CN213424272U - Modularized heart pulsation simulation device and biological simulation esophagus ultrasonic simulation system - Google Patents

Abstract

The utility model relates to a medical treatment simulation teaching aid field especially relates to a modularization heart pulsation analogue means and biological simulation esophagus ultrasonic simulation system. The modularized heart pulsation simulation device comprises a simulation heart, a left heart pulsation simulation unit and a right heart pulsation simulation unit which are respectively communicated with the simulation heart; the simulated heart is arranged in the ultrasonic operation unit; the left heart pulsation simulation unit comprises an aorta compliance module, an aorta damping module and a left atrium liquid volume module which are sequentially communicated, and further comprises a left ventricle pulsation driving module; and/or the right heart pulsation simulation unit comprises a pulmonary artery compliance module, a pulmonary artery damping module and a right atrium liquid containing module which are sequentially communicated, and further comprises a right ventricle pulsation driving module. The utility model discloses can highly bionically simulate actual human physiology pulsating flow effect, the application of various scenes can be satisfied in the modular design, can train the doctor to develop heart disease diagnosis and treatment effectively.

Description

Modularized heart pulsation simulation device and biological simulation esophagus ultrasonic simulation system

Technical Field

The utility model relates to a medical treatment simulation teaching aid field especially relates to a modularization heart pulsation analogue means and biological simulation esophagus ultrasonic simulation system.

Background

Interventional techniques are an effective treatment for structural heart disease. Conventional intracardiac interventions are image guided by means of digital subtraction angiography techniques. With the updating of medical concept and the technological progress of biomedical engineering, the interventional therapy technology of structural heart diseases tends to be complicated and has no radioactive radiation, and thus the emergence of the interventional technology of cardiovascular ultrasound is promoted. Compared with the traditional interventional imaging technology, the heart color Doppler ultrasonic energy provides visual key anatomical information of an intracardiac structure, so that the key roles of real-time navigation, positioning, evaluation and the like can be played in the interventional treatment of the structural heart disease. The key point of successful cardiovascular ultrasonic interventional therapy for surgeons is the need of establishing precise image mapping relation among the ultrasonic image, the lesion entity and the surgical instrument in the brain. Especially in transcatheter valve repair surgery, critical operative implementations of the surgical procedure require multi-planar ultrasound sections to provide comprehensive information of the diseased valve for guidance. Conventional cardiac interventionalists lack knowledge and skill in this regard. It is clear that new technology iterations require simulated training platforms that conform to physiological and anatomical features to better guide clinical practice. The simulation training platform can provide an effective means to help the cardiac interventional doctor to learn the cardiac ultrasonic technology, train the doctor to establish the image mapping relation necessary for the ultrasonic interventional operation and effectively guide the operator to perform the ultrasonic interventional operation.

The prior art lacks a modularized heart pulsation simulation device which flexibly realizes a plurality of heart simulation modes by selecting different connection modes between modules through modularized design.

SUMMERY OF THE UTILITY MODEL

In view of the above-mentioned shortcomings of the prior art, the present invention provides a modularized heart pulsation simulation device and a biological simulation esophageal ultrasound simulation system, which provides an effective training means to train the physician to diagnose and treat heart diseases for the needs of the clinician and the design of the real operation environment.

To achieve the above and other related objects, an aspect of the present invention provides a modular heart pulsation simulation apparatus, including a simulation heart and a left heart pulsation simulation unit and/or a right heart pulsation simulation unit respectively communicating with the simulation heart; the simulated heart is arranged in the ultrasonic operation unit; the left heart pulsation simulation unit comprises an aorta compliance module, an aorta damping module and a left atrium liquid volume module which are sequentially communicated, wherein the aorta compliance module is communicated with the aorta, and the left atrium liquid volume module is communicated with the left atrium of the simulated heart; the left ventricle pulsation driving module is used for simulating the relaxation or contraction of the left ventricle of the simulated heart;

and/or the right heart pulsation simulation unit comprises a pulmonary artery compliance module, a pulmonary artery damping module (33) and a right atrium liquid containing module which are sequentially communicated, wherein the pulmonary artery compliance module is communicated with a pulmonary artery, and the right atrium liquid containing module is communicated with the right atrium of the simulated heart; the right ventricular pulse drive module is used for simulating the diastole or contraction of the right ventricle of the simulated heart.

Another aspect of the present invention provides a biological simulation esophagus ultrasound simulation system, including the modular heart pulsation simulation apparatus of the present invention, which further includes a simulation esophagus, wherein the simulation esophagus is located outside the bottom of the heart.

The modular heart pulsation simulation device of the utility model comprises a simulation heart, a pulsation driving module, an artery compliance simulation module and an atrium liquid volume module, and is provided with a first pulsation controller and a second pulsation controller; a group of pulse driving modules, an artery compliance simulation module and an atrium liquid containing module are adopted and connected with the left heart or the right heart of a simulated heart to form a left heart or right heart pulse simulation unit, and a first pulse controller drives a motor to operate, so that left heart pulse simulation or right heart pulse simulation can be realized. Two groups of pulse driving modules, an artery compliance simulation module, an atrium liquid capacity module and a pulse controller are adopted and connected with a simulated heart to form a left heart pulse simulation unit and a right heart pulse simulation unit, the first pulse controller drives a motor of one group of pulse simulation units to run, an auxiliary waveform synchronous line and the first pulse controller share the same motor driving waveform to drive a motor of the other group of pulse simulation units to run, and left and right heart synchronous pulse simulation is achieved. The modularized heart pulsation simulation device can also be provided with an auxiliary valve, and the heart pulsation simulation is realized on the premise of keeping the heart apex of the simulated heart complete. The utility model discloses can highly bionically simulate actual human physiology pulsating flow effect, the application of various scenes can be satisfied in the modular design, can train the doctor to develop heart disease diagnosis and treatment effectively.

Drawings

Fig. 1 is a schematic view of a modular heart pulsation simulation apparatus according to a first embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 2 is a schematic perspective view of a first embodiment of the modular heart pulsation simulation apparatus and a corresponding ultrasound simulation system for simulating esophagus in biological simulation according to the present invention.

Fig. 3 is a schematic view of a modular heart pulsation simulation apparatus according to a second embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 4 is a schematic perspective view of a modular heart pulsation simulation apparatus according to a second embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 5 is a schematic view of a modularized heart pulsation simulation apparatus according to a third embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 6 is a schematic perspective view of a modularized heart pulsation simulation apparatus according to a third embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 7 is a schematic view of a modularized heart pulsation simulation apparatus according to a fourth embodiment of the present invention and a biological simulation esophageal ultrasound simulation system.

Fig. 8 is a schematic perspective view of a fourth embodiment of the modularized cardiac pulsation simulator and a corresponding ultrasound simulation system for simulated esophagus according to the present invention.

Fig. 9 is a schematic structural diagram of a fifth embodiment of the modular heart pulsation simulator and a biological simulation esophageal ultrasound simulation system according to the present invention.

Fig. 10 is a schematic perspective view of a fifth embodiment of the modularized cardiac pulsation simulation apparatus of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 11 is a schematic structural diagram of a modularized heart pulsation simulation apparatus according to a sixth embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 12 is a schematic perspective view of a modularized heart pulsation simulation apparatus according to a sixth embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 13 is a schematic front view of a modularized heart pulsation simulation apparatus according to a seventh embodiment of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 14 is a schematic perspective view of a seventh embodiment of the modular heart pulsation simulation apparatus of the present invention and a corresponding ultrasound simulation system of a biological simulation esophagus.

Fig. 15 is a schematic front view of an eighth embodiment of the modular heart pulsation simulator and a corresponding ultrasonic simulation system of a biological simulation esophagus.

Fig. 16 is a schematic perspective view of an eighth embodiment of the modular heart pulsation simulator according to the present invention and a corresponding ultrasonic simulation system of a biological simulation esophagus.

Fig. 17 is a schematic structural diagram of the heart simulation, esophagus simulation and ultrasound operation unit according to the present invention.

Fig. 18 is a schematic bottom view of the left ventricular pulse driver module according to the present invention.

