CN115083250A

CN115083250A - Ventricular simulator and in-vitro simulation circulating system

Info

Publication number: CN115083250A
Application number: CN202211016136.2A
Authority: CN
Inventors: 高琪; 徐可伟; 刘星利
Original assignee: Hangzhou Shengshi Technology Co ltd; Zhejiang University ZJU
Current assignee: Hangzhou Shengshi Technology Co ltd; Zhejiang University ZJU
Priority date: 2022-08-24
Filing date: 2022-08-24
Publication date: 2022-09-20
Anticipated expiration: 2042-08-24
Also published as: CN115083250B

Abstract

The application relates to the field of medical device experiments, and provides a ventricular simulation device and an extracorporeal simulation circulatory system. The ventricle simulation device includes a ventricle module and a coronary artery module. The ventricle module includes a ventricle housing, a driving part, an output pipeline, an input pipeline, a first one-way structure and a second one-way structure; a ventricle cavity is formed in the ventricle housing. , the driving part drives the ventricular cavity to dilate or contract periodically; the first ends of the output pipeline and the input pipeline are both connected to the ventricular cavity, and the second ends of the output pipeline and the input pipeline are used to connect to the extracorporeal simulated circulatory system, The first one-way structure is arranged on the output pipeline, and the second one-way structure is arranged on the input pipeline; the coronary artery module includes an inflow pipeline, an outflow pipeline and a first test area; the liquid inlet end of the inflow pipeline is connected to the output Pipeline, the liquid outlet end of the outflow pipeline is connected to the input pipeline, and the first test area is located between the liquid outlet end of the inflow pipeline and the liquid inlet end of the outflow pipeline. The first test area is used to connect a variety of Coronary artery models in different physiological states.

Description

Ventricular simulator and in-vitro simulation circulating system

Technical Field

The application relates to the technical field of medical instrument experiments, and provides a ventricular simulation device and an in-vitro simulation circulation system.

Background

The human body in-vitro simulated circulation system (MCL) can simulate the cardiovascular physiological flow of a human body outside the human body, reappear the blood flow under a normal or pathological state, and is used for testing the hemodynamics states of a ventricular assist device, an artificial valve, a vascular graft and local important organs. The MCL in the related technology only contains systemic circulation, and part of the MCL has pulmonary circulation, so that parameters such as ventricular pressure, aortic pressure, stroke volume, heart rate and the like can be simulated, and some Cardiovascular Auxiliary Devices (CAD) can be tested. However, the influence of CAD on the human body is systemic, and the function of the physiological state that can be simulated by the conventional MCL for testing is limited, so that CAD cannot be more comprehensively evaluated.

Disclosure of Invention

In view of the above, embodiments of the present disclosure provide a ventricular simulator and an extracorporeal simulation circulatory system integrated with a coronary artery circuit, which can more broadly simulate a physiological state of a heart.

One aspect of the embodiments of the present application provides a ventricular simulator, configured to access an extracorporeal simulation circulatory system, including a ventricular module and a coronary module, where the ventricular module includes a ventricular housing, a driving portion, an output pipeline, an input pipeline, a first unidirectional structure, and a second unidirectional structure; a ventricular cavity is formed in the ventricular housing, and the driving part drives the ventricular cavity to periodically relax or contract; the first ends of the output pipeline and the input pipeline are communicated with the heart chamber, the second ends of the output pipeline and the input pipeline are used for being connected into the extracorporeal simulation circulation system, the first one-way structure is arranged on the output pipeline so that liquid in the output pipeline can flow out of the heart chamber in one way, and the second one-way structure is arranged on the input pipeline so that liquid in the input pipeline can flow into the heart chamber in one way;

the coronary module comprises an inflow pipeline, an outflow pipeline and a first test area; the inlet end of the inflow pipeline is communicated with the output pipeline, the outlet end of the outflow pipeline is communicated with the input pipeline, the first test area is located between the outlet end of the inflow pipeline and the inlet end of the outflow pipeline, and the first test area is used for being connected into coronary artery models in various different physiological states.

In some embodiments, the coronary module comprises a flow simulator; the flow simulation part is arranged on the inflow pipeline or the outflow pipeline and comprises a first branch pipe, a second branch pipe, a first resistance regulating valve and a first electromagnetic valve; the first resistance adjusting valve is arranged on the first branch pipe, the first electromagnetic valve is arranged on the second branch pipe, and the first branch pipe and the second branch pipe are arranged in parallel;

the first electromagnetic valve is opened when the ventricular cavity is in a diastole state; the first solenoid valve is closed when the ventricular chamber is in a contracted state.

In some embodiments, the flow simulation portion includes a second resistance adjustment valve disposed on the inlet line or the outlet line.

In some embodiments, the coronary artery module comprises a coronary artery side branch pipeline and a second electromagnetic valve arranged on the coronary artery side branch pipeline, and two ends of the coronary artery side branch pipeline are respectively communicated with the liquid outlet end of the inflow pipeline and the liquid inlet end of the outflow pipeline; and the second electromagnetic valve can be selectively and automatically opened under the condition that the flow of the outflow pipeline is lower than a preset critical value.

In some embodiments, the coronary module comprises an inflow flow sensor disposed on the inflow line and an outflow flow sensor disposed on the outflow line; and/or the presence of a gas in the gas,

the coronary module comprises an inflow pressure sensor arranged on the inflow pipeline and an outflow pressure sensor arranged on the outflow pipeline.

In some embodiments, the coronary module includes a coronary compliance chamber for simulating coronary compliance, the coronary compliance chamber disposed on the inflow conduit or the outflow conduit.

In some embodiments, the first unidirectional structure is disposed upstream of the inlet end of the inlet conduit; the second one-way structure is arranged at the downstream of the liquid outlet end of the outflow pipeline.

In some embodiments, the coronary module includes a second test site for accessing a coronary bypass, the second test site being located between the second end of the outlet line and the inlet end of the outlet line.

In some embodiments, the driving portion includes a linear motor and a piston, the ventricular housing is a piston cylinder, the piston cylinder is formed with a piston groove which is open at one end in the transverse direction, the piston is slidably disposed in the piston groove, the piston and the piston groove jointly enclose to form the ventricular cavity, and the linear motor drives the piston to slide in the piston groove in the transverse direction to increase or decrease the volume of the ventricular cavity.

In some embodiments, the linear motor includes a motor coil and a motor slide bar, the motor slide bar is sleeved in the motor coil in a transversely slidable manner, the piston is connected to one transverse end of the motor slide bar, the motor coil drives the motor slide bar to transversely slide in an excited state, and the motor slide bar drives the piston to transversely slide.

In some embodiments, the driving portion includes a first travel switch, a second travel switch, and a toggle member disposed on the motor slide bar;

when the heart chamber is in the maximum volume state, the motor slide bar drives the toggle piece to trigger the first travel switch; when the heart chamber is in a minimum volume state, the motor slide bar drives the toggle piece to trigger the second travel switch;

the heart chamber simulation device comprises an electromagnetic relay, the coronary artery module comprises a flow simulation part arranged on the inflow pipeline or the outflow pipeline, and the flow simulation part comprises a first electromagnetic valve;

when the second travel switch is triggered, the first electromagnetic valve is kept open;

when the first travel switch is triggered, the first solenoid valve closes.

In some embodiments, the toggle member is a toggle piece, the toggle piece is connected to one end of the motor slide rod away from the transverse direction of the piston, the contact of the first travel switch is located on one side of the toggle piece away from the piston, the contact of the second travel switch is located on one side of the toggle piece close to the piston, and the toggle piece is transversely slidably disposed between the contact of the first travel switch and the contact of the second travel switch.

In some embodiments, the ventricular module includes a base to which the ventricular housing is secured, and the drive portion includes a motor mount through which the motor coil is secured to the base.

In some embodiments, the ventricular module comprises a stroke adjustment portion and a clamping portion; the clamping part is provided with a clamping space for clamping the first travel switch or the second travel switch;

the stroke adjustment portion includes adjusting screw and adjusts the seat, it is fixed in to adjust the seat on the base, it is formed with along the regulation screw of horizontal extension to adjust the seat, adjusting screw's one end is worn to locate adjust in the screw and with the clamping part is connected, adjusting screw is relative the rotation of adjusting the screw can make adjusting screw moves along the transverse direction, in order to adjust the clamping part is along the position of transverse direction.

