In-vitro simulation cycle test system driven by double power sources

Abstract

The invention relates to the technical field of blood circulation simulation devices, and provides an in-vitro simulation circulation test system driven by double power sources, which comprises a heart module, a lung module and a blood vessel branch module, the heart module comprises a motor pump group branch and a gas-liquid converter branch which are connected in parallel, and a motor pump group and a gas-liquid converter are respectively used as power sources; the motor pump set branch and the gas-liquid converter branch are respectively connected to the ventricular cavity through a reversing valve, and the reversing valve is used for switching the flow direction of the in-vitro simulation cycle test loop, so that the motor pump set or the gas-liquid converter is selected to drive the ventricular cavity, and simulation of different pressure waveforms and pulsation rhythms of the ventricle is realized. The system not only has high response control capability, but also can simulate flexible and slowly changing ventricular pulsation characteristics. According to the structure, the problems that a traditional system is single in driving mode and poor in adaptability are effectively solved, and the simulation precision and the adaptation capacity of various cycle scenes are remarkably improved.

Description

Technical Field

[0001] This invention relates to the technical field of blood circulation simulation devices, specifically to an in vitro simulated circulation test system driven by dual power sources. Background Technology

[0002] The statements in this section are merely background information related to the present invention and do not necessarily constitute prior art.

[0003] With the rapid development of interventional medical devices such as artificial hearts, vascular stents, and heart valves, the demand for simulation of the circulatory system is increasing. Constructing a controllable model of the human cardiovascular system in a laboratory environment not only allows for the evaluation of the performance of medical devices in dynamic fluid environments during the preclinical stage, but also enables applications in teaching, disease mechanism research, and drug delivery simulation. Especially when simulating the complex pressure waveforms and blood flow rhythms generated during ventricular contraction and relaxation, accurately reproducing the mechanical behavior of the ventricles becomes a core challenge in building a simulation system. Therefore, developing a circulatory simulation platform with high simulation capabilities, strong adjustability, and the ability to cover various cardiac operating conditions has become a key direction for interdisciplinary research in medical engineering.

[0004] However, existing blood circulation simulation technologies still have significant shortcomings. On the one hand, traditional systems mostly use motor-driven pumps or compressed air sources as a single power source, which is simple in structure but limited in function, and cannot simultaneously meet the dual simulation requirements of high responsiveness and flexible pulsation. On the other hand, most existing systems have weak control over hemodynamic parameters (such as pressure fluctuation range, flow rate variation patterns, etc.), making it difficult to adapt to different clinical application scenarios and testing requirements. In addition, the systems often cannot dynamically switch drive modes under different operating conditions, limiting their ability to simulate abnormal pathological states (such as arrhythmia, heart failure, etc.) and failing to fully reflect the impact of hemodynamic abnormalities on device performance or physiological systems. Summary of the Invention

[0005] To address the aforementioned problems, this invention proposes an in vitro circulatory simulation system driven by dual power sources. By connecting two power sources in parallel to the simulated ventricular cavity and achieving interference-free switching via a reversing valve, the system possesses both high-response control capabilities and the ability to simulate flexible, slowly changing ventricular contraction characteristics. This structure effectively overcomes the problems of traditional systems having a single driving method and poor adaptability, significantly improving the simulation accuracy and adaptability for various circulatory scenarios.

[0006] To achieve the above objectives, the present invention adopts the following technical solution: One or more embodiments provide an in vitro simulated circulatory testing system driven by dual power sources, including: a heart module, a lung module, and a vascular branch module; The heart module includes a parallel-connected motor pump branch and a gas-liquid converter branch, which serve as the power sources for the motor pump branch and the gas-liquid converter, respectively. The motor pump branch and the gas-liquid converter branch are connected to the simulated ventricular cavity through reversing valves. The reversing valves are used to switch the flow direction of the in vitro simulated circulation test loop to select whether the simulated ventricular cavity is driven by the motor pump or the gas-liquid converter, thereby simulating different pressure waveforms and pulsation rhythms of the ventricle.

[0007] Compared with the prior art, the beneficial effects of the present invention are as follows: This invention addresses the technical shortcomings of traditional systems that rely on a single power source, making it difficult to simulate different ventricular pulsation characteristics. This embodiment innovatively employs a dual-power-source structure of a motor pump and a gas-liquid converter. This structure can simulate different pressure waveforms and pulsation rhythms of the ventricle. By using the motor pump and the gas-liquid converter as two different types of power sources for the in vitro circulatory simulation system, and connecting them to the ventricular cavity in parallel, flexible switching of the drive scheme for the in vitro circulatory simulation system can be achieved. The motor pump directly controls the pressure and flow rate of simulated blood by adjusting the pump speed, suitable for test environments requiring high response accuracy. The gas-liquid converter indirectly drives the liquid chamber to achieve blood suction and discharge by adjusting the pressure of its gas chamber through a gas source, suitable for test requirements simulating flexible pulsation characteristics. The two power sources operate independently, switching between them via a reversing valve. This effectively solves the problem of traditional systems being limited to a single power source and a single drive method, improving adaptability to various simulated circulatory scenarios and enhancing the accuracy and adjustability of hemodynamic control.

[0008] The advantages of the present invention, as well as its additional advantages, will be described in detail in the following specific embodiments. Attached Figure Description

[0009] The accompanying drawings, which form part of this invention, are used to provide a further understanding of the invention. The illustrative embodiments of the invention and their descriptions are used to explain the invention and do not constitute a limitation thereof.

