Blood circulation simulator of aneurysm simulation device

Abstract

The utility model discloses a blood circulation simulator of an aneurysm simulation device. The blood circulation simulator comprises a shell, a driving shaft, a deflection disc and a pump body, a cavity is formed in the shell, and the driving shaft, the deflection disc and the pump body are arranged in the cavity. A deflection disc is movably arranged at the end part of the driving shaft; the deflection disc can continuously adjust the angle between the deflection disc and the driving shaft; the pump body is movably connected to the lower portion of the deflection disc and can be driven by the driving shaft to rotate so as to pump simulation liquid. The mode that rotating speed control is matched with plunger stroke length control is adopted, the control air cylinder connected with the deflection disc is arranged in the shell and can control the inclination angle of the deflection disc, then the stroke length of a pump column in the pump body is controlled, the rotating speed of the rotating disc located at the bottom of the deflection disc is adjusted in cooperation with the driving shaft, and therefore the pumping frequency of the pump column is adjusted. The effect of finely controlling the pumping amount is achieved, and therefore accurate dynamic simulation of blood pressure changes is achieved.

Description

Technical Field

[0001] The utility model relates to the technical field of medical equipment, in particular to a blood circulation simulator of an aneurysm simulation device. Background Art

[0002] An aneurysm simulation device is an in vitro model of an aneurysm with realistic proportions and morphology constructed using imaging and 3D printing technologies. In order to study the characteristics of an aneurysm and prepare for surgery, it is usually necessary to simulate blood circulation within the in vitro model, that is, a blood pump is required to establish blood circulation within the in vitro model.

[0003] Since the human heart circulates blood through the body through the movement and contraction of the heart muscle, a simulator with a plunger pump structure is typically used to simulate the heart's operation and establish blood circulation in an in vitro model. During the simulation process, the pump displacement of the simulator is typically adjusted by controlling the speed of the plunger pump structure to simulate changes in human blood pressure. Although this method of adjusting the pump displacement by controlling the speed of the plunger pump structure can achieve the effect of regulating blood pressure, human blood pressure typically fluctuates slightly between 80 and 140 mmHg. The pump displacement of the plunger pump structure is positively correlated with its swash plate inclination angle (i.e., plunger stroke length) and speed. Therefore, adjusting the speed to control the pumping volume while keeping the plunger stroke length unchanged results in a large difference in pumping volume for each unit change in speed. That is, for every unit increase or decrease in speed, the pumping volume changes significantly, making it difficult to accurately adjust the pumping volume to accurately simulate dynamic blood pressure changes.

[0004] Therefore, the existing blood circulation simulator that uses the internal plunger pump structure to control the rotation speed to simulate the dynamic changes in blood pressure is difficult to finely adjust the pumping volume of its internal plunger pump structure, resulting in a large change in the pumping volume during the adjustment process, which affects the blood pressure change range and thus affects the effect of in vitro model simulation. Utility Model Content

[0005] The purpose of the present utility model is to provide a blood circulation simulator for an aneurysm simulation device, so as to solve the technical problem in the prior art that the pumping volume of the internal plunger pump structure is finely adjusted, resulting in a large change in the pumping volume during the adjustment process, affecting the change in blood pressure, and thus affecting the effect of in vitro model simulation.

[0006] In order to solve the above technical problems, the present invention specifically provides the following technical solutions:

[0007] A blood circulation simulator device for an aneurysm simulation device, comprising:

[0008] A shell, wherein a liquid inlet and a liquid outlet are provided on one side of the shell and a cavity is formed inside the shell;

[0009] A drive shaft, a deflection disk, and a pump body are provided inside the cavity. The deflection disk is movably connected to the end of the drive shaft and can be continuously adjusted to change the inclination angle between the deflection disk and the drive shaft. The lower portion of the deflection disk is movably connected to the pump body. The pump body can rotate with the deflection disk under the drive of the drive shaft, thereby generating a pressure difference to drive the simulated liquid to flow.

