WO2018019235A1 - 腔肺辅助循环装置 - Google Patents

腔肺辅助循环装置 Download PDF

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Publication number
WO2018019235A1
WO2018019235A1 PCT/CN2017/094338 CN2017094338W WO2018019235A1 WO 2018019235 A1 WO2018019235 A1 WO 2018019235A1 CN 2017094338 W CN2017094338 W CN 2017094338W WO 2018019235 A1 WO2018019235 A1 WO 2018019235A1
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WO
WIPO (PCT)
Prior art keywords
chamber
cavity
circulation device
blood
assisted circulation
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Application number
PCT/CN2017/094338
Other languages
English (en)
French (fr)
Inventor
袁海云
庄建
陈寄梅
Original Assignee
广东省心血管病研究所
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Publication of WO2018019235A1 publication Critical patent/WO2018019235A1/zh

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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
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • 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
    • A61M60/80—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
    • A61M60/882—Devices powered by the patient, e.g. skeletal muscle powered 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
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/89—Valves
    • A61M60/894—Passive valves, i.e. valves actuated by the blood
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/02—General characteristics of the apparatus characterised by a particular materials
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/04—General characteristics of the apparatus implanted
    • 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
    • A61M2210/10—Trunk
    • A61M2210/1025—Respiratory system
    • A61M2210/1039—Lungs
    • 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 invention relates to the field of medical instruments, in particular to a cavity lung auxiliary circulation device.
  • Fontan surgery and its improved procedures are often used to treat congenital heart malformations leading to functional single ventricular conditions.
  • With the advancement of surgical techniques and the development of postoperative monitoring measures more and more functional single ventricular children survive to adulthood. Because of the prolonged survival of the child, the limitations and long-term complications of the Fontan cycle began to appear, greatly affecting the quality of life of the child.
  • the industry has proposed the concept of dynamic Fontan. In the past few decades, some research has been done on the research of cavity-assisted circulation devices for achieving the dynamic Fontan cycle, but there has been no product in the industry that can meet the needs of clinical use.
  • One of the objects of the embodiments of the present invention is to provide a cavity lung assisted circulation device for achieving normal circulation of blood in a single ventricular patient.
  • Embodiments of the present invention provide a cavity-assisted circulation device including a first cavity and a power source, the first cavity including a first chamber, an inflow tube for communicating with the vena cava, and a communication with the pulmonary artery An outflow tube; the inflow tube and the outflow tube are all in communication with the first chamber; the power source is configured to provide the first chamber with power to cause contraction and relaxation.
  • the power source is for connection to an aortic lumen to deliver a pressure change of the aorta to the first chamber;
  • the power source is configured to be coupled to the ventricular lumen by a pulmonary valve annulus to deliver systolic and diastolic pressures of the ventricle to the first chamber.
  • the power source includes a second chamber, a connecting tube, and a fluid, the fluid filling the second chamber and the connecting tube, the second chamber and the a connecting tube communicating, the connecting tube being provided with a diaphragm away from an end of the second chamber; the diaphragm for placing on the aortic blood vessel wall or the pulmonary valve annulus such that the diaphragm contracts or relaxes with the ventricle And exercise;
  • the second chamber and a part of the wall of the first chamber are fixed or have a unitary structure.
  • the luminal assisted circulation device further includes an inner membrane having a membrane inside the inner membrane cavity divided into two sub-cavities, wherein one of the sub-cavities serves as the One chamber and the other sub-chamber serve as the second chamber.
  • the first chamber or the inflow tube is provided with a directional adjustment member that causes blood to flow unidirectionally from the inflow tube into the first chamber.
  • the directional adjustment member includes an anti-reflux membrane located at a point where the inflow tube communicates with the first chamber.
  • the anti-reflux film is fixed or integrally formed on the inner wall of the first chamber at an end upstream of the blood inflow direction, and the anti-reflux film is located at one end downstream of the blood inflow direction. be free.
  • the luminol assisted circulation device further includes a support for supporting the first cavity and the power source.
  • the support body and the first cavity are ellipsoidal or spherical structures
  • the outflow tube extends through a gap between the outer wall of the first chamber and the inner wall of the support body to the outside of the support body; and/or the first inlet of the inflow tube is located at the support body Externally, the other portion of the inflow tube is located in a gap between the outer wall of the first chamber and the inner wall of the support.
  • the communication of the inflow tube with the first chamber is adjacent to the communication of the outflow tube and the first chamber.
  • the outflow tube is provided with a one-way adjustment member for unidirectional flow of blood to the pulmonary artery via the first chamber.
  • the material of the starting section and/or the middle section of the outflow tube is soft.
  • the support is a mesh structure or a film structure.
  • the support is a film-like structure, and a gap between the support and the first cavity and the power source is filled with a lightweight and non-immunogenic material.
  • the diaphragm is resilient.
  • the outflow tube second inlet is located near the top or top of the first chamber.
  • the first inlet of the inflow tube has a size equal to the size of the second outlet of the outflow tube
  • the size of the first inlet of the inflow tube is smaller than the size of the first outlet of the inflow tube; and/or the size of the second outlet of the outflow tube is less than or equal to the size of the second inlet of the outflow tube.
  • the distance between the first outlet and the first inlet is greater than the distance between the second inlet and the first inlet.
  • the embodiments of the present invention can at least produce the following technical effects:
  • the above-mentioned technical solution provides a cavity-assisted circulation device, the first cavity enables blood to enter and exit the first chamber, and the power source provides power for the inflow and outflow of blood in the first cavity.
  • the inflow tube is connected to the vena cava, and the outflow tube is connected to the pulmonary artery.
  • the cavity lung assist circulation device repeatedly repeats two actions of blood drawing and pumping, so that the human blood can circulate and flow.
