Component for in-vitro near physiological simulation of isolated heart

Abstract

The invention discloses an assembly for in-vitro near physiological simulation of an isolated heart, and belongs to the technical field of medical instruments. The design aims to solve a plurality of problems of the existing heart in-vitro simulation device, more accurately simulate the physiological movement of the heart and simplify the valve movement observation process. The assembly comprises a transparent shell, a top cover and a reciprocating pump. The shell is provided with a containing cavity for containing an isolated heart, the top cover is provided with an inflow channel and an outflow channel which are connected with a left atrioventricular opening and an aorta opening of the heart respectively, and the top cover is provided with an observation window for observing valve movement. The reciprocating pump changes hydraulic pressure of the containing cavity through the isolating membrane to enable the heart to contract and relax. The assembly is further provided with a plurality of pressure measuring interfaces and pressure measuring assemblies, and the shell is polyhedral so that observation can be facilitated. The component can be used for accurately simulating heart movement, is suitable for evaluating heart implantation interventional medical instruments, such as evaluating parameters such as functions, biomechanical characteristics, damage mechanisms and the like of instruments such as interventional artificial valves, and provides a reliable in-vitro simulation environment for research, development and verification of the medical instruments.

Description

Technical Field

[0001] The invention relates to the technical field of medical devices, and in particular to a component for in vitro near-physiological simulation of an isolated heart. Background Art

[0002] In vitro evaluation plays a vital role in the design and verification of implantable medical devices. Especially for cardiac implants such as interventional artificial valves, mitral valve shaping rings, ventricular septal occluders, blood pumps, etc., when evaluating their functions, biomechanical properties, damage mechanisms and other parameters, an in vitro near-physiological simulation device that can simulate the complex biomechanical environment of the heart is needed.

[0003] In order to accurately simulate the complex movement of the heart's myocardium and its subvalvular structures as well as the flow field in the ventricle, existing simulation methods usually adopt the following methods:

[0004] (1) Driving an isolated animal heart: Using an isolated heart for simulation, especially the pig heart, which is the first choice because its anatomical structure is closest to the human heart.

[0005] (2) 3D printed heart model: The heart model is manufactured by 3D printing technology, which is easy to integrate with the pulsatile flow platform, but it is difficult to fully replicate the biomechanical properties of the heart.

[0006] (3) Heart model cast with polyvinyl alcohol: The heart model cast with polyvinyl alcohol material is also convenient for integration with the pulsatile flow platform, but it has limitations in simulating the biomechanical properties of the heart.

[0007] In order to drive the dynamic motion of the heart model, two different pressurization methods are usually used:

[0008] ① Internal pressurization method: The reciprocating pump is connected to the ventricle through a hollow connector at the apex of the heart, and the liquid is periodically injected / extracted from the left ventricle to simulate cardiac movement. The characteristic of this pressurization method is that the liquid in the reciprocating pump participates in the systemic circulation, but the change in ventricular volume is opposite to the physiological state.

[0009] ② External pressurization method: Place the heart model in a container filled with liquid, and use vacuum technology to form a closed space. Use a reciprocating pump to periodically inject / extract liquid into the container to drive the movement of the ventricular wall. In this method, the liquid in the reciprocating pump does not participate in the systemic circulation, and the change in ventricular volume is consistent with the physiological state.

[0010] Although the above methods can simulate the dynamic process of the heart to a certain extent, there are still some key problems:

[0011] 1) Ex vivo animal heart model: Although it can simulate the biomechanical properties of the heart well, there is currently a lack of a device that can maintain the structure and function of the pig heart aortic valve and mitral valve and is convenient for access to the pulsatile flow platform;

[0012] 2) Although the external pressurization method can simulate physiological ventricular volume changes, fixing the apex and base of the heart leads to the fixation of the mitral valve ring and the aortic valve ring, which is inconsistent with the physiological situation;

[0013] 3) Observation of valve movement: In the prior art, observation of valve movement mainly relies on endoscopes, which require additional branch circuits and complicated installation processes.