[0010] Figure 1 This is a schematic diagram of an in vitro simulated cycle test system driven by dual power sources according to Embodiment 1 of the present invention; Figure 2 This is a schematic diagram of the motor pump group branch of the heart module in Embodiment 1 of the present invention; Figure 3 This is a schematic diagram of the gas-liquid converter branch of the heart module in Embodiment 1 of the present invention; Figure 4 This is a schematic diagram of the vascular branch module and lung module of Embodiment 1 of the present invention; Figure 5This is a schematic diagram of the heart module, blood vessel branch module, and kidney module model of Embodiment 1 of the present invention; Among them: 1.1 Air source I; 1.2 Air source II; 2.1 Pneumatic triplet I; 2.2 Pneumatic triplet II; 3.1 First electro-proportional pressure reducing valve; 3.2 Second electro-proportional pressure reducing valve; 3.3 Third electro-proportional pressure reducing valve; 3.4 Fourth electro-proportional pressure reducing valve; 4.1 First silencer; 4.2 Second silencer; 5.1 Two-position three-way solenoid valve I; 5.2 Two-position three-way solenoid valve II; 6.1 First diverter valve; 6.2 Second diverter valve; 7.1 Speed ​​control valve II; 7.2 Speed ​​control valve I; 8.1 Two-position three-way handle-type directional control valve I; 8.2 Two-position three-way handle-type directional control valve II; 8.3 Two-position three-way handle-type directional control valve III; 8.4 Two-position three-way handle-type directional control valve IV; 9.1 First pressure gauge; 9.2 Second pressure gauge; 9.3 Third pressure gauge; 9.4 Fourth pressure gauge; 9.5 Fifth pressure gauge; 10. Isolated gas accumulator VI; 11. Isolated gas accumulator V; 12.1 First flow meter; 12.2 Second flow meter; 12.3 Third flow meter; 12.4 Fourth flow meter; 12.5 Fifth flow meter; 12.6 Sixth flow meter; 12.7 Seventh flow meter; 13.1 Check Valve I; 13.2 Check Valve II; 13.3 Check Valve III; 13.4 Check Valve IV; 13.5 Check Valve V; 13.6 Check Valve VI; 14. Artificial heart; 15. Temperature regulator; 16.1. Electric pump unit II; 16.2. Electric pump unit I; 17. First container; 18. Isolated gas accumulator II; 19. Gas-liquid converter II; 20. Gas-liquid converter I; 21. Second container; 22. Isolated gas accumulator I; 23.1 Second electro-proportional switching valve II; 23.2 First electro-proportional switching valve II; 23.3 Second electro-proportional switching valve I; 23.4 First electro-proportional switching valve I; 24.1 First shut-off valve; 24.2 Second shut-off valve; 24.3 Third shut-off valve; 24.4 Fourth shut-off valve; 24.5 Fifth shut-off valve; 25.1 First relief valve; 25.2 Second relief valve; 26 Third container; 27 Fourth container; 28.1 First adjustable flow valve; 28.2 Second adjustable flow valve; 28.3 Third adjustable flow valve; 28.4 Fourth adjustable flow valve; 28.5 Fifth adjustable flow valve; 29 Isolated gas accumulator III; 30 Isolated gas accumulator IV; 31 Cooler; 32 Gas mixer; 33 Temperature sensor. Detailed Implementation

[0011] The present invention will be further described below with reference to the accompanying drawings and embodiments.

[0012] It should be noted that the following detailed descriptions are exemplary and intended to provide further illustration of the invention. Unless otherwise specified, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains.

[0013] It should be noted that the terminology used herein is for describing particular embodiments only and is not intended to limit the exemplary embodiments of the present invention. As used herein, the singular form is intended to include the plural form as well, unless the context clearly indicates otherwise. Furthermore, it should be understood that when the terms "comprising" and / or "including" are used in this specification, they indicate the presence of features, steps, operations, devices, components, and / or combinations thereof. It should be noted that, without conflict, the various embodiments and features within those embodiments can be combined with each other. The embodiments will now be described in detail with reference to the accompanying drawings.

[0014] This invention proposes a simulated human blood circulation test bench for medical device testing and physiological simulation, featuring reconfigurable structure, switchable pathways, highly biomimetic power, and adjustable parameters. By introducing a dual-power-source driven multi-channel switching structure for the ventricles, a modular organ interface, and an artificial heart and lung insertion / removal testing mechanism, it solves the problems of existing simulation systems such as fixed functions, poor adaptability, and inability to realistically reproduce complex circulatory characteristics. It achieves a high degree of simulation and dynamic control of the entire process of human systemic and pulmonary circulation. This system can be widely used for performance evaluation and physiological and pathological state reproduction of devices such as artificial hearts, blood pumps, vascular stents, and valves. Specific embodiments are described below.

[0015] Example 1 In one or more of the technical solutions disclosed in the embodiments, such as Figures 1 to 5 As shown, an in vitro circulatory simulation test system driven by dual power sources includes: a heart module, a lung module, and a vascular branch module; The heart module includes a parallel-connected motor pump branch and a gas-liquid converter branch, which serve as the power sources for the motor pump branch and the gas-liquid converter branch, respectively. The motor pump branch and the gas-liquid converter branch are connected to the ventricular cavity through reversing valves. The reversing valves are used to switch the flow direction of the in vitro simulated circulation test circuit to select whether the ventricular cavity is driven by the motor pump or the gas-liquid converter, thereby simulating different pressure waveforms and pulsation rhythms of the ventricle.

[0016] To address the limitations of traditional systems that rely on a single power source and struggle to simulate different ventricular pulsation characteristics, this embodiment innovatively employs a dual-power-source structure of an electric pump and a gas-liquid converter. This structure can simulate different pressure waveforms and pulsation rhythms of the ventricle. By using the electric pump and the gas-liquid converter as two different types of power sources for the in vitro circulatory simulation system and connecting them to the ventricular cavity in parallel, flexible switching of the drive scheme for the in vitro circulatory simulation system can be achieved. The electric pump directly controls the pressure and flow rate of simulated blood by adjusting the pump speed, making it suitable for test environments requiring high response accuracy. The gas-liquid converter, on the other hand, indirectly drives the liquid chamber to achieve blood suction and discharge by adjusting the pressure of its gas chamber through a gas source, making it suitable for tests simulating flexible pulsation characteristics. The two power sources operate independently, switching between them via a reversing valve. This effectively solves the problem of traditional systems being limited by a single power source and a single drive method, improving adaptability to various simulated circulatory scenarios and enhancing the accuracy and adjustability of hemodynamic control.

[0017] The electric pump unit and the gas-liquid converter serve as the power source for the in vitro circulatory simulation system. They are arranged in parallel within the system, with one unit operating and generating power while the other remains inactive and disconnected. The main difference lies in their working principles and the methods for regulating simulated blood pressure and flow (or blood pressure and blood flow). Both the electric pump unit and the gas-liquid converter can be used to simulate the left and right ventricles of the human heart.

[0018] In some embodiments, the in vitro circulatory simulation test system is mounted on a test bench and includes two motor pump sets and two gas-liquid converters. One motor pump set and one gas-liquid converter are connected in parallel to simulate the working state of the left ventricle of the human heart; the other motor pump set and the other gas-liquid converter are also connected in parallel to simulate the working state of the right ventricle.

[0019] As one of the power sources of the in vitro simulated circulation test system, the motor pump unit is connected to the corresponding ventricular cavity. By adjusting the pump speed, the flow rate and pressure of the simulated blood output can be dynamically controlled, which is suitable for simulating the active pumping process of ventricular contraction.