  • FIG. 1 is a cross-sectional structural view of a cavity lung assisting circulation device according to an embodiment of the present invention
  • FIG. 2 is a top plan view of a cavity lung assisting circulation device according to an embodiment of the present invention
  • FIG. 3 is a schematic bottom view of a cavity lung assisting circulation device according to an embodiment of the present invention.
  • FIG. 4 is a schematic view showing a connecting tube and a diaphragm in a blood-sucking state of a cavity-assisted circulation device according to an embodiment of the present invention
  • FIG. 5 is a schematic view of a lumen-assisted circulation device in a pumping state connecting tube and a diaphragm according to an embodiment of the present invention
  • FIG. 6 is a schematic diagram of a cavity lung assisting circulation device in a blood drawing state according to an embodiment of the present invention
  • FIG. 7 is a schematic diagram of a cavity-assisted circulation device according to an embodiment of the present invention in a pumping state.
  • an embodiment of the present invention provides a cavity lung assist circulation device (also referred to as a “cavity-lung auxiliary circulation device”), including a first cavity 1 and a power source 2.
  • the first cavity 1 includes a first chamber 11, an inflow tube 12 for communicating with the vena cava, and an outflow tube 13 for communicating with the pulmonary artery. Both the inflow pipe 12 and the outflow pipe 13 communicate with the first chamber 11.
  • the power source 2 is used to provide the first chamber 11 with power to contract and relax.
  • the power source 2 powers the first chamber 11 so that the first chamber 11 can contract and relax.
  • the cavity lung assist circulation device pumps blood outward, and the first chamber 11 is dilated, and the cavity lung assist circulation device draws blood.
  • the first chamber 11 is a blood chamber, and blood drawing and pumping operations are mainly implemented in the blood chamber.
  • the power source 2 provides the power to relax the first chamber 11, the blood in the vena cava flows to the inside of the first chamber 11 via the inflow tube 12, that is, the chamber lung assist circulation device is in a blood drawing state, see FIG.
  • the power source 2 provides the power to contract the first chamber 11, the blood in the first chamber 11 is pumped out into the pulmonary artery via the outflow tube 13, that is, the chamber lung assist circulation device is in a pumping state, see FIG.
  • the power source of the power source 2 may be external power, but it is preferably driven by the patient's own blood power, and a specific implementation thereof will be given later.
  • the first inlet 17 of the inflow tube 12 is for communication with the vena cava.
  • the first outlet 15 of the inflow tube 12 is in communication with the first chamber inlet 111 of the first chamber 11.
  • the second inlet 19 of the outflow tube 13 is in communication with the first chamber outlet 112 of the first chamber 11, and the second outlet 20 of the outflow tube 13 is for communication with the pulmonary artery.
  • the second inlet 19 of the outflow tube 13 is located near the top or top of the first chamber 11.
  • the second inlet 19 is disposed at this position in accordance with blood fluid dynamics, so that blood is easily discharged from the first chamber 11; in addition, the cavity lung assist circulation device has sufficient space to set the outflow tube 13 to be long It is convenient to set a flat structure in the initial section or the middle section of the outflow tube 13, and when the blood chamber is pumping and sucking blood, the wide or flat initial section or the middle section can be closed to counter the backflow of blood in the outflow tube 13.
  • the size of the first inlet 17 of the inflow tube 12 is smaller than the size of the first outlet 15 of the inflow tube 12. And/or, the size of the second outlet 20 of the outflow tube 13 is less than or equal to the size of the second inlet 19 of the outflow tube 13.
  • the size of the first inlet 17 of the inflow tube 12 is equal to the size of the second outlet 20 of the outflow tube 13.
  • the first outlet 15 is in an enlarged configuration to facilitate placement of the anti-reflux membrane 14 at the first outlet 15, see Figure 1, and to reduce blood flow disturbances.
  • the vicinity of the second inlet 19 is an enlarged structure, which facilitates blood flow at the second inlet 19, thereby reducing blood flow disorder.
  • the distance between the first outlet 15 and the first inlet 17 is greater than the distance between the second inlet 19 and the first inlet 17.
  • the above-described distance relationship is expressed as the positional relationship illustrated in FIG. 2, taking the direction shown in FIG. 2 as an example, and the position of the second inlet 19 is located between the first outlet 15 and the first inlet 17.
  • the inflow pipe 12 and the outflow pipe 13 may be integrally formed with the first chamber 11, integrally formed, or formed by 3D printing.
  • the first chamber 11 or the inflow tube 12 is provided such that blood flows unidirectionally from the inflow tube 12 into the first chamber.
  • the direction adjusting member may be a one-way valve or the like.
  • the direction adjusting member includes an anti-reflux film 14 located at a position where the inflow pipe 12 communicates with the first chamber 11.
  • the anti-reflux film 14 is specifically connected in such a manner that one end of the anti-reflux film 14 upstream of the blood inflow direction is fixed or integrally formed on the inner wall of the first chamber 11, and the anti-reflux film 14 is located in the blood inflow direction. The downstream end is free.
  • An anti-reflux film 14 is extended at the first chamber inlet 111.
  • the anti-reflux film 14 is located inside the first chamber 11.
  • the anti-reflux film 14 is expanded by the blood flowing in through the inflow tube 12, and the anti-reflux film 14 is away from the inner wall A of the first chamber 11, See Figure 6.
  • the anti-reflux film 14 abuts against the inner wall A of the first chamber 11 to prevent blood in the blood chamber from flowing back into the inflow tube 12, as shown in FIG.
  • the luminal assisted circulation device is used to assist the abnormal heart and provide the required power for the pulmonary circulation of the human blood.
  • the human heart relaxes and blood is drawn; the human heart contracts and pumps blood.
