 56 and the number of profiling parts 66 are also two, corresponding to the pins 50 one by one.
  • the number of pins 50 is two, the number of the locking projection 74 and the operating member 80 is only one, that is, one operating member 80 and one locking projection 74 can operate two pins 50 at the same time, not only locking is reliable, but also Easy to operate.
  • the number of the pin 50, the lock groove 48, the first elastic member 56, and the profiling member 66 can be more than two, and will not be repeated here.
  • the first direction is referred to as a clockwise direction
  • the second direction is referred to as a counterclockwise direction. But this is only for convenience of description, and does not constitute a limitation to the present invention.
  • the reset force of the first elastic member 56 pushes the pin 50 to move radially inwards and inserts into the lock groove 48
  • the reset force of the second elastic member 70 pushes the locking protrusion 74 to rotate counterclockwise until the second stop
  • the blocking surface 78 abuts against the counterclockwise inner wall of the track opening 72 .
  • the locking protrusion 74 rotates counterclockwise to drive the ring-shaped main part 64 and the profiling part 66 away from the pin 50 , and the pin 50 is inserted into the locking groove 48 under the action of the first elastic member 56 and remains locked.
  • first elastic member 56 and the second elastic member 70 are compressed to store energy and have a tendency to reset. Therefore, the restoring action of the first elastic member 56 and the second elastic member 70 can be performed simultaneously.
  • the operator pushes the operating member 80 to rotate clockwise, and the clockwise rotation of the operating member 80 drives the locking protrusion 74 to overcome the force of the second elastic member 70 to rotate clockwise, and the locking protrusion 74 rotates clockwise Drive the ring-shaped main part 64 and the profiling part 66 to rotate clockwise.
  • the profiling component 66 rotates clockwise to abut against the corner of the pin 50 , the profiling component 66 pushes the pin 50 to move radially outward against the force of the first elastic member 56 , thereby realizing unlocking.
  • the intervening end bushing 40 is configured to insert the bushing
  • the motor end bushing 20 is configured to receive the bushing
  • the front end of the motor housing 12 is configured to support Sleeve 52.
  • the configuration of the inserting bush and the receiving bush can be substantially opposite to the above example. That is, the insertion end bush 40 is configured to receive the bush, the motor end bush 20 is configured to be inserted into the bush, and the support sleeve 52 is an additional component that complies with the description of the above embodiments.
  • the device 100 of the present invention needs to be sufficiently compact in structure, and the size of each component needs to be sufficiently precise and small enough. Insertion fit between the insert bush and the receiving bush, because the size of the insert bush and the receiving bush is sufficiently precise, when the two are plugged and fitted, the space between the insert bush and the receiving bush is small, and the assembly resistance is relatively small Large, the assembly operation is not easy.
  • a drag reducing structure is provided between the inserting bush and the receiving bush.
  • the drag reducing structure is configured to reduce the insertion resistance to the inserting bush formed by compressed gas during the insertion of the inserting bush into the receiving bush.
  • a gap is formed between the support sleeve 52 and the receiving bush;
  • the drag reducing structure includes a pressure relief hole 86 penetrating through the side wall of the receiving bush. It communicates with the external space through the gap between the support sleeve 52 and the receiving bush. Therefore, when the inserting bush is inserted into the receiving bush, the gas between the inserting bush and the receiving bush can be discharged to the external space through the pressure relief hole 86, reducing or even avoiding the resistance of the compressed gas to the inserting bush.
  • the drag reducing structure includes a pressure relief groove formed on the inner wall of the receiving bush and/or the outer wall of the insertion bush, and the pressure relief groove communicates with the external space.
  • the pressure relief groove can store a part of air to reduce the resistance of the air; on the other hand, the pressure relief groove communicates with the external space, and the air can be discharged to the external space through the pressure relief groove, reducing or even avoiding the compression of the gas on the insert bushing formed resistance.
  • the pressure relief groove extends along the insertion direction of the insert bush, and the extension may be a straight line or a curved line, such as a helical extension.
  • the distal end of the pressure relief groove is connected to the proximal end of the inner wall of the receiving bushing and/or the distal end of the outer wall of the inserting bushing to realize communication with the external space.
  • the pressure relief groove is only formed on the inner wall of the receiving bush.
  • the pressure relief groove and the outer wall of the inserting liner define a passage leading to the external space to realize pressure relief.
  • the pressure relief groove can also be formed only on the outer wall of the insert bush.
  • the pressure relief grooves are simultaneously formed on the inner wall of the receiving bush and the outer wall of the inserting bush.
  • the drag reducing structure includes a space formed between the insert bush and the receive bush when the insert bush and the receive bush are in an engaged state. This space is used to temporarily store the compressed air during the insertion of the inserting bush into the receiving bushing to indirectly achieve the purpose of pressure relief, thereby reducing the resistance of the compressed gas to the inserting bush.
  • the space includes a groove formed in the insertion bush that is open toward the end.
  • the groove makes there is a space between the inserting bush and the receiving bush, and at the same time, the gap between the outer wall of the inserting bush and the inner wall of the receiving bush can still be small enough, and the small enough gap not only makes the structure compact, but also makes the inserting bush and the receiving bush
  • the receiving bush can be slidably fitted but not relatively shaken, which ensures the normal operation of the device 100 .
  • the transmission link of the working assembly 30 includes a passive magnet 42, a connecting shaft 44 on which the passive magnet 42 is installed, a drive shaft 34 connected to the far end of the connecting shaft 44, and a pump 36 connected to the far end of the drive shaft 34 .
  • the motor shaft 16 drives the active magnet 22 to rotate
  • the passive magnet 42 is magnetically coupled with the active magnet 22
  • the passive magnet 42 is driven to rotate by the active magnet 22
  • the passive magnet 42 rotates to drive the connecting shaft 44 and the drive shaft 34 to rotate in turn.
  • the drive shaft 34 rotates to drive the pump 36 to pump blood.
  • the inserting end bush 40 is provided with a first axial channel 101 , and the connecting shaft 44 is rotatably provided in the first axial channel 101 .
  • At least one bearing 90 is arranged on the outside of the connecting shaft 44 , and a damping member 92 is arranged between the outer ring of the bearing 90 and the inner wall of the first axial passage 101 .
  • the damping member 92 can not only reduce vibration, but also provide a certain movement buffer space, so that the passive magnet 42 and the active magnet 22 can be aligned as much as possible, and the transmission efficiency can be improved.