[0010] Among them, the pump body includes a main body and several pump columns movably arranged inside the main body. The pump columns are movably connected to the deflection disk. When the pump body rotates with the deflection disk, the pump columns can perform piston motion in the main body, thereby pumping simulated liquid. At the same time, the deflection disk movably adjusts the inclination angle, adjusts the stroke length of the pump column, and cooperates with the drive shaft to adjust the speed and adjust the pumping frequency of the pump column, thereby finely adjusting the pumping volume of the simulated liquid, thereby accurately simulating the dynamic changes of blood pressure.

[0011] As a preferred solution of the present invention, the deflection disk includes an outer adjustment disk and an inner rotating disk, the drive shaft can directly drive the rotating disk to rotate, and the adjustment disk can adjust the inclination angle of the rotating disk;

[0012] The rotating disk and the pump column are connected via a ball and socket joint.

[0013] As a preferred solution of the present invention, one side of the adjustment disk has a connecting piece, the side of the connecting piece facing the pump body is provided with a control cylinder, and the other side is provided with a spring, and the control cylinder can be telescopically adjusted to adjust the inclination angle of the deflection disk.

[0014] As a preferred solution of the present invention, the cylinder rod end of the control cylinder is rotatably connected to the connecting piece, and the cylinder body end thereof is rotatably arranged on one side of the pump body.

[0015] As a preferred solution of the present invention, an arc-shaped rack is fixedly provided at the center of the adjusting disk, the teeth of the rack are distributed on the inner side, and a rotating gear is provided on the driving shaft. The rotating gear is engaged with the rack and can rotate back and forth to adjust the inclination angle of the adjusting disk.

[0016] As a preferred solution of the present invention, the central angle of the rack is greater than or equal to 180 degrees, and the diameter of the rotating gear is less than or equal to the radius of the rack.

[0017] Compared with the prior art, the present invention has the following beneficial effects:

[0018] The utility model adopts a method of speed control combined with plunger stroke length control. A control cylinder connected to the deflection disk is set in the shell, so that it can control the inclination angle of the deflection disk, and then control the stroke length of the pump column in the pump body. The drive shaft is used to adjust the speed of the rotating disk located at the bottom of the deflection disk, thereby adjusting the pumping frequency of the pump column, achieving the effect of fine control of the pumping volume, and thus realizing accurate dynamic simulation of blood pressure changes. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] To more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for the embodiments or the description of the prior art. Obviously, the drawings described below are merely illustrative, and those skilled in the art can, without inventive effort, derive other implementation drawings based on the provided drawings.

[0020] Figure 1 A schematic structural diagram of a blood circulation simulator for an aneurysm simulation device is provided for an embodiment of the present utility model;

[0021] Figure 2 A partial structural diagram of embodiment 1 is provided for the embodiment of the present utility model;

[0022] Figure 3 A partial structural diagram of embodiment 2 is provided for the embodiment of the present utility model;

[0023] Figure 4 A partial structural schematic diagram of a pump column is provided for an embodiment of the utility model.

[0024] The numbers in the figure represent the following:

[0025] 1-shell; 2-chamber; 3-drive shaft; 4-deflection plate; 5-pump body;

[0026] 11-liquid inlet; 12-liquid outlet; 31-rotating gear; 41-adjusting disk; 42-rotating disk; 43-connecting piece; 44-control cylinder; 45-spring; 46-rack; 51-main body; 52-pump column. DETAILED DESCRIPTION

[0027] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the embodiments described are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0028] like Figure 1As shown, the utility model provides a blood circulation simulator of an aneurysm simulation device, comprising:

[0029] The housing 1 has a liquid inlet 11 and a liquid outlet 12 on one side, and a cavity 2 inside.

[0030] The cavity 2 is provided with a drive shaft 3, a deflection plate 4, and a pump body 5. The deflection plate 4 is movably connected to the end of the drive shaft 3 and can be continuously adjusted to change the inclination angle between the deflection plate 4 and the drive shaft 3. The lower part of the deflection plate 4 is movably connected to the pump body 5. The pump body 5 can rotate with the deflection plate 4 under the drive of the drive shaft 3, forming a pressure difference to drive the flow of the simulated liquid.

