WO2017133425A1 - Right ventricular assist device - Google Patents

Right ventricular assist device Download PDF

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Publication number
WO2017133425A1
WO2017133425A1 PCT/CN2017/071195 CN2017071195W WO2017133425A1 WO 2017133425 A1 WO2017133425 A1 WO 2017133425A1 CN 2017071195 W CN2017071195 W CN 2017071195W WO 2017133425 A1 WO2017133425 A1 WO 2017133425A1
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WO
WIPO (PCT)
Prior art keywords
length
end surface
assist device
outflow
heart assist
Prior art date
Application number
PCT/CN2017/071195
Other languages
French (fr)
Chinese (zh)
Inventor
丁以群
Original Assignee
丁以群
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Publication date
Application filed by 丁以群 filed Critical 丁以群
Publication of WO2017133425A1 publication Critical patent/WO2017133425A1/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—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
    • A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow pumps
    • A61M60/242—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow pumps with the outlet substantially perpendicular to the axis of rotation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
    • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
    • A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
    • 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
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
    • A61M60/546—Regulation using real-time blood pump operational parameter data, e.g. motor current of blood flow, e.g. by adapting rotor speed
    • 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
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
    • A61M60/554—Regulation using real-time blood pump operational parameter data, e.g. motor current of blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/804—Impellers
    • A61M60/806—Vanes or blades
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/871—Energy supply devices; Converters therefor
    • A61M60/876—Implantable batteries
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • 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
    • A61M2210/00—Anatomical parts of the body
    • A61M2210/12—Blood circulatory system
    • A61M2210/125—Heart

Definitions

  • the present invention relates to the field of medical device technology, and in particular to a right heart assist device.
  • a right ventricular assist device For patients with right heart failure, in the case of ineffective drug treatment, it is usually necessary to set up a right ventricular assist device, the purpose of which includes: (1) waiting for the donor to prepare for heart transplantation; Restore heart function.
  • right heart assist devices mainly including pneumatic pumps and centrifugal pumps.
  • the main features are open chest insertion, perforation in the avascular free area of the right ventricle, and drainage of right ventricular blood into the right heart assist device.
  • the blood is pumped into the pulmonary artery via the artificial blood vessel.
  • the advantages of the pneumatic pump are that the consumables are easy to replace, the driving device is simple in design, and the pulsating blood flow is formed; the disadvantage is that the driving device is large and is not suitable for being placed in the body, and the pump body and the visible pumping activity exposed to the outside of the body are not suitable. , adversely affect the patient's psychology; need to connect the heart chamber and the aorta with a tube, increase energy consumption, and easily form a thrombus.
  • the advantage of the centrifugal pump is that it has small blood damage and is suitable for installation in the thoracic cavity.
  • the disadvantage is that the right wall of the right chamber is perforated, destroying the integrity of the ventricle, and negatively affecting the recovery of ventricular function; the pump is connected to the pump body and the pulmonary artery, and the power consumption is large. The fever is large and it is easy to cause thrombosis.
  • the pump body has been greatly reduced, it is still located between the outer membrane of the heart and the pericardium, forming a steric hindrance, and aggravating foreign matter friction due to the non-physiological curve structure.
  • the technical problem to be solved by the present invention is to provide a right heart assist device that can be built into the heart cavity without damaging the heart structure.
  • Providing a right heart assist device comprising:
  • the first duct includes an inflow portion and an outflow portion that communicate with each other, a central perpendicular of the inflow end surface of the inflow portion is a first vertical line, and a center perpendicular of the outflow end surface of the outflow portion is a second perpendicular line. a first perpendicular intersects the second perpendicular and forms an angle of 45° to 100°;
  • the driving device is located outside the outflow portion, the outflow portion includes a bottom wall disposed opposite to the outflow end surface, and the blade and the driving device are respectively located at two sides of the bottom wall
  • the driving device is used to drive the blades to rotate.
  • the outflow portion includes a connecting end surface connecting the inflow portion, wherein a length of the connecting end surface is a first length and a length of the outflow portion is a second length in a vertical direction of the outflow end surface, The second length is greater than or equal to twice the first length.
  • the length of the blade in the vertical direction of the outflow end surface is a third length, and the third length is greater than or equal to twice the first length and less than the second length.
  • the blade includes a first end adjacent to the bottom wall, a distance between the first end and the bottom wall is a fourth length, and the fourth length is less than or equal to the first length.
  • the length of the inflow portion is a fifth length, and the fifth length is greater than the first length.
  • the outer diameter of the inflow end surface is a first diameter
  • the outer diameter of the outflow end surface is a second diameter
  • the first diameter is greater than or equal to the second diameter
  • the right heart auxiliary device further includes a second pipe, and the second pipe is detachably connected to the outflow portion.
  • the second pipe includes a connecting portion, and the connecting portion is detachably connected to the outflow portion, and the connecting portion is made of a hard material.
  • the inflow portion is provided with a bypass flow inlet, and the bypass flow inlet is spaced apart from the inflow end surface of the inflow portion.
  • the sewing ring is provided at one end of the inflow portion toward the inflow end surface.
  • the material of the first pipe is titanium metal.
  • the right-heart auxiliary device further includes a support frame and a rotating shaft disposed in the outflow portion, the support frame is fixed on an inner wall of the outflow portion, and includes a first bracket and a second bracket disposed opposite to each other, The blade is disposed around the rotating shaft, the axis of the rotating shaft is perpendicular to the outflow end surface, and the rotating shaft is rotatably connected between the first bracket and the second bracket.
  • the driving device includes a motor and a controller, the motor is configured to drive the blade to rotate, and the controller is electrically connected to the motor to adjust an output power of the motor;
  • the right-hand auxiliary device further includes a partition wall fixed to a side of the bottom wall facing away from the outflow end surface, and forming an isolation cavity together with the bottom wall, wherein the motor is located in the isolation cavity internal.
  • the right heart assist device further includes a first battery component and a second battery component
  • the first battery component is electrically connected to the motor to provide electrical energy to the motor;
  • the second battery component wirelessly charges the first battery component.
  • the first battery component includes an electrically connected first battery and a first charging interface, the first battery electrically connecting the motor;
  • the second battery assembly includes an electrically connected second battery and a second charging interface, and the second charging interface is wirelessly connected to the first charging interface to transfer electrical energy in the second battery to the The first battery.
  • the right heart assist device further comprises a sensing device and a signal processing device
  • the sensing device is configured to detect a fluid parameter in the first conduit and form a first signal to be transmitted to the signal processing device;
  • the signal processing device is configured to receive, store, and process the first signal and form a second signal to the controller to cause the controller to adjust an output power of the motor.
  • the signal processing device comprises a chip and a processor
  • the chip transmits raw data to the processor
  • the processor receives the raw data, forms feedback data, and transmits the feedback signal to the chip;
  • the processor includes a display screen for displaying the raw data and/or the feedback data.
  • the present invention has the following beneficial effects:
  • the first conduit of the right-heart assist device of the present invention forms a flow channel similar to a " ⁇ " type, and since the " ⁇ "-type flow passage conforms to the physiological anatomy of the right ventricle, the right ventricular physiological curve is not destroyed,
  • the first conduit can be built into the right ventricle of the patient, and the inflow end surface connects the intramedullary tricuspid annulus to achieve fixation of the first conduit.
  • the outflow end face of the first conduit communicates with the pulmonary artery of the patient.
  • the driving device drives the blade to rotate, and blood in the right atrium of the patient flows into the first duct from the inflow end surface, and flows out from the outflow end surface under the pushing and pressing of the blade
  • the first tube flows into the patient's pulmonary artery. Therefore, the right heart assist device of the present embodiment can provide an alternative right ventricle for patients with right heart failure, and includes a blood pressure pump for replacing the flow channel and driving force for returning the body vein into the right atrium. Into the pulmonary artery.
  • the right heart assisting device of the embodiment can realize the built-in heart cavity, and the shape of the flow channel conforms to the physiological anatomy of the right ventricle, and does not damage the heart structure.
  • FIG. 1 is a schematic structural diagram of a right-heart assist device according to an embodiment of the present invention.
  • FIG. 2 is a schematic structural view of a first duct of a right-heart assist device according to an embodiment of the present invention.
  • FIG 3 is a top plan view of a first duct of a right-heart assist device according to an embodiment of the present invention.
  • Figure 4 is an enlarged schematic view showing the structure of A in Figure 1.
  • Figure 5 is an enlarged schematic view showing the structure of B in Figure 1.
  • FIG. 6 is a schematic structural diagram of a first inner pipe component of a right-heart assist device according to an embodiment of the present invention.
  • FIG. 7 is another schematic structural diagram of a first inner pipe component of a right-heart assist device according to an embodiment of the present invention.
  • FIG. 8 is a schematic structural diagram of another first conduit of a right-center assisting device according to an embodiment of the present invention.
  • FIG. 9 is a schematic diagram of a signal transmission process of a right-heart assist device according to an embodiment of the present invention.
  • an embodiment of the present invention provides a right heart assist device that can be applied to a patient with right heart failure.
  • the right-heart assist device comprises a first duct 1, a blade 2 and a drive device 3.
  • the first duct 1 includes an inflow portion 11 and an outflow portion 12 that communicate with each other, and a center perpendicular of the inflow end surface 110 of the inflow portion 11 is a first vertical line 111, and a center of the outflow end surface 120 of the outflow portion 12 is suspended.
  • the line is a second perpendicular line 121 that intersects the second perpendicular line 121 and forms an angle ⁇ and satisfies 45° ⁇ ⁇ ⁇ 100°.
  • the vane 2 is rotatably coupled to the interior of the outflow portion 12 for propelling fluid within the first conduit 1 from the outflow end surface 120.
  • the driving device 3 is located outside the outflow portion, and the outflow portion 12 includes a bottom wall 122 disposed opposite to the outflow end surface 120, and the blade 2 and the driving device 3 are respectively located at the bottom wall 122. On both sides, the driving device 3 is used to drive the blade 2 to rotate.
  • the center perpendicular of the two end faces of the first duct 1 of the right-heart assist device (ie, the first perpendicular line 111 and the second perpendicular line 121) form 45°.
  • the angle to 100°, that is, the first duct 1 forms a flow path similar to the " ⁇ " type. Since the " ⁇ " type flow path conforms to the physiological anatomy of the right ventricle and does not damage the right ventricular physiological curve, the first conduit 1 can be built into the patient when the right heart assist device is installed in the patient. In the right ventricle, and the inflow end face 110 is connected to the intramedullary tricuspid annulus to effect fixation of the first conduit 1.
  • the right heart assist device of the present embodiment can provide an alternative right ventricle for patients with right heart failure, and includes a blood pressure pump for replacing the flow channel and driving force for returning the body vein into the right atrium.
  • the right heart assisting device of the embodiment can realize the built-in heart cavity, and the shape of the flow channel conforms to the right ventricle anatomy without damaging the heart structure.
  • the shape of the " ⁇ "-type flow channel of the right-heart assist device in this embodiment is similar to the blood flow trajectory at the right ventricle of the healthy heart.
  • the flow trajectory in the right-heart assist device can be reached. Consistent with the blood flow trajectory at the right ventricle of a healthy heart.
  • the flow of the patient's blood from the right atrium to the inflowing pulmonary artery is the shortest, and the flow trajectory is closest to the healthy heart, so the blade 2 only needs to exert a small pushing force on the blood to push the flow thereof, the driving device 3
  • the efficiency is high and the energy consumption is small, thereby also reducing the energy consumption of the right-heart assist device.
  • the first vertical line 111 and the second vertical line 121 intersect and form an angle ⁇ , so the inflow portion 11 and the outflow portion of the first duct 1 12 is roughly in the same plane, small in size, easy to put into the right ventricle.
  • the blood is usually rushed to the horizontal edge flow channel by the vertical central flow channel, and the flow is long, the blood is continuously reversed during the flow, and the direction is not coplanar. Therefore, the energy loss is extremely large, and the centrifugal pump consumes a large amount of power.