[0020] The gas-liquid converter, as another power source of the in vitro circulatory simulation system, connects its gas chamber to an external gas source via a pneumatic triplet. The triplet filters and stabilizes the incoming gas. By adjusting the input gas pressure, the gas-liquid converter indirectly controls the suction capacity of the liquid chamber on the simulated blood, thus simulating the diastolic process of the heart. The greater the pressure change, the stronger the suction force of the simulated ventricle, allowing for active adjustment of the pulsatility as needed.

[0021] This embodiment can simulate the circulatory process of an independent in vitro circulatory simulation test system for the left and right ventricles respectively, adapting to different test parameter settings and hemodynamic changes in different populations and disease states, thus improving the diversity, flexibility and simulation accuracy of the simulation system.

[0022] In some embodiments, the motor pump set branch includes an isolated gas accumulator, a first electro-proportional switching valve, a container, a motor pump set, a second electro-proportional switching valve, an electro-proportional pressure reducing valve, and an overflow valve, which are connected in sequence through pipelines. An isolated gas accumulator is used to simulate pressure blood storage in the branch chamber of the left atrial motor pump unit; The first proportional switching valve simulates the ventricular diastolic process, and the second proportional switching valve simulates the left ventricular systolic process. The opening and closing times of the first and second proportional switching valves are opposite; when one opens, the other closes. Specifically, two electro-proportional switching valves alternately open and close, simulating the rhythmic movements of ventricular diastole and systole. When the first electro-proportional switching valve opens, simulated blood in the isolated gas accumulator flows into container one under the pressure of its internal gas, realizing the release of diastolic volume. When the second electro-proportional switching valve opens, the motor pump unit starts to draw simulated blood from container one and pressurizes it for output, forming a systolic blood jet.

[0023] Container 1 simulates the volume of the ventricle for storing blood. When the first electroproportional switch valve is opened, the simulated blood in the isolation gas accumulator flows to the pressureless container 1. The motor pump unit provides a power source for the in vitro simulated circulation test system of the motor pump unit branch. When the first electro-proportional switch valve is opened, it draws in the simulated blood in container one and pumps it out under pressure. The electro-proportional pressure reducing valve is used to regulate the pressure of the pressurized simulated blood pumped by the motor pump unit, ensuring that the simulated blood flow conforms to the set physiological parameters. The relief valve serves as a pressure protection element to prevent the system from operating under overpressure.

[0024] The simulated blood flows in two directions: when the pressure of the simulated blood in the isolated gas accumulator is lower than that of the simulated blood pumped out by the electric pump set, the simulated blood first flows upward into the isolated gas accumulator to prepare for the next cycle, and then flows downward into the aorta where the one-way valve is located. This completes one heartbeat cycle using the electric pump set heart simulation scheme.

[0025] Furthermore, the electric pump set can use DC motors and small centrifugal pumps, but is not limited to these. Any simple changes to the type of motor and the type and displacement of the pump in the electric pump set are within the scope of protection of this patent. The simulation schemes for the motor pump unit branches of the left and right ventricles are described below: Container 1 uses the second container 21 in the left ventricle simulation and the first container 17 in the right ventricle simulation; the electro-proportional pressure reducing valve and the overflow valve use the third electro-proportional pressure reducing valve 3.3 and the first overflow valve 25.1 in the left ventricle simulation; the electro-proportional pressure reducing valve and the overflow valve use the fourth electro-proportional pressure reducing valve 3.4 and the second overflow valve 25.2 in the right ventricle simulation. A specific implementation scheme for left ventricular simulation, such as Figure 1 and Figure 2 As shown, for the motor pump branch constructed for the left ventricle, such as Figure 2 As shown on the right, the system includes an isolated gas accumulator I22, a first electro-proportional switching valve I23.4, a second container 21, a motor pump I16.2, a second electro-proportional switching valve I23.3, and a third electro-proportional pressure reducing valve 3.3, all connected sequentially via pipelines. The output of the third electro-proportional pressure reducing valve 3.3 is divided into two branches. The first branch is connected to the isolated gas accumulator I22 via a third shut-off valve 24.3, and the second branch flows to the aortic simulated passage via a one-way valve III13.3. The third electro-proportional pressure reducing valve 3.3 is also connected to a first overflow valve 25.1. When the simulated blood pressure in the isolated gas accumulator I22 is lower than the simulated blood pumped out by the electric pump unit I16.2, the simulated blood first flows upward into the isolated gas accumulator I22 to prepare for the next cycle, and then flows downward into the one-way valve III13.3 to enter the aortic simulated pathway. This completes one cardiac cycle using the electric pump unit cardiac simulation scheme.

[0026] A specific implementation scheme for right ventricular simulation, such as Figure 1 and Figure 2 As shown, for the motor pump branch constructed for the right ventricle, such as Figure 2 As shown on the left, the system includes an isolated gas accumulator II 18, a first electro-proportional switching valve II 23.2, a first container 17, a motor pump group II 16.1, a second electro-proportional switching valve II 23.1, and a fourth electro-proportional pressure reducing valve 3.4, all connected sequentially via pipelines. The output of the fourth electro-proportional pressure reducing valve 3.4 is divided into two branches: the first branch is connected to the isolated gas accumulator II 18 via a fourth shut-off valve 24.4, and the second branch flows to the pulmonary artery simulation pathway via a one-way valve II 13.2. The fourth electro-proportional pressure reducing valve 3.4 is also connected to a second overflow valve 25.2. When the simulated blood pressure in the isolated gas accumulator II 18 is lower than the simulated blood pumped out by the electric pump unit II 16.1, the simulated blood will first flow upward into the isolated gas accumulator II 18 to prepare for the next cycle, and then flow downward into the pulmonary artery simulated pathway connected to the one-way valve II 13.2. This completes one cardiac cycle using the electric pump unit cardiac simulation scheme.

[0027] Through the above configuration, the impeller speed of the motor pump unit II 16.1 and the valve port action of the third electro-proportional pressure reducing valve 3.3 achieve the regulation of simulated ventricular beat intensity; the flow of fluid between the isolated gas accumulator II 18 and the first container 17 achieves the conversion of ventricular pressure and volume; and the switching duration of the first electro-proportional switching valve II 23.2 and the second electro-proportional switching valve II 23.1 achieves the adjustment of simulated ventricular beat frequency. Therefore, the motor pump unit simulation scheme can dynamically simulate the pressure changes, volume changes, and beat rhythm of the ventricle under actual physiological conditions, and has good physiological simulation and controllability.

