A device for simulating hemodynamics of aortic dissection

Abstract

The present invention discloses a device for simulating the hemodynamics of aortic dissection. The device comprises a servo drive device, a ventricular simulation device, an artificial valve device, an aortic dissection model, a damping plate, a one-way valve and a liquid storage system, which are sequentially connected through a systemic circulation pipeline and fixed to a support plate with a transparent outer cover and an aortic support plate; the servo drive device, a pressure sensor, a flow meter and a high-speed camera are externally connected to a computer control system. After the servo drive device pulsates, the fluid medium flows from the liquid storage device through the ventricular simulation device and reaches the ascending aorta root of the aortic dissection model under the one-way action of the artificial valve device. The fluid medium then flows back into the liquid storage system through the damping plate and one-way valve built into the aortic arch three-branch artery circuit and the descending aorta circuit. A high-speed camera collects the hemodynamic changes during the dissection rupture and tearing process. The device achieves real-time hemodynamic simulation by changing the model type, blood pressure, fluid viscosity and posture.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a device for simulating the hemodynamics of aortic dissection. Background Art

[0002] With the advancement of society, cardiovascular diseases have attracted increasing attention. Common cardiovascular diseases such as hypertension and atherosclerosis are now widely recognized. In contrast, the incidence of aortic dissection, a more serious "invisible bomb" among cardiovascular diseases, has also been increasing year by year. Compared with other cardiovascular diseases, the incidence of aortic dissection is 1 in 100,000 to 1 in 200,000 people per year, which is lower than the incidence of cardiovascular diseases such as hypertension and atherosclerosis. This may lead to aortic dissection receiving less attention than other cardiovascular diseases.

[0003] Currently, among the research methods for aortic dissection, simulation studies of aortic dissection, which employ an engineering-based approach to medical research, have yielded substantial results for many researchers in various fields. For aortic dissection devices to ultimately be used clinically in humans, simulation conclusions must be validated through actual physical experiments. However, most research on physical experiments simulating aortic dissection has been conducted abroad, primarily focusing on simple aortic extracorporeal circulation simulation devices. For details on a vascular simulation device that has been studied domestically, please refer to application number CN201911252668.4. This simulation device excels in accurately assessing the effectiveness of extracorporeal vascular stent implantation. Further research is needed in physical model experiments of aortic dissection to assess individualized dissections, simulate blood pressure, and investigate the influence of human posture. From popularizing knowledge about aortic dissection, demonstrating the actual pathogenesis of the disease, to teaching and learning, the integration of theory and practice needs to be addressed step by step. Summary of the Invention

[0004] Based on an in-depth study of the background technology, the purpose of the present invention is to provide a device for simulating the hemodynamics of aortic dissection, which can simulate the hemodynamics of personalized aortic dissection with a physical model. While meeting the basic pulsating circulation environment and vascular compliance conditions of extracorporeal circulation, it appropriately considers the influencing factors of personalized blood viscosity and aortic dissection models, the Windeck-Salle mechanism of blood vessels, standing or supine human posture, high and low blood pressure, heart valves, dissection rupture, etc., and can more accurately simulate the actual human aortic dissection hemodynamic evolution process.

[0005] To achieve the above object, the present invention intends to adopt the following technical solutions:

[0006] The device includes a servo drive device (B), a ventricular simulation device (C), an artificial valve device (D), an aortic dissection model (F), a damping plate (K), a one-way valve (L) and a liquid storage system (E), which are connected in sequence through a systemic circulation pipeline and fixed together with a transparent outer cover (H) on a support plate (A1) in a support device (A), and a fluid medium is built into the pipeline; the aortic support plate (G) in the transparent outer cover (H) is vertically fixed on the support plate (A1), and the support plate (A1) meets the settings of standing and supine postures. The overall shape of the flexible aortic dissection model changes in diameter accordingly with the pulsation situation, and the aortic support plate fixes the aortic dissection (F) model with a single degree of freedom. The servo drive device (B), pressure sensor (J), flow meter (I) and high-speed camera (M) are externally connected to a computer control system (N), wherein the upper liquid storage chamber (E1) and the lower liquid storage chamber (E2) of the liquid storage system (E) are both cube-shaped and equipped with an open end cover (E3), a manual air valve (E4) and a liquid storage switch (E5); the upper liquid storage chamber (E1) is connected to the three-branch circulation pipeline of the aortic arch near the back side of the support plate (A1) on the lower bottom surface, and the branch passes through the support plate pipeline at a height lower than 1 / 4 of the back side of the upper liquid storage chamber to form a total return fluid circulation pipeline, which is connected around the back of the support plate. The manual air valve (E4) provided in the lower liquid storage chamber and the upper liquid storage chamber adjusts the overall compliance and internal environment pressure of the device, and is suitable for embodiments under hypertension. The lower liquid storage chamber pipeline is connected to the ventricular simulation device (C), the upper liquid storage chamber total return pipeline and the descending aorta return pipeline, and the connection height does not exceed 1 / 2 of the lower liquid storage chamber height. The total amount of liquid in the upper liquid storage chamber is less than 4 / 5 of the upper liquid storage chamber. When implementing hypertension, the manual air valve (E4) is adjusted to the overall pressure of the device to the patient's hypertension value. The settings of a series of end surfaces such as the front side, the rear side, and the lower bottom surface are selected based on the posture state.