In some embodiments, the clamping portion comprises a first clamping plate, a second clamping plate and a fastening adjusting assembly, the first clamping plate and the second clamping plate are oppositely arranged in the transverse direction, one end of the adjusting screw is connected with the first clamping plate, the second clamping plate is connected with the first clamping plate through the fastening adjusting assembly, the clamping space is formed between the first clamping plate and the second clamping plate, and the fastening adjusting assembly is used for adjusting the size of the clamping space.

In some embodiments, the fastening adjustment assembly includes a fastening bolt and a fastening nut, the first clamping plate, the second clamping plate and the fastening nut are sequentially sleeved on the fastening bolt along a transverse direction, the first travel switch or the second travel switch is located in the clamping space, and the fastening nut is screwed and abutted on the second clamping plate so as to clamp the first travel switch or the second travel switch in the clamping space.

In some embodiments, the ventricular housing is formed with an exhaust port in communication with the ventricular cavity, and the ventricular module includes an exhaust valve openably and closably disposed at the exhaust port.

In some embodiments, the ventricular housing is formed with a ventricular cavity sensor interface in communication with the ventricular cavity, and the ventricular module includes a ventricular cavity pressure sensor coupled to the ventricular cavity sensor interface.

Another aspect of the present application provides an extracorporeal simulation circulation system, which includes a main circulation pipeline, the ventricular simulator described in any one of the above, and an arterial compliance chamber, a systemic circulation resistance regulating valve, a venous chamber, and a main circulation flow sensor disposed on the main circulation pipeline;

the arterial compliance chamber is used for simulating the compliance of an artery and is positioned at the upstream of the venous chamber, the second end of the output pipeline is communicated with the first end of the main circulation pipeline, and the second end of the input pipeline is communicated with the second end of the main circulation pipeline.

The ventricle simulation device provided by the embodiment of the application can be used for accessing an extracorporeal simulation circulation system, and the ventricle module can provide running power for the extracorporeal simulation circulation system. On the other hand, the first test area in the coronary module can be accessed to coronary models in various different physiological states, simulation under various working conditions of coronary circulation can be realized according to the coronary models in different physiological states, such as a coronary artery stenosis model, and more comprehensive evaluation can be provided for the performance and effect of medical equipment such as CAD (computer aided design).

Drawings

FIG. 1 is a schematic diagram illustrating an overall configuration of a ventricular simulator according to an embodiment of the present application;

FIG. 2 is a schematic structural view of a coronary module of the configuration shown in FIG. 1;

FIG. 3 is a schematic diagram of a partial structure of a ventricular module of the structure shown in FIG. 1; the main structure of the linear motor is schematically shown;

FIG. 4 is a partial schematic block diagram of a ventricular module of the configuration shown in FIG. 1; the main structures of the ventricular housing, the piston and the exhaust valve are schematically shown;

FIG. 5 is a schematic diagram of a partial structure of a ventricular module of the structure shown in FIG. 1; the main structures of the driving part, the clamping part and the stroke adjusting part are schematically shown;

FIG. 6 is a schematic view of the structure of the clamping portion and the stroke adjustment portion of the ventricular module of the configuration shown in FIG. 1;

FIG. 7 is an exploded view of the structure shown in FIG. 6;

FIG. 8 is a schematic diagram of the structure of FIG. 2 after being accessed into a normal coronary model;

FIG. 9 is a schematic diagram of the structure of FIG. 2 after the structure has been connected to a coronary model having a coronary stenosis;

FIG. 10 is a schematic view of the structure of FIG. 2 after placement of a coronary stent in a coronary model having coronary stenosis;

FIG. 11 is a schematic view of the structure of FIG. 2 after simultaneous access to a coronary model with coronary stenosis and a coronary bypass;

FIG. 12 is a schematic circuit diagram of the structure of FIG. 1 for controlling a second solenoid valve;

FIG. 13 is a schematic circuit diagram of the configuration of FIG. 1 for controlling a first solenoid;

FIG. 14 is a schematic circuit diagram of the structure shown in FIG. 13 when the toggle member toggles the second travel switch;

FIG. 15 is a schematic electrical circuit diagram of the structure of FIG. 13 with the ventricular chambers in a diastolic state;

FIG. 16 is a schematic circuit diagram of the arrangement of FIG. 13 when the toggle member actuates the first travel switch;

fig. 17 is a schematic diagram illustrating an overall structure of an extracorporeal simulated circulation system according to an embodiment of the present application.

Description of the reference numerals

A ventricular simulator 100; a ventricular module 1; a ventricular housing 11; ventricular chamber 11 a; a piston groove 11 b; an exhaust port 11 c; ventricular chamber sensor interface 11 d; the first communication port 11 e; a second communication port 11 f; a drive section 12; a linear motor 121; a motor coil 1211; a motor slide bar 1212; a piston 122; a first travel switch 123; a second travel switch 124; a toggle member 125; a motor mount 126; an output line 131; an input line 132; a first unidirectional structure 141; a second unidirectional structure 142; a base 15; a plate body 151; a strip-shaped section bar 152; a stroke adjusting section 16; an adjusting screw 161; an adjustment seat 162; an adjustment screw hole 162 a; a clamping portion 17; the holding space 17 a; a first clamping plate 171; a second clamping plate 172; a fastening adjustment assembly 173; fastening bolts 1731; a fastening nut 1732; an exhaust valve 18; a ventricular chamber pressure sensor 19; a coronary module 2; a first test zone 2 a; an inflow line 21; an outflow line 22; a diversion point 22 a; a confluence point 22 b; a flow rate simulation unit 23; a first branch pipe 231; a second branch pipe 232; a first resistance adjustment valve 233; a first solenoid valve 234; a second resistance adjustment valve 235; a coronary side branch line 24; a second electromagnetic valve 25; an inflow flow sensor 261; an outflow flow sensor 262; an inflow pressure sensor 271; an outflow pressure sensor 272; a coronary compliance chamber 28; a second test zone 2 b; an electromagnetic relay 3; an electromagnet 31; a movable contact 32; a normally closed contact 33; a normally open contact 34; an armature 35; a spring 36; a first series circuit 3 a; a second series circuit loop 3 b; a third series circuit loop 3 c; a central processing unit 4; an analog signal switch 5; an extracorporeal simulated circulation system 900; a main circulation line 91; an arterial compliance chamber 92; a systemic circulation resistance regulating valve 93; the venous compartment 94; a main circulation flow sensor 95; the atrial chamber 96; a coronary artery model a; coronary artery bypass b; and (c) coronary artery stents.

Detailed Description

It should be noted that, in the present application, technical features in examples and embodiments may be combined with each other without conflict, and the detailed description in the specific embodiment should be understood as an explanation of the gist of the present application and should not be construed as an improper limitation to the present application.

In the description of the embodiments of the present application, the "lateral", "longitudinal", "up", "down" orientation or positional relationship is the orientation or positional relationship of the ventricular simulator during normal use. Such as the orientation or positional relationship shown in fig. 1. The term "first/second/third/fourth/fifth" merely distinguishes between different objects and does not denote the same or a relationship between the two. It is to be understood that such directional terms are merely for convenience in describing the present application and for simplicity in description, and are not intended to indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and are not to be considered limiting of the present application.

The coronary circulation in the human blood circulation is the circulation of the heart itself. Blood is pumped from the left ventricle, from the coronary sinus at the root of the aorta into the coronary artery, carrying nutrients to the heart muscle cells, and then through the veins back to the heart. Since the coronary circulation plays a very important role in maintaining the normal function of the heart, in order to more widely simulate the state of the heart, especially some cardiovascular diseases, such as coronary artery stenosis, heart failure, myocardial infarction and the like, the combined operation of the coronary circulation and the simulated ventricle in the MCL is required.