  • the “center vertical line” refers to a line located at the center of the designated plane and perpendicular to the designated plane.
  • the first vertical line 111 refers to a line located at the center of the inflow end surface 110 and perpendicular to the inflow end surface 110.
  • the second vertical line 121 refers to a line located at the center of the outflow end surface 120 and perpendicular to the outflow end surface 120.
  • the resistance of the fluid in the first conduit 1 is the smallest.
  • the inflow portion 11 of the first duct 1 includes a small section of a circular tube adjacent to the inflow end surface 110 and a flat tube portion connected to the outflow portion 12,
  • the outflow portion 12 has a circular tube shape, that is, the shape of the pipe of the first pipe 1 changes from the inflow end surface 110 to the outflow end surface 120 as follows: a circular tube - a flat tube - a round tube, and the flat tube
  • the flow area is not required to be constant.
  • the shape change of the pipe is a gentle transition.
  • the round tube portion of the inflow portion 11 is for facilitating connection of the inflow end surface 110 to the tricuspid annulus; the flat tube portion of the inflow portion 11 is for reducing the first duct 1 perpendicular to the outflow end surface
  • the size in the direction of 120 that is, the reduction
  • the volume of the first duct 1 is provided to provide a space for other components (for example, the driving device 3) so that the components of the right heart assisting device are placed in a reasonable and compact position, and the volume of the right-center assisting device is reduced.
  • the shape of the pipe of the first pipe 1 can be designed and changed according to the requirements of the specific application environment, and is not limited to the shape described in the above embodiments.
  • the blade 2 and the driving device 3 are respectively disposed on two sides of the bottom wall 122, that is, the bottom wall 122 is completely separated.
  • the drive device 3 and the blade 2 are opened, and the drive device 3 wirelessly drives the blade 2 to rotate.
  • the wireless driving such as electromagnetic driving, etc.
  • the present embodiment can be designed with reference to the achievable wireless driving mode, and is not described here.
  • the outflow portion 12 of the first duct 1 includes a connecting end surface 123, and the connecting end surface 123 connects the inflow portion 11.
  • the length of the connecting end surface 123 is a first length L1
  • the length of the outflow portion 12 is a second length L2
  • the second length L2 is greater than or equal to two times
  • the first length L1 causes the fluid in the first conduit 1 to be sufficiently pressurized within the outflow portion 12.
  • connection end face 123 in the embodiment of the present invention can be understood as the plane in which the flow inlet of the outflow portion 12 is located.
  • the surface having the smallest flow area among the plurality of planes of the joining portion of the inflow portion 11 and the outflow portion 12 is defined as the connecting end surface 123.
  • the length of the blade 2 in the vertical direction of the outflow end surface 120 is a third length L3, and the third length L3 is greater than or equal to twice the first
  • the length L1 is smaller than the second length L2 such that the blade 2 has a sufficiently long advancement area.
  • the third length L3 is greater than or equal to two-thirds of the second length L2, that is, the length of the outflow portion 12 only needs to be slightly greater than or equal to the length of the blade 2.
  • the blade 2 includes a first end 21 adjacent to the bottom wall 122 , and a distance between the first end 21 and the bottom wall 122 is The fourth length L4 is less than or equal to the first length L1. That is, the distance between the first end 21 and the bottom wall 122 is small, so that the energy consumption of the driving device 3 can be reduced.
  • the driving device 3 and the blade 2 are both close to the The bottom wall 122 is disposed.
  • the blood in the first duct 1 directly enters the propulsion region of the vane 2 from the inflow portion 11 (the rotation region of the vane 2 is its propulsion region), which reduces the flow of the fluid and reduces the Fluid resistance, the driving device 3
  • the energy consumption is reduced and the efficiency of the right heart assist device is increased.
  • the length of the inflow portion 11 is a fifth length L5, and the fifth length L5 is greater than the first length L1. That is, in the direction perpendicular to the outflow end surface 120, the size of the first duct 1 has a long-short-long change, and the junction area of the inflow portion 11 and the outflow portion 12 forms a joint.
  • the recessed area of the first duct 1 is used to accommodate the supracondylar structure of the chamber, so that the first duct 1 is more in line with the physiological anatomy of the right heart of the patient.
  • the respective portions of the first duct 1 have the same size, that is, the structure as shown in FIG. At this time, in the process in which blood flows from the inflow end surface 110 to the connection end surface 123, the flow area is reduced and the flow velocity is increased.
  • the outer diameter of the inflow end surface 110 is a first outer diameter D1
  • the outer diameter of the outflow end surface 120 is a second diameter D2
  • the second diameter D2 is greater than or equal to enable the first duct 1 to be smoothly installed into the right ventricle of the patient.
  • the right-hand auxiliary device further includes a second duct 4, and the second duct 4 is detachably connected to the outflow portion. 12, that is, one end of the second duct 4 is connected to the outflow end surface 120.
  • the second duct 4 since the second duct 4 is provided, the other end of the second duct 4 can be passed through the pulmonary valve annulus of the patient into the pulmonary artery to allow blood to enter the patient from the first duct 1 Pulmonary artery.
  • the length of the outflow portion 12 may be short, and the distance from the outflow end surface 120 to the pulmonary valve annulus is filled by the second duct 4, so that the right heart assisting device can be applied to various types. Different application environments improve versatility.
  • one end of the second duct 4 is detachably connected to the outflow end surface 120 of the first duct 1, and the detachable connection refers to a detachable connecting member for connection, such as a key connection. , pin connections, threaded connections and clamp connections.
  • the second duct 4 includes a connecting portion and a circulation portion, and the connecting portion is detachably connected to the outflow portion 12, and the connecting portion is made of a hard material to facilitate connection.
  • a groove 1201 is disposed at a position of the outer wall of the outflow portion 12 adjacent to the outflow end surface 120 (that is, the connecting portion), and an inner wall of one end of the second pipe 4 is provided with a protrusion. 41.
  • the protrusion 41 is snapped into the groove 1201 to form a connecting member, and a fastening ring 42 is jacketed on the connecting member to fix the second pipe 4 to the first pipe 1.
  • the flow area of the circulation portion is not fixed and can be flexibly designed according to the physical condition of the patient.
  • the flow area of the circulation portion may be smaller than the flow area of the connection portion (that is, smaller than the flow area of the outflow portion 12), and the flow portion may be provided with a convergent structure at a position where the connection portion is connected.
  • the inflow portion 11 is provided with a bypass flow inlet 112 , and the bypass flow inlet 112 is spaced apart from the inflow end surface 110 of the inflow portion 11 , that is, the The bypass inflow port 112 and the inflow end surface 110 are independent of each other such that the bypass inflow port 112 becomes an inlet of the other inflow portion 11.
  • the bypass flow inlet 112 may be provided in plurality and its position may be adjusted depending on the heart condition of the patient. For example, the bypass flow inlet 112 may be opened on a side of the inflow portion 11 away from the outflow portion 12.
  • an end of the inflow portion 11 facing the inflow end surface 110 (for example, a portion of the round tube of the inflow portion 11) is provided with a sewing ring 113, the sewing ring
  • the inner ring of 113 is stitched or ferred on the inflow portion 11, and the outer ring of the sewing ring 113 is used for sewing to the tricuspid annulus of the heart, thereby fixing the inflow end surface 110 of the first duct 1 To the heart.
  • the sewing ring 113 employs a biocompatible, non-absorbable woven material, such as polyester that can be used for stitching.
  • a recessed area 1130 is disposed at an outer wall of the inflow portion 11 near the inflow end surface 110 , and the sewing ring 113 is engaged in the recessed area 1130 . The fixing to the inflow portion 11 is achieved.
  • the material of the first pipe 1 is set to be a hard material, that is, the first pipe 1 is No deformation or very slight deformation occurs under the pressure of the fluid, thereby enabling fluid to flow along a predetermined flow path trajectory to reduce energy consumption of the right heart assist device.
  • the first pipe 1 can be made of lightweight titanium, which has high strength, small density, high hardness, high melting point and strong corrosion resistance.
  • the material of the second pipe 4 may be a flexible material (for example, an artificial blood vessel) or a rigid material (for example, titanium metal).
  • a coating may be applied on the surface of the first conduit 1, which uses an antithrombotic substance to reduce the formation of blood clots.
  • the coating may be coated with a polytetrafluoroethylene.
  • the right-heart assist device further includes a support frame 200 and a rotating shaft 20 disposed in the outflow portion 12 , and the support frame 200 is fixed at the outflow.
  • the axis 203 of the rotating shaft 20 is perpendicular to the outflow end surface 120, that is, the direction of the propulsive force of the vane 2 is perpendicular to the outflow end surface 120, and the fluid in the first duct 1 is very
  • the small blade 2 can be smoothly ejected from the outflow end surface 120 under the propulsive force, so that the right-heart auxiliary device consumes less energy and is more energy-saving.
  • the shape of the blade 2 can be rationally designed to have greater propulsive force while reducing the impact of blood flow on the side wall of the outflow portion 12 to reduce losses.
  • the first bracket 201 includes a first ring portion 2011 and a first spoke 2012, and the first spoke 2012 is disposed at the first ring portion.
  • a first groove 2013 is provided in a middle portion of the first spoke 2012;
  • the second bracket 202 includes a second ring portion 2021 and a second spoke 2022, the second The spokes 2022 are disposed at any one of the diameters of the inner circumference of the second ring portion 2021, and the second portion of the second spokes 2022 is provided with a second groove 2023.
  • the support frame 200 further includes a positioning bracket 204, and the positioning bracket 204 connects the first bracket 201 and the second bracket 202 for fixing between the first bracket 201 and the second bracket 202. spacing.
  • a maximum distance between the first groove 2013 and the second groove 2023 is greater than a total length of the rotating shaft 20, the first groove 2013 and The minimum spacing between the second grooves 2023 (for example, between the edges of the two grooves) is smaller than the total length of the rotating shaft 20, so that the rotating shaft 2032 has a slight relative movement space, so that the rotating shaft 20 And the blade 2 has a certain self-adjusting space during rotation or operation, which facilitates the flow of the rotating shaft 20 and the blade 2 according to the fluid in the first pipe 1 Condition adjustments with buffering and optimization capabilities.
  • the blade 2 and the rotating shaft 20 are both made of a hard material, preferably a lightweight titanium material.
  • the rotating shaft 20 is hollow in design to reduce the quality and reduce the energy consumption of the driving device 3.
  • the driving device 3 of the right-heart assist device includes a motor 5 and a controller 6 for driving the blade 2 to rotate; the controller 6 electrically connecting the motor 5 for adjusting the output power of the motor 5.
  • the motor 5 and the blade 2 are respectively disposed on two sides of the bottom wall 122, that is, the bottom wall 122 completely separates the motor 5 from the blade 2,
  • the motor 5 wirelessly drives the blade 2 to rotate.
  • the wireless driving such as electromagnetic driving, etc.
  • the present embodiment can be designed with reference to the achievable wireless driving mode, and is not described here.
  • the spacing between the motor 5 and the blade 2 should be as small as possible to reduce the energy consumption of the motor 5.
  • the motor 5 and the blade 2 are both disposed adjacent to the bottom wall 122.
  • the right-hand auxiliary device further includes a partition wall 51 fixed to a side of the bottom wall 122 facing away from the outflow end surface 120, and The bottom wall 122 collectively forms an isolation chamber 50 in which the motor 5 is placed.
  • the controller 6 is also placed within the isolation chamber 50.
  • the isolation chamber 50 is a sealed chamber.
  • the first pipe 1 and the partition wall 51 are designed to adopt a transitional design such as a circular arc or a slope, so as to avoid the use of a right angle or a protruding protrusion to prevent Form a thrombus.
  • the right-heart assist device further includes a first battery component 71 and a second battery component 72.
  • the first battery assembly 71 is electrically connected to the motor 5 for supplying electric power to the motor 5.
