Test device for artificial heart pumps

Abstract

The present application relates to the technical field of artificial heart pump, and discloses a testing device for artificial heart pump.The testing device for artificial heart pump comprises a simulated left atrium cavity, a simulated bicuspid valve, a simulated left ventricle cavity, a simulated aortic valve, a simulated aorta cavity and a simulated vein cavity for forming a blood circulation flow system, so that the blood circulation process in the human body can be simply and accurately reproduced, the hemodynamic characteristics of the natural heart of the human body under different degrees of failure and different physiological states can be simulated, the auxiliary blood pumping effect of the artificial heart pump under different degrees of failure of the simulated left ventricle cavity and the simulated left atrium cavity and under different physiological states can be tested, and the hydraulic performance experiment and the extracorporeal blood circulation experiment of the artificial heart pump can be carried out based on the testing device, so that the accuracy of the testing result of the artificial heart pump and the integrity of the testing performance are ensured.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of artificial heart pumps, in particular to a testing device for artificial heart pumps. BACKGROUND

[0002] Heart failure is a common problem faced by the world today. In addition to heart transplantation treatment, artificial heart pumps have become a hope and effective treatment approach for many patients to prolong their survival. In the development process of artificial heart pumps, a series of processes need to be experienced, including theoretical design, simulation verification, experimental testing, animal experiments and clinical trials. The experimental testing is a relatively key link.

[0003] At present, simulation technology means is usually used to simulate the hemodynamic characteristics of the natural heart of the human body under different degrees of failure and under different physiological states, so as to simulate and test the auxiliary pumping effect of the artificial heart pump under different degrees of failure of the natural heart and under different physiological states.

[0004] However, the actual working environment of the natural heart and the artificial heart pump in the human body is quite complex, and is easily affected by sudden conditions and external interference, which cannot guarantee the accuracy and reliability of the test results of the simulated artificial heart pump.

[0005] Therefore, there is an urgent need for a testing device for artificial heart pumps to solve the above problems. SUMMARY

[0006] One object of the present application is to provide a testing device for artificial heart pumps, which can accurately simulate the actual working environment of the natural heart and the artificial heart pump in the human body, so as to accurately test the auxiliary pumping effect of the artificial heart pump under different degrees of failure of the natural heart and under different physiological states, and ensure high accuracy and reliability of the test results of the artificial heart pump.

[0007] To achieve this object, the present application adopts the following technical solutions:

[0008] The testing device for artificial heart pumps comprises a testing table and the following components respectively arranged on the testing table:

[0009] a simulated left ventricular cavity for pumping blood to a simulated aorta and capable of adjusting the blood flow rate;

[0010] a simulated left atrial cavity connected to the inlet of the simulated left ventricular cavity, the simulated left atrial cavity being used for returning blood to the simulated left ventricular cavity and capable of adjusting the blood flow rate;

[0011] a simulated mitral valve connected between the simulated left ventricle cavity and the simulated left atrium cavity, the simulated mitral valve being configured to define a one-way flow of the simulated blood pumped by the simulated left atrium cavity to the simulated left ventricle cavity;

[0012] a simulated aortic valve connected to an outlet of the simulated left ventricle cavity, the simulated aortic valve being configured to define a one-way flow of the simulated blood pumped by the simulated left ventricle cavity to the simulated aorta, and a mechanical heart pump connected between the outlet of the simulated left ventricle cavity and an inlet of the simulated aortic valve, the mechanical heart pump being capable of pumping the simulated blood from the simulated left ventricle cavity to the simulated aorta;

[0013] a simulated aorta cavity connected to an outlet of the simulated aortic valve, the simulated aorta cavity being configured to simulate the compliance of the aorta;

[0014] a simulated vein cavity having one end connected to an outlet of the simulated aorta cavity and the other end connected to an inlet of the simulated left atrium cavity, the simulated vein cavity being configured to simulate the storage of blood.

[0015] Optionally, a manual ball valve is connected between the mechanical heart pump and the simulated left ventricle cavity, the manual ball valve being configured to control the communication or blockage between the mechanical heart pump and the simulated left ventricle cavity.

[0016] Optionally, the simulated left atrium cavity has the same structure as the simulated left ventricle cavity; the simulated left ventricle cavity comprises:

[0017] a driving motor;

[0018] a first hollow cylinder connected to the test bench, the first hollow cylinder being configured to contain the simulated blood, and a first piston being sealingly and slidably arranged in the first hollow cylinder, an output shaft of the driving motor being configured to be connected to the first piston to drive the first piston to reciprocally slide along the height direction of the first hollow cylinder, so that the first piston extrudes the simulated blood downward to be pumped out of the first hollow cylinder to the simulated aorta, and when the first piston moves upward to reset, the simulated blood flows from the simulated left atrium cavity into the first hollow cylinder.

[0019] Optionally, the simulated left ventricle cavity further comprises:

[0020] a sliding table, the output shaft of the driving motor being connected to the sliding table to drive the sliding table to reciprocally slide along the height direction of the first hollow cylinder;

[0021] a sliding rod having one end connected to the sliding table and the other end slidingly and sealingly inserted into the first hollow cylinder and connected to the first piston.