Referring to fig. 1 to 7, in one aspect, the present embodiment provides a ventricular simulator 100, which includes a ventricular module 1 and a coronary module 2. The ventricular module 1 is used to simulate the diastole and contraction of the ventricles of the heart. The coronary module 2 is used to simulate the blood flow of the coronary arteries in the blood circulation.

The ventricular module 1 includes a ventricular housing 11, a drive section 12, an output line 131, an input line 132, a first unidirectional structure 141, and a second unidirectional structure 142.

A ventricular chamber 11a is formed in the ventricular housing 11, and the driving portion 12 drives the ventricular chamber 11a to periodically expand or contract. That is, the driving portion 12 drives the ventricular cavity 11a to change the volume so that the volume of the ventricular cavity 11a exhibits periodic increase or decrease, specifically, the volume of the ventricular cavity 11a increases in the diastolic state of the ventricular cavity 11 a; in the collapsed state of the ventricular chamber 11a, the volume of the ventricular chamber 11a decreases.

First ends of the output pipeline 131 and the input pipeline 132 are communicated with the ventricular chamber 11a, and second ends of the output pipeline 131 and the input pipeline 132 are used for connecting the extracorporeal simulation circulation system 900. That is, when the ventricular chamber 11a is in the diastolic state, the input line 132 is connected to the extracorporeal simulation circulation system 900, and the liquid in the extracorporeal simulation circulation system 900 flows into the ventricular chamber 11a through the input line 132; when the ventricular cavity 11a is in the contraction state, the output pipeline 131 is connected into the extracorporeal simulation circulation system 900, and the liquid in the extracorporeal simulation circulation system 900 flows out of the ventricular cavity 11a through the output pipeline 131.

It should be noted that the fluid in the extracorporeal circulation simulation system 900 includes, but is not limited to, a fluid medium which is a glycerol aqueous solution, and the viscosity of the fluid medium can be determined according to the blood viscosity to be simulated.

The first one-way structure 141 is disposed on the output pipeline 131 to make the liquid in the output pipeline 131 flow out of the chamber 11a in one way, and the second one-way structure 142 is disposed on the input pipeline 132 to make the liquid in the input pipeline 132 flow into the chamber 11a in one way. That is, the first one-way structure 141 is capable of allowing the liquid in the ventricular chamber 11a to flow into the outlet line 131 while blocking the backflow of the liquid in the outlet line 131 to the ventricular chamber 11 a; likewise, the second one-way structure 142 can allow fluid in the inlet line 132 to flow into the ventricular chamber 11a while blocking fluid in the ventricular chamber 11a from flowing back into the inlet line 132.

The first one-way structure 141 and the second one-way structure 142 include, but are not limited to, a one-way conduction structure such as a prosthetic valve or a one-way valve.

The coronary module 2 comprises an inflow conduit 21, an outflow conduit 22 and a first test zone 2 a. The liquid inlet end of the inflow pipeline 21 is communicated with the output pipeline 131, the liquid outlet end of the outflow pipeline 22 is communicated with the input pipeline 132, the first test area 2a is positioned between the liquid outlet end of the inflow pipeline 21 and the liquid inlet end of the outflow pipeline 22, and the first test area 2a is used for being connected with coronary artery models a in various different physiological states. Specifically, after the first test area 2a is connected to the coronary artery model a in any physiological state, the liquid outlet end of the inflow pipeline 21 and the liquid inlet end of the outflow pipeline 22 are communicated through the coronary artery model a, so that a complete coronary circulation loop is formed. The inflow pipeline 21 is used for introducing the liquid flowing out from the output pipeline 131 into the coronary artery model a, and simulating the flow of blood into the coronary artery after the blood is pumped out from the ventricular cavity 11 a; the outflow line 22 is used to return the fluid from the coronary model a to the input line 132, so as to simulate the coronary artery to return to the ventricular chamber 11a after the myocardial cells are completely supplied.

The form of the liquid inlet end of the inlet pipeline 21 communicating with the output pipeline 131 is not limited, and includes, but is not limited to, a tee joint.

The form of the outlet end of the outflow pipeline 22 communicating with the input pipeline 132 is not limited, and includes, but is not limited to, a tee joint.

The ventricular simulator 100 provided in the embodiment of the present application, on the one hand, can be used to access the extracorporeal simulation circulatory system 900, and the ventricular module 1 can provide the extracorporeal simulation circulatory system 900 with operational power. On the other hand, the first test area 2a in the coronary module 2 can be accessed to the coronary models a in various different physiological states, and according to the coronary models a in different physiological states, such as a coronary artery stenosis model, simulation of coronary circulation under various working conditions can be achieved, and more comprehensive evaluation can be provided for performance and effects of medical instruments such as CAD.

To better explain the working principle of the ventricular simulator 100, please refer to fig. 1 to 7 for example, another aspect of the embodiment of the present application provides an extracorporeal simulation circulatory system 900, which includes a main circulatory line 91, an arterial compliance chamber 92, a systemic resistance regulating valve 93, a venous chamber 94, a main circulatory flow sensor 95, and the ventricular simulator 100 according to any one of the embodiments of the present application.

Arterial compliance chamber 92, systemic resistance regulator valve 93, venous chamber 94 and main circulation flow sensor 95 are all disposed on main circulation line 91. Specifically, the systemic resistance regulator 93 can regulate the flow and pressure of the liquid in the main circulation line 91 to simulate the resistance and flow of the main circulation. The venous chamber 94 has a reservoir function for simulating venous blood storage in a human body. The main circulation flow sensor 95 is used to measure the flow rate of the liquid in the main circulation line 91.

Arterial compliance chamber 92 is used to simulate arterial compliance and is located upstream of venous chamber 94. Specifically, the arterial compliance chamber 92 is a container with an upper part for storing air and a lower part for storing liquid, and is used for simulating the elasticity of an artery, and plays a role in buffering the pressure and the flow of the liquid in the main circulation pipeline 91.

A second end of the outlet line 131 communicates with a first end of the main circulation line 91 and a second end of the inlet line 132 communicates with a second end of the main circulation line 91. Specifically, the second end of the output line 131 is connected to the first end of the main circulation line 91, and the second end of the input line 132 is connected to the second end of the main circulation line 91, thereby forming a main blood circulation circuit of the human body.

The locations of the main circulation flow sensor 95 and the circulation resistance adjustment valve disposed on the main circulation pipeline 91 are not limited, and in one embodiment, referring to fig. 1 to 7 and fig. 17, the main circulation flow sensor 95 and the body circulation resistance adjustment valve 93 are disposed between the arterial compliance chamber 92 and the venous chamber 94, and the body circulation resistance adjustment valve 93 is disposed downstream of the main circulation flow sensor 95.

For example, in one embodiment, referring to fig. 17, the extracorporeal simulation circulatory system 900 includes an atrial chamber 96, the atrial chamber 96 disposed on the inlet line 132 and between the second unidirectional structure 142 and the outlet end of the outlet line 22. The atrial chamber 96 has a reservoir function for simulating the left atrial reservoir of a human body.

When the extracorporeal simulation circulation system 900 is in operation, the driving unit 12 drives the ventricular cavity 11a to periodically expand or contract, and the liquid in the ventricular cavity 11a flows into the first end of the main circulation pipeline 91 through the output pipeline 131, flows through the arterial compliance chamber 92 and the venous chamber 94 in sequence, flows out from the second end of the main circulation pipeline 91 to the input pipeline 132, and finally flows back to the ventricular cavity 11a through the atrial cavity 96 on the input pipeline 132.

In one embodiment, referring to fig. 1 to 7, the coronary module 2 includes a flow simulation unit 23. The flow simulation unit 23 simulates the pressure and flow characteristics of coronary blood vessels in the coronary circulation.

The flow rate simulator 23 is provided in the inlet pipe 21 or the outlet pipe 22. That is, the position of the flow rate simulator 23 on the coronary circulation may be provided upstream of the first test zone 2a or downstream of the first test zone 2a depending on the actual situation.

The flow rate simulator 23 includes a first branch pipe 231, a second branch pipe 232, a first resistance adjustment valve 233, and a first solenoid valve 234; the first resistance adjustment valve 233 is provided on the first branch pipe 231, the first solenoid valve 234 is provided on the second branch pipe 232, and the first branch pipe 231 and the second branch pipe 232 are provided in parallel. Specifically, the first resistance adjustment valve 233 is used to adjust the pressure and flow rate of the liquid in the first branch pipe 231, and the first solenoid valve 234 is used to control the on/off of the liquid in the second branch pipe 232.

