A vascular flow simulation device for a systemic / pulmonary double circulation system based on hydraulic drive

Abstract

The present invention relates to the technical field of biomedicine, and particularly relates to a vascular flow simulation device for a systemic / pulmonary double circulation system based on hydraulic drive. It includes a systemic circulation simulation area, a pulmonary circulation simulation area, and a cardiac pulsation simulation area; by controlling solenoid valve I, solenoid valve II, solenoid valve III, solenoid valve IV, solenoid valve V, and solenoid valve VI, the cardiac pulsation simulation area simulates the blood pressure conditions during the isovolumetric contraction period, rapid ejection period, slow ejection period, pre-diastolic period, and diastolic period of the heart, and changing the switching frequency of the solenoid valve can change the simulated heart rate; at the same time, the systemic circulation simulation area is used to simulate the systemic circulation of the human body, and the pulmonary circulation simulation area is used to simulate the pulmonary circulation of the human body. Therefore, the present invention studies the situation when the systemic circulation and the pulmonary circulation interact. In addition, the present invention uses one power source to achieve the drive control of the systemic circulation and the pulmonary circulation, avoiding the problem that it is difficult for two power sources to be synchronized.

Description

Technical Field

[0001] The present invention relates to the field of biomedical technologies, and in particular, to a vascular flow simulation device for the systemic / pulmonary double circulation system based on hydraulic drive. Background Art

[0002] The blood circulation system is continuously driven by the beating of the heart to circulate blood in blood vessels. A good working state of the blood circulation system is a condition for the survival of the body. Related diseases caused by vascular lesions will seriously endanger human health. However, in the process of vascular disease research, the research cycle is long and the research progress is slow. Therefore, it is of great significance to study an in vitro blood circulation simulation device.

[0003] At present, most in vitro blood circulation simulation devices simulate the systemic circulation or the pulmonary circulation separately, and there are limitations in studying the interaction between the systemic and pulmonary circulations. A few devices that can simulate the systemic and pulmonary circulations simultaneously are obtained by connecting the systemic circulation or the pulmonary circulation systems in series, and they have the following disadvantages:

[0004] (1) The systemic circulation and the pulmonary circulation each use a power source, and in this case, the power sources often cannot be synchronized. When using air as the power source, due to the compressibility of air, the accuracy of the device is reduced, and the elastic membrane used will produce fatigue, reducing the repeatability of the experiment.

[0005] (2) In the simulation of blood pressure during the cardiac cycle, only the systolic and diastolic phases are simulated, lacking further simulation. If a peristaltic pump or a blood pump is used to simulate blood flow pulsation, its adjustment range is small, and the pulsation generated is different from the real physiological waveform.

[0006] (3) The simulation of ventricular compliance is lacking, and the impact generated by the rapid contraction of the ventricle will reduce the service life of the pipeline. If air is used to simulate the ventricular compliance, a large volume of air is required, resulting in a large structural volume of the ventricular simulation cavity.

[0007] (4) A throttle valve is used to simulate peripheral resistance, and the blood vessel radius is adjusted through the throttle valve to change the blood vessel resistance. However, the sudden contraction and expansion of the pipe diameter will bring an impact, making the simulated blood flow velocity unstable. In addition, the adjustment accuracy of the throttle valve cannot meet the adjustment requirements, and the simulated blood after passing through the throttle valve requires a long pipeline to fully develop the flow. Summary of the Invention

[0008] The purpose of the present invention is to provide a vascular flow simulation device for the systemic / pulmonary double circulation system based on hydraulic drive, which can provide a reliable in vitro simulation experiment platform for the hemodynamic research of human blood circulation in various states and clinical medical teaching.

[0009] The specific technical solution of the present invention is as follows: A vascular flow simulation device for a systemic / pulmonary double circulation system based on hydraulic drive, comprising a systemic circulation simulation area 2, a pulmonary circulation simulation area 3, and a cardiac pulsation simulation area 1;

[0010] The cardiac pulsation simulation area 1 includes a gear pump 101, an electromagnetic reversing valve I 102, an electromagnetic reversing valve II 103, an electromagnetic reversing valve III 104, an electromagnetic reversing valve IV 105, an electromagnetic reversing valve V 106, an electromagnetic reversing valve VI 107, a relief valve I 108, a relief valve II 109, a check valve I 110, a check valve II 111, a left ventricular simulation cavity 112, and a right ventricular simulation cavity 113;

[0011] The outlet of the gear pump 101 is respectively connected to the inlets of the electromagnetic reversing valve I 102 and the electromagnetic reversing valve II 103 through pipelines,

[0012] The outlet of the electromagnetic reversing valve I 102 is respectively connected to the relief valve I 108 and the check valve I 110 through pipelines,

[0013] The outlet of the magnetic reversing valve II is respectively connected to the relief valve II 109 and the check valve II 111 through pipelines,

