Compression hemostasis device for errhysis after central venous catheter intubation

Abstract

The invention discloses a compression hemostasis device for errhysis after central venous catheter intubation, and relates to the technical field of medical treatment, the compression hemostasis device comprises a body, an arc-shaped guide plate fixed at the bottom in the body and a driving part mounted on the arc-shaped guide plate; the first arc-shaped fixing plate is elastically arranged at the output end of the driving part and is driven by the driving part to be radially and elastically compressed. By arranging the elastic energy storage bag and the compression bag, a contact compression state can be kept all the time, compression failure caused by separation of the compression bag and a puncture point in the pressure relief process is effectively avoided, meanwhile, the compression hemostasis stability is further effectively kept and the compression hemostasis effect is improved while the compression hemostasis device adapts to external pressure changes, and the compression hemostasis effect is improved. Pressure mutation in the whole compression period can be dealt with, so that pressure stability of the compression area is dynamically maintained, the compression area is in dynamic balance, and the problem that a patient feels uncomfortable due to pressure mutation is effectively solved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical treatment, in particular to a compression hemostasis device for blood leakage after central venous catheterization. BACKGROUND

[0002] After central venous catheterization, blood leakage often occurs at the catheterization site, which is usually below the clavicle. Generally, a salt bag and gauze are bound to the catheterization site by a bandage for compression hemostasis or artificial assistance is used for compression hemostasis. However, the applied pressure completely depends on the experience of medical staff, which is difficult to quantify and has poor stability. Too little pressure may lead to incomplete hemostasis, and too much pressure may easily cause local skin ischemia, necrosis or nerve compression injury. Moreover, when the patient coughs, changes body position or central venous pressure fluctuates, the intrathoracic pressure suddenly rises, which may cause instantaneous insufficient local compression force to lead to blood leakage, and after the pressure is relieved, the effective compression cannot be automatically restored. SUMMARY

[0003] In view of the deficiencies in the prior art, the present application provides a compression hemostasis device for blood leakage after central venous catheterization.

[0004] In order to achieve the above-mentioned purpose, the technical scheme of the present application is as follows:

[0005] A compression hemostasis device for blood leakage after central venous catheterization, comprising:

[0006] a body, an arc-shaped guide plate fixed to the inner bottom of the body, and a driving member installed on the arc-shaped guide plate;

[0007] a first arc-shaped fixed plate elastically arranged at the output end of the driving member, which is driven to be elastically compressed radially by the driving member;

[0008] a compression sac fixed to the inner wall of the first arc-shaped fixed plate and in an initial state of extreme inflation, which moves synchronously with the first arc-shaped fixed plate and compresses the end portion against the catheterization area of the patient;

[0009] a pressure balance unit, comprising:

[0010] an elastic energy storage sac in parallel communication with the compression sac to form a closed air path;

[0011] a first pressure differential valve and a second pressure differential valve, the compression sac, the first pressure differential valve, the elastic energy storage sac and the second pressure differential valve are connected in sequence through an air path to form a closed one-way gas circulation loop;

[0012] When the pressure outside the compression bag increases suddenly and the pressure inside the compression bag exceeds the opening threshold of the first pressure difference valve, the first pressure difference valve opens to allow the gas in the compression bag to flow into the elastic energy storage bag through the first pressure difference valve and to make the elastic energy storage bag expand elastically to store energy, and the pressure inside the compression bag decreases synchronously.

[0013] When the pressure outside the compression bag increases suddenly and the pressure inside the compression bag exceeds the opening threshold of the first pressure difference valve, the first pressure difference valve opens to allow the gas in the compression bag to flow into the elastic energy storage bag through the first pressure difference valve and to make the elastic energy storage bag expand elastically to store energy, and the pressure inside the compression bag decreases synchronously.

[0014] Preferably, the opening threshold of the first pressure difference valve is greater than the stable pressure inside the compression bag in the initial compression state.

[0015] Preferably, the compression bag is provided with at least three compression bags, which are uniformly distributed along the circumference of the arc-shaped guide plate to form a C-shaped pressing surface to wrap the intubation area in the shape of a pipeline.

[0016] Preferably, the compression bag is a corrugated and telescopic air bag to realize directional contraction.

[0017] Preferably, the compression bag and the elastic energy storage bag are connected in parallel through the air inlet pipe and the air outlet pipe, the first pressure difference valve is arranged in the air inlet pipe, and the second pressure difference valve is arranged in the air outlet pipe to form a closed one-way gas circulation loop.