[0007] Furthermore, the servo drive device (B) includes a servo motor (B1), a screw slide (B2) and a compression cylinder (B3); the screw slide (B2) is provided with a limit switch (B4); the limit switch (B4) is only related to the piston stroke in the compression cylinder (B3) caused by heartbeat; a flexible sealing ring (B5) is provided between the internal piston and the external cylinder body of the compression cylinder (B3); the piston and the external cylinder body are clearance-matched and the center always maintains repeated movement on the same straight line; the lubricating coating is white fluorosilicone grease.

[0008] Furthermore, the ventricular simulation device (C) is a square cavity, which can be processed into cavities of other shapes if necessary, but the function remains the same. A circular hole with an average diameter of 30 mm for male and female aortas is processed at the geometric center of the surface after the liquid inlet and outlet of the ventricular simulation device, which is nested and connected to the head pipeline of the compression cylinder (B3). After the gap is matched, the outside is sealed with a sealing ring.

[0009] Furthermore, the artificial valve device (D) is an artificial aortic valve and an artificial mitral valve; the left valve clamp (D1) and the right valve clamp (D3) and the clamp sleeve (D4) are made of transparent materials, the valve material is hard silicone and the thickness is 2mm; the artificial mitral valve is provided with two valves, the artificial aortic valve is provided with three valves and the systemic circulation pipeline is completely filled in the circular section, and the structural style of the artificial valve device is a stepped shaft with a through hole; the stepped shaft has a large diameter of 50mm and is processed with an M2 coarse thread external thread, the outer sleeve has a middle diameter of 50mm and an internal threaded sleeve, the stepped shaft has a small diameter of 35mm and is interference fit with the pipeline, and the internal through hole has a diameter of 30mm. When installing the clamp sleeve (D4), ensure that the left and right valve clamps exert a clamping force of 3-5N on the valve diaphragm (D2), screw in the clamp sleeve (D4) until the two sides of the valve diaphragm (D2) are symmetrical, and after installation, there is no gap in the internal valve diaphragm (D2). The sealing properties of the silicone gasket itself take effect after the clamps on the left and right sides are tightened, and the sleeve maintains internal stress.

[0010] Furthermore, the aortic dissection model (F) is divided into three layers with a thickness ratio of 1:5:2 for the inner, middle and outer membranes. It is made by 3D printing from a personalized patient model. The model material is soft silicone. The dissection rupture site is a single-layer intima or a double-layer intima and media according to the degree of the lesion, and the outer membrane is not ruptured. The length of Stanford type A dissection is shorter than the total length of the ascending aorta and the aortic arch, and the length of Stanford type B dissection must not exceed the total length of the descending aorta.

[0011] Furthermore, the pressure sensor (J) is installed at the inlet and descending aorta return lines of the aortic dissection model. A damping plate (K) and a one-way valve (L) are placed in the pipelines connecting the three branches of the aortic arch to the upper fluid reservoir. The damping plate (K) is made of a 2mm thick porous material. The order of damping plate first and one-way valve second in the aortic arch artery line cannot be changed to simplify the Windkessel model.

[0012] Furthermore, the transparent outer cover (H) should include the entire aortic dissection model (F). The outer cover is a cube made of a transparent acrylic plate. A leakage switch (H3) is installed at the bottom of the outer cover. The outer cover upper cover (H1) is provided with an outer cover switch (H2) at the opening and closing part and is sealed with a sealing ring. After the aortic dissection model (F) ruptures, the servo drive device (B) is immediately stopped, and the manual air valve (E4) and the liquid storage switch (E5) are opened. After the fluid medium in the liquid storage system (E) flows out, the outer cover upper cover (H1) and the outer cover switch (H2) are opened to clean the leaked liquid.