[0022] As an option, the structure of the simulated mitral valve is the same as the structure of the simulated aortic valve; the simulated aortic valve comprises:

[0023] The first and second sub-acrylic flanges are oppositely arranged, the first sub-acrylic flange is connected to the outlet of the simulated left ventricular cavity, and the second sub-acrylic flange is respectively connected to the inlet of the simulated aortic cavity and the outlet of the artificial heart pump;

[0024] The silica gel gasket is connected between the first and second sub-acrylic flanges, and the simulated blood is limited to flow unidirectionally from the first sub-acrylic flange to the second sub-acrylic flange through the silica gel gasket.

[0025] As an option, the simulated aortic cavity comprises:

[0026] The second hollow cylinder is connected to the test bench, and the simulated blood is arranged in the second hollow cylinder;

[0027] The air pressure regulating valve is arranged at the top end of the second hollow cylinder, and the air pressure regulating valve is used to adjust the air capacity in the second hollow cylinder, and the air capacity in the second hollow cylinder is in a linear relationship with the compliance of the simulated aortic valve;

[0028] The laser range finder is arranged at the top end of the second hollow cylinder, and the laser range finder is used to detect the liquid level of the simulated blood in the second hollow cylinder, and the air capacity in the second hollow cylinder corresponds to the liquid level of the simulated blood in the second hollow cylinder.

[0029] As an option, the simulated venous cavity comprises:

[0030] The third hollow cylinder is connected to the test bench, and the simulated blood is stored in the third hollow cylinder.

[0031] As an option, the test device of the artificial heart pump further comprises:

[0032] The ultrasonic blood flow meter is connected between the simulated aortic cavity and the simulated venous cavity, and the ultrasonic blood flow meter is used to detect the blood flow size in the simulated vein.

[0033] As an option, the test device of the artificial heart pump further comprises:

[0034] The electric proportional valve is connected between the simulated aortic cavity and the ultrasonic blood flow meter, and the electric proportional valve is used to adjust the percentage of the valve opening to simulate the change of the flow resistance of the circulating blood.

[0035] As an alternative, the test device of the artificial heart pump further comprises:

[0036] a control module, which is in control connection with the driving motor and the electric proportional valve respectively;

[0037] a pressure sensor for measuring blood pressure information, and the simulated left ventricular cavity, the simulated aorta and the simulated vein are respectively provided with the pressure sensor.

[0038] The present application has the following advantages:

[0039] The simulated left ventricular cavity, the simulated left atrial cavity, the simulated mitral valve, the simulated aortic valve, the simulated aortic cavity and the simulated venous cavity are formed by mechanical structure, so that the simulated blood can form a circulating flow between the simulated left atrial cavity, the simulated mitral valve, the simulated left ventricular cavity, the simulated aortic valve, the simulated aortic cavity, the simulated venous cavity and the simulated left atrial cavity, and the blood circulation process of the natural heart of the human body is reproduced more accurately by designing the mechanical structure to simulate the key organs in the human blood circulation. BRIEF DESCRIPTION OF DRAWINGS

[0040] Figure 1 is a structural schematic diagram of the test device of the artificial heart pump provided by the present application.

[0041] Reference signs:

[0042] 10-simulated left ventricular cavity; 101-driving motor; 102-first hollow cylinder; 103-first piston; 104-sliding rod; 105-simulated blood;

[0043] 2-simulated left atrial cavity; 3-simulated mitral valve; 4-simulated aortic valve; 5-simulated aortic cavity; 51-second hollow cylinder; 52-air pressure regulating valve; 53-laser range finder; 6-simulated venous cavity; 7-hand-operated ball valve; 8-one-way valve; 9-electric proportional valve; 11-artificial heart pump; 12-pressure sensor; 13-simulated aorta; 14-simulated vein; 15-ultrasonic blood flow meter;

[0044] 161-industrial computer; 162-data acquisition card. DETAILED DESCRIPTION

[0045] In order to make the technical problems solved by the present application, the technical solutions adopted and the technical effects achieved more clear, the technical solutions of the present application will be further described below in combination with the drawings and through specific embodiments.

[0046] In the description of the present application, unless explicitly defined and limited, the terms "connected", "connected", "fixed" should be understood broadly, for example, it can be fixedly connected, or it can be detachably connected, or it can be integrated; it can be mechanically connected, or it can be electrically connected; it can be directly connected, or it can be indirectly connected through an intermediate medium; it can be the internal communication of two elements or the interaction relationship between two elements. For those skilled in the art, the specific meaning of the above terms in the present application can be understood according to the specific circumstances.

[0047] In the present application, unless explicitly defined and limited, the first feature "on" or "under" the second feature can include that the first and second features are in direct contact, or that the first and second features are not in direct contact but are in contact through another feature between them. Moreover, the first feature "on", "above" and "above" the second feature includes that the first feature is directly above and obliquely above the second feature, or only indicates that the horizontal height of the first feature is higher than that of the second feature. The first feature "below", "below" and "below" the second feature includes that the first feature is directly below and obliquely below the second feature, or only indicates that the horizontal height of the first feature is less than that of the second feature.