[0018] Preferably, the first pressure difference valve comprises a first one-way valve and a first conical valve arranged elastically.

[0019] Preferably, the second pressure difference valve comprises a second one-way valve and a second conical valve arranged elastically.

[0020] Preferably, the pressing end of the compression bag is fixedly provided with a pressing plate arranged in an arc shape, and the arc-shaped pressing surface of the pressing plate is provided with replaceable pressing cotton.

[0021] Preferably, the control processor is arranged at the top of the body, and the output end of the driving member is provided with a pressure sensor in communication connection with the control processor.

[0022] Preferably, the bottom of the body is arranged in an arc shape, and the bottom of the body is fixedly provided with an anti-skid pad.

[0023] Compared with the prior art, the present application has the following beneficial effects:

[0024] This invention utilizes an elastic energy storage bladder and a compression bladder. When the external pressure of the compression bladder suddenly increases and the internal pressure exceeds the opening threshold of the first differential pressure valve, the first differential pressure valve opens. This allows gas from the compression bladder to flow unidirectionally into the elastic energy storage bladder for temporary storage, causing the elastic energy storage bladder to elastically expand and store energy. Simultaneously, the pressure inside the compression bladder decreases. When the sudden increase in external pressure is eliminated, the elastic restoring force of the elastic energy storage bladder rises to exceed the opening threshold of the second differential pressure valve. Driven by this restoring force, the elastic energy storage bladder then unidirectionally returns the temporarily stored gas to the compression bladder via the second differential pressure valve. By dynamically maintaining pressure stability in the compression area, it can not only maintain constant contact and compression, effectively preventing compression failure caused by the compression bladder disengaging from the puncture point during decompression, but also further maintain the stability of compression hemostasis while adapting to changes in external pressure, thus improving the effect of compression hemostasis. It can also cope with pressure surges throughout the entire compression cycle, thereby dynamically maintaining pressure stability in the compression area, keeping the compression area in dynamic equilibrium, effectively solving the problem of patient discomfort caused by pressure surges, and effectively improving the continuity of hemostasis and the effect of compression hemostasis. Attached Figure Description

[0025] The disclosure of this invention is illustrated with reference to the accompanying drawings. It should be understood that the drawings are for illustrative purposes only and are not intended to limit the scope of protection of this invention. In the drawings, the same reference numerals are used to refer to the same parts. Wherein:

[0026] Figure 1 This is a top view of the present invention;

[0027] Figure 2 This is a bottom-view perspective view of the present invention;

[0028] Figure 3 This is a schematic diagram of the front cross-sectional structure of the present invention;

[0029] Figure 4 For the present invention Figure 3 Enlarged view of point A;

[0030] Figure 5 This is a schematic diagram of the side cross-sectional structure of the present invention;

[0031] Figure 6 For the present invention Figure 5 Enlarged view of point B;

[0032] Figure 7 This is a schematic diagram of the first modified structure of the present invention;

[0033] Figure 8 For the present invention Figure 7 Enlarged view of point C;

[0034] Figure 9This is a schematic diagram of the second modified structure of the present invention;

[0035] Figure 10 For the present invention Figure 9 Enlarged diagram of point D;

[0036] Figure 11 For the present invention Figure 4 Enlarged view of point E;

[0037] Figure 12 For the present invention Figure 10 Enlarged schematic diagram at point F.

[0038] The diagram shows the following components: 1. Main body; 2. Anti-slip pad; 3. Pressing cotton; 4. Strap buckle; 5. Control processor; 6. Arc-shaped guide plate; 7. Electric push rod; 8. First arc-shaped fixing plate; 9. Compression bladder; 10. Pressure sensor; 11. First spring; 12. Pressing plate; 13. Elastic energy storage bladder; 14. Air inlet pipe; 15. First cone valve; 16. First one-way valve; 17. Air outlet pipe; 18. Second cone valve; 19. Second one-way valve. Detailed Implementation

[0039] It is readily understood that, based on the technical solution of this invention, those skilled in the art can propose various interchangeable structural methods and implementations without altering the essential spirit of the invention. Therefore, the following detailed embodiments and accompanying drawings are merely illustrative examples of the technical solution of this invention and should not be considered as the entirety of the invention or as limitations or restrictions on the technical solution of this invention.