  • the function of the cavity-pulmonary assisted circulation device is similar to that of the human heart, and it is necessary to draw blood and pump blood for the blood circulation of the human blood cavity.
  • the first cavity 1 enables blood to enter and exit the first chamber 11, and the power source 2 provides the first chamber 11 with the power required for blood to flow in and out.
  • the inflow tube 12 is in communication with the vena cava
  • the outflow tube 13 is in communication with the pulmonary artery.
  • the chamber lung assist circulation device repeatedly repeats two actions of blood drawing and pumping, so that the blood can circulate and flow.
  • the power source 2 can drive the first cavity 1 to draw blood and pump blood by using the patient's own blood power.
  • the power source 2 is connected to the aortic cavity to transmit aortic blood pressure changes to the first chamber 11.
  • the power source 2 is configured to be coupled to the ventricular chamber through a pulmonary valve annulus to deliver systolic and diastolic pressures of the ventricle to the first chamber 11.
  • the power source 2 is connected to the aortic cavity; if the pulmonary valve annulus If the development is good, the power source 2 is connected to the ventricular chamber through the pulmonary valve annulus; if the aorta and pulmonary artery structures are difficult to meet the requirements, the power source 2 is connected to other power devices.
  • the power source 2 includes a second chamber 21, a connecting tube 22, and a fluid filled with the second chamber 21 and the connecting tube 22, and the fluid may be physiological saline.
  • the second chamber 21 is in communication with the connecting tube 22, and the end of the connecting tube 22 away from the second chamber 21 is provided with a diaphragm 23.
  • the second chamber 21 and a part of the wall of the first chamber 11 are fixed or have a unitary structure. If the power source 2 is connected to the aortic lumen, the septum 23 is placed on the aortic vessel wall.
  • Fig. 4 is a view showing the state of the diaphragm during the blood drawing of the cavity lung assist circulation device
  • Fig. 5 is a view showing the state of the diaphragm during the blood pumping process of the cavity lung assisting circulation device.
  • the end of the connecting tube 22 is provided with a diaphragm 23, and the diaphragm 23 is placed on the aortic blood vessel wall or the pulmonary valve annulus.
  • the ventricular contraction and relaxation cause the pressure change of the aorta or the ventricular chamber to drive the diaphragm to swing synchronously.
  • the oscillation of the diaphragm causes the volume of the second chamber 21 to change. Since the second chamber 21 and a part of the wall of the first chamber 11 are fixed or in a unitary structure, the volume of the second chamber 21 is changed such that the volume of the first chamber 11 changes inversely: the second chamber 21 is dilated Then, the first chamber 11 is contracted; when the second chamber 21 is contracted, the first chamber 11 is relaxed.
  • the first chamber 11 is dilated, and blood in the vein enters the first chamber 11 via the inflow tube 12; the first chamber 11 contracts, and blood in the first chamber 11 is forced out into the outflow tube 13 and then delivered into the pulmonary artery.
  • the diaphragm 23 can be made of a variable shape material such as an umbrella structure, and the umbrella structure can be contracted or unfolded. Other structures may be employed for the diaphragm 23, and in this example, the diaphragm 23 is resilient.
  • the diaphragm 23 is made of such a material, which can facilitate the conduction of pressure through the connecting pipe 22 to the second chamber 21, and also contributes to the protection of the heart function.
  • the second chamber 21 and a part of the wall of the first chamber 11 are of a unitary structure: the first chamber 11 and the second chamber 21 are adjacent to each other, and both pass through the diaphragm 3 . separate. That is, the diaphragm 3 is at the same time a partial wall of the second chamber 21 and the first chamber 11.
  • the luminal assisted circulation device further includes an inner membrane 5, and the inner membrane 5 is internally provided with a membrane 3 that divides the inner membrane cavity into two sub-cavities.
  • One of the sub-cavities serves as the first chamber 11 and the other sub-chamber serves as the second chamber 21.
  • the inner membrane 5 facilitates the attachment and growth of vascular endothelial cells, facilitating the intimalization of the first chamber 11.
  • the diaphragm 3 is made of a material having a variable shape. In this embodiment, the diaphragm 3 is elastic.
  • the diaphragm 3 can also be made of a self-contained pericardium or a material having a similar effect.
  • the diaphragm 3 adopts the material, can reduce the energy consumption during the working process of the cavity lung auxiliary circulation device, and makes the membrane 3 simple in structure and convenient for manufacturing and production, so that the cavity lung auxiliary circulation device is small in volume.
  • the second chamber 21 is contracted, the diaphragm 3 is bent toward the second chamber 21, the volume of the first chamber 11 is increased, and blood is drawn into the first chamber 11, and the above process is a cavity-assisted circulation device.
  • the process of drawing blood During the blood drawing, the liquid flow in the second chamber 21 is as shown in Fig. 6, and the blood flow in the first chamber 11 is as shown in Fig. 6.
  • the second chamber 21 is dilated, the diaphragm 23 is bent toward the first chamber 11, the volume of the first chamber 11 is reduced, and the blood is pumped out of the first chamber 11, which is the pump of the chamber assisting circulation device. Blood process.
  • the liquid flow in the second chamber 21 is as shown in Fig. 7, and the blood flow in the first chamber 11 is as shown in Fig. 7.
  • the inner chamber 5 and the diaphragm 3 of an entire ellipsoidal structure are used to form the first chamber 11 and the second chamber 21.
  • the first chamber 11 serves as a blood chamber
  • the second chamber 21 is filled with physiological saline.
  • the volume change of the second chamber 21 causes the volume of the first chamber 11 to also change.
  • the structure of the entire cavity-assisted circulation device is simple, small in size, and has almost no useless space.
  • the support body 4 and the first cavity 1 can also adopt a spherical structure.
