CN219979017U - Cardiac afterload hemodynamic simulator - Google Patents
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- CN219979017U CN219979017U CN202321263818.3U CN202321263818U CN219979017U CN 219979017 U CN219979017 U CN 219979017U CN 202321263818 U CN202321263818 U CN 202321263818U CN 219979017 U CN219979017 U CN 219979017U
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Abstract
The utility model discloses a heart afterload hemodynamic simulator, which comprises a shell similar to the body shape of the upper half of a human body, wherein the shell is connected with a power supply through a connecting wire; the multifunctional hemodynamic dynamic change simulator is characterized in that a heart module, a lung circulation module and a power pump module are arranged in a shell, the heart module, the power pump module and the lung circulation module are connected through the circulation module, and the multifunctional hemodynamic dynamic change simulator has the functions of simulating heart structures, peripheral circulation, circulation resistance, lung circulation and blood viscosity, and has the function of assisting an instrument to measure various numerical changes.
Description
Technical Field
The utility model belongs to a dynamic auxiliary device in the medical field, in particular to a heart afterload hemodynamic simulator which is mainly used for heart structure simulation, peripheral circulation simulation, circulation resistance simulation, pulmonary circulation simulation and blood viscosity simulation, and is simultaneously suitable for heart hemodynamic theory teaching and clinical practice application.
Background
The heart is an important organ of the human body, mainly plays a role in conveying blood to the whole body, and has the purposes of contracting and dilating to convey the blood to the periphery, so that the tissue metabolism requirement can be met. The heart needs to overcome the afterload to perform an effective ejection. The afterload of the heart refers to the pressure load of the heart, and is mainly determined by the compliance of the aorta, peripheral vascular resistance, blood viscosity, and peripheral circulatory capacity. For the left ventricle, factors that cause an increase in afterload are an increase in Systemic Vascular Resistance (SVR) and an increase in left ventricular volume. For the right ventricle, the factor that causes the afterload to increase is an increase in Pulmonary Vascular Resistance (PVR) and an increase in right ventricular volume. From the medical ohm's law, a sharp rise in afterload, a decrease in myocardial shortening rate, a decrease in stroke volume and an increase in end-diastole volume are caused by a decrease in ejection during the limited systolic phase, which results in a secondary rise in left ventricular end-diastole volume (preload), the intrinsic ability of the heart to resume normal stroke volume upon an increase in acute afterload is known as the Anrep effect. Abnormal afterload can lead to palpitation, shortness of breath, nausea, dizziness, insufficient supply of cardiovascular and cerebrovascular vessels, and overweight is caused by heart failure.
Clinically, piCCO hemodynamic monitoring calculates afterloaded Systemic Vascular Resistance (SVR) from blood pressure and Cardiac Output (CO). The Systemic Vascular Resistance Index (SVRI) is the ratio of Systemic Vascular Resistance (SVR) to body surface area (BMI), and if the SVRI is increased, the heart contractility must be increased to maintain the same ejection volume, and if the afterload exceeds the tolerance range of the myocardial fibers, compensatory manifestations of the heart may occur. Management of perioperative volume balance and hemodynamic stability requires real-time monitoring of afterload stability. The situation of patients with unbalanced load is critical, and it is important to find and take corresponding measures in time to maintain the load balance. There is little clinical training opportunity for primary physicians, and therefore there is a strong need for a cardiac afterload hemodynamic simulator that assists physicians in the understanding of afterload. At present, the afterload simulator applied to clinical teaching has few varieties and single functions, and cannot meet the training requirements under complex conditions.
Therefore, the existing simulators are not satisfactory to solve the medical, teaching and research problems in the field, and a novel cardiac afterload hemodynamic simulator which can be repeatedly used needs to be designed.
Disclosure of Invention
Aiming at the teaching requirement of clinicians, the utility model aims at providing a heart afterload hemodynamic simulator which has the functions of heart structure simulation, peripheral circulation simulation, circulation resistance simulation, lung circulation simulation and blood viscosity simulation.