[0014] The outlet of the check valve I 110 is respectively connected to the electromagnetic reversing valve III 104 and the left ventricular simulation cavity 112 through pipelines, and the outlet of the left ventricular simulation cavity 112 is connected to the inlet of the electromagnetic reversing valve V 106 through a pipeline,

[0015] The outlet of the check valve II 111 is respectively connected to the electromagnetic reversing valve IV 105 and the right ventricular simulation cavity 113 through pipelines, and the outlet of the right ventricular simulation cavity 113 is connected to the inlet of the electromagnetic reversing valve VI 107 through a pipeline,

[0016] The inlet of the gear pump 101, the outlet of the relief valve I 108, and the outlet of the relief valve II 109 are connected through a four-way I pipeline;

[0017] The inlet of the four-way I, the outlet of the electromagnetic reversing valve III 104, and the outlet of the electromagnetic reversing valve IV 105 are connected to the system inlet through a four-way II pipeline;

[0018] The systemic circulation simulation area 2 includes an aortic simulation cavity 21, a rectifier I 22, a flow sensor I 23, a peripheral resistance simulation pipeline, a rectifier II 26, a venous simulation cavity 27, and a left atrial simulation cavity 28 connected in sequence through pipelines. The peripheral resistance simulation pipeline is used to simulate various resistances suffered by blood when flowing in the blood vessels of the systemic circulation;

[0019] The pulmonary circulation simulation area 3 includes a pulmonary artery simulation cavity 31, a rectifier III 32, a flow sensor II 33, a pulmonary resistance simulation pipeline, a rectifier IV 34, a pulmonary vein simulation cavity 35, and a right atrium simulation cavity 36 that are sequentially connected through pipelines. The pulmonary resistance simulation pipeline is used to simulate the resistance suffered by blood when flowing in the blood vessels of the pulmonary circulation;

[0020] The outlet of the left atrium simulation cavity 28 and the outlet of the right atrium simulation cavity 36 are connected to the system outlet through pipelines;

[0021] During operation, by controlling the opening and closing of the electromagnetic directional valve I 102, electromagnetic directional valve II 103, electromagnetic directional valve III 104, electromagnetic directional valve IV 105, electromagnetic directional valve V 106, and electromagnetic directional valve VI 107, the cardiac pulsation simulation area 1 simulates the blood pressure conditions in the isovolumetric contraction period, rapid ejection period, slow ejection period, pre-diastolic period, and diastolic period of the heart. Changing the switching frequency of the electromagnetic directional valve can change the simulated heart rate; at the same time, the systemic circulation simulation area 2 is used to simulate the systemic circulation of the human body, and the pulmonary circulation simulation area 3 is used to simulate the pulmonary circulation of the human body.

[0022] Furthermore, the peripheral resistance simulation pipeline and the pulmonary resistance simulation pipeline have the same structure, both including two parallel pipelines, and a resistance valve 24 and a check valve III 25 are sequentially provided on each pipeline;

[0023] Each resistance valve 24 includes a valve body 241, an adjusting rod 242, and a valve core 243 made of porous material copper foam. The upper end of the valve body 241 is hermetically connected to the valve cover through a sealing ring. An outlet is provided in the middle of the valve body 241, and an inlet is provided at the lower part of the valve body 241.

[0024] The adjusting rod 242 is vertically inserted into the valve body 241 through thread fitting, and the lower end of the adjusting rod 242 is connected to the valve core 243. By adjusting the position of the adjusting rod 242, the relative position between the valve core 243 and the outlet of the resistance valve 24 is changed.

[0025] Furthermore, each rectifier I 22 and rectifier II 26 has the same structure, both including a cylindrical sleeve 221 and rectifying plates 222 uniformly arranged in the sleeve 221. Each rectifying plate 222 is in the shape of a regular hexagonal cylinder, each rectifying plate 222 is coaxially arranged with the sleeve 221, and rectifying holes are uniformly opened on each side plate of the regular hexagon.

[0026] Furthermore, the aortic simulation cavity 21 and the pulmonary artery simulation cavity 31 have the same structure, both including an arterial cavity body 211, an arterial cavity piston 212, and an arterial displacement sensor 213. Inlets and outlets are respectively provided at the lower part of the arterial cavity body 211, and an adjusting hole is provided at the upper end of the arterial cavity body 211;

[0027] The arterial cavity piston 212 is fitted inside the arterial cavity 211. The arterial displacement sensor 213 is vertically inserted into the arterial cavity 211, and the lower end of the arterial displacement sensor 213 is inserted onto the arterial cavity piston 212 through a magnetic ring.

[0028] Furthermore, the venous simulation cavity 27, the left atrium simulation cavity 28, the pulmonary vein simulation cavity 35, and the right atrium simulation cavity 36 are all open cylindrical containers, and the inner walls of the containers are provided with scales.