  • the flexible damping member 92 By setting the damping member 92 between the bearing 90 and the first axial channel 101, and configuring the damping member 92 to be flexible, the flexible damping member 92 can be squeezed and deformed by the connecting shaft 44, thereby reducing the vibration of the passive magnet 42. Provide radial deformation space. The extruded deformation of the damping member 92 will store energy at the same time, thereby providing a restoring effect on the connecting shaft 44 to make it axially centered, so that the alignment of the two magnets can be restored.
  • the damping element 92 is substantially circular and sleeved on the outer peripheral surface of the bearing 90 . It should be noted that the damping element 92 may be continuous in the circumferential direction, or discontinuous in the circumferential direction, that is, it may comprise a plurality of arc-shaped damping elements. Due to the ring-shaped structural design of the damping member 92 , the damping member 92 can reset the vibration of the passive magnet 42 along a 360° circumferential direction.
  • the forward portion of the pump and catheter is advanced by the subject's vasculature. While it is known that the vasculature is tortuous, in particular there are bends where the angle may be less than 30°.
  • the driving shaft 34 Since the driving shaft 34 is passed through the catheter 32, the catheter 32 and the driving shaft 34 will bend to conform to the vasculature when being transported in such a tortuous vasculature. However, since the softness of the driving shaft 34 and the catheter 32 are different, and the driving shaft 34 is located inside the catheter 32 . Therefore, the drive shaft 34 will move axially in the conduit 32 during the delivery curve.
  • the driving shaft 34 and the connecting shaft 44 are slidably fitted in the axial direction. Further, since the connecting shaft 44 needs to transmit the rotation to the driving shaft 34 , the driving shaft 34 and the connecting shaft 44 are circumferentially fixed.
  • the proximal end of the drive shaft 34 is provided with or formed with a connecting portion 94, and the cross section of the connecting portion 94 is in any shape other than a circle;
  • the distal end of the connecting shaft 44 is formed with a matching channel adapted to the connecting portion 94 , the connecting portion 94 is slidably inserted into the mating channel in the axial direction.
  • the cross-section of the connecting portion 94 is any shape other than a circle, such as a square or an ellipse, configured as a flat shaft, which can prevent rotation in the circumferential direction, and ensure that the drive shaft 34 and the connecting shaft 44 are fixed in the circumferential direction, so that the drive shaft 34 and the connecting shaft 44 are fixed in the circumferential direction.
  • the shaft 34 rotates synchronously with the connecting shaft 44 .
  • the connecting portion 94 can be integrally constructed with the drive shaft 34 and can be configured as a part of the structure of the drive shaft 34 , specifically, the rear end of the drive shaft 34 can be obtained by a non-circular process.
  • the connecting portion 94 may be a component additionally provided at the rear end of the drive shaft 34 and have a cross-sectional shape conforming to the above description.
  • the pump 36 defines the distal position in the axial direction, that is to say, the mating channel and the pump 36 respectively define the proximal position and the distal position of the drive shaft 34 in the axial direction, so the drive shaft 34 will not be connected to the connecting shaft 44 slip fit and come off.
  • the working assembly 30 includes a conduit 32 , a drive shaft 34 passing through the conduit 32 , and a pump 36 driven by the drive shaft 34 .
  • the drive shaft 34 is penetrated in the catheter 32, and the catheter 32 prevents the drive shaft 34 from contacting with the outside world. On the one hand, it ensures the normal operation of the drive shaft 34. On the other hand, it prevents the drive shaft 34 from directly contacting the subject during the working process. cause harm.
  • the pump 36 which can be delivered to the desired location of the heart through the conduit 32 to pump blood, includes a pump casing 363 connected to the distal end of the conduit 32 and having an inlet end 361 and an outlet end 362, an impeller (not shown) housed in the pump casing ), the impeller is rotated by the drive shaft 34 to draw blood into the pump housing 363 from the inlet port 361 and discharge it from the outlet port 362 .
  • the pump casing 363 includes a metal lattice bracket 3631 made of nickel or titanium alloy and an elastic film 3632 covering the bracket 3631 .
  • the metal lattice of the bracket 3631 has a mesh design
  • the coating 3632 covers the part of the bracket 3631
  • the mesh of the front end of the bracket 3631 not covered by the coating 3632 forms the inlet end 361 .
  • the rear end of the membrane 3632 covers the outside of the distal end of the catheter 32
  • the outlet end 362 is an opening formed at the rear end of the membrane 3632 .
  • the impeller includes a hub connected to the distal end of the drive shaft 34 and blades supported on the outer wall of the hub.
  • the blades may be in a helical shape, and the number of the blades may be one, or multiple such as two.
  • the distal end of the drive shaft 34 is connected to the hub, and a proximal bearing chamber (not shown) is connected between the distal end of the catheter 32 and the proximal end of the bracket 3631 . That is, the bracket 3631 is connected with the catheter 32 through the proximal bearing chamber.
  • the drive shaft 34 passes through the proximal bearing located in the proximal bearing chamber.
  • a distal bearing chamber 37 is provided between the distal end of the bracket 3631 and the protection head 38 . That is, the protective head 38 is connected with the bracket 3631 through the distal bearing chamber.
  • the distal end of the hub 12 is inserted into a distal bearing located in the distal bearing chamber 37 .
  • the limit of the impeller 9 is formed by the proximal and distal bearings, so that the impeller can be preferably held in the pump casing 363, and the pump gap between the impeller and the pump casing 363 is stably maintained.
  • the pump 36 is a collapsible pump with a compressed state and an expanded state.
  • the pump housing 363 and the impeller are configured to: be in a compressed state in the corresponding interventional configuration of the pump 36, so that the pump 36 delivers in the subject's vasculature with a smaller first outer diameter dimension, and, when the pump 36 36 is in a deployed state corresponding to the operative configuration such that pump 36 pumps blood at a desired location with a second radial dimension that is greater than the first radial dimension.
  • the size and hydrodynamic performance of the pump 363 are two conflicting parameters. In short, it is desirable that the size of the pump 363 be small from the standpoint of relieving the subject's pain and ease of intervention. In order to provide a strong auxiliary function for the subject, it is desirable that the flow rate of the pump 363 be large, which generally requires a large size of the pump 363 .
  • the pump 363 has a smaller collapsed size and a larger expanded size, so as to reduce the pain of the subject during the intervention/transportation process, facilitate the intervention, and provide a large flow rate demand.
  • the multi-mesh design of the pump casing 3631 can achieve better folding, and at the same time, it can be unfolded by virtue of the memory characteristics of nickel-titanium alloy.
  • the impeller includes a hub connected to the distal end of the drive shaft 34 and blades supported on the outer wall of the hub, the blades are configured to wrap around the outer wall of the hub and at least partially contact the inner wall of the pump housing when the pump 36 is in a corresponding intervention configuration, and
  • the pump 36 extends radially outward from the hub and is spaced from the inner wall of the pump 36 in the corresponding operative configuration.
