Hemodynamics testing device of heart and kidney auxiliary blood pump

Abstract

The utility model discloses a hemodynamics testing device of a heart and kidney auxiliary blood pump. The hemodynamics testing device comprises a circulation loop formed by sequentially connecting a ventricle simulator, an aorta model, an after-load simulator, an ultraviolet sterilization device and a liquid storage cavity. The switching tool is connected with the aorta model, and a blood pump to be tested penetrates through the switching tool and is arranged near a renal artery branch of the aorta model; each branch of the aorta model converges to the post-load simulator through an auxiliary pipeline, the post-load simulator is connected with the ultraviolet sterilization device, the ultraviolet sterilization device is connected with the liquid storage cavity, the liquid storage cavity is connected with the ventricular simulator, and the ventricular simulator is connected with the aorta model to form a complete circulation loop; wherein the post-load simulator may simultaneously adjust compliance and peripheral resistance in the circulation loop. Based on the real aorta structure of the human body, the working performance of the blood pump in the body of a patient can be evaluated, and the hemodynamic characteristics of the blood pump in the human body environment can be mastered more effectively and more accurately.

Description

TECHNICAL FIELD

[0001] The utility model relates to a kind of blood flow dynamics test devices of heart and kidney auxiliary blood pump, belong to medical instrument test technical field. BACKGROUND

[0002] Heart and kidney auxiliary blood pump is applicable to the heart failure patient of drug cannot control and is not suitable for cardiac surgery, can improve the blood perfusion of kidney organ, and reduce the pressure load after heart contraction.Specific principle is: blood pump is implanted into the descending aorta of patient, blood flowing into blood pump is accelerated by impeller, to form jet downstream at high speed, while high-speed blood flow promotes the blood flow between blood pump and inner wall of aorta, so that the whole blood in descending aorta is accelerated, finally realizes aorta and each branch perfusion, and the effect of reducing heart load.

[0003] Blood pump belongs to three categories of implantable medical devices, and the blood flow dynamics performance of blood pump needs to be strictly evaluated before clinical use, mainly involving the test of pressure and flow.The existing technology generally uses simple and modular circulation loop to carry out extracorporeal test on the flow, pressure and other performances of blood pump, and such test device often does not conform to the pulsatile blood flow environment in patient's body, so that the blood flow dynamics characteristics obtained by in-vivo and in-vitro test of blood pump are different;In addition, the existing blood flow dynamics test device of blood pump cannot evaluate the perfusion effect on renal artery, and has certain limitation for preclinical use evaluation. SUMMARY

[0004] Therefore, in view of the above-mentioned shortcomings of the prior art, the purpose of the utility model is to provide a blood flow dynamics test device of heart and kidney auxiliary blood pump, which is based on the real aortic structure of human body, helps to evaluate the working performance of blood pump in patient's body, and more effectively and accurately masters the blood flow dynamics characteristics of blood pump in human body environment.

[0005] To achieve the above-mentioned purpose, the utility model adopts the following technical solutions:

[0006] A blood flow dynamics test device of heart and kidney auxiliary blood pump, comprising a circulation loop formed by a ventricle simulator, an aortic model, a afterload simulator, an ultraviolet sterilization device and a liquid storage cavity connected in sequence;Among them,

[0007] The ventricle simulator comprises a motor, a cavity, an exhaust valve and a piston, the motor is directly connected with the piston, so that the piston makes reciprocating linear motion in the cavity, and the downward process and upward process of the piston simulate the contraction and diastole process of heart respectively;

[0008] The aorta model comprises three branches of the aortic arch and a renal artery branch structure, and each branch of the aorta model is connected to a post-load simulator through an auxiliary pipeline, the renal artery branch is arranged on the descending aorta, two pressure monitoring points are arranged on the descending aorta, a first pressure monitoring point is used for monitoring the blood pump inlet pressure, and a second monitoring point is used for monitoring the blood pump outlet pressure; the blood pump to be tested passes through an adapter tool and is arranged near the renal artery branch of the aorta model.

[0009] The post-load simulator comprises a main channel, a compliance regulator connected to the main channel, and a peripheral resistance regulator connected to the main channel, and is used for simultaneously adjusting the compliance and the peripheral resistance in the circulation loop.

[0010] Further, unidirectional valves are arranged on both sides of the inlet and outlet of the ventricle simulator respectively; wherein, the first unidirectional valve simulates the aortic valve and is connected to the aorta model; and the second unidirectional valve simulates the mitral valve and is connected to the liquid storage cavity.

[0011] Further, the reciprocating motion cycle of the piston of the ventricle simulator is preferably 0.5-1.5 s, and the time ratio of the advancing and the retreating is preferably 0.6-1.2.