Fig. 19 is a schematic view of the sectional structure a-a of the left ventricular pulsation driver module according to the present invention.

Fig. 20 is a front view of the aortic compliance module and aortic damping module according to the present invention.

Fig. 21 is a schematic diagram of a cross-sectional B-B structure of the aortic compliance module and aortic damping module according to the present invention.

Fig. 22 is a front view of the left atrial hydrodynamic chamber of the present invention.

Fig. 23 is a schematic bottom view of the right ventricular pulse driver module according to the present invention.

Fig. 24 is a schematic view of the cross-sectional structure of the right ventricular pulsation driving module according to the present invention.

Fig. 25 is a front view structural diagram of the pulmonary artery compliance module and the pulmonary artery damping module according to the present invention.

Fig. 26 is a schematic diagram of a cross-sectional structure of a pulmonary artery compliance module and a pulmonary artery damping module according to the present invention.

Fig. 27 is a front view of the right atrium liquid container module according to the present invention.

Fig. 28 is a schematic diagram of the modularized heart pulsation simulation apparatus and the biological simulation esophageal ultrasound simulation system according to the present invention. Element numbers in the figures:

1 simulating the heart

11 left atrium

12 left ventricle

13 Right atrium

14 right ventricle

15 aorta

16 pulmonary artery

17 vena cava

18 pulmonary vein

2 left heart pulsation simulation unit

21 left ventricular pulse driver module

211 first electric machine

212 first simulated ventricular cavity

213 first drain valve

214 first pressure monitor

215 first endoscope interface

22 aortic compliance module

221 first vent valve

23 aorta damping module

24 left atrium liquid volume module

241 first liquid storage tank

242 third pressure monitor

243 third endoscope interface

244 first temperature sensor

245 first heater

25 first base

251 second endoscope interface

252 second pressure monitor

3 right heart pulsation analog unit

31 right ventricular pulse driver module

311 second electric machine

312 second simulated ventricular cavity

313 second drain valve

314 fourth pressure monitor

315 fourth endoscope interface

32 pulmonary artery compliance module

321 second vent valve

33 pulmonary artery damping module

34 right atrium liquid volume module

341 second liquid storage tank

342 sixth pressure monitor

343 sixth endoscope interface

344 second temperature sensor

345 second heater

35 second base

351 fifth endoscope interface

352 fifth pressure monitor

4 ultrasonic operating unit

5 first pulse controller

6 second pulse controller

7 waveform synchronous line

8 simulated esophagus

9 auxiliary valve

Detailed Description

The following describes the present invention in further detail with reference to the accompanying drawings. These embodiments are provided only for illustrating the present invention and are not intended to limit the present invention.

In the description of the present invention, it should be noted that the terms "center", "longitudinal", "lateral", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", and the like indicate the orientation or positional relationship based on the orientation or positional relationship shown in the drawings, and are only for convenience of description and simplification of the description, but do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and thus, should not be construed as limiting the present invention. Furthermore, the terms "first" and "second" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance.

In the description of the present invention, it is to be noted that, unless otherwise explicitly specified or limited, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected; can be mechanically or electrically connected; they may be connected directly or indirectly through intervening media, or they may be interconnected between two elements. The specific meaning of the above terms in the present invention can be understood according to specific situations by those skilled in the art.

In addition, in the description of the present invention, "a plurality" means two or more unless otherwise specified.

As shown in fig. 1-14, an embodiment of the present invention provides a modular heart pulse simulator. The modular heart pulsation simulation apparatus comprises a simulated heart 1 and a left heart pulsation simulation unit 2 and/or a right heart pulsation simulation unit 3 in communication with the simulated heart 1. Wherein the simulated heart 1 may for example be a simulated heart or an animal ex vivo heart (which may for example be a porcine ex vivo heart). The simulated heart 1 comprises a left atrium 11, a left ventricle 12, a right atrium 13, a right ventricle 14. Right ventricle 14 communicates with pulmonary artery 16 and left ventricle 12 communicates with aorta 15. According with the actual condition of human physiology. The left pericardium contains the critical structures of the left atrium 11, left ventricle 12, aortic valve and mitral valve. The right heart contains the critical structures of the right atrium 13, right ventricle 14, pulmonary valve and tricuspid valve. The simulated heart 1 is arranged in an ultrasound operating unit 4.

The utility model provides an among the modularization heart pulsation analogue means, as figure 1 ~ 4 and as figure 9 ~ 16 left side heart pulsation analogue means 2 holds module 24 including the aorta compliance module 22, aorta damping module 23 and the left atrium liquid that communicate in proper order, aorta compliance module 22 and aorta 15 intercommunication, left atrium liquid holds module 24 and left atrium 11 intercommunication. A left ventricular pulse driver module 21 is also included for simulating the relaxation or contraction of the left ventricle 12 of the simulated heart 1.

The first embodiment is left heart transapical driving, as shown in fig. 1 and 2, which can realize that the power source drives the heart to realize the left heart pulsating circulation through simulating the apex of the left ventricle of the heart. The left heart alone may be simulated transapically, i.e. the left ventricular pulse driver module 21 is in communication with the left ventricle 12 of the simulated heart 1. It should be noted that the modular heart pulsation simulation apparatus includes a simulated heart 1 and a left heart pulsation simulation unit 2 in communication with the simulated heart 1. Wherein the simulated heart 1 may for example be a simulated heart or an animal ex vivo heart (which may for example be a porcine ex vivo heart). The simulated heart 1 has a complete left heart structure (including a left atrium 11, a left ventricle 12, an aortic valve, a mitral valve, an aorta 15, a pulmonary vein 18 and other key structures), and conforms to the actual physiological condition of a human body. In this case, the right heart structures (including right atrium 13, right ventricle 14, pulmonary valve, tricuspid valve, pulmonary artery, and other critical structures) are not necessary. The simulated heart 1 is arranged in an ultrasound operating unit 4.

In a first embodiment, as shown in fig. 1 and 2, the left heart pulsation simulation unit 2 comprises a left ventricle pulsation driving module 21 communicated with the left ventricle apex through the left ventricle apex, an aorta compliance module 22, an aorta damping module 23 and a left atrium liquid volume module 24 communicated in sequence. The aortic compliance module 22 is in communication with the aorta 15, and the left atrial fluid volume module 24 is in communication with the left atrium 11. More specifically, the left ventricular pulsation driver module 21 may be connected to the left ventricle 12 via a first connection, the left atrium 11 may be connected to the exit side of the left atrial fluid volume module 24 via a second connection, and the aorta 15 may be connected to the entrance side of the aortic compliance module 22 via a third connection. The position of the third joint inserted into the aorta 15 can be selected to be inserted into the ascending aorta 15 region, the aorta 15 arch region and the descending aorta 15 region according to requirements, and the outlet side of the aorta compliance module 22 is connected with the inlet side of the aorta damping module 23; the outlet side of aortic damping module 23 is connected to the inlet side of left atrial fluid volume module 24. Thus, a left ventricular pulsation driver module 21 connected to the left ventricle 12 is formed, and the fluid flows through the left ventricle 12, sequentially through the aortic valve, aorta 15, aortic compliance module 22, aortic damping module 23, left atrial fluid containment module 24, pulmonary veins 18, left atrium 11, and the mitral valve, and then returns to the left ventricle 12, the left cardiac pulsation simulation unit 2.

