CN211213114U - Arteriovenous vascular access external physical simulation device - Google Patents
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Abstract
The utility model discloses an extracorporeal physical simulation device of an arteriovenous vascular access, which comprises a main body and a main body; the water outlet of the water tank is connected with the water inlet of the water tank through a pipeline; a section of stenosis model simulating a vascular stenosis model is arranged on the pipeline; a first one-way valve, a pulsating flow generating device, a second one-way valve, a first compliance chamber, a flowmeter, a first pressure gauge, a second compliance chamber and a resistance valve are sequentially arranged on the pipeline along the flowing direction of liquid; the pulsating flow generating device simulates the contraction and relaxation of the heart chamber to realize the blood suction from the vein and the blood ejection from the heart; the first and second compliance chambers are used to simulate the cushioning capacity of the arterial vessel wall; the first check valve and the second check valve are used for preventing liquid backflow; the frictional resistance of the inner wall of the pipeline and the resistance provided by the resistance valve simulate the resistance of the blood vessel. The simulator can measure hemodynamics parameters which are difficult to measure in the AVA of a hemodialysis patient.
Description
Technical Field
The utility model belongs to the medical equipment field, concretely relates to arteriovenous vascular passageway external physical simulation device.
Background
Chronic Kidney Disease (CKD) is a serious disease that endangers human health. Dialysis treatment with chronic use of unnatural vascular access is accompanied by various vascular access complications, and related epidemiological investigations have shown that the second cause of hospitalization of hemodialysis patients is the stenosis or occlusion of venous vascular access (AVA). Therefore, detection of AVA stenosis is very important for hemodialysis patients. Meanwhile, with the continuous improvement of medical level, the long-term normal use of maintaining the arteriovenous vascular access is imperative, which requires the joint efforts of medical care personnel and patients, and thus the demand for developing a portable arteriovenous vascular access monitoring device is increasing. The prior art has employed a variety of sensing means to detect vascular access status. However, the abnormal features resulting from vascular access complications found in different studies are not identical. The reason for the discrepancy may be that the previous studies were analyzed based on clinically measured data, but the state of the vascular access is affected by other various hemodynamic parameters (length, elastic modulus, poisson's ratio, blood density, blood viscosity, etc.). The hemodynamic parameters of the vascular access can be effectively controlled through the vascular access physical simulation model, and conditions are provided for quantitative research of the vascular access hemodynamic.
In a related study of the in vitro simulation of vascular pulsatile flow, approximate pulsatile flow changes in the vessel segment were essentially achieved by varying the fluid input in the model. The peristaltic pump, the breathing machine and the blood pump have fixed frequency and capacity, and the pulsating flow generated by the simulation model cannot accurately simulate physiological waveforms and cannot be adjusted in a large range. The aortic pressure waveform is reconstructed by a method for simulating the volume change of the left ventricle, the method can accurately reproduce the aortic pressure, but the arteriolar pulsating flow waveform is not directly connected with a ventricular volume curve, and a volume signal generates a large error when reaching a blood vessel passage with a long distance.
Hemodynamics is an important part of the blood circulation system, is mainly based on the physical laws governing blood flow, and is the same as the general principles of hydrodynamics, and the object of study is the relationship between blood flow volume, blood flow resistance, and blood pressure. Blood vessels are not rigid tubes, elastic and dilatant, so that the flow dynamics based on classical viscosity cannot explain the hemodynamics. The following is a study of the relationship between blood flow I, blood flow resistance R, and blood pressure P in the vascular pathway.
The circuit parameter model of the hemodynamics is a cylindrical model for a real physiological environment, is a bridge between solving actual problems and theories, has great convenience in the aspect of blood circulation system explanation due to the application of the circuit parameter model, can reveal a blood vessel access blood pressure generation mechanism, and provides design instructions for physiological or pathological conditions. However, the introduction of the circuit parameter model to perform model analysis of the whole blood circulation system requires more details of simulation, and therefore, it is advantageous to simplify certain parts of the system. The circuit parameter model provides guidance for designing a simulation system, can indicate the relation between variables, and can control various hemodynamic parameters by changing the parameters of the simulation system for in-depth analysis.
SUMMERY OF THE UTILITY MODEL
The utility model aims at providing an external physical simulation device of arteriovenous vascular passageway should utilize this simulation device to measure difficult measuring hemodynamic parameter in the hemodialysis patient AVA, provides probably for further understanding the blood flow condition in the blood vessel.