[0028] In some embodiments, the gas-liquid converter branch includes a gas-liquid converter and a gas supply passage; the gas-liquid converter serves as the power source for the ventricle, and its liquid chamber is connected to a simulated passage between the ventricle and the artery via a shut-off valve, while the gas supply passage is used to provide the operating power for the gas-liquid converter. The gas supply passage includes a gas-liquid converter, a speed control valve, a two-position three-way solenoid valve, an electro-proportional pressure reducing valve, a pneumatic triplet, and a gas source connected in sequence; one end of the two-position three-way solenoid valve is connected to a silencer. The gas chamber of the gas-liquid converter is connected to a two-position three-way solenoid valve via a speed control valve; the gas generated by the gas source is cleaned and filtered by a pneumatic triplet before being introduced into an electro-proportional pressure reducing valve; the electro-proportional pressure reducing valve, connected to the two-position three-way solenoid valve, adjusts the gas pressure introduced into the gas chamber of the gas-liquid converter to simulate different ventricular contraction forces. In this embodiment, a two-position three-way solenoid valve is installed between the electro-proportional pressure reducing valve and the gas-liquid converter. The two-position three-way solenoid valve receives periodic electrical signals and opens and closes the connection between the gas chamber of the gas-liquid converter and the gas source at a set frequency, thereby simulating the heartbeat frequency in the in vitro circulatory test circuit. The speed control valve can adjust the movement speed of the piston in the gas-liquid converter. When using the first heart simulation scheme, i.e., the motor pump group branch, the first shut-off valve 24.1 is used to close the gas-liquid converter to prevent interference between the two schemes. This completes one heartbeat cycle as shown in the second heart simulation scheme, with the gas-liquid converter branch serving as the simulation circuit.

[0029] The simulation schemes for the gas-liquid converter branches of the left and right ventricles are described below. In the left ventricle simulation, gas-liquid converter I20 is used, and in the right ventricle simulation, gas-liquid converter II19 is used. The speed control valve I7.2 is used in the left ventricle simulation, and speed control valve II7.1 is used in the right ventricle simulation. The two-position three-way solenoid valve II5.2 is used in the left ventricle simulation, and two-position three-way solenoid valve I5.1 is used in the right ventricle simulation. The electro-proportional pressure reducing valve 3.2 is used in the left ventricle simulation, and the first electro-proportional pressure reducing valve 3.1 is used in the right ventricle simulation. The pneumatic triplet and air source both use pneumatic triplet I2.1 and air source I1.1. A specific implementation scheme for left ventricular simulation, such as Figure 1 and Figure 3 As shown, the gas-liquid converter branch constructed for the left ventricle includes a gas-liquid converter I20, a speed control valve I7.2, a two-position three-way solenoid valve II5.2, a second electro-proportional pressure reducing valve 3.2, a pneumatic triplet I2.1, and a gas source I1.1; one end of the two-position three-way solenoid valve II5.2 is connected to the second silencer 4.2, as shown. Figure 3 The right half is shown. The liquid chamber of the gas-liquid converter I20 is connected to the simulated pathway of the aorta via the second shut-off valve 24.2; The gas-liquid converter I20 has a gas chamber on its right side, connected to a 2-position 3-way solenoid valve II5.2. Gas from gas source I1.1 is cleaned and filtered by the pneumatic triplet I2.1 before entering the second electro-proportional pressure reducing valve 3.2. The function of the second electro-proportional pressure reducing valve 3.2 is to regulate the gas pressure entering the gas chamber of the gas-liquid converter I20, simulating different contraction forces of the left ventricle. A 2-position 3-way solenoid valve II5.2 is installed between the second electro-proportional pressure reducing valve 3.2 and the gas-liquid converter I20. The 2-position 3-way solenoid valve II5.2 receives periodic electrical signals and opens and closes the extracorporeal simulated circulation test circuit according to a set frequency to simulate the heart's beating frequency. The speed control valve I7.2 can adjust the movement speed of the piston in the gas-liquid converter I20. When the left ventricle is using heart simulation scheme one (i.e., the motor-pump branch), the second shut-off valve 24.2 is used to close the gas-liquid converter I20 to prevent interference between the two schemes. This completes one heart beating cycle as shown in heart simulation scheme two.

[0030] A specific implementation scheme for right ventricular simulation, such as Figure 1 and Figure 3 As shown, the gas-liquid converter branch constructed for the right ventricle includes a gas-liquid converter II 19, a speed control valve II 7.1, a two-position three-way solenoid valve I 5.1, a first electro-proportional pressure reducing valve 3.1, a pneumatic triplet I 2.1, and a gas source I 1.1; one end of the two-position three-way solenoid valve I 5.1 is connected to the first silencer 4.1, as shown. Figure 3 The left half is shown. The liquid chamber of the gas-liquid converter II 19 is connected to the simulated pulmonary artery pathway via the first shut-off valve 24.1; The right heart simulation scheme is similar to the left heart simulation scheme, except that: the left heart inlet is connected to the pulmonary vein and the outlet is connected to the aorta, while the right heart inlet is connected to the superior and inferior vena cava and the outlet is connected to the pulmonary artery.