  • the blades are made of soft and elastic materials, which store energy when they are folded, and release the energy storage of the blades to unfold them after the external constraints are removed.
  • the pump 36 is folded by means of external constraints, and after the constraints are removed, the pump 36 realizes self-deployment.
  • the "compressed state” refers to the state in which the pump 36 is radially constrained, that is, the state in which the pump 36 is radially compressed and folded into a minimum radial dimension under external pressure.
  • the “deployed state” refers to the state in which the pump 36 is not radially constrained, that is, the state in which the bracket 3631 and the radially outer side of the impeller are deployed to the maximum radial size.
  • the aforementioned external constraints are applied by sliding a folded sheath (not shown) over the catheter 32 .
  • the pump 36 can be accommodated in it as a whole, so that the pump 36 can be forcibly folded.
  • the radial constraint on the pump 36 is lost and the pump 36 self-deploys.
  • the retraction of the pump 36 is realized by means of the radial restraint force exerted by the folded sheath.
  • the impeller contained in the pump 36 is accommodated in the pump casing 363. Therefore, in essence, the folding process of the pump 36 is: the folded sheath exerts a radial constraint force on the pump casing 363, and when the pump casing 363 radially compresses, it exerts a force on the impeller. radial restraint.
  • the pump casing 363 is folded directly under the action of the folding sheath, while the impeller is directly folded under the action of the pump casing 363 .
  • the impeller has elasticity. Therefore, although the impeller is in the collapsed state, the energy storage of the impeller always has a tendency to expand radially, and then the impeller will contact the inner wall of the pump casing 363 and exert a reaction force on the pump casing 363 .
  • the pump housing 363 supports the expansion of the elastic membrane under the action of its own memory characteristic, and the impeller self-expands under the action of the released energy storage.
  • the outer diameter of the impeller is smaller than the inner diameter of the pump housing 363 .
  • the pump clearance size be kept at a small value.
  • the outer diameter of the impeller is slightly smaller than the inner diameter of the bracket 3631, so that the pump clearance is as small as possible under the condition that the impeller rotates without bumping against the wall.
  • the main means of maintaining the pump clearance is the supporting strength provided by the bracket 3631, which can resist the back pressure of the fluid (blood) without deformation, thereby keeping the shape of the pump casing 363 stable, and the pump clearance is also maintained. Hold steady.
  • the pump 36 is radially constrained (compressed) due to an externally applied radial constraining force.
  • the stent 3631 uses its own memory characteristics and the blades of the impeller expand autonomously with the release of energy storage, so the pump 36 automatically assumes its unconstrained shape (deployed state).
  • the device 100 completes its work and needs to be withdrawn from the subject, use the foldable sheath to fold the pump 36. After the pump 36 is completely withdrawn from the subject, remove the restraint of the foldable sheath on the pump 36 to make the pump 36 returns to the natural state with the least stress, that is, the unfolded state.
  • the device 100 also includes a perfusion channel that basically runs through the entire working assembly 30 . Specifically, the perfusion channel runs through the transmission link from the passive magnet 42 to the pump 36 .
  • fluid can be injected into the perfusion channel, and the fluid is the Purge liquid described above, which can lubricate and cool down the transmission link.
  • the proximal inlet 96 of the perfusion channel is a cavity provided at the proximal end of the intervention-end bushing 40 and containing the passive magnet 42 therein.
  • the cavity not only accommodates the passive magnet 42, but also accommodates the passive magnet protection component 46 therein.
  • the passive magnet 42 is the starting point of the transmission chain in the working assembly 30, and the proximal entrance 96 of the perfusion channel is set as a cavity in which the passive magnet 42 is accommodated, and fluid can be perfused in the cavity, and the fluid lubricates and cools the passive magnet 42 . Therefore, the perfusion channel lubricates and cools the transmission link from the starting point of the transmission link of the working component 30 to ensure the effective work of the working component 30 .
  • the perfusion channel runs from the proximal end of the coupler to the distal end of the pump 36 . It should be particularly noted that this structural design can achieve the beneficial effect of convenient exhaust operation.
  • the specific instructions are as follows:
  • the perfusion fluid interface is located between the two ends of the working component, and is generally located closer to the proximal end of the working component, that is, the proximal end of the coupler.
  • the working assembly is divided into a proximal section and a distal section located on both sides of the perfusion fluid interface. In this way, the exhaust operation needs to be performed on the proximal section and the distal section respectively.
  • the exhaust operation needs to be performed twice. Specifically:
  • a perfusion fluid source is connected to the perfusion fluid interface (set on the coupler shell), and the perfusion fluid source can be a syringe.
  • Perfusate is accommodated in the syringe, and the perfusate is injected into the working component through the perfusate interface by pushing the syringe.
  • the length of the distal section is much longer than that of the proximal section; in addition, the distal section is mainly composed of a catheter 32 , a drive shaft 34 and a pump 36 . Therefore, the flow resistance of the liquid in the distal section is much greater than the flow resistance in the proximal section.
  • the perfusate enters the proximal section first, evacuating the proximal section of air.
  • the fact that the air in the proximal section is evacuated can be verified by the perfusate flowing out from the end surface of the proximal section, that is, the first guide channel of the sealing member 118 described below.
  • the proximal section is sealed, that is, the first guiding channel of the sealing member 118 is sealed (the specific sealing method is described below). Then use the syringe to pour liquid into the working components. Since the proximal section is sealed, perfusate can only flow toward the distal section, evacuating the distal section of air. Wherein, the air in the distal section is evacuated can be verified by perfusate flowing out from the end of the distal section, that is, the front end of the catheter 32 and/or the distal end of the hub of the impeller.
  • the starting point of the perfusion channel in the embodiment of the present invention is the cavity for accommodating the passive magnet 42 , and the cavity is located at the proximal end of the entire working assembly.
  • the perfusate enters from the proximal end of the entire perfusion channel, and the flow path of the perfusate can only go toward the far end of the working component.
  • only one operation is required to realize the emptying of the working components, which greatly simplifies the emptying operation.
  • the access end hub 40 is provided with a perfusion input channel 98 in communication with the lumen, the outer end of the perfusion input channel 98 passes out of the connection assembly and is intended to communicate with a source of perfusate.
  • the outer end passes through the connecting component to facilitate communication with the perfusion fluid source, so as to provide fluid for the perfusion channel.
  • the extension direction of the perfusion input channel 98 is set at an angle to the axial direction, so that the outer end of the perfusion input channel 98 is away from the proximal end of the working component 30, so as to avoid affecting the installation of the working component 30 and the driving component 10, and the perfusion is also more convenient.