In order to realize the purpose of the utility model, the utility model provides a following technical scheme:
an extracorporeal physical simulation device of a venous vascular access, comprising:
the water tank is filled with liquid simulating blood, and a water outlet of the water tank is connected with a water inlet of the water tank through a pipeline simulating a venous blood vessel passage; a section of stenosis model simulating a blood vessel stenosis region is arranged on the pipeline;
a first one-way valve, a pulsating flow generating device, a second one-way valve, a first compliance chamber, a flow meter and a first pressure meter are sequentially arranged on the pipeline between the water outlet and the narrow model along the liquid flowing direction;
a second pressure gauge, a second compliance chamber and a resistance valve are sequentially arranged on the pipeline between the narrow model and the water inlet along the liquid flowing direction;
the pulsating flow generation device simulates the contraction and the relaxation of a ventricle by being capable of sucking liquid from veins and spraying the liquid outwards, so as to realize the blood sucking from the veins and the blood shooting from the heart;
the first and second compliance chambers are used to simulate the cushioning capacity of an arterial vessel wall;
the first one-way valve and the second one-way valve are used for preventing the pulsating flow generation device from generating liquid backflow when blood is sucked from a vein;
the frictional resistance of the inner wall of the pipeline and the resistance provided by the resistance valve simulate the resistance of the blood vessel.
Preferably, the pulsating flow generation device comprises a chamber simulating a heart chamber, a piston is arranged in the chamber, the fixed end of the piston is connected with one end of a linear reciprocating motion connecting rod, and the outer wall of the chamber is provided with a speed regulating motor which is connected with the other end of the linear reciprocating motion connecting rod;
the speed regulating motor drives the linear reciprocating motion connecting rod to do linear motion so as to drive the piston to do linear motion in the cavity, the rotating speed of the speed regulating motor simulates heart rate, the stroke of the piston driven by the motion of the linear reciprocating motion structure simulates blood flow, and the heart rate and the blood flow are regulated by controlling the rotating speed of the speed regulating motor.
Preferably, the first compliance chamber and the second compliance chamber are a sealed container with coexisting gas and liquid, the lower part of the container is liquid, the upper part of the container is gas, and the compliance is changed by changing the pressure of the gas. Further, the first and second compliance chambers are syringes. The compliance of the compliance chamber is varied by fixing the molar content of air within the syringe.
Preferably, the resistance valve is a ball valve; the pipeline is a silicone tube, and the elasticity coefficient and the Poisson ratio of the pipeline are the same as the physical properties of the clinically adopted polymer graft.
Preferably, the narrow model is prepared by 3D printing of a resin material and is placed in an O-shaped sealing ring to form a combined body, and the combined body is tightly attached to the inner wall of the pipeline.
Preferably, the liquid simulating blood is a mixed solution of water and glycerol according to a certain proportion, and the viscosity speed of the mixed solution is 3.2 × 10-6m at the temperature of 28 DEG C2Density 1090kg/m3。
Compared with the prior art, the utility model discloses the beneficial effect who has does:
the utility model provides an external physical simulation device of vein vascular access way can simulate the blood condition of flowing in the blood vessel, and the target of simulation is the true condition that artery and vein pressure pulsation, blood flow satisfy AVA, and the controllable parameter of simulation has rhythm of the heart, heart beat volume (blood flow), vascular resistance, artery and vein compliance, systolic phase and diastolic phase ratio.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required to be used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to these drawings without creative efforts.
Fig. 1 is a schematic structural diagram of an extracorporeal physical simulation apparatus of a venous vascular access provided in this embodiment;
FIG. 2 is a schematic view of the linear reciprocating motion of the connecting rod;
fig. 3 is a circuit parameter diagram of a venous vascular access extracorporeal physical simulation apparatus.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more clearly understood, the present invention is further described in detail with reference to the accompanying drawings and embodiments. It should be understood that the detailed description and specific examples, while indicating the scope of the invention, are intended for purposes of illustration only and are not intended to limit the scope of the invention.