[0014] The technical problems mentioned above indicate that there is an urgent need in the market for an improved in vitro near-physiological cardiac simulation device that can more accurately simulate the physiological movement of the heart while simplifying the observation process of valve movement. Summary of the invention

[0015] The object of the present invention is to provide a component for in vitro near-physiological simulation of an isolated heart, so as to solve the problems existing in the above-mentioned prior art, simulate the physiological movement of the heart more accurately, and facilitate the observation of valve movement.

[0016] To achieve the above object, the present invention provides the following solutions:

[0017] The present invention provides a component for in vitro near-physiological simulation of an isolated heart, comprising:

[0018] A transparent shell, wherein a containing cavity is provided in the shell, wherein the containing cavity is used to place an isolated heart, wherein a first opening is provided on the top surface of the shell, a second opening is provided on one side of the shell, and a liquid passage is provided at the bottom of the shell, wherein a first plug is detachably installed at the liquid passage;

[0019] A top cover sealedly connected to the top surface of the shell, wherein the first opening is located directly below the top cover, and the top cover includes a top plate and an inclined plate; an inflow channel and a first joint communicating with the inflow channel are fixedly provided on the top plate, and an outflow channel and a second joint communicating with the outflow channel are fixedly provided on the inclined plate; an end of the inflow channel close to the accommodating chamber is used to communicate with the left atrioventricular orifice of the isolated heart through a first connecting tube, and an end of the outflow channel close to the accommodating chamber is used to communicate with the aortic orifice on the isolated heart through a second connecting tube, and a first observation window and a second observation window are detachably mounted on the top cover, wherein the first observation window is opposite to an end of the inflow channel away from the accommodating chamber, and the second observation window is opposite to an end of the outflow channel away from the accommodating chamber;

[0020] A reciprocating pump, wherein the liquid inlet and the liquid outlet of the reciprocating pump are respectively sealedly connected to the first end of the third connecting tube, the second end of the third connecting tube is sealedly connected to the side wall of the shell, and the third connecting tube is opposite to the second opening, and an isolation membrane is provided at the second opening, and the isolation membrane isolates the third connecting tube from the accommodating cavity, and the area of ​​the isolation membrane is larger than the area of ​​the second opening.

[0021] Preferably, the angle between the top plate and the inclined plate is a first angle, the angle between the aortic valve and the mitral valve in the isolated heart is a second angle, and the first angle is equal to the second angle.

[0022] Preferably, the shell is in a polyhedral shape.

[0023] Preferably, the isolation membrane is sealed and connected to the housing.

[0024] Preferably, the top cover is also provided with a cavity pressure measuring interface, and the cavity pressure measuring interface is used to install a pressure sensor; the cavity pressure measuring interface is communicated with the accommodating cavity;

[0025] The inclined plate is provided with an aortic pressure measuring interface which is in communication with the outflow channel, and the aortic pressure measuring interface is used for installing a pressure sensor.

[0026] Preferably, a left atrial pressure measuring interface is also provided on the top cover, and the left atrial pressure measuring interface is used to install a pressure sensor; the left atrial pressure measuring interface is communicated with the inflow channel.

[0027] Preferably, the top cover is also provided with a left ventricular pressure measuring interface, and the left ventricular pressure measuring interface is used to install a pressure sensor; it also includes a left ventricular pressure measuring assembly, and the left ventricular pressure measuring assembly includes a connecting hose and a pressure measuring head, and the pressure measuring head is in the shape of a hollow cylinder, one end of the connecting hose is sealedly connected to the left ventricular pressure measuring interface, and the other end is sealedly connected to one end of the pressure measuring head, the other end of the pressure measuring head is pointed and provided with a plurality of openings, and the end of the pressure measuring head away from the connecting hose is used for insertion into the left ventricle of the isolated heart.

[0028] Preferably, an exhaust interface is provided at the top end of the third connecting pipe, and a second plug is detachably installed at the exhaust interface.

