Pulsating pump system and medical instrument implantation intervention simulation system

Abstract

The utility model discloses a pulsating pump system and a medical instrument implantation intervention simulation system, and relates to the technical field of medical instrument testing, and the pulsating pump system comprises a ventricular simulation cavity, a ventricular intervention simulation cavity, a ventricular intervention simulation cavity, a ventricular intervention simulation cavity, a ventricular intervention simulation cavity and a ventricular intervention simulation cavity, a liquid inlet and a liquid outlet of the ventricular simulation cavity are respectively connected with a liquid inlet pipe and a liquid outlet pipe through one-way valves; the driving assembly is relatively and fixedly connected with the ventricular simulation cavity and is used for driving the diaphragm to do regular reciprocating motion; the flow sensor is connected to the liquid outlet pipe in series and used for detecting the flow velocity of the liquid medium of the circulating system; the pressure sensor is connected to the liquid outlet pipe in series and used for detecting the pressure of liquid at the designated position of the circulating system; the pulse pump system and the medical instrument implantation intervention simulation system can accurately reproduce the physiological waveform in the blood vessel of the human body through closed-loop control.

Description

Technical Field

[0001] This utility model relates to the field of medical device testing technology, and more specifically, to a pulse pump system and a medical device implantation simulation system. Background Technology

[0002] For high-risk vascular stent implants such as coronary stents, rigorous performance testing, animal experiments, and in vivo clinical implantation studies are required before the product can be marketed. Among these, the design of the delivery system that delivers the vascular stent to the designated lesion site is particularly important, especially its compatibility with the vascular access and ease of use during delivery, which have always been key focuses of research and development.

[0003] Currently, the early methods for simulating the use of implants in vitro involved releasing the stent into a matching straight silicone tube and observing the morphology of the stent after expansion. With the improvement of relevant regulatory systems, biomimetic silicone simulated blood vessels have begun to emerge. This allows for better evaluation of the delivery performance, bending performance, retraction performance, and stent release accuracy of vascular stent delivery systems.

[0004] However, current testing processes either select a static environment or use a simple DC pump or eccentric wheel-piston transmission mechanism to drive the flow of solution inside the simulated blood vessels. This cannot simulate the real human blood vessel environment or reproduce complex physiological waveforms (such as aortic pulsation or abnormal pulsation of diseased blood vessels), thus casting doubt on the accuracy of the simulation results.

[0005] In summary, how to solve the problem that existing simulation systems cannot simulate the real human vascular environment and are difficult to reproduce complex physiological waveforms is a problem that urgently needs to be solved by those skilled in the art. Utility Model Content

[0006] In view of this, the purpose of this utility model is to provide a pulsating pump system that drives the diaphragm in the simulated ventricular cavity to reciprocate through a drive component, simulating the pulsating blood supply of the ventricle. Furthermore, the physiological waveform of the output fluid in the simulated ventricular cavity is detected through flow and pressure sensors. The detection results can be used to correct the control of the drive component to accurately reproduce the physiological waveform in human blood vessels. Moreover, complex physiological waveforms can be simulated by changing the control parameters of the control component.

[0007] Another objective of this invention is to provide a medical device implantation simulation system that includes the above-mentioned pulsating pump system, has the same technical features, and can solve the same technical problems.

[0008] To achieve the above objectives, this utility model provides the following technical solution:

[0009] A pulsating pump system for simulating medical device implantation, comprising:

[0010] The ventricular simulation chamber has a diaphragm inside, which is used to change the pressure inside the ventricular simulation chamber by the action of the diaphragm. The inlet and outlet of the ventricular simulation chamber are respectively connected to the inlet pipe and the outlet pipe by one-way valves. The inlet pipe and the outlet pipe are used to connect the circulation system in series.

[0011] A drive assembly, which is fixedly connected to the simulated ventricular chamber, is used to drive the diaphragm to perform regular reciprocating motion;

[0012] A flow sensor, connected in series with the outlet pipe, is used to detect the flow rate of the liquid medium in the circulation system;

[0013] A pressure sensor, connected in series with the outlet pipe, is used to detect the pressure of the liquid at a specified location in the circulation system.

[0014] Preferably, the simulated ventricular cavity is equipped with a heating component and a temperature sensor for regulating the temperature of the liquid medium within the simulated ventricular cavity.

[0015] Preferably, a first compliance chamber is connected to the outlet of the ventricular simulation chamber to eliminate turbulence in the outlet tube.