The extracorporeal physical simulation device for the venous vascular access provided by the embodiment can simulate the pulsating flow in the blood supply artery of a patient similar to hemodialysis, and is used for obtaining the blood flow in AVA under the condition of different hemodynamic parameters. The physical simulation model can adjust, measure, display and record heart rate pulsation and blood pressure of an outlet and an inlet (simulated artery anastomotic stoma and vein anastomotic stoma) in the simulated AVA in real time. As shown in fig. 1, the device comprises a water tank 1, a first check valve 2, a pulsating flow generation device 3, a second check valve 4, a first compliance chamber 5, a flow meter 6, a first pressure gauge 7, a second pressure gauge 8, a second compliance chamber 9, a resistance valve 10 and a narrow model 11 which are connected in sequence through pipelines.
Wherein the water tank 1 is filled with blood-simulating liquid which is a mixed solution of water and glycerol at a certain ratio, such as 0.38: 0.62, and has a viscosity speed of 3.2 × 10-6m at 28 deg.C2Density 1090kg/m3。
The water outlet of the water tank 1 is connected with the water inlet of the water tank 1 through a pipeline simulating a vein blood vessel passage; the pipeline is provided with a section of stenosis model 11 for simulating a blood vessel stenosis region.
On a pipeline between a water outlet and the narrow model 11, a first one-way valve 2, a pulsating flow generating device 3, a second one-way valve 4, a first compliance chamber 5, a flow meter 6 and a first pressure gauge 7 are sequentially arranged along the flowing direction of liquid; on the pipe between the narrow pattern 11 and the water inlet, a second pressure gauge 8, a second compliance chamber 9, a resistance valve 10 are arranged in order in the direction of the liquid flow.
The utility model discloses in, the pulsation flow produces the contraction and the diastole of the main simulation ventricle of device 3 and is in order to realize from vein blood suction and heart ejection, realizes from vein fluid suction and outside injection liquid through the mode of motor drive piston promptly. Specifically, the pulsating flow generation device 3 comprises a chamber simulating a ventricle, a piston is arranged in the chamber, the fixed end of the piston is connected with one end of a linear reciprocating motion connecting rod, a speed regulating motor is arranged on the outer wall of the chamber, and the speed regulating motor is connected with the other end of the linear reciprocating motion connecting rod. The speed regulating motor drives the linear reciprocating motion connecting rod to do linear motion so as to drive the piston to do linear motion in the cavity, the rotating speed of the speed regulating motor simulates heart rate, the stroke of the piston driven by the motion of the linear reciprocating motion connecting rod simulates blood flow, and the heart rate and the blood flow are regulated by controlling the rotating speed of the speed regulating motor. The pulsatile flow generating means 3 generates a pulsatile flow waveform similar to that generated by the left ventricle.
As shown in figure 2, when the speed regulating motor pushes the piston to move downwards through the straight reciprocating motion connecting rod to simulate the contraction of the ventricle, the pulsating flow generation device simulates the ejection of blood from the heart, the speed regulating motor drives the piston to move upwards through the straight reciprocating motion connecting rod to simulate the relaxation of the ventricle, and the pulsating flow generation device sucks blood from the vein. Ventricular systolic relaxation time is very short, so to the acceleration of buncher and direction change requirement than higher, and the piston can produce a large amount of frictional force if adopting O-type sealing washer in addition, and is higher to motor power requirement, consequently, the utility model discloses select adjustable rotational speed's 220V linear alternating current motor as buncher.
The first and second compliance chambers 5, 9 are primarily intended to simulate the cushioning capacity of the arterial vessel wall, i.e. to simulate the elasticity of the vessel and the cushioning and reflux of the veins, which are the intrinsic elastic characteristics of the vessel wall. The utility model discloses design first compliance room 5 and second compliance room 9 as a gas-liquid coexistent sealed container, the container lower part is liquid, and upper portion is gaseous, changes the compliance through the pressure that changes gas. From the pressure-volume relationship of compliance, the formula is listed:
Pfl d＝Pair+ρghfluid(1)
Vtank＝Vfluid+Vair(2)
PairVairconstant (3) of nRT ═ n rt
The differentiation is obtained by equations (1) to (3):
dPfluid＝dPair+(ρg)dhfluid
dVfluid＝-dVair
the compliance E is then:
wherein, PfluidAnd PairPressure of liquid, gas, respectively, VfluidAnd VairVolume of liquid, gas, respectively, hfluidIs the liquid height, ρ is the liquid density, g is the gravitational acceleration, and A is the compliant chamber bottom area. n represents the molar quantity of the gaseous species, T represents the thermodynamic temperature of the ideal gas, and there is a constant: r is an ideal gas constant, and the product of the three is a constant. Since the syringe is cylindrical, Vfluid＝A*hfluid。
Due to the fact that
The first term is negligible with respect to being small, so the compliance of the compliance chamber can be adjusted by simply adjusting the volume of air in the compliance chamber.