[0029] Preferably, a first sealing ring is sandwiched between the top cover and the shell, a second sealing ring and a third sealing ring are sandwiched between the third connecting pipe and the shell, and the outer diameter of the second sealing ring is smaller than the inner diameter of the third sealing ring.

[0030] Preferably, both the first joint and the second joint are pagoda joints.

[0031] Compared with the prior art, the present invention has achieved the following technical effects:

[0032] When in use, the component for in vitro near-physiological simulation of an isolated heart of the present invention places the isolated heart in a containing chamber, and the containing chamber is filled with liquid. The isolated heart is not fixed, so the physiological movement of the isolated heart can be simulated more accurately; the movement of the mitral valve can be conveniently observed through the first observation window, and the movement of the aortic valve can be conveniently observed through the second observation window.

[0033] Furthermore, the shell of the present invention is transparent and polyhedral, which is convenient for observing the movement of the isolated heart from different angles and can facilitate real-time three-dimensional movement measurement of the ventricular wall.

[0034] Furthermore, both the inflow channel and the outflow channel are transparent, so the flow of the circulating liquid can be easily observed.

[0035] Furthermore, this component can be used to accurately simulate cardiac movement and is suitable for the evaluation of cardiac implantable medical devices, such as the evaluation of device functions, biomechanical properties, and damage mechanisms of interventional artificial valves, providing a reliable in vitro simulation environment for the development and verification of medical devices. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0037] Figure 1 A schematic diagram of a partial structure of a component for in vitro near-physiological simulation of an isolated heart according to the present invention Figure 1 ;

[0038] Figure 2 A schematic diagram of a partial structure of a component for in vitro near-physiological simulation of an isolated heart according to the present invention Figure 2 ;

[0039] Figure 3 It is a schematic structural diagram of the first connecting tube in the assembly for in vitro near-physiological simulation of an isolated heart according to the present invention;

[0040] Figure 4 It is a schematic structural diagram of the second connecting tube in the component for in vitro near-physiological simulation of an isolated heart according to the present invention;

[0041] Figure 5 It is a schematic structural diagram of the third connecting tube in the assembly for in vitro near-physiological simulation of an isolated heart according to the present invention;

[0042] Figure 6 It is a schematic structural diagram of a shell in a component for in vitro near-physiological simulation of an isolated heart according to the present invention;

[0043] Figure 7 A schematic diagram of a partial structure of a component for in vitro near-physiological simulation of an isolated heart according to the present invention Figure 3 ;

[0044] Figure 8 A schematic diagram of a partial structure of a component for in vitro near-physiological simulation of an isolated heart according to the present invention Figure 4 ;

[0045] In the figure: 1. shell; 2. top cover; 3. first observation window; 4. second observation window; 5. second joint; 6. first joint; 7. third connecting pipe; 8. exhaust interface; 9. connecting hose; 10. pressure measuring head; 11. left atrial pressure measuring interface; 12. left ventricular pressure measuring interface; 13. inflow channel; 14. outflow channel; 15. first connecting pipe; 16. second connecting pipe; 17. first opening; 18. second opening; 19. first plug; 20. cavity pressure measuring interface; 21. aortic pressure measuring interface. DETAILED DESCRIPTION

[0046] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0047] The object of the present invention is to provide a component for in vitro near-physiological simulation of an isolated heart, so as to solve the problems existing in the above-mentioned prior art, simulate the physiological movement of the heart more accurately, and facilitate the observation of valve movement.

[0048] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the present invention is further described in detail below with reference to the accompanying drawings and specific embodiments.