In order to achieve the above task, the present utility model adopts the following technical solutions:
a heart afterload hemodynamic simulator comprises a shell similar to the body of the upper half of a human body, wherein the shell is connected with a power supply through a connecting wire; the heart module, the power pump module and the lung circulation module are connected by the circulation module, wherein:
the shell is a hollow box body, a bracket for fixing a heart module, a power pump module and a lung circulation module is arranged in the shell, the front surface of the box body is covered with a replaceable epidermis, a sternum structure is inlaid below the epidermis, a silica gel clamping groove is fixed at the inner edge of the base, the heart module is fixed at the chest cavity position, and the power pump module is fixed at the abdominal cavity position; the circulation module is used for connecting the heart module, the lung circulation module and the power pump module to form a closed liquid circulation system, and is arranged around the inner edge of the box body and is arranged in the silica gel clamping groove at the inner edge of the shell;
the circulation module adopts a plastic hose, a heating wire is embedded in the hose and used for simulating a human body blood vessel, a spiral interface is arranged at the joint, a universal one-way valve is arranged, the heart module, the power pump module and the lung circulation module can be connected to form a closed liquid circulation system, and the hose is rubbed by an electric pump rotating wheel to generate uniform-speed unidirectional simulated blood flow;
the heart module is an integrated heart model and a pericardium model which are encapsulated in soft silica gel and are tightly attached to the epidermis of the shell and the sternum frame; wherein:
the image data of the heart model is taken from a patient real CT, the material is silica gel, the heart model is formed by 3D printing, a liquid inlet and a liquid outlet are provided with spiral interfaces, and the heart model is in butt joint with the circulation module;
the pericardial model is made of self-healing materials, and the touch sense is simulated;
the power pump module comprises an aortic pump, a pulmonary artery pump, an upper and lower vena cava pump and a pulmonary vein pump, is connected with the circulation module through a spiral interface and is used for realizing normal blood flow simulation, and the electric rotating wheels of the aortic pump, the pulmonary artery pump, the upper and lower vena cava pump and the pulmonary vein pump are used for giving uniform blood flow in the circulation module;
the lung circulation module is a closed container, two ends of the lung circulation module are connected with the circulation module, and the lung circulation module is filled with heat-conducting gel pellets for increasing the contact between liquid and air, slowing down the flow speed of the liquid and simulating the effect of lung circulation.
Other features of the utility model are:
the liquid flowing in the hose consists of polyvinyl alcohol, glycerol, aqueous solution and proper starch diluent.
The cardiac afterload hemodynamic simulator has the functions of simulating cardiac structure, peripheral circulation, circulation resistance, pulmonary circulation and blood viscosity, and has the function of assisting an instrument to measure various numerical changes, and is a multifunctional hemodynamic dynamic change simulator.
Drawings
FIG. 1 is a schematic illustration of the housing of a post-cardiac load hemodynamic simulator of the present utility model;
FIG. 2 is a schematic view of the internal distribution of the housing;
FIG. 3 is a schematic diagram of a circulation module;
FIG. 4 is a schematic diagram of a pulmonary circulation module configuration;
fig. 5 is a schematic diagram of the heart module structure.
Fig. 6 is a schematic diagram of the internal structural details of the post-cardiac load hemodynamic simulator of the present utility model.
The utility model is described in further detail below with reference to the drawings and examples.
Detailed Description
Referring to fig. 1 to 6, the present embodiment provides a cardiac afterload hemodynamic simulator, comprising a housing, the housing being connected to a power source by a connection wire; the heart module, the power pump module and the lung circulation module are connected through the circulation module. The cardiac afterload hemodynamic simulator, wherein each module is characterized by:
1. outer casing
The shell is a hollow box body, the shape of the shell is an adult male upper half model, and a bracket for fixing a heart module, a power pump module and a lung circulation module is arranged in the shell. The front surface of the box body is covered with a replaceable epidermis, and a sternum structure is inlaid below the epidermis. The inner edge of the base is fixed with a silica gel clamping groove, the heart module is fixed at the chest cavity position, and the power pump module is fixed at the abdominal cavity position. The circulation module adopts a hose for connecting the heart module, the lung circulation module and the power pump module to form a closed liquid circulation system, and the hose is arranged around the inner edge of the box body and is arranged in a silica gel clamping groove at the inner edge of the shell.