[0016] Preferably, an atrial simulation chamber is connected to the inlet of the ventricular simulation chamber. The atrial simulation chamber is a cylindrical structure with an open top, and the bottom of the cylindrical structure is connected to the inlet pipe. In practical use, a low-pressure environment in the atrium can be simulated by adjusting the height of the water column in the atrial simulation chamber.

[0017] Preferably, the inlet pipe upstream of the atrial simulation chamber is connected in series with a vascular damping simulation component and a second compliance chamber. The vascular damping simulation component is used to simulate the flow damping of liquid media in blood vessels, and the second compliance chamber is used to simulate the contraction / dilation of blood vessels.

[0018] Preferably, the drive assembly includes a linear motor and a piston;

[0019] The linear motor is fixedly connected to the simulated ventricular cavity and is used to drive the piston to reciprocate.

[0020] The piston is fixedly connected to the diaphragm.

[0021] Preferably, the drive assembly further includes a displacement sensor for detecting the displacement of the piston.

[0022] In practical applications, by detecting the piston displacement, the output per beat of the motor can be derived, thereby improving the control accuracy of the simulation.

[0023] A medical device implantation simulation system includes a bionic blood vessel system and a pulsating pump system as described above, wherein the inlet pipe is connected to the outlet of the bionic blood vessel system, and the outlet pipe is connected to the inlet of the bionic blood vessel system.

[0024] The pulsating pump system provided by this utility model has at least the following advantages compared with the prior art:

[0025] 1. A diaphragm is placed inside the simulated ventricular chamber, and a drive component is used to drive the diaphragm to reciprocate, thereby simulating the pulsatile pumping of blood in the ventricle. By changing the reciprocating frequency and stroke length of the diaphragm, different physiological waveforms of blood supply to the ventricle can be simulated. That is, by changing the control parameters of the drive component, different and complex physiological waveforms can be simulated.

[0026] 2. Simultaneously, a pressure sensor and a flow sensor are integrated after the outlet tube to detect the pressure and flow rate of the fluid exiting the simulated ventricular chamber. This facilitates the mapping of the physiological waveform of the fluid output from the simulated ventricular chamber, which is then compared with the simulated physiological waveform. The parameters of the diaphragm motion drive component are then corrected to achieve closed-loop control of the entire pulse pump system, ensuring accurate reproduction of the physiological waveform within human blood vessels.

[0027] The medical device implantation simulation system provided by this utility model includes the above-mentioned pulsating pump system and has the same beneficial effects. Attached Figure Description

[0028] To more clearly illustrate the technical solutions in the embodiments of this utility model or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on the provided drawings without creative effort.

[0029] Figure 1 This is a schematic diagram of the pulsating pump system provided by this utility model;

[0030] Figure 2 This is a front view of the pulsating pump system provided by this utility model;

[0031] Figure 3 A top view of the pulsating pump system provided by this utility model;

[0032] Figure 4 for Figure 2 Sectional view at point AA;

[0033] Figure 5 for Figure 2 Sectional view at point BB;

[0034] Figure 6 for Figure 3 Sectional view at CC;

[0035] Figure 7 This is a schematic diagram of the biomimetic blood vessel system provided by this utility model.

[0036] Figures 1-6 middle:

[0037] 1. Simulated ventricular chamber; 11. Diaphragm; 12. Heating assembly; 13. Outlet check valve; 14. Inlet check valve;

[0038] 2. Drive components; 21. Linear motor; 22. Displacement sensor; 23. Piston;

[0039] 3. First compliance cavity;

[0040] 4. Flow sensor;

[0041] 5. Second compliance cavity;

[0042] 6. Vascular damping simulation component;

[0043] 7. Simulated atrial cavity.

[0044] Figure 7 middle:

[0045] Part I represents intracranial vessels; Part II represents the thoracic aortic vessels; Part III represents the lower limb vessels; a represents the left middle cerebral artery; b represents the right middle cerebral artery; c represents the tibiofibular artery; d represents the femoropopliteal artery; and e represents the left ventricular outlet. Detailed Implementation

[0046] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0047] The core of this invention is to provide a pulsating pump system that drives the diaphragm in the simulated ventricular cavity to reciprocate through a drive component, simulating the pulsating blood supply of the ventricle. Furthermore, the physiological waveform of the output fluid from the simulated ventricular cavity is detected by a flow sensor and a pressure sensor. The detection results can be used to correct the control of the drive component in order to accurately reproduce the physiological waveform in human blood vessels.

[0048] Another core aspect of this invention is to provide a medical device implantation simulation system that includes the aforementioned pulsating pump system, possessing the same technical features and capable of solving the same technical problems.