  • the cavity lung assist circulation device further includes a support body 4 for supporting the first cavity 1 and the power source 2.
  • the support body 4 can take a variety of structures, such as a mesh structure, to reduce weight.
  • the support body 4 is made of a material having good tissue compatibility or absorption, the body's own tissue can grow along the gap of the network structure to increase the tissue compatibility.
  • the support 4 evolves into an autologous tissue that grows later.
  • the support 4 is a film structure.
  • the support body 4 specifically includes an outer film 6, and a support cavity 41 formed by the outer film 6 encloses the first chamber 11, the second chamber 21, and most of the inflow tube 12 and the outflow tube 13.
  • the first cavity 1 and the power source 2 are disposed inside the support body 4.
  • the support body 4 is disposed in the patient body, and the material can be used as a patient body with good compatibility or absorption. a part of.
  • the communication between the inflow pipe 12 and the first chamber 11 is adjacent to the communication between the outflow pipe 13 and the first chamber 11, and the outflow pipe 13 passes through the outer wall of the first chamber 11 and supports A gap between the inner walls of the body 4 projects to the outside of the support body 4.
  • the first inlet 17 of the inflow pipe 12 is located outside the support body 4, and the other portion of the inflow pipe 12 other than the first inlet 17 is located in the gap between the outer wall of the first chamber 11 and the inner wall of the support body 4.
  • the initial section and/or the intermediate section 16 of the outflow tube 13 may be formed entirely or partially by the outer wall of the first chamber 11 and the floating wall adjacent the outer membrane 6.
  • the floating wall is independent of the inner wall of the support body 4, and the floating wall can be fitted to the outer wall of the first chamber 11 to prevent blood from flowing back.
  • the initial section and/or the middle section of the outflow pipe 13 are made of an anti-blocking and soft material. In the blood drawing phase of the first chamber 11, the initial section or the middle section of the outflow tube 13 is softly fitted together, thereby preventing blood from flowing back.
  • the one-way adjustment member is for allowing blood to flow in one direction to the pulmonary artery via the first chamber 11 and cannot be reversely reversed.
  • the one-way adjustment member may employ a one-way valve or the like.

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Abstract

