Ventricular pacing device and extracorporeal circulation simulation system

Abstract

The utility model relates to medical instrument technical field provides a kind of ventricle pulsation device and extracorporeal circulation simulation system, and the inside structure of pulsation base in ventricle pulsation device has ventricle cavity, the side wall of pulsation base is equipped with mounting port, mounting port is communicated with ventricle cavity, the top wall of pulsation base is equipped with opening, opening is communicated with ventricle cavity;One-way valve is located in mounting port;Piston is by opening and is extended into ventricle cavity, and with the cavity wall of ventricle cavity abuts;The mounting mechanism in driving assembly is located in pulsation base, and mounting mechanism is provided with mounting space;Voice coil motor is fixed in mounting space, and the output shaft of voice coil motor is connected with piston, for driving piston linear reciprocating motion along the cavity wall of ventricle cavity.The utility model directly drives by voice coil motor, can solve the problem of traditional pneumatic drive lag, large screw transmission gap, realized the high-precision simulation of ventricle systole and diastole process, while compact structure, response fast, can be widely applied in biomedical engineering field.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to a ventricular pulsation device and an extracorporeal circulation simulation system. Background Technology

[0002] Extracorporeal circulation simulation systems are key devices used to simulate human blood circulation function, playing an irreplaceable role in the research, testing, and evaluation of high-end medical devices such as artificial hearts, artificial valves, and ventricular assist devices. Among them, the ventricular pacing device, as the core component of the system, directly affects the simulation accuracy of the hemodynamic environment and is crucial for evaluating the functional adaptability of the ventricular pacing device under different physiological states.

[0003] With increasing clinical demands, high-precision simulation of the dynamic processes of ventricular contraction (especially high-frequency transient changes) has become a research hotspot. However, existing simulation schemes for ventricular systole and diastole still have many shortcomings. Currently, Chinese patent publication number CN216746724U discloses a testing system for ventricular assist devices, which simulates the contraction and relaxation of ventricles by driving changes in gas pressure. However, due to the compressibility of gases, the pneumatic drive system is prone to significant dynamic lag during the response process, making it difficult to meet the accurate simulation requirements of high-frequency (such as rapid beats) and transient (such as sudden pressure changes) processes of the ventricle. In addition, this pneumatic system requires large peripherals such as air compressors and vacuum pumps, and the pipeline connections are complex, resulting in a large overall size and cumbersome structure of the device, making it unsuitable for miniaturized and integrated application scenarios.

[0004] Chinese patent publication number CN110648580A discloses an experimental device for simulating left ventricular function. It uses a servo motor to drive a lead screw or synchronous belt, which in turn drives a piston in reciprocating motion to simulate ventricular contraction and relaxation. However, the transmission mechanism of the servo motor (such as lead screw backlash and synchronous belt elastic deformation) inevitably has transmission delays, resulting in millisecond-level dynamic response lag and loss of output accuracy, making it difficult to reproduce the instantaneous changes in ventricular contractions (such as the rapid switching between the rapid filling and ejection phases).

[0005] In summary, existing ventricular pulsation devices still have limitations in terms of dynamic response speed, system compactness, and simulation accuracy, and cannot meet the high-precision simulation requirements of high-frequency and transient dynamic processes. Utility Model Content

[0006] This invention provides a ventricular pulsation device and an extracorporeal circulation simulation system to address the aforementioned technical deficiencies in the prior art. By using a voice coil motor for direct drive, sinusoidal motion control, and a sealed cavity structure design, it solves the problems of lag in traditional pneumatic drive and large clearance in lead screw transmission, achieving high-precision simulation of the ventricular contraction and relaxation process. At the same time, it has a compact structure and fast response, and can be widely used in the field of biomedical engineering.

[0007] The first aspect of this utility model provides a ventricular pulsation device, comprising: The pulsating base has an internal ventricular cavity. The side wall of the pulsating base has an installation port that communicates with the ventricular cavity. The top wall of the pulsating base has an opening that communicates with the ventricular cavity. A one-way valve is provided at the mounting port; The piston extends into the ventricular cavity through the opening and abuts against the cavity wall of the ventricular cavity; The driver component includes: An installation mechanism is provided on the pulsating base, and the installation mechanism is provided with an installation space; A voice coil motor is fixedly installed in the mounting space. The output shaft of the voice coil motor is connected to the piston and is used to drive the piston to perform linear reciprocating motion along the cavity wall of the ventricle.