  • the second battery component 72 wirelessly charges the first battery component 71.
  • the first battery component 71 includes a first battery 711 electrically connected to the first charging interface 712, and the first battery 711 is electrically connected to the motor 5.
  • the second battery assembly 72 includes a second battery 721 and a second charging interface 722 that are electrically connected.
  • the first charging interface 712 Wirelessly connecting with the second charging interface 722 to transfer electrical energy in the second battery 721 to the first battery 711.
  • the first battery assembly 71 When the right heart assist device is mounted to a human body, the first battery assembly 71 is placed in the body and the second battery assembly 72 is placed outside the body.
  • the first battery assembly 71 is connected to the motor 5 by wires, and the first battery assembly 71 is placed outside the heart and buried under the skin (bath is preferred).
  • the second battery assembly 72 is disposed on a waist belt, and the second battery assembly 72 faces the first battery assembly 71 after the user wears the belt.
  • the second battery component 72 wirelessly charges the second battery component 72, and the wireless charging reference may be implemented by a wireless charging mode.
  • the right-heart assist device further includes a sensing device 100 and a signal processing device 101.
  • the sensing device 100 is configured to detect a fluid parameter in the first conduit 1 (and the second conduit 4) and form a first signal S1 to be transmitted to the signal processing device 101.
  • the signal processing device 101 is configured to receive, store, and process the first signal S1, and form a second signal S2 to be transmitted to the controller 6, so that the controller 6 adjusts the output power of the motor 5.
  • the fluid parameters described in this embodiment include, but are not limited to, pressure, viscosity, flow rate, temperature, density, and the like.
  • the sensing device 100 may be provided with multiple sensors at the same time to detect a plurality of different parameters, or multiple sensors installed simultaneously in multiple positions of the first pipe 1 (with the second pipe 4) To detect the same parameter at multiple different locations. Further, the sensing device 100 can simultaneously detect the operating parameters of the blade 2 and/or the motor 5, such as the rotational speed, power, etc., while transmitting relevant data to the signal processing device 101 to obtain more The ideal second signal S2 increases the operating efficiency of the motor 5 and reduces the energy consumption of the right-heart assist device. Of course, the sensing device 100 can also detect other parameters according to specific needs.
  • the signal processing device 101 of the right-heart assist device includes a chip 81 and a processor 82.
  • the chip 81 transmits raw data S3 to the processor 82.
  • the processor 82 receives the raw data S3, forms feedback data S4, and transmits the feedback data S4 to the chip 81.
  • the processor 82 includes a display screen 821 for displaying the raw data S3 and/or the feedback data S4.
  • the chip 81 and the processor 82 both have signal processing capabilities, and the processor 82 further has the ability to modify the internal data/program of the chip 81 to cause the signal processing device 101.
  • the processor 82 According to the user's physical state changes (rest or exercise state, vascular resistance changes, etc.) Reasonable adjustment is made to make the right heart auxiliary device conform to the real-time physiological state of the patient, and at the same time, the battery life time can be extended, and the service life of the right heart auxiliary device can be prolonged.
  • the display screen 821 in the embodiment can intuitively express the physical condition of the user and the working state of the right-heart assist device, and is useful for diagnosing and treating the user.
  • the controller 6 and the chip 81 are placed in the body.
  • the chip 81 is connected to the controller 6 through a data line, and the first chip 81 is placed outside the heart and buried under the skin (bath is preferred).
  • the processor 82 can be integrally disposed on a belt provided with a second battery assembly 72, and the processor 82 faces the chip 81 after the user wears the belt.
  • the processor 82 wirelessly transmits data to the chip 81 in both directions.
  • the display screen 821 may be disposed on an outer surface of the waist belt, and the user may directly view the display image of the display screen 821.

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Abstract

A right ventricular assist device, comprising: a first conduit (1) comprising an inflow portion (11) and an outflow portion (12) in communication with each other, wherein a center vertical line of an inflow end face (110) of the inflow portion (11) is a first vertical line (111), a center vertical line of an outflow end face (120) of the outflow portion (12) is a second vertical line (121), and the first vertical line (11) intersects the second vertical line (121) to form an angle ranging from 45° to 100°; a vane (2) rotatably connected to the interior of the outflow portion (12), to push a fluid in the first conduit (1) to flow out from the outflow end face (120); and a drive means (3) located outside the outflow portion (12). The outflow portion (12) comprises a bottom wall (122) opposite to the outflow end face (120). The vane (2) and the drive means (3) are respectively located on two sides of the bottom wall (122). The drive means (3) is used to drive the vane (2) to rotate. The right ventricular assist device can be placed in a ventricle without damaging the heart structure.

Description

右心辅助装置Right heart assist device
本发明要求2016年2月2日递交的发明名称为“右心辅助装置”的申请号201610074520.6的在先申请优先权，上述在先申请的内容以引入的方式并入本文本中。The present invention claims the priority of the prior application of the application No. 201610074520.6, entitled "Right-Aid Assist", filed on February 2, 2016, the content of which is incorporated herein by reference.
技术领域Technical field
本发明涉及医疗器械技术领域，特别涉及一种右心辅助装置。The present invention relates to the field of medical device technology, and in particular to a right heart assist device.
背景技术Background technique
对于右心功能衰竭的患者，在药物治疗无效的情况下，通常需要设置右心辅助装置(Right ventricular assist device)，其目的包括：(一)、等待供体，为心脏移植准备；(二)、恢复心脏功能。For patients with right heart failure, in the case of ineffective drug treatment, it is usually necessary to set up a right ventricular assist device, the purpose of which includes: (1) waiting for the donor to prepare for heart transplantation; Restore heart function.
目前的右心辅助装置较少，主要包括气动泵和离心泵，其主要特点为开胸置入，在右心室游离壁无血管区打孔，将右心室血液引流进入右心辅助装置，加压后的血液经人造血管泵入肺动脉。At present, there are few right heart assist devices, mainly including pneumatic pumps and centrifugal pumps. The main features are open chest insertion, perforation in the avascular free area of the right ventricle, and drainage of right ventricular blood into the right heart assist device. The blood is pumped into the pulmonary artery via the artificial blood vessel.
其中，气动泵的优点在于耗材易于更换，驱动装置设计简单，且形成搏动性血流；缺点在于：驱动装置庞大，不适合置于体内，而暴露于体外的泵体和可视的泵血活动，对患者心理造成不良影响；需要管道连接心腔和主动脉，增加能耗，并容易形成血栓。Among them, the advantages of the pneumatic pump are that the consumables are easy to replace, the driving device is simple in design, and the pulsating blood flow is formed; the disadvantage is that the driving device is large and is not suitable for being placed in the body, and the pump body and the visible pumping activity exposed to the outside of the body are not suitable. , adversely affect the patient's psychology; need to connect the heart chamber and the aorta with a tube, increase energy consumption, and easily form a thrombus.
而离心泵的优点在于血液破坏小、适用于胸腔内安装，缺点在于：右室游离壁打孔，破坏心室的完整性，对心室功能恢复产生负面影响；管道连接泵体和肺动脉，功耗大、发热大，容易造成血栓；泵体虽然已经大幅度缩小，但依然位于心脏外膜和心包之间，形成位阻，并因非生理性曲线结构而加重异物摩擦。The advantage of the centrifugal pump is that it has small blood damage and is suitable for installation in the thoracic cavity. The disadvantage is that the right wall of the right chamber is perforated, destroying the integrity of the ventricle, and negatively affecting the recovery of ventricular function; the pump is connected to the pump body and the pulmonary artery, and the power consumption is large. The fever is large and it is easy to cause thrombosis. Although the pump body has been greatly reduced, it is still located between the outer membrane of the heart and the pericardium, forming a steric hindrance, and aggravating foreign matter friction due to the non-physiological curve structure.
发明内容Summary of the invention
本发明所要解决的技术问题在于提供一种可内置于心脏腔且不会破坏心脏结构的右心辅助装置。 The technical problem to be solved by the present invention is to provide a right heart assist device that can be built into the heart cavity without damaging the heart structure.
为了实现上述目的，本发明实施方式采用如下技术方案：In order to achieve the above object, the embodiments of the present invention adopt the following technical solutions:
提供一种右心辅助装置，包括：Providing a right heart assist device comprising:
第一管道，包括彼此连通的流入部和流出部，所述流入部的流入端面的中心垂线为第一垂线，所述流出部的流出端面的中心垂线为第二垂线，所述第一垂线与所述第二垂线相交且形成45°至100°的角；The first duct includes an inflow portion and an outflow portion that communicate with each other, a central perpendicular of the inflow end surface of the inflow portion is a first vertical line, and a center perpendicular of the outflow end surface of the outflow portion is a second perpendicular line. a first perpendicular intersects the second perpendicular and forms an angle of 45° to 100°;
叶片，转动连接至所述流出部的内部，用以推进所述第一管道内的流体从所述流出端面流出；及a blade rotatably coupled to the interior of the outflow portion for propelling fluid in the first conduit from the outflow end surface; and
驱动装置，所述驱动装置位于所述流出部的外部，所述流出部包括与所述流出端面相对设置的底壁，所述叶片与所述驱动装置分别位于所述底壁的两侧，所述驱动装置用以驱动所述叶片转动。a driving device, the driving device is located outside the outflow portion, the outflow portion includes a bottom wall disposed opposite to the outflow end surface, and the blade and the driving device are respectively located at two sides of the bottom wall The driving device is used to drive the blades to rotate.
其中，所述流出部包括连接所述流入部的连接端面，在所述流出端面的垂直方向上，所述连接端面的长度为第一长度，所述流出部的长度为第二长度，所述第二长度大于等于二倍的所述第一长度。The outflow portion includes a connecting end surface connecting the inflow portion, wherein a length of the connecting end surface is a first length and a length of the outflow portion is a second length in a vertical direction of the outflow end surface, The second length is greater than or equal to twice the first length.
其中，所述叶片在所述流出端面的垂直方向上的长度为第三长度，所述第三长度大于等于二倍的所述第一长度并且小于所述第二长度。The length of the blade in the vertical direction of the outflow end surface is a third length, and the third length is greater than or equal to twice the first length and less than the second length.
其中，所述叶片包括靠近所述底壁的第一端，所述第一端与所述底壁之间的距离为第四长度，所述第四长度小于等于所述第一长度。Wherein the blade includes a first end adjacent to the bottom wall, a distance between the first end and the bottom wall is a fourth length, and the fourth length is less than or equal to the first length.
其中，在所述流出端面的垂直方向上，所述流入部的长度为第五长度，所述第五长度大于所述第一长度。Wherein, in the vertical direction of the outflow end surface, the length of the inflow portion is a fifth length, and the fifth length is greater than the first length.
其中，所述流入端面的外径长度为第一直径，所述流出端面的外径长度为第二直径，所述第一直径大于等于所述第二直径。The outer diameter of the inflow end surface is a first diameter, and the outer diameter of the outflow end surface is a second diameter, and the first diameter is greater than or equal to the second diameter.
其中，所述右心辅助装置还包括第二管道，所述第二管道可拆连接至所述流出部。Wherein, the right heart auxiliary device further includes a second pipe, and the second pipe is detachably connected to the outflow portion.
其中，所述第二管道包括连接部，所述连接部可拆连接至所述流出部，所述连接部的材质采用硬质材料。The second pipe includes a connecting portion, and the connecting portion is detachably connected to the outflow portion, and the connecting portion is made of a hard material.
其中，所述流入部开设有旁通流入口，所述旁通流入口与所述流入部的流入端面间隔设置。The inflow portion is provided with a bypass flow inlet, and the bypass flow inlet is spaced apart from the inflow end surface of the inflow portion.
其中，所述流入部的靠向所述流入端面的一端设置有缝合环。The sewing ring is provided at one end of the inflow portion toward the inflow end surface.
其中，所述第一管道的材质为钛金属。 Wherein, the material of the first pipe is titanium metal.
