Extracorporeal life support simulation model and training system

Abstract

This application provides an in vitro life support simulation model and training system, relating to the field of medical technology. The simulation model includes a human body model containing simulated arteries, simulated veins, an arterial blood pump, and a venous blood pump. The internal channels of the simulated arteries are used to contain a first chromogenic material, and the internal channels of the simulated veins are used to contain a second chromogenic material. The arterial blood pump is configured to pump the first chromogenic material within the simulated artery, and the venous blood pump is configured to pump the second chromogenic material within the simulated vein. Both the arterial and venous blood pumps are centrifugal pumps. The simulated arteries and veins—the carotid artery, radial artery, femoral artery, jugular vein, radial vein, and femoral vein—are all detachably equipped with puncture units. Each puncture unit comprises, from the inside out, a rigid support layer, an impermeable layer, and an elastic rubber layer. It can simulate the flow of arterial and venous blood in the human body and can be used for puncture and catheter placement training.

Description

Technical Field

[0001] This application relates to the field of medical technology, and more specifically, to an in vitro life support simulation model and training system. Background Technology

[0002] Continuous renal replacement therapy (CRRT) is a blood purification therapy technique that continuously and slowly removes water and various solutes from the kidneys to replace damaged kidney function. CRRT can be performed for 8-12 hours daily, or even 24 hours or longer, depending on the patient's condition. CRRT plays a crucial role in the treatment of critically ill patients. Due to the long treatment time, successful and well-positioned CRRT catheter placement is a prerequisite for CRRT. Healthcare professionals need to be familiar with procedures such as internal jugular and femoral vein catheterization, obtaining blood gas analysis results via the radial artery during treatment to guide treatment adjustments, and understanding CRRT treatment protocols and modalities. Proficiency is crucial for the successful long-term implementation of CRRT. Therefore, providing relevant professional knowledge training to CRRT medical staff is of paramount importance.

[0003] Because healthcare professionals new to CRRT often lack direct understanding and opportunities to practice CRRT catheterization, arterial blood gas sampling, and the CRRT treatment process, their theoretical knowledge often becomes detached from practical application. This leads to common clinical problems such as serious complications due to improper catheterization, catheter failure, inadequate flow due to poor catheter placement, frequent alarms from the treatment device, and difficulties in arterial blood gas sampling. Furthermore, unfamiliarity with tubing connections in different CRRT treatment modes, and a lack of understanding of common alarm causes (such as abnormal arterial / venous pressure, transmembrane pressure exceeding the upper limit, filter or venous reservoir clotting, air alarms, and blood leakage alarms) and their handling protocols hinders the successful implementation of CRRT. Currently, however, there is a lack of in vitro teaching models that realistically simulate clinical catheterization procedures. Utility Model Content

[0004] This application provides an extracorporeal life support simulation model and training system. The extracorporeal life support simulation model can simulate the flow of blood in the arteries and veins of the human body and can be used for teaching and training such as puncture and catheterization and arterial blood gas collection.

[0005] This application is implemented as follows: In a first aspect, this application provides an in vitro life support simulation model, comprising a human body model, wherein the human body model is provided with simulated arteries, simulated veins, an arterial blood pump, and a venous blood pump. The internal channel of the simulated artery is used to contain a first chromogenic material, the internal channel of the simulated vein is used to contain a second chromogenic material, the arterial blood pump is used to pump the first chromogenic material to flow within the simulated artery, and the venous blood pump is used to pump the second chromogenic material to flow within the simulated vein; wherein, both the arterial blood pump and the venous blood pump are centrifugal pumps, the arterial blood pump includes backward-curved blades with an impeller diameter of 50-80 mm, and the output pipeline of the arterial blood pump is provided with an overflow valve and a first throttling valve; the venous blood pump is a centrifugal pump, including forward-curved blades with an impeller diameter of 30-50 mm, and the output pipeline of the venous blood pump is provided with a second throttling valve; The simulated arteries include the radial artery, carotid artery, thoracic aorta, abdominal aorta, and femoral artery, which are interconnected. The simulated veins include the radial vein, jugular vein, superior vena cava, inferior vena cava, and femoral vein, which are interconnected. The carotid artery, radial artery, femoral artery, jugular vein, radial vein, and femoral vein are all detachably equipped with puncture units. The puncture units are configured to be repeatedly punctured. The puncture units include, from the inside out, a rigid support layer, a waterproof layer, and an elastic rubber layer.