[0008] According to the ventricular pulsation device provided by this utility model, the effective stroke of the voice coil motor is positively correlated with the stroke volume of the ventricular cavity.

[0009] According to the ventricular pulsation device provided by this utility model, the stroke volume ranges from 20 to 100 mL.

[0010] According to the ventricular pulsation device provided by this utility model, the mounting mechanism includes: The fixing plate is fixedly connected to the pulsating base; Support plates are spaced apart and oppositely disposed on the fixed plate; A limiting plate is fixedly disposed at one end of the support plate away from the fixing plate; The fixing plate, the support plate, and the limiting plate enclose the installation space, and the voice coil motor is mounted in the installation space via a motor mounting bracket.

[0011] The ventricular pulsation device provided by this utility model further includes: A position detection element is disposed in the mounting mechanism and is used to detect the displacement information of the voice coil motor; A control component is connected to both the position detection element and the driver of the voice coil motor, and is used to receive displacement information from the position detection element and to control the operation of the voice coil motor.

[0012] According to the ventricular pulsation device provided by this utility model, the piston is provided with a star-shaped sealing ring, and the star-shaped sealing ring is in frictional contact with the cavity wall of the ventricular cavity.

[0013] According to the ventricular pulsation device provided by this utility model, the pulsation base includes: The base body has an internal cavity. A sleeve is disposed in the receiving cavity and is interference-fitted with the inner wall of the receiving cavity. The height of the sleeve is adapted to the effective stroke of the piston. The piston abuts against the inner wall of the sleeve, and the sleeve, the bottom wall of the accommodating cavity, and the piston together enclose the relatively closed ventricular cavity.

[0014] According to the ventricular pulsation device provided by this utility model, the base body is provided with a pressure relief groove and an overflow groove, the pressure relief groove is connected to the receiving cavity, and the overflow groove is connected to the pressure relief groove; The pressure relief groove is arranged along the circumferential direction of the accommodating cavity, and the overflow groove is arranged along the radial direction of the accommodating cavity and extends to the outer side of the base body.

[0015] According to the ventricular pulsation device provided by this utility model, the sleeve has pressure relief holes arranged in an array along the circumferential direction near the top end, and the positions of the pressure relief holes correspond to the positions of the pressure relief grooves.

[0016] A second aspect of this invention provides an extracorporeal circulation simulation system, including any of the ventricular pulsation devices described in the invention, wherein the ventricular pulsation device is used to simulate the contraction and relaxation of the heart and drive the simulated blood fluid to flow in the circulation pipeline.

[0017] The ventricular pulsation device provided by this utility model solves the problems of lag in traditional pneumatic drive and large clearance in lead screw transmission by direct drive of voice coil motor, sinusoidal motion control and sealed cavity structure design. It realizes high-precision simulation of ventricular contraction and relaxation process, and has a compact structure and fast response. It can be widely used in the field of biomedical engineering.

[0018] Traditional ventricular simulation devices often employ pneumatic drives (such as air compressors and pneumatic cylinders) or servo motors and lead screw / synchronous belt drives. Pneumatic drives suffer from dynamic lag due to the compressibility of gas, while servo drives experience millisecond-level delays due to transmission gaps (such as lead screw backlash and elastic deformation of the synchronous belt). This invention, however, uses a voice coil motor to directly drive the piston, fundamentally solving these problems.

[0019] Specifically, the voice coil motor features a linear drive structure consisting of a permanent magnet and a coil, eliminating intermediate transmission components such as lead screws and belts. Its output shaft is rigidly connected to the piston or directly coupled via a coupling, eliminating backlash errors inherent in traditional transmission mechanisms, such as displacement deviations caused by lead screw backlash. Combined with a closed-loop control position detection element that provides real-time feedback on piston displacement, the control component adjusts the voice coil motor output, achieving sub-millimeter or even micrometer-level displacement control accuracy. This precisely reproduces the sinusoidal trajectory of ventricular contractions, significantly outperforming pneumatic drives and servo motor-driven lead screw solutions.

[0020] The magnetic force of a voice coil motor acts directly on the coil, eliminating mechanical transmission losses such as lead screw friction and belt slippage during operation. Its dynamic response time depends solely on the rate of current change, far exceeding solutions using pneumatic drives and servo motors with lead screws. This characteristic matches the high-frequency switching requirements of ventricular contractions. In normal hearts, the switching frequency between diastole and systole can reach 1-3 Hz, and even higher in pathological conditions, ensuring rapid and synchronized filling and ejection of the ventricular cavity.