[0012] Further, the first pressure monitoring point is located upstream of the renal artery branch, the second monitoring point is located at the intersection of the renal artery branch and the descending aorta, the blood pump inlet is located downstream of the first pressure monitoring point, and the blood pump outlet is located upstream of the second pressure monitoring point.

[0013] Further, the distance between the two pressure monitoring points is 5-10 cm. The two pressure monitoring points are measured by using disposable invasive medical pressure sensors, and are fed back in real time through a monitor or other data acquisition equipment.

[0014] Further, the main body structure of the adapter tool is cross-shaped and has four interfaces, wherein, the first interface, the second interface and the third interface all have a pagoda structure, the first interface is connected to the first outflow port of the aorta model; the second interface and the third interface are connected to the auxiliary pipeline, and the fourth interface is used for the blood pump to pass through.

[0015] Further, the fourth interface of the adapter tool is provided with a sealing gasket and a locking cap, the sealing gasket is fixed in the fourth interface through the locking cap and the threaded connection, and the center of the sealing gasket is provided with a cross-shaped opening.

[0016] Further, the compliance adjuster comprises an auxiliary channel communicated with the main channel, an air cavity communicated with the auxiliary channel, and a first exhaust valve arranged in the air cavity, the first exhaust valve being used to adjust the gas volume and gas pressure in the air cavity, so as to realize the compliance adjustment function of the testing device; the peripheral resistance adjuster comprises a valve core and a top cover, the top cover is penetrated through and fixed on the side wall of the main channel, the valve core is connected with the top cover through threads, the valve core is reciprocated in the vertical direction by rotating the valve core, so as to control the flow area of the main channel, and then the peripheral resistance of the testing device is changed.

[0017] The heart-lung auxiliary blood pump blood flow hemodynamics testing device has the advantages that:

[0018] Since different patients have different aortic structures and blood flow hemodynamics characteristics, the blood flow hemodynamics testing device is built based on the real aortic structure of the human body, which is helpful to evaluate the working performance of the blood pump in different patients, and more effectively and accurately master the blood flow hemodynamics characteristics of the blood pump in the human body environment; at the same time, the testing device can be more close to the implantation state of the blood pump in the aorta, provide an in-vitro test basis for precise medical treatment for different patients, and be helpful to preoperative evaluation of the renal artery perfusion effect. BRIEF DESCRIPTION OF DRAWINGS

[0019] In order to more clearly illustrate the technical scheme in the embodiments of the utility model, the drawings needed to be used in the embodiments or the prior art description will be briefly introduced below.

[0020] Figure 1 It is a structure schematic view of the heart-lung auxiliary blood pump blood flow hemodynamics testing device.

[0021] Figure 2 It is a structure schematic view of the heart-lung auxiliary blood pump.

[0022] Figure 3 It is a structure schematic view of the aortic model.

[0023] Figure 4 It is a structure schematic view of the adapter tool.

[0024] Figure 5 It is a sectional view of the adapter tool.

[0025] Figure 6 It is a structure schematic view of the afterload simulator.

[0026] Figure 7 It is a sectional view of the afterload simulator.

[0027] Figure 8 It is a structure schematic view of the ventricle simulator. DETAILED DESCRIPTION

[0028] In order to make the purpose, technical scheme and advantages of the utility model clearer and more apparent, the utility model will be further described in detail below in combination with the drawings and examples.

[0029] In the description of the utility model, it should be understood that the orientation or position relationship indicated by the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer" and the like is based on the orientation or position relationship shown in the drawings, and is only for the convenience of describing the utility model, and therefore cannot be understood as a specific position that the device or structure must have, thus cannot be understood as a limitation on the utility model.

[0030] In addition, the terms "first" and "second" are only for the purpose of description, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined with "first" and "second" can explicitly or implicitly include one or more of the features. In the description of the utility model, the meaning of "multiple" is two or more, unless otherwise specifically limited.

[0031] Reference Figure 1 As shown in the drawings, the utility model provides a kind of hemodynamics testing device suitable for heart and kidney auxiliary blood pump, including ventricle simulator 11, aortic model 12, adapter tool 13, afterload simulator 14, ultraviolet sterilization device 15, liquid storage cavity 16, auxiliary pipeline 17 and base support 18.Ventricle simulator 11 is used to reproduce the pulsatile blood flow environment of human body, and is connected with aortic model 12;Aortic model 12 is converged to afterload simulator 14 by auxiliary pipeline 17, and afterload simulator 14 is used to adjust the compliance and peripheral resistance of pipeline system, afterload simulator 14 is connected with ultraviolet sterilization device 15, ultraviolet sterilization device 15 is connected with liquid storage cavity 16, liquid storage cavity 16 is connected with ventricle simulator 11, finally all components are installed and fixed on base support 18.Open liquid storage cavity 16 is communicated with atmosphere, for simulating atrium and vein.