[0006] In one possible implementation, the puncture unit is detachably and sealed to the carotid artery, the radial artery, the femoral artery, the jugular vein, the radial vein, and the femoral vein via a Luer connector or a photosensitive resin connector.

[0007] In one possible implementation, the connecting end of the Luer connector or the photosensitive resin connector is provided with an annular groove, and a sealing ring is installed in the annular groove. The depth of the groove is 60% to 70% of the height of the sealing ring. The inner surface of the connecting port of the carotid artery, the radial artery, the femoral artery, the jugular vein, the radial vein, and the femoral vein is provided with a smooth sealing surface that mates with the sealing ring, and a sealed connection is achieved through the sealing ring.

[0008] In one possible implementation, the molecular particle size of the second colorimetric material is >10nm, and it cannot pass through the semipermeable membrane.

[0009] In one possible implementation, the arterial blood pump has a first blood reservoir containing a first colorimetric material, and the first blood reservoir is in communication with the simulated artery.

[0010] In one possible implementation, the venous blood pump has a second blood storage chamber containing a second colorimetric material, and the second blood storage chamber is in communication with the simulated vein.

[0011] In one possible implementation, the simulated artery and the simulated vein are located on the left and right sides of the human body model.

[0012] Secondly, this application provides an extracorporeal life support simulation training system, including a monitoring and control device and an extracorporeal life support simulation model as described in the first aspect. The monitoring and control device includes a display and a microprocessor control device. The microprocessor control device is electrically connected to the arterial blood pump and the venous blood pump via a pressure sensor. The centrifugal pumps of the arterial blood pump and the venous blood pump are driven by variable frequency speed-regulating motors. The microprocessor control device is used to adjust the speed of the variable frequency speed-regulating motors of the arterial blood pump and the venous blood pump, and to adjust the opening degree of the overflow valve, the first throttle valve, and the second throttle valve, so as to adjust the simulated blood pressure of the simulation model. The display is capable of displaying the simulated blood pressure.

[0013] This application has at least the following beneficial effects: This application discloses an extracorporeal life support simulation model and training system, featuring simulated arteries and veins. An arterial blood pump allows a first chromogenic material to flow within the simulated artery, while a venous blood pump allows a second chromogenic material to flow within the simulated vein. These arterial and venous blood pumps simulate the heart's pumping action and the flow of blood within the human body. Furthermore, the carotid, radial, femoral, jugular, radial, and femoral veins are all detachably equipped with puncture units. Each puncture unit comprises a rigid support layer, a leak-proof layer, and an elastic rubber layer, ensuring that repeated punctures will not result in leakage. These units can also be removed and replaced later. The extracorporeal life support simulation model can be used for training and teaching medical personnel on simulated catheter placement and arterial blood gas collection. A microprocessor control device can adjust the simulated blood pressure of the model and display the results on a monitor, providing visualization and a more realistic simulation of human conditions, thus accumulating more experience for subsequent clinical operations. Attached Figure Description

[0014] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of this application and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0015] Figure 1 This is an in vitro life support simulation model for an embodiment of this application.

[0016] Icons: 10 - Extracorporeal life support simulation model; 11 - Simulated artery; 111 - Carotid artery; 112 - Radial artery; 113 - Femoral artery; 12 - Simulated vein; 121 - Jugular vein; 122 - Radial vein; 123 - Femoral vein; 13 - Arterial blood pump; 14 - Venous blood pump; 15 - Puncture unit. Detailed Implementation

[0017] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. The components of the embodiments of this application described and shown in the accompanying drawings can generally be arranged and designed in various different configurations.

[0018] Therefore, the following detailed description of the embodiments of this application provided in the accompanying drawings is not intended to limit the scope of the claimed application, but merely to illustrate selected embodiments of the application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without inventive effort are within the scope of protection of this application.