[0029] Furthermore, the left ventricle simulation cavity 112 and the right ventricle simulation cavity 113 have the same structure, and both include a ventricle cavity 1121, a ventricle cavity piston 1122, a ventricle displacement sensor 1123, and a spring 1124. Inlets and outlets are respectively opened in the lower parts of the ventricle cavities 1121. The ventricle cavity piston 1122 is fitted inside the ventricle cavity 1121. The ventricle displacement sensor 1123 is vertically inserted into the ventricle cavity 1121, and the lower end of the ventricle displacement sensor 1123 is inserted onto the ventricle cavity piston 1122 through a magnetic ring. A spring 1124 is sleeved on the ventricle displacement sensor 1123 corresponding to the upper end of the ventricle cavity piston 1122. The upper end of the spring 1124 is positioned and connected through a boss on the end cover of the ventricle cavity 1121, and the lower end of the spring 1124 is positioned and connected through a boss on the upper end of the ventricle cavity piston 1122.

[0030] Furthermore, the one-way valve I 110, the one-way valve II 111, and each one-way valve III 25 are all elastic diaphragm one-way valves, so that their starting pressures are small, and the elastic diaphragms can absorb and buffer impact forces.

[0031] The beneficial technical effects of the present invention are as follows:

[0032] (1) The hydraulic-driven body / lung double-circulation system blood vessel flow simulation device of the present invention includes a systemic circulation simulation area, a pulmonary circulation simulation area, and a heart pulsation simulation area; it realizes the simultaneous simulation of the systemic and pulmonary circulations in the blood circulation system to study the situation when the systemic and pulmonary circulations interact with each other. At the same time, a single power source, namely a gear pump, can be used to control the systemic and pulmonary circulations with different pressures, avoiding the problem that it is difficult for two power sources to be synchronized.

[0033] (2) The hydraulic-driven body / lung double-circulation system blood vessel flow simulation device of the present invention uses a gear pump, ventricle simulation cavities, and an electromagnetic directional valve to simulate the heart pumping blood. The gear pump supplies liquid to the ventricle simulation cavities. The ventricle simulation cavities store energy. When the electromagnetic directional valve is opened, the ventricle simulation cavities eject blood, and the simulation of blood pressure during isovolumetric contraction, rapid ejection, slow ejection, early diastole, and diastole is realized by changing the opening and closing sequence of the electromagnetic directional valve.

[0034] (3) In the vascular flow simulation device of the hydraulic-driven systemic / pulmonary double circulation system of the present invention, a spring is used to simulate the compliance of the ventricular simulation cavity in the left ventricular simulation cavity and the right ventricular simulation cavity. Compliance is the ratio of the volume change to the pressure change. Combining the state equation of the gas and Hooke's law, the spring stiffness required for simulating the compliance can be obtained, and thus the specific parameters of the spring can be obtained; the gear pump pumps blood into the left ventricular simulation cavity and the right ventricular simulation cavity to increase the internal pressure, and the energy in the loop is converted into the elastic potential energy of the spring for storage, and the piston in the ventricular cavity moves upward; after the one-way valve I and the one-way valve II are opened, the left ventricular simulation cavity and the right ventricular simulation cavity squeeze the simulated blood into the subsequent pipeline. The displacement sensor and the magnetic ring are used in combination to measure the rising height of the piston in the ventricular cavity, and the pressure in the ventricular simulation cavity can be calculated from the spring stiffness. Among them, the stiffness coefficient of the spring can be very large, so the volume of the ventricular simulation cavity is small, the adjustment range is wide, and the repeatability is high.

[0035] (4) In the vascular flow simulation device of the hydraulic-driven systemic / pulmonary double circulation system of the present invention, a resistance valve using porous medium foam copper as the valve core is designed. The foam copper has a dispersing and buffering effect on the fluid, reducing the harm of the water hammer effect to the pipeline. The designed resistance valve can flexibly adjust the volume of the liquid flowing through the foam copper to set different resistances. At the same time, the rectifier I, the rectifier II, the rectifier III, and the rectifier IV enable the simulated blood to form a fully developed flow in a short length. Description of the Drawings

[0036] Figure 1 is the structural schematic diagram of the present invention.

[0037] Figure 2 is the control principle and experimental area diagram of the present invention.

[0038] Figure 3 is the cross-sectional view of the ventricular simulation cavity of the present invention.

[0039] Figure 4 is the cross-sectional view of the arterial simulation cavity of the present invention.

[0040] Figure 5 is the schematic diagram of the rectifier of the present invention.

[0041] Figure 6 is the schematic diagram of the rectifier plate of the rectifier of the present invention.

[0042] Figure 7 is the cross-sectional view of the peripheral resistance simulation valve of the present invention.

[0043] Figure 8 is the AMESim software simulation diagram of the cardiac cycle of the present invention.

[0044] Figure 9 is the solenoid valve switch sequence diagram of the present invention.