其中，所述右心辅助装置还包括设置在所述流出部内的支撑架和转轴，所述支撑架固定在所述流出部的内壁，并且包括相对设置的第一支架和第二支架，所述叶片围绕所述转轴设置，所述转轴的轴线垂直于所述流出端面，所述转轴转动连接在所述第一支架与所述第二支架之间。Wherein the right-heart auxiliary device further includes a support frame and a rotating shaft disposed in the outflow portion, the support frame is fixed on an inner wall of the outflow portion, and includes a first bracket and a second bracket disposed opposite to each other, The blade is disposed around the rotating shaft, the axis of the rotating shaft is perpendicular to the outflow end surface, and the rotating shaft is rotatably connected between the first bracket and the second bracket.
其中，所述驱动装置包括电机和控制器，所述电机用以驱动所述叶片转动，所述控制器电连接所述电机，用以调节所述电机的输出功率；The driving device includes a motor and a controller, the motor is configured to drive the blade to rotate, and the controller is electrically connected to the motor to adjust an output power of the motor;
所述右心辅助装置还包括隔离壁，所述隔离壁固定至所述底壁背离所述流出端面的一侧，并与所述底壁共同形成隔离腔，所述电机位于所述隔离腔的内部。The right-hand auxiliary device further includes a partition wall fixed to a side of the bottom wall facing away from the outflow end surface, and forming an isolation cavity together with the bottom wall, wherein the motor is located in the isolation cavity internal.
其中，所述右心辅助装置还包括第一电池组件和第二电池组件；Wherein the right heart assist device further includes a first battery component and a second battery component;
所述第一电池组件电连接所述电机，用以为所述电机提供电能；The first battery component is electrically connected to the motor to provide electrical energy to the motor;
所述第二电池组件对所述第一电池组件进行无线充电。The second battery component wirelessly charges the first battery component.
其中，所述第一电池组件包括电连接的第一蓄电池和第一充电接口，所述第一蓄电池电连接所述电机；Wherein the first battery component includes an electrically connected first battery and a first charging interface, the first battery electrically connecting the motor;
所述第二电池组件包括电连接的第二蓄电池和第二充电接口，所述第二充电接口与所述第一充电接口之间无线连接，使所述第二蓄电池内的电能转移至所述第一蓄电池。The second battery assembly includes an electrically connected second battery and a second charging interface, and the second charging interface is wirelessly connected to the first charging interface to transfer electrical energy in the second battery to the The first battery.
其中，所述右心辅助装置还包括传感装置和信号处理装置；Wherein the right heart assist device further comprises a sensing device and a signal processing device;
所述传感装置用以检测所述第一管道内的流体参数，并形成第一信号传送至所述信号处理装置；The sensing device is configured to detect a fluid parameter in the first conduit and form a first signal to be transmitted to the signal processing device;
所述信号处理装置用以接收、存储以及处理所述第一信号，并形成第二信号传送至所述控制器，使所述控制器调节所述电机的输出功率。The signal processing device is configured to receive, store, and process the first signal and form a second signal to the controller to cause the controller to adjust an output power of the motor.
其中，所述信号处理装置包括芯片和处理器；Wherein the signal processing device comprises a chip and a processor;
所述芯片传送原始数据至所述处理器；The chip transmits raw data to the processor;
所述处理器接收所述原始数据、形成反馈数据，并传送所述反馈信号至所述芯片；The processor receives the raw data, forms feedback data, and transmits the feedback signal to the chip;
所述处理器包括显示屏，所述显示屏用以显示所述原始数据和/或所述反馈数据。The processor includes a display screen for displaying the raw data and/or the feedback data.
相较于现有技术，本发明具有以下有益效果： Compared with the prior art, the present invention has the following beneficial effects:
本发明所述右心辅助装置的所述第一管道形成类似“√”型的流道，由于“√”型的流道符合右心室的生理解剖结构，不会破坏右心室生理性曲线，因此在患者体内安装所述右心辅助装置时，可以将所述第一管道内置于患者的右心室内，并且所述流入端面连接心脏内三尖瓣环以实现所述第一管道的固定。同时，所述第一管道的所述流出端面连通患者的肺动脉。此时，所述驱动装置驱动所述叶片转动，患者的右心房内血液由所述流入端面流入所述第一管道，在所述叶片的推动和加压下，自所述流出端面流出所述第一管道并流进患者肺动脉。故，本实施例所述右心辅助装置能够为右心功能衰竭的患者提供一个替代的右心室，且包括有替代流道和驱动力，用以将体静脉回流入右心房的血加压泵入肺动脉。综上所述，本实施例所述右心辅助装置可以实现心脏腔内置入，其流道形状符合右心室生理解剖结构，不会破坏心脏结构。The first conduit of the right-heart assist device of the present invention forms a flow channel similar to a "√" type, and since the "√"-type flow passage conforms to the physiological anatomy of the right ventricle, the right ventricular physiological curve is not destroyed, When the right heart assist device is installed in the patient, the first conduit can be built into the right ventricle of the patient, and the inflow end surface connects the intramedullary tricuspid annulus to achieve fixation of the first conduit. At the same time, the outflow end face of the first conduit communicates with the pulmonary artery of the patient. At this time, the driving device drives the blade to rotate, and blood in the right atrium of the patient flows into the first duct from the inflow end surface, and flows out from the outflow end surface under the pushing and pressing of the blade The first tube flows into the patient's pulmonary artery. Therefore, the right heart assist device of the present embodiment can provide an alternative right ventricle for patients with right heart failure, and includes a blood pressure pump for replacing the flow channel and driving force for returning the body vein into the right atrium. Into the pulmonary artery. In summary, the right heart assisting device of the embodiment can realize the built-in heart cavity, and the shape of the flow channel conforms to the physiological anatomy of the right ventricle, and does not damage the heart structure.
附图说明DRAWINGS
为了更清楚地说明本发明的技术方案，下面将对实施方式中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本发明的一些实施方式，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以如这些附图获得其他的附图。In order to more clearly illustrate the technical solutions of the present invention, the drawings used in the embodiments will be briefly described below. It is obvious that the drawings in the following description are only some embodiments of the present invention, which are common in the art. For the skilled person, other drawings can be obtained as shown in these drawings without any creative work.
图1是本发明实施例提供的一种右心辅助装置的结构示意图。FIG. 1 is a schematic structural diagram of a right-heart assist device according to an embodiment of the present invention.
图2是本发明实施例提供的一种右心辅助装置的第一管道的结构示意图。2 is a schematic structural view of a first duct of a right-heart assist device according to an embodiment of the present invention.
图3是本发明实施例提供的一种右心辅助装置的第一管道的俯视图。3 is a top plan view of a first duct of a right-heart assist device according to an embodiment of the present invention.
图4是图1中A处结构的放大示意图。Figure 4 is an enlarged schematic view showing the structure of A in Figure 1.
图5是图1中B处结构的放大示意图。Figure 5 is an enlarged schematic view showing the structure of B in Figure 1.
图6是本发明实施例提供的一种右心辅助装置的第一管道内部件的结构示意图。FIG. 6 is a schematic structural diagram of a first inner pipe component of a right-heart assist device according to an embodiment of the present invention.
图7是本发明实施例提供的一种右心辅助装置的第一管道内部件的另一结构示意图。FIG. 7 is another schematic structural diagram of a first inner pipe component of a right-heart assist device according to an embodiment of the present invention.
图8是本发明实施例提供的一种右心辅助装置的另一种第一管道的结构示意图。FIG. 8 is a schematic structural diagram of another first conduit of a right-center assisting device according to an embodiment of the present invention.
图9是本发明实施例提供的一种右心辅助装置的信号传送流程示意图。 FIG. 9 is a schematic diagram of a signal transmission process of a right-heart assist device according to an embodiment of the present invention.
具体实施方式detailed description
下面将结合本发明实施例中的附图，对本发明实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本发明一部分实施例，而不是全部的实施例。基于本发明中的实施例，本领域普通技术人员在没有作出创造性劳动前提下所获得的所有其他实施例，都属于本发明保护的范围。The technical solutions in the embodiments of the present invention are clearly and completely described in the following with reference to the accompanying drawings in the embodiments of the present invention. It is obvious that the described embodiments are only a part of the embodiments of the present invention, but not all embodiments. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without creative efforts are within the scope of the present invention.
请一并参阅图1和图2，本发明实施例提供一种右心辅助装置，可适用于右心功能衰竭的患者。所述右心辅助装置包括第一管道1、叶片2以及驱动装置3。所述第一管道1包括彼此连通的流入部11和流出部12，所述流入部11的流入端面110的中心垂线为第一垂线111，所述流出部12的流出端面120的中心垂线为第二垂线121，所述第一垂线111与所述第二垂线121相交且形成角α，且满足45°≤α≤100°。所述叶片2转动连接至所述流出部12的内部，用以推进所述第一管道1内的流体从所述流出端面120流出。所述驱动装置3位于所述流出部的外部，所述流出部12包括与所述流出端面120相对设置的底壁122，所述叶片2与所述驱动装置3分别位于所述底壁122的两侧，所述驱动装置3用以驱动所述叶片2转动。Referring to FIG. 1 and FIG. 2 together, an embodiment of the present invention provides a right heart assist device that can be applied to a patient with right heart failure. The right-heart assist device comprises a first duct 1, a blade 2 and a drive device 3. The first duct 1 includes an inflow portion 11 and an outflow portion 12 that communicate with each other, and a center perpendicular of the inflow end surface 110 of the inflow portion 11 is a first vertical line 111, and a center of the outflow end surface 120 of the outflow portion 12 is suspended. The line is a second perpendicular line 121 that intersects the second perpendicular line 121 and forms an angle α and satisfies 45° ≤ α ≤ 100°. The vane 2 is rotatably coupled to the interior of the outflow portion 12 for propelling fluid within the first conduit 1 from the outflow end surface 120. The driving device 3 is located outside the outflow portion, and the outflow portion 12 includes a bottom wall 122 disposed opposite to the outflow end surface 120, and the blade 2 and the driving device 3 are respectively located at the bottom wall 122. On both sides, the driving device 3 is used to drive the blade 2 to rotate.
在本实施例中，所述右心辅助装置的所述第一管道1的两个端面的中心垂线(即所述第一垂线111与所述第二垂线121)之间形成45°至100°的角，也即所述第一管道1形成类似“√”型的流道。由于“√”型的流道符合右心室的生理解剖结构，不会破坏右心室生理性曲线，因此在患者体内安装所述右心辅助装置时，可以将所述第一管道1内置于患者的右心室内，并且所述流入端面110连接心脏内三尖瓣环以实现所述第一管道1的固定。同时，所述第一管道1的所述流出端面120连通患者的肺动脉。此时，所述驱动装置3驱动所述叶片2转动，患者的右心房内血液由所述流入端面110流入所述第一管道1，在所述叶片2的推动和加压下，自所述流出端面120流出所述第一管道1并流进患者肺动脉。故，本实施例所述右心辅助装置能够为右心功能衰竭的患者提供一个替代的右心室，且包括有替代流道和驱动力，用以将体静脉回流入右心房的血加压泵入肺动脉。综上所述，本实施例所述右心辅助装置可以实现心脏腔内置入，其流道形状符合右心室解剖结构，不会破坏心脏结构。 In this embodiment, the center perpendicular of the two end faces of the first duct 1 of the right-heart assist device (ie, the first perpendicular line 111 and the second perpendicular line 121) form 45°. The angle to 100°, that is, the first duct 1 forms a flow path similar to the "√" type. Since the "√" type flow path conforms to the physiological anatomy of the right ventricle and does not damage the right ventricular physiological curve, the first conduit 1 can be built into the patient when the right heart assist device is installed in the patient. In the right ventricle, and the inflow end face 110 is connected to the intramedullary tricuspid annulus to effect fixation of the first conduit 1. At the same time, the outflow end face 120 of the first conduit 1 communicates with the pulmonary artery of the patient. At this time, the driving device 3 drives the blade 2 to rotate, and the blood in the right atrium of the patient flows into the first duct 1 from the inflow end surface 110, under the pushing and pressing of the blade 2, from the The outflow end face 120 flows out of the first conduit 1 and into the patient's pulmonary artery. Therefore, the right heart assist device of the present embodiment can provide an alternative right ventricle for patients with right heart failure, and includes a blood pressure pump for replacing the flow channel and driving force for returning the body vein into the right atrium. Into the pulmonary artery. In summary, the right heart assisting device of the embodiment can realize the built-in heart cavity, and the shape of the flow channel conforms to the right ventricle anatomy without damaging the heart structure.
