A component for in vitro near-physiological simulation of an isolated heart

Abstract

The present invention discloses a component for in vitro near-physiological simulation of an isolated heart, belonging to the field of medical device technology. Its design purpose is to solve the many problems existing in existing in vitro heart simulation devices, simulate the physiological movement of the heart more accurately and simplify the valve movement observation process. The component includes a transparent shell, a top cover and a reciprocating pump. The shell has a accommodating chamber for placing the isolated heart, and the top cover has inflow and outflow channels respectively connected to the left atrioventricular orifice and the aortic orifice of the heart. An observation window is provided on the top cover to observe the valve movement. The reciprocating pump changes the hydraulic pressure of the accommodating chamber through an isolation membrane to cause the heart to contract and relax. The component is also provided with multiple pressure measuring interfaces and pressure measuring components, and the shell is polyhedron for easy observation. The 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 parameters such as the function, biomechanical properties and damage mechanism of interventional artificial valves, etc., providing a reliable in vitro simulation environment for the development and verification of medical devices.

Description

Technical Field

[0001] The present 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 crucial role in the design and validation of implantable medical devices. This is especially true for cardiac implants such as prosthetic valves, mitral valve rings, ventricular septal occluders, and blood pumps. Evaluating their function, biomechanical properties, and failure mechanisms requires an in vitro, near-physiological simulation device that can mimic the complex biomechanical environment of the heart.

[0003] To accurately simulate the complex motion of the cardiac myocardium and its subvalvular structures, as well as the flow field within the ventricle, existing simulation methods generally use 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 that of the human heart.

[0005] (2) 3D printed heart model: The heart model is manufactured using 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] To drive the dynamic motion of the heart model, two different pressurization methods are usually used:

[0008] ① Internal pressurization: A reciprocating pump is connected to the ventricle via a hollow connector at the apex of the heart. Fluid is periodically pumped into and out of the left ventricle to simulate cardiac motion. This pressurization method is characterized by the fluid in the reciprocating pump participating in systemic circulation, but the changes in ventricular volume are opposite to those in the physiological state.

[0009] ② External pressurization: The heart model is placed in a fluid-filled container, which is sealed using vacuum technology. A reciprocating pump periodically pumps fluid into and out of the container to drive ventricular wall movement. In this method, the fluid in the reciprocating pump does not participate in systemic circulation, and changes in ventricular volume are consistent with physiological conditions.

[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) Isolated animal heart models: Although they can effectively simulate the biomechanical properties of the heart, there is currently a lack of a device that can maintain the structure and function of the porcine aortic and mitral valves while also being easily accessible to a pulsatile flow platform.

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

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

[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 to more accurately simulate the physiological movement of the heart while simplifying the observation process of valve movement. Summary of the Invention

[0015] The purpose of the present invention is to provide a component for in vitro near-physiological simulation of an isolated heart 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 having a housing chamber therein for accommodating an isolated heart, a first opening on a top surface of the shell, a second opening on a side of the shell, and a liquid port at a bottom of the shell, wherein a first plug is detachably mounted on the liquid port;

[0019] a top cover sealedly connected to the top surface of the shell, the first opening being located directly below the top cover, the top cover comprising 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 aorta orifice on the isolated heart through a second connecting tube, and a first observation window and a second observation window are further detachably mounted on the top cover, the first observation window facing the end of the inflow channel away from the accommodating chamber, and the second observation window facing the 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, 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 polyhedron shape.

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

[0024] Preferably, the top cover is further provided with a cavity pressure measuring interface, 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, the top cover is further 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.

[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 hollow cylindrical, 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 several openings, and the end of the pressure measuring head away from the connecting hose is used to be inserted 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, the first joint and the second joint are both 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 receiving chamber filled with liquid, and the isolated heart is not fixed, which can more accurately simulate the physiological movement of the isolated heart; 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 has a polyhedral shape, which makes it easy to observe the movement of the isolated heart from different angles and to perform real-time three-dimensional movement measurement of the ventricular wall.

[0034] Furthermore, both the inflow channel and the outflow channel are transparent, making it easy to observe the flow of the circulating liquid.

[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 following briefly introduces the drawings required for use in the embodiments. 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 any creative work.

[0037] Figure 1 Schematic diagram of the partial structure of the components for in vitro near-physiological simulation of isolated heart according to the present invention Figure 1 ;

[0038] Figure 2 Schematic diagram of the partial structure of the components for in vitro near-physiological simulation of isolated heart according to the present invention Figure 2 ;

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

[0041] Figure 5 Schematic diagram of the structure 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 This is a schematic structural diagram of a housing in a component for in vitro near-physiological simulation of an isolated heart according to the present invention;

[0043] Figure 7 Schematic diagram of the partial structure of the components for in vitro near-physiological simulation of isolated heart according to the present invention Figure 3 ;

[0044] Figure 8 Schematic diagram of the partial structure of the components for in vitro near-physiological simulation of 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 connector; 6. First connector; 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. Aorta pressure measuring interface. DETAILED DESCRIPTION

[0046] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. 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 making creative efforts are within the scope of protection of the present invention.