[0045] Among them: the heart pulsation simulation area 1, gear pump 101, electromagnetic directional valve I 102, electromagnetic directional valve II 103, electromagnetic directional valve III 104, electromagnetic directional valve IV 105, electromagnetic directional valve V 106, electromagnetic directional valve VI 107, overflow valve I 108, overflow valve II 109, check valve I 110, check valve II 111, left ventricle simulation cavity 112, right ventricle simulation cavity 113, ventricle cavity body 1121, ventricle cavity piston 1122, ventricle displacement sensor 1123, spring 1124, systemic circulation simulation area 2, aorta simulation cavity 21, artery cavity body 211, artery cavity piston 212, artery displacement sensor 213, rectifier I 22, sleeve 221, rectifying plate 222, flow sensor I 23, resistance valve 24, valve body 241, adjusting rod 242, valve core 243, check valve III 25, rectifier II 26, vein simulation cavity 27, left atrium simulation cavity 28, pulmonary circulation simulation area 3, pulmonary artery simulation cavity 31, rectifier III 32, flow sensor II 33, rectifier IV 34, pulmonary vein simulation cavity 35, right atrium simulation cavity 36. Specific implementation manners

[0046] In order to make the objectives, technical solutions and advantages of the present invention clearer and more understandable, the present invention will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific implementation manners described herein are only used to explain the present invention and are not used to limit the present invention. Embodiment 1

[0047] See Figure 1 , a vascular flow simulation device for a systemic / pulmonary double circulation system based on hydraulic drive, comprising a systemic circulation simulation area 2, a pulmonary circulation simulation area 3, and a heart pulsation simulation area 1;

[0048] The heart pulsation simulation area 1 includes a gear pump 101, an electromagnetic directional valve I 102, an electromagnetic directional valve II 103, an electromagnetic directional valve III 104, an electromagnetic directional valve IV 105, an electromagnetic directional valve V 106, an electromagnetic directional valve VI 107, an overflow valve I 108, an overflow valve II 109, a check valve I 110, a check valve II 111, a left ventricle simulation cavity 112, and a right ventricle simulation cavity 113;

[0049] The outlet of the gear pump 101 is respectively connected to the inlets of the electromagnetic directional valve I 102 and the electromagnetic directional valve II 103 through pipelines,

[0050] The outlet of the electromagnetic directional valve I 102 is respectively connected to the overflow valve I 108 and the check valve I 110 through pipelines,

[0051] The outlet of the electromagnetic directional valve II 103 is respectively connected to the overflow valve II 109 and the check valve II 111 through pipelines,

[0052] The outlet of the one-way valve Ⅰ 110 is respectively connected to the electromagnetic directional valve Ⅲ 104 and the left ventricle simulation cavity 112 through pipelines. The outlet of the left ventricle simulation cavity 112 is connected to the inlet of the electromagnetic directional valve Ⅴ 106 through a pipeline.

[0053] The outlet of the one-way valve Ⅱ 111 is respectively connected to the electromagnetic directional valve Ⅳ 105 and the right ventricle simulation cavity 113 through pipelines. The outlet of the right ventricle simulation cavity 113 is connected to the inlet of the electromagnetic directional valve Ⅵ 107 through a pipeline.

[0054] The inlet of the gear pump 101, the outlet of the relief valve Ⅰ 108 and the outlet of the relief valve Ⅱ 109 are connected through a four-way Ⅰ pipeline.

[0055] The inlet of the four-way Ⅰ, the outlet of the electromagnetic directional valve Ⅲ 104 and the outlet of the electromagnetic directional valve Ⅳ 105 are connected to the system inlet through a four-way Ⅱ pipeline.

[0056] The systemic circulation simulation area 2 includes an aortic simulation cavity 21, a rectifier Ⅰ 22, a flow sensor Ⅰ 23, a peripheral resistance simulation pipeline, a rectifier Ⅱ 26, a venous simulation cavity 27 and a left atrium simulation cavity 28 that are sequentially connected through pipelines. The peripheral resistance simulation pipeline is used to simulate various resistances suffered by blood when flowing in the blood vessels of the systemic circulation.

[0057] The pulmonary circulation simulation area 3 includes a pulmonary artery simulation cavity 31, a rectifier Ⅲ 32, a flow sensor Ⅱ 33, a pulmonary resistance simulation pipeline, a rectifier Ⅳ 34, a pulmonary vein simulation cavity 35 and a right atrium simulation cavity 36 that are sequentially connected through pipelines. The pulmonary resistance simulation pipeline is used to simulate the resistance suffered by blood when flowing in the blood vessels of the pulmonary circulation. The outlet of the left atrium simulation cavity 28 and the outlet of the right atrium simulation cavity 36 are connected to the system outlet through pipelines.

[0058] During operation, by controlling the opening and closing of the electromagnetic directional valve Ⅰ 102, the electromagnetic directional valve Ⅱ 103, the electromagnetic directional valve Ⅲ 104, the electromagnetic directional valve Ⅳ 105, the electromagnetic directional valve Ⅴ 106 and the electromagnetic directional valve Ⅵ 107, the heart pulsation simulation area 1 simulates the blood pressure conditions of the isovolumic contraction period, rapid ejection period, slow ejection period, pre-diastolic period and diastolic period of the heart. Changing the switching frequency of the electromagnetic directional valve can change the simulated heart rate. At the same time, the systemic circulation simulation area 2 is used to simulate the systemic circulation of the human body, and the pulmonary circulation simulation area 3 is used to simulate the pulmonary circulation of the human body.