  • the design is very reasonable.
  • the connecting shaft 44 is connected to the passive magnet 42 , specifically as mentioned above, the passive magnet 42 is sheathed on the installation part at the proximal end of the connecting shaft 44 .
  • the connecting shaft 44 is installed on the coupler, specifically, the connecting shaft 44 is installed on the inserting end bushing 40, the inserting end bushing 40 is provided with a first axial channel 101, and the connecting shaft 44 is rotatably arranged in the first axial channel 101 middle.
  • the connecting shaft 44 has an axially extending axial hollow cavity, which can also be referred to as a second axial channel 102 .
  • the perfusion channel includes in the coupling part: the second axial channel 102 formed in the connecting shaft 44, the first gap formed between the connecting shaft 44 and the first axial channel 101; the second axial channel 102, the first axial channel 101 A gap communicates with the cavity.
  • the fluid after the fluid is input from the perfusion input channel 98 , it first flows through the cavity for accommodating the passive magnet 42 , and then passes through the bearing and the first gap in sequence.
  • the connecting portion 94 of the drive shaft 34 is plug-fitted with the matching passage of the connecting shaft 44 , the connecting portion 94 is hollow, and the connecting shaft 44 communicates with the inner axial passage of the driving shaft 34 .
  • the mating channel is part of the second axial channel 102 .
  • the matching channel is the distal part of the second axial channel 102, and the matching channel communicates with the proximal part of the second axial channel 102, and the radial width of the two is different to form a step, which is convenient for connection.
  • the portion 94 is used to limit the axial direction of the proximal end.
  • the fluid flows through the matching channel to cool down and lubricate the inside of the far end of the connecting shaft 44 and the connecting portion 94 at the proximal end of the drive shaft 34, and rationally utilize the installation of the connecting shaft 44 and the drive shaft 34.
  • the structure cools and lubricates the two, and ensures the smoothness of the flow channel, and the structural design is very reasonable.
  • the working assembly 30 includes a guide tube 32 , and the drive shaft 34 passes through the guide tube 32 .
  • the perfusion channel also includes a second gap formed between the drive shaft 34 and the shaft lumen of the catheter 32 .
  • the coupler also includes a positioning sleeve 108 connected to the distal end of the intervention end bushing 40; the proximal end of the catheter 32 is accommodated in the positioning sleeve 108, and the proximal end of the drive shaft 34 is exposed
  • the positioning sleeve 108 is connected with the connecting shaft 44 .
  • the positioning sleeve 108 includes a connected proximal part and a distal part, the end of the proximal part is connected to the inserting end bushing 40, and the proximal part is recessed from the proximal end surface along the direction toward the distal end to form an accommodating space 110 , the distal part forms a catheter storage cavity for receiving the catheter 32, the proximal end of the catheter 32 is stored in the catheter storage cavity, and the proximal end of the drive shaft 34 extends out of the catheter storage cavity and passes through the accommodation space 110 to connect with the connecting shaft 44.
  • the radial width of the accommodating space 110 is greater than the width of the catheter receiving cavity. Therefore, a relatively large amount of fluid can be stored in the accommodating space 110, so that the liquid flows out from the first gap and the axial channel connecting the shaft 44, and then enters the fluid after being transferred and buffered in the larger accommodating space 110.
  • the conduit 32 and the second gap prevent the liquid from holding pressure.
  • the accommodating space 110 with larger diameter and larger volume is formed at the proximal part of the positioning sleeve 108 , which facilitates the assembly of the positioning sleeve 108 with the inserting end sleeve 40 and the housing 112 (described below).
  • a radial lug structure 1081 is formed on the proximal end of the positioning sleeve 108
  • a radial stopper 1121 is formed on the proximal inner wall of the housing 112 .
  • the lug structure 1081 of the positioning sleeve 108 is clamped between the distal end of the inserting end bushing 40 and the stopper 1121 , thereby realizing the fixing of the positioning sleeve 108 .
  • the positioning sleeve 108 is centrally arranged in the housing 112 and is used to straighten the axial position of the catheter 32 so that the center of the catheter 32 is aligned with the connecting shaft 44 and prevent the drive shaft 34 protruding from the proximal opening of the catheter 32 from bending.
  • the position of the positioning sleeve 108 is fixed through the cooperation between the lug structure 1081 and the stopper 1121 .
  • the positioning sleeve 108 is located in the center of the housing 112 by the abutting effect of the lug structure 1081 and the inner wall of the housing 112 , and the central passage of the positioning sleeve 108 is aligned with the axial passage of the connecting shaft 44 .
  • the lug structure 1081 is made of soft and elastic material, in the shape of a ring, and its outer diameter is slightly greater than or equal to the inner diameter of the body 112 . In this way, it is ensured that the proximal end of the driving shaft 34 cooperates with the connecting shaft 44 in an incomplete or slightly bent posture.
  • the second gap communicates with the first gap through the positioning sleeve 108 .
  • the second gap communicates with the first gap through the accommodating space 110 of the positioning sleeve 108 .
  • the outlet end (distal end) of the first gap communicates with the accommodating space 110
  • the inlet end (proximal end) of the second gap communicates with the accommodating space 110 . Therefore, after the fluid flows out of the first gap, it flows into the second gap through the accommodating space 110 of the positioning sleeve 108 , thereby cooling and lubricating the outer surface of the drive shaft 34 .
  • the coupler also includes a housing 112 that is connected to the distal end of the inserting end bushing 40 and accommodates the positioning sleeve 108 therein.
  • the housing 112 is configured when the coupler and the socket are in a connected state.
  • the outer surface is even. It not only avoids scratches that may be caused by uneven outer surfaces, but also has a regular and beautiful appearance.
  • the distal opening of the housing 112 is provided with a retaining sleeve 114 for the catheter 32 to pass through.
  • the proximal end of the retaining sleeve 114 is opposite or connected to the distal end of the positioning sleeve 108. or center channel alignment.
  • the distal end of the retaining sleeve 114 extends for a certain length and has a strength greater than that of the catheter 32, which can support and prevent the catheter 32 from bending, and further play a role of fixing, providing a strength support transition for the catheter 32 at the outlet of the housing 112 , to avoid the phenomenon that the lead-out part of the catheter 32 is broken due to strong and/or frequent bending.
  • the drive shaft 34 is axially penetrated, that is, the entire drive shaft 34, including the connecting portion 94 located at the proximal end of the drive shaft 34 and mated with the connecting shaft 44, has an axially extending axial hollow cavity, and the axial hollow The cavity forms a third axial channel 103 which communicates with the second axial channel 102 .