[0019] In the description of this application, it should be noted that the terms "first," "second," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0020] In the description of this application, it should also be noted that, unless otherwise expressly specified and limited, the terms "setup" and "connection" 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 direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances. Example

[0021] Please refer to Figure 1 This embodiment provides an extracorporeal life support simulation model 10, which includes a human body model, and the human body model is equipped with a simulated artery 11, a simulated vein 12, an arterial blood pump 13 and a venous blood pump 14.

[0022] The number of puncture sites available for dialysis in the human body is limited, generally including the legs, neck, and arms, where arteries and veins are adjacent. Veins are difficult to see clearly through the skin and require blind puncture. Typically, after locating the artery by feeling the pulse, the vein is located a certain distance to the left and right, allowing for puncture. In this embodiment, the skin of the mannequin is designed to resemble real human skin and is not transparent. Alternatively, the skin corresponding to the puncture unit could be opaque, while the rest is transparent. The location of arteries and veins on the left or right side of the legs, neck, and arms is consistent with real human conditions, allowing for practice of blind puncture. The operator locates the artery by touch and then finds the vein by shifting a certain distance to the left or right, enabling venous puncture.

[0023] The internal channels of the simulated artery 11 are used to contain a first chromogenic material, and the internal channels of the simulated vein 12 are used to contain a second chromogenic material. An arterial blood pump 13 is configured to pump the first chromogenic material into the simulated artery 11, and a venous blood pump 14 is configured to pump the second chromogenic material into the simulated vein 12. The arterial blood pump 13 and the venous blood pump 14 can simulate the pumping action of the heart, eliminating the need for a physical heart structure to simulate the human heart. The first chromogenic material may not circulate within the simulated artery 11, and the second chromogenic material may not circulate within the simulated vein 12. The simulated artery 11 and the simulated vein 12 have varying thicknesses to simulate the size of human arteries and veins; exemplarily, the simulated artery 11 and the simulated vein 12 are located on the left and right sides of the human model.

[0024] Furthermore, the different colors of the first and second color-developing materials facilitate the differentiation between simulated arterial and venous blood. For example, the first color-developing material is bright red, and the second color-developing material is dark red. Moreover, the second color-developing material is rapidly soluble and does not clump, has a molecular particle size >10nm, and cannot permeate a semi-permeable membrane.

[0025] Furthermore, in this embodiment, both the first and second colorimetric materials are obtained by compounding a colorimetric concentrate with different volumes of deionized water, and the specific ratio can be adjusted as needed. The colorimetric concentrate is prepared by uniformly mixing nano-iron oxide particles (20-200 mg / g; particle size 10-100 nm), sodium polycarboxylate dispersant (0.1-2 wt%), magnesium aluminum silicate suspending agent (0.2-5 wt%), and deionized water. The above-mentioned colorimetric concentrate can meet the requirements of simulating blood circulation in the dialyzer tubing. The colored nano-iron oxide particles cannot penetrate the hollow fiber membrane of the dialysis equipment, will not contaminate the PVC dialysis tubing, and have good stability (shelf life greater than or equal to 1 year).

[0026] The simulated arteries 11 include interconnected carotid artery 111, radial artery 112, thoracic aorta, abdominal aorta, and femoral artery 113. The simulated veins 12 include interconnected jugular vein 121, radial vein 122, superior vena cava, inferior vena cava, and femoral vein 123. Each of the carotid artery 111, radial artery 112, femoral artery 113, jugular vein 121, radial vein 122, and femoral vein 123 is detachably equipped with a puncture unit 15. The puncture unit 15 comprises, from the inside out, a rigid support layer, an impermeable layer, and an elastic rubber layer. The puncture unit 15 will not leak even after repeated punctures and can be disassembled and replaced later. This extracorporeal life support simulation model can be used for training and teaching medical personnel in simulated catheter placement and collection.

