CN211633745U - In-vitro simulation circulation system for artificial heart test - Google Patents

Abstract

The utility model discloses an external simulation circulation system for artificial heart test, including ventricle simulation subassembly, pulmonary circulation simulation subassembly, body circulation simulation subassembly has realized the simulation of human blood flow state and organ perfusion state. In the simulator of controlling the ventricle, the utility model discloses a flexible connector simulation cardiac muscle uses the shrink and the diastole of elastic element simulation cardiac muscle to use stopper simulation cardiac muscle shrink and diastolic extreme state, realized around the heart when load change the passive regulation of ventricle pulsation state. Simultaneously, through simulating different blood flow path and different organ perfusion levels, the utility model discloses can carry out the test and the optimization of multiple type "artificial heart" (ventricle auxiliary pump) device, objectively test and optimize the hydrodynamics performance of product.

Description

In-vitro simulation circulation system for artificial heart test

Technical Field

The utility model relates to the technical field of medical equipment detection, in particular to an in vitro simulation circulation system for artificial heart test.

Background

The heart failure is used as the final outcome of various cardiovascular diseases, at least 1000 thousands of heart failure patients exist at home, the prognosis of the patients is poor, the mortality rate is high, and the mortality rate within 5 years is up to 60%. Heart transplantation is the first choice for the treatment of end-stage heart failure, but is limited by donor deficiency, and only hundreds of heart transplantation operations are performed annually in China. Therefore, the temporary or permanent replacement of heart transplantation with artificial hearts is a very promising direction of development.

Currently, artificial hearts are classified by type into Left Ventricular Assist Devices (LVADs), Right Ventricular Assist Devices (RVADs), biventricular assist devices (BVADs), and Total Artificial Hearts (TAHs), which are respectively applied to different types of heart failure diseases. During the design and development phase of an artificial heart and before it is put into clinical use, extensive tests must be performed to ensure its safety, effectiveness and durability. The in vitro simulation circulation system can accurately simulate the blood flowing state in a human body, the artificial heart is tested through the in vitro simulation circulation system, the time and the cost of animal experiments can be saved, and meanwhile, the basis is provided for the clinical application of the artificial heart.

In the extracorporeal circulation simulation system, the simulation of the left ventricle and the right ventricle is the core part of the extracorporeal circulation simulation system and is also the difficulty of the extracorporeal circulation simulation system. The simulation of the left and right ventricles requires accurate simulation of the state of ventricular beats during rest, exercise, and heart failure. In the actual heart beating process, the heart beating simulation system is divided into four phases of isovolumetric contraction, ejection, isovolumetric relaxation and filling, and the existing simulated circulatory system at home and abroad is difficult to simulate a Frank-Starling mechanism of myocardial contraction and relaxation, namely a passive regulation mechanism of the beating state when the load around the heart changes.

During use of an actual artificial heart, especially during initial pump speed adjustments, the left and right ventricular flows may be unequal, possibly due to different organ perfusion conditions. At present, extracorporeal circulation simulation systems at home and abroad are closed circulation systems, wherein the flow rates passing through a left ventricle simulator and a right ventricle simulator are equal, which is inconsistent with the actual clinical situation, so that further optimization and improvement are needed.

SUMMERY OF THE UTILITY MODEL

The present invention aims at solving at least one of the technical problems in the related art to a certain extent.

Therefore, the utility model aims to provide an external simulation circulation system for artificial heart test, this system can simulate human blood flow state and organ perfusion state to can external different forms "artificial heart (ventricle auxiliary pump)" product, the hydrodynamics performance of objective test product, thereby can effectively predict different artificial hearts and implant the influence of patient self blood flow state after internal to patient, and solve the problem that exists among the present external circulation simulation system.