再者，本实施例中所述右心辅助装置的“√”型流道形状类似于健康心脏的右心室处的血液流动轨迹，最优的，所述右心辅助装置内的流动轨迹可以达到与健康心脏的右心室处的血液流动轨迹一致。此时，患者血液自右心房流出到流入肺动脉的流程最短、流动轨迹最接近健康心脏，因此所述叶片2仅需要对血液施加很小的推动力即可以推动其流动，所述驱动装置3的效率高、耗能小，从而也降低了所述右心辅助装置的能耗。Furthermore, the shape of the "√"-type flow channel of the right-heart assist device in this embodiment is similar to the blood flow trajectory at the right ventricle of the healthy heart. Preferably, the flow trajectory in the right-heart assist device can be reached. Consistent with the blood flow trajectory at the right ventricle of a healthy heart. At this time, the flow of the patient's blood from the right atrium to the inflowing pulmonary artery is the shortest, and the flow trajectory is closest to the healthy heart, so the blade 2 only needs to exert a small pushing force on the blood to push the flow thereof, the driving device 3 The efficiency is high and the energy consumption is small, thereby also reducing the energy consumption of the right-heart assist device.
应当理解的，本实施例中，所述第一垂线111与所述第二垂线121之间相交且形成角α，因此所述第一管道1的所述流入部11和所述流出部12大致处于同一平面，体积小巧，容易置入右心室。同时，在现有技术中，血液在被离心泵加压的过程中，通常由垂直的中心流道冲向水平的边缘流道，流程长、血液在流动过程中不断换向且方向不共面，因此能量损耗极大，离心泵功耗大。而在本实施例中，患者血液在所述第一管道1内流动的过程中，血液的流动方向始终是处于相同平面的，且流动路径简短。因此相较于现有技术，本实施例所述右心辅助装置的所述第一管道1的形状使得所述驱动装置3的效率高、能耗小，也即降低了所述右心辅助装置的能耗。所述“中心垂线”是指位于指定平面中心且垂直于指定平面的线，例如所述第一垂线111是指位于所述流入端面110中心且垂直于所述流入端面110的线，所述第二垂线121是指位于所述流出端面120中心且垂直于所述流出端面120的线。It should be understood that, in this embodiment, the first vertical line 111 and the second vertical line 121 intersect and form an angle α, so the inflow portion 11 and the outflow portion of the first duct 1 12 is roughly in the same plane, small in size, easy to put into the right ventricle. At the same time, in the prior art, during the process of being pressurized by the centrifugal pump, the blood is usually rushed to the horizontal edge flow channel by the vertical central flow channel, and the flow is long, the blood is continuously reversed during the flow, and the direction is not coplanar. Therefore, the energy loss is extremely large, and the centrifugal pump consumes a large amount of power. In the present embodiment, however, during the flow of the patient's blood in the first conduit 1, the flow direction of the blood is always in the same plane, and the flow path is short. Therefore, compared with the prior art, the shape of the first duct 1 of the right-heart assist device of the embodiment makes the driving device 3 have high efficiency and low energy consumption, that is, the right-heart assist device is reduced. Energy consumption. The “center vertical line” refers to a line located at the center of the designated plane and perpendicular to the designated plane. For example, the first vertical line 111 refers to a line located at the center of the inflow end surface 110 and perpendicular to the inflow end surface 110. The second vertical line 121 refers to a line located at the center of the outflow end surface 120 and perpendicular to the outflow end surface 120.
进一步地，请一并参阅图2和图8，所述α优选45°、60°(如图2所示)、75°、90°(如图8所示)，特别是α＝90°时，所述第一管道1内流体的阻力最小。Further, please refer to FIG. 2 and FIG. 8 together, wherein α is preferably 45°, 60° (as shown in FIG. 2 ), 75°, 90° (shown in FIG. 8 ), especially when α=90°. The resistance of the fluid in the first conduit 1 is the smallest.
举例而言，请一并参阅图1至图3，所述第一管道1的所述流入部11包括邻近所述流入端面110的一小段圆管部分和连接至流出部12的扁管部分，流出部12呈圆管形状，也即所述第一管道1的管道形状自所述流入端面110至流出端面120呈现如下变化：圆管——扁管——圆管，且所述扁管的流通面积并不要求恒定不变，为了使所述第一管道1内的流体所受阻力最小，且不产生涡流区，上述管道的形状变化均为平缓过渡。所述流入部11的圆管部分是为方便所述流入端面110连接至三尖瓣环；所述流入部11的扁管部分是为了减小所述第一管道1在垂直于所述流出端面120的方向上的尺寸，也即减小所 述第一管道1的体积，以为其他部件(例如驱动装置3)提供放置空间，使整个所述右心辅助装置的部件放置位置合理、紧凑，减小所述右心辅助装置的体积。当然，所述第一管道1的管道形状可以依据具体应用环境的需求进行设计和变换，并不限于上述实施例所描述的形状。For example, referring to FIG. 1 to FIG. 3, the inflow portion 11 of the first duct 1 includes a small section of a circular tube adjacent to the inflow end surface 110 and a flat tube portion connected to the outflow portion 12, The outflow portion 12 has a circular tube shape, that is, the shape of the pipe of the first pipe 1 changes from the inflow end surface 110 to the outflow end surface 120 as follows: a circular tube - a flat tube - a round tube, and the flat tube The flow area is not required to be constant. In order to minimize the resistance of the fluid in the first pipe 1, and the vortex zone is not generated, the shape change of the pipe is a gentle transition. The round tube portion of the inflow portion 11 is for facilitating connection of the inflow end surface 110 to the tricuspid annulus; the flat tube portion of the inflow portion 11 is for reducing the first duct 1 perpendicular to the outflow end surface The size in the direction of 120, that is, the reduction The volume of the first duct 1 is provided to provide a space for other components (for example, the driving device 3) so that the components of the right heart assisting device are placed in a reasonable and compact position, and the volume of the right-center assisting device is reduced. Of course, the shape of the pipe of the first pipe 1 can be designed and changed according to the requirements of the specific application environment, and is not limited to the shape described in the above embodiments.
同时，请一并参阅图1和图2，在本实施例中，所述叶片2与所述驱动装置3分别设置在所述底壁122的两侧，也即所述底壁122完全分隔开所述驱动装置3与所述叶片2，所述驱动装置3无线驱动所述叶片2转动。在现有技术中，关于无线驱动已经有较多实施方式，例如电磁驱动等，本实施例参考可实现的无线驱动方式进行设计即可，此处不再累述。At the same time, please refer to FIG. 1 and FIG. 2 together. In this embodiment, the blade 2 and the driving device 3 are respectively disposed on two sides of the bottom wall 122, that is, the bottom wall 122 is completely separated. The drive device 3 and the blade 2 are opened, and the drive device 3 wirelessly drives the blade 2 to rotate. In the prior art, there are many implementations of the wireless driving, such as electromagnetic driving, etc., and the present embodiment can be designed with reference to the achievable wireless driving mode, and is not described here.
进一步地，请一并参阅图1和图2，所述第一管道1的所述流出部12包括连接端面123，所述连接端面123连接所述流入部11。在所述流出端面120的垂直方向上，所述连接端面123的长度为第一长度L1，所述流出部12的长度为第二长度L2，所述第二长度L2大于等于二倍的所述第一长度L1，使得所述第一管道1内的流体在所述流出部12内被充分加压。应当理解的是，本发明实施例所述“连接端面123”可理解为所述流出部12的流入口所在的平面。在本发明描述中，将位于所述流入部11与所述流出部12的衔接区域的多个平面中的、流通面积最小的面定义为所述连接端面123。Further, referring to FIG. 1 and FIG. 2 together, the outflow portion 12 of the first duct 1 includes a connecting end surface 123, and the connecting end surface 123 connects the inflow portion 11. In the vertical direction of the outflow end surface 120, the length of the connecting end surface 123 is a first length L1, the length of the outflow portion 12 is a second length L2, and the second length L2 is greater than or equal to two times The first length L1 causes the fluid in the first conduit 1 to be sufficiently pressurized within the outflow portion 12. It should be understood that the "connection end face 123" in the embodiment of the present invention can be understood as the plane in which the flow inlet of the outflow portion 12 is located. In the description of the present invention, the surface having the smallest flow area among the plurality of planes of the joining portion of the inflow portion 11 and the outflow portion 12 is defined as the connecting end surface 123.
进一步地，请一并参阅图1和图2，所述叶片2在所述流出端面120的垂直方向上的长度为第三长度L3，所述第三长度L3大于等于二倍的所述第一长度L1并且小于所述第二长度L2，使得所述叶片2具有足够长的推进区域。优选的，所述第三长度L3大于等于三分之二的所述第二长度L2，也即所述流出部12的长度仅需要略大于或者等于所述叶片2的长度即可。Further, referring to FIG. 1 and FIG. 2, the length of the blade 2 in the vertical direction of the outflow end surface 120 is a third length L3, and the third length L3 is greater than or equal to twice the first The length L1 is smaller than the second length L2 such that the blade 2 has a sufficiently long advancement area. Preferably, the third length L3 is greater than or equal to two-thirds of the second length L2, that is, the length of the outflow portion 12 only needs to be slightly greater than or equal to the length of the blade 2.
进一步地，请一并参阅图1、图2和图4，所述叶片2包括靠近所述底壁122的第一端21，所述第一端21与所述底壁122之间的距离为第四长度L4，所述第四长度L4小于等于所述第一长度L1。也即所述第一端21距离所述底壁122的距离很小，从而能够降低所述驱动装置3的能耗，最佳的，所述驱动装置3与所述叶片2均紧靠所述底壁122设置。此时，所述第一管道1内的血液自所述流入部11直接进入所述叶片2的推进区域(叶片2旋转区域均为其推进区域)，减少了所述流体的流程，降低了所述流体阻力，所述驱动装置3 能耗降低，所述右心辅助装置的效率升高。Further, referring to FIG. 1 , FIG. 2 and FIG. 4 , the blade 2 includes a first end 21 adjacent to the bottom wall 122 , and a distance between the first end 21 and the bottom wall 122 is The fourth length L4 is less than or equal to the first length L1. That is, the distance between the first end 21 and the bottom wall 122 is small, so that the energy consumption of the driving device 3 can be reduced. Preferably, the driving device 3 and the blade 2 are both close to the The bottom wall 122 is disposed. At this time, the blood in the first duct 1 directly enters the propulsion region of the vane 2 from the inflow portion 11 (the rotation region of the vane 2 is its propulsion region), which reduces the flow of the fluid and reduces the Fluid resistance, the driving device 3 The energy consumption is reduced and the efficiency of the right heart assist device is increased.