[0021] Furthermore, the voice coil motor has a compact structure with no complex transmission components. Its assembly with the mounting mechanism (fixed plate, support plate, limit plate) only requires fixing the motor housing and the support plate, eliminating the need for additional adjustments to the transmission clearance or calibration of the lead screw pitch. In addition, the output shaft of the drive assembly is directly connected to the piston, simplifying the power transmission path and reducing debugging difficulty. For example, there is no need to align the coaxiality of the lead screw and piston, significantly improving the ease of operation of the device. Compared to traditional drive methods, it reduces the installation space of the drive assembly. Through the direct-drive structural design of the voice coil motor, it achieves systematic advantages in accuracy, response speed, ease of operation, and miniaturization and modularity. It can meet the needs of high-fidelity simulation of ventricular contractions in cardiovascular disease research, artificial heart testing, and other scenarios, demonstrating significant clinical and engineering application value.

[0022] The extracorporeal circulation simulation system provided by this utility model includes the aforementioned ventricular pulsation device, and therefore possesses all the advantages of the aforementioned ventricular pulsation device. Attached Figure Description

[0023] To more clearly illustrate the technical solutions in 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 some embodiments of this utility model. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0024] Figure 1 This is a schematic diagram of the ventricular pulsation device provided in an embodiment of the present invention.

[0025] Figure 2 This is an exploded view of the ventricular pulsation device provided in an embodiment of the present invention.

[0026] Figure 3 This is a top view of the ventricular pulsation device provided in this embodiment of the utility model.

[0027] Figure 4 yes Figure 3 Axonometric sectional view along line AA.

[0028] Figure 5 This is a schematic diagram of the use of the ventricular assist device provided in this embodiment of the present invention.

[0029] Figure label: 10. Pulsating base; 11. Base body; 111. Receiving cavity; 112. Mounting port; 113. Pressure relief groove; 114. Overflow groove; 12. Sleeve; 121. Pressure relief hole; 20. One-way valve; 30. Piston; 40. Drive assembly; 41. Mounting mechanism; 411. Fixing plate; 412. Support plate; 413. Limiting plate; 42. Voice coil motor; 421. Motor mounting base; 50. Star-shaped sealing ring; 60. Position detection element. Detailed Implementation

[0030] To make the objectives, technical solutions, and advantages of this utility model clearer, the technical solutions of this utility model will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this utility model, not all embodiments. Based on the embodiments of this utility model, all other embodiments obtained by those skilled in the art without creative effort are within the protection scope of this utility model.

[0031] In the description of the embodiments of this application, it should be noted that, unless otherwise explicitly specified and limited, the terms "connected" and "linked" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in the embodiments of this application based on the specific circumstances.

[0032] In the embodiments of this application, unless otherwise expressly specified and limited, "above" or "below" the second feature can mean that the first feature is in direct contact with the second feature, or that the first feature is in indirect contact with the second feature through an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0033] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of the embodiments of this application. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples. Moreover, without contradiction, those skilled in the art can combine and integrate the different embodiments or examples described in this specification, as well as the features of different embodiments or examples.

[0034] Figure 1 This is a schematic diagram of the ventricular pulsation device provided in an embodiment of the present invention. Figure 2 This is an exploded view of the ventricular pulsation device provided in an embodiment of the present invention. Figure 3 This is a top view of the ventricular pulsation device provided in this embodiment of the utility model. Figure 4 yes Figure 3 Axonometric sectional view along line AA.

[0035] See Figures 1 to 4 This invention provides a ventricular pulsation device that simulates the dynamic pulsation characteristics of the ventricle (such as the displacement-time relationship of a sine curve) to study the mechanism of ventricular dysfunction or verify the performance of artificial hearts. It can be widely applied in cardiovascular disease pathology research, artificial heart design and optimization, and medical device performance testing.

[0036] The ventricular pulsation device provided by this utility model includes a pulsation base 10, a one-way valve 20, a piston 30, and a drive assembly 40.

[0037] The pulsating base 10 serves as the supporting foundation for the entire device. Internally, it contains a ventricular cavity that holds liquid and provides space for the reciprocating motion of the piston 30. The side wall of the pulsating base 10 has a mounting port 112, which communicates with the ventricular cavity and is used to mount a one-way valve 20. The top wall of the pulsating base 10 has an opening that communicates with the ventricular cavity, allowing the piston 30 to extend into it.