  • the perfusion channel also includes a third axial channel 103 formed in the drive shaft 34 at the portion of the catheter 32 and the drive shaft 34 .
  • the fluid flowing through the second axial channel 102 of the connecting shaft 44 enters the third axial channel 103 of the drive shaft 34 through the hollow connection part 94, and finally flows out into the body of the subject at the distal end of the drive shaft 34, as Subjects were provided with physical support.
  • the drive shaft 34 is constructed as a multi-ply braided structure so that its sidewalls are liquid permeable. That is, the fluid flowing through the second gap and the third axial channel 103 can not only permeate through the side wall of the drive shaft 34 to achieve balance, but also can completely cool down and lubricate the entire drive shaft 34 .
  • the position of the perfusate interface may be located far from the proximal end of the drive shaft . In this case, it is difficult for Purge fluid to enter the drive shaft from the proximal opening thereof.
  • the drive shaft can only be constructed so that the side walls are liquid permeable.
  • the proximal end of the perfusion channel in the embodiment of the present invention is a cavity for accommodating the passive magnet 42 , and the entering Purge liquid will enter the drive shaft 34 through the cavity and the connecting shaft 44 in sequence.
  • the Purge liquid can also enter the interior of the drive shaft 34 .
  • This provides a more flexible selection space for the drive shaft 34 of the present invention, which is of great benefit to the manufacturing process of the drive shaft 34 .
  • the priming channel includes, at the part of the pump 36 , a fourth axial channel formed in the hub and communicating with the third axial channel 103 .
  • the fluid flowing through the third axial channel 103 can flow into the fourth axial channel and flow out through the fourth axial channel.
  • the distal outlet of the perfusion channel includes the distal opening of the catheter 32, further including the distal opening of the hub. That is, the fluid flowing through the second gap flows out through the distal opening of the conduit 32; the fluid flowing through the fourth axial channel flows out through the distal opening of the hub.
  • the perfusion channel of the working component 30 runs through the transmission link from the passive magnet 42 to the pump 36 , and the perfusion channel first flows through the cavity containing the passive magnet 42 to cool down and lubricate the passive magnet 42 .
  • the perfusion passage is divided into two paths, one path flows through the second axial passage 102 inside the connecting shaft 44, the third axial passage 103 inside the drive shaft 34, the fourth axial passage inside the hub of the pump 36, And flow out from the distal opening of the hub; the other path flows through the first gap between the intervening end bush 40 and the outer wall of the connecting shaft 44, the bearing 92, the accommodating space 110 of the positioning sleeve 108, the gap between the conduit 32 and the outer wall of the drive shaft 34
  • the second gap flows out from the distal opening of the catheter 32 , and the Purge liquid that is shunted in this way can lubricate and cool down various components such as the bearing 92 , the connecting shaft 44 , the driving shaft 34 , and the
  • the entire perfusion channel is designed reasonably, the fluid flow is smooth, and the multi-branch diversion design is adopted, which can increase the perfusion volume of Purge solution.
  • the Purge fluid flows through the relative rotating parts, it can naturally have lubricating and cooling effects, so as to avoid heat accumulation on the rotating parts, especially the driving shaft 34 .
  • the Purge liquid can enter the drive shaft 34 to cool down and lubricate the entire drive shaft 34 comprehensively.
  • the pump 36, catheter 32, and the distal portion of the drive shaft 34 of the device 100 need to be delivered to the subject before the device 100 can function.
  • the part that can be delivered into the body of the subject is called the access component.
  • the device 100 also includes a guide channel through the pump 36, the drive shaft 34 and the coupler.
  • a guiding wire is sent into the body of the subject through the vasculature.
  • the user generally a medical staff
  • the proximal end of the coupler specifically the first guide channel of the seal 118 described below, or the bypass outlet 120 of the intervening end bushing 40 ) passes out.
  • the pump 36 is then delivered in the compressed state to the desired location (eg, the left ventricle) along the guided path established by the guidewire in the subject's vasculature. Until, after the proximal end of the pump 36 is sent to the desired position, the guide wire is pulled out, the constraint on the pump 36 is removed to resume deployment, the working component 30 is connected to the driving component 10, and the motor is activated to start working.
  • the desired location eg, the left ventricle
  • the hub of the pump 36 has a fourth axial passage
  • the drive shaft 34 has a third axial passage 103
  • the connecting shaft 44 has a second axial passage 102
  • the fourth axial passage the third axial passage 103
  • the second axial channels 102 are connected in sequence to form the first guiding channel.
  • the protection head 38 is a hollow structure, which is in butt communication with the fourth axial channel of the hub.
  • the inner channel of the protective head 38 forms part of the first first guide channel.
  • the guide channel also includes an end face outlet 116 located on the proximal end face of the intervening end bushing 40 , and the distal end outlet of the hub communicates with the end face outlet 116 through the first guide channel. That is to say, the working component 30 has a first guiding channel extending axially, and the first guiding channel can guide the guide wire to pass through the end face outlet 116, so as to send the access component into the body of the subject.
  • the end surface outlet 116 formed on the proximal end surface of the interventional end bush 40 constitutes the proximal starting cavity of the perfusion channel. Therefore, the end face outlet 116 needs to be designed to be re-openable or sealed.
  • a seal 118 having a resealable first guide channel is disposed in the end face outlet 116 .
  • the seal 118 has two states - a closed seal state and an open state.
  • the sealing member 118 when the sealing member 118 is in the first state, the first guiding channel is sealed, and the first guiding channel is in a closed sealing state.
  • the sealing member 118 closes the opening on the end face, preventing the fluid in the perfusion channel from flowing out from the end face outlet 116 and preventing the Purge liquid from corroding the motor 14 .
  • the sealing member 118 When the sealing member 118 is in the second state, the first guiding channel is opened, and the first guiding channel is in a communicating state for the guide wire to pass through, so as to send the access assembly into the body of the subject.
  • the sealing member 118 can be opened, so that the guide wire can pass through the first guiding channel, ensuring that the pump 36 enters the body of the subject. After the intervention of the pump 36 is completed, the guide wire is withdrawn to seal the seal 118 to avoid leakage of the Purge fluid during the operation of the pump 36 .
  • the seal 118 is a flexible sealing plug that can move axially in the face outlet 116 .
  • the outer wall of the flexible sealing plug and/or the inner wall of the end face outlet 116 are designed to be inclined, so that the flexible sealing plug is squeezed and switched to the first state when it moves axially toward the first direction, and when it moves in the second direction opposite to the first direction radially expands to switch to the second state.