In order to achieve the above object, the present invention provides an in vitro simulation circulatory system for artificial heart test, comprising: a ventricular simulation assembly comprising a left ventricular simulator, a right ventricular simulator, first to fourth check valves, and first to twelfth gate valves, wherein the ventricular simulator is used for simulating the pulsating state of the left and right ventricles, and the first to fourth check valves are used for simulating a mitral valve, an aortic valve, a tricuspid valve, and a pulmonary valve, respectively; the first to twelfth gate valves are used for simulating different blood flow paths when the artificial heart is accessed; a pulmonary circulation simulation assembly comprising a first sealed container, a first open container, a first throttle valve, a first flow sensor, a first pressure sensor, a second pressure sensor, wherein the first sealed container is configured to simulate pulmonary artery compliance, the first open container is configured to simulate pulmonary vein compliance, the first throttle valve is configured to simulate pulmonary circulation resistance, and the first flow sensor, the first pressure sensor, and the second pressure sensor are configured to measure pulmonary circulation blood flow, pulmonary artery pressure, and pulmonary vein pressure; a body circulation simulation assembly comprising a perfusion simulator, a second sealed container, a second open container, a second throttle valve, a second flow sensor, a third pressure sensor, a fourth pressure sensor, wherein the perfusion simulator is configured to simulate a perfusion status of an internal body organ, the second sealed container is configured to simulate aortic compliance, the second open container is configured to simulate aortic compliance, the second throttle valve is configured to simulate body circulation resistance, and the second flow sensor, the third pressure sensor, and the fourth pressure sensor are configured to measure a body circulation blood flow, aortic pressure, and aortic venous pressure.

The in-vitro simulation circulation system for the artificial heart test realizes the simulation of the blood flowing state and the organ perfusion state of the human body and provides a standardized test environment for the in-vitro test of the artificial heart; the flexible connector is used for simulating cardiac muscle, so that the passive regulation of the ventricular pulse state is realized when the load changes around the heart; by simulating different blood flow paths and different organ perfusion levels, the artificial heart product with different forms can be externally connected, and the fluid mechanical property of the product can be objectively tested and optimized.

Further, still include: and the control assembly is used for simulating different blood flow paths through controlling the opening and closing states of the gate valve so as to test and optimize various types of artificial heart devices.

Further, the ventricle simulator comprises a linear motor, a flexible connector and a piston cylinder, wherein the linear motor and the piston cylinder are used for simulating heart pulsation, and blood output of the piston cylinder is controlled through driving of the linear motor so as to simulate a human body state; the flexible connector is used for simulating automatic adjustment of cardiac blood output when the front load and the rear load are changed.

Further, the flexible connector comprises an elastic element, a diastole limiter, a contraction limiter, a linear motor connector and a piston cylinder connector, wherein the elastic element is used for simulating the contraction and the relaxation of the cardiac muscle, and the limiter is used for simulating the limit state of the contraction and the relaxation of the cardiac muscle.

Further, the elastic element may be a mechanical spring or a magnetic spring.

Further, the perfusion simulator comprises a third throttle valve and a third open container connected in parallel with the systemic circulation, wherein the liquid level state in the third open container is used for representing organ perfusion insufficiency, perfusion normality and perfusion excess, and simultaneously realizing a non-constant state of blood flow in the extracorporeal simulated circulation system.

Additional aspects and advantages of the invention will be set forth in part in the description which follows and, in part, will be obvious from the description, or may be learned by practice of the invention.

Drawings

The above and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:

fig. 1 is a schematic structural diagram of an extracorporeal simulated circulation system for artificial heart testing according to an embodiment of the present invention;

fig. 2 is a schematic structural diagram of an extracorporeal simulated circulation system for artificial heart testing according to an embodiment of the present invention;

FIG. 3 is a schematic diagram of an extracorporeal simulated circulatory system for artificial heart testing, in accordance with an embodiment of the present invention;

FIG. 4 is a schematic illustration of a Left Ventricular Assist Device (LVAD) test according to a first embodiment of the present invention;

fig. 5 is a schematic diagram of a Right Ventricular Assist Device (RVAD) test according to a first embodiment of the present invention;

fig. 6 is a schematic diagram of a bi-ventricular assist device (BVAD) test according to a first embodiment of the present invention;

fig. 7 is a schematic diagram of a Total Artificial Heart (TAH) test according to a first embodiment of the present invention;

fig. 8 is a schematic view of the operation of the perfusion simulator according to the first embodiment of the present invention;

fig. 9 is a schematic view of a ventricular simulator in accordance with a second embodiment of the present invention;

fig. 10 is a schematic view of a flexible connector according to a second embodiment of the present invention;