一种腔肺辅助循环装置，涉及医疗器械领域，用以实现单心室患者体内血液的正常循环。该腔肺辅助循环装置包括第一腔体(1)和动力源(2)，第一腔体(1)包括第一腔室(11)、用于与腔静脉连通的流入管(12)和用于与肺动脉连通的流出管(13)；流入管(12)、流出管(13)都与第一腔室(11)连通；动力源(2)用于为第一腔室(11)提供使其收缩、舒张的动力。在腔肺辅助循环装置中，第一腔体(1)使得血液能够进出第一腔室(11)，动力源(2)为第一腔体(1)内血液的流入、流出提供动力。使用时，将流入管(12)与腔静脉连通，流出管(13)与肺动脉连通，腔肺辅助循环装置反复重复抽血、泵血两个动作，使得血液能够循环流动。

Description

腔肺辅助循环装置 技术领域
本发明涉及医疗器械领域，具体涉及一种腔肺辅助循环装置。
背景技术
Fontan手术及其改进术式经常用来治疗先天性心脏畸形导致功能性单心室的病症。随着手术技巧的进步和术后监护措施的发展，越来越多的功能性单心室患儿得以存活到成年。因为患儿生存时间延长，Fontan循环的局限性和远期并发症开始显现，极大地影响了患儿的生存质量。为解决上述问题，业内提出了动力性Fontan概念。在过去的几十年里，用以实现动力性Fontan循环的腔肺辅助循环装置的相关研究取得了一些进展，但是业内一直没有能够满足临床使用需要的产品。
发明内容
本发明实施例的其中一个目的是提出一种腔肺辅助循环装置，用以实现单心室患者体内血液的正常循环。
为实现上述目的，本发明实施例提供了以下技术方案：
本发明实施例提供了一种腔肺辅助循环装置，包括第一腔体和动力源，所述第一腔体包括第一腔室、用于与腔静脉连通的流入管和用于与肺动脉连通的流出管；所述流入管、所述流出管都与所述第一腔室连通；所述动力源用于为所述第一腔室提供使其收缩、舒张的动力。
在可选或优选的实施例中，所述动力源用于与主动脉腔连接，以将所述主动脉的压力变化传递至所述第一腔室；
或者，所述动力源用于通过肺动脉瓣环与心室腔连接，以将心室的收缩压、舒张压传递至所述第一腔室。
在可选或优选的实施例中，所述动力源包括第二腔室、连接管和流体，所述流体充满所述第二腔室和所述连接管，所述第二腔室与所述连接管连通，所述连接管远离所述第二腔室的端部设有隔膜；所述隔膜用于置于主动脉血管壁或肺动脉瓣环上，以使得所述隔膜随着心室收缩或舒张而运动；
其中，所述第二腔室和所述第一腔室的部分壁体固定或为一体式结构。
在可选或优选的实施例中，腔肺辅助循环装置还包括内膜，所述内膜内部设有将内膜腔体分成两个子腔体的膜片，其中一个子腔体作为所述第一腔室，另一个子腔体作为所述第二腔室。
在可选或优选的实施例中，所述第一腔室或所述流入管内设有使得血液从所述流入管单向流入第一腔室的方向调节部件。
在可选或优选的实施例中，所述方向调节部件包括抗返流膜，所述抗返流膜位于所述流入管与所述第一腔室连通处。
在可选或优选的实施例中，所述抗返流膜位于血液流入方向上游的一端固定或一体成型于所述第一腔室的内壁，所述抗返流膜位于血液流入方向下游的一端是自由的。
在可选或优选的实施例中，腔肺辅助循环装置还包括支撑体，所述支撑体用于支撑所述第一腔体和所述动力源。
在可选或优选的实施例中，所述支撑体和所述第一腔体为椭圆体状或球状结构；
所述流出管穿过所述第一腔室外壁和所述支撑体内壁之间的缝隙伸出到所述支撑体的外部；和/或，所述流入管第一入口位于所述支撑体的外部，所述流入管的其他部分位于所述第一腔室外壁和所述支撑体内壁之间的缝隙内。
在可选或优选的实施例中，所述流入管与所述第一腔室的连通处与所述流出管和所述第一腔室的连通处邻近。
在可选或优选的实施例中，所述流出管内设有单向调节部件，所述单向调节部件用于使得血液经由所述第一腔室单向流至肺动脉。
在可选或优选的实施例中，所述流出管起始段和/或中段的材质柔软。
在可选或优选的实施例中，所述支撑体为网状结构或者膜状结构。
在可选或优选的实施例中，所述支撑体为膜状结构，所述支撑体与所述第一腔体和所述动力源之间的缝隙内填充有轻便且无免疫原性的材料。
在可选或优选的实施例中，所述膜片是有弹性的。
在可选或优选的实施例中，所述流出管第二入口位于所述第一腔室的顶部或者顶部附近。
在可选或优选的实施例中，所述流入管第一入口的尺寸等于所述流出管第二出口的尺寸；
所述流入管第一入口的尺寸小于所述流入管第一出口的尺寸；和/或，所述流出管第二出口的尺寸小于或等于所述流出管第二入口的尺寸。
在可选或优选的实施例中，所述第一出口与所述第一入口的距离大于所述第二入口与所述第一入口的距离。
基于上述技术方案，本发明实施例至少可以产生如下技术效果：
上述技术方案提供的腔肺辅助循环装置，第一腔体使得血液能够进、出第一腔室，动力源为第一腔体内血液的流入、流出提供动力。使用时，将流入管与腔静脉连通，流出管与肺动脉连通，腔肺辅助循环装置反复重复抽血、泵血两个动作，使得人体血液能够循环流动。
附图说明
此处所说明的附图用来提供对本发明的进一步理解，构成本申请的一部分，本发明的示意性实施例及其说明用于解释本发明，并不构成对本发明的不当限定。在附图中：
图1为本发明实施例提供的腔肺辅助循环装置剖视结构示意图；
图2为本发明实施例提供的腔肺辅助循环装置俯视示意图；
图3为本发明实施例提供的腔肺辅助循环装置仰视示意图；
图4为本发明实施例提供的腔肺辅助循环装置处于抽血状态连接管及隔膜的示意图；
图5为本发明实施例提供的腔肺辅助循环装置处于泵血状态连接管及隔膜的示意图；
图6为本发明实施例提供的腔肺辅助循环装置处于抽血状态的示意图；
图7为本发明实施例提供的腔肺辅助循环装置处于泵血状态的示意图。
附图标记：
1、第一腔体；2、动力源；3、膜片；4、支撑体；5、内膜；6、外膜；11、第一腔室；12、流入管；13、流出管；14、抗返流膜；15、第一出口；16、中段；17、第一入口；18、后段；19、第二入口；20、第二出口；21、第二腔室；22、连接管；23、隔膜；24、连接管接口；41、支撑腔体；111、第一腔室入口；112、第一腔室出口。
具体实施方式
下面结合图1～图7对本发明提供的技术方案进行更为详细的阐述。
参见图1至图3，本发明实施例提供一种腔肺辅助循环装置(也可称为“腔-肺辅助循环装置”)，包括第一腔体1和动力源2。第一腔体1包括第一腔室11、用于与腔静脉连通的流入管12和用于与肺动脉连通的流出管13。流入管12、流出管13都与第一腔室11连通。动力源2用于为第一腔室11提供使其收缩、舒张的动力。
