Device for detecting resilience force of hemostatic sheath

Abstract

The utility model discloses a hemostasis sheath resilience force detection device. The hemostasis sheath resilience force detection device comprises a linear conveying mechanism, a base assembly and a force value sensor. The linear conveying mechanism is used for conveying blood taking needles in the first direction. The base assembly defines a channel extending in the first direction and a needle tube inlet communicated with the channel, and the inner diameter of the channel is configured to be larger than the outer diameter of a needle tube of the blood taking needle and smaller than the outer diameter of a hemostasis sheath of the blood taking needle so as to prevent the hemostasis sheath from entering the channel. The inner diameter of the needle tube inlet is configured to be larger than the needle tube outer diameter of the blood taking needle so that the needle tube of the blood taking needle can penetrate through and enter the channel. The force value sensor is connected to the linear conveying mechanism and used for detecting the axial resistance generated when the needle tube continues to stretch into the channel when the hemostasis sheath is blocked. In the application, the needle tube can enter the channel, the hemostasis sheath is blocked outside the channel, the needle tube continues to extend into the channel, and the axial resistance is measured through the force value sensor, so that the elastic force of the hemostasis sheath is obtained.

Description

Technical Field

[0001] This utility model relates to the field of medical device testing technology, and in particular to a hemostatic sheath rebound force testing device. Background Technology

[0002] The blood collection needle consists of a hemostatic sheath and a blood collection needle tube, with the hemostatic sheath covering the outside of the blood collection needle tube. The hemostatic sheath should be able to effectively rebound after multiple punctures by the blood collection needle, thus preventing leakage. Therefore, the elasticity of the hemostatic sheath is a key parameter of this product.

[0003] In related technologies, there is a lack of a dedicated device for testing the rebound force of hemostatic sheaths, making it difficult to detect the elasticity of the hemostatic sheaths. Utility Model Content

[0004] The present invention aims to at least solve one of the technical problems existing in the prior art. Therefore, one objective of the present invention is to provide a hemostatic sheath rebound force detection device, which can detect the rebound force of the hemostatic sheath of a blood collection needle.

[0005] This utility model provides a hemostatic sheath rebound force detection device, which includes a linear conveying mechanism, a base assembly, and a force sensor. The linear conveying mechanism is used to convey a blood collection needle along a first direction. The base assembly defines a channel extending along the first direction and a needle inlet communicating with the channel. The inner diameter of the channel is configured to be larger than the outer diameter of the blood collection needle tube and smaller than the outer diameter of the hemostatic sheath of the blood collection needle to prevent the hemostatic sheath from entering the channel. The inner diameter of the needle inlet is configured to be larger than the outer diameter of the blood collection needle tube to allow the blood collection needle tube to pass through and enter the channel. The force sensor is connected to the linear conveying mechanism and is used to detect the axial resistance generated when the hemostatic sheath is blocked and the needle tube continues to extend into the channel.

[0006] In some embodiments, the inner diameter of the channel is 0.6 mm to 2.2 mm.

[0007] In some embodiments, the extension length of the channel is at least 20 mm.

[0008] In some embodiments, the needle inlet is configured as a tapered shape that tapers toward one side of the channel.

[0009] In some embodiments, the minimum inner diameter of the needle inlet is the same as the inner diameter of the channel and is axially aligned.

[0010] In some embodiments, the base assembly includes a base and a test fixture; the base and the test fixture are connected by a detachable structure; the test fixture has the channel and the needle inlet.

[0011] In some embodiments, the detachable structure includes a protrusion on the base and a slot through the test fixture; both the protrusion and the slot extend along a second direction, which is perpendicular to the first direction.

[0012] In some embodiments, the cross-sectional shape of the card protrusion and the card slot perpendicular to the second direction is T-shaped or cross-shaped.

[0013] In some embodiments, the linear delivery mechanism includes a clamping assembly and a driving assembly, the driving assembly being connected to the clamping assembly to drive the clamping assembly to move along the first direction, and the force sensor being disposed between the clamping assembly and the driving assembly; the clamping assembly is used to clamp the blood collection needle.

[0014] In some embodiments, the drive assembly includes a drive plate, and the clamping assembly includes a three-jaw chuck disposed on the drive plate.

[0015] As can be seen from the technical solution, the embodiments provided by this utility model have the following advantages:

[0016] (1) The linear conveying mechanism drives the entire blood collection needle to move in the first direction. The needle tube of the blood collection needle can enter the channel through the needle tube inlet. The hemostatic sheath of the blood collection needle is blocked outside the channel. The needle tube continues to extend into the channel. At this time, the rebound force of the hemostatic sheath is directly converted into the axial resistance encountered by the needle tube when it moves. The axial resistance is measured by a force sensor connected to the linear conveying mechanism, thereby obtaining the elastic force of the hemostatic sheath.