[0031] Furthermore, the motor pump branch and the gas-liquid converter branch are respectively connected to the ventricular cavity via reversing valves. The reversing valves are used to switch the flow direction of the in vitro simulated circulation test circuit to select whether the ventricular cavity is driven by the motor pump or the gas-liquid converter. The reversing valves can be two-position three-way handle type reversing valves set at the branch inlets of the motor pump branch and the gas-liquid converter branch, that is, at the inlet of the power source simulating the left ventricle and the right ventricle (heart module), respectively. By switching the valve position, the direction of the oil circuit can be flexibly changed, and the two simulation schemes of motor pump and gas-liquid converter can be selected. Specifically, a two-position three-way handle-type reversing valve Ⅲ8.3 is installed for the left ventricle to select the motor pump group branch and the gas-liquid converter branch that simulates the operation of the left ventricle; a two-position three-way handle-type reversing valve Ⅱ8.2 is installed for the right ventricle to select the motor pump group branch and the gas-liquid converter branch that simulates the operation of the right ventricle. It is feasible to use the fourth container 27 to simulate the atrium. The left atrium simulated by the fourth container 27 is connected to the inlet of the two-position three-way handle-type reversing valve Ⅲ 8.3 through the one-way valve V 13.5, and the seventh flow meter 12.7 is installed on the connecting passage; the right atrium simulated by the third container 26 is connected to the inlet of the two-position three-way handle-type reversing valve Ⅱ 8.2 through the one-way valve Ⅳ 13.4, and the sixth flow meter 12.6 is installed on the connecting passage; Optionally, to achieve unidirectional blood flow in the simulation system, a one-way valve is used as the valve simulation component. The heart module includes one-way valve II 13.2, one-way valve III 13.3, one-way valve IV 13.4 and one-way valve V 13.5, which are used to simulate the pulmonary valve, aortic valve, tricuspid valve and mitral valve, respectively. Optionally, a flow meter can be used to monitor the flow rate data of simulated blood, such as... Figure 1 As shown, it includes a first flow meter 12.1, a second flow meter 12.2, a third flow meter 12.3, a fourth flow meter 12.4, a fifth flow meter 12.5, a sixth flow meter 12.6, and a seventh flow meter 12.7; It is feasible to simulate blood using liquids with similar density and viscosity to blood, such as aqueous glycerol solution, water-glycerol-urea solution, xanthan gum (XG) based solution, nylon particle suspension, etc. A further technical solution is that the in vitro simulated circulation test system also includes an artificial heart 14, which adopts a centrifugal blood pump structure driven by a magnetic levitation motor as an auxiliary power source for the in vitro simulated circulation test system; the artificial heart 14 is connected in parallel on both sides of the one-way valve used to simulate the aortic valve; Specifically, in this embodiment, the artificial heart 14 is connected in parallel on both sides of the one-way valve Ⅲ 13.3 used to simulate the aortic valve. That is, the inlet of the artificial heart 14 is connected to the simulated left ventricular cavity (corresponding to the inlet side of the one-way valve), and the outlet is connected to the outlet side of the one-way valve Ⅲ 13.3. After meeting with the aortic pipeline, it enters the simulated passage of the flow meter 12.3 connected to the aorta.

[0032] Optionally, the artificial heart inlet is equipped with a third pressure gauge 9.3; The artificial heart can work in parallel with a motor-pump assembly or with a gas-liquid converter. When the artificial heart is working, the motor-pump assembly or gas-liquid converter and one-way valve III13.3 remain operational, but the flow of simulated blood through one-way valve III13.3 will decrease accordingly, which is similar to the physiological response of the human body after a clinical artificial heart transplant. The artificial heart can serve as a power source for an auxiliary in vitro circulatory simulation testing system, effectively increasing the pressure and flow rate of simulated blood in the system.

[0033] Furthermore, the artificial heart 14 can also be actively speed modulated according to waveforms such as sine, square, and triangular waves to change the amplitude and frequency of the artificial heart's rotational speed, so that its output pulsatile blood flow matches the pulse rhythm of the human blood circulation.

[0034] The artificial heart 14 uses a centrifugal blood pump driven by a fully magnetically levitated motor. When the simulated blood circulation test bench is adjusted to the human ventricular failure mode, the artificial heart 14 can be used as an auxiliary power source for the extracorporeal simulated circulation test system. By adjusting its impeller speed, it can help the human body restore blood flow to a normal level. It can also be used to detect and evaluate the working condition and performance of the artificial heart 14.

[0035] In this embodiment, the artificial heart serves as the power source for the auxiliary extracorporeal simulated circulation test system, significantly enhancing the system's simulation output capability. Furthermore, the speed modulation function improves the realism and controllability of the simulated pulsating flow, enabling it to adapt to more complex physiological simulation needs. It is particularly suitable for scenarios such as preoperative simulation of artificial heart implantation and device linkage response testing.

[0036] Alternatively, the artificial heart 14 can also be an axial flow blood pump, a pulsatile heart, or an in vivo or external centrifugal pump. Furthermore, the application of the artificial heart 14 is not limited to assisting the left ventricle in pumping blood; it can also be used to assist the right ventricle or to use two artificial hearts simultaneously to assist both the left and right ventricles. Any simple changes to the number and position of the artificial hearts are within the scope of protection of this patent. In some embodiments, a specific implementation scheme of the lung module is as follows: Figure 1 and Figure 4As shown, it includes an isolated gas accumulator Ⅲ29 and a two-position three-way handle-type directional valve Ⅳ8.4 connected in sequence. One output of the two-position three-way handle-type directional valve Ⅳ8.4 is connected to the cooler 31, and the other is connected to the output of the pulmonary vein via a fourth adjustable flow valve 28.4. The cooler 31 is connected to the output of the pulmonary vein via a first adjustable flow valve 28.1. The output of the pulmonary vein is connected to a fourth container 27 used to simulate the left atrium. As the main functional component of the respiratory system simulation device, the cooler 31 also includes a gas source II1.2, a pneumatic triplet II2.2, a one-way valve VI13.6, and a gas mixer 32 connected in sequence. The pure oxygen supplied by the gas source II1.2 is cleaned and filtered by the pneumatic triplet II2.2 and checked by the one-way valve VI13.6. After forming mixed air in the gas mixer 32, it is introduced into the cooling pipe of the cooler 31. Furthermore, the gas mixer 32 is connected to an oxygen tank and an oxygenator, which (i.e., cooler 31) is used to simulate the conversion of hypoxic venous blood into oxygen-rich arterial blood. Furthermore, a semi-permeable membrane is used to separate the cooling pipes and cooling pipes of the cooler 31 to simulate the molecular exchange process between the vascular system and the respiratory system in the human lungs. The cooler 31 is connected to a first adjustable flow valve 28.1 that simulates the resistance formed by the capillaries in the lungs.

[0037] Optionally, a second flow meter 12.2, a pressure gauge V9.5, an isolation gas accumulator IV30, and a third adjustable flow valve 28.3 are provided on the connection passage between the output end of the pulmonary vein and the fourth container 27.

[0038] In this embodiment, the two-position three-way handle-type directional valve Ⅳ8.4 is located at the inlet of the adjustable flow valve and the cooler (with cooling pipe) (lung module). By switching the valve position, the direction of the oil circuit is changed, and the selection can be made between two simulation schemes: the fourth adjustable flow valve 28.4 (which only simulates organ resistance) and the cooler 31 (with cooling pipe), which can simulate both organ resistance and organ working principle. Simulated blood enters the lung module from the simulated pulmonary artery inlet, passing through the following components in sequence: First, simulated blood output from the right ventricle of the heart module flows into the pulmonary artery via the one-way valve II 13.2, which simulates the pulmonary valve to prevent backflow. Then, the blood flows through the fourth flow meter 12.4 and the fourth pressure gauge 9.4 to detect the flow and pressure signals entering the pulmonary circulation. Next, the blood enters the isolated gas accumulator III 29 to simulate the elastic energy storage function on the arterial side of the pulmonary circulation.