[0059] See Figure 3, the left ventricular simulation cavity 112 and the right ventricular simulation cavity 113 have the same structure, both including a ventricular cavity 1121, a ventricular cavity piston 1122, a ventricular displacement sensor 1123 and a spring 1124. The lower parts of the ventricular cavity 1121 are respectively provided with an inlet and an outlet. The ventricular cavity piston 1122 is fitted in the ventricular cavity 1121. The ventricular displacement sensor 1123 is vertically inserted into the ventricular cavity 1121, and the lower end of the ventricular displacement sensor 1123 is inserted on the ventricular cavity piston 1122 through a magnetic ring. A spring 1124 is sleeved on the ventricular displacement sensor 1123 corresponding to the upper end of the ventricular cavity piston 1122, and the upper end of the spring 1124 is positioned and connected through the end cover boss of the ventricular cavity 1121, and the lower end of the spring 1124 is positioned and connected through the boss at the upper end of the ventricular cavity piston 1122.

[0060] Compliance is the ratio of the volume change to the pressure change. Combining the state equation of the gas and Hooke's law, the stiffness of the spring 1124 required for simulating compliance can be obtained, and then the specific parameters of the spring 1124 can be obtained. The gear pump 101 pumps blood into the left ventricular simulation cavity 112 and the right ventricular simulation cavity 113, increasing the internal pressure. The energy in the circuit is converted into the elastic potential energy of the spring 1124 for storage, and the ventricular cavity piston 1122 moves upward. After the one-way valve I 110 and the one-way valve II 111 are opened, the left ventricular simulation cavity 112 and the right ventricular simulation cavity 113 squeeze the simulated blood into the subsequent pipeline. The displacement sensor 1123 and the magnetic ring are used in combination to measure the rising height of the ventricular cavity piston 1122, and the pressure in the simulation cavity can be calculated from the stiffness of the spring 1124.

[0061] See Figure 4 , the aortic simulation cavity 21 and the pulmonary artery simulation cavity 31 have the same structure, both including an arterial cavity 211, an arterial cavity piston 212 and an arterial displacement sensor 213. The lower parts of the arterial cavity 211 are respectively provided with an inlet and an outlet, and an adjustment hole is provided at the upper end of the arterial cavity 211;

[0062] The arterial cavity piston 212 is fitted in the arterial cavity 211, and the arterial displacement sensor 213 is vertically inserted into the arterial cavity 211, and the lower end of the arterial displacement sensor 213 is inserted on the arterial cavity piston 212 through a magnetic ring.

[0063] The arterial displacement sensor 213 and the magnetic ring are used in combination to measure the rising height of the arterial displacement sensor 213. According to the gas state equation, the pressure in the simulation cavity can be calculated. The adjustment hole can be connected to an air bag to adjust the gas-liquid ratio in the simulation cavity to simulate different compliances, and the adjustment hole is closed during the working state.

[0064] See Figure 5 and Figure 6, the structures of each of the rectifier Ⅰ 22 and the rectifier Ⅱ 26 are the same, each including a cylindrical sleeve 221 and rectifying plates 222 uniformly arranged within the sleeve 221. Each rectifying plate 222 is in the shape of a regular hexagonal cylinder, and each rectifying plate 222 is coaxially arranged with the sleeve 221, and rectifying holes are uniformly formed on each side plate of the regular hexagon. The rectifying holes on the rectifying plate 222 are used for pressure exchange and pressure balance, simulating the rectification of blood so that it is fully developed within a relatively short distance.

[0065] See Figure 7 , the structures of the peripheral resistance simulation pipeline and the pulmonary resistance simulation pipeline are the same, each including two parallel pipelines or other pipelines connected in parallel according to system requirements, and a resistance valve 24 and a check valve Ⅲ 25 are successively arranged on each pipeline;

[0066] Each of the resistance valves 24 includes a valve body 241, an adjusting rod 242, and a valve core 243 made of porous material copper foam. The upper end of the valve body 241 is hermetically connected to a valve cover through a sealing ring. An outlet is formed in the middle of the valve body 241, and an inlet is formed in the lower part of the valve body 241.

[0067] The adjusting rod 242 is vertically inserted into the valve body 241 through threaded fit, and the lower end of the adjusting rod 242 is connected to the valve core 243. By adjusting the position of the adjusting rod 242, the relative position between the valve core 243 and the outlet of the resistance valve 24 is changed.