In the first embodiment, as shown in fig. 2 and 19, the left ventricular pulse driver module 21 includes a first simulated ventricular cavity 212 and a first motor 211 disposed on the first simulated ventricular cavity 212, and the first motor 211 is mounted above the first simulated ventricular cavity 212 and can move along the first simulated ventricular cavity 212. The first motor 211 may be, for example, a linear motor, a stepping motor, or the like. Further, in the first embodiment described above, which relates to the transapical driving of the left heart, the first simulated ventricular cavity 212 and the left ventricle 12 are combined into a first chamber, and in general, a purse-string insertion connection joint can be sewn at the apex of the left ventricle 12, and after the connection joint is connected with the first joint of the left ventricular pulse driving module 21 by a silicone tube, the first simulated ventricular cavity 212 and the left ventricle 12 can be combined into the same chamber. When the linear motor moves towards the direction of the first simulated ventricular cavity 212, i.e. during the downward operation of the linear motor, the first chamber volume decreases, the internal pressure rises, the aortic valve opens, the mitral valve closes, and the test fluid is drained from the left ventricle 12 to the aorta 15 through the opened aortic valve, thereby simulating the contraction of the left ventricle 12; when the linear motor moves away from the first simulated ventricular cavity 212, i.e. during the upward operation of the linear motor, the chamber volume increases, the internal pressure decreases, the aortic valve closes, the mitral valve opens, and the test fluid flows from the left atrium 11 to the left ventricle 12 through the open mitral valve, thereby simulating the relaxation of the left ventricle 12.

In a first embodiment, as shown in fig. 1, 18 and 19, the first simulated ventricular cavity 212 is provided with a first endoscope interface 215, which functions to allow an endoscope to enter the interior of the left ventricle 12 through the first endoscope interface 215 for observation, and to maintain a seal to prevent fluid from leaking from the interior of the heart.

In the first embodiment, as shown in fig. 2, a first pulse controller 5 connected to the first motor 211 is further included, which controls the operation state of the first motor 211, and can load any motor driving waveform, and adjust the motor frequency, the operation amplitude and the offset. The first pulsation controller 5 is a pulsation controller in the related art.

In the first embodiment, as shown in fig. 19, the left ventricular pulse driver module 21 is further provided with a first drain valve 213 and a first pressure monitor 214. Wherein the first drain valve 213 may be used to add or drain the test fluid. The first pressure monitor 214 may monitor left ventricular 12 pressure. The first pressure monitor 214 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like.

In a first embodiment, as shown in fig. 1 and 21, the aortic compliance module 22 may be, for example, a reservoir tank installed in the flow path of the aorta 15, and is installed with a first vent valve 221, the first vent valve 221 may be open to the atmosphere, and the amount of gas remaining in the aortic compliance module 22 is adjusted by the first vent valve 221 to adjust the aortic compliance.

In a first embodiment, as shown in fig. 1 and 21, the aortic compliance module 22 and the aortic damping module 23 are both disposed on the first base 25, and typically, a flow channel is disposed in the first base 25, and the aortic compliance module 22 is in communication with the aortic damping module 23 via the flow channel. In use, the test fluid flows from the left ventricle 12 through the aorta 15 into the flow channel of the first base 25, through the aortic compliance module 22, and then through the aortic damping module 23. The first base 25 is provided with a second pressure monitor 252, and the second pressure monitor 252 may be, for example, an invasive blood pressure sensor, a monocrystalline silicon pressure sensor, or the like. The second pressure monitor 252 may monitor the pressure of the aorta 15.

In the first embodiment, as shown in fig. 1 and 20, the first base 25 is provided with a second endoscope interface 251, which is used for allowing an endoscope to enter the aorta 15 through the second endoscope interface 251, observing the aortic valve exit side morphology, and maintaining a seal to ensure that liquid inside the aorta 15 does not leak.

In a first embodiment, the aortic damping module 23 comprises a first damping valve. The first damping valve may be, for example, a conical damping valve. The resistance generated by the fluid can be adjusted by adjusting the damping knob on the first damping valve.

In a first embodiment, as shown in fig. 1 and 22, after passing through the aortic damping module 23, the test fluid flows into the left atrial fluid volume module 24 via a connecting tube. The left atrium fluid reservoir module 24 includes a first reservoir 241, the first reservoir 241 simulating a low pressure environment of the left atrium 11 by communicating with the atmosphere. The left atrial fluid containment module 24 also includes a third pressure monitor 242 that monitors the pressure in the left atrium 11. Third pressure monitor 242 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like. The outlet side of the left atrial reservoir block 24 communicates with the left atrium 11 via a connection tube and fitting. Typically, the left atrial reservoir module 24 is further provided with a first temperature sensor 244 and a first heater 245 for monitoring and adjusting the temperature within the left heart pulsation simulation unit 2. The left atrium liquid containment module 24 is further provided with a third endoscopic interface 243, which is used for allowing an endoscope to enter the left atrium 11 through the third endoscopic interface 243, observing the inside of the left atrium 11 and the mitral valve entrance side morphology, and maintaining the seal to ensure that the liquid in the left atrium 11 does not leak.

The second embodiment is a left heart driven through the aorta, as shown in fig. 3 and 4, which can realize that the power source drives the heart through the simulated heart aorta to realize the left heart pulsating cycle. The left ventricle pulsation driver module 21 can be modeled transarterially on the left heart alone, i.e., on the communicating line between the aorta 15 and the aortic compliance module 22. The heart pulsation simulation apparatus includes a simulated heart 1 and a left heart pulsation simulation unit 2 communicating with the simulated heart 1. Wherein the simulated heart 1 may for example be a simulated heart or an animal ex vivo heart (which may for example be a porcine ex vivo heart). The simulated heart 1 has a complete left heart structure (including key structures such as a left atrium 11, a left ventricle 12, a mitral valve, an aorta 15, a pulmonary vein 18 and the like), and accords with the actual physiological condition of a human body, and the aortic valve is cut or not arranged. In this case, the right heart structures (right atrium 13, right ventricle 14, pulmonary valve, tricuspid valve, pulmonary vein 18, pulmonary artery 16) are not necessary. The simulated heart 1 is arranged in an ultrasound operating unit 4.

In a second embodiment, as shown in fig. 3 and 4, the left heart pulsation simulation unit 2 includes a left ventricle pulsation driving module 21 communicated with the left ventricle 12 through the aorta 15, an auxiliary valve 9 (which may be a mechanical valve such as a ball cage valve) installed in the left ventricle pulsation driving module 21 and allowing the test fluid to flow from the simulated ventricle cavity to the outside, and an aorta compliance module 22, an aorta damping module 23 and a left atrium fluid volume module 24 communicated in sequence. The aortic compliance module 22 communicates with the left ventricular pulse drive module 21 and the left atrial volume module 24 communicates with the left atrium 11. More specifically, the pulsation driving module is connected with the aorta 15 through a first joint, the left atrium 11 is connected with the outlet side of the left atrial liquid volume module 24 through a second joint, and the auxiliary valve 9 is fixed on the pulsation driving module and is connected with the inlet side of the aorta compliance module 22 through a third joint. The outlet side of the aortic compliance module 22 is connected to the inlet side of the aortic damping module 23; the outlet side of aortic damping module 23 is connected to the inlet side of left atrial fluid volume module 24. Thus, a left ventricular pulsation driver module 21 connected to the left ventricle 12 is formed, and the fluid flows through the left ventricle 12, sequentially through the aorta 15 without aortic valve, the left ventricular pulsation driver module 21, the auxiliary valve 9, the aortic compliance module 22, the aortic damping module 23, the left atrial fluid reservoir module 24, the pulmonary veins 18, the left atrium 11, and the mitral valve, and then returns to the left ventricular pulsation simulation unit 2 of the left ventricle 12.

In the second embodiment, as shown in fig. 4 and 19, the left ventricular pulse driver module 21 includes a first simulated ventricular cavity 212 and a first motor 211 disposed on the first simulated ventricular cavity 212, and the first motor 211 is mounted above the first simulated ventricular cavity 212 and can move along the first simulated ventricular cavity 212. The first motor 211 may be, for example, a linear motor, a stepping motor, or the like.