动力源2为第一腔室11提供动力，使得第一腔室11能够收缩、舒张。第一腔室11收缩则腔肺辅助循环装置向外泵血，第一腔室11舒张则腔肺辅助循环装置抽血。
第一腔室11为血室，抽血、泵血操作主要在血室内实现。在动力源2提供使得第一腔室11舒张的动力时，腔静脉中的血液经由流入管12流到第一腔室11内部，即腔肺辅助循环装置处于抽血状态，参见图6。在动力源2提供使得第一腔室11收缩的动力时，第一腔室11内的血液经由流出管13泵出到肺动脉中，即腔肺辅助循环装置处于泵血状态，参见图7。
动力源2的动力来源可以是外部动力，但较佳的是利用患者自身的血液动力驱动，后文将给出其具体实现方式。
参见图1和图2，流入管12的第一入口17用于与腔静脉连通。流入管12的第一出口15与第一腔室11的第一腔室入口111连通。流出管13的第二入口19与第一腔室11的第一腔室出口112连通，流出管13的第二出口20用于与肺动脉连通。
参见图2，流出管13的第二入口19位于第一腔室11的顶部或者顶部附近。将第二入口19设置在该位置，符合血液流体动力学，使得血液易于从第一腔室11流出；再则，使得腔肺辅助循环装置有足够的空间，可以将流出管13设置得比较长，便于在流出管13的起始段或者中段设置一段扁平状结构，在血室抽、吸血液时，宽扁的起始段或者中段可以闭合，对抗流出管13内血液的返流。
参见图2，流入管12的第一入口17的尺寸小于流入管12的第一出口15的尺寸。和/或，流出管13的第二出口20的尺寸小于或等于流出管13的第二入口19的尺寸。流入管12的第一入口17的尺寸等于流出管13第二出口20的尺寸。本实施例中以同时采用上述设置为例。第一出口15处为膨大结构，利于在第一出口15处设置抗返流膜14，参见图1，并减少血流紊乱现象。第二入口19附近为膨大状结构，利于第二入口19血液流动，可减少血流紊乱现象。
参见图2，进一步地，第一出口15与第一入口17的距离大于第二入口19与第一入口17的距离。在图2中，上述距离关系表现为图2中示意的位置关系，以图2所示方向为例，第二入口19的位置位于第一出口15与第一入口17之间。采用上述设置，使得血液在第一腔室11内形成循环流动，可减少血流紊乱以及血栓现象的发生。
流入管12、流出管13可以与第一腔室11一体成型、一体制造或采用3D打印成型。
参见图1，进一步地，为了防止血液经由第一腔室入口111反流至流入管12中，第一腔室11或流入管12内设有使得血液从流入管12单向流入第一腔室11的方向调节部件。方向调节部件可以采用单向阀或者类似结构。
参见图1，本实施例中，方向调节部件包括抗返流膜14，抗返流膜14位于流入管12与第一腔室11连通处。
参见图1，抗返流膜14具体采用下述方式连接：抗返流膜14位于血液流入方向上游的一端固定或一体成型于第一腔室11的内壁，抗返流膜14位于血液流入方向下游的一端是自由的。
第一腔室入口111处延长出一段抗返流膜14。抗返流膜14位于第一腔室11内部，在抽血过程中，抗返流膜14被经由流入管12流入的血液撑开，抗返流膜14远离第一腔室11的内壁A，参见图6所示。在泵血过程中，抗返流膜14贴紧第一腔室11的内壁A，防止血室内的血液回流至流入管12中，参见图7所示。
腔肺辅助循环装置用于辅助非正常的心脏，为人体血液的腔肺循环提供所需要的动力。人体心脏舒张，实现抽血；人体心脏收缩，实现泵血。腔肺辅助循环装置的作用与人体心脏类似，提供人体血液腔肺循环所需要抽血、泵血动力。
上述技术方案提供的腔肺辅助循环装置，第一腔体1使得血液能够进出第一腔室11，动力源2为第一腔室11提供了血液流入、流出所需要的动力。使用时，将流入管12与腔静脉连通，流出管13与肺动脉连通，腔肺辅助循环装置反复重复进行抽血、泵血两个动作，使得血液能够循环流动。
承上述，本实施例中，动力源2可采用患者自身的血液动力驱动第一腔体1抽血、泵血动作。具体如下：动力源2与主动脉腔连接，以将主动脉血液压力变化传递至第一腔室11。或者，动力源2用于通过肺动脉瓣环与心室腔连接，以将心室的收缩压、舒张压传递至第一腔室11。
手术过程中，若患者主动脉结构良好，则将动力源2与主动脉腔连接；若肺动脉瓣环 发育良好，则将动力源2通过肺动脉瓣环与心室腔连接；若主动脉和肺动脉结构都难以满足要求，则将动力源2与其它动力装置连接。
参见图1和图5，下面介绍动力源的具体实现方式：动力源2包括第二腔室21、连接管22以及流体，流体充满第二腔室21和连接管22，流体可以为生理盐水。第二腔室21与连接管22连通，连接管22远离第二腔室21的端部设有隔膜23。其中，第二腔室21和第一腔室11的部分壁体固定或为一体式结构。若动力源2与主动脉腔连接，隔膜23置于主动脉血管壁上。心室收缩、舒张导致主动脉压力变化，主动脉压力变化会带动隔膜23摆动。若动力源2通过肺动脉瓣环与心室腔连接，隔膜23置于肺动脉瓣环上，心室收缩、舒张导致心室腔压力变化，心室腔压力变化会带动隔膜23摆动。图4示意了腔肺辅助循环装置抽血过程中隔膜的状态，图5示意了腔肺辅助循环装置泵血过程中隔膜的状态。
连接管22端部设有隔膜23，隔膜23置于主动脉血管壁或肺动脉瓣环上，心室收缩、舒张导致主动脉或心室腔的压力变化会带动膜片同步摆动。膜片的摆动，会使得第二腔室21的容积发生变化。由于第二腔室21和第一腔室11的部分壁体固定或为一体式结构，第二腔室21的体积发生变化使得第一腔室11的体积反向变化：第二腔室21舒张，则第一腔室11收缩；第二腔室21收缩，则第一腔室11舒张。第一腔室11舒张，静脉中血液经由流入管12进入到第一腔室11；第一腔室11收缩，第一腔室11内血液被压出到流出管13中然后输送到肺动脉中。
隔膜23可采用可变形状的材质，比如伞状结构，伞状结构可以收缩或者展开。隔膜23也可采用其它结构，本实例中，隔膜23是有弹性的。隔膜23采用这种材质，可以利于压力通过连接管22传导至第二腔室21，也利于保护心功能。
参见图1，本实施例中，第二腔室21和第一腔室11的部分壁体为一体式结构：第一腔室11和第二腔室21相邻，且两者通过膜片3分开。即膜片3同时是第二腔室21和第一腔室11的部分壁体。
具体而言，腔肺辅助循环装置还包括内膜5，内膜5内部设有将内膜腔体分成两个子腔体的膜片3。其中一个子腔体作为第一腔室11，另一个子腔体作为第二腔室21。内膜5有利于血管内皮细胞贴附和生长，利于第一腔室11的内膜化。