Due to the fact that
Relatively small to the first term is negligible, so the compliance of the compliance chamber can be adjusted by simply adjusting the volume of air in the chamber, which corresponds to a circuit parameter of capacitance C0＝1/E。
In this embodiment, the first compliance chamber 5 and the second compliance chamber 9 are selected to be modified syringes. The syringe and the piston of the injector are both fixed on the iron stand by the test tube clamp, so that the total volume of the liquid and the gas is not changed when the pressure of the liquid in the injector is changed.
In the vein blood channel extracorporeal physical simulation device, according to the fluid network theory, blood pressure and blood flow can be respectively compared by voltage and current in a circuit, blood flow resistance can be compared by resistance, blood inertia can be compared by inductance, and blood flow compliance can be compared by capacitance, so that the simulation device can be converted into a circuit parameter model shown in fig. 3. The circuit model can be used for calculating the setting parameters of the first and second compliance chambers, the resistance valve and the motor, and calculating the impedance, the capacitive reactance and the inductive reactance of the blood vessel access through the parameters, the input end pressure and the output end pressure of the blood vessel access and the blood flow. The resistance of the blood vessel mainly comes from two parts, namely the inner wall friction resistance of the pipeline and the resistance provided by the resistance valve, wherein the inner wall friction resistance R of the pipeline can be calculated according to the formula (4).
Where η is a constant and can be the blood viscosity coefficient, l is the blood vessel length, and r is the blood vessel radius. The resistance valve is a manual or electric valve, and the resistance is changed by changing the cross-sectional area of the valve. Because the resistance of the resistance valve is far larger than that of the connecting pipe, only the resistance of the resistance valve can be considered in the circuit parameter model. In this embodiment, a ball valve may be selected as the resistance valve.
The main source of the blood flow inertia L is the difficulty degree of the blood flow change in the pipeline, and the calculation formula is as follows:
where ρ is a constant, which can be the blood viscosity coefficient, l is the vessel length, and r is the vessel radius. Since the value is small and the influence on the current and voltage is not large, the inertia of the blood flow in the connecting channel is ignored in the circuit parameter diagram, and only the inertia of the blood flow in the blood vessel channel is considered.
Blood flow compliance comes primarily from the elasticity of the compliance chamber and the blood vessels, where the capacitance C of the compliance chamber 01/E. Capacitance C of compliance of vessel elasticity1Can be calculated from equation (6):
wherein l is the length of the blood vessel, r is the radius of the blood vessel, Δ D is the variation of the diameter of the blood vessel, and Δ P is the variation of the blood pressure. The compliance of the connecting conduit is ignored since it is much less than the compliance of the first and second compliance chambers.
In the utility model, the first one-way valve 2 and the second one-way valve 4 are used for preventing the pulsating flow generating device 3 from generating liquid backflow when sucking blood from veins; the first pressure gauge 7 and the second pressure gauge 8 are used for measuring the simulated blood pressure in front of and behind the vascular stenosis model 11, and the flow meter 6 is used for measuring the simulated blood flow passing through the vascular stenosis model 11.
In this embodiment, the pipeline is a silicone tube, the inner diameter is 6.0mm, the elastic coefficient and the poisson ratio are the same as the physical properties of a clinically-used polymer graft, the narrow model 11 is prepared by 3D printing of a resin material, the manufacturing precision is 200um, and the narrow model is placed in an O-shaped sealing ring to form a combined body, the combined body is tightly attached to the inner wall of the pipeline, and the narrow degree of the narrow model 11 is changed from 50% to 95%.
The external physical simulation device for the arteriovenous blood channel realizes the near-physiological pulse change of the pressure and the flow of the AVA blood supply artery pulsating flow on the basis of stable laminar flow, and the pressure range is as follows: 0-26.67 kPa; the pressure fluctuation range is +/-8 kPa; the fluctuation frequency is 0-2.5 Hz; the flow rate is 0-2L/min.