(1) Epidermis: the simulation human surface skin is made of silica gel material, has simulated touch feeling, and can be detached, replaced, cleaned and maintained;
(2) sternum: the structure of the sternum of a human body is simulated, and rib gaps are formed, so that the function of the rib gaps is to support epidermis. The skeleton structure can be buckled on the inner edge of the base and can be disassembled and replaced;
2. circulation module
Referring to fig. 3, the circulation module adopts a plastic hose for simulating a human body blood vessel, a screw joint is arranged at the joint, a universal one-way valve is arranged at the joint, and each module (such as a module A to a module B in the figure) can be connected to form a closed liquid circulation system. The plastic hose is rubbed by the electric pump rotating wheel of the power pump module to generate uniform unidirectional simulated blood flow, and the partial advantage is that blood flows in a closed environment without an external water tank. The plastic hose worn by the rotating wheel can be replaced, and the length of the plastic hose can be increased. The plastic hose is arranged on the periphery of the inner edge of the shell, is clamped in the silica gel on the inner edge of the shell, and the silica gel is tightly attached to the surface of the shell and the sternum frame. The plastic hose is internally embedded with a heating wire, a medium ("blood") flowing in the plastic hose adopts a solution composed of polyvinyl alcohol, glycerol and water, and a small amount of starch diluent is added. Heating causes starch gelatinization, increasing the "blood" viscosity, simulating an increase in peripheral circulation resistance.
3. Pulmonary circulation module
Referring to fig. 4, the pulmonary circulation module is a closed container, and two ends are connected with a circulation device (plastic hose), wherein the circulation device is filled with heat-conducting gel pellets. The blood enters the lung circulation module through the circulation module, so that the contact between the liquid and the air is increased, the blood flow speed is properly slowed down, and the effect of the lung circulation is simulated in an image. When the blood is heated to 40 ℃ through the circulation module, the heat-conducting gel pellets absorb water and expand, gaps among the pellets are reduced, namely pulmonary vascular resistance (PVC) is increased, pulmonary arterial hypertension is vividly simulated, and the afterload of the right ventricle is increased. At the same time, peripheral circulation capacity decreases and cardiac output decreases accordingly. The left end of the pulmonary circulation module is connected with a heart pulmonary artery, and the right end is connected with a pulmonary vein.
4. Heart module
Referring to fig. 5, the heart module mainly includes pericardium (layer), papillary muscle, heart (layer), tricuspid valve, pulmonary vein, active vein, aorta, atrial septum, pulmonary artery, pulmonary valve, superior and inferior vena cava, chordae tendineae, ventricular septum;
(1) heart model: the heart model image data is obtained from the real CT of a patient, 3D printing is carried out through MIICS software, the material is silica gel, a liquid inlet and a liquid outlet are provided with screw interfaces, and the screw interfaces are in butt joint with a plastic hose;
(2) pericardial model: made of self-healing materials conventional in the art and simulated to the touch.
The heart module is formed by integrally packaging a heart model and a pericardium model in soft silica gel, is replaceable, and is tightly attached to the epidermis of the shell and the framework of the sternum.
5. Power pump module
The device mainly comprises an aortic pump, a pulmonary artery pump, an upper vena cava pump and a lower vena cava pump, wherein the pulmonary vein pump is provided with a spiral interface connected with a circulation module (a plastic hose) and is electrified for use. Through aortic pump, pulmonary artery pump, upper and lower vena cava pump, pulmonary vein pump realizes normal blood flow simulation, and power pump module gives the blood flow at the plastic hose uniform velocity that blocks in it through the electric runner of pump, and the switch can be realized to the switch of opening after the circular telegram.