[0032] Reference Figure 1 And 2 As shown in the drawings, heart and kidney auxiliary blood pump 2 includes sequentially assembled structures such as elastic support 21, pump shell 22, impeller 23, micro motor 24 and cable conduit 25, the rear end of elastic support 21 is connected to the outside of pump shell 22, blood pump inlet 221 is located at the front side of pump shell 22, and blood pump outlet 222 is located at the rear side of pump shell 22.Blood pump 2 is implanted into aortic model 12 through adapter tool 13, and finally makes pump shell 22 be placed near renal artery branch.In test, elastic support 21 can anchor the inner wall of descending aorta of aortic model 12, to improve the stability of blood pump 2 in test.

[0033] Reference Figure 3 As shown in the drawings, the aortic model 12 can be converted based on the MRI or CT image of the patient and by using three-dimensional reconstruction technology, and then made by 3D printing or injection molding process. The aortic model 12 should be made of elastic and transparent material to facilitate observation of the working state of the blood pump 2 in the test, and can be made of silicone or polyurethane material. The aortic model 12 includes three branches 121 of the aortic arch and a renal artery branch 122, and two pressure monitoring points 1211 and 1212 are provided in the descending aorta; wherein the distance between the first pressure monitoring point 1211 and the second pressure monitoring point 1212 is 5-10 cm. The second pressure monitoring point 1212 is located at the intersection of the descending aorta and the renal artery, and the first pressure monitoring point 1211 is located at the upstream position of the second pressure monitoring point 1212. The pump shell 22 of the blood pump 2 is placed between the first pressure monitoring point 1211 and the second pressure monitoring point 1212, the blood pump inlet 221 is located downstream of the first pressure monitoring point 1211, and the blood pump outlet 222 is located upstream of the second pressure monitoring point. The first pressure monitoring point 1211 is used to measure the inlet pressure of the blood pump 2, and the second pressure monitoring point 1212 is used to measure the outlet pressure of the blood pump 2. The pressure monitoring points 1211 and 1212 are measured by using disposable invasive medical pressure sensors, and are fed back in real time by using a monitor or other data acquisition equipment.

[0034] Reference Figure 4 As shown in the drawings, the main body structure 131 of the adapter tool 13 is in the shape of a "cross", and has four interfaces, namely a first interface 1311, a second interface 1312, a third interface 1313 and a fourth interface 1314; wherein the first interface 1311, the second interface 1312 and the third interface 1313 have a pagoda structure to facilitate quick connection of the auxiliary pipeline 17; in addition, the first interface 1311 is connected with the first flow outlet 123 of the aortic model 12, the second interface 1312 and the third interface 1313 are connected with the auxiliary pipeline 17, and the fourth interface 1314 is used for the blood pump 2 to pass through. Figure 5 As shown in the drawings, the adapter tool 13 includes a sealing gasket 132 and a locking cap 133, which are arranged at the fourth interface 1314. The sealing gasket 132 is fixed at the fourth interface 1314 by thread connection of the locking cap 133 and the fourth interface 1314. The sealing gasket 132 is made of silicone or polyurethane material, and has a "cross" opening at the center of the sealing gasket 132, so that the blood pump 2 can pass through the adapter tool 13 and be placed in the aortic model 12.

[0035] Reference Figure 6 and Figure 7As shown, the afterload simulator 14 comprises a compliance adjuster 141, a peripheral resistance adjuster 142, a base 143, and a main channel 144; the main channel 144 is arranged inside the base 143 through the base 143, and the compliance adjuster 141 and the peripheral resistance adjuster 142 are sequentially arranged on the base 143 and connected with the main channel 144. The compliance adjuster 141 is provided with a first exhaust valve 1411, an air cavity 1412, an auxiliary channel 1413, a gland plate 1414, and a silica gel ring 1415, wherein the air cavity 1412 is communicated with the main channel 144 through the auxiliary channel 1413, the air cavity 1412 is provided with the gland plate 1414 on the side opposite to the auxiliary channel 1413, the first exhaust valve 1411 is arranged on the gland plate 1414, and the silica gel ring 1415 is arranged inside the top end of the compliance adjuster 141 and fixedly arranged by the gland plate 1414. Before the test starts, the first exhaust valve 1411 is manually opened, the air height ratio in the air cavity 1412 is adjusted, and the compliance adjustment function of the test device is realized by adjusting the gas capacity and gas pressure of the air cavity 1412. The peripheral resistance adjuster 142 comprises a valve core 1421 and a top cover 1422, the top cover 1422 is arranged through and fixed on the side wall of the main channel 144, and the valve core 1421 and the top cover 1422 are connected by threads. By rotating the handle of the valve core 1421, the valve core 1421 reciprocates in the vertical direction, so that the flow area of the main channel 144 can be controlled, and the peripheral resistance of the test device is changed. By adjusting the compliance and the peripheral resistance of the test device, the blood flow hemodynamic environment of different human bodies can be simulated, and the performance evaluation of the blood pump under various clinical conditions can be realized. In addition, the compliance and the peripheral resistance adjustment functions are integrated in the afterload simulator 14, which is convenient for the test device to be built and tested.