[0017] (2) By defining the channel and needle inlet through the base assembly, the hemostatic sheath is blocked in a suitable position and the needle is inserted into the channel, simulating the force on the hemostatic sheath during the needle puncture process when using a blood collection needle. This structural design ensures the accuracy of force transmission and measurement during the test, thereby improving the accuracy of the elasticity test of the hemostatic sheath and more closely resembling the elasticity performance of the hemostatic sheath due to puncture in actual use, making the test results more valuable for evaluating the actual performance of the product. Attached Figure Description

[0018] To more clearly illustrate the technical solutions in the embodiments of this utility model or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 This is a schematic diagram of the overall structure of the hemostatic sheath rebound force detection device according to an embodiment of the present utility model;

[0020] Figure 2 It is based on Figure 1 A partial schematic diagram;

[0021] Figure 3 This is a schematic diagram of the overall structure of the hemostatic sheath rebound force detection device according to an embodiment of the present utility model;

[0022] Figure 4 Yes, according to Figure 3 A partial schematic diagram;

[0023] Figure 5 This is a schematic diagram of the test fixture according to an embodiment of the present utility model;

[0024] Figure 6 This is a schematic diagram of the test fixture according to an embodiment of the present utility model;

[0025] Figure 7 This is a schematic diagram of the blood collection needle.

[0026] Figure label:

[0027] Hemostatic sheath rebound force testing device 100, blood collection needle 200, needle tube 201, hemostatic sheath 202, needle hub 203;

[0028] Linear conveyor mechanism 1, clamping assembly 11, drive assembly 12;

[0029] Base assembly 2, base 21, test fixture 22, channel 221, needle inlet 222, detachable structure 23, locking protrusion 231, locking groove 232. Detailed Implementation

[0030] The embodiments of this utility model are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this utility model, and should not be construed as limiting this utility model.

[0031] In the description of this utility model, it should be understood that the terms "center," "longitudinal," "transverse," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," "axial," "inner diameter," and "circumferential," etc., indicating the orientation or positional relationship shown in the accompanying drawings, are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this utility model. Furthermore, features defined with "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this utility model, unless otherwise stated, "a plurality of" means two or more.

[0032] In the description of this utility model, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "joining" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model based on the specific circumstances.

[0033] The following is for reference. Figures 1-7 Description of a hemostatic sheath rebound force detection device 100 according to an embodiment of the present invention.

[0034] Example 1

[0035] like Figure 1 As shown, this embodiment provides a hemostatic sheath rebound force detection device 100, which includes a linear conveying mechanism 1, a base assembly 2, and a force sensor (not shown in the figure).

[0036] Combination Figure 1 and Figure 3 The linear conveying mechanism 1 can convey the blood collection needle 200 along the first direction.

[0037] like Figure 1 As shown, the base assembly 2 has a channel 221 and a needle inlet 222. The channel 221 extends along a first direction, and the needle inlet 222 communicates with the channel 221.

[0038] Please see Figure 3 and Figure 4As shown, the inner diameter of channel 221 is configured to be larger than the outer diameter of needle tube 201 of blood collection needle 200 and smaller than the outer diameter of hemostatic sheath 202 of blood collection needle 200 to prevent hemostatic sheath 202 from entering channel 221, and the inner diameter of needle tube inlet 222 is configured to be larger than the outer diameter of needle tube 201 of blood collection needle 200 to allow needle tube 201 of blood collection needle 200 to pass through and enter channel 221.

[0039] Please see Figure 4 This means that the inner diameter of the needle inlet 222 depends on the outer diameter of the needle tube 201 of the blood collection needle 200 in the actual product. The inner diameter of the needle inlet 222 should be designed to be larger than the outer diameter of the needle tube 201, so that the needle inlet 222 can allow the needle tube 201 of the blood collection needle 200 to pass through. The inner diameter of the channel 221 depends on the outer diameter of the needle tube 201 of the blood collection needle 200 and the outer diameter of the hemostatic sheath 202 in the actual product. That is, the inner diameter of the channel 221 is greater than or equal to the outer diameter of the needle tube 201 of the blood collection needle 200 and smaller than the outer diameter of the hemostatic sheath 202, so that the needle tube 201 of the blood collection needle 200 can enter the channel 221 through the needle inlet 222.

[0040] It should also be noted that, when designing the base assembly 2, those skilled in the art can adjust the matching relationship between the inner diameter of the channel 221, the inner diameter of the needle inlet 222, and the outer diameter of the hemostatic sheath 202 according to actual testing requirements. For example, for a hemostatic sheath 202 with a larger outer diameter, the outer diameter of the needle inlet 222 and the outer diameter of the channel 221 can be increased accordingly, but the dimensional constraint that the inner diameter of the channel 221 is smaller than the outer diameter of the hemostatic sheath 202 must still be met.

[0041] A force sensor is connected to the linear conveying mechanism 1. When the hemostatic sheath 202 is blocked, the needle 201 continues to extend into the channel 221 until the needle 201 pierces the hemostatic sheath 202. During this process, the force sensor detects the axial resistance applied by the hemostatic sheath 202 to the needle 201.

[0042] like Figure 4 As shown, when the hemostatic sheath 202 is blocked outside the channel 221, it undergoes compression deformation, and the needle 201 continues to extend into the channel 221 until the hemostatic sheath 202 is punctured by the needle 201.