Details of the internal structure of the post-cardiac load hemodynamic simulator of this embodiment are shown in fig. 6. The using process is as follows:
before the heart afterload hemodynamic simulator is electrified, checking whether equipment is complete, whether connection among all modules is tight and fixed, whether the heating function of a circulation module is normal, whether the gel pellet function of a lung circulation module is normal, and whether the whole shell is internally provided with water leakage or not, so that electric shock danger is avoided. The epidermis is disinfected according to a normal flow and placed in a supine position, so that the liquid distribution in the simulated human body is ensured to be uniform.
Physiological application of ohm's law if Cardiac Output (CO) is considered as current and the difference between mean arterial blood pressure (MAP) and Central Venous Pressure (CVP) is considered as voltage. Wherein, MAP measuring point is beta point, CVP measuring point is alpha point. The Systemic Vascular Resistance Index (SVRI) is considered as resistance, then a formula is generated: svri= (MAP-CVP)/CO. Pulmonary Artery Catheter (PAC) is a gold standard for monitoring Cardiac Output (CO), with measurement point γ, using thermal dilution of pulmonary artery catheter.
The cardiac cycle t=1 s is specified, i.e. the heart rate is 60bpm/min. When the heart rate is accelerated, the cardiac cycle is particularly ventricular comfortZhang Qi shorten, i.e. (T) BC +T AD )-(T * BC +T * AD ) < 1s, wherein T is the present cardiac cycle, T * For the next cardiac cycle, ABCD is the identity of each powered pump. In the case of constant ventricular filling duration, i.e. (T) BC +T AD )-(T * BC +T * AD ) The faster the venous return speed, i.e. (V) BC +V AD )-(V * BC +V * AD ) The more venous blood volume is returned to the heart < 0. Wherein V is heart rate of the current period, V * For the next cycle heart rate.
1) Normal mode:
the heart afterload hemodynamic simulator is electrified, the power pump module operates to drive 'blood' in the circulation module to move unidirectionally at a uniform speed, the smooth operation process is checked, the connection of the modules is tight, the heating guide wire of the circulation module does not work at the moment, the whole simulated human environment is room temperature, the afterload is normal, and the hemodynamics are stable. Observing and recording cardiac output;
2) Peripheral circulation resistance mode:
the pump in the power pump module is kept to rotate at a constant speed in a unidirectional way, the circulation module is in a low-temperature environment (an ice bag is paved in the shell), the circulation module adopts a silica gel hose, the silica gel hose is hardened and contracted in a low-temperature state, the simulated peripheral circulation resistance is increased, the afterload is increased, the cardiac output is reduced, and the cardiac contractility is increased in order to keep the cardiac output unchanged; the ice bag is removed to restore the room temperature, the afterload is reduced, the cardiac output is increased to weaken the heart contractility, and the cardiac output is restored to be normal.
3) Blood viscosity pattern
Maintaining uniform unidirectional rotation of each pump in the power pump module, starting the heating guide wire of the circulation module to work, heating to cause the starch diluent to reach a gelatinization critical temperature value (60 ℃), maintaining the temperature, increasing the blood viscosity to cause afterload to aggravate, breaking hemodynamic balance, reducing cardiac output, and increasing the systole force to maintain the cardiac output unchanged; restoring room temperature gelatinization, reducing afterload, increasing cardiac output, weakening heart contractility, and restoring cardiac output to normal.
4) Aortic compliance mode
The pumps in the power pump module rotate at a constant speed in a unidirectional manner, the heart module is in a low-temperature environment (an ice bag is paved in a base), the silica gel is hardened and contracted in a low-temperature state, the heart module is weighted by afterload caused by weakening of aortic compliance, hemodynamic balance is broken, cardiac output is reduced, and the heart contractility needs to be increased in order to maintain the cardiac output unchanged; restoring room temperature compliance increases, afterload decreases, cardiac output increases, and heart contractility decreases, restoring cardiac output to normal.