  • the first direction may be a direction toward the inner side of the inserting end bush 40
  • the second direction may be a direction away from or toward the outer side of the inserting end bushing 40
  • the first direction may be a rightward direction as shown in FIGS. 9 and 10
  • the second direction may be a leftward direction as shown in FIGS. 9 and 10 .
  • the passive magnet 42 accommodated in the cavity is sheathed on the mounting portion 441 with a larger diameter.
  • the proximal end of the mounting portion 441 is recessed inwardly to form an escape groove 4411 for receiving the inner end of the flexible sealing plug.
  • the proximal end of the central channel 102 of the connecting shaft 44 is connected to the escape groove 4411 .
  • the inner end of the flexible sealing plug is generally conical, and the inner wall of the outlet 116 on the end surface is generally configured to match the conical shape. In this way, the tapered flexible sealing plug and the end surface outlet 116 have a flow guiding effect, leading the Purge liquid from the cavity to the central channel 102 smoothly.
  • the sealing member 118 may be a balloon structure similar to a hemostatic valve, which is made of elastic material and has an inner cavity and a channel similar to the above-mentioned first guiding channel.
  • the bladder structure communicates with a fluid source of filling medium or elastic material, and has a bulging state and a collapsed state.
  • the first state is the above-mentioned swollen state, which corresponds to the state when the bladder structure is filled with fluid medium or elastic material, and the channel is occupied by the swollen side wall of the bladder structure to achieve sealing.
  • the second state is the above-mentioned collapsed state, which corresponds to the state after the fluid medium in the capsule structure is at least partially released, and the channel is exposed to realize opening.
  • the guide channel includes a bypass outlet 120 located on the side of the bushing 40 at the intervention end.
  • the proximal end of the working assembly 30 is provided with a passive magnet 42 and a cavity for accommodating the passive magnet 42.
  • the guide wire can pass through the bypass outlet 120 without having to pass through the end face outlet 116.
  • the end surface outlet 116 can be omitted and the seal 118 can be omitted, thereby shortening the distance between the passive magnet 42 and the active magnet 22 and improving transmission efficiency.
  • the inserting end bushing 40 is provided with a first bypass passage 121, and the first bypass passage 121 connects the bypass outlet 120 and the axial passage for receiving the connecting shaft 44 inside the inserting end bushing 40, that is, the first bypass passage. 121 extends from the bypass outlet 120 to the first axial channel 101 that receives the intervening bushing 40 .
  • the side wall of the connecting shaft 44 is provided with a second bypass passage 122, and the second bypass passage 122 communicates with the inner passage of the connecting shaft 44, that is, the second bypass passage 122 extends from the opening of the side wall of the connecting shaft 44 to the connecting shaft 44
  • the second axial channel 102 The second bypass channel 122 is selectively communicated with the first bypass channel 121 .
  • the second bypass channel 122 is disposed on the connecting shaft 44 , and the connecting shaft 44 is rotatable and mated with the bushing 40 at the intervention end. Therefore, the two interfaces where the second bypass channel 122 and the first bypass channel 121 are close to each other have two states of facing and staggering.
  • the guide wire When the two interfaces are facing each other, it is convenient for the guide wire to pass through; when the two interfaces are staggered, the guide wire cannot pass through the bypass outlet 120 .
  • the rotating pump 36 specifically the rotatable impeller, can be manually adjusted to drive the drive shaft 34 and the connecting shaft 44 to rotate in sequence.
  • the guide wire can pass through the second bypass channel 122 , the first bypass channel 121 , and the bypass outlet 120 .
  • the working assembly 30 further includes a guidewire bypass cannula 124 .
  • the guide wire bypass cannula 124 is operable to be inserted through the two bypass channels in sequence, and the inner end of the guide wire bypass cannula 124 is connected to the drive shaft.
  • the second axial channel 102 of 34 is butt connected.
  • the guide wire bypass cannula 124 can make the insertion of the guide wire more convenient.
  • bypass outlet 120 communicates with the first axial passage 101 constituting the perfusion passage through the first bypass passage 121, in order to avoid the Purge liquid flowing through the first axial passage 101 in the perfusion passage from spraying during the operation of the pump 36
  • a sealing plug (not shown) is optionally provided in the bypass outlet 120 to seal the perfusion channel and prevent the purge liquid from being sprayed out through the bypass outlet 120 .
  • the optional setting of the sealing plug is embodied in that when the device 100 is in the state of passing the guide wire when the guide wire needs to pass through the bypass outlet 120, the sealing plug is configured to be removed from the bypass outlet 120, and the removal can be human To be pulled out manually. In this way, the bypass guiding channel of the guide wire is opened, and the bypass passing operation of the guide wire can be performed.
  • the sealing plug is inserted into the bypass outlet 120 when it is in any other working state except the state of passing through the guide wire.
  • the other arbitrary working states mainly include: the state where the pump 36 is turned on after the threading operation of the guide wire is completed (at this time, Purge fluid needs to be pumped into the perfusion channel), the state of threading the guide wire from the end surface, and so on.
  • the working assembly 30 is provided with the end face outlet 116 and also provided with the bypass outlet 120 , and the guide channel is configured to guide the guide wire through one of the end face outlet 116 and the bypass outlet 120 . Passing through the end face outlet 116 provides smoother guidance; while passing through the bypass outlet 120 can avoid the influence of the sealing member 118 on the passive magnet 42 and the perfusion channel.
  • the bypass outlet 120 is in a sealed state.
  • the end surface outlet 116 is in a sealed state.
  • the purpose of this design is mainly to keep the target threading path of the guide wire unobstructed, avoid the guide wire from passing into the non-target guiding path, and ensure the efficient completion of the guide wire threading.
  • the passing path of the guide wire is relatively straight. At this time, it is unnecessary and impossible to insert the guidewire bypass cannula 124 into the first and second bypass channels 121 , 122 .
  • the guide wire bypass cannula 124 is used to force the guide wire to change direction from the original straight direction to the bent direction at the proximal end.
  • the guidewire bypass cannula 124 is inserted, the passage of the guidewire through the end face outlet 116 is blocked to force the guidewire to pass through the bypass.
  • the inner end surface of the guide wire bypass cannula 124 is a wedge-shaped surface, and the angle between the wedge-shaped surface and the axial direction of the guide wire bypass cannula 124 is different from that of the first or second bypass channel.
  • the inclinations of 121 and 122 are the same, for example, both are 45°. In this way, after the guidewire bypass cannula 124 is inserted, its inner end surface is substantially vertical, so as to achieve surface-to-surface fit with the proximal end surface of the drive shaft 32 .
  • the channel through which the guide wire passes through the bypass outlet 120 is called the second guiding channel.