Further, in the second embodiment described above, which relates to left heart transarterial drive, the auxiliary valve 9 may be a mechanical valve such as a ball cage valve, mounted on the left ventricular pulsatile drive module 21, allowing the test fluid to flow from the first simulated ventricular cavity 212 to the outside. The first simulated ventricular cavity 212 and the left ventricle 12 combine to simulate a left ventricle. In this case, a simulated heart without an aortic valve or an isolated animal heart with a native aortic valve removed is used, and the first simulated ventricular cavity 212 and the left ventricle 12 are combined to form a simulated left ventricle after inserting a connection joint into the aorta 15 and fixing the connection joint and connecting the first joint with the left ventricular pulsation driving module 21 through a silicone tube. When the first motor 211 moves towards the first simulated ventricle cavity 212, i.e. during the downward operation of the motor, the first simulated ventricle cavity 212 decreases in volume, increases in internal pressure, the auxiliary valve 9 replacing the aortic valve opens, the mitral valve closes, and the test fluid is discharged from the left ventricle 12 to the aorta 15 through the opened auxiliary valve 9, thereby simulating the contraction of the left ventricle 12; when the linear motor moves in a direction away from the simulated ventricular cavity, namely during the upward operation of the linear motor, the volume of the chamber is increased, the internal pressure is reduced, the auxiliary valve 9 is closed, the mitral valve is opened, and the test liquid flows from the left atrium 11 to the left ventricle 12 through the opened mitral valve, so that the left ventricle 12 diastole is simulated.

In a second embodiment, as shown in fig. 3, 18 and 19, the first simulated ventricular cavity 212 is provided with a first endoscope interface 215, which functions to allow an endoscope to enter the interior of the left ventricle 12 through the first endoscope interface 215 for observation, and to maintain a seal to prevent fluid inside the heart from leaking.

In the second embodiment, as shown in fig. 4, a first pulse controller 5 connected to the first motor 211 is further included, which controls the operation state of the first motor 211, and can load any motor driving waveform, and adjust the motor frequency, the operation amplitude and the offset. The first pulsation controller 5 is a pulsation controller in the related art.

In the second embodiment, as shown in fig. 19, the left ventricular pulse driver module 21 is further provided with a first drain valve 213 and a first pressure monitor 214. Wherein the first drain valve 213 may be used to add or drain the test fluid. The first pressure monitor 214 may monitor left ventricular 12 pressure. The first pressure monitor 214 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like.

In a second embodiment, as shown in fig. 3 and 21, the aortic compliance module 22 may be, for example, a reservoir tank installed in the flow path of the aorta 15, and is installed with a first vent valve 221, the first vent valve 221 may be open to the atmosphere, and the amount of gas remaining in the aortic compliance module 22 is adjusted by the first vent valve 221 so as to adjust the aortic compliance.

In a second embodiment, as shown in fig. 3 and 21, the aortic compliance module 22 and the aortic damping module 23 are both disposed on the first base 25, and typically, a flow channel is disposed in the first base 25, and the aortic compliance module 22 is in communication with the aortic damping module 23 via the flow channel. In use, the test fluid flows from the left ventricle 12 through the aorta 15 into the flow channel of the first base 25, through the aortic compliance module 22, and then through the aortic damping module 23. The first base 25 is provided with a second pressure monitor 252, and the second pressure monitor 252 may be, for example, an invasive blood pressure sensor, a monocrystalline silicon pressure sensor, or the like. The second pressure monitor 252 may monitor the pressure of the aorta 15.

In a second embodiment, as shown in fig. 3 and 20, the first base 25 is provided with a second endoscope interface 251, which is used for allowing an endoscope to enter the aorta 15 through the second endoscope interface 251, observing the aortic valve exit side morphology, and maintaining a seal to ensure that liquid inside the aorta 15 does not leak.

In a second embodiment, the aortic damping module 23 comprises a first damping valve. The first damping valve may be, for example, a conical damping valve. The resistance generated by the fluid can be adjusted by adjusting the damping knob on the first damping valve.

In a second embodiment, shown in fig. 3 and 22, after passing through the aortic damping module 23, the test fluid flows into the left atrial fluid volume module 24 via a connecting tube. The left atrium fluid reservoir module 24 includes a first reservoir 241, the first reservoir 241 simulating a low pressure environment of the left atrium 11 by communicating with the atmosphere. The left atrial fluid containment module 24 also includes a third pressure monitor 242 that monitors the pressure in the left atrium 11. Third pressure monitor 242 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like. The outlet side of the left atrial reservoir block 24 communicates with the left atrium 11 via a connection tube and fitting. Typically, the left atrial reservoir module 24 is further provided with a first temperature sensor 244 and a first heater 245 for monitoring and adjusting the temperature within the left heart pulsation simulation unit 2. The left atrium liquid containment module 24 is further provided with a third endoscopic interface 243, which is used for allowing an endoscope to enter the left atrium 11 through the third endoscopic interface 243, observing the inside of the left atrium 11 and the mitral valve entrance side morphology, and maintaining the seal to ensure that the liquid in the left atrium 11 does not leak.

The modularized heart pulsation simulation device provided by the present invention, as shown in fig. 5 to 8 and fig. 9 to 16, further comprises a right ventricle pulsation driving module 31 communicated with the right ventricle 14; the right heart pulsation simulation unit 3 comprises a pulmonary artery compliance module 32, a pulmonary artery damping module 33 and a right atrium liquid containing module 34 which are sequentially communicated, wherein the pulmonary artery compliance module 32 is communicated with a pulmonary artery 16, and the right atrium liquid containing module 34 is communicated with a right atrium 13.

The third embodiment is right heart transapical driving, and as shown in fig. 5-6, the power source can be used for simulating the cardiac apex of the right ventricle of the heart to drive the heart to realize right heart pulsation circulation. The right heart simulation alone can be performed transapically, i.e. the right ventricular pulse driver module 31 is in communication with the right ventricle 14 of the simulated heart 1. The heart pulsation simulation apparatus includes a simulated heart 1 and a right heart pulsation simulation unit 3 communicating with the simulated heart 1. Wherein the simulated heart 1 may for example be a simulated heart or an animal ex vivo heart (which may for example be a porcine ex vivo heart). The simulated heart 1 has a complete right heart structure (including a right atrium 13, a right ventricle 14, a pulmonary valve, a tricuspid valve, a pulmonary artery 16, a vena cava 17 and other key structures), and accords with the actual physiological condition of a human body. In which case left cardiac structures (including the critical structures of the left atrium 11, left ventricle 12, aortic valve, mitral valve, aorta 15, pulmonary veins 18, etc.) are not necessary. The simulated heart 1 is arranged in an ultrasound operating unit 4.

In a third embodiment, as shown in fig. 5 to 6, the right heart pulsation simulation unit 3 includes a pulmonary artery compliance module 32, a pulmonary artery damping module 33, and a right atrium liquid volume module 34, which are sequentially communicated with the right heart ventricle apex and the right heart ventricle pulsation driving module 31. The pulmonary artery compliance module 32 is in communication with the pulmonary artery 16, and the right atrium fluid volume module 34 is in communication with the right atrium 13. More specifically, the right ventricular pulsation driver module 31 may be connected to the right ventricle 14 through a fourth connector, the right atrium 13 may be connected to the outlet side of the right atrial fluid containment module 34 through a fifth connector, it is generally necessary to clamp the vena cava 17 with hemostatic forceps, one end of the fifth connector is inserted into the vena cava 17 and connected to the right atrium 13 through the vena cava 17, and the other end of the fifth connector stays outside the vena cava 17 and is connected to the outlet side of the right atrial fluid containment module 34. The pulmonary artery 16 and the inlet side of the pulmonary artery compliance module 32 may be connected by a sixth junction. The outlet side of the pulmonary artery compliance module 32 is connected to the inlet side of the pulmonary artery damping module 33; the outlet side of pulmonary artery damping module 33 is connected to the inlet side of right atrial fluid volume module 34. Thus, a right ventricular pulsation driver module 31 connected to the right ventricle 14 is formed, and the fluid flows through the right ventricle 14, sequentially through the pulmonary valve, the pulmonary artery 16, the pulmonary artery compliance module 32, the pulmonary artery damping module 33, the right atrial fluid volume module 34, the vena cava 17, the right atrium 13, and the tricuspid valve, and then returns to the right ventricle 14, as the right ventricular pulsation simulation unit 3.

In the third embodiment, as shown in fig. 5 and 24, the right ventricular pulse driver module 31 includes a second simulated ventricular cavity 312 and a second motor 311 disposed on the second simulated ventricular cavity 312, and the second motor 311 is mounted above the second simulated ventricular cavity 312 and can move along the second simulated ventricular cavity 312. The second motor 311 may be, for example, a linear motor, a stepping motor, or the like.