[0048] In the description of the present embodiment, the terms "up", "down", "left", "right" and other orientation or position relationships are based on the orientation or position relationship shown in the drawings, and are only for the convenience of description and simplification of operation, and do not indicate or imply that the indicated structure or element must have a particular orientation, be constructed and operated in a particular orientation, and therefore cannot be understood as a limitation on the present application. In addition, the terms "first", "second" are only used to distinguish in description and have no special meaning.

[0049] The embodiment provides a testing device for an artificial heart pump, which can accurately simulate the actual working environment of a natural heart and the artificial heart pump in a human body, so that the auxiliary blood pumping effect of the artificial heart pump under different degrees of natural heart failure and different physiological states can be accurately tested, and the testing result of the artificial heart pump obtained through simulation can be reversely verified, so that the accuracy and reliability of the testing result of the artificial heart pump are ensured.

[0050] Specifically, as shown in the figure, Figure 1 The testing device for the artificial heart pump comprises a test table and a simulation left ventricular cavity 10, a simulation left atrial cavity 2, a simulation mitral valve 3, a simulation aortic valve 4, a simulation aortic cavity 5 and a simulation venous cavity 6 which are arranged on the test table; the simulation left ventricular cavity 10 can simulate the beating blood pumping of the natural left ventricular cavity of the human body, and is used for pumping blood to the simulation aorta 13 and adjusting the blood flow size; the simulation left atrial cavity 2 can simulate the beating blood pumping of the natural left atrial cavity of the human body, is connected to the inlet of the simulation left ventricular cavity 10, and is used for pumping blood back to the simulation left ventricular cavity 10 and adjusting the blood flow size; the simulation mitral valve 3 can simulate the natural mitral valve of the human body, is connected between the simulation left ventricular cavity 10 and the simulation left atrial cavity 2, and is used for limiting the one-way flow of the simulation blood 105 pumped by the simulation left atrial cavity 2 to the simulation left ventricular cavity 10; the simulation aortic valve 4 can simulate the natural aortic valve of the human body, is connected to the outlet of the simulation left ventricular cavity 10, and is used for limiting the one-way flow of the simulation blood 105 pumped by the simulation left ventricular cavity 10 to the simulation aorta 13; and the artificial heart pump 11 is connected between the outlet of the simulation left ventricular cavity 10 and the outlet of the simulation aortic valve 4, can pump the simulation blood 105 from the simulation left ventricular cavity 10 to the simulation aorta 13, and is used for auxiliary blood pumping; the simulation aortic cavity 5 is connected to the outlet of the simulation aortic valve 4, and can simulate the compliance of the aorta in the human body; one end of the simulation venous cavity 6 is connected to the outlet of the simulation aortic cavity 5, and the other end of the simulation venous cavity 6 is connected to the inlet of the simulation left atrial cavity 2, and the simulation venous cavity 6 can simulate the storage of blood in the veins of the human body.

[0051] The test device of the artificial heart pump in the embodiment can accurately simulate the key organs in the human blood circulation relative to the prior art. The simulated left ventricular cavity 10, the simulated left atrial cavity 2, the simulated mitral valve 3, the simulated aortic valve 4, the simulated aortic cavity 5, and the simulated venous cavity 6 are formed by mechanical structures, so that the simulated blood 105 can form a circulating flow between the simulated left atrial cavity 2, the simulated mitral valve 3, the simulated left ventricular cavity 10, the simulated aortic valve 4, the simulated aortic cavity 5, the simulated venous cavity 6, and the simulated left atrial cavity 2 in sequence, thereby realizing the simulation of the key organs in the human blood circulation by designing mechanical structures, and accurately reproducing the blood circulation process of the natural heart of the human body. Meanwhile, the artificial heart pump 11 is connected between the outlet of the simulated left ventricular cavity 10 and the outlet of the simulated aortic valve 4, so that the artificial heart pump 11 can pump the simulated blood 105 from the simulated left ventricular cavity 10 to the simulated aorta 13. In addition, the blood flow rate pumped by the simulated left ventricular cavity 10 and the simulated left atrial cavity 2 can be adjusted according to the changes of the natural heart in different degrees of failure and different physiological states, so as to accurately simulate the actual working environment of the natural heart and the artificial heart pump 11 in the human body, accurately simulate the hemodynamic characteristics of the natural heart in different degrees of failure and different physiological states, accurately test the auxiliary blood pumping effect of the artificial heart pump 11 in the natural heart in different degrees of failure and different physiological states, and verify the test results obtained by the artificial heart pump 11 through simulation according to the test results, thereby ensuring the accuracy and reliability of the test results of the artificial heart pump 11.

[0052] It is worth noting that, since the simulated left ventricular cavity 10, the simulated left atrial cavity 2, the simulated mitral valve 3, the simulated aortic valve 4, the simulated aortic cavity 5, and the simulated venous cavity 6 formed by the mechanical structures can accurately simulate the key organs in the human blood circulation, the hydraulic performance test and the blood circulation test of the artificial heart pump 11 can be carried out outside the human body based on the test device of the artificial heart pump in the embodiment, thereby ensuring the comprehensiveness and integrity of the test of the artificial heart pump 11.