膜片3采用可变形状的材质，本实施例中，膜片3是有弹性的。膜片3还可以采用自体心包或具有类似效果的材质。膜片3采用这种材质，可以降低腔肺辅助循环装置工作过程中的能量消耗，且使得膜片3结构简单，便于制造生产，使得腔肺辅助循环装置体积小。
参见图6，第二腔室21收缩，膜片3向着第二腔室21弯曲，第一腔室11体积变大，血液被抽到第一腔室11中，上述过程即腔肺辅助循环装置的抽血过程。抽血过程中，第二腔室21中液体流向如图6所示，第一腔室11内血液流向如图6所示。参见图7，第二腔室21舒张，隔膜23向着第一腔室11弯曲，第一腔室11体积变小，血液被泵出第一腔室11，上述过程即腔肺辅助循环装置的泵血过程。泵血过程中，第二腔室21中液体流向如图7所示，第一腔室11内血液流向如图7所示。
本实施例中，采用一整个椭圆体状结构的内膜5和膜片3形成第一腔室11和第二腔室21。第一腔室11作为血室，第二腔室21内装满生理盐水。第二腔室21的体积变化会使得第一腔室11的体积也发生变化。使得整个腔肺辅助循环装置的结构简洁，体积小巧，且几乎没有无用空间。当然，支撑体4和第一腔体1也可采用球状结构。
参见图1，腔肺辅助循环装置还包括支撑体4，支撑体4用于支撑第一腔体1和动力源2。
支撑体4可以采用多种结构，比如为网状结构，用以减少重量。当支撑体4采用组织相容性好或者可以吸收的材料，人体自身组织可以沿网状结构的间隙长入，增加组织相容性。当外源性材料被吸收后，支撑体4演变为后期长入的自体组织。或者，支撑体4为膜状结构。这样支撑体4和内膜5之间的就存在一些空腔，这些空腔中可以填入一些轻便且无免疫原性的材料，比如与支撑体4相同材质的材料、聚乙烯等。
参见图1，支撑体4具体包括外膜6，外膜6形成的支撑腔体41包住了第一腔室11、第二腔室21以及大部分的流入管12和流出管13。
本实施例中，第一腔体1和动力源2的大部分都设在支撑体4内部，支撑体4设于患者体内，其可以采用相容性较好或者可吸收的材质，作为患者身体的一部分。
承上述，参见图1和图2，流入管12与第一腔室11的连通处与流出管13和第一腔室11的连通处邻近，流出管13穿过第一腔室11外壁和支撑体4内壁之间的缝隙伸出到支撑体4的外部。和/或，流入管12的第一入口17位于支撑体4的外部，流入管12除第一入口17之外的其他部分位于第一腔室11外壁和支撑体4内壁之间的缝隙内。本实施例以同时采用上述结构为例。
流出管13的起始段和/或中段16可以完全采用或部分采用第一腔室11的外壁和靠近外膜6的浮动壁形成。浮动壁与支撑体4内壁相互独立，浮动壁能与第一腔室11的外壁贴合以防止血液回流。具体如下：流出管13的起始段和/或中段采用抗粘连、柔软的材质。 在第一腔室11抽血阶段，流出管13的起始段或者中段内壁柔软贴合在一起，这样可以防止血液回流。
当然，也可以在流出管13内设置单向调节部件结构，保证血液的单向流动。单向调节部件用于使得血液能经由第一腔室11单向流至肺动脉，不能反向回流。单向调节部件可采用单向阀或类似结构。
在本发明的描述中，需要理解的是，术语“中心”、“纵向”、“横向”、“前”、“后”、“左”、“右”、“竖直”、“水平”、“顶”、“底”、“内”、“外”等指示的方位或位置关系为基于附图所示的方位或位置关系，仅是为便于描述本发明和简化描述，而不是指示或暗指所指的装置或元件必须具有特定的方位、为特定的方位构造和操作，因而不能理解为对本发明保护内容的限制。
最后应说明的是：以上实施例仅用以说明本发明的技术方案，而非对其限制；尽管参照前述实施例对本发明进行了详细的说明，本领域的普通技术人员应当理解：其依然可以对前述各实施例所记载的技术方案进行修改，或者对其中部分技术特征进行等同替换，但这些修改或者替换，并不使相应技术方案的本质脱离本发明各实施例技术方案的精神和范围。

Claims (18)

  1. 一种腔肺辅助循环装置，其特征在于，包括第一腔体(1)和动力源(2)，所述第一腔体(1)包括第一腔室(11)、用于与腔静脉连通的流入管(12)和用于与肺动脉连通的流出管(13)；所述流入管(12)、所述流出管(13)都与所述第一腔室(11)连通；所述动力源(2)用于为所述第一腔室(11)提供使其收缩、舒张的动力。
  2. 根据权利要求1所述的腔肺辅助循环装置，其特征在于，所述动力源(2)用于与主动脉腔连接，以将所述主动脉的压力变化传递至所述第一腔室(11)；
    或者，所述动力源(2)用于通过肺动脉瓣环与心室腔连接，以将心室的收缩压、舒张压传递至所述第一腔室(11)。
  3. 根据权利要求2所述的腔肺辅助循环装置，其特征在于，所述动力源(2)包括第二腔室(21)、连接管(22)和流体，所述流体充满所述第二腔室(21)和所述连接管(22)；所述第二腔室(21)与所述连接管(22)连通，所述连接管(22)远离所述第二腔室(21)的端部设有隔膜(23)；所述隔膜(23)用于置于主动脉血管壁或肺动脉瓣环上，以使得所述隔膜(23)随着心室收缩或舒张而运动；
    其中，所述第二腔室(21)和所述第一腔室(11)的部分壁体固定或为一体式结构。
  4. 根据权利要求3所述的腔肺辅助循环装置，其特征在于，还包括内膜(5)，所述内膜(5)内部设有将内膜腔体分成两个子腔体的膜片(3)，其中一个子腔体作为所述第一腔室(11)，另一个子腔体作为所述第二腔室(21)。
  5. 根据权利要求1-4任一所述的腔肺辅助循环装置，其特征在于，所述第一腔室(11)或所述流入管(12)内设有使得血液从所述流入管(12)单向流入第一腔室(11)的方向调节部件。
  6. 根据权利要求5所述的腔肺辅助循环装置，其特征在于，所述方向调节部件包括抗返流膜(14)，所述抗返流膜(14)位于所述流入管(12)与所述第一腔室(11)连通处。
  7. 根据权利要求6所述的腔肺辅助循环装置，其特征在于，所述抗返流膜(14)位于血液流入方向上游的一端固定或一体成型于所述第一腔室(11)的内壁，所述抗返流膜(14)位于血液流入方向下游的一端是自由的。
  8. 根据权利要求1-4任一所述的腔肺辅助循环装置，其特征在于，还包括支撑体 (4)，所述支撑体(4)用于支撑所述第一腔体(1)和所述动力源(2)。
  9. 根据权利要求8所述的腔肺辅助循环装置，其特征在于，所述支撑体(4)和所述第一腔体(1)为椭圆体状或球状结构；