Further, in the third embodiment, the second simulated ventricle cavity 312 and the right ventricle 14 are combined into a second chamber, and in general, a purse string insertion connection joint can be sewn at the apex of the right ventricle 14 and connected to the fourth joint of the right ventricular pulse driver module 31 by a silicone tube, so that the second simulated ventricle cavity 312 and the right ventricle 14 can be combined into the same chamber. When the linear motor moves towards the direction of the second simulated ventricle cavity 312, namely in the downward operation process of the linear motor, the volume of the second cavity is reduced, the internal pressure is increased, the pulmonary valve is opened, the tricuspid valve is closed, and the test liquid is discharged to the outside of the right ventricle 14 through the pulmonary artery 16 so as to simulate the contraction of the right ventricle 14; when the linear motor moves away from the second simulated ventricular cavity 312, i.e. during upward motion of the linear motor, the chamber volume increases and the test fluid flows into the right ventricle 14 through the right atrium 13 due to the action of the valve, thereby simulating the relaxation of the right ventricle 14.

In a third embodiment, as shown in fig. 5, 23 and 24, the second simulated ventricular cavity 312 is provided with a fourth endoscope port 315, which functions to allow an endoscope to enter the right ventricle 14 through the port for observation and to maintain a seal to prevent the leakage of fluid inside the heart.

In the third embodiment, as shown in fig. 5 and 24, a second pulse controller 6 connected to the second motor 311 is further included. The second pulse controller 6 controls the running state of the second motor 311, and can load any motor driving waveform and adjust the motor frequency, the running amplitude and the offset. The second pulse controller 6 can independently adjust the motor operating amplitude and offset. The second pulse controller 6 is a prior art pulse controller.

In the third embodiment, as shown in fig. 5 and 24, the right ventricular pulse driver module 31 is further provided with a second drain valve 313 and a fourth pressure monitor 314. Wherein the second drain valve 313 may be used to add or drain test fluid. Fourth pressure monitor 314 may monitor right ventricular 14 pressure via an acquisition device. The fourth pressure monitor 314 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like.

In a third embodiment, as shown in fig. 5 and 26, the pulmonary artery compliance module 32 may be, for example, a fluid reservoir mounted in the flow path of the pulmonary artery 16. The pulmonary artery compliance module 32 includes a second vent valve 321 that is open to atmosphere, and the amount of gas retained in the pulmonary artery compliance module 32 is adjusted by the second vent valve 321 to adjust the compliance of the pulmonary artery 16.

In a third embodiment, as shown in fig. 5 and 26, the pulmonary artery compliance module 32 and the pulmonary artery damping module 33 are both disposed on the second base 35, and normally, a flow passage is disposed in the second base 35, and the pulmonary artery compliance module 32 is communicated with the pulmonary artery damping module 33 through the flow passage. During application, the test solution flows from the right ventricle 14 through the pulmonary artery 16 into the flow channel of the second base 35, passes through the pulmonary artery compliance module 32, and then flows through the pulmonary artery damping module 33. A fifth pressure monitor 352 is disposed on the second base 35, and the fifth pressure monitor 352 may be, for example, an invasive blood pressure sensor, a monocrystalline silicon pressure sensor, or the like. A fifth pressure monitor 352 may monitor pulmonary artery 16 pressure.

In a third embodiment, as shown in fig. 5, 25 and 26, the second base 35 is provided with a fifth endoscope interface 351, which is used for allowing an endoscope to enter the pulmonary artery 16 through the fifth endoscope interface 351, observing the exit side morphology of the pulmonary valve, and maintaining a seal to ensure that liquid inside the pulmonary artery 16 does not leak.

In a third embodiment, the pulmonary artery damping module 33 comprises a second damping valve. The second damping valve may be, for example, a conical damping valve. The resistance generated by the fluid can be adjusted by adjusting the damping knob on the second damping valve.

In a third embodiment, as shown in fig. 5 and 27, after flowing through the pulmonary artery damping module 33, the test fluid flows into the right atrial fluid volume module 34 via the connecting tube. The right atrium liquid container module 34 includes a second liquid reservoir 341, and the second liquid reservoir 341 is communicated with the atmosphere to simulate the low pressure environment of the right atrium 13. The right atrium liquid volume module 34 further comprises a sixth pressure monitor 342, which can monitor the pressure in the right atrium 13. Sixth pressure monitor 342 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like. The outlet side of right atrium liquid containment module 34 is in communication with right atrium 13 via a connecting tube and fitting. Typically, the right atrium liquid container module 34 is further provided with a second temperature sensor 344 and a second heater 345 for monitoring and adjusting the temperature inside the right heart pulsation simulation unit 3. The right atrium liquid container module 34 is further provided with a sixth endoscope interface 343, which is used for allowing an endoscope to enter the right atrium 13 through the sixth endoscope interface 343, observing the inside of the right atrium 13 and the inlet side morphology of the tricuspid valve, and maintaining a seal to ensure that liquid in the right atrium 13 does not leak.

The fourth embodiment is right heart pulmonary artery drive, and as shown in fig. 7-8, the power source can be used for driving the heart to realize right heart pulsation circulation by simulating the pulmonary artery of the heart. The right ventricle pulsation driver module 31 can be used for right ventricle simulation alone in a transarterial manner, namely, the right ventricle pulsation driver module is arranged on a communication pipeline between the pulmonary artery 16 and the pulmonary artery compliance module 32. The heart pulsation simulation apparatus includes a simulated heart 1 and a right heart pulsation simulation unit 3 communicating with the simulated heart 1. Wherein the simulated heart 1 may for example be a simulated heart or an animal ex vivo heart (which may for example be a porcine ex vivo heart). The simulated heart 1 has a complete right heart structure (right atrium 13, right ventricle 14, tricuspid valve, pulmonary artery 16, vena cava 17), and conforms to the actual physiological condition of a human body, and the pulmonary valve is cut off or not arranged. In this case, the right cardiac structure (including the critical structures such as the left atrium 11, left ventricle 12, mitral valve, aorta 15, pulmonary veins 18) is not necessary. The simulated heart 1 is arranged in an ultrasound operating unit 4.

In a fourth embodiment, as shown in fig. 7 to 8, the right heart pulsation simulation unit 3 includes a right ventricle pulsation driving module 31 communicated with the right ventricle 14 through the pulmonary artery 16, an auxiliary valve 9 (which may be a mechanical valve such as a ball cage valve) installed in the pulsation driving module and allowing the test solution to flow from the simulated ventricle cavity to the outside, and a pulmonary artery compliance module 32, a pulmonary artery damping module 33, and a right atrium liquid container module 34 that are sequentially communicated. The pulmonary artery compliance module 33 is in communication with the pulmonary artery compliance module 32, and the right atrial fluid volume module 34 is in communication with the right atrium 13. More specifically, the pulsation driver module 34 is connected to the pulmonary artery 16 through a fourth joint, the right atrium 13 is connected to the outlet side of the right atrium liquid volume module 34 through a fifth joint, and the auxiliary valve 9 is fixed to the pulsation driver module and connected to the inlet side of the pulmonary artery compliance module 32 through a sixth joint. The outlet side of the pulmonary artery compliance module 32 is connected to the inlet side of the pulmonary artery damping module 33; the outlet side of pulmonary artery damping module 33 is connected to the inlet side of right atrial fluid volume module 34. Thus, a right ventricular pulse driver module 31 connected to the right ventricle 14 is formed, and the fluid flows through the right ventricle 14, the pulmonary artery without the pulmonary valve, the right ventricular pulse driver module 31, the auxiliary valve 9, the pulmonary artery compliance module 32, the pulmonary artery damping module 33, the right atrial fluid container module 34, the vena cava 17, the right atrium 13, and the tricuspid valve in sequence, and then returns to the right ventricular pulse simulator unit 3 of the right ventricle 14.