[0049] like Figures 1 to 8 As shown, this embodiment provides a component for in vitro near-physiological simulation of an isolated heart, including:

[0050] A transparent shell 1 is provided with a receiving cavity in the shell 1, and the receiving cavity is used to place an isolated heart. A first opening 17 is provided on the top surface of the shell 1, a second opening 18 is provided on one side of the shell 1, and a liquid passage is provided at the bottom of the shell 1, and a first plug 19 is detachably installed at the liquid passage;

[0051] A top cover 2 is sealedly connected to the top surface of the shell 1, and the first opening 17 is located directly below the top cover 2. The top cover 2 includes a top plate and an inclined plate; an inflow channel 13 and a first joint 6 connected to the inflow channel 13 are fixedly provided on the top plate, and an outflow channel 14 and a second joint 5 connected to the outflow channel 14 are fixedly provided on the inclined plate; an end of the inflow channel 13 close to the accommodating chamber is used to communicate with the left atrioventricular orifice of the isolated heart through a first connecting tube 15, and an end of the outflow channel 14 close to the accommodating chamber is used to communicate with the aortic orifice on the isolated heart through a second connecting tube 16. A first observation window 3 and a second observation window 4 can also be detachably installed on the top cover 2, and the first observation window 3 is opposite to the end of the inflow channel 13 away from the accommodating chamber, and the second observation window 4 is opposite to the end of the outflow channel 14 away from the accommodating chamber;

[0052] A reciprocating pump (not shown in the figure), the liquid inlet and the liquid outlet of the reciprocating pump are respectively sealedly connected to the first end of the third connecting pipe 7, the second end of the third connecting pipe 7 is sealedly connected to the side wall of the shell 1, and the third connecting pipe 7 is opposite to the second opening 18, and an isolation membrane (not shown in the figure) is provided at the second opening 18, the isolation membrane isolates the third connecting pipe 7 from the accommodating cavity, and the area of ​​the isolation membrane is larger than the area of ​​the second opening 18.

[0053] When the reciprocating pump is working, it periodically sucks the liquid in the third connecting tube 7 or discharges the liquid into the third connecting tube 7, so that the volume of the liquid in the third connecting tube 7 changes. When the volume of the liquid in the third connecting tube 7 changes, the isolation membrane is driven to move. The movement of the isolation membrane causes the hydraulic pressure in the accommodating chamber to change. The change in the hydraulic pressure in the accommodating chamber causes the isolated heart to contract and relax, thereby performing a near-physiological simulation of the isolated heart.

[0054] In this embodiment, it is more preferred that the angle between the top plate and the inclined plate is the first angle, the angle between the aortic valve and the mitral valve in the isolated heart is the second angle, and the first angle is equal to the second angle; through the design of the top plate and the inclined plate, it is convenient to complete the in vitro near-physiological simulation of the isolated heart without changing the physiological angle between the mitral valve and the aortic valve, making the simulation process more accurate.

[0055] In this embodiment, it is more preferred that the shell 1 is in a polyhedron shape. The polyhedron design is convenient for setting up multiple cameras from different angles to capture the heart movement in real time, which is convenient for in vitro evaluation.

[0056] In this embodiment, it is more preferred that the isolation membrane is sealed and connected to the shell 1. The isolation membrane isolates the liquid in the accommodating cavity in the shell 1 from the liquid in the third connecting pipe 7, which can prevent the liquid in the accommodating wall from contaminating the liquid pumped by the reciprocating pump, ensure the stability of the reciprocating pump, and increase the service life of the reciprocating pump.

[0057] In this embodiment, preferably, the top cover 2 is further provided with a cavity pressure measuring interface 20, a left atrial pressure measuring interface 11 and a left ventricular pressure measuring interface 12, and this embodiment also includes a left ventricular pressure measuring assembly; the cavity pressure measuring interface 20, the left atrial pressure measuring interface 11 and the left ventricular pressure measuring interface 12 are used to install a pressure sensor, and specifically, an interface matching the cavity pressure measuring interface 20, the left atrial pressure measuring interface 11 and the left ventricular pressure measuring interface 12 is provided on the pressure sensor, so as to facilitate the installation of the pressure sensor on the cavity pressure measuring interface 20, the left atrial pressure measuring interface 11 or the left ventricular pressure measuring interface 12;

[0058] The cavity pressure measuring interface 20 is communicated with the accommodating cavity. When a pressure sensor is installed on the cavity pressure measuring interface 20, the pressure value in the container cavity can be directly measured; an aortic pressure measuring interface 21 connected to the outflow channel 14 is provided on the inclined plate, and the aortic pressure measuring interface 21 is used to install a pressure sensor; when in use, a pressure sensor is usually required to be installed on the cavity pressure measuring interface 20, the left atrial pressure measuring interface 11, the aortic pressure measuring interface 21 and the left ventricular pressure measuring interface 12 respectively, to facilitate pressure monitoring.