[0047] The purpose of the present invention is to provide a component for in vitro near-physiological simulation of an isolated heart 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, comprising:

[0050] A transparent housing 1 is provided with a receiving chamber for receiving an isolated heart. The housing 1 has a first opening 17 on the top surface, a second opening 18 on one side, and a liquid port on the bottom surface. A first plug 19 is detachably mounted on the liquid port.

[0051] A top cover 2 is sealedly connected to the top surface of the housing 1, and a 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 connector 6 communicating with the inflow channel 13 are fixedly provided on the top plate, and an outflow channel 14 and a second connector 5 communicating with the outflow channel 14 are fixedly provided on the inclined plate; an end of the inflow channel 13 near 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 near the accommodating chamber is used to communicate with the aorta on the isolated heart through a second connecting tube 16. A first observation window 3 and a second observation window 4 are also detachably mounted on the top cover 2, the first observation window 3 facing the end of the inflow channel 13 away from the accommodating chamber, and the second observation window 4 facing the end of the outflow channel 14 away from the accommodating chamber;

[0052] A reciprocating pump (not shown in the figure) has its liquid inlet and liquid outlet sealedly connected to the first end of the third connecting pipe 7, respectively. 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. 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 housing 1 is in a polyhedron shape. The polyhedron design facilitates the installation of multiple cameras from different angles to capture cardiac movements in real time, thereby facilitating 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 improve 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. 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 pressure sensors. Specifically, the pressure sensor is provided with an interface that matches the cavity pressure measuring interface 20, the left atrial pressure measuring interface 11, and the left ventricular pressure measuring interface 12, 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 in communication with the inflow channel 13. Since the inflow channel 13 is in communication with the left atrium of the isolated heart via 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 several openings. The pressure measuring head 10 is away from the end of the connecting hose 9 and is used to insert 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 the liquid in the left ventricle of the isolated heart from leaking 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 first sealing ring enhances the sealing of the connection between the top cover 2 and the shell 1; 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 second sealing ring and the third sealing ring are arranged to ensure the sealing of the connection between the third connecting pipe 7 and the shell 1.

[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 the 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, which 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 one-to-one to the three aortic sinuses, 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 do 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 can be a human heart, or a pig heart, a cow heart, a sheep heart, a dog heart, or other heart with a similar structure to the human heart. 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 preserved, and the left and right coronary arteries are clamped at the coronary root, so that the left heart only forms a left atrium-left ventricle-aorta circuit, without other side branches. Next, 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, connect the first connecting tube 15 to the inflow channel 13 through a hose, connect the second connecting tube 16 to the outflow channel 14 through a hose, install the first observation window 3 and the second observation window 4 on the top cover 2, and block the other openings so that only one passage remains between the pig heart and the top cover 2: the inflow channel 13 - the pig heart (i.e., the isolated heart) - the outflow channel 14. Check the sealing between the pig heart and the top cover 2. Then, insert the tip of the pressure probe from the bottom end of the pig heart into the left ventricle of the pig heart, and ensure the sealing between the pressure probe and the pig heart.

[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 interface 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 at the same time 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% normal saline, the cavity pressure measuring interface 20 on the top cover 2 is closed to prevent the normal saline in the container cavity from leaking through the cavity pressure measuring interface 20; then the first plug 19 is installed. 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 normal saline instead of blood circulates between the pig heart (i.e., the isolated heart) and the external circulation unit, making it convenient to observe the movement of the mitral valve through the first observation window 3 and the movement of the aortic valve 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 intended to help understand the method and core concept of the present invention. At the same time, those skilled in the art will find that the specific implementation methods and application scopes may vary based on the concept of the present invention. In summary, the contents of this specification should not be construed 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 having a housing chamber therein for accommodating an isolated heart, a first opening on a top surface of the shell, a second opening on a side of the shell, and a liquid port on a bottom surface of the shell. A first plug is detachably mounted on the liquid port. a top cover sealedly connected to the top surface of the shell, the first opening being located directly below the top cover, the top cover comprising 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 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 aorta on the isolated heart through a second connecting tube, and a first observation window and a second observation window are further detachably mounted on the top cover, the first observation window facing the end of the inflow channel away from the accommodating chamber, and the second observation window facing the 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, 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 polyhedron 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, which 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, which 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, which is used to install a pressure sensor; it also includes a left ventricular pressure measuring assembly, which includes a connecting hose and a pressure measuring head. The pressure measuring head is hollow cylindrical, 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 several openings. The end of the pressure measuring head away from the connecting hose is used to be inserted 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 are both pagoda joints.

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