[0040] like Figures 1-12 As shown, a compression hemostatic device for bleeding after central venous catheter insertion includes:

[0041] The main body 1, the arc-shaped guide plate 6 fixed to the bottom of the inside of the main body 1, and the driving component installed on the arc-shaped guide plate 6;

[0042] The first arc-shaped fixing plate 8, which is elastically set at the output end of the driving component, is radially elastically compressed by the driving component.

[0043] The compression bag 9, which is fixed to the inner wall of the first arc-shaped fixation plate 8 and is initially in a state of extreme expansion, moves synchronously with the first arc-shaped fixation plate 8 and presses its end against the patient's intubation area.

[0044] Pressure balancing unit, comprising:

[0045] An elastic energy storage bag 13 is connected in parallel with the compression bag 9 to form a closed air passage;

[0046] The first differential pressure valve and the second differential pressure valve, the pressure bladder 9, the first differential pressure valve, the elastic energy storage bladder 13 and the second differential pressure valve are connected in sequence through the air passage to form a closed one-way gas circulation loop.

[0047] When the external pressure of the compression bladder 9 increases suddenly and the internal pressure of the compression bladder 9 exceeds the opening threshold of the first differential pressure valve, the first differential pressure valve opens so that the gas in the compression bladder 9 flows into the elastic energy storage bladder 13 through the first differential pressure valve for temporary storage, and the elastic energy storage bladder 13 expands elastically to store energy, and the pressure in the compression bladder 9 decreases synchronously.

[0048] When the sudden increase in pressure outside the compression bladder 9 is eliminated, the elastic restoring force of the elastic energy storage bladder 13 rises to exceed the opening threshold of the second differential pressure valve. The elastic energy storage bladder 13 then uses the elastic restoring force to drive the temporarily stored gas to flow back into the compression bladder 9 through the second differential pressure valve in one direction, so as to dynamically maintain the pressure stability of the compression area.

[0049] After central venous catheter insertion, bleeding is common at the insertion site, which is usually below the clavicle. Hemostasis is typically achieved by applying pressure with a saline bag and gauze, or through manual compression. However, the applied pressure relies entirely on the experience of medical personnel, making it difficult to quantify and inconsistent. The main body 1, when in use, first secures both ends of the catheter within the catheter limiting grooves on both sides of the main body 1, thus limiting and fixing the catheter. This effectively prevents displacement of the catheter during pressure hemostasis, avoiding pulling on the puncture site and causing bleeding. This establishes an initial anti-bleeding barrier and positions the catheter puncture point within the guide channel inside the arc-shaped guide plate 6, further limiting and guiding the catheter. Simultaneously, it creates a physical barrier at the puncture site, preventing external forces from pulling or applying excessive pressure, which could lead to bleeding at the insertion site.

[0050] Furthermore, the catheter puncture point is positioned within the guide channel inside the arc-shaped guide plate 6, and the bottom surface of the main body 1 is positioned to fit against the patient's skin. After positioning, the main body 1 is secured to the patient using straps pre-attached to the strap buckles 4 on both sides of the main body 1, thus fixing the main body 1 at the positioning point. The drive mechanism is activated, causing the first arc-shaped fixing plate 8, installed at the output end of the drive mechanism, to move radially. This causes the compression balloon 9, fixed to the inner arc wall of the first arc-shaped fixing plate 8, to move radially towards the catheter puncture point, bringing the compression balloon 9 into contact with the catheter and skin surface at the puncture point. As the drive mechanism continues to operate, the first spring 11, located between the output end of the drive mechanism and the first arc-shaped fixing plate 8, is elastically compressed to a preset distance, thereby compressing the catheter. An elastic pre-pressure is applied to the puncture site to compress the skin and catheter in the puncture point and surrounding area. Because the compression balloon 9 is in a state of maximum expansion, the compression end of the compression balloon 9 deforms under the combined action of the elastic pre-pressure and the catheter, thereby better filling the irregular gaps between the skin and the compression end of the compression balloon 9. The compression end of the compression balloon 9 fits the shape of the catheter more closely, achieving surface contact rather than point contact, making the pressure distribution more uniform. It is suitable for hemostasis by compression during catheter insertion in the jugular vein and other catheters, and hemostasis is more precise. It effectively reduces pressure on surrounding normal tissues, improves patient comfort during catheter insertion, and can provide continuous automatic compression for a long time without the need for manual compression by medical staff. This effectively ensures the stability of the compression, reduces the burden on staff, and improves the compression effect.