[0013] Furthermore, the support device (A) includes a support plate (A1), a walking wheel (A2), a support frame (A3), a camera support (A4) and a blood vessel support; the support plate (A1) is bolted to a fixing element, the walking wheel (A2) is provided with a locking device, and the support plate is placed horizontally when the support frame (A3) is opened.

[0014] Furthermore, the fluid medium is a glycerol-water solution, with a viscosity determined based on the individualized blood viscosity of the dissection patient. During the experiment, yellow-green fluorescent powder or fluorescent microfilaments are added to the fluid medium. Infrared measurement of fluid motion requires the presence of opaque impurity particles, which are added to simulate atherosclerotic blood.

[0015] In summary, the device for simulating hemodynamics under aortic dissection of the present invention has the following beneficial effects: changing the type of dissection model, internal pressure, fluid viscosity, personalized blood flow simulation, human body posture influence and hypertension to achieve personalized hemodynamic simulation under aortic dissection state and corresponding stent flow field verification. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] Figure 1 This is a flow chart of a device for simulating the hemodynamics of aortic dissection;

[0017] Figure 2 This is a general front view of a device for simulating the hemodynamics of aortic dissection;

[0018] Figure 3 A side view of a device for simulating the hemodynamics of aortic dissection;

[0019] Figure 4 A schematic diagram of a servo drive device for simulating the hemodynamics of aortic dissection;

[0020] Figure 5 The figure shows the cross section and exploded view of a device used to simulate the hemodynamics of aortic dissection.

[0021] Figure 6 A schematic diagram of an aortic dissection model for simulating the hemodynamics of aortic dissection;

[0022] Figure 7 A schematic diagram of a fluid storage system for a device used to simulate the hemodynamics of aortic dissection;

[0023] Figure 8 The present invention is a side view of a second embodiment of a device for simulating hemodynamics of aortic dissection.

[0024] Figure serial number:

[0025] A-Support device: A1-Support plate, A2-Travel wheel, A3-Support frame, A4-Camera bracket; B-Servo drive device: B1-Servo motor, B2-Screw slide, B3-Compression cylinder, B4-Limit switch, B5-Sealing ring; C-Ventricular simulation device; D-Artificial valve device: D1-Left valve clamp, D2-Valve diaphragm, D3-Right valve clamp, D4-Clamp sleeve; E-Liquid storage system: E1-Upper liquid storage chamber, E2-Lower liquid storage chamber, E3- Opening end cap, E4-manual air valve, E5-liquid storage switch; F-aortic dissection model; G-aortic support plate; H-transparent outer cover: H1-outer cover upper cover, H2-outer cover switch, H3-leakage switch; I1, I2, I3-flow meter; J1, J2, J3-pressure sensor; K1, K2, K3-damping plate; L1, L2, L3-check valve; M-high-speed camera; N-computer control system: N1-computer, N2-oscilloscope, N3-power supply. DETAILED DESCRIPTION

[0026] The present invention will be described in further detail below in conjunction with the accompanying drawings. To facilitate understanding of the technical content of the present invention, its technical solution will be further explained below in conjunction with the accompanying drawings. The words "front", "back", "upper", "lower" and other words indicating directions used in the description of the present invention are all statements based on the relationship between the drawings. The purpose is to facilitate description and they cannot be considered as limitations on the technical content of the present invention. Unless otherwise clearly defined, the words "connection" and other matching relationships involved should be understood in a broad sense. They can be direct matching, indirect matching, fixed connection, detachable connection, etc. People in this field can understand the implementation methods based on the purpose of the present invention.

[0027] As the process of this device Figure 1 As shown, the main body of the present invention is a systemic circulation connection device driven by a servo drive device, which is connected in sequence to form a closed loop according to the connection sequence of the human body circulation. Its installation and working sequence is from the servo drive device, ventricular simulation device, artificial valve device, aortic dissection model, damping plate, one-way valve to the upper and lower liquid storage systems to complete the simulated fluid reflux process.