[0053] Further, as Figure 1As shown, a manual ball valve 7 is connected between the artificial heart pump 11 and the simulated left ventricular chamber 10. The manual ball valve 7 is used to control the connection or blockage between the artificial heart pump 11 and the simulated left ventricular chamber 10. This allows for control of the interventional pumping of the artificial heart pump 11 and the extent of interventional pumping according to varying degrees of failure and physiological states of the simulated left ventricular chamber 10. In this embodiment, a common manual ball valve 7 in the prior art is employed. The use of a manually operated manual ball valve 7 increases the reliability of the connection or blockage between the artificial heart pump 11 and the simulated left ventricular chamber 10, thereby better ensuring the accuracy and reliability of the test results of the artificial heart pump 11.

[0054] The structures of the simulated left ventricular cavity 10 and the simulated left atrial cavity 2 are described in detail below:

[0055] The simulated left ventricular cavity is the most critical structure in the entire artificial heart pump test device. By simulating the left ventricular cavity, the heart beat can be simulated to complete blood pumping. In the current simulated left ventricular cavity, the volume of gas in the compressed container is usually used to simulate the heart beat to complete blood pumping. However, this simulation method is prone to slow response and is difficult to match the rapid response characteristics of the human body's natural heart. In addition, it is difficult to adjust the blood flow rate pumped out by the simulated left ventricular cavity using the output method of the air pump, and thus it is difficult to change the hemodynamic characteristics of the simulated left ventricular cavity pumping blood, which cannot meet the task requirements of in-depth research on artificial heart pumps.

[0056] In order to solve the above problems, Figure 1 As shown, the simulated left ventricular cavity 10 in this embodiment includes a drive motor 101 and a first hollow cylinder 1021; wherein the first hollow cylinder 1021 is fixedly connected to the test bench, simulated blood 105 is set in the first hollow cylinder 1021, and a first piston 1031 is sealed and slidably set in the first hollow cylinder 1021. The output shaft of the drive motor 101 is used to connect with the first piston 1031. The drive motor 101 is used to drive the first piston 1031 to slide back and forth along the height direction of the first hollow cylinder 1021, so that the first piston 1031 squeezes the simulated blood 105 downward and pumps it out along the outlet of the first hollow cylinder 1021 to the simulated aorta 13. When the first piston 1031 moves upward and resets, the simulated blood 105 flows from the simulated left atrial cavity 2 into the first hollow cylinder 1021. The drive motor 101 can specifically be a linear motor or a stepping motor. In this embodiment, the first hollow cylinder 1021 is a sealed cavity made of acrylic material.

[0057] The movement stroke and movement frequency of the first piston 1031 are controlled by the driving motor 101 to control the blood flow output size and heart rate size of the simulated left ventricular cavity 10, and the natural heart periodic contraction and diastolic function can be accurately simulated through the simulated left ventricular cavity 10, and the simulation mode of driving the first piston 1031 by the driving motor 101 is rapid in response and high in accuracy, so as to match the natural heart of the human body. The natural heart is rapid in response, and various different working conditions of the natural heart can be simulated, so that the hemodynamic characteristics of the simulated left ventricular cavity 10 can be easily changed, and the task demand of in-depth research on the artificial heart pump 11 can be met.

[0058] Among them, the various different working conditions of the natural heart are simulated, for example, the natural heart is in a sleep state, a resting state, a slight exercise state, a severe exercise state, 10% heart failure, 20% heart failure, 30% heart failure, 40% heart failure or 50% heart failure.

[0059] Further, as shown in Figure 1 , the simulated left ventricular cavity 10 further comprises a sliding table and a sliding rod 104; wherein the output shaft of the driving motor 101 is connected with the sliding table, and the driving motor 101 is used to drive the sliding table to reciprocate along the height direction of the first hollow cylinder 1021; one end of the sliding rod 104 is fixedly connected with the sliding table, the other end of the sliding rod 104 is slidably and downwardly sealingly inserted into the first hollow cylinder 1021, and the other end of the sliding rod 104 is fixedly connected with the first piston 1031, so as to drive the first piston 1031 to reciprocate in the first hollow cylinder 1021 through the sliding rod 104. The sliding table is a linear sliding table.

[0060] Specifically, as shown in Figure 1 , when the simulated left ventricular cavity 10 works, the driving motor 101 drives the sliding table to move downward along the height direction of the first hollow cylinder 1021, so that the sliding table drives the sliding rod 104 to push the first piston 1031 to move downward, so that the first piston 1031 extrudes the simulated blood 105 in the first hollow cylinder 1021 downward, that is, the contraction action of the left ventricular cavity in the human body can be simulated, so that the simulated left ventricular cavity 10 pumps out the simulated blood 105 towards the simulated aorta 13; after the contraction of the simulated left ventricular cavity 10 ends, the driving motor 101 drives the sliding table to move upward along the height direction of the first hollow cylinder 1021, so that the sliding table drives the first piston 1031 to move upward through the sliding rod 104, to control the volume of the first hollow cylinder 1021, so that the pressure in the first hollow cylinder 1021 decreases, at this time, the simulated liquid flows into the first hollow cylinder 1021 from the simulated left atrial cavity 2, that is, the diastolic action of the left ventricular cavity in the human body can be simulated.