[0039] Subsequently, simulated blood flows through the fourth adjustable flow valve 28.4, the change in its opening degree can simulate the pulmonary circulation arterial resistance; it then enters the cooler 31, where a semi-permeable membrane structure is set between the inside of the cooling pipe and the outside pipe of the cooler to simulate the molecular exchange process between the alveoli and the blood.

[0040] The simulated gas system is supplied with oxygen by gas source II1.2. After being cleaned and filtered by pneumatic triplet II2.2, it is prevented from flowing back by one-way valve VI13.6 and mixed with circulating gas in gas mixer 32 to form simulated breathing gas. This gas then enters cooler 31 to complete gas exchange with blood.

[0041] After passing through the cooler, the blood flows through the first adjustable flow valve 28.1, a throttling element, to simulate the flow resistance at the end of the pulmonary capillaries; then it enters the isolation gas accumulator Ⅳ30, simulating the elastic characteristics of the pulmonary vein side; subsequently, it passes through the third adjustable flow valve 28.3 to simulate the vascular resistance characteristics of the vein side, and finally flows into the left atrium after passing through the second flow meter 12.2 and the fifth pressure gauge 9.5 to monitor the flow and pressure signals at the pulmonary vein outlet, completing the pulmonary circulation process.

[0042] The cooler 31 with cooling pipes simulates the human lungs. Simulated blood flows into or out of the cooling pipes of the cooler 31. The cooler pipes are connected to a gas source, and a semi-permeable membrane separates the cooling pipes from the cooler pipes. In this way, the exchange of small molecules such as oxygen and carbon dioxide between the simulated blood and the gas source can be achieved, thereby simulating the molecular exchange process between the human vascular system and respiratory system.

[0043] Through the above structural configuration, the lung module can flexibly adjust parameters such as flow rate, pressure, gas exchange efficiency, vascular resistance, and elasticity of simulated blood between the pulmonary artery and pulmonary vein, effectively reproducing the dynamic characteristics of human pulmonary circulation and improving the physiological realism and adjustability of the simulation system.

[0044] Alternative technical solutions are available. The test bench proposed in this embodiment uses, but is not limited to, the cooler (with cooling pipe) to simulate human lungs. Alternative solutions such as flat membrane or hollow fiber artificial membrane lung medical devices can also be used.

[0045] It is feasible that the simulated object of the cooler 31 (with cooling pipes) is not limited to the human lungs, but can also be used to simulate the process of substance exchange between the circulatory system and other human systems, such as the kidneys (or dialysis machines) and the digestive tract. Any simple changes to the number of coolers (with cooling pipes) or the simulated object are within the scope of this patent. In some embodiments, a specific implementation scheme of the vascular branching module is as follows: Figure 1 and Figure 4As shown, it includes a two-position three-way handle-type directional valve I8.1. One output terminal of the two-position three-way handle-type directional valve I8.1 is connected in parallel to a first diverter valve 6.1 and a second diverter valve 6.2. The other output terminal of the two-position three-way handle-type directional valve I8.1 is connected to the input terminal of a fifth adjustable flow valve 28.5. The output terminals of the first diverter valve 6.1 and the second diverter valve 6.2 are connected to the output terminal of the fifth adjustable flow valve 28.5 through a fifth shut-off valve 24.5, serving as the output terminals of the vascular branching module. The two-position three-way handle-type directional valve I8.1 has two output channels for switching between different simulation schemes: one output is connected in parallel to the first shunt valve 6.1 and the second shunt valve 6.2, simulating the branching structure of aortic blood flow into multiple small vessels, where each shunt valve simulates the local flow resistance caused by different pipe diameters; the other output is directly connected to the input of the fifth adjustable flow valve 28.5, which is used to simulate the overall resistance characteristics of the vessel tip. The outputs of the first shunt valve 6.1 and the second shunt valve 6.2 merge with the output of the fifth adjustable flow valve 28.5 through the third shut-off valve 24.3, forming a common output path for the vascular branching module.

[0046] Furthermore, at the input end of the two-position three-way handle-type directional valve I8.1 of the vascular branch module, an isolation gas accumulator V11, a first flow meter 12.1, a third flow meter 12.3, and a second pressure gauge 9.2 are also connected; V11 is an isolated gas accumulator used to simulate the elastic properties of arteries in the systemic circulation. The first flow meter 12.1 is used to detect the flow rate of simulated blood in the aorta before it enters the vascular branch pathway; the third flow meter 12.3 and the second pressure gauge 9.2 are used to detect the flow rate and pressure of blood pumped out by the left ventricle of the heart module, respectively. Furthermore, on the output pipeline of the vascular branch module, there are also an isolation gas accumulator VI10, a first pressure gauge 9.1, a fifth flow meter 12.5, a one-way valve I 13.1, a temperature regulator 15, a temperature sensor 33, and a second adjustable flow valve 28.2. The output end of the second adjustable flow valve 28.2 is connected to the third container 26 of the simulated right atrium. The isolated gas accumulator VI10 is used to simulate the vascular elasticity of the venous side of the systemic circulation; The first pressure gauge 9.1 and the fifth flow meter 12.5 are used to detect changes in pressure and flow rate of simulated blood on the venous side, respectively; One-way valve I13.1 is used to control the unidirectional flow of simulated blood to the heart return path; Temperature regulator 15 and temperature sensor 33 together form a temperature control function to regulate and monitor blood temperature and simulate human body temperature regulation; it can be used to simulate normal or abnormal (such as hypothermia and fever) human body temperature range, and based on this, simulate the changes in blood flow parameters when human body temperature changes.

[0047] The second adjustable flow valve 28.2 is used to simulate the vascular resistance of the systemic veins, and its output is connected to the third container 26 that simulates the right atrium to complete the closed-loop connection of the systemic circulation circuit.

[0048] Through the above structure, the vascular branch module can comprehensively simulate arterial elasticity, vascular branch resistance, venous return characteristics and blood temperature in the systemic circulation, thereby improving the ability of the in vitro simulated circulation test system to simulate the dynamic response and physiological realism of the human circulatory system.

[0049] In the above scheme, both the adjustable flow valves and the diverter valves are used to simulate the flow resistance of blood in the human vascular system. The adjustable flow valves regulate their opening degree, thereby directly controlling the flow rate of simulated blood in the tubing of the in vitro simulated circulation test system; while the diverter valves divert the simulated blood from the main circuit of the in vitro simulated circulation test system to multiple branches, simulating the flow resistance characteristics generated when blood flows from large-diameter vessels to multiple small-diameter vessels. The adjustable flow valves and diverter valves do not directly correspond to specific human organs, but rather simulate the changes in peripheral resistance in the vascular system.