  • the guide wire can alternatively pass through the first guide channel or the second guide channel, so that the guide wire threading operation has more options, and provides users with flexible guide wire configurations.
  • first guiding channel and the second guiding channel have overlapping parts. Specifically, the distal ends of the first guiding channel and the second guiding channel overlap, and the proximal ends are separated, communicating with the end surface outlet 116 and the bypass outlet 120 respectively.
  • the device 100 can also only be provided with the end face outlet 116 or the bypass outlet 120 , which will not be described in detail here, and any solution that is the same as or similar to this embodiment is within the protection scope of the present invention.
  • the driving assembly 10 and the working assembly 30 of the device 100 in this embodiment are detachably connected through a locking mechanism between the insertion bush and the receiving bush.
  • the locking mechanism is operated to separate the driving component 10 from the working component 30;
  • the cooperation of the guide channel sends the access assembly (pump 36 in the collapsed state) into the desired position in the subject; the guide wire is removed, and the first guide channel or the second guide channel (i.e., the end face opening and bypass outlet); pour fluid into the working assembly 30 through the perfusion channel; then, connect the drive assembly 10 with the working assembly 30 through the locking mechanism, remove the radial constraint of the pump on the pump 36, and make it unfold.
  • the driving assembly 10 can drive the pump 36 of the working assembly 30 to be in a working configuration, thereby realizing the blood pumping function of assisting the heart.
  • a second locking mechanism is provided to realize the locking and unlocking between the inserting bush and the receiving bush, specifically:
  • the outer surface of the inserting bushing 199 is recessed to form a lock groove 193L; the inner wall of the receiving bushing 197 is formed with a substantially annular receiving groove 191 , and the locking member is configured as a substantially annular spring ring 195 formed on the inner wall of the receiving bushing 197 , the spring ring 195 is limited in the receiving groove 191 .
  • the depth of the receiving groove 191 is smaller than the diameter of the spring ring 195 .
  • the spring coil 195 is a canted coil spring, and the projection of the spring coil 195 on a radial plane is an ellipse.
  • the depth of the receiving groove 191 is smaller than the major axis width of the spring ring 195 .
  • the spring ring 195 protrudes from the inner surface of the receiving bushing 197, and the spring ring 195 has a recoverable deformation in the radial direction.
  • the spring ring 195 can be snapped into the locking groove 193L and the receiving groove 191 at the same time.
  • the receiving groove 191 realizes locking.
  • Spring coil 195 is configured to sink deeper into receiving groove 191 when inserting bush 199 is engaged with receiving bush 197 than it is when inserting bush 199 is not engaged with receiving bush 197 . That is to say, when the inserting bush 199 engages with the receiving bush 197 , the reaction force of the inserting bush 199 to the spring ring 195 makes the spring ring 195 further sink into the receiving groove 191 . Guarantee the reliability of locking.
  • the recoverable deformation of the spring coil 195 is not more than 20%, further not more than 15%, and further not more than 10%. This makes the locking and unlocking operations more reliable.
  • the inserting bush 199 is also provided with an escape groove 193U spaced apart from the locking groove 193L.
  • the depth of the escape groove 193U is greater than the depth of the lock groove 193L, and the width of the avoidance groove 193U is greater than the width of the lock groove 193L.
  • the escape groove 193U is farther away from the receiving bush 197 relative to the lock groove 193L.
  • the distance between the bottom of the locking groove 193L and the bottom of the receiving groove 191 is smaller than the width of the major axis of the spring ring 195 .
  • the distance between the groove bottom of the escape groove 193U and the groove bottom of the receiving groove 191 is greater than or equal to the major axis width of the spring ring 195 .
  • FIG. 193U An avoidance groove 193U is set on the insert bushing 199, which can make the unlocking operation easier.
  • Figures a to d in Figure 11 show the process from locking to unlocking.
  • the inserting bush 199 is inserted into the receiving bush 197.
  • the spring ring 195 located in the receiving groove 191 is snapped into the locking groove 193L, and the inserting bushing 199 is connected to the receiving groove 191.
  • the receiving bushing 197 is relatively locked.
  • the inclination direction of the spring coil 195 is the same as the insertion direction of the insertion bush 199 . That is to say, during the inserting process of the inserting bush 199 , the spring ring 195 is pushed by the inserting bush 199 to be deformed toward the insertion direction and snapped into the locking groove 193L to realize locking.
  • the bushing 197 is pulled out and inserted into the bushing 199, as shown in figure d, during the pulling out process, the pulling out direction of the inserting bushing 199 is the same as the deformation direction of the spring ring 195, even if the spring ring 195 passes through the locking groove 193L, there will be a jam. After a while, the insertion bush 199 can still be fully pulled out of the receiving bush 197 to realize unlocking.
  • a third locking mechanism is provided to realize the locking and unlocking between the inserting bush and the receiving bush, specifically:
  • the locking groove 185 is recessed outward from the inner surface of the receiving bush 187, and the locking member is configured as a protrusion 183 formed on the outer wall of the inserting bush 189;
  • the groove 181 and the second groove 179 connected to the first groove 181 , the extending direction of the second groove 179 and the extending direction of the first groove 181 form an angle not equal to 0°.
  • the inner wall of the second groove 179 forms a stop surface 177 for the protrusion 183 to be hooked on.
  • the protrusion 183 When locking is required, the protrusion 183 is aligned with the opening of the first groove 181 and slides in the first groove 181, and the inserting bush 189 and the receiving bush 187 are axially close; subsequently, the protrusion 183 slides from the first groove 181 Insert the second groove 179, and when sliding in the second groove 179 to abut against the stop surface 177, the inserting bush 189 and the receiving bush 187 are relatively fixed.
  • the angle between the first groove 181 and the second groove 179 is 90°, so as to prevent the protrusion 183 from sliding into the first groove 181 in the locked state, and the locking is reliable.
  • the locking scheme of the structure requires relative rotation of the two bushings. Through the 90° angle design of the two slots, it can comply with the rotation of the two bushings. Then, when locking, the two bushes only need to be rotated without axial movement, and the locking operation is convenient.
  • a fourth locking mechanism is provided to realize the locking and unlocking between the inserting bush and the receiving bush, specifically:
  • the bushing at the motor end is mated with the bushing at the intervening end, one of which is configured as a plug, the other of which contains a socket for receiving the plug; defining a bush configured as a plug as an inserting bush, define the bushing defining the slot as the receiving bushing;
  • the device also includes a locking mechanism for engaging and securing the insert bush and the receiving bush, the locking mechanism being configured to achieve axial fixation of the insert bush and the receiving bush by increasing friction.