[0061] Further, by controlling the reciprocating frequency and reciprocating stroke of the sliding table through the driving motor 101, the pumping characteristics of the simulated left ventricular cavity 10 under normal heart, different degrees of heart failure and different physiological conditions can be simulated; specifically, since the maximum volume of the normal left ventricular cavity in the human body is about 300 mL, and the single outward pumping volume of the left ventricular cavity is about 70 mL; therefore, in the present embodiment, the inner diameter of the first hollow cylinder 1021 is 80 mm, the height of the first hollow cylinder 1021 is 150 mm, and the rated load of the sliding table is 35 kg, the travel speed of the sliding table is 1.5 m / s, and the driving motor 101 is an 800w stepper motor, thereby meeting the application requirements of simulating different heart rates and different degrees of heart failure under the condition of simulating the left ventricular cavity 10, and further ensuring that the simulated left ventricular cavity 10 can more accurately simulate the left ventricular cavity in the human body.

[0062] Specifically, as shown in Figure 1 the structure and working principle of the simulated left atrial cavity 2 are the same as those of the simulated left ventricular cavity 10, only the working parameters of the reciprocating stroke and reciprocating frequency of the first piston 1031 are different; therefore, in the present embodiment, the structure and working principle of the simulated left atrial cavity 2 are not described in detail, and the above description of the structure and working principle of the simulated left ventricular cavity 10 can be referred to, so as to ensure that the simulated left atrial cavity 2 can accurately simulate the left atrial cavity in the human body.

[0063] The structures of the simulated aortic valve 4 and the simulated mitral valve 3 are described in detail as follows:

[0064] At present, most of the simulated aortic valves in the test devices for simulating blood circulation outside the body simply use a one-way valve structure to simulate the one-way flow function, although the one-way flow function can be satisfied, but the flow resistance and the along-the-way loss of the pure mechanical one-way valve structure are large, resulting in low accuracy of the obtained blood pressure information; and the one-way valve structure does not have the physiological characteristics of the aortic valve in the human body, and it is difficult to accurately simulate the aortic valve in the human body.

[0065] In order to solve the above problems, the simulated aortic valve 4 in the present embodiment includes a silica gel gasket, a first acrylic flange and a second acrylic flange arranged oppositely; wherein the first acrylic flange is connected to the outlet of the first hollow cylinder 1021 of the simulated left ventricular cavity 10, and the second acrylic flange is connected to the inlet of the simulated aortic cavity 5 and the outlet of the artificial heart pump 11 respectively; the silica gel gasket is connected between the first acrylic flange and the second acrylic flange, and the simulated blood 105 is limited to flow through the first acrylic flange to the second acrylic flange through the silica gel gasket in one direction. In the present embodiment, the thickness of the silica gel gasket is about 0.5mm-1mm, and the inner diameter of the silica gel gasket is about 25mm.

[0066] By setting the three-opening structure of the simulation aortic valve 4 composed of the first acrylic flange, the silica gel gasket and the second acrylic flange, on the one hand, the one-way flow effect of the simulation blood 105 in circulation can be ensured; on the other hand, the silica gel gasket can make the simulation aortic valve 4 have the physiological characteristics of the aortic valve in the human body, so that the aortic valve in the human body can be accurately simulated, and the whole artificial heart pump test device can better restore the blood circulation system in the human body, and ensure that the test result of the artificial heart pump 11 is more accurate and reliable.

[0067] Specifically, as shown in Figure 1 , the structure and working principle of the simulation mitral valve 3 are the same as those of the simulation aortic valve 4, and both of them are to ensure the one-way flow of the simulation blood 105 in circulation; here, the structure and working principle of the simulation mitral valve 3 are not described in detail, and the above description of the structure and working principle of the simulation aortic valve 4 can be referred to, so that the simulation mitral valve 3 can accurately simulate the mitral valve in the human body.

[0068] The structure of the simulation aortic cavity 5 is described in detail as follows:

[0069] Specifically, as shown in Figure 1 , the simulation aortic cavity 5 includes a second hollow cylinder 51, which is fixedly connected to the test table, and the simulation blood 105 is arranged in the second hollow cylinder 51. In this embodiment, the second hollow cylinder 51 is a sealed cavity made of acrylic material, and the inner diameter of the second hollow cylinder 51 is 140 mm, the height of the second hollow cylinder 51 is 150 mm, and the volume of the second hollow cylinder 51 is about 2300 mL.

[0070] Specifically, in order to simulate the compliance of the aorta in the human body under various different states, it is necessary to establish a relationship expression between the air capacity change in the second hollow cylinder 51 and the compliance value of the aorta, that is, the relationship formula 1 based on the compliance of the aorta:

[0071]

[0072] ΔV air in the relationship formula 1 represents the change amount of the air capacity in the second hollow cylinder 51, with the unit of mL; ΔP air represents the change amount of the air pressure in the second hollow cylinder 51, with the unit of mmHg, and C represents the compliance value of the aorta; after the simulation left ventricular cavity 10 pumps out the simulation blood 105 to the simulation aorta 13 each time, the air capacity and air pressure in the second hollow cylinder 51 will change, and it is assumed that the air capacity and air pressure in the second hollow cylinder 51 before pumping blood are V air1 , Pair1 , the air volume and air pressure in the second hollow cylinder 51 after pumping blood are V air2 , P air2 , and the following relationship 2 is obtained:

[0073]