[0038] It is understandable that the pulsating base 10 can be a single integral structure or composed of separate components. When the pulsating base 10 is composed of separate components, it includes a base body 11 and a sleeve 12. The base body 11 has an internal cavity 111. The sleeve 12 is located in the cavity 111 and is press-fitted to the inner wall of the cavity 111. The height of the sleeve 12 is adapted to the effective stroke of the piston 30, meaning that the sleeve 12 is only located near the top of the cavity 111 and does not completely cover the inner wall of the cavity 111, thus not obstructing the connection between the mounting port 112 and the ventricular cavity. Figure 4 As shown.

[0039] The piston 30 abuts against the inner wall of the sleeve 12, and the sleeve 12, the bottom wall of the accommodating cavity 111, and the piston 30 together enclose a relatively closed ventricular cavity. During operation, the piston 30 reciprocates within the ventricular cavity, changing its volume and causing it to change periodically, thus simulating the contraction and relaxation of the heart.

[0040] The sleeve 12 ensures that the piston 30 moves along a fixed trajectory during reciprocating motion, preventing deviation or wobbling and guaranteeing the accuracy and stability of the entire ventricular pulsation device. The inner wall of the sleeve 12 cooperates with the sealing ring of the piston 30 to provide a seal, maintaining stable pressure inside the ventricular pulsation device. Simultaneously, the sleeve 12 can be made of stainless steel or alloy, protecting the piston 30 and reducing the possibility of wear, corrosion, or other damage. Furthermore, the sleeve 12 can be replaced individually if damaged, without replacing the entire base body 11, effectively saving on operating costs.

[0041] Furthermore, the base body 11 is provided with a pressure relief groove 113 and an overflow groove 114. The pressure relief groove 113 is connected to the receiving cavity 111, and the overflow groove 114 is connected to the pressure relief groove 113. The pressure relief groove 113 is arranged along the circumferential direction of the receiving cavity 111, and the overflow groove 114 is arranged along the radial direction of the receiving cavity 111 and extends to the outside of the base body 11. This is used to balance the pressure inside and outside the ventricular pulsation device and prevent the piston 30 and sleeve 12 and other components from deforming due to pressure difference, thereby affecting the normal operation of the ventricular pulsation device.

[0042] For example, if there is too much simulated fluid in the ventricular cavity, it can flow out from the pressure relief tank 113 and the overflow tank 114 during operation, so that the internal pressure can be released and the pressure balance can be maintained.

[0043] Near the top of the sleeve 12, pressure relief holes 121 are arranged in a circumferential array. The positions of the pressure relief holes 121 correspond to the positions of the pressure relief grooves 113, and are used to balance the pressure inside and outside the sleeve 12. When the piston 30 reciprocates inside the sleeve 12, the pressure relief holes 121 can balance the pressure inside and outside the sleeve 12, preventing the piston 30 from being affected by pressure difference, ensuring smooth and stable movement, and preventing problems such as sealing failure and movement jamming caused by pressure buildup.

[0044] Essentially, the pulsating base 10 serves as the basic load-bearing structure, with a circular accommodating cavity 111 inside the pulsating base 10. A sleeve 12 is fitted inside the accommodating cavity 111, and the bottom wall of the accommodating cavity 111 of the pulsating base 10, the sleeve 12, and the piston 30 form a sealed ventricular cavity to withstand the pressure impact during liquid flow, ensuring that it does not deform or leak during long-term use.

[0045] A one-way valve 20 is located at the mounting port 112 of the pulsating base 10 and is used to simulate a valve to control the flow of liquid. Its specific type can be selected according to the requirements (such as spring-loaded one-way valve 20, diaphragm one-way valve 20), and its function is to allow liquid to flow only in a specific direction when the piston 30 reciprocates.

[0046] For example, when piston 30 moves outward, one-way valve 20 opens, and simulated liquid flows into the ventricular cavity; when piston 30 moves inward, one-way valve 20 closes, and liquid is squeezed out.

