Bandage type external counterpulsation device and system thereof

Abstract

According to the bandage type external counterpulsation device and the bandage type external counterpulsation system, the extrusion force can be accurately controlled, and the noise is small, a motor is arranged in a machine box, and a binding belt and a winding shaft are arranged above the machine box; the motor drives the winding shaft to rotate forwards to wind the bandage on the outer ring of the binding belt through the transmission mechanism so as to reduce the area of the winding and binding area or rotate backwards to release the binding belt so as to increase the area of the winding and binding area. Compared with a traditional air bag inflation pressurization mode for controlling the extrusion force, the motor control precision is higher, response is more timely, and the external counterpulsation effect is ensured. Compared with a traditional air bag inflation pressurization mode for controlling the extrusion force, the motor control precision is higher, response is more timely, and the external counterpulsation effect is ensured. Meanwhile, the motor and the binding belt are arranged up and down, the whole device is small in occupied area, and the case is not only a container for containing the motor, but also equivalent to a trolley and is convenient to move.

Description

Technical Field

[0001] The utility model relates to the technical field of external counterpulsation equipment, in particular to a bandage-type external counterpulsation device and a system thereof. Background Art

[0002] EECP is a method of non-invasively pressing the lower body externally to relieve and eliminate angina symptoms and improve the hypoxic-ischemic state of important organs of the body. It is also a medical device used to prevent and treat cardiovascular and cerebrovascular diseases. Traditional EECP devices use air bags wrapped around the limbs and buttocks to inflate and pressurize the air bags during the diastole of the heart, prompting blood from the limb arteries and veins to return to the heart, significantly increasing diastolic pressure, improving blood perfusion of important organs such as the heart and brain, and reducing cardiac afterload; during the systole of the heart, the air bags are quickly deflated, the pressure is relieved, and the systolic pressure in the aorta is reduced, minimizing the resistance of the heart's ejection phase, and accelerating the blood flow to the distal end, thereby achieving the counterpulsation effect.

[0003] However, the traditional airbag inflation and pressurization method does not accurately control the extrusion force and has a slow speed response. Specifically, the airbag inflation and pressurization process is a gas compression transfer process, that is, the movement of gas in the gas path is a pressure equalization process under the condition of pressure difference. Compared with contact-type mechanical extrusion, this process has a slower response speed; at the same time, since the gas path pressure change is nonlinear, the control is more complicated. Utility Model Content

[0004] One purpose of the utility model is to provide a bandage-type external counterpulsation device which can accurately control the squeezing force and has low noise.

[0005] In order to achieve the above-mentioned purpose, the technical solution adopted by the utility model is: a bandage-type external counterpulsation device, a motor is arranged in the chassis, a binding belt and a winding shaft are arranged above the chassis, the motor drives the winding shaft through a transmission mechanism to rotate the bandage around the outer ring of the binding belt forward to reduce the area of ​​the binding area or reversely release the binding belt to increase the area of ​​the binding area.

[0006] The transmission mechanism comprises a driving pulley arranged at the end of the motor shaft and a driven pulley arranged at the end of the winding shaft. The driving pulley and the driven pulley are matched with each other through a synchronous belt to form a belt transmission. The end of the bandage is fixed on the winding shaft.

[0007] A guide roller group is also rotatably arranged above the chassis, the axis of the guide roller group is parallel to the axis of the winding shaft, and the middle section of the bandage is sandwiched in the gap between the rollers of the guide roller group to form a sliding and guiding fit.

[0008] The inner wheel surfaces of the driving pulley and the driven pulley are both provided with teeth, and the synchronous belt is also provided with a rack correspondingly, and the teeth and the rack mesh to form a synchronous transmission.

[0009] The binding belt is a double-layer structure, including an inner airbag and an outer bandage. The bandage is made of a non-compliant material, and the bandage is wrapped around the periphery of the airbag and passes through a guide roller group.

[0010] The guide roller groups are arranged on both sides of the airbag, and each guide roller group includes at least two guide rollers.

[0011] Two binding belts are symmetrically arranged above the chassis, and the bandages of the two binding belts are fixed on the same winding shaft. When the motor drives the winding shaft to rotate, the two binding belts synchronously reduce or release the winding area.

[0012] The chassis is provided with a base, and the base is provided with an arc-shaped groove with an opening facing upwards. The binding belt is arranged in the arc-shaped groove, and the winding shaft is arranged at the symmetrical midline position of the two arc-shaped grooves.