[0074] Since the air in the second hollow cylinder 51 is in a sealed cavity, according to the perfect gas state equation, the following relationship 3 is obtained:

[0075] P air1 ·V air1 =P air2 ·V air2

[0076] From the above relationship 2 and relationship 3, the following relationship 4 is obtained:

[0077] P air1 ·V air1 =(P air1 +ΔP air )·(V air1 -C·ΔP air )

[0078] The above relationship 4 is simplified to obtain the following relationship 5:

[0079] V air1 =C(P air1 +ΔP air )

[0080] With respect to the atmospheric pressure P air1 , the change amount ΔP air of the air pressure in the second hollow cylinder 51 is often particularly small, so (P air1 +ΔP air ) can be approximately regarded as the atmospheric pressure, that is, (P air1 +ΔP air ) is a constant value; then the following relationship 5 can be obtained: the compliance value C of the aorta and the air volume in the second hollow cylinder 51 have a linear relationship, so the compliance of the aorta can be directly modified by modifying the air volume in the second hollow cylinder 51, and the only variable affecting the air volume in the second hollow cylinder 51 is the liquid level of the simulated blood 105 in the second hollow cylinder 51, so the compliance of the aorta can be changed by modifying the liquid level of the simulated blood 105 in the second hollow cylinder 51.

[0081] Therefore, as shown in Figure 1As shown, the simulated aorta cavity 5 in this embodiment further includes an air pressure regulating valve 52 and a laser rangefinder 53; wherein, the air pressure regulating valve 52 is provided at the top end of the second hollow cylinder 51, and the air pressure regulating valve 52 is used to adjust the air volume in the second hollow cylinder 51, and the air volume in the second hollow cylinder 51 is linearly related to the compliance of the simulated aorta 13; the laser rangefinder 53 is provided at the top end of the second hollow cylinder 51, and the laser rangefinder 53 is used to detect the liquid level of the simulated blood 105 in the second hollow cylinder 51, and the air volume in the second hollow cylinder 51 corresponds to the liquid level of the simulated blood 105 in the second hollow cylinder 51.

[0082] Specifically, since compliance is the most critical feature of the aorta in the human body, in order to simulate the compliance of the aorta in the human body by simulating the aortic cavity 5, the principle of gas compressibility is used in the second hollow cylinder 51, and the air volume in the second hollow cylinder 51 is adjusted by the air pressure regulating valve 52. That is, by directly adjusting the liquid level of the simulated blood 105 in the second hollow cylinder 51, the different compliances of the aorta in the human body can be accurately simulated, so as to better restore the blood circulation system in the human body.

[0083] The structure of the simulated venous cavity 6 is described in detail below:

[0084] Specifically, if Figure 1 As shown, the simulated venous cavity 6 includes a third hollow cylinder, which is fixedly connected to the test bench and is used to store simulated blood 105. Considering that the total amount of blood in human veins is approximately 3.6L, in this embodiment, the third hollow cylinder is designed as an acrylic sealed cavity with an inner diameter of 180mm and a height of 220mm, resulting in a total capacity of 5.6L. This ensures that the simulated venous cavity 6 can meet the functional simulation requirements of venous blood storage during blood circulation. A one-way valve 8 is connected between the simulated venous cavity 6 and the simulated left atrial cavity 2 to limit the flow of simulated blood 105 from the simulated venous cavity 6 to the simulated left atrial cavity 2.

[0085] It is worth noting that the veins in the human body are organs and tissues that recover and store blood. The compliance of the veins is particularly large compared to the compliance of the aorta and arteries at all levels. Therefore, when designing the simulated aortic cavity 5, the influence of the compliance of the veins can be ignored. It is only necessary to ensure that the simulated venous cavity 6 can simulate the characteristics of venous blood storage.

[0086] The structures of the ultrasonic blood flowmeter 15, the electric proportional valve 9, the pressure sensor 12 and the control module are described in detail below:

[0087] Further, since the blood flow information in the simulated vein 14 needs to be obtained during the test; therefore, as shown in Figure 1 the test device of the artificial heart pump in this embodiment also includes an ultrasonic blood flow meter 15 connected between the simulated aortic cavity 5 and the simulated vein cavity 6, which is used to detect the blood flow in the simulated vein 14. Specifically, the ultrasonic blood flow meter 15 includes a detection host and a probe communicatively connected to the detection host, which is used to detect the blood flow in the simulated vein 14 and feedback to the detection host. Among them, the detection host specifically refers to all the structures in the ultrasonic blood flow meter 15 except the probe.

[0088] Specifically, the ultrasonic blood flow meter 15 in this embodiment is a flow structure specially used for blood flow measurement, and the specific model of the ultrasonic blood flow meter 15 is T402-TB, and the specific range of the probe is ±12.5L / min, which can meet the measurement requirements of the ultrasonic blood flow meter 15 for blood flow, and can realize real-time monitoring of blood flow.