[0050] In the above scheme, a certain number of one-way valves are distributed and installed in the pipeline of the simulation system to prevent the backflow of simulated blood. The function of the one-way valve corresponds to the physiological function of human vascular valves (arterial / venous valves) in preventing blood backflow.

[0051] In the above scheme, a certain number of isolated gas accumulators are distributed throughout the pipeline of the simulation system to simulate the pressure-volume changes in the human ventricular cavity (left / right ventricle) and the vascular elasticity characteristics of major blood vessels (such as the aorta and pulmonary artery). The isolated gas accumulators passively adapt to pressure changes in the in vitro simulated circulatory test system, altering the pressure of their internal sealed gas to simulate ventricular pressure changes; simultaneously, they can also actively adjust the sealed gas pressure to simulate the elasticity changes of blood vessels under different physiological states (such as exercise and sleep). The isolated gas accumulators do not directly correspond to specific human organs, but rather simulate the compliance changes of the heart and blood vessels in the vascular system.

[0052] The system comprises four containers, all open to the outside air, used for temporary storage of simulated blood. Two containers simulate the blood storage in the left and right atria and a portion of the veins. Since it is difficult to ensure that the volume of simulated blood in the extracorporeal circulation test tubing in an actual test bench is exactly the same as the blood storage volume in normal human veins, these two containers are introduced to correct for the blood storage volume in the veins. The other two containers are used to simulate the volumetric blood storage function of the left and right ventricles. In the heart module, an isolated gas accumulator works in conjunction with one container to simulate changes in the ventricular pressure-volume loop.

[0053] Optionally, the simulated blood can be a liquid, such as a mixture of glycerol and water in a 4:6 volume ratio, or fresh animal blood. The total volume of simulated blood required for the test bench is 4-6 L, which can be adjusted according to different simulated objects. The normal temperature of the simulated test bench is maintained between 36°C and 37.5°C, the temperature range for hypothermia is <35°C, and the temperature range for fever is between 37.5°C and 42°C.

[0054] The in vitro cyclic simulation test system with dual power source drive proposed in this embodiment can perform experiments including but not limited to: Flow rate and pressure test of artificial heart pump: The inlet and outlet pressure of artificial heart are measured by the second pressure gauge 9.2 and the third pressure gauge 9.3, and the flow rate through the left ventricle is measured by the third flow meter 12.3 and the seventh flow meter 12.7.

[0055] Minimum response time of artificial heart speed regulation in human blood flow: Adjust the frequency of artificial heart speed fluctuation, and measure the corresponding range of artificial heart outlet pressure fluctuation affected by artificial heart speed fluctuation and the minimum limit frequency that can affect human blood flow through the first pressure gauge 9.1 and the second pressure gauge 9.2.

[0056] The effects of constant and speed-modulated rotation speed of an artificial heart impeller on the human circulatory system: Blood flow parameters of a simulated circulatory system were measured using pressure gauges (1st pressure gauge 9.1, 2nd pressure gauge 9.2, 3rd pressure gauge 9.3) and flow meters (1st flow meter 12.1, 3rd flow meter 12.3, 5th flow meter 12.5, 7th flow meter 12.7). Two modes of adjusting the artificial heart impeller rotation speed—speed modulation and constant speed—were investigated to study their effects on blood flow in the simulated circulatory system. Speed ​​modulation of the artificial heart impeller rotation speed included, but was not limited to, sine waves, square waves, and triangular waves.

[0057] Matching the pulse frequency of the artificial heart with that of the human heart: Blood pressure and flow extremes were detected using the second pressure gauge (9.2), the third pressure gauge (9.3), the third flow meter (12.3), and the seventh flow meter (12.7). The fluctuation frequency of the artificial heart's rotational speed was adjusted to match the pulsation frequency of the simulated left ventricle, meaning that the simulated left ventricle output blood flow was maximized when the instantaneous rotational speed of the artificial heart was at its maximum.

[0058] The impact of valvular heart disease or systemic valvular heart disease on hemodynamics: By monitoring all pressure gauges and flow meters in the simulation system, the operation of simulation components related to valvular heart disease or systemic valvular heart disease is actively stopped, such as electro-proportional valves, check valves, and other valves; to simulate the impact of valvular heart disease or systemic valvular heart disease on hemodynamics; Simulation of Frank-Starling mechanism changes at different stages of ventricular failure: In the early stage of ventricular failure, vascular resistance increases to raise blood pressure. This is achieved by monitoring all pressure gauges and flow meters in the simulation system, reducing the output flow and pressure of the motor pump or gas-liquid converter, and reducing the opening of the throttle valve to increase its resistance, thus obtaining the pressure and flow change curves. The correspondence between changes in human body temperature and changes in blood flow parameters: By monitoring all pressure gauges and flow meters in the simulation system, and heating or cooling the temperature of the medium in the blood circulation system, the study was conducted on how blood flow parameters changed.

[0059] The impact of different vascular resistances on the entire blood circulation in the human body: By monitoring all pressure gauges and flow meters in the simulation system, the impact on blood flow pressure and flow parameters was detected by changing the opening of each throttle valve.

[0060] Simulation of the characteristics of the circulatory system at different ages and under different physiological conditions: Taking the elderly as an example, their heart rate is low, their blood vessels are less elastic, and their blood flow is low. Correspondingly, the switching frequency of the valve is reduced, there is less air in the isolated gas accumulator, and the output flow of the motor pump or gas-liquid converter is reduced; this can be simulated by controlling various components. Taking heart failure as an example, the heart beats at a high frequency, blood flow is low, and vascular resistance is high. This corresponds to an increased switching frequency of the valves, a decrease in the flow rate output by the motor pump or gas-liquid converter, and a smaller opening of the throttling valves in the vascular branches. Experimental study on research and treatment pathways for various blood circulation-related diseases (such as arteriosclerosis, arterial occlusion, and intracardiac valvular regurgitation): By actively stopping or destroying a normally functioning component in the blood circulation system, it represents the occurrence of certain organic diseases in the human body. For example, arteriosclerosis is achieved by reducing the gas inside the isolation gas accumulator, arterial occlusion is achieved by reducing the diameter of the tube, and intracardiac valvular regurgitation is achieved by the incomplete closure of the proportional switch valve regulated by electrical signals.