In the diastolic state of the ventricular chamber 11a, the first solenoid valve 234 is opened. When the cardiac muscle of human body is in diastole, the blood vessels in the coronary vessels can smoothly circulate. Therefore, when the ventricular chamber 11a is in the diastolic state, the first solenoid valve 234 is opened, and the first branch 231 and the second branch 232 are simultaneously conducted, so as to simulate the situation that the coronary blood flow is large when the ventricular chamber 11a is in the diastolic state.

In the contracted state of the ventricular chamber 11a, the first solenoid valve 234 is closed. When the cardiac muscle of human body contracts, the coronary blood vessel will be squeezed to cause the phenomenon of blood flow reduction. Thus, the first solenoid valve 234 is closed in the contraction state of the chamber 11 a. At this time, only the first branch 231 is turned on, and the second branch 232 is turned off, thereby simulating a case where the flow rate of the coronary blood vessel is small in the ventricular chamber 11a in the contracted state.

That is, by controlling the opening degree of the first resistance adjustment valve 233 and the opening and closing of the first solenoid valve 234, the flow rate time phase characteristics of the coronary artery can be reproduced more easily.

In one embodiment, referring to fig. 1 to 7, the flow simulation unit 23 includes a second resistance adjustment valve 235, and the second resistance adjustment valve 235 is disposed on the inlet pipeline 21 or the outlet pipeline 22. Specifically, the second resistance adjustment valve 235 may be selectively disposed on the inlet pipeline 21 or the outlet pipeline 22 according to the actual pipeline assembly.

In an exemplary embodiment, referring to fig. 1 to 7, the flow simulating units 23 are disposed on the outlet pipeline 22, the outlet pipeline 22 has a splitting point 22a and a merging point 22b, the splitting point 22a communicates with the inlet end of the first branch pipe 231 and the inlet end of the second branch pipe 232, the merging point 22b communicates with the outlet end of the first branch pipe 231 and the outlet end of the second branch pipe 232, and the second resistance adjusting valve 235 is located downstream of the merging point 22 b.

It can be seen that the second resistance adjustment valve 235 is provided in the inlet pipe 21 or the outlet pipe 22, and the total flow rate after the first branch pipe 231 and the second branch pipe 232 are merged can be uniformly adjusted. Therefore, by adjusting the second resistance adjustment valve 235 in combination with adjusting the first resistance adjustment valve 233, the flow time phase characteristics of the coronary blood vessel can be reproduced more accurately, and the effect of reproducing the coronary circulation is better.

Under normal resting conditions, coronary blood flow is about 225 mL/min. If a thrombus occurs in the coronary artery, the flow of the coronary artery will be reduced. After a vessel has become occluded, a person will develop coronary collateral vessels around the occluded coronary vessels for a period of time in order to compensate for the reduced blood supply. Coronary collateral blood supply is an important mechanism for maintaining coronary flow, myocardial survival and normal heart function.

In order to simulate the phenomenon of auxiliary blood supply of coronary artery side branch vessels, in an embodiment, referring to fig. 1 to 7, the coronary artery module 2 includes a coronary artery side branch pipeline 24 and a second electromagnetic valve 25 disposed on the coronary artery side branch pipeline 24, and two ends of the coronary artery side branch pipeline 24 are respectively communicated with the liquid outlet end of the inflow pipeline 21 and the liquid inlet end of the outflow pipeline 22. That is, the coronary artery side branch line 24 is connected in parallel to the first test area 2a for accessing the coronary artery model a, the coronary artery side branch line 24 can be used to simulate blood supply of the coronary artery side, and the second electromagnetic valve 25 is provided on the coronary artery side branch line 24 to control on/off of the coronary artery side branch line 24.

Specifically, in order to simulate the function of automatically adjusting the coronary flow, in one embodiment, referring to fig. 1 to 7, the second solenoid valve 25 may be selectively and automatically opened in a state where the flow rate of the outflow line 22 is lower than a predetermined threshold value. That is to say, the second electromagnetic valve 25 is opened, so that the coronary artery side branch pipeline 24 is conducted, and the conducted coronary artery side branch pipeline 24 and the coronary artery model a accessed to the first test area 2a together simulate blood supply for coronary artery circulation, so that the coronary artery flow is restored to a normal value, and the function of automatically adjusting the coronary artery flow is realized. The preset critical value Q can be set correspondingly according to different experimental working conditions.

It should be noted that the second solenoid valve 25 is selectively opened automatically, which means that when the automatic adjustment function for simulating the coronary flow is required, the second solenoid valve 25 is opened in a state that the flow rate of the outflow line 22 is lower than a preset threshold value, and when the automatic adjustment function for simulating the coronary flow is not required, the second solenoid valve 25 is kept closed.

In one embodiment, referring to fig. 1 to 7, the coronary module 2 includes an inflow sensor 261 disposed on the inflow pipeline 21 and an outflow sensor 262 disposed on the outflow pipeline 22. Inflow sensor 261 is used to measure coronary inflow on inflow line 21 and outflow sensor 262 is used to measure coronary outflow on outflow line 22. The measured values of the coronary inflow and outflow flows can reflect the flow characteristics of the coronary circulation and evaluate the performance and effect of medical instruments such as CAD and the like, and on the other hand, the first resistance regulating valve 233 and the second resistance regulating valve 235 can be used for providing feedback flow data for reappearing the coronary circulation according to the flow characteristics.

In one embodiment, referring to fig. 1 to 7, the coronary module 2 includes an inlet pressure sensor 271 disposed on the inlet pipeline 21 and an outlet pressure sensor 272 disposed on the outlet pipeline 22. An inlet pressure sensor 271 is used to measure the coronary inflow pressure on the inlet line 21 and an outlet pressure sensor 272 is used to measure the coronary outflow pressure on the outlet line 22.

The measured values of the coronary inflow pressure and the coronary outflow pressure can reflect the pressure condition of the coronary circulation on one hand, evaluate the performance and the effect of medical instruments such as CAD and the like, and on the other hand, the first resistance regulating valve 233 and the second resistance regulating valve 235 can be used for providing feedback pressure data for the recurrence of the coronary circulation according to the pressure condition.

In one embodiment, referring to fig. 1, the ventricular simulator 100 includes a central processor 4, wherein the central processor 4 is configured to receive measurement data from an inflow sensor 261, an outflow sensor 262, an inflow pressure sensor 271 and an outflow pressure sensor 272. The central processor 4 includes, but is not limited to, a computer having a signal processing module.

In one embodiment, referring to fig. 12, the ventricular simulator 100 includes an analog signal switch 5, the analog signal switch 5 and the second solenoid valve 25 form a series circuit, and when the analog signal switch 5 is closed, the second solenoid valve 25 is electrically opened; in the off state of the analog signal switch 5, the second electromagnetic valve 25 is turned off.

For example, a preset critical value Q of the coronary outflow of the outflow line 22 is set, and the signal processing module of the cpu 4 receives a plurality of instantaneous coronary outflow for a period of time from the outflow sensor 262 and calculates an average Q of the coronary outflow _cor Is mixing Q with _cor Comparing with Q, if Q _cor <And Q, the signal processing module sends an electric signal to the signal simulation switch, the signal simulation switch is controlled to be closed, the second electromagnetic valve 25 is powered on and opened, the coronary artery side branch pipeline 24 is conducted, the conducted coronary artery side branch pipeline 24 and the coronary artery model a accessed to the first test area 2a jointly simulate blood supply for coronary artery circulation, and therefore the flow of the coronary artery is gradually increased and is recovered to a normal value, and automatic adjustment of the flow of the coronary artery is achieved. This flow automatic adjustment can be used selectively to it can be based on different experimental operating conditions to predetermine critical value Q and set for.