[0051] Furthermore, when a patient coughs, changes position, or experiences fluctuations in central venous pressure, the intrathoracic pressure may suddenly increase, and the local pressure may be momentarily insufficient, leading to bleeding and causing discomfort to the patient. After the pressure is relieved, effective pressure cannot be automatically restored. With the pressure balancing unit in place, the compression bladder 9 is initially in a state of extreme expansion. Both the initial elastic pre-pressure and the internal pressure of the compression bladder 9 in its extreme expansion state are less than the opening threshold of the first differential pressure valve. The initial pressure inside the elastic energy storage bladder 13 is less than the opening threshold of the second differential pressure valve. At this time, the overall pressure of the pressure balancing unit is in a balanced state. When the patient coughs or changes position, causing a sudden increase in intrathoracic pressure, the first spring 11 between the first arc-shaped fixing plates 8 is further elastically compressed, and the elastic pre-pressure increases sharply, resulting in a sharp increase in the external pressure of the compression bladder 9. Since the compression bladder 9 is initially in a state of extreme expansion, when the external pressure of the compression bladder 9 increases sharply, the internal pressure of the compression bladder 9 also increases sharply. At this time, the sharp increase in the internal pressure of the compression bladder 9 acts in reverse on the second differential pressure valve, thereby keeping the second differential pressure valve closed under the combined action of the sharp increase in the internal pressure of the compression bladder 9 and the pressure required for the second differential pressure valve to open.

[0052] Furthermore, when the internal pressure of the compression bladder 9 exceeds the opening threshold of the first differential pressure valve, the first differential pressure valve opens under the action of the sudden increase in internal pressure of the compression bladder 9. Under the pressure of the sudden increase in external pressure, some of the gas inside the compression bladder 9 flows rapidly into the elastic energy storage bladder 13 through the first differential pressure valve in one direction. The elastic energy storage bladder 13 inflates and deforms, converting the gas energy into its own elastic potential energy for storage. Moreover, the internal pressure of the elastic energy storage bladder 13 after inflation and deformation is greater than the opening threshold of the second differential pressure valve, but less than the combined pressure of the sudden increase in internal pressure of the compression bladder 9 and the pressure required for the second differential pressure valve to open. Therefore, the second differential pressure valve remains closed at this time.

[0053] Furthermore, as the gas volume decreases, the pressure in the compression bladder 9 shrinks. At this time, the first spring 11 partially recovers its elastic compression, thereby reducing the sudden increase in elastic pre-pressure and relieving the pressure surge. This effectively prevents sudden pressure changes and excessive compression caused by patient coughing or changes in body position, thus reducing patient discomfort. Simultaneously, the partial recovery of elastic compression by the first spring 11 pushes the elastic energy storage bladder 13 to maintain constant contact and compression with the skin and tubing at the puncture point. This effectively prevents the compression bladder 9 from detaching from the puncture point during pressure relief, thus maintaining the stability of compression hemostasis while adapting to changes in external pressure and improving the effectiveness of compression hemostasis.

[0054] Furthermore, when the patient calms down and the external pressure is eliminated, the first spring 11 quickly recovers its deformation, and the elastic pre-pressure rapidly returns to its initial pre-pressure. However, because the volume of the compression bladder 9 decreases during the decompression process, the first spring 11 continues to recover its extended compression deformation after returning to its initial elastic compression state to compensate for the reduced volume of the compression bladder 9, thus ensuring that the compression bladder 9 always compresses the puncture point. At this time, the elastic pre-pressure of the first spring 11 further decreases, thus falling below the opening threshold of the first differential pressure valve, and the first differential pressure valve automatically closes. Simultaneously, because the internal pressure of the elastic energy storage bladder 13 after inflation and deformation after the elimination of external pressure is greater than the opening threshold of the second differential pressure valve, the second differential pressure valve opens, and the elastic energy storage bladder 13 recovers its elasticity. Deformation releases energy, thereby compressing the gas inside the elastic energy storage bladder 13. The gas then flows back to the compression bladder 9 through the second differential pressure valve. After the compression bladder 9 returns to its initial limit expansion state, the elastic energy storage bladder 13 and the second differential pressure valve return to their initial equilibrium state. The second differential pressure valve closes, and the first spring 11 is further elastically compressed to its initial compression state during the deformation process of the compression bladder 9. This restores the external pressure of the compression bladder 9 to its initial elastic pre-pressure, thus restoring the initial equilibrium state. This can cope with pressure changes throughout the entire compression cycle, thereby dynamically maintaining the pressure stability of the compression area and keeping the compression area in dynamic equilibrium. This effectively solves the problem of patient discomfort caused by pressure changes and also effectively improves the continuity of hemostasis and the effect of compression hemostasis.