进一步地，请一并参阅图1和图2，所述流出端面120的垂直方向上，所述流入部11的长度为第五长度L5，所述第五长度L5大于所述第一长度L1。也即在垂直于所述流出端面120的方向上，所述第一管道1的尺寸有长——短——长的变化，所述流入部11与所述流出部12的衔接区形成了所述第一管道1的凹陷区，所述凹陷区用于容纳室上嵴结构，从而使所述第一管道1更加符合患者右心的生理解剖结构。再者，在如图1所示视图平面的垂直方向上，所述第一管道1的各个部分的尺寸一致，也即如图3所示结构。此时，血液自所述流入端面110流至所述连接端面123的过程中，流通面积减小、流速加快。Further, referring to FIG. 1 and FIG. 2 together, in the vertical direction of the outflow end surface 120, the length of the inflow portion 11 is a fifth length L5, and the fifth length L5 is greater than the first length L1. That is, in the direction perpendicular to the outflow end surface 120, the size of the first duct 1 has a long-short-long change, and the junction area of the inflow portion 11 and the outflow portion 12 forms a joint. The recessed area of the first duct 1 is used to accommodate the supracondylar structure of the chamber, so that the first duct 1 is more in line with the physiological anatomy of the right heart of the patient. Further, in the vertical direction of the plane of view as shown in FIG. 1, the respective portions of the first duct 1 have the same size, that is, the structure as shown in FIG. At this time, in the process in which blood flows from the inflow end surface 110 to the connection end surface 123, the flow area is reduced and the flow velocity is increased.
进一步地，请一并参阅图1和图2，所述流入端面110的外径长度为第一外径D1，所述流出端面120的外径长度为第二直径D2，所述第一直径D1大于等于所述第二直径D2，以使所述第一管道1能够顺利安装至患者的右心室内。Further, please refer to FIG. 1 and FIG. 2 together, the outer diameter of the inflow end surface 110 is a first outer diameter D1, and the outer diameter of the outflow end surface 120 is a second diameter D2, the first diameter D1 The second diameter D2 is greater than or equal to enable the first duct 1 to be smoothly installed into the right ventricle of the patient.
作为本发明的一种优选实施例，请一并参阅图1、图2以及图5，所述右心辅助装置还包括第二管道4，所述第二管道4可拆连接至所述流出部12，也即所述第二管道4的一端连接至所述流出端面120。在本实施例中，由于设置有所述第二管道4，因此可以使所述第二管道4的另一端穿过患者的肺动脉瓣环进入肺动脉，以使血液自所述第一管道1进入患者肺动脉。在本实施例中，所述流出部12的长度可以很短，所述流出端面120至肺动脉瓣环的距离由所述第二管道4补齐，使得所述右心辅助装置可以适用于多种不同的应用环境，提高了通用性。As a preferred embodiment of the present invention, please refer to FIG. 1, FIG. 2 and FIG. 5 together, the right-hand auxiliary device further includes a second duct 4, and the second duct 4 is detachably connected to the outflow portion. 12, that is, one end of the second duct 4 is connected to the outflow end surface 120. In the present embodiment, since the second duct 4 is provided, the other end of the second duct 4 can be passed through the pulmonary valve annulus of the patient into the pulmonary artery to allow blood to enter the patient from the first duct 1 Pulmonary artery. In the present embodiment, the length of the outflow portion 12 may be short, and the distance from the outflow end surface 120 to the pulmonary valve annulus is filled by the second duct 4, so that the right heart assisting device can be applied to various types. Different application environments improve versatility.
在本实施例中，所述第二管道4的一端可拆连接至所述第一管道1的流出端面120，所述可拆连接是指用于连接的连接件可拆卸，常用的例如键连接、销连接、螺纹连接和卡箍连接等。举例而言，所述第二管道4包括连接部和流通部，所述连接部可拆连接至所述流出部12，所述连接部的材质采用硬质材料，以方便实现连接。如图5所示，所述流出部12的外壁邻近所述流出端面120的位置处(也即所述连接部)设置有凹槽1201，所述第二管道4的一端的内壁设置有凸起41，所述凸起41卡入所述凹槽1201形成连接件，并在所述连接件外套设紧固环42，使所述第二管道4固定至所述第一管道1。应当注意 的是，所述流通部的流通面积并不是固定的，可以依据患者的身体情况进行灵活设计。例如，所述流通部的流通面积可以小于所述连接部的流通面积(也即小于所述流出部12的流通面积)，所述流通部连接所述连接部的位置处设置有收敛结构。In this embodiment, one end of the second duct 4 is detachably connected to the outflow end surface 120 of the first duct 1, and the detachable connection refers to a detachable connecting member for connection, such as a key connection. , pin connections, threaded connections and clamp connections. For example, the second duct 4 includes a connecting portion and a circulation portion, and the connecting portion is detachably connected to the outflow portion 12, and the connecting portion is made of a hard material to facilitate connection. As shown in FIG. 5, a groove 1201 is disposed at a position of the outer wall of the outflow portion 12 adjacent to the outflow end surface 120 (that is, the connecting portion), and an inner wall of one end of the second pipe 4 is provided with a protrusion. 41. The protrusion 41 is snapped into the groove 1201 to form a connecting member, and a fastening ring 42 is jacketed on the connecting member to fix the second pipe 4 to the first pipe 1. Should pay attention The flow area of the circulation portion is not fixed and can be flexibly designed according to the physical condition of the patient. For example, the flow area of the circulation portion may be smaller than the flow area of the connection portion (that is, smaller than the flow area of the outflow portion 12), and the flow portion may be provided with a convergent structure at a position where the connection portion is connected.
进一步地，请一并参阅图1至图3，所述流入部11开设有旁通流入口112，所述旁通流入口112与所述流入部11的流入端面110间隔设置，也即所述旁通流入口112与所述流入端面110相互独立，以使所述旁通流入口112成为另一个所述流入部11的入口。当所述右心辅助装置置于所述右心室内时，所述右心室内的血液在负压的作用下，通过所述旁通流入口112流入所述流入部11，从而避免右心室内血液淤积而导致右心室膨胀。应当理解的，所述旁通流入口112可以设置有多个，且其位置可以依据患者的心脏情况进行调节。例如，所述旁通流入口112可以开设在所述流入部11远离所述流出部12的一面。Further, referring to FIG. 1 to FIG. 3 , the inflow portion 11 is provided with a bypass flow inlet 112 , and the bypass flow inlet 112 is spaced apart from the inflow end surface 110 of the inflow portion 11 , that is, the The bypass inflow port 112 and the inflow end surface 110 are independent of each other such that the bypass inflow port 112 becomes an inlet of the other inflow portion 11. When the right heart assist device is placed in the right ventricle, the blood in the right ventricle flows into the inflow portion 11 through the bypass flow inlet 112 under the action of a negative pressure, thereby avoiding the right ventricle Blood stasis causes the right ventricle to swell. It should be understood that the bypass flow inlet 112 may be provided in plurality and its position may be adjusted depending on the heart condition of the patient. For example, the bypass flow inlet 112 may be opened on a side of the inflow portion 11 away from the outflow portion 12.
进一步地，请一并参阅图1至图3，所述流入部11的靠向所述流入端面110的一端(例如所述流入部11的圆管部分)设置有缝合环113，所述缝合环113的内圈缝合或者卡套在所述流入部11上，所述缝合环113的外圈用以缝合至心脏的三尖瓣环，从而使所述第一管道1的所述流入端面110固定至心脏。所述缝合环113采用具有生物相容性、不可吸收的编织材料，例如可用于缝合的涤纶。举例而言，请一并参阅图1至图3，所述流入部11的外壁靠近所述流入端面110的位置处设置有一凹陷区1130，所述缝合环113卡合在所述凹陷区1130内以实现与所述流入部11的固定。Further, referring to FIG. 1 to FIG. 3, an end of the inflow portion 11 facing the inflow end surface 110 (for example, a portion of the round tube of the inflow portion 11) is provided with a sewing ring 113, the sewing ring The inner ring of 113 is stitched or ferred on the inflow portion 11, and the outer ring of the sewing ring 113 is used for sewing to the tricuspid annulus of the heart, thereby fixing the inflow end surface 110 of the first duct 1 To the heart. The sewing ring 113 employs a biocompatible, non-absorbable woven material, such as polyester that can be used for stitching. For example, please refer to FIG. 1 to FIG. 3 , a recessed area 1130 is disposed at an outer wall of the inflow portion 11 near the inflow end surface 110 , and the sewing ring 113 is engaged in the recessed area 1130 . The fixing to the inflow portion 11 is achieved.
进一步地，请参阅图1，为了使所述右心辅助装置内的流体沿最佳流动轨迹流动，设置所述第一管道1的材质均为硬质材料，也即所述第一管道1在所述流体的压力下不发生形变或者很微小的形变，从而使流体能够沿着预定的流道轨迹流动，以降低所述右心辅助装置的能耗。优选的，所述第一管道1可采用轻质钛金属，其强度大，密度小，硬度大，熔点高，抗腐蚀性很强。所述第二管道4的材质可以是柔性材质(例如人工血管)，也可以是刚性材质(例如钛金属)。Further, referring to FIG. 1 , in order to flow the fluid in the right-heart assist device along the optimal flow trajectory, the material of the first pipe 1 is set to be a hard material, that is, the first pipe 1 is No deformation or very slight deformation occurs under the pressure of the fluid, thereby enabling fluid to flow along a predetermined flow path trajectory to reduce energy consumption of the right heart assist device. Preferably, the first pipe 1 can be made of lightweight titanium, which has high strength, small density, high hardness, high melting point and strong corrosion resistance. The material of the second pipe 4 may be a flexible material (for example, an artificial blood vessel) or a rigid material (for example, titanium metal).
进一步地，可以在所述第一管道1的表面进行涂层，所述涂层采用抗血栓物质，以减少血栓的形成。优选的，所述涂层可采用聚四氟乙烯涂层。 Further, a coating may be applied on the surface of the first conduit 1, which uses an antithrombotic substance to reduce the formation of blood clots. Preferably, the coating may be coated with a polytetrafluoroethylene.
进一步地，请一并参阅图1、图2以及图6，所述右心辅助装置还包括设置在所述流出部12内的支撑架200和转轴20，所述支撑架200固定在所述流出部12的内壁，所述支撑架200包括相对设置的第一支架201和第二支架202，所述叶片2围绕所述转轴20设置，所述转轴20的轴线203垂直于所述流出端面120(优选的，所述轴线203与所述第二垂线121共线)，所述转轴20卡设在所述第一支架201与所述第二支架202之间。Further, referring to FIG. 1 , FIG. 2 and FIG. 6 , the right-heart assist device further includes a support frame 200 and a rotating shaft 20 disposed in the outflow portion 12 , and the support frame 200 is fixed at the outflow. An inner wall of the portion 12, the support frame 200 includes a first bracket 201 and a second bracket 202 disposed opposite to each other, the blade 2 is disposed around the rotating shaft 20, and an axis 203 of the rotating shaft 20 is perpendicular to the outflow end surface 120 ( Preferably, the axis 203 is collinear with the second perpendicular line 121, and the rotating shaft 20 is interposed between the first bracket 201 and the second bracket 202.
在本实施例中，所述转轴20的轴线203垂直于所述流出端面120，也即所述叶片2的推进力方向垂直于所述流出端面120，所述第一管道1内的流体在很小的叶片2的推进力下即能够顺利地自所述流出端面120喷射出，使得所述右心辅助装置能耗小、更节能。当然，可以对所述叶片2的形状进行合理设计，使其具有更大的推进力，同时减小血流对所述流出部12侧壁的冲击，以减小损耗。In this embodiment, the axis 203 of the rotating shaft 20 is perpendicular to the outflow end surface 120, that is, the direction of the propulsive force of the vane 2 is perpendicular to the outflow end surface 120, and the fluid in the first duct 1 is very The small blade 2 can be smoothly ejected from the outflow end surface 120 under the propulsive force, so that the right-heart auxiliary device consumes less energy and is more energy-saving. Of course, the shape of the blade 2 can be rationally designed to have greater propulsive force while reducing the impact of blood flow on the side wall of the outflow portion 12 to reduce losses.