[0013] One purpose of the utility model is to provide a bandage-type external counterpulsation system which can accurately control the squeezing force and has low noise.

[0014] In order to achieve the above-mentioned purpose, the technical solution adopted by the utility model is: a bandage-type external counterpulsation system, the airbag is connected to the air pump through a pipeline, the control system adjusts the pre-charge volume of the airbag according to the thickness of the patient's limbs, the pressure sensor collects the pressure of the airbag on the limbs and feeds it back to the control system, and the control system controls the motor to transmit a winding signal, a holding signal and a release signal to the motor in sequence within a cardiac pacing cycle.

[0015] In the above scheme, the patient's limbs are wrapped with a strap, and the motor drives the winding shaft to wind the strap to squeeze the user's limbs. The structure is simple and can effectively achieve orderly squeezing and pressure relief of the user's limbs. Compared with the traditional airbag inflation and pressurization method to control the squeezing force, the motor control accuracy is higher and the response is more timely, ensuring the effect of external counterpulsation. At the same time, the motor and the strap are arranged in upper and lower positions, and the entire device occupies a small area. The chassis is not only a container for accommodating the motor, but also equivalent to a trolley, which is easy to move. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] Figure 1 is a stereoscopic diagram of an external counterpulsation device;

[0017] Figure 2 for Figure 1 The main view of

[0018] Figure 3 for Figure 1 The structural diagram in which the chassis is removed;

[0019] Figure 4 for Figure 1 Right view of;

[0020] Figure 5 for Figure 4 AA section view. DETAILED DESCRIPTION

[0021] Combine the following Figure 1-Figure 5 The utility model is further described in detail.

[0022] A bandage-type external counterpulsation device is provided. A motor 20 is provided in a case 10. A binding belt 30 and a winding shaft 40 are provided above the case 10. The motor 20 drives the winding shaft 40 through a transmission mechanism 50 to rotate the bandage 31 of the outer circle of the binding belt 30 forward to reduce the area of ​​the binding area or reversely release the binding belt 30 to increase the area of ​​the binding area. In the utility model, the patient's limbs are wrapped by the binding belt 30, and the motor 20 drives the winding shaft 40 to wind the binding belt 30 to achieve compression of the user's limbs. The structure is simple and can effectively achieve orderly compression and pressure release of the user's limbs. Compared with the traditional method of controlling the compression force by inflating and pressurizing the airbag, the motor control accuracy is higher and the response is more timely, ensuring the effect of the external counterpulsation. In addition, the air pump, the complex solenoid valve and the connecting pipeline are eliminated. The whole system structure is simple and the working noise is small.

[0023] At the same time, the motor 20 and the binding belt 30 are arranged in upper and lower positions, so that the entire device occupies a small area. The chassis 10 is not only a container for accommodating the motor 20, but also equivalent to a trolley, which is easy to move. The height of the chassis 10 can be set to be the same as the height of an ordinary bed. When in use, the counterpulsation device can be directly moved to the end of the bed to perform counterpulsation treatment on the patient.

[0024] Furthermore, the transmission mechanism 50 includes a driving pulley 51 disposed at the end of the motor 20 shaft and a driven pulley 52 disposed at the end of the winding shaft 40 shaft. The driving pulley 51 and the driven pulley 52 form a belt drive through a synchronous belt 53, and the end of the bandage 31 is fixed on the winding shaft 40. The synchronous belt transmission method is used to transmit the power of the motor 20 located below to the winding shaft 40 above. The synchronous belt transmission method has at least the following advantages: (1) accurate transmission ratio, no slippage, and small force on the shaft during transmission; (2) compact structure, good oil resistance, wear resistance, and good anti-aging performance; (3) with buffering and shock absorption capabilities, low noise; (4) high transmission efficiency, which can reach 98%. These advantages are particularly beneficial to the extracorporeal counterpulsation device and are conducive to improving the effect of extracorporeal counterpulsation.

[0025] In order to effectively squeeze the binding band 30, a guide roller group 54 is also rotatably arranged on the top of the chassis 10, and the axis of the guide roller group 54 is parallel to the axis of the winding shaft 40. The middle section of the bandage 31 is sandwiched between the rollers of the guide roller group 54 to form a sliding and guiding fit. The guide roller group 54 has the functions of reversing and guiding. On the one hand, it is conducive to the winding and releasing of the bandage 31, ensuring that the bandage 31 can return to its original state after each winding and release; on the other hand, it will not pull the airbag 32 to one side, ensuring the position of the airbag 32; it can also increase the contact area between the bandage 31 and the outer surface of the airbag 32, so that the squeezing force on the airbag 32 is more uniform, improving the anti-pulling effect.