[0055] It should be noted that the aforementioned driving component can be a motor, a screw and connecting rod, or any other technical means known to those skilled in the art.

[0056] The opening threshold of the first differential pressure valve is greater than the internal stable pressure of the compression bladder 9 under the initial compression state.

[0057] At least three compression bladders 9 are provided and are evenly distributed around the arc-shaped guide plate 6 to form a C-shaped pressing surface to provide a wrapping compression that conforms to the shape of the tube in the insertion area.

[0058] Specifically, the driving component is an electric actuator 7, and one electric actuator 7 controls one corresponding compression bladder 9. The three compression bladders 9 are evenly distributed at approximately 120°, forming a stable mechanical triangle. When the electric actuator 7 applies radial pressure, these three points can synchronously and evenly transmit pressure to the catheter and the surrounding puncture tissue. This design effectively avoids pressure concentration that may be caused by a single compression point or strip compression band, significantly reducing the risk of local skin pressure sores and tissue ischemic necrosis. Moreover, the triangular distribution structure provides good anti-rotational stability. When the patient's head turns or the body moves, the device is not easy to twist or deviate around the catheter, and can always maintain the position of the preset compression point, ensuring the continuity of hemostasis.

[0059] Furthermore, for central venous puncture sites, effective hemostasis requires pressure to close the rupture in the vessel wall. The C-shaped wrapping formed by the three compression sacs can generate a circumferential force on the catheter and subcutaneous vessel segment from multiple directions, which better meets the physiological requirement of closing the vascular rupture. Compared with unidirectional compression, it can achieve a more reliable hemostatic effect with a smaller total pressure, improving hemostasis efficiency and quality.

[0060] Furthermore, the three compression bladders 9 can be designed as individual pressure balancing units. When a patient coughs, causing a sudden increase in pressure on one side of the puncture site, the compression bladder 9 that mainly bears that pressure can independently activate the corresponding pressure balancing unit to achieve zoned and precise pressure buffering. This is more refined than the overall buffering of a single large air bladder and can maintain the stability of the pressure in other unaffected areas to the greatest extent, further improving the overall compression effect of the device.

[0061] The compression bladder 9 is a corrugated telescopic air bladder to achieve directional contraction.

[0062] Specifically, when a conventional airbag is compressed, its deformation direction is uncontrollable, potentially inflating laterally or in a non-compression direction, resulting in energy waste and localized pressure instability. The corrugated telescopic airbag, due to its physical structure, has its compression and expansion strictly limited to the radial compression direction consistent with the driving direction of the electric actuator 7. This ensures that the force applied by the electric actuator 7 and changes in external pressure can be converted almost losslessly and without deviation into compression of the gas inside the compression bladder 9 along a predetermined direction. This effectively improves the device's response sensitivity to sudden pressure fluctuations. Furthermore, the directional deformation characteristic allows the compression bladder 9 to maintain its regular initial shape when uncompressed and contract linearly when compressed, avoiding irregular twisting or interference with adjacent components within a limited space. This improves the overall structural compactness and operational reliability. Directional contraction prevents the compression bladder 9 from unintendedly expanding into surrounding soft tissues, maximizing the concentration of pressure on the target vascular puncture area, reducing traction and compression on surrounding normal tissues, and further enhancing patient comfort.

[0063] An air inlet pipe 14 and an air outlet pipe 17 are connected in parallel between the compression bladder 9 and the elastic energy storage bladder 13. A first differential pressure valve is installed in the air inlet pipe 14 and a second differential pressure valve is installed in the air outlet pipe 17 to form a closed one-way gas circulation loop.

[0064] The first differential pressure valve includes a first check valve 16 and a resiliently configured first cone valve 15.

[0065] The second differential pressure valve includes a second check valve 19 and a resiliently configured second cone valve 18.