[0047] Piston 30 extends into receiving cavity 111 through an opening in the top wall of pulsating base 10. The outer surface of piston 30 abuts against the cavity wall of the ventricle, achieving reciprocating sealing through sealing materials such as silicone or rubber. For example, a star-shaped sealing ring 50 is embedded in piston 30, and the star-shaped sealing ring 50 makes frictional contact with the cavity wall of the ventricle. The lip direction of the star-shaped sealing ring 50 can simultaneously block media leakage in two directions, such as the bidirectional pressure when piston 30 moves in and out, eliminating the need for additional reverse sealing components. When the pressure in the ventricle changes periodically, the multiple sealing lips can automatically adjust the contact pressure through elastic deformation, avoiding single-point leakage. Furthermore, if there are slight machining errors between the ventricle and piston 30, the multiple sealing lips can respectively conform to the surfaces at different locations, reducing the risk of leakage.

[0048] Driven by the voice coil motor 42, the piston 30 reciprocates along the axis of the sleeve 12. The reciprocating motion of the piston 30 changes the volume of the ventricular cavity, pushing the fluid to flow and simulating the contraction (volume decrease) and relaxation (volume increase) processes of the ventricle. The stroke of the piston 30 directly determines the stroke volume.

[0049] Continue reading Figure 2 and Figure 4 The drive assembly 40 includes a mounting mechanism 41 and a voice coil motor 42. The mounting mechanism 41 is fixedly mounted on the pulsating base 10 to fix the voice coil motor 42 and provide a stable mounting space for the voice coil motor 42. The mounting mechanism 41 includes a fixing plate 411, a support plate 412, and a limiting plate 413.

[0050] The fixing plate 411 is fixedly connected to the pulsating base 10, such as by bolts. The fixing plate 411 has fixing holes and guide grooves. Support plates 412 are spaced apart and opposite to the fixing plate 411, that is, the two support plates 412 are arranged in parallel, and are used to support the limiting plate 413. The limiting plate 413 is fixedly installed at the end of the support plate 412 away from the fixing plate 411. The limiting plate 413 is parallel to the fixing plate 411. The limiting plate 413, the fixing plate 411, and the support plate 412 together enclose the installation space for accommodating the voice coil motor 42. Through the structural design of the fixing plate 411, the support plate 412, and the limiting plate 413, the coaxiality and stability of the voice coil motor 42 during operation are ensured, and vibration interference is reduced.

[0051] The motor mounting base 421 is made of a rigid metal plate and is designed with mounting holes and positioning pins that match the voice coil motor 42. The voice coil motor 42 is fixed to the motor mounting plate 411 by bolts, which can effectively prevent the vibration generated by the voice coil motor 42 during reciprocating motion from causing positional displacement and ensure the stable transmission of motor output force.

[0052] The voice coil motor 42, as the power output device, adopts a linear motion design. Its output shaft is rigidly connected to the piston 30 via a coupling or directly, directly driving the piston 30 to reciprocate along a sinusoidal curve. With the cooperation of the one-way valve 20, it achieves unidirectional periodic flow of liquid, thereby simulating the pulsating function of the ventricle. Its effective stroke is 24.9 mm, providing a stroke volume of 20~100 mL. The voice coil motor 42 features fast response speed, high thrust density, and no transmission backlash, enabling precise sinusoidal displacement output.

[0053] It should be noted that the voice coil motor 42, as the core drive source, directly drives the piston 30 through the output shaft. Its sinusoidal motion displacement output accurately reproduces the pulsation trajectory of the real ventricle; the characteristic of no transmission backlash avoids the millisecond-level delay of traditional servo motors.

[0054] Furthermore, the effective stroke of the voice coil motor 42 is positively correlated with the stroke volume of the ventricular cavity (the volume of fluid output per stroke); depending on the actual simulation requirements, the stroke volume range can be set to 20~100mL (covering the normal stroke volume range of the adult heart, and can also be extended to abnormal values ​​under pathological conditions).

[0055] The ventricular pulsation device may also include a position detection element 60 and a control component (not shown in the figure). The position detection element 60 is mounted on the mounting mechanism 41, such as fixed to the housing of the voice coil motor 42 or the piston rod 30, and is used to detect the displacement information of the piston 30 in real time. The control component is connected to the position detection element 60 and the driver of the voice coil motor 42, respectively, receives the displacement information and provides feedback to adjust the operation of the voice coil motor 42, ensuring that the piston 30 moves strictly according to a sine curve, thereby realizing closed-loop control of the voice coil motor 42.