    所述流出管(13)穿过所述第一腔室(11)外壁和所述支撑体(4)内壁之间的缝隙伸出到所述支撑体(4)的外部；和/或，所述流入管(12)第一入口(17)位于所述支撑体(4)的外部，所述流入管(12)的其他部分位于所述第一腔室(11)外壁和所述支撑体(4)内壁之间的缝隙内。
  10. 根据权利要求1-4任一所述的腔肺辅助循环装置，其特征在于，所述流入管(12)与所述第一腔室(11)的连通处与所述流出管(13)和所述第一腔室(11)的连通处邻近。
  11. 根据权利要求1-4任一所述的腔肺辅助循环装置，其特征在于，所述流出管(13)内设有单向调节部件，所述单向调节部件用于使得血液经由所述第一腔室(11)单向流至肺动脉。
  12. 根据权利要求1-4任一所述的腔肺辅助循环装置，其特征在于，所述流出管(13)起始段和/或中段的材质柔软。
  13. 根据权利要求8所述的腔肺辅助循环装置，其特征在于，所述支撑体(4)为网状结构或者膜状结构。
  14. 根据权利要求8所述的腔肺辅助循环装置，其特征在于，所述支撑体(4)为膜状结构，所述支撑体(4)与所述第一腔体(1)和所述动力源(2)之间的缝隙内填充有轻便且无免疫原性的材料。
  15. 根据权利要求4所述的腔肺辅助循环装置，其特征在于，所述膜片(3)是有弹性的。
  16. 根据权利要求1所述的腔肺辅助循环装置，其特征在于，所述流出管(13)第二入口(19)位于所述第一腔室(11)的顶部或者顶部附近。
  17. 根据权利要求1所述的腔肺辅助循环装置，其特征在于，
    所述流入管(12)第一入口(17)的尺寸等于所述流出管(13)第二出口(20)的尺寸；
    所述流入管(12)第一入口(17)的尺寸小于所述流入管(12)第一出口(15)的尺寸；和/或，所述流出管(13)第二出口(20)的尺寸小于或等于第二入口(19)的尺寸。
  18. 根据权利要求17所述的腔肺辅助循环装置，其特征在于，所述第一出口(15)与所述第一入口(17)的距离大于所述第二入口(19)与所述第一入口(17)的距离。
PCT/CN2017/094338 2016-07-26 2017-07-25 腔肺辅助循环装置 WO2018019235A1 (zh)

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CN112237681B (zh) * 2020-09-15 2023-09-22 安徽通灵仿生科技有限公司 一体化微创导管式心脏辅助装置
CN115068807B (zh) * 2022-05-31 2024-05-28 绍兴梅奥心磁医疗科技有限公司 脉冲式体外肺膜动力泵及体外膜肺氧合装置
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Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4078267A (en) * 1975-12-31 1978-03-14 Akademia Medyczna Artificial heart propelled by respiratory muscles
US20030032854A1 (en) * 2001-08-13 2003-02-13 Arthur Palmer Blood pump
US20040152945A1 (en) * 2003-01-31 2004-08-05 Adrian Kantrowitz Stable aortic blood pump implant
CN104606730A (zh) * 2015-02-15 2015-05-13 李鸿雁 一种搏动式心室辅助装置
US9227002B1 (en) * 2013-06-13 2016-01-05 University Of Louisville Research Foundation, Inc. Systems and methods for providing cavopulmonary support
CN105561412A (zh) * 2016-02-02 2016-05-11 丁以群 心脏辅助装置

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4976730A (en) * 1988-10-11 1990-12-11 Kwan Gett Clifford S Artificial pericardium
CN2178532Y (zh) * 1993-07-13 1994-10-05 广东省心血管病研究所 左心辅助血泵
CN104436339A (zh) * 2013-09-25 2015-03-25 李温斌 无动力性人工心室装置
CN105381510A (zh) * 2015-12-24 2016-03-09 天津汇康医用设备有限公司 隔膜泵头

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4078267A (en) * 1975-12-31 1978-03-14 Akademia Medyczna Artificial heart propelled by respiratory muscles
US20030032854A1 (en) * 2001-08-13 2003-02-13 Arthur Palmer Blood pump
US20040152945A1 (en) * 2003-01-31 2004-08-05 Adrian Kantrowitz Stable aortic blood pump implant
US9227002B1 (en) * 2013-06-13 2016-01-05 University Of Louisville Research Foundation, Inc. Systems and methods for providing cavopulmonary support
CN104606730A (zh) * 2015-02-15 2015-05-13 李鸿雁 一种搏动式心室辅助装置
CN105561412A (zh) * 2016-02-02 2016-05-11 丁以群 心脏辅助装置

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