In one embodiment, referring to fig. 2, the coronary module 2 includes a coronary compliance chamber 28 for simulating coronary compliance, and the coronary compliance chamber 28 is disposed on the inflow conduit 21 or the outflow conduit 22. Specifically, the coronary compliance chamber 28 is a reservoir that stores liquid above and below the reservoir, and is used to simulate the elasticity of the coronary artery, and to cushion the pressure and flow of liquid in the coronary circulation.

In an exemplary embodiment, referring to fig. 2, fig. 8 to fig. 11, a coronary artery compliance chamber 28, an inflow flow sensor 261, an inflow pressure sensor 271 and a first Y-shaped three-way joint are sequentially disposed in the inflow pipeline 21 along the liquid flowing direction, and three interfaces of the first Y-shaped three-way joint are respectively in butt joint with and communicate with an outflow end of the inflow pipeline 21, an inflow end of the coronary artery model a and an inflow end of the coronary artery side branch pipeline 24.

In an exemplary embodiment, referring to fig. 2, 8 to 11, the outflow pipeline 22 is sequentially provided with a cross joint at the diversion point 22a, a first branch pipe 231 with a first resistance regulating valve 233 and a second branch pipe 232 with a first electromagnetic valve 234 which are connected in parallel, a second Y-shaped three-way joint at the confluence point 22b, a second resistance regulating valve 235, an outflow sensor 262 and an outflow pressure sensor 272 along the liquid flowing direction; the four interfaces of the cross joint are respectively in butt joint communication with the outflow end of the coronary artery model a, the outflow end of the coronary artery side branch pipeline 24, the inflow end of the first branch pipe 231 and the inflow end of the second branch pipe 232, and the three interfaces of the second Y-shaped three-way joint are respectively in butt joint communication with the outflow end of the first branch pipe 231, the outflow end of the second branch pipe 232 and the inflow end of the second resistance adjusting valve 235.

It should be noted that the cross joint can be replaced by a combination of two Y-shaped three-way joints to achieve the same function.

In an embodiment, referring to fig. 1 and 17, the first unidirectional structure 141 is disposed upstream of the liquid inlet end of the liquid inlet pipeline 21; the second one-way structure 142 is disposed downstream of the outlet end of the outlet flow line 22. If the first one-way structure 141 is provided downstream of the inlet end of the inlet line 21, the inlet line 21 may flow backward in the diastolic state of the ventricular chamber 11 a. The first one-way structure 141 is disposed upstream of the liquid inlet end of the inlet pipeline 21 to ensure that the liquid flowing out from the output pipeline 131 enters the inlet pipeline 21 in one way. Similarly, if the second one-way structure 142 is disposed upstream of the inlet end of the inlet conduit 21, the outlet conduit 22 will flow backwards when the ventricular chamber 11a is in the contracted state. Therefore, the second one-way structure 142 is disposed downstream of the outlet end of the outlet pipeline 22 to ensure that the liquid flowing out from the outlet pipeline 22 enters the inlet pipeline 132 in one way.

In one embodiment, referring to fig. 11, the coronary module 2 comprises a second test area 2b for accessing the coronary bypass b, and the second test area 2b is located between the second end of the output pipeline 131 and the inlet end of the outlet pipeline 22. Specifically, the coronary artery bypass b is used for simulating a blood vessel of Coronary Artery Bypass Grafting (CABG), after the coronary artery bypass b is connected, one end of the coronary artery bypass b is in butt joint communication with the second end of the output pipeline 131 so as to simulate that the coronary artery bypass b directly draws blood from the output pipeline 131 used for simulating aorta, and the other end of the coronary artery bypass b is in butt joint communication with the liquid inlet end of the outflow pipeline 22.

The purpose of the coronary artery bypass b transplantation is to enable blood ejected from the heart to cross stenosis or obstruction through the blood vessel of the coronary artery bypass b, so that the flow of the coronary artery is improved. The effectiveness of coronary bypass b grafting and thus the performance of coronary bypass b for CAD can be evaluated by monitoring the measurements of inflow sensor 261 and outflow sensor 262.

Coronary bypass b includes, but is not limited to, plain tubing, silicone models, or biological vessels.

In one embodiment, referring to fig. 1 to 7, the driving portion 12 includes a linear motor 121 and a piston 122, the ventricular housing 11 is a piston cylinder, the piston cylinder is formed with a piston groove 11b opened along one lateral end, the piston 122 is slidably disposed in the piston groove 11b, the piston 122 and the piston groove 11b together enclose a ventricular chamber 11a, and the linear motor 121 drives the piston 122 to slide along the lateral direction in the piston groove 11b to increase or decrease the volume of the ventricular chamber 11 a. That is, the present invention adopts the reciprocating sliding of the piston 122 in the piston groove 11b to simulate the expansion and contraction of the ventricular cavity 11a, and simultaneously adopts the linear motor 121 as the driving power source, so that the structure is relatively simple, compared with the rotary motor, no other device is needed to change the rotary motion of the rotary motor into the linear motion, the structural weight and volume of the driving part 12 can be greatly simplified, and the structure of the ventricular module 1 is more compact. Meanwhile, the linear motor 121 can also directly regulate the speed according to the requirement, and the effect of simulating the ventricular cavity 11a is better.

The positions of communication of the inlet line 132 and the outlet line 131 with the ventricular chambers 11a, respectively, are not limited. For example, referring to fig. 1 and 4, a transverse end surface of the piston cylinder away from the piston 122 is formed with a first communication port 11e and a second communication port 11f, a first end of the input line 132 is in butt communication with the first communication port 11e, and a first end of the output line 131 is in butt communication with the second communication port 11 f.

The linear motor 121 drives the piston 122 in a non-limiting manner, and for example, in an embodiment, referring to fig. 3, the linear motor 121 includes a motor coil 1211 and a motor sliding rod 1212. The motor slide bar 1212 is slidably sleeved in the motor coil 1211 in a transverse direction, the piston 122 is connected to one end of the motor slide bar 1212 in the transverse direction, the motor coil 1211 drives the motor slide bar 1212 to slide in the transverse direction in an excited state, and the motor slide bar 1212 drives the piston 122 to slide in the transverse direction. Specifically, the axial direction of the motor slide bar 1212 is parallel to the lateral direction. The motor coil 1211 corresponds to a primary side of the linear motor 121, and the motor slide 1212 corresponds to a secondary side of the linear motor 121. One end of the motor slide 1212 is directly connected to the piston 122, so that the motor slide 1212 directly drives the piston 122 to slide laterally.

Illustratively, in the diastolic state of the chamber 11a, the motor coil 1211 is excited in a forward direction, the driving motor rod 1212 drives the piston 122 to slide in a lateral direction away from the piston cylinder, and the volume of the chamber 11a gradually increases. When the chamber 11a is in a contracted state, the motor coil 1211 is excited in a reverse direction, the driving motor sliding rod 1212 drives the piston 122 to slide along a transverse direction close to the piston cylinder, and the volume of the chamber 11a is gradually reduced.

The connection mode of the piston 122 connected to the transverse end of the motor sliding rod 1212 is not limited, and includes, but is not limited to, a threaded connection, a socket connection, a snap connection, a welding connection, and the like.

A sealing member which slides synchronously with the piston 122 is arranged between the piston 122 and the piston groove 11b, and the sealing member is used for sealing a gap between the piston groove 11b and the piston 122 and preventing gas and liquid in the heart chamber 11a from leaking from the gap, and the sealing member includes, but is not limited to, an O-ring.

In one embodiment, referring to fig. 3 to 7, the driving portion 12 includes a first travel switch 123, a second travel switch 124 and a toggle member 125. The toggle piece 125 is disposed on the motor sliding rod 1212, so that the toggle piece 125 can slide transversely along with the motor sliding rod 1212.

When the heart chamber 11a is in the maximum volume state, the motor sliding rod 1212 drives the toggle piece 125 to trigger the first travel switch 123, and when the heart chamber 11a is in the minimum volume state, the motor sliding rod 1212 drives the toggle piece 125 to trigger the second travel switch 124.

It should be noted that the first and second travel switches 123 and 124 are used to control 234 the operation of the first solenoid valve, so as to realize the function of increasing the flow rate of the coronary module 2 in the diastolic state of the ventricular cavity 11a and decreasing the flow rate of the coronary module 2 in the systolic state of the ventricular cavity 11 a.