[0056] The position detection element 60 can be an encoder, laser displacement sensor, etc. When the position detection element 60 is an encoder, the grating reading head is the core component of the encoder. It scans the lines of the grating ruler and converts the displacement into an electrical signal to achieve high-precision position measurement. The encoder is installed close to the voice coil motor 42 and can detect the displacement changes of the voice coil motor 42's mover in real time. It converts the displacement information into an electrical signal and feeds it back to the control component. It features high precision, resistance to strong magnetic interference, and stable and reliable operation, providing high-precision position feedback for the closed-loop control of the voice coil motor 42 and ensuring the accuracy of the piston 30's movement. The control component can be an industrial-grade CPU, microcontroller, or embedded controller (MCU / DSP), etc.

[0057] The working process of the ventricular pulsation device provided in this embodiment of the invention is as follows: Initialization and parameter setting: Connect the encoder's grating reading head and the driver of the voice coil motor 42 to the PC. The control component sets the motion parameters (amplitude, frequency, phase) of the voice coil motor 42 according to the simulation requirements (such as target stroke volume and beat frequency). The stroke volume can be set from 20 to 100 mL and the beat frequency from 60 to 180 bpm. The required motor stroke is calculated based on the input parameters. The initial position of the piston 30 is initialized through the position detection element 60. When the piston 30 is fully extended, the ventricular cavity volume is at its maximum, corresponding to "end-diastole".

[0058] The drive piston 30 moves in a sinusoidal curve: the control component sends a command to the driver of the voice coil motor 42, the voice coil motor 42 starts, and the drive piston 30 moves linearly and reciprocally according to the set parameters, squeezing the fluid in the ventricular cavity to achieve unidirectional flow under the action of the one-way valve 20. The grating reading head can detect the motor position in real time and feed it back to the PC to achieve precise control of the motor.

[0059] Diastole (piston 30 moves outward): When piston 30 rises along a sine curve to its maximum displacement (x=Xmax), the ventricular cavity volume increases, from the minimum volume Vmin to the maximum volume Vmax=Vmin+Xmax⋅S, where S is the cross-sectional area of ​​piston 30, and the pressure inside the cavity decreases. At this time, one-way valve 20 opens under the action of external pressure difference, and liquid (such as simulated blood) flows into the ventricular cavity from the external pipeline through the installation port 112, completing the "filling" process.

[0060] During systole (piston 30 moves inward): When piston 30 descends along a sinusoidal curve to its minimum displacement (x=0), the volume of the ventricular cavity decreases (from Vmax to Vmin), and the pressure inside the cavity increases. At this time, the one-way valve 20 closes in the reverse direction due to the pressure difference, and the fluid is squeezed out through the connection channel between the ventricular cavity and the external pipeline, completing the "ejection" process.

[0061] Closed-loop control and dynamic adjustment: The position detection element 60 detects the displacement information of the piston 30 in real time. For example, it reads the motor rotation angle through the encoder, converts it into the displacement of the piston 30, and feeds it back to the control component. The control component compares the actual displacement with the target sine curve. If there is a deviation (such as increased resistance due to changes in liquid viscosity), it adjusts the drive current of the voice coil motor 42 to correct the motion trajectory of the output shaft, ensuring that the piston 30 moves strictly according to the preset sine curve, maintaining the accuracy of ventricular cavity pressure and volume changes.

[0062] During operation, the sleeve 12 of the pulsating base 10 and the piston 30 are tightly abutted by a sealing material (such as silicone). The structural strength of the ventricular cavity is optimized (such as by using high-strength aluminum alloy or engineering plastic) and can withstand the periodic pressure impact during fluid flow (such as high pressure during systole), avoiding deformation or leakage after long-term use.

[0063] The embodiments of this utility model are described in detail below with reference to specific parameters: Example 1: Simulating the left ventricular pulsation of a normal adult Target parameters: stroke volume 60 mL, stroke rate 75 beats / minute (i.e., frequency 1.25 Hz), sinusoidal motion amplitude Xmax = 30 mm.

[0064] Working process: The voice coil motor 42 drives the piston 30 in a sinusoidal curve, with a displacement range of 0~30mm and a cycle of 0.8 seconds (corresponding to a frequency of 1.25Hz). During diastole, the piston 30 moves outward to 30mm, increasing the ventricular cavity volume from Vmin=50mL to Vmax=110mL, and the one-way valve 20 opens, allowing 60mL of fluid to flow in. During systole, the piston 30 moves inward to 0mm, reducing the volume to 50mL, and the one-way valve 20 closes, allowing 60mL of fluid to be discharged, completing one beat.