本实施例中，请一并参阅图1、图6以及图7，所述第一支架201包括第一环部2011和第一辐条2012，所述第一辐条2012设置在所述第一环部2011的内圆的任一条直径的位置处，所述第一辐条2012的中部设置有第一凹槽2013；所述第二支架202包括第二环部2021和第二辐条2022，所述第二辐条2022设置在所述第二环部2021的内圆的任一条直径的位置处，所述第二辐条2022的中部设置有第二凹槽2023。所述转轴20的两端分别形成有第一凸起2031和第二凸起2032，所述第一凸起2031和所述第二凸起2032分别卡在所述第一凹槽2013和所述第二凹槽2023内。因此，所述转轴20卡设在所述第一支架201和所述第二支架202之间，避免了所述转轴20和所述叶片2来回摆动和上下位移。所述支撑架200还包括定位支架204，所述定位支架204连接所述第一支架201和所述第二支架202，用以固定所述第一支架201和所述第二支架202之间的间距。进一步地，所述第一凹槽2013与所述第二凹槽2023之间的最大间距(例如两个凹槽底部之间)大于所述转轴20的总长度，所述第一凹槽2013与所述第二凹槽2023之间的最小间距(例如两个凹槽的边缘之间)小于所述转轴20的总长度，从而使所述转轴2032具有微小的相对移动空间，使得所述转轴20和所述叶片2在转动或者运行过程中具有一定的自调节空间，有利于所述转轴20和所述叶片2根据所述第一管道1内流体的流动情 况进行调整，具有缓冲和优化能力。In this embodiment, referring to FIG. 1 , FIG. 6 and FIG. 7 , the first bracket 201 includes a first ring portion 2011 and a first spoke 2012, and the first spoke 2012 is disposed at the first ring portion. At a position of any diameter of the inner circle of 2011, a first groove 2013 is provided in a middle portion of the first spoke 2012; the second bracket 202 includes a second ring portion 2021 and a second spoke 2022, the second The spokes 2022 are disposed at any one of the diameters of the inner circumference of the second ring portion 2021, and the second portion of the second spokes 2022 is provided with a second groove 2023. Two ends of the rotating shaft 20 are respectively formed with a first protrusion 2031 and a second protrusion 2032, and the first protrusion 2031 and the second protrusion 2032 are respectively stuck in the first groove 2013 and the The second groove 2023 is inside. Therefore, the rotating shaft 20 is locked between the first bracket 201 and the second bracket 202, and the rotating shaft 20 and the blade 2 are prevented from swinging back and forth and up and down. The support frame 200 further includes a positioning bracket 204, and the positioning bracket 204 connects the first bracket 201 and the second bracket 202 for fixing between the first bracket 201 and the second bracket 202. spacing. Further, a maximum distance between the first groove 2013 and the second groove 2023 (for example, between the bottoms of the two grooves) is greater than a total length of the rotating shaft 20, the first groove 2013 and The minimum spacing between the second grooves 2023 (for example, between the edges of the two grooves) is smaller than the total length of the rotating shaft 20, so that the rotating shaft 2032 has a slight relative movement space, so that the rotating shaft 20 And the blade 2 has a certain self-adjusting space during rotation or operation, which facilitates the flow of the rotating shaft 20 and the blade 2 according to the fluid in the first pipe 1 Condition adjustments with buffering and optimization capabilities.
在本实施例中，所述叶片2及所述转轴20均采用硬质材料，优选轻质钛金属材料。所述转轴20中空设计以减轻质量，降低所述驱动装置3的能耗。In this embodiment, the blade 2 and the rotating shaft 20 are both made of a hard material, preferably a lightweight titanium material. The rotating shaft 20 is hollow in design to reduce the quality and reduce the energy consumption of the driving device 3.
进一步地，请一并参阅图1和图4，所述右心辅助装置的所述驱动装置3包括电机5和控制器6，所述电机5用以驱动所述叶片2转动；所述控制器6电连接所述电机5，用以调节所述电机5的输出功率。在本实施例中，所述电机5与所述叶片2分别设置在所述底壁122的两侧，也即所述底壁122完全分隔开所述电机5与所述叶片2，所述电机5无线驱动所述叶片2转动。在现有技术中，关于无线驱动已经有较多实施方式，例如电磁驱动等，本实施例参考可实现的无线驱动方式进行设计即可，此处不再累述。应当注意的是，在本实施例中，所述电机5与所述叶片2之间的间距应该尽可能的小，以降低所述电机5的能耗。优选的，所述电机5与所述叶片2均紧靠所述底壁122设置。Further, referring to FIG. 1 and FIG. 4, the driving device 3 of the right-heart assist device includes a motor 5 and a controller 6 for driving the blade 2 to rotate; the controller 6 electrically connecting the motor 5 for adjusting the output power of the motor 5. In this embodiment, the motor 5 and the blade 2 are respectively disposed on two sides of the bottom wall 122, that is, the bottom wall 122 completely separates the motor 5 from the blade 2, The motor 5 wirelessly drives the blade 2 to rotate. In the prior art, there are many implementations of the wireless driving, such as electromagnetic driving, etc., and the present embodiment can be designed with reference to the achievable wireless driving mode, and is not described here. It should be noted that in the present embodiment, the spacing between the motor 5 and the blade 2 should be as small as possible to reduce the energy consumption of the motor 5. Preferably, the motor 5 and the blade 2 are both disposed adjacent to the bottom wall 122.
进一步地，请一并参阅图1和图4，所述右心辅助装置还包括隔离壁51，所述隔离壁51固定至所述底壁122背离所述流出端面120的一侧，并与所述底壁122共同形成隔离腔50，所述电机5置于所述隔离腔50内。优选的，所述控制器6也置于所述隔离腔50内。所述隔离腔50为密封的腔室，当所述右心辅助装置安装至人体时，所述隔离壁51同样内置于右心室内，所述隔离壁51将所述电机5和所述控制器6与心脏内的血液相隔离，提高了所述右心辅助装置的生物相容性，同时保障了所述电机5与所述控制器6具有良好的使用环境、提高其使用寿命。应当注意的是，在本发明中，所述第一管道1与所述隔离壁51在设计时均采用圆弧或斜坡等过渡式的设计，避免使用直角或出现突兀的凸起部，以防止形成血栓。Further, referring to FIG. 1 and FIG. 4 together, the right-hand auxiliary device further includes a partition wall 51 fixed to a side of the bottom wall 122 facing away from the outflow end surface 120, and The bottom wall 122 collectively forms an isolation chamber 50 in which the motor 5 is placed. Preferably, the controller 6 is also placed within the isolation chamber 50. The isolation chamber 50 is a sealed chamber. When the right-heart assist device is mounted to a human body, the partition wall 51 is also built in the right ventricle, and the partition wall 51 connects the motor 5 and the controller. 6 is isolated from the blood in the heart, which improves the biocompatibility of the right heart assist device, and at the same time ensures that the motor 5 and the controller 6 have a good use environment and improve the service life thereof. It should be noted that, in the present invention, the first pipe 1 and the partition wall 51 are designed to adopt a transitional design such as a circular arc or a slope, so as to avoid the use of a right angle or a protruding protrusion to prevent Form a thrombus.
进一步地，请一并参阅图1和图4，所述右心辅助装置还包括第一电池组件71和第二电池组件72。所述第一电池组件71电连接所述电机5，用以为所述电机5提供电能。所述第二电池组件72对所述第一电池组件71进行无线充电。Further, referring to FIG. 1 and FIG. 4 together, the right-heart assist device further includes a first battery component 71 and a second battery component 72. The first battery assembly 71 is electrically connected to the motor 5 for supplying electric power to the motor 5. The second battery component 72 wirelessly charges the first battery component 71.
在本实施例中，所述第一电池组件71包括电连接的第一蓄电池711与第一充电接口712，所述第一蓄电池711电连接所述电机5。所述第二电池组件72包括电连接的第二蓄电池721和第二充电接口722。所述第一充电接口712 与所述第二充电接口722之间无线连接，使所述第二蓄电池721内的电能转移至所述第一蓄电池711。In the present embodiment, the first battery component 71 includes a first battery 711 electrically connected to the first charging interface 712, and the first battery 711 is electrically connected to the motor 5. The second battery assembly 72 includes a second battery 721 and a second charging interface 722 that are electrically connected. The first charging interface 712 Wirelessly connecting with the second charging interface 722 to transfer electrical energy in the second battery 721 to the first battery 711.
当所述右心辅助装置安装至人体时，所述第一电池组件71置于体内、所述第二电池组件72置于体外。所述第一电池组件71通过电线连接至电机5，所述第一电池组件71置于心脏外，埋设在皮下即可(腹部为佳)。所述第二电池组件72设置在一个腰带上，使用者佩戴腰带后，所述第二电池组件72正对所述第一电池组件71。所述第二电池组件72对所述第二电池组件72进行无线充电，所述无线充电参考可实现的无线充电方式即可。When the right heart assist device is mounted to a human body, the first battery assembly 71 is placed in the body and the second battery assembly 72 is placed outside the body. The first battery assembly 71 is connected to the motor 5 by wires, and the first battery assembly 71 is placed outside the heart and buried under the skin (bath is preferred). The second battery assembly 72 is disposed on a waist belt, and the second battery assembly 72 faces the first battery assembly 71 after the user wears the belt. The second battery component 72 wirelessly charges the second battery component 72, and the wireless charging reference may be implemented by a wireless charging mode.
进一步地，请一并参阅图1和图9，所述的右心辅助装置还包括传感装置100和信号处理装置101。所述传感装置100用以检测所述第一管道1(与所述第二管道4)内的流体参数，并形成第一信号S1传送至所述信号处理装置101。所述信号处理装置101用以接收、存储以及处理所述第一信号S1，并形成第二信号S2传送至所述控制器6，使所述控制器6调节所述电机5的输出功率。应当理解是的，本实施例所述流体参数包括但不限于压力、粘度、流速、温度、密度等。所述传感装置100可以依据需求，同时设置有多个传感器以检测多个不同的参数，或者在所述第一管道1(与所述第二管道4)的多个位置同时安装多个传感器以检测多个不同位置的同一个参数。进一步地，所述传感装置100也可以同时检测所述叶片2和/或所述电机5的工作参数，例如转速、功率等，同时传送相关数据至所述信号处理装置101，以获得更为理想的第二信号S2，从而提高所述电机5的工作效率、降低所述右心辅助装置的能耗。当然，所述传感装置100也可以依据具体需求检测其他参数。Further, referring to FIG. 1 and FIG. 9 together, the right-heart assist device further includes a sensing device 100 and a signal processing device 101. The sensing device 100 is configured to detect a fluid parameter in the first conduit 1 (and the second conduit 4) and form a first signal S1 to be transmitted to the signal processing device 101. The signal processing device 101 is configured to receive, store, and process the first signal S1, and form a second signal S2 to be transmitted to the controller 6, so that the controller 6 adjusts the output power of the motor 5. It should be understood that the fluid parameters described in this embodiment include, but are not limited to, pressure, viscosity, flow rate, temperature, density, and the like. The sensing device 100 may be provided with multiple sensors at the same time to detect a plurality of different parameters, or multiple sensors installed simultaneously in multiple positions of the first pipe 1 (with the second pipe 4) To detect the same parameter at multiple different locations. Further, the sensing device 100 can simultaneously detect the operating parameters of the blade 2 and/or the motor 5, such as the rotational speed, power, etc., while transmitting relevant data to the signal processing device 101 to obtain more The ideal second signal S2 increases the operating efficiency of the motor 5 and reduces the energy consumption of the right-heart assist device. Of course, the sensing device 100 can also detect other parameters according to specific needs.
进一步地，请一并参阅图1、图4和图9，所述右心辅助装置的所述信号处理装置101包括芯片81和处理器82。所述芯片81传送原始数据S3至所述处理器82。所述处理器82接收所述原始数据S3、形成反馈数据S4，并传送所述反馈数据S4至所述芯片81。所述处理器82包括显示屏821，所述显示屏821用以显示所述原始数据S3和/或所述反馈数据S4。Further, referring to FIG. 1 , FIG. 4 and FIG. 9 together, the signal processing device 101 of the right-heart assist device includes a chip 81 and a processor 82. The chip 81 transmits raw data S3 to the processor 82. The processor 82 receives the raw data S3, forms feedback data S4, and transmits the feedback data S4 to the chip 81. The processor 82 includes a display screen 821 for displaying the raw data S3 and/or the feedback data S4.