FIG. 11 is a schematic view of the operation of the flexible connector during normal beating of the heart in accordance with the second embodiment of the present invention;

fig. 12 is a schematic view of the operation of a flexible connector according to a second embodiment of the present invention with increased preload;

fig. 13 is a schematic view of the operation of the flexible connector according to the second embodiment of the present invention when the afterload is increased.

Description of reference numerals:

10: an in vitro simulated circulatory system for artificial heart testing; 1: a pulmonary circulation simulation component; 2: a heart simulation component; 3: a volume circulation simulation component; 4: a control component; 101: a first pressure sensor; 102: a first sealed container; 103: a first throttle valve; 104: a first flow sensor; 105: a first open container; 106: a second pressure sensor; 201: a first gate valve; 202: a second gate valve; 203: a third gate valve; 204: a fourth gate valve; 205: a fifth gate valve; 206: a sixth gate valve; 207: a seventh gate valve; 208: an eighth gate valve; 209: a ninth gate valve; 210: a tenth gate valve; 211: an eleventh gate valve; 212: a twelfth gate valve; 221: a first check valve; 222: a second one-way valve; 223: a third check valve; 224: a fourth check valve; 231: a left ventricle simulator; 232: a right ventricle simulator; 241: left Ventricular Assist Devices (LVADs); 242: right Ventricular Assist Devices (RVADs); 243: total Artificial Heart (TAH); 301: a third pressure sensor; 302: a second sealed container; 303: a second throttle valve; 304: a second flow sensor; 305: a second open container; 306: a fourth pressure sensor; 307: a third throttle valve; 308: a third open container; 41: a flexible connector; 42: a linear motor; 43: a piston cylinder; 411: an elastic element; 412: a diastole limiter; 413: a retraction stopper; 414: a linear motor connector; 415: a piston cylinder connector.

Detailed Description

Reference will now be made in detail to embodiments of the present invention, examples of which are illustrated in the accompanying drawings, wherein like reference numerals refer to the same or similar elements or elements having the same or similar function throughout. The embodiments described below with reference to the drawings are exemplary and intended to be used for explaining the present invention, and should not be construed as limiting the present invention.

An extracorporeal simulated circulation system for artificial heart testing according to an embodiment of the present invention will be described with reference to the accompanying drawings.

Fig. 1 is a schematic structural diagram of an extracorporeal simulated circulation system for artificial heart testing according to an embodiment of the present invention.

As shown in fig. 1, the in vitro simulated circulatory system 10 for artificial heart testing includes: a pulmonary circulation simulation module 1, a ventricular simulation module 2 and a systemic circulation simulation module 3.

The pulmonary circulation simulation assembly 1 comprises a first sealed container, a first open container, a first throttle valve, a first flow sensor, a first pressure sensor and a second pressure sensor, wherein the first sealed container is used for simulating pulmonary artery compliance, the first open container is used for simulating pulmonary vein compliance, the first throttle valve is used for simulating pulmonary circulation resistance, and the first flow sensor, the first pressure sensor and the second pressure sensor are used for measuring pulmonary circulation blood flow, pulmonary artery pressure and pulmonary vein pressure. The ventricle simulation assembly 2 comprises a left ventricle simulator, a right ventricle simulator, first to fourth one-way valves and first to twelfth gate valves, wherein the ventricle simulator is used for simulating the pulsating state of the left ventricle and the right ventricle, and the first to fourth one-way valves are respectively used for simulating a mitral valve, an aortic valve, a tricuspid valve and a pulmonary valve; the first to twelfth gate valves are used to simulate different blood flow paths when accessing the artificial heart. The body circulation simulation assembly 3 comprises a perfusion simulator, a second sealed container, a second open container, a second throttle valve, a second flow sensor, a third pressure sensor and a fourth pressure sensor, wherein the perfusion simulator is used for simulating the perfusion state of internal organs, the second sealed container is used for simulating the compliance of an aorta, the second open container is used for simulating the compliance of a main vein, the second throttle valve is used for simulating the resistance of body circulation, and the second flow sensor, the third pressure sensor and the fourth pressure sensor are used for measuring the blood flow, the pressure of the aorta and the pressure of the main vein of the body circulation. The utility model discloses system 10 can simulate human blood flow state and organ perfusion state to can external different forms "artificial heart (ventricle auxiliary pump)" product, the hydrodynamics performance of objective test product, thereby can effectively predict different artificial hearts and to the influence of patient self blood flow state after implanting the patient is internal, and solve the problem that exists in the present extrinsic cycle analog system.