[0068] When the volume of the simulated blood flowing through the valve core 243 increases, the resistance increases. When the heart rate and the displacement of the gear pump 101 remain unchanged, the pressures in the aortic simulation cavity 21 and the pulmonary artery simulation cavity 31 increase, and the system flow rate will decrease; when the volume of the simulated blood flowing through the valve core 243 decreases, the resistance decreases. When the heart rate and the displacement of the gear pump 101 remain unchanged, the pressures in the aortic simulation cavity 21 and the pulmonary artery simulation cavity 31 decrease, and the system flow rate increases.

[0069] The venous simulation cavity 27, the left atrium simulation cavity 28, the pulmonary vein simulation cavity 35, and the right atrium simulation cavity 36 are all open cylindrical containers, and scales are provided on the inner wall of the containers. The scales can quantify the height difference between the simulated blood in the cavity and the pipeline, and thus the pressure of the simulated blood in the subsequent pipeline can be monitored.

[0070] The check valve Ⅰ 110, the check valve Ⅱ 111, and each check valve Ⅲ 25 are all elastic diaphragm check valves, which have a small starting pressure, and the elastic diaphragm can absorb and buffer the impact force.

[0071] See Figure 8 Figure 9, by controlling the opening and closing of electromagnetic directional valve Ⅰ102, electromagnetic directional valve Ⅱ103, electromagnetic directional valve Ⅲ104, electromagnetic directional valve Ⅳ105, electromagnetic directional valve Ⅴ106, and electromagnetic directional valve Ⅵ107, the blood pressure conditions during the isovolumic contraction period, rapid ejection period, slow ejection period, early diastolic period, and diastolic period of the simulated heart are realized. Changing the switching frequency of the electromagnetic directional valve can change the simulated heart rate, specifically as follows:

[0072] At the beginning of the isovolumic contraction period, electromagnetic directional valve Ⅰ102 and electromagnetic directional valve Ⅱ103 are opened, and electromagnetic directional valve Ⅲ104, electromagnetic directional valve Ⅳ105, electromagnetic directional valve Ⅴ106, and electromagnetic directional valve Ⅵ107 are closed. The gear pump 101 pumps blood into the left ventricular simulation cavity 112 and the right ventricular simulation cavity 113, and the pressure in the left ventricular simulation cavity 112 and the right ventricular simulation cavity 113 rises rapidly.

[0073] After the isovolumic contraction period is completed, electromagnetic directional valve Ⅴ106 and electromagnetic directional valve Ⅵ107 are opened to simulate the opening process of the arterial valve. The ventricular simulation cavity rapidly ejects blood into the arterial simulation cavity, and the rising trend of the blood pressure in the ventricular simulation cavity slows down and tends to the limiting pressure of relief valve Ⅰ108 and relief valve Ⅱ109. The blood pressure in the arterial simulation cavity rises with the rise of the blood pressure in the ventricular simulation cavity, and enters the rapid ejection period.

[0074] After the rapid ejection period ends, electromagnetic directional valve Ⅰ102 and electromagnetic directional valve Ⅱ103 are closed, and the gear pump 101 no longer supplies liquid to the ventricular simulation cavity. The blood pressure in the ventricular simulation cavity drops slowly, and the speed of the simulated blood stored therein injected into the arterial simulation cavity slows down, entering the slow ejection period.

[0075] After the slow ejection period ends, electromagnetic directional valve Ⅲ104 and electromagnetic directional valve Ⅳ105 are opened, and electromagnetic directional valve Ⅴ106 and electromagnetic directional valve Ⅵ107 are closed. The remaining pressure in the ventricular simulation cavity is quickly released through electromagnetic directional valve Ⅲ104 and electromagnetic directional valve Ⅳ105 from the connecting pipeline. The blood pressure in the aortic simulation cavity is no longer affected by the blood pressure in the ventricular simulation cavity, and due to arterial compliance, its internal blood pressure drops slowly, entering the early diastolic period.

[0076] After the early diastolic period is completed, electromagnetic directional valve Ⅰ102 and electromagnetic directional valve Ⅱ103 are opened, and the gear pump 101 supplies blood to the ventricular simulation cavity, entering the diastolic period.

[0077] After the diastolic period ends, a cycle of heart contraction and relaxation is completed. Changing the switching frequency of electromagnetic directional valve Ⅰ102, electromagnetic directional valve Ⅱ103, electromagnetic directional valve Ⅲ104, electromagnetic directional valve Ⅳ105, electromagnetic directional valve Ⅴ106, and electromagnetic directional valve Ⅵ107 per minute can change the heart rate. Embodiment 2

[0078] Such as Figure 2, a vascular flow simulation device of a body / lung double circulation system based on hydraulic drive in Embodiment 1 is divided into a heart experiment area 4, an artery experiment area 5, and a peripheral experiment area 6.

[0079] The heart experiment area 4 includes a solenoid directional valve III 104, a solenoid directional valve IV 105, a relief valve I 108, a relief valve II 109, a check valve I 110, a check valve II 111, a left ventricle simulation cavity 112, and a right ventricle simulation cavity 113.