[0028] As the attached Figure 2As shown, the servo drive device of the device is fixedly installed on the support plate in a bolted manner, and the working condition of the servo drive device is related to the size of the aortic dissection model rupture and the working condition of the human blood pressure. When the rupture of the aortic dissection model is large (rupture diameter ≥ 20mm) and the personalized human body circulation environment is hypertension (systolic pressure ≥ 120mmHg), the force exerted by the servo drive device on the support plate is positively correlated with the blood pressure and the size of the rupture. The larger the aortic dissection rupture, the higher the relative positive pressure exerted on the outer membrane of the blood vessel wall, which is very easy to rupture the outer membrane. The influence of the amplitude on the stability of the support plate is the main influencing factor of the hemodynamic internal flow field observation experiment. According to the above working conditions, the servo drive device for observing hemodynamics is arranged in the horizontal direction of the lower liquid storage chamber, and the overall drive system is indirectly connected to the support plate. The support plate is connected, and the device directly connected to the support plate is a ventricular simulation device. At this time, the fluid starts from the lower liquid storage chamber and is horizontally moved to the left by the return stroke of the piston through the ventricular simulation device to reach the compression cylinder. The push stroke pushes the systemic circulation pipeline upward according to the unidirectional action of the valve to complete the feeding; when the rupture is small (rupture diameter <20mm) and the blood pressure is within the normal range prescribed by medicine (80-120mmHg), the servo drive device can be installed and fixed on the support plate, and the stroke of the internal piston is in an up and down pulsating state. The upper surface of the ventricular simulation device is provided with two outlets connecting the compression cylinder and the systemic circulation pipeline, and the right side is provided with an inlet of the lower liquid storage chamber.

[0029] If the artificial valve device of this device is attached Figure 5 As shown, the artificial valve device is installed before the device works. The installation sequence is to first clamp the hard silicone diaphragm with the valve clamps on both sides, and observe that the center of the opening position of the central hole valve coincides with the geometric center of the inner hole of the valve clamp. At this time, the outer circle of the silicone diaphragm should coincide with the maximum outer circle of the clamp, and then screw in the clamp sleeve. When installing the clamp sleeve, ensure that the clamping force of the left and right valve clamps on the middle diaphragm is 3-5N, and then screw in the clamp sleeve until the two sides of the valve diaphragm are symmetrical. The artificial valve device and the clamp sleeve are transparent materials. After installation, observe that the internal valve diaphragm is not deformed and the installation is completed.

[0030] As the attached Figure 8 As shown, in the preferred embodiment 2 of this invention, during the normal blood pressure supine position simulation, it is important to note that when the device is horizontal, the support frame is open and not in contact with the support plate, and is connected to the side in a triangular structure. When the device is vertical, the support frame is closed and closely attached to the support plate. Because gravity does not promote liquid flow, fluid can be added to the upper and lower reservoirs separately.

[0031] The installation process of the device is as follows:

[0032] First, determine the simulated hemodynamic parameters, including the blood pressure range, the size of the aortic dissection model rupture, the simulated operating conditions (standing or supine), and the compliance level. After determining these parameters, lock the running wheels. When in the supine position, open the support frame and position the device horizontally. Install the servo drive unit according to the diagram above. Then connect the ventricular simulator. Install the previously assembled prosthetic valve device on the surface of the ventricular simulator and seal it. Connect the systemic circulation and install three-way valves at the sensor-mounted aortic dissection model inlet and the descending aortic return line. Connect the sensors to the transparent cover, which is fixed to the support plate based on the position of the aortic dissection model. The internally installed aortic dissection model is placed over the upper access pipe and secured with cable ties. Damping plates and check valves are placed in the systemic circulation lines connecting the three branches of the aortic arch. The damping plates are made of porous material and are 2 mm thick. The number of damping plates is calculated based on the resistance of the individual Windkosel model's aortic arch. The diameter of the damping plates should be 1-2 mm larger than the systemic circulation lines. The one-way valve placed after the damping plate is connected to the lower surface of the upper liquid storage chamber near the support plate. The upper liquid storage chamber reflux total circulation pipeline is connected to the lower liquid storage chamber through the back support plate. In the same way, a damping plate and a one-way valve are set at the outlet of the descending aorta to connect with the external sensor. The pipeline connected to the outlet of the descending aorta is connected to the lower liquid storage chamber. After the aortic dissection model is installed, the aortic support plate is fixed vertically on the support plate. During installation, there should be no interaction force between the aortic dissection model and the aortic support plate. The transparent outer cover must cover the entire aortic dissection model and the aortic support plate to prevent the outer membrane of the dissection from rupturing during the experiment, resulting in uncontrolled fluid. The sensor, flow meter and servo drive device are connected to the computer control system.