It is understood that the system 10 of the present invention includes a ventricle simulation module, a lung circulation simulation module, and a body circulation simulation module, which realize the simulation of the blood flow state and the organ perfusion state of the human body. In the simulator of controlling the ventricle, the embodiment of the utility model provides a through flexible connector simulation cardiac muscle, use the shrink and the diastole of elastic element simulation cardiac muscle to use stopper simulation cardiac muscle shrink and diastolic extreme state, realized around the heart when load change the passive regulation of ventricle pulsation state. Simultaneously, through simulating different blood flow path and different organ perfusion levels, the embodiment of the utility model provides a can carry out the test and the optimization of multiple type "artificial heart" (ventricular assist pump) device, objectively test and optimize the hydrodynamics performance of product. The elastic element may be a spring, and the like, and is not particularly limited herein.

Further, in an embodiment of the present invention, the ventricle simulator includes a linear motor, a flexible connector, a piston cylinder, wherein the linear motor and the piston cylinder are used for simulating heart pulsation, and the blood output of the piston cylinder is controlled by the driving of the linear motor to simulate the human body state; the flexible connector is used for simulating automatic adjustment of cardiac blood output when the front and back loads change.

The linear motor and the piston cylinder are used for simulating heart pulsation, and the blood output of the piston cylinder is controlled by the driving of the linear motor and is used for simulating states of rest, movement, heart failure and the like; the flexible connector is used for simulating myocardial contraction and relaxation, and can automatically adjust blood output when the load changes before and after the heart, so that self-adaptive adjustment is realized.

Further, in an embodiment of the present invention, the flexible connector includes an elastic element, a diastole limiter, a contraction limiter, a linear motor connector, a piston cylinder connector, wherein the elastic element is used for simulating the contraction and the diastole of the myocardium, and the limiter is used for simulating the limit state of the contraction and the diastole of the myocardium. The elastic element can be a mechanical spring or a magnetic spring.

Further, in an embodiment of the present invention, the perfusion simulator comprises a third throttle valve and a third open container connected in parallel with the systemic circulation, wherein the liquid level state in the third open container is used for indicating insufficient perfusion, normal perfusion and excessive perfusion (extravasated blood) of the organ, and simultaneously realizing the non-constant state of the blood flow in the extracorporeal simulation circulation system.

Further, in an embodiment of the present invention, as shown in fig. 2, the system 10 of the embodiment of the present invention further includes: a control assembly 4. Wherein the control assembly 4 is used for simulating different blood flow paths through controlling the opening and closing states of the gate valve so as to test and optimize various types of artificial heart devices.

It can be appreciated that the system 10 of the embodiment of the present invention can simulate different blood flow paths by controlling the on/off state of the gate valve, and can realize the testing and optimization of various artificial heart devices, including left ventricle assisting device, right ventricle assisting device, double ventricle assisting device and total artificial heart.

The in vitro simulated circulatory system 10 for artificial heart testing will be further described with reference to specific embodiments.