The ventricular simulator 100 includes an electromagnetic relay 3, the coronary artery module 2 includes a flow simulator 23 provided on the inflow line 21 or the outflow line 22, and the flow simulator 23 includes a first electromagnetic valve 234. When the second travel switch 124 is triggered, the first solenoid valve 234 remains open. When the first travel switch 123 is triggered, the first solenoid valve 234 closes. Specifically, referring to fig. 13 to 16, the electromagnetic relay 3 includes an electromagnet 31, a movable contact 32, a normally closed contact 33, a normally open contact 34, an armature 35, and a spring 36; the armature 35 has both ends connected to the movable contact 32 and the spring 36, respectively. When the electromagnet 31 is in a power-off state, the armature 35 is only acted by the elastic reset force of the spring 36, so that the movable contact 32 connected to the armature 35 keeps in contact with the normally closed contact 33, the normally closed contact 33 is closed, and the normally open contact 34 is opened; when the electromagnet 31 is powered, the armature 35 is attracted to move towards the electromagnet 31, and the moving contact 32 is driven to be separated from the normally closed contact 33 and to be in contact with the normally open contact 34, the normally open contact 34 is closed, and the normally closed contact 33 is opened.

Illustratively, to achieve the function of the first solenoid valve 234 being closed when the chamber 11a is in the contracted state and the first solenoid valve 234 being kept open when the chamber 11a is in the diastolic state. Referring to fig. 13 to 16, the first travel switch 123 is a normally closed switch, and the second travel switch 124 is a normally open switch. The electromagnet 31, the first travel switch 123, and the second travel switch 124 of the electromagnetic relay 3 constitute a first series circuit 3 a; the normally open contact 34 of the electromagnetic relay 3, the first electromagnetic valve 234, and the first stroke switch 123 constitute a second series circuit 3 b; the electromagnet 31 of the electromagnetic relay 3, the normally open contact 34 of the electromagnetic relay 3, and the first stroke switch 123 constitute a third series circuit 3 c. Note that the first series circuit loop 3a, the second series circuit loop 3b, and the third series circuit loop 3c are schematically shown by dashed arrow boxes in fig. 13 to 16.

When the ventricular chamber 11a is switched from the contraction state to the relaxation state, the toggle element 125 contacts the second travel switch 124 to trigger the second travel switch 124 to be closed, the first series circuit 3a is conducted, the electromagnet 31 of the electromagnetic relay 3 is electrified, the normally open contact 34 of the electromagnetic relay 3 is closed, the second series circuit 3b and the third series circuit 3c are both conducted, and the first electromagnetic valve 234 is kept open.

When the ventricular chamber 11a is switched from the contraction state to the relaxation state, the toggle piece 125 contacts the first travel switch 123 to trigger the first travel switch 123 to be switched off, the second series circuit 3b and the third series circuit 3c are both switched off, the electromagnet 31 of the electromagnetic relay 3 is powered off, the normally open contact 34 of the electromagnetic relay 3 is switched off, and the first electromagnetic valve 234 is switched off.

In one embodiment, referring to fig. 5 to 7, the toggle member 125 is a toggle piece, the toggle piece is connected to one end of the motor sliding rod 1212, which is away from the piston 122 in the transverse direction, the contact of the first stroke switch 123 is located on one side of the toggle piece, which is away from the piston 122, the contact of the second stroke switch 124 is located on one side of the toggle piece, which is close to the piston 122, and the toggle piece is slidably disposed between the contact of the first stroke switch 123 and the contact of the second stroke switch 124 in the transverse direction. Specifically, the shifting piece is a rectangular sheet structure with a relatively long side length along the longitudinal direction and a relatively short side length along the transverse direction. The body of the first travel switch 123 and the body of the second travel switch 124 are disposed on two sides of the paddle in the longitudinal direction, the contact of the first travel switch 123 and the contact of the second travel switch 124 both extend in the longitudinal direction toward the paddle, and the paddle is in contact with the contact of the first travel switch 123 or the contact of the second travel switch 124 to switch the ventricular cavity 11a between the contraction state and the relaxation state.

With the arrangement, the poking pieces are arranged in a staggered manner relative to the body of the first travel switch 123 and the body of the second travel switch 124 along the transverse direction, so that the situation that the poking pieces are not in contact with the contacts flexibly, and the motor sliding rod 1212 collides with the body of the first travel switch 123 or the body of the second travel switch 124 can be avoided.

In one embodiment, referring to fig. 1 to 7, the ventricular module 1 includes a base 15, the ventricular housing 11 is fixed on the base 15, the driving portion 12 includes a motor seat 126, and the motor coil 1211 is fixed on the base 15 through the motor seat 126. Illustratively, the base 15 includes a plate body 151 and a bar-shaped profile 152 connected to a lower end of the plate body 151. Specifically, the two bar-shaped profiles 152 extend in the transverse direction, the two bar-shaped profiles 152 are arranged at the lower end of the plate body 151 at intervals along the longitudinal direction, and the motor base 126 and the ventricular housing 11 are both fixed on the upper end surface of the plate body 151.

The material of the plate body 151 includes, but is not limited to, PMMA plastic with high structural strength, corrosion resistance and good insulating property.

The strip-shaped section bar 152 includes, but is not limited to, an aluminum section bar with a light structure and good corrosion resistance.

The connection manner of the plate body 151 and the bar-shaped profile 152 includes, but is not limited to, bolting, clamping, welding, etc.

Attachment of the ventricular housing 11 to the base 15 includes, but is not limited to, gluing by plexiglas glue.

The connection mode of the motor base 126 to fix the base 15 includes, but is not limited to, bolting, clamping, welding, etc.

In one embodiment, referring to fig. 1-7, the ventricular module 1 includes a stroke adjustment portion 16 and a clamping portion 17. The clamping portion 17 is formed with a clamping space 17a for clamping the first or

second stroke switch

123, 124. The stroke adjusting portion 16 includes an adjusting screw 161 and an adjusting seat 162, the adjusting seat 162 is fixed on the base 15, the adjusting seat 162 is formed with an adjusting screw hole 162a extending along the transverse direction, one end of the adjusting screw 161 is inserted into the adjusting screw hole 162a and connected with the clamping portion 17, and the rotation of the adjusting screw 161 relative to the adjusting screw hole 162a can make the adjusting screw 161 move along the transverse direction to adjust the position of the clamping portion 17 along the transverse direction.

With such an arrangement, on the one hand, the screw thread fit structure through the screw and the adjusting screw hole 162a in the adjusting seat 162 is simple, and the adjusting precision is high, and on the other hand, after the clamping portion 17 is adjusted to the preset position, the screw does not slide in the transverse direction without rotating the screw, and the adjusting reliability is high.

Illustratively, one clamping portion 17 and one stroke adjusting portion 16 together form a set of clamping components, the first stroke switch 123 and the second stroke switch 124 are respectively matched with the set of clamping components, and the two sets of clamping components are arranged on the plate body 151 of the base 15 at intervals along the longitudinal direction.

The fixing manner of the adjusting seat 162 and the base 15 includes, but is not limited to, gluing through organic glass glue, clamping through bolt connection, welding, etc.

In one embodiment, referring to fig. 5 to 7, the clamping portion 17 includes a first clamping plate 171, a second clamping plate 172 and a fastening adjustment assembly 173, the first clamping plate 171 and the second clamping plate 172 are transversely disposed opposite to each other, one end of the adjustment screw 161 is connected to the first clamping plate 171, the second clamping plate 172 is connected to the first clamping plate 171 through the fastening adjustment assembly 173, a clamping space 17a is formed between the first clamping plate 171 and the second clamping plate 172, and the fastening adjustment assembly 173 is used for adjusting the size of the clamping space 17 a. Specifically, one end of the adjusting screw 161 in the transverse direction is connected to the first clamping plate 171, the second clamping plate 172 is connected to the first clamping plate 171 through the fastening adjusting assembly 173, and when the adjusting screw 161 moves in the transverse direction relative to the adjusting seat 162, the first clamping plate 171 and the second clamping plate 172 can also move synchronously with the adjusting screw 161.