在本实施例中，所述芯片81和所述处理器82均具有信号处理能力，而所述处理器82更具有修改所述芯片81内部数据/程序的能力，以使所述信号处理装置101依据使用者的身体状态变化(静息或运动状态、血管阻力变化等) 进行合理调整，使所述右心辅助装置符合患者实时的生理状态，同时还可延长电池续航时间、延长所述右心辅助装置的使用寿命等。同时，本实施例中所述显示屏821更是能够直观地表达出使用者的身体情况和所述右心辅助装置的工作状态，有助于诊断和治疗使用者。In this embodiment, the chip 81 and the processor 82 both have signal processing capabilities, and the processor 82 further has the ability to modify the internal data/program of the chip 81 to cause the signal processing device 101. According to the user's physical state changes (rest or exercise state, vascular resistance changes, etc.) Reasonable adjustment is made to make the right heart auxiliary device conform to the real-time physiological state of the patient, and at the same time, the battery life time can be extended, and the service life of the right heart auxiliary device can be prolonged. In the meantime, the display screen 821 in the embodiment can intuitively express the physical condition of the user and the working state of the right-heart assist device, and is useful for diagnosing and treating the user.
当所述右心辅助装置安装至人体时，所述控制器6和所述芯片81置于体内。所述芯片81通过数据线连接至所述控制器6，所述第一芯片81置于心脏外，埋设在皮下即可(腹部为佳)。所述处理器82可以集成设置在设置有第二电池组件72的腰带上，使用者佩戴腰带后，所述处理器82正对所述芯片81。所述处理器82与所述芯片81双向无线传送数据。When the right heart assist device is mounted to a human body, the controller 6 and the chip 81 are placed in the body. The chip 81 is connected to the controller 6 through a data line, and the first chip 81 is placed outside the heart and buried under the skin (bath is preferred). The processor 82 can be integrally disposed on a belt provided with a second battery assembly 72, and the processor 82 faces the chip 81 after the user wears the belt. The processor 82 wirelessly transmits data to the chip 81 in both directions.
同时，所述显示屏821可以设置在所述腰带的外表面，使用者可以直接观看所述显示屏821的显示图像。Meanwhile, the display screen 821 may be disposed on an outer surface of the waist belt, and the user may directly view the display image of the display screen 821.
以上对本发明实施例进行了详细介绍，本文中应用了具体个例对本发明的原理及实施方式进行了阐述，以上实施例的说明只是用于帮助理解本发明的方法及其核心思想；同时，对于本领域的一般技术人员，依据本发明的思想，在具体实施方式及应用范围上均会有改变之处，综上所述，本说明书内容不应理解为对本发明的限制。 The embodiments of the present invention have been described in detail above, and the principles and implementations of the present invention are described in detail herein. The description of the above embodiments is only for helping to understand the method of the present invention and its core ideas; It should be understood by those skilled in the art that the present invention is not limited by the scope of the present invention.

Claims (17)

  1. 一种右心辅助装置，其特征在于，包括：A right heart assisting device, comprising:
    第一管道，包括彼此连通的流入部和流出部，所述流入部的流入端面的中心垂线为第一垂线，所述流出部的流出端面的中心垂线为第二垂线，所述第一垂线与所述第二垂线相交且形成45°至100°的角；The first duct includes an inflow portion and an outflow portion that communicate with each other, a central perpendicular of the inflow end surface of the inflow portion is a first vertical line, and a center perpendicular of the outflow end surface of the outflow portion is a second perpendicular line. a first perpendicular intersects the second perpendicular and forms an angle of 45° to 100°;
    叶片，转动连接至所述流出部的内部，用以推进所述第一管道内的流体从所述流出端面流出；及a blade rotatably coupled to the interior of the outflow portion for propelling fluid in the first conduit from the outflow end surface; and
    驱动装置，所述驱动装置位于所述流出部的外部，所述流出部包括与所述流出端面相对设置的底壁，所述叶片与所述驱动装置分别位于所述底壁的两侧，所述驱动装置用以驱动所述叶片转动。a driving device, the driving device is located outside the outflow portion, the outflow portion includes a bottom wall disposed opposite to the outflow end surface, and the blade and the driving device are respectively located at two sides of the bottom wall The driving device is used to drive the blades to rotate.
  2. 如权利要求1所述的右心辅助装置，其特征在于，所述流出部包括连接所述流入部的连接端面，在所述流出端面的垂直方向上，所述连接端面的长度为第一长度，所述流出部的长度为第二长度，所述第二长度大于等于二倍的所述第一长度。The right-heart assist device according to claim 1, wherein the outflow portion includes a connecting end surface connecting the inflow portion, and the length of the connecting end surface is a first length in a vertical direction of the outflow end surface The length of the outflow portion is a second length, and the second length is greater than or equal to twice the first length.
  3. 如权利要求2所述的右心辅助装置，其特征在于，所述叶片在所述流出端面的垂直方向上的长度为第三长度，所述第三长度大于等于二倍的所述第一长度并且小于所述第二长度。The right-heart assist device according to claim 2, wherein a length of the blade in a vertical direction of the outflow end surface is a third length, and the third length is greater than or equal to twice the first length And less than the second length.
  4. 如权利要求2所述的右心辅助装置，其特征在于，所述叶片包括靠近所述底壁的第一端，所述第一端与所述底壁之间的距离为第四长度，所述第四长度小于等于所述第一长度。A right-heart assist device according to claim 2, wherein said blade includes a first end adjacent said bottom wall, and a distance between said first end and said bottom wall is a fourth length. The fourth length is less than or equal to the first length.
  5. 如权利要求2所述的右心辅助装置，其特征在于，在所述流出端面的垂直方向上，所述流入部的长度为第五长度，所述第五长度大于所述第一长度。The right-heart assist device according to claim 2, wherein a length of the inflow portion is a fifth length in a vertical direction of the outflow end surface, and the fifth length is greater than the first length.
  6. 如权利要求1所述的右心辅助装置，其特征在于，所述流入端面的外径长度为第一直径，所述流出端面的外径长度为第二直径，所述第一直径大于等于所述第二直径。The right-heart assist device according to claim 1, wherein an outer diameter of the inflow end surface is a first diameter, and an outer diameter of the outer end surface is a second diameter, and the first diameter is greater than or equal to Said second diameter.
  7. 如权利要求1所述的右心辅助装置，其特征在于，所述右心辅助装置还包括第二管道，所述第二管道可拆连接至所述流出部。The right-heart assist device according to claim 1, wherein said right-heart assist device further comprises a second duct, said second duct being detachably coupled to said outflow portion.
  8. 如权利要求7所述的右心辅助装置，其特征在于，所述第二管道包括连 接部，所述连接部可拆连接至所述流出部，所述连接部的材质采用硬质材料。A right-heart assist device according to claim 7, wherein said second conduit comprises The connecting portion is detachably connected to the outflow portion, and the connecting portion is made of a hard material.
  9. 如权利要求1所述的右心辅助装置，其特征在于，所述流入部开设有旁通流入口，所述旁通流入口与所述流入部的流入端面间隔设置。The right-heart assist device according to claim 1, wherein the inflow portion is provided with a bypass flow inlet, and the bypass flow inlet is spaced apart from an inflow end surface of the inflow portion.
  10. 如权利要求1所述的右心辅助装置，其特征在于，所述流入部的靠向所述流入端面的一端设置有缝合环。The right-heart assist device according to claim 1, wherein a stitching ring is provided at one end of the inflow portion that faces the inflow end surface.
  11. 如权利要求1所述的右心辅助装置，其特征在于，所述第一管道的材质为钛金属。The right-heart assist device according to claim 1, wherein the first conduit is made of titanium metal.
  12. 如权利要求1所述的右心辅助装置，其特征在于，所述右心辅助装置还包括设置在所述流出部内的支撑架和转轴，所述支撑架固定在所述流出部的内壁，并且包括相对设置的第一支架和第二支架，所述叶片围绕所述转轴设置，所述转轴的轴线垂直于所述流出端面，所述转轴转动连接在所述第一支架与所述第二支架之间。A right-heart assist device according to claim 1, wherein said right-heart assisting device further comprises a support frame and a rotating shaft provided in said outflow portion, said support frame being fixed to an inner wall of said outflow portion, and a first bracket and a second bracket are disposed, the blades are disposed around the rotating shaft, an axis of the rotating shaft is perpendicular to the outflow end surface, and the rotating shaft is rotatably coupled to the first bracket and the second bracket between.
  13. 如权利要求1所述的右心辅助装置，其特征在于，所述驱动装置包括电机和控制器，所述电机用以驱动所述叶片转动，所述控制器电连接所述电机，用以调节所述电机的输出功率；The right-heart assist device according to claim 1, wherein said driving device comprises a motor and a controller, said motor for driving said blade to rotate, said controller electrically connecting said motor for adjusting Output power of the motor;
    所述右心辅助装置还包括隔离壁，所述隔离壁固定至所述底壁背离所述流出端面的一侧，并与所述底壁共同形成隔离腔，所述电机位于所述隔离腔的内部。The right-hand auxiliary device further includes a partition wall fixed to a side of the bottom wall facing away from the outflow end surface, and forming an isolation cavity together with the bottom wall, wherein the motor is located in the isolation cavity internal.
  14. 如权利要求13所述的右心辅助装置，其特征在于，所述右心辅助装置还包括第一电池组件和第二电池组件；The right-heart assist device according to claim 13, wherein the right-heart assist device further comprises a first battery component and a second battery component;
    所述第一电池组件电连接所述电机，用以为所述电机提供电能；The first battery component is electrically connected to the motor to provide electrical energy to the motor;
    所述第二电池组件对所述第一电池组件进行无线充电。The second battery component wirelessly charges the first battery component.
  15. 如权利要求14所述的右心辅助装置，其特征在于，所述第一电池组件包括电连接的第一蓄电池和第一充电接口，所述第一蓄电池电连接所述电机；The right-heart assist device according to claim 14, wherein said first battery assembly comprises an electrically connected first battery and a first charging interface, said first battery electrically connecting said motor;
    所述第二电池组件包括电连接的第二蓄电池和第二充电接口，所述第二充电接口与所述第一充电接口之间无线连接，使所述第二蓄电池内的电能转移至所述第一蓄电池。The second battery assembly includes an electrically connected second battery and a second charging interface, and the second charging interface is wirelessly connected to the first charging interface to transfer electrical energy in the second battery to the The first battery.
  16. 如权利要求13所述的右心辅助装置，其特征在于，所述右心辅助装 置还包括传感装置和信号处理装置；A right heart assist device according to claim 13 wherein said right heart assisted device The device further includes a sensing device and a signal processing device;
    所述传感装置用以检测所述第一管道内的流体参数，并形成第一信号传送至所述信号处理装置；The sensing device is configured to detect a fluid parameter in the first conduit and form a first signal to be transmitted to the signal processing device;
    所述信号处理装置用以接收、存储以及处理所述第一信号，并形成第二信号传送至所述控制器，使所述控制器调节所述电机的输出功率。The signal processing device is configured to receive, store, and process the first signal and form a second signal to the controller to cause the controller to adjust an output power of the motor.
  17. 如权利要求16所述的右心辅助装置，其特征在于，所述信号处理装置包括芯片和处理器；The right-heart assist device according to claim 16, wherein said signal processing device comprises a chip and a processor;
    所述芯片传送原始数据至所述处理器；The chip transmits raw data to the processor;
    所述处理器接收所述原始数据、形成反馈数据，并传送所述反馈信号至所述芯片；The processor receives the raw data, forms feedback data, and transmits the feedback signal to the chip;
    所述处理器包括显示屏，所述显示屏用以显示所述原始数据和/或所述反馈数据。 The processor includes a display screen for displaying the raw data and/or the feedback data.
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US11724089B2 (en) 2019-09-25 2023-08-15 Shifamed Holdings, Llc Intravascular blood pump systems and methods of use and control thereof

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