[0080] The artery experiment area 5 includes a solenoid directional valve V 106, a solenoid directional valve VI 107, an aorta simulation cavity 21, a pulmonary artery simulation cavity 31, and the artery simulation pipelines where they are located.

[0081] When simulating aortic valve and pulmonary valve insufficiency, throttle valves can be connected in parallel at the solenoid directional valve V 106 and the solenoid directional valve VI 107.

[0082] When simulating aortic valve and pulmonary valve stenosis, a resistance valve 24 can be connected in series between the solenoid directional valve V 106, the solenoid directional valve VI 107, the aorta simulation cavity 21, and the pulmonary artery simulation cavity 31.

[0083] When simulating main and pulmonary artery sclerosis, the compliance can be changed by changing the gas volume of the aorta simulation cavity 21 and the pulmonary artery simulation 31.

[0084] When simulating an aneurysm, the aneurysm simulation device is connected to the interface downstream of the aorta simulation cavity 21 and in front of the peripheral resistance simulation pipeline to simulate the pulsating load applied to the aneurysm.

[0085] The peripheral experiment area 6 includes a resistance valve 24 and a check valve 25, and the number of parallel pipelines can be changed according to the experimental requirements.

[0086] When simulating the hepatic portal vein, the hepatic portal vein simulation device is connected after the peripheral resistance simulation valve 24, and the resistance of the peripheral resistance simulation valve 24 is adjusted to simulate the resistance in front of the hepatic portal vein, and the pulsating load applied to the hepatic portal vein is simulated.

[0087] The heart experiment area 4, the artery experiment area 5, and the peripheral experiment area 6 cooperate to conduct experiments. For example, when simulating heart failure, the starting pressures of the relief valve I 108 and the relief valve II 109 are reduced, so that the set pressures of the left ventricle simulation cavity 112 and the right ventricle simulation cavity 113 are reduced, and further the pressures in the aorta simulation cavity 21 and the pulmonary artery simulation cavity 31 are reduced; the volume of the foam copper through which the simulated blood flows through the resistance valve 24 is increased to reduce the system flow rate; the simulated blood in the venous simulation cavity 27 and the pulmonary vein simulation cavity 35 is increased to raise the liquid level; the switching frequency of the two-way solenoid directional valve per minute is increased to accelerate the set heart rate.

[0088] Those skilled in the art can easily understand that the above is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present invention shall be included within the protection scope of the present invention.

Claims

1. A vascular flow simulation device for a systemic / pulmonary double circulation system based on hydraulic drive, characterized in that: It includes a systemic circulation simulation area (2), a pulmonary circulation simulation area (3), and a cardiac pulsation simulation area (1); The cardiac pulsation simulation area (1) includes a gear pump (101), an electromagnetic directional valve I (102), an electromagnetic directional valve II (103), an electromagnetic directional valve III (104), an electromagnetic directional valve IV (105), an electromagnetic directional valve V (106), an electromagnetic directional valve VI (107), a relief valve I (108), a relief valve II (109), a check valve I (110), a check valve II (111), a left ventricular simulation cavity (112), and a right ventricular simulation cavity (113); The outlet of the gear pump (101) is respectively connected to the inlets of the electromagnetic directional valve I (102) and the electromagnetic directional valve II (103) through pipelines; The outlet of the electromagnetic directional valve I (102) is respectively connected to the relief valve I (108) and the check valve I (110) through pipelines; The outlet of the electromagnetic directional valve II (103) is respectively connected to the relief valve II (109) and the check valve II (111) through pipelines; The outlet of the check valve I (110) is respectively connected to the electromagnetic directional valve III (104) and the left ventricular simulation cavity (112) through pipelines, and the outlet of the left ventricular simulation cavity (112) is connected to the inlet of the electromagnetic directional valve V (106) through a pipeline; The outlet of the check valve II (111) is respectively connected to the electromagnetic directional valve IV (105) and the right ventricular simulation cavity (113) through pipelines, and the outlet of the right ventricular simulation cavity (113) is connected to the inlet of the electromagnetic directional valve VI (107) through a pipeline; The inlet of the gear pump (101), the outlet of the relief valve I (108), and the outlet of the relief valve II (109) are connected through a four-way I pipeline; The inlet of the four-way I, the outlet of the electromagnetic directional valve III (104), and the outlet of the electromagnetic directional valve IV (105) are connected to the system inlet through a four-way II pipeline; The systemic circulation simulation area (2) includes an aortic simulation cavity (21), a rectifier I (22), a flow sensor I (23), a peripheral resistance simulation pipeline, a rectifier II (26), a venous simulation cavity (27), and a left atrial simulation cavity (28) that are sequentially connected through pipelines. The peripheral resistance simulation pipeline is used to simulate various resistances suffered by blood when flowing in the blood vessels of the systemic circulation; The pulmonary circulation simulation area (3) includes a pulmonary artery simulation cavity (31), a rectifier III (32), a flow sensor II (33), a pulmonary resistance simulation pipeline, a rectifier IV (34), a pulmonary vein simulation cavity (35), and a right atrial simulation cavity (36) that are sequentially connected through pipelines. The pulmonary resistance simulation pipeline is used to simulate the resistance suffered by blood when flowing in the blood vessels of the pulmonary circulation; The outlets of the left atrial simulation cavity (28) and the right atrial simulation cavity (36) are connected to the system outlet through pipelines; During operation, by controlling the opening and closing of electromagnetic directional valve I (102), electromagnetic directional valve II (103), electromagnetic directional valve III (104), electromagnetic directional valve IV (105), electromagnetic directional valve V (106), and electromagnetic directional valve VI (107), the blood pressure conditions of the isovolumic contraction period, rapid ejection period, slow ejection period, pre-diastolic period, and diastolic period of the heart are simulated in the cardiac pulsation simulation area (1). Changing the switching frequency of the electromagnetic directional valve can change the simulated heart rate; at the same time, the systemic circulation simulation area (2) is used to simulate the systemic circulation of the human body, and the pulmonary circulation simulation area (3) is used to simulate the pulmonary circulation of the human body.