[0066] Specifically, the tip of the first cone valve 15 faces the air inlet port of the air inlet pipe 14, and the non-tip of the first cone valve 15 is provided with a second spring. The tip of the second cone valve 18 faces the direction away from the air outlet port of the air outlet pipe 17, and the non-tip of the second cone valve 18 is provided with a third spring.

[0067] Furthermore, such as Figure 6 As shown, the compression bladder 9 is initially in a state of extreme expansion, and both the initial elastic pre-pressure and the internal pressure of the compression bladder 9 in the state of extreme expansion are less than the pressure required for the second spring to deform. The initial pressure inside the elastic energy storage bladder 13 is less than the pressure required for the third spring to deform. At this time, the overall pressure of the pressure balance unit is in a state of equilibrium. When the patient coughs or changes position, causing a sudden increase in intrathoracic pressure, it causes the first spring 11 between the first arc-shaped fixing plates 8 to be further elastically compressed, and the elastic pre-pressure increases sharply, which in turn causes a sharp increase in the external pressure of the compression bladder 9. Since the compression bladder 9 is initially in a state of extreme expansion, when the external pressure of the compression bladder 9 increases sharply, the internal pressure of the compression bladder 9 also increases sharply. At this time, the internal pressure of the compression bladder 9 increases sharply, which acts in the opposite direction on the non-pointed surface of the second cone valve 18, thereby pushing the cone surface of the second cone valve 18 and the outlet end of the first contact tube set on the inner wall of the outlet port of the outlet pipe 17 to always be in contact and sealed, so that the outlet port of the outlet pipe 17 remains closed.

[0068] Furthermore, such as Figure 8 As shown, when the internal pressure of the compression bladder 9 increases and exceeds the pressure required for the second spring to deform, the internal pressure of the compression bladder 9 acts on the conical surface of the first conical valve 15, and pushes the first conical valve 15 to push the second spring to compress elastically. The conical surface of the first conical valve 15 disengages from the second contact pipe provided on the inner wall of the air inlet end of the air inlet pipe 14, thereby opening the air inlet end of the air inlet pipe 14. Under the pressure of the sudden increase in external pressure, part of the gas inside the compression bladder 9 flows rapidly into the elastic energy storage bladder 13 through the first one-way valve 16. The elastic energy storage bladder 13 inflates and deforms, converting the gas energy into the elastic potential energy of the elastic energy storage bladder 13 itself. After the elastic energy storage bladder 13 inflates and deforms, the internal pressure is greater than the pressure required for the third spring to deform, but less than the combined pressure of the sudden increase in the internal pressure of the compression bladder 9 and the pressure required for the third spring to deform. Therefore, at this time, the air outlet port of the air outlet pipe 17 remains closed.

[0069] Furthermore, such as Figure 10As shown, when the patient calms down and the external pressure is eliminated, the first spring 11 quickly recovers its deformation, and the elastic pre-pressure rapidly returns to the initial pre-pressure. However, because the volume of the compression bladder 9 decreases during the decompression process, the first spring 11 continues to recover its extended portion of compression deformation after returning to its initial elastic compression state to compensate for the reduced volume of the compression bladder 9, thus ensuring that the compression bladder 9 always compresses the puncture point. At this time, the elastic pre-pressure of the first spring 11 further decreases, becoming less than the pressure required for the second spring to deform. The second spring then recovers its deformation and pushes against the conical surface of the first conical valve 15. The two contact tubes contact and block the outlet of the second contact tube, thereby blocking the inlet end of the inlet pipe 14. At the same time, after the external pressure is eliminated, the internal pressure of the elastic energy storage bladder 13 after inflation and deformation is greater than the pressure required for the third spring to deform. Therefore, the conical surface of the second conical valve 18 is disengaged from the outlet end of the first contact tube provided on the inner wall of the outlet port of the outlet pipe 17, thereby opening the outlet port of the outlet pipe 17. The elastic energy storage bladder 13 restores its elastic deformation and releases energy, thereby compressing the gas inside the elastic energy storage bladder 13, which enters the outlet pipe 17 and flows back to the compression bladder 9 through the second one-way valve 19.

[0070] The compression bladder 9 is fixedly provided with an arc-shaped compression plate 12 at the compression end, and the arc-shaped compression surface of the compression plate 12 is provided with replaceable compression cotton 3.