[0027] For example, the outer layer of the puncture unit 15 is made of medical-grade high-elasticity silicone rubber with a Shore A hardness of 25-30 degrees and an elongation at break of ≥500%; the middle layer (impermeable layer) is made of modified (e.g., introducing disulfide bonds / Diessel-Alder reaction pairs) medical polyurethane (with 3-10% nano-bentonite filler added) with a Shore A hardness of 40-45 degrees and a tensile strength of ≥18 MPa. The nano-bentonite filler (particle size 50-100 nm) in the modified polyurethane can be uniformly dispersed in the polyurethane matrix. After puncture, the tiny pores (diameter 0.3-0.5 mm) left by the needle tip will be quickly closed by the "elastic recovery polyurethane + nanoparticle filling"; the inner layer (support layer) is made of medical-grade rigid PVC (model: PVC-U medical grade) or nylon 66 with a Shore D hardness of 65-70 degrees and a flexural strength of ≥80 MPa. The rigid support layer, the impermeable layer, and the elastic rubber layer are bonded together using medical-grade EVA hot melt adhesive / polyurethane adhesive / epoxy adhesive. Before bonding, the contact surfaces of each layer are subjected to plasma treatment (treatment time 30s, power 50W) to ensure that the interlayer peel strength is ≥5N / cm, thus preventing interlayer separation after multiple punctures.

[0028] Furthermore, the puncture unit 15 is detachably and sealed to the carotid artery 111, radial artery 112, femoral artery 113, jugular vein 121, radial vein 122, and femoral vein 123 via Luer connectors or photosensitive resin connectors. The connection between the connector and other components is sealed using sealing rings to prevent liquid leakage. The connecting end of the connector has an annular groove that closely matches the outer diameter of the sealing ring. The sealing ring is installed within the annular groove, with a groove depth of 60% to 70% of the sealing ring's height to ensure appropriate compression after installation. Simultaneously, a smooth sealing surface is machined on the inner surface of the connection ports of the simulated artery 11 and simulated vein 12 to mate with the sealing rings of the first and second Luer connectors. The roughness of the sealing surface is controlled within Ra0.8 to Ra1.6 μm to reduce the impact of microscopic irregularities on the sealing effect. When the first Luer connector and the second Luer connector are screwed into the simulated artery 11 and simulated vein 12 interfaces respectively, the sealing ring is squeezed and deformed, its outer surface tightly fits the side wall of the groove, and its inner surface fully contacts the sealing surface of the simulated artery and vein, filling the tiny gaps and achieving a reliable seal.

[0029] To further enhance the sealing effect, a thin layer of medical-grade lubricating silicone grease can be applied to the surface of the sealing ring. This not only reduces friction during installation and prevents damage to the sealing ring, but also fills any tiny gaps that may exist between the sealing ring and the sealing surface, enhancing the reliability of the seal. Additionally, adding an appropriate amount of reinforcing agent, such as fumed silica, to the sealing ring's material formulation can improve its mechanical strength and resistance to compression set, ensuring it maintains good sealing performance even under long-term use and frequent pressure changes.

[0030] The carotid artery 111, radial artery 112, and femoral artery 113 can pulsate synchronously via arterial blood pump 13, while the jugular vein 121, radial vein 122, and femoral vein 123 can pulsate synchronously via venous blood pump 14. The pulsation intensity of the simulated artery 11 is greater and the pressure is higher than that of the simulated vein 12; for example, the pressure of the simulated artery 11 pulsation is 80-100 mmHg, and the pressure of the simulated vein 12 pulsation is 3-15 mmHg. To meet the high-pressure output requirements of arterial blood, arterial blood pump 13 is a centrifugal pump with an impeller diameter of 50-80 mm and typically 6-8 blades. The blades are designed with a backward-curved shape, which allows the impeller to efficiently convert mechanical energy into liquid kinetic and pressure energy during high-speed rotation, reducing energy loss. At a rotation speed of 800-1000 rpm, a pressure output of 80-100 mmHg can be achieved, effectively simulating human arterial blood pressure. The blade surface is polished to reduce the roughness to Ra0.2 - Ra0.4μm, thereby reducing frictional resistance during blood flow and minimizing the risk of hemolysis.

[0031] The arterial blood pump 13 features a tapered pump chamber design, with the cross-sectional area gradually decreasing from the inlet to the outlet. This design allows the blood flow velocity to gradually increase within the pump chamber. According to Bernoulli's principle, increased flow velocity leads to increased pressure, thereby assisting the impeller in increasing pressure output. The inner wall of the pump chamber is made of a biocompatible material, such as polyetheretherketone (PEEK), and undergoes an ultra-smooth treatment with a surface roughness of Ra0.1 - Ra0.2 μm, reducing blood stagnation and the risk of thrombosis within the pump chamber.