2. The vascular flow simulation device of a body / lung double circulation system based on hydraulic drive according to claim 1, characterized in that: The structures of the peripheral resistance simulation pipeline and the pulmonary resistance simulation pipeline are the same, and a resistance valve (24) and a check valve III (25) are sequentially provided on each pipeline. Each of the resistance valves (24) includes a valve body (241), an adjusting rod (242), and a valve core (243) made of porous material foam copper. The upper end of the valve body (241) is hermetically connected to the valve cover through a sealing ring. An outlet is provided in the middle of the valve body (241), and an inlet is provided at the lower part of the valve body (241). The adjusting rod (242) is vertically inserted into the valve body (241) through thread fitting, and the lower end of the adjusting rod (242) is connected to the valve core (243). By adjusting the position of the valve core (243) with the adjusting rod (242), the relative position between the valve core (243) and the outlet of the resistance valve (24) is changed.

3. The vascular flow simulation device of a systemic / pulmonary double circulation system based on hydraulic drive according to claim 1, characterized in that: The structures of each of the rectifiers I (22) and rectifiers II (26) are the same, and each includes a cylindrical sleeve (221) and rectifying plates (222) uniformly arranged in the sleeve (221). Each rectifying plate (222) is in the shape of a regular hexagonal cylinder, and each rectifying plate (222) is coaxially arranged with the sleeve (221), and rectifying holes are uniformly provided on each side plate of the regular hexagon.

4. The vascular flow simulation device of a body / lung double circulation system based on hydraulic drive according to claim 1, wherein: The aortic simulation cavity (21) and the pulmonary artery simulation cavity (31) have the same structure, and each includes an arterial cavity body (211), an arterial cavity piston (212), and an arterial displacement sensor (213). Inlets and outlets are respectively provided at the lower part of the arterial cavity body (211), and an adjustment hole is provided at the upper end of the arterial cavity body (211); the arterial cavity piston (212) is fitted in the arterial cavity body (211), and the arterial displacement sensor (213) is vertically inserted into the arterial cavity body (211), and the lower end of the arterial displacement sensor (213) is inserted onto the arterial cavity piston (212) through a magnetic ring.

5. The vascular flow simulation device of a body / lung double circulation system based on hydraulic drive according to claim 1, wherein: The venous simulation cavity (27), the left atrium simulation cavity (28), the pulmonary vein simulation cavity (35), and the right atrium simulation cavity (36) are all open cylindrical containers, and scales are provided on the inner walls of the containers.

6. The vascular flow simulation device of a systemic / pulmonary double circulation system based on hydraulic drive according to claim 1, wherein: The left ventricular simulation cavity (112) and the right ventricular simulation cavity (113) have the same structure, and both include a ventricular cavity body (1121), a ventricular cavity piston (1122) and a ventricular displacement sensor (1123). An inlet and an outlet are respectively arranged at the lower part of the ventricular cavity body (1121). The ventricular cavity piston (1122) is arranged in the ventricular cavity body (1121) in a matching manner. The ventricular displacement sensor (1123) is vertically inserted into the ventricular cavity body (1121), and the lower end of the ventricular displacement sensor (1123) is inserted onto the ventricular cavity piston (1122) through a magnetic ring. A spring (1124) is sleeved on the ventricular displacement sensor (1123) corresponding to the upper end of the ventricular cavity piston (1122), and the upper end of the spring (1124) is positioned and connected through the end cover boss of the ventricular cavity body (1121), and the lower end of the spring (1124) is positioned and connected through the boss at the upper end of the ventricular cavity piston (1122).

7. The vascular flow simulation device for the systemic / pulmonary double circulation system based on hydraulic drive according to claim 2, wherein: The check valve I (110), the check valve II (111) and each check valve III (25) are all elastic diaphragm check valves.

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