[0065] Example 2: Simulating ventricular contractions under pathological conditions (such as heart failure, with stroke volume reduced to 40 mL). Adjusting parameters: The effective stroke of the voice coil motor 42 is adjusted to 20mm (Xmax=20mm), and the cross-sectional area of ​​the piston 30 remains unchanged. Then the output per stroke V=20mm×20cm2=2cm×20cm2=40cm3=40mL.

[0066] Working process: The control component modifies the sinusoidal motion amplitude of the voice coil motor 42 to 20mm, and maintains the frequency at 1.25Hz. The rest of the process is the same as in Example 1, which can simulate the low stroke volume ventricular function under pathological conditions.

[0067] It is understood that the ventricular pulsation device provided in this embodiment of the present invention solves the problems of lag in traditional pneumatic drive and large clearance in lead screw transmission by directly driving the voice coil motor 42, controlling the sinusoidal motion and designing a sealed cavity structure. It achieves high-precision simulation of the ventricular contraction and relaxation process, and has a compact structure and fast response, and can be widely used in the field of biomedical engineering.

[0068] Traditional ventricular simulation devices often employ pneumatic drives (such as air compressors and pneumatic cylinders) or servo motors and lead screw / synchronous belt transmission schemes. Pneumatic drives suffer from dynamic lag due to the compressibility of gas, while servo drives experience millisecond-level delays due to transmission gaps (such as lead screw backlash and elastic deformation of the synchronous belt). This invention, however, uses a voice coil motor 42 to directly drive the piston 30, fundamentally solving these problems.

[0069] Specifically, the voice coil motor 42 features a linear drive mechanism consisting of a permanent magnet and a coil, eliminating intermediate transmission components such as lead screws and belts. Its output shaft is rigidly connected to the piston 30 or directly coupled via a coupling, eliminating backlash errors inherent in traditional transmission mechanisms, such as displacement deviations caused by lead screw backlash. Combined with real-time feedback of the piston 30 displacement from the closed-loop control position detection element 60, the control component adjusts the output of the voice coil motor 42, achieving sub-millimeter or even micrometer-level displacement control accuracy. This precisely reproduces the sinusoidal trajectory of ventricular beats, significantly outperforming pneumatic drives and servo motor-lead screw solutions.

[0070] The magnetic force of the voice coil motor 42 acts directly on the coil, eliminating mechanical transmission losses such as lead screw friction and belt slippage during operation. Its dynamic response time depends only on the rate of current change, far exceeding the solutions using pneumatic drives and servo motors with lead screws. This characteristic matches the high-frequency switching requirements of ventricular beats. For example, the switching frequency between diastole and systole in a normal heart can reach 1~3Hz, and even higher in pathological conditions, ensuring rapid and synchronous filling and ejection of the ventricular cavity.

[0071] Furthermore, the voice coil motor 42 has a compact structure with no complex transmission components. Its assembly with the mounting mechanism 41 (fixed plate 411, support plate 412, and limiting plate 413) only requires fixing the motor housing and the support plate 412, without the need for additional adjustment of transmission clearance or calibration of the lead screw pitch. In addition, the output shaft of the drive assembly 40 is directly connected to the piston 30, simplifying the power transmission path and reducing the difficulty of debugging. For example, there is no need to align the coaxiality of the lead screw and the piston 30, which significantly improves the ease of operation of the device. Compared with traditional drive methods, the installation space of the drive assembly 40 can be reduced.

[0072] This invention securely connects the fixing plate 411 to the pulsation base 10, arranges parallel and spaced support plates 412, and closes the end with a limiting plate 413, enclosing the voice coil motor 42 within the installation space. This structure eliminates the need for additional installation space expansion; the thickness of the voice coil motor 42 can be directly matched to the height of the installation space. For example, using a 20mm thick voice coil motor 42 requires only a 25mm installation space height, significantly reducing the axial dimension of the drive assembly 40. Through the direct-drive design of the voice coil motor 42, it achieves systematic advantages in accuracy, response speed, ease of operation, and miniaturization and modularity. It can meet the high-fidelity simulation requirements of ventricular pulsation in cardiovascular disease research, artificial heart testing, and other scenarios, demonstrating significant clinical and engineering application value.

[0073] Figure 5 This is a schematic diagram of the use of the ventricular assist device provided in this embodiment of the present invention.