  • the locking mechanism includes a hoop 169 sheathed outside the receiving bush and a locking operating member 167 operable to lock or release the hoop.
  • the hoop includes a circumferentially extending body 165 that extends circumferentially through an angle of less than 360 degrees.
  • the hoop further includes a first end portion 161 and a second end portion 162 connected to two ends of the main body 165 and extending radially.
  • the locking operation member is a cam
  • the cam has a cam surface 157 with a gradually changing radial dimension, and the cam surface 157 abuts against a surface of the first end portion 161 away from the second end portion 162 .
  • the locking mechanism also includes a fitting 159 connected to the cam. One end of the fitting 159 is connected to the cam, and the other end passes through the first end 161 and the second end 162 and is away from the second end 162 from the end of the first end 161. surface abutment.
  • the cam rotates so that the cam surface 157 with different radial dimensions abuts against the first end 161, and the cam rotates and pulls the fitting 159 to move to change the distance between the first end 161 and the second end 162 of the hoop, so that the hoop
  • the hoop clamps or loosens the receiving bushing, so that the receiving bushing clamps or loosens the inserting bushing to realize locking and unlocking.
  • a fifth locking mechanism is provided to realize the locking and unlocking between the inserting bush and the receiving bush, specifically:
  • the joint part is an opening through the side wall of the receiving bush or a groove only through the inner wall of the receiving bush;
  • the outer surface of the insert bushing is recessed inwardly to form a receiving groove
  • the locking member is configured as a pin or a ball that is at least partially accommodated in the receiving groove and movable in the radial direction; the radially outer end of the pin or the ball has The unlocked state that does not exceed the outer surface of the insert bush to unlock the insert bush and the receiving bush, and the locked state that extends radially outward from the outer surface of the insert bush to fit into the joint to fix the insert bush and the receiving bush .
  • An elastic reset member is biased between the pin or the ball and the accommodating groove, and the reset force applied by the elastic reset member to the pin or the ball makes it always move radially outward to maintain the locked state or move toward the locked state. trend.
  • the elastic reset member makes the pin or ball automatically snap into the opening or groove of the receiving bush to realize locking; when unlocking is required, the inserting bush and the receiving bush are axially pulled /or receive the bushing, and overcome the force of the elastic reset member, so that the ball or ball breaks away from the opening or groove, and then the unlocking can be realized.
  • a sixth locking mechanism is provided to realize the locking and unlocking between the inserting bush and the receiving bush, specifically:
  • the locking mechanism is configured to achieve axial fixation of the insert bushing and the receiving bushing by increasing friction.
  • the locking mechanism includes a threaded hole penetrating through the side wall of the receiving bush, and a bolt screwed into the threaded hole; the bolt is operable to rotate its inner end to compress or break away from the outer surface of the inserting bushing, thereby realizing insertion Locking and unlocking between bushing and receiving bushing.

Landscapes

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

Abstract

L'invention concerne un dispositif (100) d'assistance cardiaque en cas d'insuffisance cardiaque, le dispositif comprenant : un cathéter (32) ; un arbre d'entraînement (34) disposé dans le cathéter (32) d'une manière pénétrante ; et une pompe (36) qui peut être distribuée à un emplacement souhaité dans le cœur par l'intermédiaire du cathéter (32) pour pomper le sang. La pompe comprend : un boîtier de pompe (363) relié à une extrémité distale du cathéter (32) et ayant une extrémité d'entrée (361) et une extrémité de sortie (362), ainsi qu'un impulseur logé dans le boîtier de pompe (363), l'impulseur étant entraîné par l'arbre d'entraînement (34) pour aspirer le sang dans le boîtier de pompe (363) par l'extrémité d'entrée (361) et le décharger par l'extrémité de sortie (362). Le boîtier de pompe (363) et l'impulseur sont conçus de telle sorte que la pompe (36) est dans un état comprimé lorsqu'elle est dans une configuration d'intervention pour permettre à la pompe (36), qui se trouve à l'intérieur d'un premier diamètre extérieur, d'être administrée au système vasculaire d'un patient ; et la pompe (36) est dans un état déployé lorsqu'elle est dans une configuration de fonctionnement pour permettre à la pompe (36), qui se trouve à l'intérieur d'un second diamètre externe qui est supérieur au premier diamètre externe, de pomper le sang jusqu'à un emplacement souhaité. Les performances du dispositif (100) peuvent ainsi être considérablement améliorées.
PCT/CN2021/105656 2021-07-12 2021-07-12 Dispositif d'assistance cardiaque en cas d'insuffisance cardiaque WO2023283751A1 (fr)

Priority Applications (9)

Application Number Priority Date Filing Date Title
PCT/CN2021/105656 WO2023283751A1 (fr) 2021-07-12 2021-07-12 Dispositif d'assistance cardiaque en cas d'insuffisance cardiaque
CN202220733003.6U CN218572654U (zh) 2021-07-12 2022-03-30 用于对心脏在发生功能衰竭时进行辅助的装置
CN202210383880.XA CN115430038A (zh) 2021-07-12 2022-04-12 用于对心脏在发生功能衰竭时进行辅助的装置
CN202210383884.8A CN115463338B (zh) 2021-07-12 2022-04-12 用于对心脏在发生功能衰竭时进行辅助的装置
CN202210382380.4A CN115463337B (zh) 2021-07-12 2022-04-12 用于对心脏在发生功能衰竭时进行辅助的装置
CN202210382379.1A CN115591107B (zh) 2021-07-12 2022-04-12 用于对心脏在发生功能衰竭时进行辅助的装置
PCT/CN2022/086472 WO2023284339A1 (fr) 2021-07-12 2022-04-13 Dispositif d'assistance cardiaque en cas d'insuffisance fonctionnelle cardiaque
CN202210795839.3A CN115382093A (zh) 2021-07-12 2022-07-06 用于对心脏在发生功能衰竭时进行辅助的装置
CN202310248247.4A CN116236683A (zh) 2021-07-12 2023-03-15 叶轮组件、泵头及介入式导管装置

Applications Claiming Priority (1)

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PCT/CN2021/105656 WO2023283751A1 (fr) 2021-07-12 2021-07-12 Dispositif d'assistance cardiaque en cas d'insuffisance cardiaque

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WO2023283751A1 true WO2023283751A1 (fr) 2023-01-19

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CN116236683A (zh) 2023-06-09
CN115591107B (zh) 2024-05-17
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CN115430038A (zh) 2022-12-06
CN115591107A (zh) 2023-01-13
CN115463338B (zh) 2024-05-14
CN115463337B (zh) 2024-07-05
CN218572654U (zh) 2023-03-07

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