The first clamping plate 171 and the second clamping plate 172 are not limited in structural shape, and illustratively, the first clamping plate 171 and the second clamping plate 172 are disc-shaped structures, which are convenient to rotate and not easy to interfere with the base 15.

In one embodiment, referring to fig. 5 to 7, the fastening adjustment assembly 173 includes a fastening bolt 1731 and a fastening nut 1732, the first clamping plate 171, the second clamping plate 172 and the fastening nut 1732 are sequentially sleeved on the fastening bolt 1731 along the transverse direction, the first stroke switch 123 or the second stroke switch 124 is located in the clamping space 17a, and the fastening nut 1732 is screwed and abutted on the second clamping plate 172 to clamp the first stroke switch 123 or the second stroke switch 124 in the clamping space 17 a.

By adopting the threaded fit of the fastening bolt 1731 and the fastening nut 1732, the distance of the clamping space 17a in the transverse direction can be adjusted, and the travel switch can automatically adapt to travel switches with different dimensions.

A fastening bolt 1731 and a fastening nut 1732 are a set of fastening adjustment assemblies 173, the number of the fastening adjustment assemblies 173 is not limited, and one or more sets of fastening adjustment assemblies 173 may be disposed between the first clamping plate 171 and the second clamping plate 172.

In one embodiment, referring to fig. 1 and 4, the ventricular housing 11 is formed with an exhaust port 11c communicating with the ventricular cavity 11a, and the ventricular module 1 includes an exhaust valve 18, and the exhaust valve 18 is disposed at the exhaust port 11c in an openable and closable manner. The exhaust valve 18 is configured to include, but not limited to, a gate valve, a butterfly valve, a ball valve, a plug valve, and other valve structures for opening and closing the exhaust port 11 c. Illustratively, in one embodiment, the exhaust port 11c is located at the upper portion of the ventricular housing 11, the exhaust valve 18 is a three-way stopcock, and a threaded luer fitting is provided at the exhaust port 11 c. Due to the characteristics of high pressure bearing and good sealing performance of the luer connector, air leakage and liquid leakage at the exhaust port 11c can be avoided.

The material of the ventricular housing 11 includes but is not limited to PMMA organic glass with good light transmittance, high structural strength, corrosion resistance and good insulating property. So that the experimenter can directly observe the inside of the ventricular cavity 11a through the ventricular housing 11.

In one embodiment, referring to fig. 1, the ventricular housing 11 is formed with a ventricular chamber sensor interface 11d communicating with the ventricular chamber 11a, the ventricular module 1 includes a ventricular chamber pressure sensor 19, and the ventricular chamber pressure sensor 19 is connected to the ventricular chamber sensor interface 11 d. Illustratively, the ventricular chamber pressure sensor 19 is disposed at a lateral end of the ventricular housing 11 distal from the piston 122. The ventricular chamber pressure sensor 19 is used to measure the pressure in the ventricular chamber 11a when the extracorporeal simulation circulation system 900 is running, and the central processor 4 can receive the measurement data from the ventricular chamber pressure sensor 19.

Embodiments of specific embodiments of the present application are described below with reference to the accompanying drawings; the specific structure and connection relationship between the ventricular simulator 100 and the extracorporeal simulation circulation system 900 are as described above, and are not described herein again.

The first embodiment:

referring to fig. 1 to 17, the ventricular simulator 100 is connected to the extracorporeal simulation circulation system 900, in this embodiment, the first test area 2a is connected by a straight pipeline, i.e., the first test area 2a does not simulate any pathological condition. The three-way plug valve is opened, liquid is added into the main circulation pipeline 91 in the in-vitro simulation circulation system 900 from the venous chamber 94, the liquid is added to a preset amount, and after the gas in the heart chamber 11a is discharged, the liquid injection is stopped, and the three-way plug valve is closed. After the rest of the electrical parameter settings are finished, the linear motor 121 is operated, and the motor sliding rod 1212 moves transversely in a straight line inside the motor coil 1211 and pushes the piston 122 to reciprocate in the piston slot 11 b.

When the ventricular cavity 11a is in a contraction state, the motor sliding rod 1212 moves towards the direction close to the second travel switch 124, and the internal volume of the ventricular cavity 11a is reduced to simulate ventricular contraction; the motor sliding rod 1212 moves forward to the top point in the direction close to the second travel switch 124, the poke sheet triggers the instant closing of the second travel switch 124 (normally open switch), the contraction of the simulated ventricle is finished, the simulated ventricle is expanded, at this time, the ventricular cavity 11a is switched from the contraction state to the expansion state, the electromagnetic relay 3 is powered, the first electromagnetic valve 234 is powered on and opened, and the coronary flow is increased;

when the ventricular cavity 11a is in a diastole state, the motor sliding rod 1212 moves towards the direction close to the first travel switch 123, and the internal volume of the ventricular cavity 11a is increased to simulate ventricular diastole; when the motor sliding rod 1212 moves forward to the top point in the direction close to the first travel switch 123, the first travel switch 123 (normally closed switch) is triggered by the poking piece to be opened instantaneously, the simulated ventricular diastole is finished, the simulated ventricular contraction is about to occur, at this time, the ventricular cavity 11a is switched from the diastolic state to the systolic state, the electromagnetic relay 3 is powered off, the first electromagnetic valve 234 is powered off and closed, and the coronary flow is reduced.

Meanwhile, the cpu 4 receives signals from an inflow flow sensor 261, an outflow flow sensor 262, an inflow pressure sensor 271, an outflow pressure sensor 272, a ventricular chamber pressure sensor 19, a main circulation flow sensor 95, and other sensors in the extracorporeal simulation circulation system 900. The experimenter may also perform experiments by connecting the ventricular simulator 100 to another extracorporeal simulation circulation system 900, or replace some components of the ventricular simulator 100 while achieving the effect.

The second embodiment:

referring to fig. 1 to 17, based on the first embodiment, the straight pipeline is replaced by a coronary silica gel model, and the model is connected to the first test area 2a, and parameters of the extracorporeal circulation are adjusted in the extracorporeal simulation circulation system 900, for example, the extracorporeal simulation circulation system 900 is adjusted to a healthy work and rest state, and preset parameters of the extracorporeal simulation circulation system 900 are recorded.

The first resistance adjustment valve 233 and the second resistance adjustment valve 235 are then adjusted so that the coronary flow curve approaches the theoretical value. Therefore, the internal hemodynamics of the coronary artery under normal healthy physiology can be simulated for further research. For example, observing changes in all physiological parameters including coronary circulation after accessing other cardiovascular aids. Experimenters can also insert the silica gel model with the specificity of the patient into the test section, or replace the silica gel model with a simple pipeline when achieving the effect.

The third embodiment:

referring to fig. 1 to 17, on the basis of the second embodiment, all parameters of the extracorporeal simulation circulation system 900 are kept unchanged, the opening degrees of the first resistance adjustment valve 233 and the second resistance adjustment valve 235 are unchanged, the coronary silicone model is changed into a narrow coronary silicone model, and the extracorporeal simulation circulation system 900 and the change of parameters in the coronary circulation, such as flow, pressure, etc., are operated and observed. By comparison with the parameter results of the second example, the effect of intracoronary stenosis on physiological parameters can be studied. Subsequent experiments such as measurement of coronary flow reserve fraction, flow field measurement, etc. may also be performed in the second embodiment.

Setting a preset critical value Q of the flow, the signal processing module of the CPU 4 receives a plurality of instantaneous coronary outflow flows of the outflow sensor 262 over a period of time, and calculates an average value Q of the coronary outflow flows _cor Is mixing Q with _cor Comparing with Q, if Q _cor <Q, the second electromagnetic valve 25 is opened, the coronary artery side branch pipeline 24 is conducted, the coronary artery flow is compensated, and the process of automatically adjusting the coronary artery side branch blood supply flow is simulated.