Example one

In this embodiment, as shown in fig. 3, before accessing the artificial heart assist device for testing, it is first necessary to accurately simulate the blood flow state of the patient. The first to fourth gate valves (201, 202, 203, 204) are opened, and the fifth to twelfth gate valves (205, 206, 207, 208, 209, 210, 211, 212) are closed. According to the required heart beating state, such as exercise, rest, heart failure and the like, the volume pre-pressure of the sealing gas in the first sealed container 102 is adjusted to simulate the compliance of the pulmonary artery, the liquid level height in the first open container 105 is adjusted to simulate the compliance of the pulmonary vein, and the first throttle valve 103 is adjusted to simulate the resistance of the pulmonary circulation blood vessel. Adjusting the volume pre-pressure of the sealing gas in the second sealed container 302 simulates aortic compliance, adjusting the liquid level height in the second open container 305 simulates aortic compliance, and adjusting the second throttle 303 and the third throttle 307 simulates systemic vascular resistance. Accurate simulation of a required blood flow state is realized by controlling the linear motor 42 in the left ventricle simulator 231 and the right ventricle simulator 232, pulmonary artery pressure is measured in real time through the first pressure sensor 101, pulmonary circulation blood flow is measured in real time through the first flow sensor 104, pulmonary vein pressure is measured in real time through the second pressure sensor 106, aortic pressure is measured in real time through the third pressure sensor 301, aortic vein pressure is measured in real time through the fourth pressure sensor 306, and body circulation blood flow is measured in real time through the second flow sensor 304.

In the case of performing an extracorporeal circulation simulation test, the blood simulation material used is a fluid material having a viscosity similar to that of blood, for example, silicone oil or a 37% glycerol aqueous solution.

In this embodiment, as shown in fig. 4, when testing the Left Ventricular Assist Device (LVAD)241, the first to sixth gate valves (201, 202, 203, 204, 205, 206) are opened, the seventh to twelfth gate valves (207, 208, 209, 210, 211, 212) are closed, and a bypass blood flow path from the mitral valve to the aortic valve, specifically, from the first check valve 221 to the second check valve 222, is established. And (3) performing performance and durability evaluation tests on the left ventricular assist device 241 according to requirements, such as the influence of the rotation speed of a blood pump on the hemodynamics, and the influence of the implanted ventricular assist device on the autologous heart.

In this embodiment, as shown in fig. 5, when testing the Right Ventricular Assist Device (RVAD)242, the first to fourth gate valves and the seventh to eighth gate valves (201, 202, 203, 204, 207, 208) are opened, the fifth to sixth gate valves and the ninth to twelfth gate valves (205, 206, 209, 210, 211, 212) are closed, and a bypass blood flow path from the tricuspid valve to the pulmonary valve, specifically, the third check valve 223 to the fourth check valve 224 is established. Performance and durability evaluation tests of the left ventricular assist device 242 were performed on demand.

In this embodiment, as shown in fig. 6, when performing a test of a biventricular assist device (BVAD), the biventricular assist device is equivalent to a left ventricular assist device 241 and a right ventricular assist device 242, which are simultaneously connected, the first to eighth gate valves (201, 202, 203, 204, 205, 206, 207, 208) are opened, the ninth to twelfth gate valves (209, 210, 211, 212) are closed, and bypass blood flow paths from the mitral valve to the aortic valve and from the tricuspid valve to the pulmonary valve are established, specifically, after the first check valve 221 to the second check valve 222 and after the third check valve 223 to the fourth check valve 224. And (4) performing performance and durability evaluation tests on the biventricular assist device according to requirements.

In this embodiment, as shown in fig. 7, when a Total Artificial Heart (TAH)243 is tested, the total artificial heart is a complete replacement for the heart, and the left and right ventricular simulators (231,232) need to be isolated during the test, and since it includes four valves, the simulated valves (221, 222, 223, 224) do not need to be accessed during the access. The ninth to twelfth gate valves (209, 210, 211, 212) are opened, the first to eighth gate valves (201, 202, 203, 204, 205, 206, 207, 208) are closed, and the total artificial heart 243 is directly connected into the lung circulation assembly 1 and the body circulation assembly 3. The performance and durability evaluation test of the total artificial heart 243 is performed according to the requirement.