[0026] In order to prevent the transmission mechanism from slipping, teeth a are provided on the inner wheel surfaces of the driving pulley 51 and the driven pulley 52, and racks b are correspondingly provided on the synchronous belt 53. The teeth a and racks b mesh to form synchronous transmission. There is no slipping between the pulley and the synchronous belt, the transmission ratio is accurate during transmission, and the force acting on the shaft is small, thereby ensuring the stable extrusion force on the binding belt 30 and improving the anti-pulling effect.

[0027] Preferably, the bandage 30 is a double-layer structure, including an inner airbag 32 and an outer bandage 31. The bandage 31 is a non-compliant material. The bandage 31 is wrapped around the periphery of the airbag 32 and passes through the guide roller group 54. The function of the bandage 30 is to wrap around the patient's limbs and squeeze the patient's limbs under the action of the winding shaft 40 to achieve counterpulsation. As the inner layer 11 of the bandage 30 directly acts on the patient's limbs, it uses a medical airbag, which can prevent long-term friction from causing abrasions on the skin of the patient's limbs, or reduce other unexpected situations. Direct compression of the patient's limbs; in addition, by providing a medical airbag with flexible characteristics, it also helps to make the pressure on the patient's legs uniform and improve the counterpulsation treatment effect; the outer bandage 31 is a non-compliant material and is inelastic.

[0028] In order to further improve the effect, the guide roller group 54 is provided on both sides of the airbag 32, and each guide roller group 54 includes at least two guide rollers 541. The structure shown in the figure is only a specific embodiment of the guide roller group 54, and other settings that can reasonably guide the bandage 31 are also possible. On the one hand, it is conducive to the winding and release of the bandage 31, ensuring that the bandage 31 can be restored to its original state after each winding and release; on the other hand, the airbag 32 will not be pulled to one side, ensuring the position of the airbag 32; it can also increase the contact area between the bandage 31 and the outer surface of the airbag 32, so that the extrusion force on the airbag 32 is more uniform, improving the anti-pulling effect.

[0029] The principle of external counterpulsation is to apply pressure to the limbs during the diastole of the heart, so that the blood in the limb arteries and veins returns to the heart, so that the diastolic pressure is significantly increased, the blood perfusion of important organs such as the heart and brain is improved, and the afterload of the heart is reduced; during the systole of the heart, the limbs are decompressed, the pressure is released, the systolic pressure in the aorta is reduced, the resistance of the heart ejection phase is reduced to the maximum extent, and the blood flows to the distal end at an accelerated speed, thereby achieving the counterpulsation effect. Therefore, it is necessary to squeeze and release the pressure of the patient's two limbs (legs) at the same time. In order to achieve the above purpose, the binding belt 30 is symmetrically arranged above the chassis 10, and the bandages 31 of the two binding belts 30 are fixed on the same winding shaft 40. When the motor 20 drives the winding shaft 40 to rotate, the two binding belts 30 synchronously reduce or release the area of ​​the winding area. The same motor 20 is used to synchronously wind the two bandages 31 to ensure that the two legs are squeezed and decompressed at the same time, thereby improving the counterpulsation effect.

[0030] In order to support the straps 30 and the limbs, a base 60 is provided on the chassis 10. The base 60 is provided with an arc-shaped groove with an opening facing upward to support the limbs. The straps 30 are arranged in the arc-shaped groove, and the winding shaft 40 is arranged at the symmetrical midline position of the two arc-shaped grooves, thereby ensuring that the winding / releasing lengths of the two straps 31 at the same time are exactly the same, that is, the squeezing force on the limbs is exactly the same.

[0031] A bandage-type external counterpulsation system, wherein the airbag 32 is connected to an air pump through a pipeline, and the control system adjusts the pre-charge volume of the airbag 32 according to the thickness of the patient's limbs. The pressure sensor collects the pressure of the airbag 32 on the limbs and feeds it back to the control system. The control system controls the motor 20 to transmit a winding signal, a holding signal and a release signal to the motor 20 in sequence within a cardiac pacing cycle.