[0049] Please refer to Figure 1 , Figure 2 and Figure 3 A pulsating pump system for simulating medical device implantation, comprising:

[0050] The ventricular simulation chamber 1 is equipped with a diaphragm 11, which is used to change the pressure inside the ventricular simulation chamber 1 by the action of the diaphragm 11. The inlet and outlet of the ventricular simulation chamber 1 are connected to the inlet pipe and the outlet pipe respectively by a one-way valve. The inlet pipe and the outlet pipe are used to connect the circulation system in series.

[0051] The drive component 2 is fixedly connected to the ventricular simulation chamber 1 and is used to drive the diaphragm 11 to perform regular reciprocating motion.

[0052] Flow sensor 4, connected in series with the outlet pipe, is used to detect the flow rate of the liquid medium in the circulation system;

[0053] A pressure sensor, connected in series with the outlet pipe, is used to detect the pressure of liquid at a specified location in the circulation system.

[0054] like Figure 1 , Figure 2 and Figure 3 As shown, an inlet check valve 14 and an outlet check valve 13 are respectively installed at the inlet and outlet of the ventricular simulation chamber 1. When the drive assembly 2 drives the diaphragm 11 to move to expand the effective volume of the ventricular simulation chamber 1, the pressure inside the ventricular simulation chamber 1 decreases, the inlet check valve 14 is opened, and the liquid medium can enter the ventricular simulation chamber 1 through the inlet. When the drive assembly 2 drives the diaphragm 11 to move to reduce the effective volume of the ventricular simulation chamber 1, the pressure inside the ventricular simulation chamber 1 increases, the outlet check valve 13 is opened, and the liquid medium inside the ventricular simulation chamber 1 is discharged through the outlet. As the drive assembly 2 drives the diaphragm 11 to reciprocate, the liquid medium is discharged from the outlet in a pulsed manner.

[0055] In this process, changing the reciprocating frequency of diaphragm 11 changes the frequency and velocity of the liquid medium pulse discharged from the outlet; changing the maximum stroke of diaphragm 11 changes the maximum pressure of the liquid medium discharged from the outlet; and changing the motion acceleration of diaphragm 11 changes the acceleration of the liquid medium flow velocity discharged from the outlet. In other words, changing any one of the reciprocating frequency, maximum stroke, and motion acceleration of diaphragm 11 can change the output waveform of the liquid medium discharged from the outlet.

[0056] By detecting the pressure and flow rate of the liquid medium discharged from the outlet using pressure sensor and flow sensor 4, the actual output waveform of the liquid medium discharged from the outlet can be obtained. The actual output waveform is compared with the physiological waveform to be imitated, and then the reciprocating frequency, maximum stroke and / or motion acceleration of diaphragm 11 are corrected. Finally, the actual output waveform is consistent with the physiological waveform to be imitated, that is, the closed-loop control of the pulsating pump system is realized, ensuring the accuracy of the simulated physiological waveform.

[0057] Moreover, the driving component 2 drives the diaphragm 11 to move. By changing the parameters of the driving component 2, the motion parameters of the diaphragm 11 can be changed, thereby simulating various physiological waveforms and meeting the simulation needs of different biomimetic vascular systems.

[0058] In some embodiments, a heating assembly 12 and a temperature sensor are provided inside the ventricular simulation chamber 1 to regulate the temperature of the liquid medium inside the ventricular simulation chamber 1.

[0059] like Figure 5 As shown, a heating component 12 and a temperature sensor are added to the ventricular simulation chamber 1 to precisely control the temperature of the liquid medium in the ventricular simulation chamber 1, so as to simulate the temperature of human blood and make the simulation scenario of the pulse pump system closer to the actual blood supply scenario of human blood vessels.

[0060] In some embodiments, a first compliant cavity 3 is connected to the outlet of the ventricular simulation cavity 1 to eliminate turbulence in the outlet tube.

[0061] like Figure 3 and Figure 4 As shown, a first compliance chamber 3 is provided at the outlet of the ventricular simulation chamber 1. The first compliance chamber 3 is a columnar structure with its bottom connected to the outlet and its top sealed. When the one-way valve 13 is open, the liquid medium enters from the bottom of the first compliance chamber 3. Part of the liquid medium flows directly along the outlet pipe, while part accumulates in the first compliance chamber 3. During this process, the air above the first compliance chamber 3 is compressed. When the one-way valve 13 is closed, the liquid medium stops entering the first compliance chamber 3. At this time, the air above the first compliance chamber 3 is restored, allowing the liquid medium originally stored in the first compliance chamber 3 to be discharged through the outlet pipe, thereby eliminating turbulence in the outlet pipe.