[0059] The left atrial pressure measuring interface 11 is communicated with the inflow channel 13. Since the inflow channel 13 is communicated with the left atrium of the isolated heart through the first connecting tube 15, when a pressure sensor is installed on the left atrial pressure measuring interface 11, the pressure value in the left atrium of the isolated heart can be directly measured.

[0060] The left ventricular pressure measuring assembly includes a connecting hose 9 and a pressure measuring head 10. The pressure measuring head 10 is in the shape of a hollow cylinder. One end of the connecting hose 9 is sealedly connected to the left ventricular pressure measuring interface 12, and the other end is sealedly connected to one end of the pressure measuring head 10. The other end of the pressure measuring head 10 is pointed and provided with a plurality of openings. The end of the pressure measuring head 10 away from the connecting hose 9 is used to be inserted into the left ventricle of the isolated heart. Since the tip of the pressure measuring head 10 is inserted into the left ventricle, the liquid in the left ventricle can communicate with the left ventricular pressure measuring interface 12 through the pressure measuring head 10, the connecting hose 9, and the left ventricular pressure measuring interface 12. Therefore, when a pressure sensor is installed on the left ventricular pressure measuring interface 12, the pressure value in the left ventricle of the isolated heart can be directly measured. It should be noted that during use, it is necessary to ensure the sealed connection between the pressure measuring head 10 and the isolated heart to avoid leakage of the liquid in the left ventricle of the isolated heart from between the isolated heart and the pressure measuring head 10.

[0061] In this embodiment, it is more preferred that an exhaust interface 8 is provided at the top end of the third connecting tube 7, and a second plug is detachably installed at the exhaust interface 8; the function of the exhaust interface 8 is to facilitate the discharge of gas in the third connecting tube 7 when liquid is filled into the third connecting tube 7. After the third connecting tube 7 is filled with liquid, the exhaust interface 8 is sealed with the second plug to prevent the liquid in the third connecting tube 7 from leaking from the exhaust interface 8.

[0062] A first sealing ring is sandwiched between the top cover 2 and the shell 1, and the sealing of the connection between the top cover 2 and the shell 1 is enhanced by the first sealing ring; the third connecting pipe 7 in this embodiment is conical, and a second sealing ring and a third sealing ring are sandwiched between the third connecting pipe 7 and the shell 1, and the outer diameter of the second sealing ring is smaller than the inner diameter of the third sealing ring. The sealing of the connection between the third connecting pipe 7 and the shell 1 is ensured by the setting of the second sealing ring and the third sealing ring.

[0063] In this embodiment, preferably, both the first joint 6 and the second joint 5 are pagoda joints.

[0064] In this embodiment, it is more preferred that one end of the first connecting tube 15 is a pagoda mouth (matching the inflow channel 13), and the shape of the other end needs to match the cross-sectional shape of the inner wall of the left atrium in a natural physiological state. In this embodiment, the end of the first connecting tube 15 inserted into the left atrium is designed with a D-shaped convex ring. This can ensure that after the first connecting tube 15 is inserted into the left atrium, the shape of the left atrium does not change, so that the shape of the mitral valve ring and the mitral valve does not change, thereby ensuring the accuracy of the simulation.