[0032] When the ECG signal sensor detects the arrival of the R wave, the control system sends a winding signal to the controller of the motor 20, and the pressure sensor measures the pressure of the airbag 32 on the limbs in real time. When the pressure reaches the specified pressure value, the control system sends the holding signal to the controller of the motor 20. After the pressure is maintained for a certain period of time, the control system sends a release signal to the controller of the motor 20, and the external counterpulsation is realized in a cycle. It should be particularly noted that before counterpulsation, the pre-charge amount of the airbag 32 is adjusted according to the thickness of the patient's limbs to ensure that the initial pressure for different patients is consistent. The precise squeezing of the limbs can be achieved by setting the winding angle of the winding shaft 20, and the real-time monitoring of the pressure sensor can be coordinated to further improve the counterpulsation effect.

[0033] It should also be noted that the various specific technical features described in the above specific embodiments can be combined in any suitable manner without contradiction. In order to avoid unnecessary repetition, the present invention will not further describe various possible combinations. In addition, the various different embodiments of the present invention can also be combined arbitrarily, as long as they do not violate the idea of ​​the present invention, they should also be regarded as the contents disclosed by the present invention.

Claims

1. A bandage-type external counterpulsation device, characterized in that: A motor (20) is arranged in the chassis (10), and a binding belt (30) and a winding shaft (40) are arranged above the chassis (10). The motor (20) drives the winding shaft (40) through a transmission mechanism (50) to rotate the bandage (31) wound around the outer ring of the binding belt (30) in a forward direction to reduce the area of ​​the binding area, or to rotate the binding belt (30) in a reverse direction to release the binding belt (30) to increase the area of ​​the binding area.

2. The bandage-type external counterpulsation device according to claim 1, characterized in that: The transmission mechanism (50) comprises a driving pulley (51) arranged at the shaft end of the motor (20) and a driven pulley (52) arranged at the shaft end of the winding shaft (40), and a belt transmission is formed between the driving pulley (51) and the driven pulley (52) via a synchronous belt (53). The end of the bandage (31) is fixed on the winding shaft (40), and the width of the bandage (31) is parallel to the axial direction of the winding shaft (40).

3. The bandage-type external counterpulsation device according to claim 2, characterized in that: The transmission mechanism (50) further comprises a guide roller group (54) rotatably arranged above the chassis (10), wherein the axis of the guide roller group (54) is parallel to the axis of the winding shaft (40), and the middle section of the bandage (31) is sandwiched in the gap between adjacent rollers of the guide roller group (54) to form a sliding and guiding fit.

4. The bandage-type external counterpulsation device according to claim 2, characterized in that: The inner wheel surfaces of the driving pulley (51) and the driven pulley (52) are both provided with teeth (a), and the synchronous belt (53) is also correspondingly provided with a rack (b), and the teeth (a) and the rack (b) are meshed to form synchronous transmission.

5. The bandage-type external counterpulsation device according to claim 3, characterized in that: The binding belt (30) is a double-layer structure, comprising an inner airbag (32) and an outer bandage (31). The bandage (31) is made of a non-compliant material. The bandage (31) is wrapped around the periphery of the airbag (32) and passes through the guide roller group (54).

6. The bandage-type external counterpulsation device according to claim 5, characterized in that: The guide roller groups (54) are arranged on both sides of the airbag (32), and each guide roller group (54) includes at least two guide rollers (541).

7. The bandage-type external counterpulsation device according to claim 5, characterized in that: Two binding belts (30) are symmetrically arranged above the chassis (10), and the bandages (31) of the two binding belts (30) are fixed on the same winding shaft (40). When the motor (20) drives the winding shaft (40) to rotate, the two binding belts (30) simultaneously reduce or release the area of ​​the binding area.

8. The bandage-type external counterpulsation device according to claim 7, characterized in that: The chassis (10) is provided with a base (60), the base (60) is provided with an arc-shaped groove with an opening facing upward, the binding belt (30) is arranged in the arc-shaped groove, and the winding shaft (40) is arranged at the symmetrical midline position of the two arc-shaped grooves.

9. A bandage-type external counterpulsation system, comprising the bandage-type external counterpulsation device according to any one of claims 1 to 8, characterized in that: The airbag (32) is connected to the air pump via a pipeline, the control system adjusts the pre-filling amount of the airbag (32) according to the thickness of the patient's limb, the pressure sensor collects the pressure of the airbag (32) on the limb and feeds it back to the control system, and the control system controls the motor (20) to transmit a winding signal, a holding signal and a release signal to the motor (20) in sequence within a cardiac pacing cycle.

Images