[0071] Specifically, by pressing the cotton 3 into contact with the skin, it not only acts as a cushion but also absorbs small amounts of blood, exudate, or sweat, keeping the puncture site dry and comfortable.

[0072] The control processor 5 is installed on the top inside the main body 1, and the output end of the drive component is equipped with a pressure sensor 10 that is connected to the control processor 5.

[0073] Specifically, the top of the main body 1 is equipped with a display screen that is electrically connected to the control processor 5. It can display the pressure value captured by the pressure sensor 10 in real time. By inputting the pre-pressure value through the control button, the electric push rod 7, which is electrically connected to the control processor 5, can be controlled to drive the compression bladder 9 to move and compress the puncture point to the input pre-pressure value.

[0074] The bottom of the main body 1 is arc-shaped, and an anti-slip pad 2 is fixedly installed on the bottom of the main body 1.

[0075] Specifically, the bottom of the main body 1 is arc-shaped to better fit the skin surface, and the anti-slip pad 2 fixedly installed at the bottom of the main body 1 further prevents the device from shifting position and improves the stability of the device.

[0076] The technical scope of this invention is not limited to the content described above. Those skilled in the art can make various modifications and variations to the above embodiments without departing from the technical concept of this invention, and all such modifications and variations should fall within the protection scope of this invention.

Claims

1. A compression hemostasis device for post-insertion bleeding of a central venous catheter, characterized in that, The utility model relates to a kind of pressure stabilizing device for patient's tracheal cannula, including: Main body, arc-shaped guide plate fixed to the inner bottom of main body and driving element installed on arc-shaped guide plate; First arc-shaped fixed plate elastically arranged at the output end of driving element, which is driven by driving element to be radially elastically compressed; Compression sac fixed to the inner wall of first arc-shaped fixed plate and in initial state limit expansion state, which moves synchronously with first arc-shaped fixed plate and makes end compression in patient's tracheal cannula area; Pressure balancing unit, including: Elastic energy storage sac in parallel communication with compression sac to form closed gas circuit; First differential pressure valve and second differential pressure valve, the compression sac, first differential pressure valve, elastic energy storage sac and second differential pressure valve are sequentially connected by gas circuit, to form closed one-way gas circulation loop; When the external pressure of compression sac increases suddenly, and the internal pressure of compression sac exceeds the opening threshold of first differential pressure valve, the first differential pressure valve opens, so that the gas in compression sac flows into elastic energy storage sac temporarily through first differential pressure valve in one-way, and the elastic energy storage sac is elastically expanded to store energy, and the pressure in compression sac is synchronously reduced; When the sudden increase in external pressure of compression sac is eliminated, the elastic restoring force of elastic energy storage sac rises to exceed the opening threshold of second differential pressure valve, and the temporarily stored gas in elastic energy storage sac flows back to compression sac in one-way driven by elastic restoring force, to dynamically maintain the pressure stability of compression area.

2. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 1, characterized in that: The opening threshold of the first differential pressure valve is greater than the internal stable pressure of the compression sac in the initial compression state.

3. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 2, characterized in that: The compression sac is provided with at least three, and is uniformly distributed along the circumference of arc-shaped guide plate, to form C-shaped pressing surface to fit the wrapping type pressing of tracheal cannula area.

4. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 3, characterized in that: The compression sac is a corrugated telescopic air bag to realize directional contraction.

5. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 4, characterized in that: Gas inlet pipe and gas outlet pipe are provided in parallel communication between the compression sac and the elastic energy storage sac, the first differential pressure valve is arranged in the gas inlet pipe, and the second differential pressure valve is arranged in the gas outlet pipe, to form closed one-way gas circulation loop.

6. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 5, characterized in that: The first differential pressure valve includes a first one-way valve and a first conical valve arranged elastically.

7. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 5, characterized in that: The second differential pressure valve includes a second one-way valve and a second conical valve arranged elastically.

8. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 5, characterized in that: The pressing end of the compression sac is fixedly provided with an arc-shaped pressing plate, and the arc-shaped pressing surface of the pressing plate is provided with replaceable pressing cotton.

9. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 1, characterized in that: A control processor is installed at the top of the main body, and a pressure sensor is arranged at the output end of the driving element in communication connection with the control processor.

10. The compression hemostasis device for post-insertion bleeding of central venous catheter according to claim 9, characterized in that: The bottom of the main body is arc-shaped, and an anti-skid pad is fixedly arranged at the bottom of the main body.

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