In a fourth embodiment, as shown in fig. 7 and 24, the right ventricular pulse driver module 31 includes a second simulated ventricular cavity 312 and a second motor 311 disposed on the second simulated ventricular cavity 312, and the second motor 311 is mounted above the second simulated ventricular cavity 312 and can move along the second simulated ventricular cavity 312. The second motor 311 may be, for example, a linear motor, a stepping motor, or the like.

Further, in the fourth embodiment, the auxiliary valve 9 may be a mechanical valve, such as a ball-cage valve, mounted on the right ventricular pulsation driver module 31, allowing the test fluid to flow from the second simulated ventricular cavity 312 to the outside. The second simulated ventricular cavity 312 and the right ventricle 14 combine to simulate a right ventricle. In this case, after a simulated heart without a pulmonary valve is used, or an isolated animal heart with a natural pulmonary valve cut out is used, and a connection joint is inserted and fixed at the pulmonary artery 16, and is connected to the third joint of the right ventricular pulsation driver module 31 by a silicone tube, the second simulated ventricular cavity 312 and the right ventricle 14 can be combined to form a simulated right ventricle. When the linear motor moves towards the direction of the second simulated ventricular cavity 312, namely, during the downward operation of the linear motor, the simulated ventricular cavity volume is reduced, the internal pressure is increased, the auxiliary valve 9 replacing the pulmonary valve is opened, the tricuspid valve is closed, and the test liquid is discharged from the right ventricle 14 to the pulmonary artery 16 through the opened auxiliary valve 9, so that the contraction of the right ventricle 14 is simulated; when the linear motor moves away from the second simulated ventricular cavity 312, i.e. during the upward operation of the linear motor, the chamber volume increases, the internal pressure decreases, the auxiliary valve 9 closes, the tricuspid valve opens, and the test fluid flows from the right atrium 13 to the right ventricle 14 through the opened tricuspid valve, thereby simulating the relaxation of the right ventricle 14.

In a fourth embodiment, as shown in fig. 7, 23 and 24, the second simulated ventricular cavity 312 is provided with a fourth endoscope port 315, which functions to allow an endoscope to enter the right ventricle 14 through the port for observation and to maintain a seal to prevent the leakage of fluid inside the heart.

In the fourth embodiment, as shown in fig. 7 and 24, a second pulse controller 6 connected to the second motor 311 is further included. The second pulse controller 6 is a prior art pulse controller. In the fourth to eighth embodiments, the second pulse controller 6 is connected to the first pulse controller 5 via the waveform synchronization line 7 to control the operation state of the second motor 311. The second pulse controller 6 shares the same motor driving waveform with the first pulse controller 5 through the waveform synchronization line 7, so that the phases and the frequencies of the waveforms of the first motor 211 and the second motor 311 are the same. The second pulse controller 6 can independently adjust the motor operating amplitude and offset. The first pulse controller 5 and the second pulse controller 6 work cooperatively to simulate physiological heartbeat forms of the left heart and the right heart which are synchronous and have the same frequency but completely different internal pressure conditions. In the synchronous simulation of the left heart and the right heart, the first pulse controller 5 and the second pulse controller 6 can be connected through the waveform synchronous wire 7, so that the beats of the left heart and the right heart can be synchronized but the amplitudes can be independently adjusted.

In the fourth embodiment, as shown in fig. 7 and 24, the right ventricular pulse driver module 31 is further provided with a second drain valve 313 and a fourth pressure monitor 314. Wherein the second drain valve 313 may be used to add or drain test fluid. Fourth pressure monitor 314 may monitor right ventricular 14 pressure via an acquisition device. The fourth pressure monitor 314 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like.

In a fourth embodiment, as shown in fig. 7 and 26, the pulmonary artery compliance module 32 may be, for example, a fluid reservoir mounted in the flow path of the pulmonary artery 16. The pulmonary artery compliance module 32 includes a second vent valve 321 that is open to atmosphere, and the amount of gas retained in the pulmonary artery compliance module 32 is adjusted by the second vent valve 321 to adjust the compliance of the pulmonary artery 16.

In a fourth embodiment, as shown in fig. 7 and 26, the pulmonary artery compliance module 32 and the pulmonary artery damping module 33 are both disposed on the second base 35, and normally, a flow passage is disposed in the second base 35, and the pulmonary artery compliance module 32 is communicated with the pulmonary artery damping module 33 through the flow passage. During application, the test solution flows from the right ventricle 14 through the pulmonary artery 16 into the flow channel of the second base 35, passes through the pulmonary artery compliance module 32, and then flows through the pulmonary artery damping module 33. A fifth pressure monitor 352 is disposed on the second base 35, and the fifth pressure monitor 352 may be, for example, an invasive blood pressure sensor, a monocrystalline silicon pressure sensor, or the like. A fifth pressure monitor 352 may monitor pulmonary artery 16 pressure.

In the fourth embodiment, as shown in fig. 7, 25 and 26, the second base 35 is provided with a fifth endoscope interface 351, which is used for allowing an endoscope to enter the pulmonary artery 16 through the fifth endoscope interface 351, observing the exit side morphology of the pulmonary valve, and maintaining a seal to ensure that liquid inside the pulmonary artery 16 does not leak.

In a fourth embodiment, the pulmonary artery damping module 33 comprises a second damping valve. The second damping valve may be, for example, a conical damping valve. The resistance generated by the fluid can be adjusted by adjusting the damping knob on the second damping valve.

In the fourth embodiment, as shown in fig. 7 and 27, after flowing through the pulmonary artery damping module 33, the test fluid flows into the right atrial fluid volume module 34 via the connecting tube. The right atrium liquid container module 34 includes a second liquid reservoir 341, and the second liquid reservoir 341 is communicated with the atmosphere to simulate the low pressure environment of the right atrium 13. The right atrium liquid volume module 34 further comprises a sixth pressure monitor 342, which can monitor the pressure in the right atrium 13. Sixth pressure monitor 342 may be, for example, an invasive blood pressure sensor, a single crystal silicon pressure sensor, or the like. The outlet side of right atrium liquid containment module 34 is in communication with right atrium 13 via a connecting tube and fitting. Typically, the right atrium liquid container module 34 is further provided with a second temperature sensor 344 and a second heater 345 for monitoring and adjusting the temperature inside the right heart pulsation simulation unit 3. The right atrium liquid container module 34 is further provided with a sixth endoscope interface 343, which is used for allowing an endoscope to enter the right atrium 13 through the sixth endoscope interface 343, observing the inside of the right atrium 13 and the inlet side morphology of the tricuspid valve, and maintaining a seal to ensure that liquid in the right atrium 13 does not leak.

The fifth embodiment is a synchronous simulation of the left and right transapical driving, as shown in fig. 9-10 and fig. 28, the left heart adopts the transapical mode of the first embodiment. The right heart is in the transapical mode of the third embodiment. The method can realize that the power source drives the heart to realize the synchronous pulsation circulation of the left heart and the right heart by simulating the apex of the left ventricle and the apex of the right ventricle of the heart. The specific steps include the whole contents of the first embodiment and the third embodiment. The second pulse controller 6 is connected to the first pulse controller 5 via a waveform synchronization line 7, and controls the operating state of the second motor 311. The second pulse controller 6 shares the same motor driving waveform with the first pulse controller 5 through the waveform synchronization line 7, so that the phases and the frequencies of the waveforms of the first motor 211 and the second motor 311 are the same. The second pulse controller 6 can independently adjust the motor operating amplitude and offset. The first pulse controller 5 and the second pulse controller 6 work cooperatively to simulate physiological heartbeat forms of the left heart and the right heart which are synchronous and have the same frequency but completely different internal pressure conditions. In the synchronous simulation of the left heart and the right heart, the first pulse controller 5 and the second pulse controller 6 can be connected through the waveform synchronous wire 7, so that the beats of the left heart and the right heart can be synchronized but the amplitudes can be independently adjusted.