[0065] In this embodiment, it is more preferred that one end of the second connecting tube 16 is a pagoda mouth (matching the outflow channel 14), and the other end is designed according to the shape of the aortic valve and the aortic sinus (in order to match different pig hearts, this design has different sizes). In this embodiment, three claws are provided at the end of the second connecting tube 16. These three claws correspond to the three aortic sinuses one by one, and the claws match the shape and size of the corresponding aortic sinuses. The surface material of the claws is silicone, and silicone has a certain elasticity, which can ensure that after the claws are inserted into the corresponding aortic sinus, they will not affect the physiological morphology of the aortic sinus and the aortic valve, thereby ensuring the accuracy of the simulation.

[0066] It is worth noting that in this embodiment, the inflow channel 13, the outflow channel 14, the first connecting tube 15 and the second connecting tube 16 are all straight tubes, and the inflow channel 13 is coaxial with the first connecting tube 15, and the outflow channel 14 is coaxial with the second connecting tube 16; wherein the inflow channel 13 and the outflow channel 14 are transparent.

[0067] The isolated heart may be a human heart, or a pig heart, a cow heart, a sheep heart, a dog heart, or other heart similar to the human heart structure. Taking a pig heart as an example, the specific method of using the component for in vitro near-physiological simulation of an isolated heart in this embodiment is as follows:

[0068] First, the pig heart is processed, unnecessary blood vessels are trimmed, the aortic root is retained, and the left and right coronary arteries are clamped from the coronary root, so that the left heart only forms a left atrium-left ventricle-aorta loop without other side branches. Secondly, the first connecting tube 15 is fixed with a cable tie so that the first connecting tube 15 is connected to the left atrioventricular orifice of the pig heart; the second connecting tube 16 is fixed with a cable tie so that the second connecting tube 16 is connected to the aortic orifice of the pig heart;

[0069] Then, the first connecting tube 15 is connected to the inflow channel 13 through a hose, and the second connecting tube 16 is connected to the outflow channel 14 through a hose, and the first observation window 3 and the second observation window 4 are installed on the top cover 2, and other openings are blocked, so that only one passage between the pig heart and the top cover 2 is left, namely, the inflow channel 13-pig heart (i.e., isolated heart)-outflow channel 14, and the sealing between the pig heart and the top cover 2 is checked; then the tip of the pressure measuring head is inserted into the left ventricle of the pig heart from the bottom end of the pig heart, and the sealing between the pressure measuring head and the pig heart is ensured;

[0070] Then, assemble the top cover 2 and the shell 1 by screws, assemble the shell 1, the third connecting pipe 7 and the reciprocating pump by screws, fill the third connecting pipe 7 with liquid in advance, and seal the exhaust port 8 with the second plug after the third connecting pipe 7 is filled with liquid; then, while ensuring that the pig heart and the top cover 2 are well sealed, connect the simulation device to the external circulation unit through the first joint 6 and the second joint 5 on the top cover 2 (the first joint 6 is connected to the liquid outlet of the external circulation unit, and the second joint 5 is connected to the liquid inlet of the external circulation unit), so that the circulating liquid can circulate in the passage of the external circulation unit, the inflow channel 13, the first connecting pipe 15, the isolated heart, the second connecting pipe 16, and the external circulation unit; remove the first plug 19, fill the accommodating cavity with 0.9% physiological saline through the liquid port, and keep the cavity pressure measuring interface on the top cover 2 20 is opened so that the gas in the container cavity can be discharged through the cavity pressure measuring interface 20. After the container cavity is filled with 0.9% saline, the cavity pressure measuring interface 20 on the top cover 2 is closed to prevent the saline in the container cavity from leaking through the cavity pressure measuring interface 20; then the first plug 19 is installed, and finally, pressure sensors are respectively installed on the cavity pressure measuring interface 20, the left atrial pressure measuring interface 11, the aortic pressure measuring interface 21 and the left ventricular pressure measuring interface 12, and then the reciprocating pump is started to simulate and record the detection values ​​of each pressure sensor. During the simulation process, the movement of the pig heart (i.e., the isolated heart) can also be directly observed through the shell 1, so that saline instead of blood circulates between the pig heart (i.e., the isolated heart) and the external circulation unit, so that the movement of the mitral valve is observed through the first observation window 3 and the movement of the aortic valve is observed through the second observation window 4.