5) Pulmonary circulation simulation
The constant speed unidirectional rotation of each pump in the power pump module is kept, and the circulation module is heated to 40 ℃ below the gelatinization critical value (60 ℃) of the starch diluent. Under normal conditions, the functions of the left ventricle and the right ventricle complement each other, and the stroke volume is equal. The heat-conducting gel pellets in the pulmonary circulation module are preheated and expanded, the pulmonary circulation resistance is increased (simulating pulmonary arterial hypertension in clinic) to break the hemodynamic balance, and the right cardiac output is reduced. To maintain the right cardiac output unchanged, the systole force needs to be increased; restoring room temperature compliance increases, afterload decreases, right cardiac output increases, and heart contractility decreases, restoring right cardiac output to normal.
6) Postoperative operation
Repeated heating and cooling operations can cause damage to the plastic hose material of the circulation module, and the starch of the "blood" content is denatured and needs to be replaced periodically. In addition, by using auxiliary equipment to monitor the relevant variation, data collection should be performed at the measurement point to avoid inaccurate data. After each operation is finished, the power supply line device is powered off, the power supply line device is collected and is located in a dry and ventilated environment, and the water leakage and looseness conditions in the simulator are checked. Checking the tightness of the interfaces between the circulating module and each module to prevent water leakage. The cleaning and disinfecting operation is carried out according to the actual clinical steps.
Claims (1)
1. A heart afterload hemodynamic simulator comprises a shell similar to the body of the upper half of a human body, wherein the shell is connected with a power supply through a connecting wire; the heart module, the power pump module and the lung circulation module are connected by the circulation module, wherein:
the shell is a hollow box body, a bracket for fixing a heart module, a power pump module and a lung circulation module is arranged in the shell, the front surface of the box body is covered with a replaceable epidermis, a sternum structure is inlaid below the epidermis, a silica gel clamping groove is fixed at the inner edge of the base, the heart module is fixed at the chest cavity position, and the power pump module is fixed at the abdominal cavity position; the circulation module is used for connecting the heart module, the lung circulation module and the power pump module to form a closed liquid circulation system, and is arranged around the inner edge of the box body and is arranged in the silica gel clamping groove at the inner edge of the shell;
the circulation module adopts a plastic hose, a heating wire is embedded in the hose and used for simulating a human body blood vessel, a spiral interface is arranged at the joint, a universal one-way valve is arranged, the heart module, the power pump module and the lung circulation module can be connected to form a closed liquid circulation system, and the hose is rubbed by an electric pump rotating wheel to generate uniform-speed unidirectional simulated blood flow;
the heart module is an integrated heart model and a pericardium model which are encapsulated in soft silica gel and are tightly attached to the epidermis of the shell and the sternum frame; wherein:
the image data of the heart model is taken from a patient real CT, the material is silica gel, the heart model is formed by 3D printing, a liquid inlet and a liquid outlet are provided with spiral interfaces, and the heart model is in butt joint with the circulation module;
the pericardial model is made of self-healing materials, and the touch sense is simulated;
the power pump module comprises an aortic pump, a pulmonary artery pump, an upper and lower vena cava pump and a pulmonary vein pump, is connected with the circulation module through a spiral interface and is used for realizing normal blood flow simulation, and the electric rotating wheels of the aortic pump, the pulmonary artery pump, the upper and lower vena cava pump and the pulmonary vein pump are used for giving uniform blood flow in the circulation module;
the lung circulation module is a closed container, two ends of the lung circulation module are connected with the circulation module, and the lung circulation module is filled with heat-conducting gel pellets for increasing the contact between liquid and air, slowing down the flow speed of the liquid and simulating the effect of lung circulation.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321263818.3U CN219979017U (en) | 2023-05-23 | 2023-05-23 | Cardiac afterload hemodynamic simulator |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321263818.3U CN219979017U (en) | 2023-05-23 | 2023-05-23 | Cardiac afterload hemodynamic simulator |
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| Publication Number | Publication Date |
|---|---|
| CN219979017U true CN219979017U (en) | 2023-11-07 |
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| CN202321263818.3U Active CN219979017U (en) | 2023-05-23 | 2023-05-23 | Cardiac afterload hemodynamic simulator |
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| Country | Link |
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| CN (1) | CN219979017U (en) |
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