The sixth embodiment is the transapical driving of the left heart and the transpulmonary artery of the right heart, as shown in fig. 11-12, the transapical mode of the first embodiment is adopted for the left heart. The right heart was simulated transarterially using the fourth example. The method can realize that the power source drives the heart to realize the synchronous pulsation circulation of the left heart and the right heart by simulating the apex of the left ventricle and the pulmonary artery of the right heart of the heart. The specific steps include the whole contents of the first embodiment and the fourth embodiment. The second pulse controller 6 is connected to the first pulse controller 5 via a waveform synchronization line 7, and controls the operating state of the second motor 311. The second pulse controller 6 shares the same motor driving waveform with the first pulse controller 5 through the waveform synchronization line 7, so that the phases and the frequencies of the waveforms of the first motor 211 and the second motor 311 are the same. The second pulse controller 6 can independently adjust the motor operating amplitude and offset. The first pulse controller 5 and the second pulse controller 6 work cooperatively to simulate physiological heartbeat forms of the left heart and the right heart which are synchronous and have the same frequency but completely different internal pressure conditions. In the synchronous simulation of the left heart and the right heart, the first pulse controller 5 and the second pulse controller 6 can be connected through the waveform synchronous wire 7, so that the beats of the left heart and the right heart can be synchronized but the amplitudes can be independently adjusted.

The seventh embodiment is the right heart driven through the aorta and the apex of the right heart, as shown in fig. 13-14, the right heart adopts the simulation of the right artery of the second embodiment. The right heart was simulated transapically using the third embodiment. The method can realize that the power source drives the heart to realize the synchronous pulsation circulation of the left heart and the right heart by simulating the heart apex of the left heart aorta and the right ventricle of the heart. The specific steps include the whole contents of the second embodiment and the third embodiment. The second pulse controller 6 is connected to the first pulse controller 5 via a waveform synchronization line 7, and controls the operating state of the second motor 311. The second pulse controller 6 shares the same motor driving waveform with the first pulse controller 5 through the waveform synchronization line 7, so that the phases and the frequencies of the waveforms of the first motor 211 and the second motor 311 are the same. The second pulse controller 6 can independently adjust the motor operating amplitude and offset. The first pulse controller 5 and the second pulse controller 6 work cooperatively to simulate physiological heartbeat forms of the left heart and the right heart which are synchronous and have the same frequency but completely different internal pressure conditions. In the synchronous simulation of the left heart and the right heart, the first pulse controller 5 and the second pulse controller 6 can be connected through the waveform synchronous wire 7, so that the beats of the left heart and the right heart can be synchronized but the amplitudes can be independently adjusted.

The eighth embodiment is the driving of the left heart through the aorta and the right heart through the pulmonary artery, as shown in fig. 15-16, the left heart adopts the transarterial simulation method of the second embodiment. The right heart was simulated transarterially using the fourth example. The method can realize that the power source drives the heart to realize the synchronous pulsation circulation of the left heart and the right heart through simulating the left heart aorta and the right heart and lung arteries of the heart. The specific steps include the whole contents of the second embodiment and the fourth embodiment. The second pulse controller 6 is connected to the first pulse controller 5 via a waveform synchronization line 7, and controls the operating state of the second motor 311. The second pulse controller 6 shares the same motor driving waveform with the first pulse controller 5 through the waveform synchronization line 7, so that the phases and the frequencies of the waveforms of the first motor 211 and the second motor 311 are the same. The second pulse controller 6 can independently adjust the motor operating amplitude and offset. The first pulse controller 5 and the second pulse controller 6 work cooperatively to simulate physiological heartbeat forms of the left heart and the right heart which are synchronous and have the same frequency but completely different internal pressure conditions. In the synchronous simulation of the left heart and the right heart, the first pulse controller 5 and the second pulse controller 6 can be connected through the waveform synchronous wire 7, so that the beats of the left heart and the right heart can be synchronized but the amplitudes can be independently adjusted.

It is further emphasized that in the foregoing embodiments, the transarterial approach can avoid occupying the apical position, preventing the transapical intervention of the medical device from being impossible or difficult to use in the simulation system.

In general, in the eight embodiments, the pressure at each position can be flexibly adjusted according to different experimental requirements. The signal source can also change the driving waveform to adapt to the special expression of the pressure under different symptoms.

In the modularized heart pulsation simulation apparatus provided by the present invention, in the eight aforementioned embodiments, the cavity of the ultrasonic operation unit 4 is provided with a liquid covering the simulated heart 1, and usually, the liquid completely submerges the simulated heart 1 to completely discharge the gas therein. The liquid medium can adopt pure water, normal saline, glycerol and water proportioning solution, ultrasonic couple sum and other liquids or blood as pulsating flow fluid, thereby meeting the requirements of the simulation training system under various conditions. The ultrasonic operation unit 4 may be, for example, an ultrasonic operation box. The ultrasonic operation unit 4 contains a liquid medium, so that the phenomenon that imaging is unclear due to an interface between the heart and the probe during ultrasonic observation is avoided.

The simulation scheme for the eight examples is as follows:

the embodiment of the utility model provides a still provide a biological simulation esophagus ultrasonic simulation system, including aforementioned modularization heart pulsation analogue means, like fig. 1, 3, 5, 7, 9, 11, 13, 15, including emulation esophagus 8, simulation heart 1 is located in hollow 4 cavitys of supersound operating unit, heart bottom outside is located to emulation esophagus 8, simulates real physiological state. The middle of the ultrasonic operation unit 4 is hollowed, and the simulated esophagus 8 penetrates through the middle, so that the relative position of the simulated heart 1 is close to the human physiological actual condition.

The embodiment of the utility model provides a still provide a biological simulation esophagus supersound analog system, still including the esophagus supersound appearance (not drawn) that is used for simulating esophagus supersound operation, ultrasonic probe can locate in emulation esophagus 8. Typically, during a pulsatile procedure, an esophageal ultrasound probe is inserted into the simulated esophagus 8 to a specific position simulating a cardiac esophageal ultrasound procedure. The Doppler color Doppler ultrasound, DSA and other equipment can be applied to a simulation training system, and can be matched with an endoscope to be mutually compared, so that the simulation training effect is greatly improved.

The utility model provides an among the biological simulation esophagus ultrasonic simulation system fill couplant between simulation esophagus 8 and the simulation heart 1 for strengthen the supersound conduction, make the supersound display image clearer. If necessary, the artificial esophagus 8 may be filled with a coupling agent. In the simulation process, the section to be viewed is adjusted by adjusting the position of the ultrasonic probe. The simulation experiment can be used as esophagus ultrasound training and can be used for training the esophagus ultrasound under the condition closer to the actual application. And the images displayed at different positions and different angles under the influence of the ultrasonic wave of the esophagus can be familiar in the experimental process. The user can master the ultrasonic use method more quickly and accumulate the image analysis experience.

The utility model discloses a working process:

the simulated heart 1 and the simulated esophagus 8 are arranged at reasonable positions according to the physical and practical situation close to the human body, and are connected through the first pulse controller 5 and the second pulse controller 6, so that the running frequency and the phase of the motors of the left heart system and the right heart system are consistent. By moving the first motor 211 towards or away from the first chamber and by moving the second motor 311 towards or away from the second chamber, ventricular relaxation is simulated, and the left ventricular 12 pressure, the aortic 15 pressure, the right atrial 13 pressure, the pulmonary artery 16 pressure are monitored by the respective pressure monitors. Simulating the specific manifestations of pressure under different symptoms. The amount of gas trapped in the aortic compliance module 22 is regulated by the second valve to regulate compliance, the amount of gas trapped in the pulmonary artery compliance module 32 is regulated by the fourth valve to regulate compliance, the resistance to fluid is regulated by the aortic damping module 23, and the resistance to fluid is regulated by the pulmonary artery damping module 33. The first reservoir 241 is in communication with the atmosphere to simulate the low pressure environment of the left atrium 11, and the second reservoir 341 is in communication with the atmosphere to simulate the low pressure environment of the right atrium 13. Through the first valve and the third valve, the test fluid can be added or discharged.