[0089] Further, since the main influencing factor of the peripheral resistance of the blood circulation in the human body is the radius of the blood vessel, therefore, as shown in Figure 1 the test device of the artificial heart pump in this embodiment also includes an electric proportional valve 9 connected between the second hollow cylinder 51 of the simulated aortic cavity 5 and the third hollow cylinder of the simulated vein cavity 6, which is used to adjust the percentage of the valve opening to simulate the change of the flow resistance of the circulating blood, so that the change of the peripheral resistance of the blood circulation in the human body can be accurately simulated through the electric proportional valve 9. In this embodiment, the specific model of the electric proportional valve 9 is EPV-375B, and the maximum flow coefficient Cv of the electric proportional valve 9 is 1.7.

[0090] Specifically, as shown in Figure 1 the test device of the artificial heart pump also includes a control module and a pressure sensor 12; wherein the control module is respectively connected with the driving motor 101 and the electric proportional valve 9 for controlling, so as to control the start and stop of the driving motor 101 and the electric proportional valve 9, control the driving stroke and driving frequency of the driving motor 101, and control the percentage of the valve opening of the electric proportional valve 9; the pressure sensor 12 is used to measure the blood pressure information, and the pressure sensor 12 is respectively installed in the simulated left ventricular cavity 10, the simulated aorta 13 and the simulated vein 14, so as to obtain the blood pressure information of the simulated left ventricular cavity 10, the blood pressure information of the simulated aorta 13 and the blood pressure information of the simulated vein 14 in the blood circulation in real time, so as to obtain the blood pressure information of each different position in real time.

[0091] In this embodiment, the specific model of the pressure sensor 12 is PX300, the range of the pressure sensor 12 is 0-375mmHg, and the measurement accuracy of the pressure sensor 12 is 0.2%, so that the blood pressure measurement requirements of each position can be met through the pressure sensor 12.

[0092] It is worth noting that, as shown in Figure 1 the simulation left atrial cavity 2, the simulation mitral valve 3, the simulation left ventricular cavity 10, the simulation aortic valve 4, the simulation aortic cavity 5, the electric proportional valve 9, the ultrasonic blood flow instrument 15, the simulation venous cavity 6, the one-way valve 8, and the simulation left atrial cavity 2 are connected in sequence by silica gel pipes to form a complete blood circulation system; and the simulation left ventricular cavity 10, the manual ball valve 7, the artificial heart pump 11, and the simulation aortic valve 4 are also connected by silica gel pipes to form an auxiliary blood pumping branch. Among them, the silica gel pipe can specifically simulate the aorta and veins in the human body.

[0093] Further, as shown in Figure 1 the control module includes a control cabinet, a data acquisition card 162, a physiological recorder, an industrial computer 161, and connecting wires; wherein the controller and the corresponding driver for controlling the two driving motors 101 in the simulation left ventricular cavity 10 and the simulation left atrial cavity 2 are placed in the control cabinet, the industrial computer 161 issues instructions to the controller to complete the action of driving the motor 101 to simulate the beating of the heart; the physiological recorder is in communication connection with the detection host, and the physiological recorder is used to obtain the detection information of the probe and record; the signals of the electric proportional valve 9, the pressure sensor 12, and the two driving motors 101 are acquired by the data acquisition card 162 and transmitted to the industrial computer 161; the physiological recorder separately acquires the detection signals of the detection host of the ultrasonic blood flow instrument 15 and transmits them to the industrial computer 161 through the data acquisition card 162; and on the control interface of the industrial computer 161, the blood flow hemodynamic characteristics of the artificial heart pump 11 under different degrees of heart failure and different physiological states can be obtained by modifying the moving stroke and moving frequency of the first piston 1031 in the simulation left ventricular cavity 10 and the simulation left atrial cavity 2, and the percentage of the valve opening of the electric proportional valve 9, so as to realize the testing purpose of the artificial heart pump 11. The specific model of the physiological recorder in this embodiment is MP160, and the control cabinet and the industrial computer 161 in this embodiment are common control structures in the prior art, and therefore, the control principle of the control cabinet and the industrial computer 161 will not be described in detail here.

[0094] The test device of the artificial heart pump in the embodiment can simulate each key organ in the human blood circulation, ensures that the test device of the artificial heart pump can better restore the blood circulation system in the human body, and can adjust the blood flow size pumped out by the simulated left ventricular cavity 10 and the simulated left atrial cavity 2 according to the change of the natural heart in different degrees of failure and in different physiological states, and can accurately test the auxiliary pumping effect of the artificial heart pump 11 in the natural heart in different degrees of failure and in different physiological states, and ensure the accuracy and reliability of the test results of the artificial heart pump 11.

[0095] The above is only the preferred embodiment of the present application, and for those skilled in the art, according to the idea of the present application, the specific implementation and application range will be changed, and the content of the description should not be understood as the limitation of the present application.