[0062] In some embodiments, an atrial simulation chamber 7 is connected to the inlet of the ventricular simulation chamber 1. The atrial simulation chamber 7 is a columnar structure with an open top, and the bottom of the columnar structure is connected to the inlet pipe.

[0063] like Figure 4 and Figure 6 As shown, an atrial simulation chamber 7 with a top opening is provided at the inlet to simulate the low pressure inside the atrium, ensuring that the inlet check valve 14 is closed when the ventricular simulation chamber 1 is under high pressure.

[0064] In practical use, the low-pressure environment of the atrium can be simulated by adjusting the height of the water column in the simulated atrial chamber 7.

[0065] In some embodiments, the inlet tube upstream of the atrial simulation chamber 7 is connected in series with a vascular damping simulation component 6 and a second compliance chamber 5. The vascular damping simulation component 6 is used to simulate the flow damping of liquid media in blood vessels, and the second compliance chamber 5 is used to simulate the contraction / dilation of blood vessels.

[0066] like Figure 4 and Figure 6 As shown, in practical applications, the inlet pipe is connected to the outlet of the bionic blood vessel system. An adjustable blood vessel damping simulation component 6 is set in the inlet pipe. By changing the internal diameter, that is, changing the resistance of the liquid medium backflow, the resistance of blood flow in the blood vessel is simulated.

[0067] Furthermore, a second compliant cavity 5 is added inside the inlet pipe. The second compliant cavity 5 is a columnar structure with its bottom connected to the inlet pipe. When the liquid medium flows through the second compliant cavity 5, it can either flow directly out of the inlet pipe or be stored in the second compliant cavity 5. The principle is as follows: when the vascular damping simulation component 6 is fully open, the liquid medium enters the second compliant cavity 5 and flows directly into the inlet pipe through the vascular damping simulation component 6. When the vascular damping simulation component 6 is partially closed, the liquid medium enters the second compliant cavity 5, part of which flows into the inlet pipe through the vascular damping simulation component 6, and part of which is stored in the second compliant cavity 5. The air in the second compliant cavity 5 is compressed. When the driving component 2 drives the diaphragm 11 to move upward, the bionic blood vessel loses its power source. At this time, the compressed air is restored, driving the liquid medium stored in the second compliant cavity 5 to flow back to the inlet pipe and the bionic blood vessel, so as to ensure the continuous positive pressure inside the bionic blood vessel and simulate the contraction / dilution of the real blood vessel when transporting blood.

[0068] In some embodiments, an openable and closable connection port is provided at the top of the second compliance cavity 5, and the connection port is connected through a gas regulating device, so that the initial air pressure at the top of the second compliance cavity 5 can be regulated to simulate the average pressure of the vasoconstriction / vasodilation process of blood vessels at different locations.

[0069] In some embodiments, the drive assembly 2 includes a linear motor 21 and a piston 23;

[0070] The linear motor 21 is fixedly connected to the ventricular simulation chamber 1 and is used to drive the piston 23 to perform reciprocating motion.

[0071] Piston 23 is fixedly connected to diaphragm 11.

[0072] like Figure 5As shown, the drive assembly 2 adopts a combination of linear motor 21 and piston 23. The reciprocating motion of linear motor 21 drives the reciprocating motion of piston 23, which in turn drives the reciprocating motion of diaphragm 11. The piston 23 is connected to diaphragm 11, and there is a large contact area between the two, which helps to avoid damage caused by concentrated force on the surface of diaphragm 11, thereby ensuring the airtightness of the ventricular simulation chamber 1.

[0073] Meanwhile, using a linear motor 21 as a power source facilitates precise control of the reciprocating frequency, maximum displacement, and motion acceleration of the diaphragm 11, thereby improving the accuracy of the output waveform.

[0074] In some embodiments, the drive assembly 2 adopts a combination of a voice coil motor and a piston 23. The voice coil motor can adjust the maximum displacement and acceleration of the piston 23 and the diaphragm 11 by changing the input power. At the same time, changing the frequency of the input current can change the reciprocating frequency of the piston 23 and the diaphragm 11, thereby simplifying the control logic of the drive assembly 2.

[0075] In some embodiments, the drive assembly 2 further includes a displacement sensor 22 for detecting the displacement of the piston 23.