[0071] The present invention uses specific examples to illustrate the principles and implementation methods of the present invention. The above examples are only used to help understand the method and core ideas of the present invention. At the same time, for those skilled in the art, according to the ideas of the present invention, there will be changes in the specific implementation methods and application scope. In summary, the content of this specification should not be understood as limiting the present invention.

Claims

1. A component for in vitro near-physiological simulation of an isolated heart, characterized in that: include: A transparent shell, wherein a containing cavity is provided in the shell, wherein the containing cavity is used to place an isolated heart, wherein a first opening is provided on the top surface of the shell, a second opening is provided on one side of the shell, and a liquid passage is provided at the bottom of the shell, wherein a first plug is detachably installed at the liquid passage; A top cover sealedly connected to the top surface of the shell, wherein the first opening is located directly below the top cover, and the top cover includes a top plate and an inclined plate; an inflow channel and a first joint connected to the inflow channel are fixedly provided on the top plate, and an outflow channel and a second joint connected to the outflow channel are fixedly provided on the inclined plate; an end of the inflow channel close to the accommodating chamber is used to communicate with the left atrium and ventricle of the isolated heart through a first connecting tube, and an end of the outflow channel close to the accommodating chamber is used to communicate with the aortic orifice on the isolated heart through a second connecting tube, and a first observation window and a second observation window are detachably mounted on the top cover, wherein the first observation window is opposite to an end of the inflow channel away from the accommodating chamber, and the second observation window is opposite to an end of the outflow channel away from the accommodating chamber; A reciprocating pump, wherein the liquid inlet and the liquid outlet of the reciprocating pump are respectively sealedly connected to the first end of the third connecting tube, the second end of the third connecting tube is sealedly connected to the side wall of the shell, and the third connecting tube is opposite to the second opening, and an isolation membrane is provided at the second opening, and the isolation membrane isolates the third connecting tube from the accommodating cavity, and the area of ​​the isolation membrane is larger than the area of ​​the second opening.

2. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The angle between the top plate and the inclined plate is a first angle, the angle between the aortic valve and the mitral valve in the isolated heart is a second angle, and the first angle is equal to the second angle.

3. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The shell is in a polyhedral shape.

4. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The isolation diaphragm is sealed and connected to the housing.

5. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The top cover is also provided with a cavity pressure measuring interface, and the cavity pressure measuring interface is used to install a pressure sensor; the cavity pressure measuring interface is communicated with the accommodating cavity; The inclined plate is provided with an aortic pressure measuring interface which is in communication with the outflow channel, and the aortic pressure measuring interface is used for installing a pressure sensor.

6. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The top cover is also provided with a left atrial pressure measuring interface, and the left atrial pressure measuring interface is used to install a pressure sensor; the left atrial pressure measuring interface is communicated with the inflow channel.

7. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The top cover is also provided with a left ventricular pressure measuring interface, and the left ventricular pressure measuring interface is used to install a pressure sensor; it also includes a left ventricular pressure measuring assembly, and the left ventricular pressure measuring assembly includes a connecting hose and a pressure measuring head. The pressure measuring head is in the shape of a hollow cylinder, one end of the connecting hose is sealedly connected to the left ventricular pressure measuring interface, and the other end is sealedly connected to one end of the pressure measuring head. The other end of the pressure measuring head is pointed and provided with a plurality of openings, and the end of the pressure measuring head away from the connecting hose is used for inserting into the left ventricle of the isolated heart.

8. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: An exhaust interface is provided at the top end of the third connecting pipe, and a second plug is detachably installed at the exhaust interface.

9. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: A first sealing ring is sandwiched between the top cover and the shell, a second sealing ring and a third sealing ring are sandwiched between the third connecting pipe and the shell, and the outer diameter of the second sealing ring is smaller than the inner diameter of the third sealing ring.

10. The component for in vitro near-physiological simulation of an isolated heart according to claim 1, characterized in that: The first joint and the second joint both adopt pagoda joints.

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