[0061] The diffusion path of a drug (which can be simulated by using a colored agent to visually distinguish it from an aqueous glycerol solution) in the human circulatory system: The movement path is observed with the naked eye by injecting a colored agent (such as ink) into the circulatory system.

[0062] The movement path of free thrombi (using viscous solids) in the human circulatory system: Free thrombi are simulated by injecting viscous solids (such as modeling clay) into the circulatory system, and their movement path is observed with the naked eye.

[0063] The main innovation lies in the construction of a highly realistic, adaptable, and scalable blood circulation simulation platform for medical device testing. The entire system has undergone systematic innovation and optimization in terms of power source, circulatory pathway, organ structure, and monitoring feedback mechanism. Unlike traditional biomimetic models that rely on a single motor drive, have a fixed structure, and closed function, this embodiment proposes for the first time a dual-power-source ventricular drive structure. By combining a motor pump and a gas-liquid converter, it simulates different ventricular physiological states, enhancing the realism and regulatory capacity of the pulsation. Employing a multi-channel fluid path switching structure and modular compartment design, it can freely reconfigure multiple pathways such as systemic circulation and pulmonary circulation, adapting to various pathological or population models. Simultaneously, it integrates a dual-regulation module for vascular resistance and compliance, as well as an artificial lung gas exchange structure, achieving a more human-like dynamic response and heat and mass exchange function. This system possesses high integration, flexible scalability, and engineering adaptability, providing a unified, efficient, and low-cost testing platform for medical devices such as artificial hearts, artificial lungs, valves, and vascular stents.

[0064] The above description is merely a preferred embodiment of the present invention and is not intended to limit the invention. Various modifications and variations can be made to the present invention by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the scope of protection of the present invention.

[0065] While the specific embodiments of the present invention have been described above in conjunction with the accompanying drawings, this is not intended to limit the scope of protection of the present invention. Those skilled in the art should understand that various modifications or variations that can be made by those skilled in the art without creative effort based on the technical solutions of the present invention are still within the scope of protection of the present invention.

Claims

1. An in vitro simulated cyclic testing system driven by dual power sources, characterized in that, include: Heart module, lung module, and vascular branch module; The heart module includes a parallel-connected motor pump branch and a gas-liquid converter branch, which serve as the power sources for the motor pump branch and the gas-liquid converter, respectively. The motor pump branch and the gas-liquid converter branch are connected to the simulated ventricular cavity through reversing valves. The reversing valves are used to switch the flow direction of the in vitro simulated circulation test loop to select whether the simulated ventricular cavity is driven by the motor pump or the gas-liquid converter, thereby simulating different pressure waveforms and pulsation rhythms of the ventricle.

2. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: The motor pump set branch includes an isolated gas accumulator, a first electro-proportional switching valve, a container, a motor pump set, a second electro-proportional switching valve, an electro-proportional pressure reducing valve, and an overflow valve, which are connected in sequence through pipelines. An isolated gas accumulator is used to simulate pressure blood storage in the branch chamber of the left atrial motor pump unit; The first proportional valve simulates the diastolic process of the ventricle, and the second proportional valve simulates the systolic process of the left ventricle. The opening and closing times of the first and second proportional valves are opposite; when one opens, the other closes.

3. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 2, characterized in that: When the first electro-proportional switching valve opens, the simulated blood in the isolated gas accumulator flows into container one under the action of its internal gas pressure, realizing the release of volume during diastole; when the second electro-proportional switching valve opens, the motor pump unit starts to draw in simulated blood from container one and pressurizes it for output, forming a blood jet during systole.

4. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 2, characterized in that: The electric pump unit uses a DC motor and a centrifugal pump.

5. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: The motor pump group branch constructed for the left ventricle includes an isolation gas accumulator I, a first electro-proportional switching valve I, a second container, a motor pump group I, a second electro-proportional switching valve I, and a third electro-proportional pressure reducing valve, which are connected in sequence through pipelines. The output of the third electro-proportional pressure reducing valve is divided into two branches. The first branch is connected to the isolation gas accumulator I through a third shut-off valve, and the second branch flows to the aortic simulated pathway through a one-way valve III. The third electro-proportional pressure reducing valve is also connected to a first overflow valve. Alternatively, for the motor pump group branch constructed for the right ventricle, it includes an isolation gas accumulator II, a first electro-proportional switching valve II, a first container, a motor pump group II, a second electro-proportional switching valve II, and a fourth electro-proportional pressure reducing valve connected in sequence through pipelines. The output of the fourth electro-proportional pressure reducing valve is divided into two branches. The first branch is connected to the isolation gas accumulator II through the fourth shut-off valve, and the second branch flows to the pulmonary artery simulation pathway through the one-way valve II. The fourth electro-proportional pressure reducing valve is also connected to a second overflow valve.

6. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: The gas-liquid converter branch includes a gas-liquid converter and a gas supply passage; the liquid chamber of the gas-liquid converter is connected to a simulated passage of artery and vein through a shut-off valve, and the gas supply passage is used to provide the operating power of the gas-liquid converter; the gas supply passage includes a gas-liquid converter, a speed control valve, a two-position three-way solenoid valve, an electro-proportional pressure reducing valve, a pneumatic triplet, and a gas source connected in sequence.

7. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: The reversing valve is a two-position three-way handle type reversing valve, which is installed at the branch inlet of the motor pump group branch and the gas-liquid converter branch.

8. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: It also includes an artificial heart, which uses a centrifugal blood pump structure driven by a magnetic levitation motor.

9. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: The lung module includes an isolated gas accumulator III and a two-position three-way handle-type reversing valve IV connected in sequence. One output of the two-position three-way handle-type reversing valve IV is connected to a cooler, and the other is connected to a fourth adjustable flow valve connected to the output of the pulmonary vein. The cooler is connected to the output of the pulmonary vein through a first adjustable flow valve. The output of the pulmonary vein is connected to a fourth container used to simulate the left atrium. The lung module also includes an air source II, a pneumatic triplet II, a one-way valve VI, and a gas mixer connected in sequence; the pure oxygen supplied by the air source II is cleaned and filtered by the pneumatic triplet II and checked by the one-way valve VI, and then mixed with air in the gas mixer before being introduced into the cooling pipe of the cooler.

10. The in vitro simulated cyclic testing system driven by dual power sources as described in claim 1, characterized in that: A second flow meter, a pressure gauge V, an isolation gas accumulator IV, and a third adjustable flow valve are installed on the connection passage between the output end of the pulmonary vein and the fourth container.

Images