The arteriovenous blood vessel passage external physical simulation device is mainly used for measuring hemodynamics parameters which are difficult to measure in AVA of a hemodialysis patient, such as blood pressure, blood flow, blood vessel wall surface shearing force and the like. The arteriovenous vascular access external physical simulation device provides possibility for further understanding of the blood flow condition in blood vessels. Meanwhile, medical personnel can further know the cause of the AVA complication through the arteriovenous vascular access in-vitro physical simulation device.
The arteriovenous vascular access external physical simulation device can effectively control variables in a vascular access, such as geometric shapes, blood flow and the like. These variables vary widely from patient to patient and are all closely related to the development of blood flow within the blood vessel, and it is difficult to accurately reflect a particular variable change versus AVA if the AVA is analyzed using only clinically actual measured data.
The arteriovenous vascular access external physical simulation device can provide verification environments such as auscultation, light volume, portable ultrasound, infrared rays and the like for different AVA complication detection methods. The model can provide a data set with controllable variables after being correspondingly modified. Meanwhile, the arteriovenous vascular access external physical simulation device can also be used as a verification platform for other disease detection methods, such as arteriosclerosis detection through radial artery pulse waveform, AVA stenosis prone position verification and the like.
The above-mentioned detailed description of the technical solution and the beneficial effects of the present invention have been described in detail, it should be understood that the above is only the most preferred embodiment of the present invention, not used for limiting the present invention, any modification, supplement, equivalent replacement, etc. made within the principle scope of the present invention should be included within the protection scope of the present invention.
Claims (7)
1. An arteriovenous vascular access external physical simulation device, which comprises:
the water tank is filled with liquid simulating blood, and a water outlet of the water tank is connected with a water inlet of the water tank through a pipeline simulating a venous blood vessel passage; a section of stenosis model simulating a blood vessel stenosis region is arranged on the pipeline;
a first one-way valve, a pulsating flow generating device, a second one-way valve, a first compliance chamber, a flow meter and a first pressure meter are sequentially arranged on the pipeline between the water outlet and the narrow model along the liquid flowing direction;
a second pressure gauge, a second compliance chamber and a resistance valve are sequentially arranged on the pipeline between the narrow model and the water inlet along the liquid flowing direction;
the pulsating flow generation device simulates the contraction and the relaxation of a ventricle by being capable of sucking liquid from veins and spraying the liquid outwards, so as to realize the blood sucking from the veins and the blood shooting from the heart;
the first and second compliance chambers are used to simulate the cushioning capacity of an arterial vessel wall;
the first one-way valve and the second one-way valve are used for preventing the pulsating flow generation device from generating liquid backflow when blood is sucked from a vein;
the frictional resistance of the inner wall of the pipeline and the resistance provided by the resistance valve simulate the resistance of the blood vessel.
2. The arteriovenous access extracorporeal physical simulation device of claim 1 wherein the pulsating flow generating means comprises a chamber simulating a ventricle, a piston disposed in the chamber and having a fixed end connected to one end of a linearly reciprocating connecting rod, and an adjustable speed motor mounted to the outer wall of the chamber and connected to the other end of the linearly reciprocating connecting rod.
3. The arteriovenous access extracorporeal physical simulation device of claim 1 wherein the first and second compliance chambers are a sealed container of a gas and liquid together, the lower portion of the container being a liquid and the upper portion being a gas, the compliance being varied by varying the molar content of the gas.
4. The arteriovenous access extracorporeal physical simulation device of claim 1 wherein the first and second compliance chambers are syringes.
5. The arteriovenous vascular access extracorporeal physical simulation device of claim 1, wherein the resistance valve is a ball valve.
6. The arteriovenous vascular access extracorporeal physical simulation device of claim 1, wherein the tubing is silicone tubing and the elastic coefficient and poisson's ratio are the same as the physical properties of clinically used polymer grafts.
7. The arteriovenous vascular access extracorporeal physical simulation device of claim 1, wherein the stenosis model is prepared by 3D printing of a resin material and is placed in an O-ring to form a combined body, and the combined body is tightly attached to the inner wall of the conduit.
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| CN110604552A (en) * | 2019-10-14 | 2019-12-24 | 浙江大学 | Arteriovenous vascular access in-vitro physical simulation device and simulation measurement method |
| CN110604552B (en) * | 2019-10-14 | 2024-08-16 | 浙江大学 | In-vitro physical simulation device and simulation measurement method for arteriovenous vascular access |
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