[0032] The venous blood pump 14 has relatively low pressure output requirements. It also uses a centrifugal pump with an impeller diameter of 30-50 mm and 4-6 blades. To accommodate the high flow rate and low pressure of venous blood, the blades can be designed with a forward-inclined shape, which provides a larger flow rate at lower speeds. At a speed of 400-800 rpm, it can generate a pressure of 3-15 mmHg, meeting the pressure requirements for venous blood return while ensuring smooth blood flow in the tubing.

[0033] The venous blood pump 14 employs a relatively large and gently sloping pump chamber design to reduce blood flow resistance within the chamber. The minimal change in the pump chamber's cross-sectional area ensures smooth blood flow, preventing damage caused by sudden pressure changes. The pump chamber material is also biocompatible, such as silicone rubber, whose softness allows it to adapt to dynamic changes in blood flow, reducing mechanical irritation to the blood.

[0034] The arterial blood pump 13 and venous blood pump 14 utilize variable frequency speed-regulating motors as their drive devices. These motors can precisely adjust their speed by changing the power supply frequency, offering advantages such as fast response, wide speed range, and high control precision. Based on these variable frequency speed-regulating motors, the arterial blood pump 13 and venous blood pump 14 can achieve stepless speed regulation within the range of 50 to 1500 rpm, meeting the different speed requirements of the arterial and venous blood pumps. The motors are connected to the pump impellers via high-precision couplings, ensuring stability and concentricity during power transmission and reducing the impact of vibration and noise on the blood.

[0035] Furthermore, the arterial blood pump 13 has a first blood reservoir (not shown in the figure), which stores a first chromogenic material and is connected to the simulated artery 11. The venous blood pump 14 has a second blood reservoir (not shown in the figure), which stores a second chromogenic material and is connected to the simulated vein 12. The stored first chromogenic material and the first chromogenic material flowing in the simulated artery 11 can be freely interchanged, and the stored second chromogenic material and the second chromogenic material flowing in the simulated artery 11 can also be freely interchanged. For example, the first chromogenic material stored in the first blood reservoir is 1000-1500 ml, and the second chromogenic material stored in the second blood reservoir is 1000-1500 ml.

[0036] This embodiment also provides an extracorporeal life support simulation training system, including a monitoring and control device and an extracorporeal life support simulation model 10. The monitoring and control device includes a display and a microprocessor control device. The microprocessor control device is electrically connected to the arterial blood pump 13 and the venous blood pump 14 through a pressure sensor. The microprocessor control device is used to adjust the speed of the variable frequency speed control motors of the arterial blood pump 13 and the venous blood pump 14, and to adjust the opening of the overflow valve, the first throttle valve, and the second throttle valve to adjust the simulated blood pressure of the simulation model. The display can display the simulated blood pressure.

[0037] The microprocessor control unit receives real-time pressure signals from pressure sensors, compares and analyzes them with preset pressure values, and then automatically adjusts the power frequency of the variable frequency drive motor according to the control algorithm, thereby achieving precise control of the blood pump speed. When the pressure sensor of arterial blood pump 13 detects that the output pressure is lower than the preset value (e.g., 60 mmHg), the microprocessor control unit automatically increases the power frequency of the motor, increasing the blood pump speed and thus increasing the output pressure. When the pressure reaches the preset value, the microprocessor control unit adjusts the motor frequency to maintain the blood pump at a stable speed and pressure output state. For venous blood pump 14, the microprocessor control unit similarly controls the speed of venous blood pump 14 within an appropriate range based on the signal fed back from the pressure sensor of venous blood pump 14, in order to maintain stable venous pressure.

[0038] To ensure the accuracy and stability of motor speed regulation, a PID (Proportional-Integral-Derivative) control algorithm is employed in the microprocessor control device. The PID control algorithm dynamically adjusts the motor control parameters based on pressure deviation, rate of change of deviation, and the integral term, enabling the blood pump speed to quickly and accurately track the preset pressure value. Through these methods, the speed regulation accuracy of the blood pump can reach ±1 rpm, and the pressure control accuracy can reach ±5 mmHg in the arterial blood pump 13 and ±2 mmHg in the venous blood pump 14, meeting the stringent requirements for pressure stability in clinical use and simulation experiments.