[0031] Among them, the pump body 5 includes a main body 51 and several pump columns 52 movably arranged inside the main body 51. The pump columns 52 are movably connected to the deflection disk 4. When the pump body 5 rotates with the deflection disk 4, the pump columns 52 can perform piston motion in the main body 51, thereby pumping the simulated liquid. At the same time, the deflection disk 4 movably adjusts the inclination angle, adjusts the stroke length of the pump columns 52, and cooperates with the drive shaft 3 to adjust the speed and adjust the pumping frequency of the pump columns 52, thereby finely adjusting the pumping volume of the simulated liquid, thereby accurately simulating the dynamic changes of blood pressure.

[0032] This embodiment mainly drives the pump body 5 to rotate by the drive shaft 3, thereby forming a pressure difference to pump the simulated liquid in the cavity 2 to the liquid outlet 12. During the pumping process, the inclination angle of the deflection plate 4 is adjusted, and the speed is adjusted in conjunction with the drive shaft 3 to achieve precise adjustment of the pumping volume of the pump body 5, thereby accurately simulating the dynamic changes of human blood pressure.

[0033] Among them, the interior of the pump column 52 is a hollow structure that gradually widens from narrow. A movable ball is provided inside the pump column 52, and a through pipe is provided on one side of the movable ball. The outer sleeve of the through pipe is provided with an elastic spring. As the pump column 52 performs piston motion in the main body 51, the movable ball can move back and forth between the internal cavity change area and the through pipe mouth under the action of hydraulic pressure and elastic spring, thereby achieving the effect of pumping simulated liquid.

[0034] like Figure 2 As shown, the deflection disk 4 includes an outer adjustment disk 41 and an inner rotating disk 42. The driving shaft 3 can directly drive the rotating disk 42 to rotate, and the adjustment disk 41 can adjust the inclination angle of the rotating disk 42.

[0035] The rotating disk 42 and the pump column 52 are connected via a ball and socket joint.

[0036] The driving shaft 3 drives the pump body 5 to rotate via the rotating disk 42 , and at the same time, the inclination angle of the rotating disk 42 is changed by the movement of the adjusting disk 41 , thereby changing the pumping volume of the pump body 5 .

[0037] In order to realize the movable adjustment of the adjustment disk 41, the following two embodiments are proposed.

[0038] Example 1:

[0039] like Figure 2 As shown, one side of the adjustment disk 41 has a connecting piece 43 , and the side of the connecting piece 43 facing the pump body 5 is provided with a control cylinder 44 , and the other side thereof is provided with a spring 45 . The control cylinder 44 can be telescopically adjusted to adjust the inclination angle of the deflection disk 4 .

[0040] The end of the cylinder rod of the control cylinder 44 is rotatably connected to the connecting piece 43 , and the end of the cylinder body thereof is rotatably arranged on one side of the pump body 5 .

[0041] Specifically, the expansion and contraction adjustment of the control cylinder 44 is carried out, and the inclination angle of the adjustment disk 41 is changed through the connecting piece 43, thereby changing the pumping volume of the pump body 5, and the expansion and contraction rate of the adjustment cylinder 44 can be set to simulate the change of human blood pressure.

[0042] Example 2:

[0043] like Figure 3 As shown, an arc-shaped rack 46 is fixedly provided at the center of the adjusting disk 41, and the teeth of the rack 46 are distributed on the inner side. A rotating gear 31 is provided on the driving shaft 3, and the rotating gear 31 is engaged with the rack 46 and can be rotated back and forth to adjust the inclination angle of the adjusting disk 41.

[0044] The central angle of the rack 46 is greater than or equal to 180 degrees, and the diameter of the rotating gear 31 is less than or equal to the radius of the rack 46 .

[0045] Specifically, the rotating gear 31 drives the rack 46 to rotate to adjust the inclination angle of the regulating disk 41, thereby changing the pumping volume of the pump body 5, and the reciprocating rotation rate of the driving gear 31 can be set to simulate the dynamic changes of human blood pressure.

[0046] Among them, the central angle of the rack 46 is greater than or equal to 180 degrees, and the diameter of the rotating gear 31 is less than or equal to the radius of the rack 46. However, in order to prevent the rotation speed required for the rotating gear 31 from being too fast and to prevent the adjustment angle from being too large, which may cause the deflection disk 4 to collide with the drive shaft 3, the central angle of the rack 46 should be controlled within a smaller range, and the diameter of the rotating gear 31 should be set relatively large to control the adjustment range of the deflection disk 4 and the rotation speed of the rotating gear 31.