[0076] like Figure 5 As shown, the displacement of the piston 23 or diaphragm 11 is detected by setting displacement sensor 22, and the detection result is directly fed back to the control module of linear motor 21 or voice coil motor to realize closed-loop control of linear motor 21 or voice coil motor and ensure the output accuracy of drive component 2.

[0077] Furthermore, by detecting the displacement of piston 23, the output per beat of the motor can be derived, thereby improving the control accuracy of the simulation.

[0078] In addition to the pulsating pump system disclosed in the above embodiments, this utility model also provides a medical device implantation simulation system including the above-mentioned pulsating pump system, comprising a bionic blood vessel system and any one of the above-mentioned pulsating pump systems, wherein the inlet pipe is connected to the outlet of the bionic blood vessel system, and the outlet pipe is connected to the inlet of the bionic blood vessel system.

[0079] like Figure 7 As shown, Part I represents intracranial blood vessels, Part II represents the thoracic aortic vessels, Part III represents the lower limb blood vessels, point a represents the left middle cerebral artery, point b represents the right middle cerebral artery, point c represents the tibiofibular artery, point d represents the femoropopliteal artery, and point e represents the left ventricular outlet.

[0080] In the actual simulation, e is connected to the outlet tube of the simulated ventricular chamber 1, and a, b, c, and d are connected to the inlet tubes respectively, forming a complete medical device implantation simulation system. The liquid medium circulates between the pulsating pump system and the bionic blood vessel system.

[0081] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on the differences from other embodiments. The same or similar parts between the various embodiments can be referred to each other.

[0082] The pulse pump system and medical device implantation simulation system provided by this utility model have been described in detail above. Specific examples have been used to illustrate the principles and implementation methods of this utility model. The descriptions of the embodiments above are only for the purpose of helping to understand the method and core ideas of this utility model. It should be noted that for those skilled in the art, several improvements and modifications can be made to this utility model without departing from the principles of this utility model, and these improvements and modifications also fall within the protection scope of the claims of this utility model.

Claims

1. A pulsating pump system for simulating medical device implantation, characterized in that, include: The ventricular simulation chamber (1) is provided with a diaphragm (11) inside, which is used to change the pressure inside the ventricular simulation chamber (1) by the action of the diaphragm (11). The inlet and outlet of the ventricular simulation chamber (1) are respectively connected to the inlet pipe and the outlet pipe through a one-way valve. The inlet pipe and the outlet pipe are used to connect the circulation system in series. The driving component (2) is fixedly connected to the simulated ventricular chamber (1) and is used to drive the diaphragm (11) to perform regular reciprocating motion. Flow sensor (4), connected in series with the outlet pipe, is used to detect the flow rate of the liquid medium in the circulation system; A pressure sensor, connected in series with the outlet pipe, is used to detect the pressure of the liquid at a specified location in the circulation system.

2. The pulsating pump system according to claim 1, characterized in that, The ventricular simulation chamber (1) is equipped with a heating component (12) and a temperature sensor for regulating the temperature of the liquid medium inside the ventricular simulation chamber (1).

3. The pulsating pump system according to claim 1, characterized in that, The ventricular simulation chamber (1) is connected to a first compliance chamber (3) at its outlet to eliminate turbulence in the outlet tube.

4. The pulsating pump system according to claim 1, characterized in that, The inlet of the ventricular simulation chamber (1) is connected to an atrial simulation chamber (7), which is a columnar structure with an open top, and the bottom of the columnar structure is connected to the inlet pipe.

5. The pulsating pump system according to claim 4, characterized in that, The inlet pipe upstream of the atrial simulation chamber (7) is connected in series with a vascular damping simulation component (6) and a second compliance chamber (5). The vascular damping simulation component (6) is used to simulate the flow damping of liquid media in blood vessels, and the second compliance chamber (5) is used to simulate the contraction / dilation of blood vessels.

6. The pulsating pump system according to claim 1, characterized in that, The drive assembly (2) includes a linear motor (21) and a piston (23); The linear motor (21) is fixedly connected to the ventricular simulation chamber (1) and is used to drive the piston (23) to reciprocate. The piston (23) is fixedly connected to the diaphragm (11).

7. The pulsating pump system according to claim 6, characterized in that, The drive assembly (2) also includes a displacement sensor (22) for detecting the displacement of the piston (23).

8. A medical device implantation simulation system, characterized in that, The system includes a biomimetic blood vessel system and a pulsating pump system as described in any one of claims 1-7, wherein the inlet pipe is connected to the outlet of the biomimetic blood vessel system, and the outlet pipe is connected to the inlet of the biomimetic blood vessel system.

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