Claims

1. A test device for an artificial heart pump, characterized in that: The invention comprises a test bench and the following components respectively arranged on the test bench: A simulated left ventricular cavity (10) is used to pump blood to a simulated aorta (13) and can adjust the blood flow rate; A simulated left atrial cavity (2) is connected to the inlet of the simulated left ventricular cavity (10), and the simulated left atrial cavity (2) is used to return blood to the simulated left ventricular cavity (10) and can adjust the blood flow rate pumped out; a simulated mitral valve (3) connected between the simulated left ventricular cavity (10) and the simulated left atrial cavity (2), the simulated mitral valve (3) being used to limit the simulated blood (105) pumped out of the simulated left atrial cavity (2) to flow unidirectionally to the simulated left ventricular cavity (10); A simulated aortic valve (4) is connected to the outlet of the simulated left ventricular cavity (10), the simulated aortic valve (4) is used to limit the simulated blood (105) pumped out of the simulated left ventricular cavity (10) to flow unidirectionally to the simulated aorta (13), and an artificial heart pump (11) is connected between the outlet of the simulated left ventricular cavity (10) and the outlet of the simulated aortic valve (4), and the artificial heart pump (11) can pump the simulated blood (105) from the simulated left ventricular cavity (10) to the simulated aorta (13); A simulated aortic cavity (5) is connected to the outlet of the simulated aortic valve (4), and the simulated aortic cavity (5) can simulate the compliance of the aorta; A simulated venous cavity (6), one end of which is connected to the outlet of the simulated aortic cavity (5) and the other end of which is connected to the inlet of the simulated left atrial cavity (2), wherein the simulated venous cavity (6) can simulate a vein to store blood; The structure of the simulated left atrial cavity (2) is the same as that of the simulated left ventricular cavity (10); the simulated left ventricular cavity (10) comprises: Drive motor (101); A first hollow cylinder (1021) is connected to the test bench, wherein simulated blood (105) is provided in the first hollow cylinder (1021), and a first piston (1031) is sealed and slidably provided in the first hollow cylinder (1021), and an output shaft of the drive motor (101) is used to connect with the first piston (1031) to drive the first piston (1031) to slide back and forth along the height direction of the first hollow cylinder (1021), so that the first piston (1031) squeezes the simulated blood (105) downward and pumps it out along the outlet of the first hollow cylinder (1021) to the simulated aorta (13), and when the first piston (1031) moves upward and resets, the simulated blood (105) flows from the simulated left atrial cavity (2) into the first hollow cylinder (1021); The simulated aorta cavity (5) comprises: A second hollow cylinder (51) is connected to the test bench, wherein simulated blood (105) is provided in the second hollow cylinder (51); an air pressure regulating valve (52) disposed at the top end of the second hollow cylinder (51), the air pressure regulating valve (52) being used to adjust the air volume in the second hollow cylinder (51), and the air volume in the second hollow cylinder (51) being linearly related to the compliance of the simulated aorta (13); A laser rangefinder (53) is provided at the top end of the second hollow cylinder (51). The laser rangefinder (53) is used to detect the liquid level of the simulated blood (105) in the second hollow cylinder (51). The air volume in the second hollow cylinder (51) corresponds to the liquid level of the simulated blood (105) in the second hollow cylinder (51).

2. The test device for an artificial heart pump according to claim 1, wherein: A manual ball valve (7) is connected between the artificial heart pump (11) and the simulated left ventricular cavity (10), and the manual ball valve (7) is used to control the connection or blocking between the artificial heart pump (11) and the simulated left ventricular cavity (10).

3. The test device for an artificial heart pump according to claim 1, wherein: The simulated left ventricular cavity (10) further comprises: A slide, the output shaft of the drive motor (101) being connected to the slide, and being used to drive the slide to slide back and forth along the height direction of the first hollow cylinder (1021); A sliding rod (104) has one end connected to the slide platform, and the other end slides downward and is sealedly inserted into the first hollow cylinder (1021) and connected to the first piston (1031).

4. The test device for an artificial heart pump according to any one of claims 1 to 3, characterized in that: The structure of the simulated mitral valve (3) is the same as that of the simulated aortic valve (4); the simulated aortic valve (4) comprises: A first acrylic flange and a second acrylic flange are arranged opposite to each other, wherein the first acrylic flange is connected to the outlet of the simulated left ventricular cavity (10), and the second acrylic flange is connected to the inlet of the simulated aortic cavity (5) and the outlet of the artificial heart pump (11), respectively; A silicone gasket is connected between the first acrylic flange and the second acrylic flange, and the simulated blood (105) is limited to flow through the first acrylic flange and the silicone gasket in a one-way manner to the second acrylic flange.

5. The test device for an artificial heart pump according to any one of claims 1 to 3, characterized in that: The simulated venous cavity (6) comprises: A third hollow cylinder is connected to the test bench, and the third hollow cylinder is used to store simulated blood (105).

6. The test device for an artificial heart pump according to claim 1 or 3, characterized in that: The test device of the artificial heart pump also includes: An ultrasonic blood flow meter (15) is connected between the simulated aortic cavity (5) and the simulated venous cavity (6), and the ultrasonic blood flow meter (15) is used to detect the blood flow in the simulated vein (14).

7. The test device for an artificial heart pump according to claim 6, wherein: The test device of the artificial heart pump also includes: An electric proportional valve (9) is connected between the simulated aortic cavity (5) and the ultrasonic blood flow meter (15). The electric proportional valve (9) is used to adjust the percentage of opening of its valve port to simulate the change in the flow resistance of circulating blood.

8. The test device for an artificial heart pump according to claim 7, wherein: The test device of the artificial heart pump also includes: A control module is respectively connected to the drive motor (101) and the electric proportional valve (9); A pressure sensor (12) is used to measure blood pressure information. The simulated left ventricular cavity (10), the simulated aorta (13), and the simulated vein (14) are respectively equipped with the pressure sensor (12).

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