Different intervention ports can be selected according to the intervention paths of different intervention instruments in the process of pulsation operation. Taking the percutaneous interventional aorta 15 as an example, the ascending aorta 15 may be connected to the aortic compliance module 22, and the descending aorta 15 side may be used as the entrance for the instrument intervention. Before intervention operation, one side of the descending aorta 15 is closed, and after pulsation simulation operation, the operation state is adjusted to enable the pressure of each position to basically meet the experiment requirement. The instrument simulation intervention can be performed from the closed side of the descending aorta 15. It should be noted that in vitro simulation cannot fully reproduce physiological conditions, so that the main parameters are satisfied. In the intervention process, the esophagus ultrasonic probe is inserted into the simulated esophagus 8 to a specific position to simulate the esophagus ultrasonic operation, and the intervention operation can be guided through the esophagus ultrasonic image.

In conclusion, the modularized heart pulsation simulation device and the biological simulation esophagus ultrasonic simulation system have high expansibility and freedom degree, the modularized heart pulsation simulation device and the biological simulation esophagus ultrasonic simulation system can simulate the actual human physiological pulsating flow effect in a highly bionic mode, and parameters can be adjusted and monitored. The animal in vitro heart that adopts can be the separation pig heart, and the separation pig heart is extremely similar with the structure of human heart, can provide best emulation training effect, and the cost is extremely low moreover, and it is convenient to install and change. Thereby simulating the motion state of the heart for different heart functions. Under the pulsating flow system, the heart esophagus ultrasonic probe is inserted through the simulated esophagus 8, so that the lesion can be scanned and the information of the lesion can be acquired.

The utility model discloses a modularization heart pulsation analogue means's design, when the right heart synchronous simulation of left heart, be same heartbeat pulsation waveform, output left ventricle pulsation drive module 21 (driver) and second pulsation module, control first motor 211 (pulse pump) and second motor (pulse pump) respectively, under the prerequisite that keeps frequency and phase place the same, realize 2 pulse pump output independent regulation, better simulation left heart and the right heart physiological state of completely different. Meanwhile, a power source connection mode is added, and the existing direct connection apical opening can prevent the simulation of partial transapical interventional instruments by connecting the aorta 15 instead of the apical opening. The pulmonary artery compliance module 32 and the aortic compliance module 22 may simulate aortic 15 and pulmonary artery 16 large vessel compliance, respectively. In addition, the utility model discloses an increase a liquid and hold module (liquid storage pot), can optimize the ultrasonic effect.

The utility model has the advantages of, under the condition that uses transparent test liquid, usable endoscope is supplementary to be observed the state in the pig heart, is favorable to operating the doctor and gets up ultrasonic image and actual influence relevance. The result of the interventional experiment can also be observed with the aid of an endoscope.

The utility model has the advantages that the simulation heart 1 can be specially processed according to different cases, so that the simulation heart is closer to the case conditions. The training and practice of the interventional operation under specific conditions can be carried out.

The above embodiments are merely illustrative of the principles and effects of the present invention, and are not to be construed as limiting the invention. Modifications and variations can be made to the above-described embodiments by those skilled in the art without departing from the spirit and scope of the present invention. Accordingly, it is intended that all equivalent modifications or changes which may be made by those skilled in the art without departing from the spirit and technical spirit of the present invention be covered by the claims of the present invention.

Claims (11)

1. A modularized heart pulsation simulation device is characterized by comprising a simulated heart (1) and a left heart pulsation simulation unit (2) and/or a right heart pulsation simulation unit (3) which are respectively communicated with the simulated heart (1);

the simulated heart (1) is arranged in the ultrasonic operation unit (4);

the left heart pulsation simulation unit (2) comprises an aorta compliance module (22), an aorta damping module (23) and a left atrium liquid containing module (24) which are sequentially communicated, the aorta compliance module (22) is communicated with an aorta (15), and the left atrium liquid containing module (24) is communicated with the left atrium (11) of the simulated heart (1); the left ventricle pulsation driving module (21) is used for simulating the relaxation or contraction of the left ventricle (12) of the simulated heart (1);

and/or the right heart pulsation simulation unit (3) comprises a pulmonary artery compliance module (32), a pulmonary artery damping module (33) and a right atrium liquid containing module (34) which are communicated in sequence, wherein the pulmonary artery compliance module (32) is communicated with a pulmonary artery (16), and the right atrium liquid containing module (34) is communicated with a right atrium (13) of the simulated heart (1); the right ventricle pulsation driving module (31) is used for simulating the relaxation or contraction of the right ventricle (14) of the simulated heart (1).

2. The modular cardiac pulse simulator of claim 1, further comprising any one or more of the following technical features:

A1) the left ventricle pulsation driving module (21) is communicated with the left ventricle (12) of the simulated heart (1);

A2) the left ventricle pulsation driving module (21) is arranged on a communication pipeline of the aorta (15) and the aorta compliance module (22);

A3) the right ventricular pulse driving module (31) is communicated with the right ventricle (14) of the simulated heart (1);

A4) the right ventricle pulsation driving module (31) is arranged on a communication pipeline of the pulmonary artery (16) and the pulmonary artery compliance module (32).

3. The modular cardiac pulsation simulation apparatus according to claim 1, wherein the left ventricular pulsation driver module (21) comprises a first simulated ventricular cavity (212) and a first motor (211) movable along the first simulated ventricular cavity (212), the first simulated ventricular cavity (212) being provided with a first endoscope interface (215); the device also comprises a first pulse controller (5) connected with the first motor (211).

4. The modular cardiac pulsation simulation apparatus as defined in claim 1, wherein the left ventricular pulsation driver module (21) is further provided with a first drain valve (213) and a first pressure monitor (214).

5. The modular cardiac pulsation simulation apparatus according to claim 1, wherein the aortic compliance module (22) comprises a first vent valve (221); the aorta compliance module (22) and the aorta damping module (23) are both disposed on a first base (25), and a second endoscope interface (251) and a second pressure monitor (252) are disposed on the first base (25).

6. The modular cardiac pulsation simulator according to claim 1, wherein the aortic damping module (23) comprises a first damping valve.

7. The modular cardiac pulsation simulation apparatus according to claim 1, wherein the left atrial fluid containment module (24) comprises a first fluid reservoir (241), the left atrial fluid containment module (24) further comprising a third pressure monitor (242), a third endoscopic interface (243), a first temperature sensor (244), and a first heater (245).

8. The modular cardiac pulsation simulation apparatus according to claim 3, wherein the right ventricular pulsation driver module (31) comprises a second simulated ventricular cavity (312) and a second motor (311) movable along the second simulated ventricular cavity (312), the second simulated ventricular cavity (312) being provided with a fourth endoscope interface (315); the device also comprises a second pulse controller (6) connected with a second motor (311); the second pulse controller (6) is connected with the first pulse controller (5) through a waveform synchronization line (7).

9. The modular cardiac pulsation simulation apparatus according to claim 1, further comprising any one or more of the following conditions:

B1) the right ventricle pulsation driving module (31) is also provided with a second liquid discharge valve (313) and a fourth pressure monitor (314);

B2) a second vent valve (321) is arranged on the pulmonary artery compliance module (32); the pulmonary artery compliance module (32) and the pulmonary artery damping module (33) are both arranged on a second base (35), and a fifth endoscope interface (351) and a fifth pressure monitor (352) are arranged on the second base (35);

B3) the pulmonary artery damping module (33) comprises a second damping valve;

B4) the right atrial fluid containment module (34) comprises a second fluid reservoir (341), the right atrial fluid containment module (34) further comprises a sixth pressure monitor (342), a sixth endoscope interface (343), a second temperature sensor (344), and a second heater (345);

B5) the cavity of the ultrasonic operation unit (4) is internally provided with a liquid medium covering the simulated heart (1).

10. A bio-simulation esophageal ultrasound simulation system, comprising the modular cardiac pulsation simulation device according to any one of claims 1 to 9, and further comprising a simulation esophagus (8), wherein the simulation esophagus (8) is disposed outside the bottom of the heart.

11. The bio-simulation esophageal ultrasound simulation system according to claim 10, further comprising an esophageal ultrasound instrument for simulating an esophageal ultrasound operation, wherein an ultrasound probe of the esophageal ultrasound instrument is disposed in the simulated esophagus (8).

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