[0039] In addition, an overflow valve is installed in the output line of the arterial blood pump 13 as the main pressure regulating valve. The overflow valve has a set opening pressure threshold. When the pressure of the arterial blood pump 13 suddenly increases due to a malfunction (such as abnormal motor speed) or operational error (such as accidental blockage at the end of the line), the overflow valve automatically opens to prevent the module connection from bursting due to overpressure and causing leakage. The rated pressure of the overflow valve needs to be selected based on the maximum output pressure of the arterial blood pump 13, generally slightly higher than the highest pressure that the arterial blood pump 13 may generate, such as selecting an overflow valve with a rated pressure of 120~140 mmHg. When the output pressure of the arterial blood pump 13 exceeds the set value (such as 120 mmHg), the overflow valve opens, returning some blood to the inlet of the arterial blood pump 13 or the first blood storage chamber, thereby reducing the pressure in the output line and ensuring that the arterial pressure is maintained within a safe and stable range. Meanwhile, a first throttle valve can be connected in series in the output line of the arterial blood pump 13 for fine-tuning the pressure. The first throttle valve changes the line resistance by adjusting the valve opening, thereby achieving fine adjustment of the output pressure of the arterial blood pump 13.

[0040] The output line of the venous blood pump 14 is also equipped with a second throttle valve as the primary means of pressure regulation. Because venous pressure is relatively low, the rated pressure of the second throttle valve is relatively low, typically 20-30 mmHg. By adjusting the opening of the second throttle valve, the flow rate and pressure of blood in the line are controlled, stabilizing the output pressure of the venous blood pump 14 within a suitable range, such as 5-15 mmHg. In some special circumstances, such as when it is necessary to prevent excessively high venous pressure from adversely affecting the patient, a safety valve can be connected in parallel. When the venous pressure exceeds the set safety upper limit (e.g., 20 mmHg), the safety valve automatically opens, diverting some blood to the low-pressure circuit to ensure the safety of the venous blood circuit.

[0041] Furthermore, the overflow valve and the second throttle valve are installed near the output end of the blood pump to ensure timely adjustment of the blood pump output pressure. Valve control can be achieved through both manual and automatic adjustment. Manual adjustment is suitable for equipment debugging and some simple experimental scenarios; the operator can directly adjust the valve opening based on the simulated blood pressure displayed on the monitor. Automatic control transmits real-time pressure signals from pressure sensors to a microprocessor control device, which automatically controls the valve opening based on preset pressure values. In the extracorporeal life support simulation model 10, the microprocessor control device automatically adjusts the openings of the overflow valve, the first throttle valve, the second throttle valve, and the safety valve based on signals from the pressure sensors of the arterial blood pump 13 and the venous blood pump 14, ensuring that the pressures of the simulated artery 11 and the simulated vein 12 are always maintained within the range simulating human physiological conditions.

[0042] The microprocessor control unit increases the pressure in the simulated artery 11 and simulated vein 12 by reducing the opening of the first and second throttle valves (increasing pipeline resistance). During arterial puncture (such as femoral artery puncture), the catheter may temporarily block the lumen after entry, causing a sudden increase in local pressure. In this case, the overflow valve responds quickly, releasing pressure to a safe range. If the fluid volume in the human model is insufficient or the pump parameters are set too low, the first and second throttle valves can be adjusted to a higher, relatively low pressure, to avoid pressure fluctuations affecting the "arterial blood gas collection simulation" (e.g., excessively low pressure leading to unsuccessful "blood gas sample" collection).

[0043] In summary, the extracorporeal life support simulation model 10 and training system of this application have simulated arteries 11 and simulated veins 12. An arterial blood pump 13 allows the first chromogenic material to flow within the simulated artery 11, and a venous blood pump 14 allows the second chromogenic material to flow within the simulated vein 12. The arterial and venous blood pumps 13 and 14 can simulate the pumping action of the heart and the flow of blood within the human body. Furthermore, the carotid artery 111, radial artery 112, femoral artery 113, jugular vein 121, radial vein 122, and femoral vein 123 are all detachably equipped with puncture units 15. Each puncture unit 15 comprises a rigid support layer, a waterproof layer, and an elastic rubber layer from the inside out. The puncture unit 15 will not leak even after repeated punctures and can be disassembled and replaced later. The extracorporeal life support simulation model 10 can be used for training and teaching medical staff on simulated catheter placement, arterial blood gas collection, etc. The microprocessor control device can adjust the simulated blood pressure of the simulation model and display it on the monitor to achieve visualization, making the simulation closer to the real human body condition, and accumulating more experience for subsequent clinical operations.