[0036] Reference Figure 8 As shown, the ventricular simulator 11 comprises a motor 111, a cavity 112, a second exhaust valve 113, and a piston 114. The motor 111 is directly connected with the piston 114, so that the piston 114 makes a reciprocating linear motion in the cavity 112, and the downward process and the upward retreat of the piston 114 simulate the contraction and diastole processes of the heart respectively. The motion period of the piston 114 is 0.5-1.5 s, and the time ratio of the process to the retreat ranges from 0.6 to 1.2. The output shaft of the motor 111, the piston 114, and the cavity 112 maintain high coaxiality, and the cavity 112 is fixed on the base support 18. Figure 1 As shown, the ventricular simulator 11 is provided with unidirectional valves on both sides of the inlet and outlet; wherein the first unidirectional valve 171 simulates the aortic valve and is connected with the aortic model 12; and the second unidirectional valve 172 simulates the mitral valve and is connected with the liquid storage cavity 16.

[0037] Since different patients have different sizes of aortic structures and hemodynamic characteristics, the utility model is based on the real aortic structure of human body to build a hemodynamic testing device, which is helpful to evaluate the working performance of the blood pump in different patients, and more effectively and accurately master the hemodynamic characteristics of the blood pump in the human body environment; at the same time, the testing device can be more close to the implantation state of the blood pump in the aorta, provide an in vitro test basis for precise medical treatment for different patients, and be helpful to preoperative evaluation of the renal artery perfusion effect.

[0038] The above is the preferred embodiment of the utility model and the technical principle used, for those skilled in the art, without departing from the spirit and scope of the utility model, any equivalent transformation, simple replacement, etc. based on the utility model technical scheme, the change that is obvious, all belong to the protection scope of the utility model.

Claims

1. A blood flow dynamics testing device for a heart-kidney assist blood pump, characterized by, The circulation loop comprises a ventricle simulator, an aorta model, a post-load simulator, an ultraviolet sterilization device and a liquid storage cavity connected in sequence. The ventricle simulator comprises a motor, a cavity, an exhaust valve and a piston. The aorta model comprises aortic arch three branches and a renal artery branch structure. The post-load simulator comprises a main channel, a compliance regulator and a peripheral resistance regulator connected to the main channel.

2. The hemodynamic testing device of claim 1, wherein, The ventricle simulator is provided with a first one-way valve and a second one-way valve on both sides of the inlet and outlet.

3. The hemodynamic testing device of claim 1, wherein, The piston reciprocating motion cycle of the ventricle simulator is 0.5-1.5 s.

4. The hemodynamic testing device of claim 3, wherein, The time ratio of the progress and the recession is 0.6-1.

2.

5. The hemodynamic testing device of claim 1, wherein, The first pressure monitoring point is located upstream of the renal artery branch, and the second monitoring point is located at the intersection of the renal artery branch and the descending aorta.

6. The hemodynamic testing device of claim 1, wherein, The distance between the two pressure monitoring points is 5-10 cm.

7. The hemodynamic testing device according to claim 1 or 6, characterized in that The two pressure monitoring points are measured by disposable invasive medical pressure sensors and are fed back in real time by a monitor or other data acquisition equipment.

8. The hemodynamic testing device of claim 1, wherein, The main body structure of the adapter tool is cross-shaped and has four interfaces.

9. The hemodynamic testing device of claim 8, wherein, The fourth interface of the adapter tool is provided with a sealing gasket and a locking cap.

10. The hemodynamic testing device of claim 1, wherein, The compliance regulator comprises an auxiliary channel communicating with the main channel and an air cavity communicating with the auxiliary channel. The peripheral resistance regulator comprises a valve core and a top cover. The top cover is fixed on the main channel, and the valve core is threadedly connected with the top cover. The valve core reciprocates in the vertical direction to control the flow area of the main channel and change the peripheral resistance of the test device.

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