The fourth embodiment:

referring to fig. 1 to 17, the third embodiment of the coronary artery silica gel model with coronary stenosis can be used to test the implantation effect of the coronary stent c. Specifically, the coronary stent c is implanted into a coronary silica gel model with coronary stenosis. The coronary artery stenosis causes the inner diameter of the coronary artery silica gel model to be reduced, so that the flow of the coronary artery is reduced, after the coronary artery stent c is implanted, the blood vessel flow channel of the coronary artery silica gel model is opened, the flow of the coronary artery is increased, and the diseases such as myocardial infarction and the like are simulated and treated. During the experiment, the effect of the coronary stent c can be evaluated by monitoring the measurement results of the inflow flow sensor 261 and the outflow flow sensor 262.

Fifth embodiment:

referring to fig. 1 to 17, a coronary bypass b-graft (CABG) simulation for coronary heart disease can be tested based on the third embodiment of the coronary silica gel model with coronary stenosis. And a coronary bypass b for simulating a blood vessel of a coronary bypass b transplantation is arranged in the second test area 2b, after the coronary bypass b is connected, one end of the coronary bypass b is in butt joint communication with a second end of the output pipeline 131 so as to simulate that the coronary bypass b directly draws blood from the output pipeline 131 for simulating the aorta, and the other end of the coronary bypass b is in butt joint communication with a liquid inlet end of the outflow pipeline 22, such as a cross joint.

The purpose of this experiment was to simulate the blood being pumped from the heart to cross a stenosis or obstruction via the coronary bypass b, increasing coronary flow. The effectiveness of coronary bypass b-grafting can be assessed by monitoring the measurements of the inflow sensor 261 and outflow sensor 262. The coronary bypass b can be a simple pipeline, a silica gel model or a biological blood vessel.

The various embodiments/implementations provided herein may be combined with each other without contradiction. The above description is only a preferred embodiment of the present application and is not intended to limit the present application, and various modifications and changes may be made by those skilled in the art. Any modification, equivalent replacement, improvement and the like made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. A ventricular simulator is used for being connected into an extracorporeal simulation circulation system and is characterized by comprising a ventricular module and a coronary module, wherein the ventricular module comprises a ventricular housing, a driving part, an output pipeline, an input pipeline, a first one-way structure and a second one-way structure; a ventricular cavity is formed in the ventricular housing, and the driving part drives the ventricular cavity to periodically relax or contract; the first ends of the output pipeline and the input pipeline are communicated with the heart chamber, the second ends of the output pipeline and the input pipeline are used for being connected into the extracorporeal simulation circulation system, the first one-way structure is arranged on the output pipeline so that liquid in the output pipeline flows out of the heart chamber in one way, and the second one-way structure is arranged on the input pipeline so that liquid in the input pipeline flows into the heart chamber in one way;

2. A ventricular simulator as claimed in claim 1, wherein the coronary module includes a flow simulator; the flow simulation part is arranged on the inflow pipeline or the outflow pipeline and comprises a first branch pipe, a second branch pipe, a first resistance regulating valve and a first electromagnetic valve; the first resistance regulating valve is arranged on the first branch pipe, the first electromagnetic valve is arranged on the second branch pipe, and the first branch pipe and the second branch pipe are arranged in parallel;

3. A ventricular simulator as claimed in claim 2, wherein the flow simulator includes a second resistance adjustment valve disposed on the inlet line or the outlet line.

4. A ventricular simulator as claimed in claim 1, wherein the coronary module includes a coronary branch line and a second solenoid valve disposed on the coronary branch line, and two ends of the coronary branch line are respectively communicated with the liquid outlet end of the inflow line and the liquid inlet end of the outflow line; and the second electromagnetic valve can be selectively and automatically opened under the condition that the flow of the outflow pipeline is lower than a preset critical value.

5. A ventricular simulator as claimed in claim 1, wherein the coronary module includes an inflow flow sensor disposed on the inflow conduit and an outflow flow sensor disposed on the outflow conduit; and/or the presence of a gas in the gas,

6. A ventricular simulation device according to claim 1, wherein the coronary module includes a coronary compliance chamber for simulating coronary compliance, the coronary compliance chamber being disposed on the inflow conduit or the outflow conduit.

7. A ventricular simulator as claimed in claim 1, wherein the first unidirectional structure is disposed upstream of the inlet end of the inlet conduit; the second one-way structure is arranged at the downstream of the liquid outlet end of the outflow pipeline.

8. A ventricular simulator as claimed in claim 1, wherein the coronary module includes a second test site for accessing a coronary bypass, the second test site being located between the second end of the outlet conduit and the inlet end of the outlet conduit.

9. A ventricular simulator as claimed in claim 1, wherein the drive portion includes a linear motor and a piston, the ventricular housing is a piston cylinder formed with a piston groove open at one end in a transverse direction, the piston is slidably disposed in the piston groove, the piston and the piston groove together enclose the ventricular chamber, and the linear motor drives the piston to slide in the piston groove in the transverse direction to increase or decrease the volume of the ventricular chamber.

10. A ventricular simulator as claimed in claim 9, wherein the linear motor includes a motor coil and a motor slide rod, the motor slide rod is slidably sleeved in the motor coil in the transverse direction, the piston is connected to one transverse end of the motor slide rod, the motor coil drives the motor slide rod to slide in the transverse direction in the excited state, and the motor slide rod drives the piston to slide in the transverse direction.

11. A ventricular simulator as claimed in claim 10, wherein the drive portion includes a first travel switch, a second travel switch and a toggle member, the toggle member being disposed on the motor slide bar;

when the first travel switch is triggered, the first solenoid valve closes.

12. A ventricular simulator as claimed in claim 11, wherein the toggle member is a toggle piece connected to a lateral end of the motor slide rod away from the piston, the contact of the first travel switch is located on a side of the toggle piece away from the piston, the contact of the second travel switch is located on a side of the toggle piece close to the piston, and the toggle piece is slidably disposed between the contact of the first travel switch and the contact of the second travel switch in a lateral direction.

13. A ventricular simulator as claimed in claim 11, wherein the ventricular module includes a base to which the ventricular housing is secured, and the drive portion includes a motor mount by which the motor coil is secured to the base.

14. A ventricular simulator as claimed in claim 13, wherein the ventricular module includes a stroke adjustment portion and a clamp portion; the clamping part is provided with a clamping space for clamping the first travel switch or the second travel switch;

the stroke control portion includes adjusting screw and adjusts the seat, it is fixed in to adjust the seat on the base, it is formed with along horizontal extension's regulation screw to adjust the seat, adjusting screw's one end is worn to locate in the regulation screw and with the clamping part is connected, adjusting screw is relative the rotation of adjusting the screw can make adjusting screw follows the transverse direction motion, in order to adjust the clamping part is along the position of transverse direction.

15. A ventricular simulator as claimed in claim 14, wherein the clamping portion includes a first clamping plate, a second clamping plate and a fastening adjustment assembly, the first clamping plate and the second clamping plate are disposed opposite to each other in the transverse direction, one end of the adjustment screw is connected to the first clamping plate, the second clamping plate is connected to the first clamping plate through the fastening adjustment assembly, the clamping space is formed between the first clamping plate and the second clamping plate, and the fastening adjustment assembly is used for adjusting the size of the clamping space.

16. A ventricular simulator as claimed in claim 15, wherein the fastening adjustment assembly includes a fastening bolt and a fastening nut, the first clamping plate, the second clamping plate and the fastening nut are sequentially sleeved on the fastening bolt in a transverse direction, the first or second travel switch is located in the clamping space, and the fastening nut is screwed to abut against the second clamping plate to clamp the first or second travel switch in the clamping space.

17. A ventricular simulator as claimed in claim 1, wherein the ventricular casing is formed with an exhaust port communicating with the ventricular chamber, and the ventricular module includes an exhaust valve openably and closably disposed at the exhaust port.

18. A ventricular simulation device according to claim 1, wherein the ventricular housing is formed with a ventricular chamber sensor interface in communication with the ventricular chamber, and the ventricular module includes a ventricular chamber pressure sensor connected to the ventricular chamber sensor interface.

19. An extracorporeal simulated circulation system comprising a main circulation pipeline, a ventricular simulator according to any one of claims 1 to 18, and an arterial compliance chamber, a systemic resistance regulator, a venous chamber, and a main circulation flow sensor disposed on the main circulation pipeline;