[0047] When this embodiment is working, the drive shaft 3 drives the pump body 5 to rotate and pump the simulated liquid through the deflection disk 4. At the same time, the telescopic cylinder 44 telescopes and adjusts the inclination angle of the adjustment disk 41, so that the pumping volume changes dynamically within a certain range. When the telescopic cylinder 44 adjusts the angle between the deflection disk 41 and the drive shaft 3 to be close to 90 degrees, the single stroke of the pump column 51 is the shortest, and the pumping volume of the simulated liquid is also small. The effect of adjusting the rotation speed of the drive shaft 3 on the pumping volume is also low. At this time, adjusting the rotation speed of the drive shaft 3 allows the telescopic cylinder 44 to adjust the pumping volume of the pump body 5 within a new range.

[0048] The above embodiments are merely exemplary embodiments of the present application and are not intended to limit the scope of the present application. The scope of protection of the present application is defined by the claims. Those skilled in the art may make various modifications or equivalent substitutions to the present application within the essence and scope of protection of the present application, and such modifications or equivalent substitutions shall also be deemed to fall within the scope of protection of the present application.

Claims

1. A blood circulation simulator for an aneurysm simulation device, characterized in that: include: A housing (1), wherein a liquid inlet (11) and a liquid outlet (12) are provided on one side of the housing (1), and a cavity (2) is provided inside the housing (1); A drive shaft (3), a deflection disk (4) and a pump body (5) are provided inside the cavity (2); the deflection disk (4) is movably connected to the end of the drive shaft (3) and can be continuously adjusted to change the inclination angle between the deflection disk (4) and the drive shaft (3); the deflection disk (4) is movably connected to the pump body (5) at the bottom; the pump body (5) can rotate with the deflection disk (4) under the drive of the drive shaft (3), thereby forming a pressure difference to drive the simulated liquid to flow; The pump body (5) includes a main body (51) and a plurality of pump columns (52) movably arranged inside the main body (51), and the pump columns (52) are connected to the deflection disk (4) through a ball joint. When the pump body (5) rotates with the deflection disk (4), the pump columns (52) can perform piston motion in the main body (51) to pump the simulated liquid. At the same time, the deflection disk (4) can movably adjust the inclination angle to adjust the stroke length of the pump columns (52), and cooperate with the drive shaft (3) to adjust the speed and adjust the pumping frequency of the pump columns (52), thereby finely adjusting the pumping volume of the simulated liquid and accurately simulating the dynamic changes of blood pressure.

2. The blood circulation simulator of the aneurysm simulation device according to claim 1, characterized in that: The deflection disk (4) comprises an outer adjustment disk (41) and an inner rotating disk (42); the driving shaft (3) can directly drive the rotating disk (42) to rotate; and the adjustment disk (41) can adjust the inclination angle of the rotating disk (42); The rotating disk (42) and the pump column (52) are connected via a ball-and-socket joint.

3. The blood circulation simulator of the aneurysm simulation device according to claim 2, characterized in that: One side of the adjusting disk (41) is provided with a connecting piece (43), and the side of the connecting piece (43) facing the pump body (5) is provided with a control cylinder (44), and the other side thereof is provided with a spring (45). The control cylinder (44) can be telescopically adjusted to adjust the inclination angle of the deflection disk (4).

4. The blood circulation simulator of the aneurysm simulation device according to claim 3, characterized in that: The cylinder rod end of the control cylinder (44) is rotatably connected to the connecting member (43), and the cylinder body end thereof is rotatably arranged on one side of the pump body (5).

5. The blood circulation simulator of the aneurysm simulation device according to claim 2, characterized in that: An arc-shaped rack (46) is fixedly provided at the center of the adjusting disk (41), and the gear teeth of the rack (46) are distributed on the inner side. A rotating gear (31) is provided on the driving shaft (3), and the rotating gear (31) is engaged with the rack (46) and can be rotated back and forth to adjust the inclination angle of the adjusting disk (41).

6. The blood circulation simulator of the aneurysm simulation device according to claim 5, characterized in that: The central angle of the rack (46) is greater than or equal to 180 degrees, and the diameter of the rotating gear (31) is less than or equal to the radius of the rack (46).

Images