In the course of the work of actual artificial heart, because the blood pump rotational speed sets up the mistake, probably make the patient various clinical symptoms appear, the utility model discloses in simulate the perfusion state of organ clinically through filling the simulator. When the indicated liquid level in the third open container 308 is low, the blood pump may need to be increased in speed for an under-filled condition. When the indicated liquid level in the third open container 308 is high, in an overpressured state, where clinically extravasated blood is likely to form in the organs, it may be necessary to reduce the speed of the blood pump, as shown in fig. 8.

Example two

As shown in fig. 9, the left ventricle simulator 231 is taken as an example, and includes: linear motor 42, flexible connector 41, piston cylinder 43. The utility model discloses in realize through flexible connector 41 that left and right ventricle simulator (231,232) carries out automatic response to the change of front and back load, flexible connector 41 structure is as shown in fig. 10, include: a resilient element 411, a diastole stop 412, a contraction stop 413, a linear motor connector 414, a piston cylinder connector 415. The stroke of the linear motor 42 is a fixed value in the process of simulating the contraction and the relaxation of the ventricles, and when the linear motor is full, the stroke of the motor is equal to the sum of the elongation of the elastic element 411 and the stroke of the piston in the filling period; during ejection, the stroke of the motor is equal to the sum of the compression amount of the elastic element 411 and the stroke of the piston during ejection.

In this embodiment, the movement of the flexible connector 41 during the ventricular normal pulsatile state is shown in FIG. 11. During isovolumetric contraction, the linear motor 42 moves downwards and compresses the elastic element 411 through the linear motor connector 412, at the moment, the elastic force generated by the elastic element 411 is smaller than the arterial pressure, and the elastic force is gradually increased along with the downward movement of the linear motor 42, so that the isovolumetric contraction process that the pressure in the ventricle is increased and the volume is kept unchanged is simulated. During ejection of blood, the elastic force generated by the elastic element 411 is equal to the arterial pressure, and the elastic element 411 pushes the piston cylinder connector 415 and pushes the piston cylinder 43, so that the ejection process is completed, and the length of the elastic element 411 is y. During isovolumic relaxation, the elastic force generated by the elastic element 411 is larger than the venous pressure, and the elastic force is gradually reduced along with the upward movement of the linear motor 42, so that the isovolumic relaxation process that the pressure in the ventricle is reduced and the volume is kept unchanged is simulated. During filling, the elastic force generated by the elastic element 411 is equal to the venous pressure, and the piston cylinder 43 moves upwards along with the linear motor 42 to complete the filling process, wherein the length of the elastic element 411 is x.

In this embodiment, the movement of the flexible connector 41 when the ventricular preload is increased is shown in fig. 12. The clinical phenomenon at increased preload is that increased venous pressure leads to increased ventricular inflow and ultimately to increased cardiac output. As the preload in the simulated circulatory system increases, the resilient element 411 needs to provide more resilient force to overcome the venous pressure, the compression of the resilient element 411 during filling decreases by Δ x, and as the motor stroke equals the sum of the extension of the resilient element 411 and the piston stroke during filling, the stroke of movement of the diastolic piston cylinder 43 increases, and thus the heart rate increases, consistent with the clinical picture.

In the present embodiment, the movement state of the flexible connector 41 when the afterload increases to the limit is shown in fig. 13. The clinical phenomenon at increased afterload is that increased arterial pressure leads to a decrease in ventricular outflow and ultimately to a decrease in cardiac output. As the afterload in the simulated circulatory system increases, the resilient element 411 needs to provide more resilient force to overcome the arterial pressure, the compression of the resilient element 411 increases by Δ y during ejection, and since the motor stroke is equal to the sum of the compression of the resilient element 411 and the piston stroke during filling, the movement stroke of the diastolic piston cylinder 43 decreases, and thus the heart rate decreases, consistent with the clinical picture.

In summary, the extracorporeal simulation circulation system for artificial heart test provided by the embodiment of the utility model realizes the simulation of the blood flow state and the organ perfusion state of the human body, and provides a standardized test environment for the extracorporeal test of the artificial heart; the flexible connector is used for simulating cardiac muscle, so that the passive regulation of the ventricular pulse state is realized when the load changes around the heart; by simulating different blood flow paths and different organ perfusion levels, the artificial heart product with different forms can be externally connected, and the fluid mechanical property of the product can be objectively tested and optimized.

Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "a plurality" means at least two, e.g., two, three, etc., unless specifically limited otherwise.

In the present application, unless expressly stated or limited otherwise, the first feature may be directly on or directly under the second feature or indirectly via intermediate members. Also, a first feature "on," "over," and "above" a second feature may be directly or diagonally above the second feature, or may simply indicate that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature may be directly under or obliquely under the first feature, or may simply mean that the first feature is at a lesser elevation than the second feature.

In the description herein, references to the description of the term "one embodiment," "some embodiments," "an example," "a specific example," or "some examples," etc., mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, the schematic representations of the terms used above are not necessarily intended to refer to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, various embodiments or examples and features of different embodiments or examples described in this specification can be combined and combined by one skilled in the art without contradiction.

Although embodiments of the present invention have been shown and described, it is understood that the above embodiments are exemplary and should not be construed as limiting the present invention, and that variations, modifications, substitutions and alterations can be made to the above embodiments by those of ordinary skill in the art without departing from the scope of the present invention.

Claims (6)

1. An in vitro simulated circulatory system for artificial heart testing, comprising:

a ventricular simulation assembly comprising a left ventricular simulator, a right ventricular simulator, first to fourth check valves, and first to twelfth gate valves, wherein the ventricular simulator is used for simulating the pulsating state of the left and right ventricles, and the first to fourth check valves are used for simulating a mitral valve, an aortic valve, a tricuspid valve, and a pulmonary valve, respectively; the first to twelfth gate valves are used for simulating different blood flow paths when the artificial heart is accessed;

a pulmonary circulation simulation assembly comprising a first sealed container, a first open container, a first throttle valve, a first flow sensor, a first pressure sensor, a second pressure sensor, wherein the first sealed container is configured to simulate pulmonary artery compliance, the first open container is configured to simulate pulmonary vein compliance, the first throttle valve is configured to simulate pulmonary circulation resistance, and the first flow sensor, the first pressure sensor, and the second pressure sensor are configured to measure pulmonary circulation blood flow, pulmonary artery pressure, and pulmonary vein pressure;

a body circulation simulation assembly comprising a perfusion simulator, a second sealed container, a second open container, a second throttle valve, a second flow sensor, a third pressure sensor, a fourth pressure sensor, wherein the perfusion simulator is configured to simulate a perfusion status of an internal body organ, the second sealed container is configured to simulate aortic compliance, the second open container is configured to simulate aortic compliance, the second throttle valve is configured to simulate body circulation resistance, and the second flow sensor, the third pressure sensor, and the fourth pressure sensor are configured to measure a body circulation blood flow, aortic pressure, and aortic venous pressure.

2. The system of claim 1, further comprising:

and the control assembly is used for simulating different blood flow paths through controlling the opening and closing states of the gate valve so as to test and optimize various types of artificial heart devices.

3. The system of claim 1, wherein the ventricular simulator comprises a linear motor, a flexible connector, a piston cylinder, wherein the linear motor and the piston cylinder are used to simulate heart beats, and the piston cylinder blood output is controlled by the drive of the linear motor to simulate a human condition; the flexible connector is used for simulating automatic adjustment of cardiac blood output when the front load and the rear load are changed.

4. The system of claim 3, wherein the flexible connector comprises an elastic element, a diastole stop, a contraction stop, a linear motor connector, a piston cylinder connector, wherein the elastic element is configured to simulate the contraction and relaxation of the myocardium and the stop is configured to simulate the extreme states of the contraction and relaxation of the myocardium.

5. The system of claim 4, wherein the resilient element is a mechanical spring or a magnetic spring.

6. The system of claim 1, wherein the perfusion simulator comprises a third throttle valve and a third open container in parallel with the systemic circulation, wherein the state of the liquid level in the third open container is used to indicate organ hypoperfusion, normerfusion and hyperperfusion while achieving a non-constant state of blood flow in the extracorporeal simulated circulation system.

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