[0074] See Figure 5 This invention also provides an extracorporeal circulation simulation system, which includes the ventricular pulsation device described above. The ventricular pulsation device is used to simulate the contraction and relaxation of the heart, driving the simulated blood fluid to flow in the circulation tubing.

[0075] The extracorporeal circulation simulation system provided by this invention can simulate the coordinated working process of the human cardiovascular and respiratory systems, providing a high-fidelity experimental environment for cardiovascular disease research, artificial organ (such as artificial heart, ventricular assist device) research and development testing, drug efficacy evaluation and medical education.

[0076] In the ventricular assist device (VAD) test, after setting the ventricular pulsation parameters, fluid from the ventricular cavity enters the compliant chamber under the action of the one-way valve 20, then flows through an adjustable flow resistance valve into the venous cavity, and finally returns to the ventricular cavity under the action of the one-way valve 20, forming extracorporeal circulation. The VAD is drained from the venous cavity and returned to the compliant chamber. Setting different pulsation parameters can simulate different physiological states, thereby testing the performance of the VAD under various conditions.

[0077] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this utility model, and not to limit it. Although this utility model has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this utility model.

Claims

1. A ventricular pulsation device, characterized in that, include: The pulsating base has an internal ventricular cavity. The side wall of the pulsating base has an installation port that communicates with the ventricular cavity. The top wall of the pulsating base has an opening that communicates with the ventricular cavity. A one-way valve is provided at the mounting port; The piston extends into the ventricular cavity through the opening and abuts against the cavity wall of the ventricular cavity; The driver component includes: An installation mechanism is provided on the pulsating base, and the installation mechanism is provided with an installation space; A voice coil motor is fixedly installed in the mounting space. The output shaft of the voice coil motor is connected to the piston and is used to drive the piston to perform linear reciprocating motion along the cavity wall of the ventricle.

2. The ventricular pulsation device according to claim 1, characterized in that, The effective stroke of the voice coil motor is positively correlated with the stroke volume of the ventricular cavity.

3. The ventricular pulsation device according to claim 2, characterized in that, The stroke volume ranges from 20 to 100 mL.

4. The ventricular pulsation device according to claim 1, characterized in that, The installation mechanism includes: The fixing plate is fixedly connected to the pulsating base; Support plates are spaced apart and oppositely disposed on the fixed plate; A limiting plate is fixedly disposed at one end of the support plate away from the fixing plate; The fixing plate, the support plate, and the limiting plate enclose the installation space, and the voice coil motor is mounted in the installation space via a motor mounting bracket.

5. The ventricular pulsation device according to claim 1, characterized in that, Also includes: A position detection element is disposed in the mounting mechanism and is used to detect the displacement information of the voice coil motor; A control component is connected to both the position detection element and the driver of the voice coil motor, and is used to receive displacement information from the position detection element and to control the operation of the voice coil motor.

6. The ventricular pulsation device according to claim 1, characterized in that, The piston is provided with a star-shaped sealing ring, which is in frictional contact with the cavity wall of the ventricle.

7. The ventricular pulsation device according to any one of claims 1 to 6, characterized in that, The pulsating base includes: The base body has an internal cavity. A sleeve is disposed in the receiving cavity and is interference-fitted with the inner wall of the receiving cavity. The height of the sleeve is adapted to the effective stroke of the piston. The piston abuts against the inner wall of the sleeve, and the sleeve, the bottom wall of the accommodating cavity, and the piston together enclose the relatively closed ventricular cavity.

8. The ventricular pulsation device according to claim 7, characterized in that, The base body is provided with a pressure relief groove and an overflow groove. The pressure relief groove is connected to the accommodating cavity, and the overflow groove is connected to the pressure relief groove. The pressure relief groove is arranged along the circumferential direction of the accommodating cavity, and the overflow groove is arranged along the radial direction of the accommodating cavity and extends to the outer side of the base body.

9. The ventricular pulsation device according to claim 8, characterized in that, Near the top of the sleeve, pressure relief holes are arranged in an array along the circumference, and the positions of the pressure relief holes correspond to the positions of the pressure relief grooves.

10. An extracorporeal circulation simulation system, characterized in that, The device includes the ventricular pulsation device according to any one of claims 1 to 9, the ventricular pulsation device being used to simulate the contraction and relaxation of the heart and drive the blood simulation fluid to flow in the circulation pipeline.

Images