[0033] The device operates as follows:

[0034] This embodiment 1 is a preferred simulation of standing posture under normal blood pressure, as shown in the attached figure. Figure 2 、 3 As shown in the figure, the device is first adjusted to the experimental position and the running wheels are secured. The air valve and upper cover of the upper reservoir are opened, and fluid is added to the upper reservoir. The fluid flows through the support plate return line into the lower reservoir. When the fluid level exceeds the lower reservoir, the computer is turned on to control the servo drive to pulse. The servo drive, ventricular simulator, and lower reservoir are depleted of air, and the device stops operating. Liquid is then added through the aortic arch to the descending aorta. A one-way valve prevents backflow from the descending aorta, limiting the flow of fluid to the descending aorta. Once the descending aorta is filled with fluid, the aortic arch gradually fills. Liquid addition is stopped when the fluid passes through the aortic arch one-way valve and reaches the upper reservoir. At this point, the compliance value is derived from the personalized data, and the air and liquid heights in the upper reservoir are calculated. The liquid level is adjusted appropriately to meet the compliance value, and the upper reservoir cover and manual air valve are closed.

[0035] Turn on the computer to monitor the pressure sensor. Operate the manual air valve to add gas to the device to increase the pressure in the systemic circulation line to 80 Hg, then stop adding gas. Control the servo drive to pulse. Turn on the high-speed camera to record the flow field changes at the interlayer. If the image is unclear, stop the device. Add fluorescent powder or fluorescent microfilaments to the liquid, re-pressurize the experiment, and record its movement within the fluid.

[0036] The following operating procedures were used to terminate the experiment: the computer stopped the drive system, and the manual air valve was opened to release pressure from the internal circulation system. After the pressure was released, the upper reservoir cover was opened, and the lower reservoir bottom switch was opened to recover the liquid. After the upper and lower reservoirs were completely drained, the entire device was placed horizontally. Due to the unidirectional effect of the artificial valve device, the liquid in the aortic dissection needs to be released horizontally. The transparent outer cover was opened, the dissection was removed and stored, and the reservoir cover, manual air valve, reservoir switch, and computer were closed. The leak was then cleaned up.

[0037] It should be emphasized that when conducting experimental analysis on a personalized model under hypertension, in addition to using the manual valve to control the internal pressure of the systemic circulation to ≥120 mmHg, it is also necessary to control the total amount of liquid in the upper liquid storage chamber to be lower than 4 / 5 of the upper liquid storage chamber to prevent excessive liquid from spraying out of the manual valve when the manual valve is opened to release the pressure.

[0038] During the experiment, once the outer membrane of the aortic dissection ruptures, causing liquid to spray out of the aortic dissection model, the experiment should be stopped immediately. In addition to the above-mentioned operating procedures for stopping the experiment, due to the rupture of the outer membrane, the fluid sprays into the transparent outer cover. During the process of recovering the liquid, open the leakage switch at the bottom of the transparent outer cover for recovery. After the liquid in the lower liquid storage chamber is drained, open the transparent outer cover, take out the aortic dissection model for storage, and turn off the switch to wipe the leakage to end.

[0039] The computer control system is LabVIEW 8.2 version, the data acquisition system controlled by NI-DAQmx, and the high-speed camera is a binocular high-definition CCD camera.

[0040] This device can also simulate hemodynamics after stent implantation. The functions and auxiliary systems of the device should not be interpreted as limiting the scope of the invention patent. Obviously, the embodiments described are only part of the embodiments of the present invention, not all of them. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

Claims

1. A device for simulating the hemodynamics of aortic dissection, characterized by: The device includes a servo drive device (B), a ventricular simulation device (C), an artificial valve device (D), an aortic dissection model (F), a damping plate (K), a one-way valve (L) and a liquid storage system (E). The above parts are connected in sequence through a systemic circulation pipeline and fixed together with a transparent outer cover (H) on a support plate (A1) in a support device (A), with a built-in fluid medium; the aortic support plate (G) in the transparent outer cover (H) is vertically fixed on the support plate (A1); the servo drive device (B), a pressure sensor (J), a flow meter (I) and a high-speed camera (M) are externally connected to a computer control system (N), wherein the upper liquid storage chamber (E1) and the lower liquid storage chamber (E2) of the liquid storage system (E) are both cubes, with It is provided with an open end cover (E3), a manual air valve (E4) and a liquid storage switch (E5); the upper liquid storage chamber (E1) is connected to the three branches of the aortic arch circulation pipeline near the back of the support plate (A1) on the lower bottom surface; the pipeline on the back side of the upper liquid storage chamber below 1 / 4 of the height passes through the support plate to form a total return fluid circulation pipeline, which goes around the back of the support plate (A1) and connects to the lower liquid storage chamber (E2); the lower liquid storage chamber pipeline is connected to the ventricular simulation device (C), the total return pipeline of the upper liquid storage chamber (E1) and the descending aorta return pipeline, and the connection height does not exceed 1 / 2 of the height of the lower liquid storage chamber, and the total amount of liquid in the upper liquid storage chamber (E1) is lower than 4 / 5 of the height of the upper liquid storage chamber; when implementing hypertension, the manual air valve (E4) is adjusted until the overall pressure of the device is the patient's hypertension value.

2. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The servo drive device (B) includes a servo motor (B1), a screw slide (B2) and a compression cylinder (B3). The screw slide (B2) is provided with a limit switch (B4). A flexible sealing ring (B5) is provided between the internal piston and the external cylinder body of the compression cylinder (B3).

3. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The ventricular simulation device (C) is a square cavity. A circular hole with a diameter of 30 mm is provided at the geometric center of the surface where the liquid is inlet and outlet of the ventricular simulation device (C). It is nested and connected to the head pipe of the compression cylinder (B3) and sealed with a sealing ring.

4. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The artificial valve device (D) is an artificial aortic valve device and an artificial mitral valve device; the left valve clamp (D1), the right valve clamp (D3) and the clamp sleeve (D4) are made of transparent materials, the valve material is hard silicone and has a thickness of 2mm, the artificial mitral valve is provided with two valves, the artificial aortic valve is provided with three valves and the systemic circulation pipeline is completely filled in the circular section, the artificial valve device structure is a stepped shaft with a through hole, the stepped shaft has a large diameter of 50mm and an M2 coarse thread external thread on the outer surface, the outer middle diameter of the stepped shaft is 50mm and the internal thread clamp sleeve (D4) is 50mm, the stepped shaft has a small diameter of 35mm and is interference fit with the systemic circulation pipeline, and the inner diameter of the clamp through hole is 30mm; when installing the clamp sleeve (D4), ensure that the pressing force of the valve clamps on the valve diaphragm (D2) on the left and right sides is 3-5N, screw the clamp sleeve (D4) until the two sides of the valve diaphragm (D2) are symmetrical, and after installation, there is no gap in the internal valve diaphragm (D2).

5. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The aortic dissection model (F) is divided into three layers, with a thickness ratio of intima, media, and adventitia of 1:5:

2. It is 3D printed according to personalized patient vascular data. The model material is soft silicone. The dissection rupture site is a single-layer intima or a double-layer intima and media according to the degree of lesion, and the adventitia is not ruptured. The length of Stanford A type dissection is shorter than the total length of the ascending aorta and aortic arch, and the length of Stanford B type dissection must not exceed the total length of the descending aorta.

6. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The pressure sensor (J) is installed at the inlet pipeline of the aortic dissection model and the descending aorta return pipeline. A damping plate (K) is first installed in the pipeline connecting the three branches of the aortic arch and the upper liquid storage cavity, and then a one-way valve (L) is connected. The damping plate (K) is a porous material with a thickness of 2 mm.

7. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The transparent outer cover (H) includes the entire aortic dissection model (F), and the outer cover is processed as a whole by a transparent acrylic plate. A leakage switch (H3) is installed at the bottom of the outer cover, and an outer cover switch (H2) is provided at the opening and closing position of the outer cover upper cover (H1) and is sealed with a sealing ring; after the aortic dissection model (F) ruptures, the servo drive device (B) is immediately stopped, and the manual air valve (E4) and the liquid storage switch (E5) are opened. After the fluid medium in the liquid storage system (E) flows out, the outer cover upper cover (H1) and the outer cover switch (H2) are opened to clean the leaked liquid.

8. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The support device (A) comprises a support plate (A1), a running wheel (A2), a support frame (A3), a camera support (A4) and a blood vessel support; the support plate (A1) is bolted to a fixing element, the running wheel (A2) is provided with a locking device, and the support plate is placed horizontally when the support frame (A3) is opened.

9. The device for simulating hemodynamics of aortic dissection according to claim 1, characterized in that: The fluid medium is a glycerol aqueous solution, and the viscosity of the solution is determined according to the personalized blood viscosity of the dissection patient. Yellow-green fluorescent powder or fluorescent microwires are added to the fluid medium during the experiment. Infrared measurement of fluid movement requires opaque impurity particles, and particulate matter is added to simulate atherosclerotic blood.

Images