[0044] The above are merely preferred embodiments of this application and are not intended to limit this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. An in vitro life support simulation model, characterized in that, It includes a human body model, which contains simulated arteries, simulated veins, an arterial blood pump, and a venous blood pump. The internal channels of the simulated arteries are used to contain a first chromogenic material, and the internal channels of the simulated veins are used to contain a second chromogenic material. The arterial blood pump is used to pump the first chromogenic material to flow within the simulated artery, and the venous blood pump is used to pump the second chromogenic material to flow within the simulated vein. Both the arterial and venous blood pumps are centrifugal pumps. The arterial blood pump includes backward-curved blades with an impeller diameter of 50-80 mm, and its output pipeline is equipped with an overflow valve and a first throttling valve. The venous blood pump is a centrifugal pump, including forward-curved blades with an impeller diameter of 30-50 mm, and its output pipeline is equipped with a second throttling valve. The simulated arteries include the radial artery, carotid artery, thoracic aorta, abdominal aorta, and femoral artery, which are interconnected. The simulated veins include the radial vein, jugular vein, superior vena cava, inferior vena cava, and femoral vein, which are interconnected. The carotid artery, radial artery, femoral artery, jugular vein, radial vein, and femoral vein are all detachably equipped with puncture units. The puncture units are configured to be repeatedly punctured. The puncture units include, from the inside out, a rigid support layer, a waterproof layer, and an elastic rubber layer.

2. The in vitro life support simulation model according to claim 1, characterized in that, The puncture unit is detachably and sealed to the carotid artery, radial artery, femoral artery, jugular vein, radial vein, and femoral vein via Luer connectors or photosensitive resin connectors.

3. The in vitro life support simulation model according to claim 2, characterized in that, The connecting end of the Luer connector or the photosensitive resin connector is provided with an annular groove, and a sealing ring is installed in the annular groove. The depth of the groove is 60% to 70% of the height of the sealing ring. The inner surface of the connecting port of the carotid artery, the radial artery, the femoral artery, the jugular vein, the radial vein, and the femoral vein is provided with a smooth sealing surface that mates with the sealing ring, and a sealed connection is achieved through the sealing ring.

4. The in vitro life support simulation model according to any one of claims 1 to 3, characterized in that, The molecular particle size of the second colorimetric material is >10nm, and it cannot pass through the semipermeable membrane.

5. The in vitro life support simulation model according to any one of claims 1 to 3, characterized in that, The arterial blood pump has a first blood storage chamber, which stores a first colorimetric material, and the first blood storage chamber is connected to the simulated artery.

6. The in vitro life support simulation model according to any one of claims 1 to 3, characterized in that, The venous blood pump has a second blood storage chamber, which stores a second colorimetric material, and the second blood storage chamber is connected to the simulated vein.

7. The in vitro life support simulation model according to any one of claims 1 to 3, characterized in that, The simulated arteries and simulated veins are located on the left and right sides of the human body model.

8. An extracorporeal life support simulation training system, characterized in that, The system includes a monitoring and control device and an extracorporeal life support simulation model as described in any one of claims 1 to 7. The monitoring and control device includes a display and a microprocessor control unit. The microprocessor control unit is electrically connected to the arterial blood pump and the venous blood pump via a pressure sensor. The centrifugal pumps of the arterial blood pump and the venous blood pump are driven by variable frequency speed-regulating motors. The microprocessor control unit is used to adjust the speed of the variable frequency speed-regulating motors of the arterial blood pump and the venous blood pump, and to adjust the opening of the overflow valve, the first throttle valve, and the second throttle valve to adjust the simulated blood pressure of the simulation model. The display is capable of displaying the simulated blood pressure.

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