[0043] In a specific application scenario, the linear conveying mechanism 1 drives the blood collection needle 200 to move along a first direction. The needle tube 201 of the blood collection needle 200 can enter the channel 221 through the needle tube inlet 222. The hemostatic sheath 202 of the blood collection needle 200 is blocked outside the channel 221. The needle tube 201 continues to extend into the channel 221. At this time, the rebound force of the hemostatic sheath 202 is directly converted into the axial resistance encountered by the needle tube 201 when it moves. The axial resistance is measured by a force sensor connected to the linear conveying mechanism 1, thereby obtaining the elastic force of the hemostatic sheath 202.

[0044] The first direction here can be the up and down direction. The linear delivery mechanism 1 is located above the base assembly 2, so the needle inlet 222 is opened on the upper surface of the base assembly 2. The linear delivery mechanism 1 drives the blood collection needle 200 downward to approach the base assembly.

[0045] As can be seen from the technical solution, the embodiments provided by this utility model have the following advantages:

[0046] (1) The linear conveying mechanism 1 drives the blood collection needle 200 to move along the first direction. The needle tube 201 of the blood collection needle 200 can enter the channel 221 through the needle tube inlet 222. The hemostatic sheath 202 of the blood collection needle 200 is blocked outside the channel 221. The needle tube 201 continues to extend into the channel 221. At this time, the rebound force of the hemostatic sheath 202 is directly converted into the axial resistance encountered by the needle tube 201 when it moves. The axial resistance is measured by a force sensor connected to the linear conveying mechanism 1, thereby obtaining the elastic force of the hemostatic sheath 202.

[0047] (2) The linear conveying mechanism 1 drives the blood collection needle to move in a fixed direction, and cooperates with the channel 221 of the base assembly 2 to limit it, forming a unidirectional linear motion path; the force sensor is directly connected to the conveying mechanism to collect resistance data in real time, eliminating manual operation steps, realizing fully automatic detection, greatly improving detection efficiency, and reducing errors introduced by human intervention.

[0048] (3) By defining the channel 221 and the needle inlet 222 through the base assembly 2, the hemostatic sheath 202 is blocked in a suitable position and the needle 201 is inserted into the channel 221, simulating the force on the hemostatic sheath 202 during the needle puncture process when the blood collection needle 200 is used. This structural design ensures the accuracy of force transmission and measurement during the test, thereby improving the accuracy of the elasticity test of the hemostatic sheath 202, which is closer to the elasticity performance of the hemostatic sheath 202 due to puncture in actual use, making the test results more valuable for the actual performance evaluation of the product.

[0049] Please refer to Figure 4Furthermore, the inner diameter of channel 221 is 0.6mm to 2mm. This means that the inner diameter of channel 221 can be 0.6mm, 0.7mm, 0.8mm, 0.85mm, 0.9mm, 1.0mm, 1.2mm, 1.4mm, 1.7mm, 1.9mm, etc., which will not be listed here; it is sufficient to configure the inner diameter of channel 221 between 0.6mm and 2.0mm. In practical applications, the outer diameter of the needle tube 201 of common blood collection needles 200 is 0.55mm, 0.7mm, 0.8mm, 1.2mm, etc., and the outer diameter of the hemostatic sheath 202 of the blood collection needle 200 is 2.3mm, 2.4mm, 2.5mm, etc. To accommodate different blood collection needles 200, those skilled in the art can adjust the matching relationship between the inner diameter of channel 221 and the blood collection needle 200 according to actual testing needs, thereby covering blood collection needles 200 of different sizes. For example, when the outer diameter of the blood collection needle 200 and needle tube 201 to be tested is 0.55mm and the hemostatic sheath 202 is 2.3mm, the inner diameter of the channel 221 can be 0.6mm~2mm.

[0050] Please refer to Figure 4 Furthermore, the extension length of channel 221 is at least 20 mm. After needle 201 enters channel 221, it needs to maintain a sufficient distance of movement so that needle 201 can move axially relative to hemostatic sheath 202 and puncture it. Part of the hemostatic sheath 202 may deform during needle insertion and fail to puncture. By setting the extension length of channel 221 to at least 20 mm, sufficient deformation release space can be provided to accommodate different compression deformation requirements of hemostatic sheath 202, avoiding incomplete resistance detection due to insufficient travel. Simultaneously, the longer channel 221 can provide guidance for needle 201, limiting its swaying or tilting during movement and improving data accuracy.

[0051] refer to Figure 5 and Figure 6 Furthermore, the needle inlet 222 is tapered, with its inner diameter gradually decreasing towards the channel 221. This tapered inlet guides the needle 201, making it easier and more accurately inserted into the channel 221. Even with some angular deviation during insertion, the tapered inlet guides the needle 201 to gradually align with the center of the channel 221, improving the success rate and accuracy of insertion and facilitating rapid and accurate positioning of the blood collection needle during automated testing.

[0052] refer to Figure 5 and Figure 6Furthermore, the minimum inner diameter of the needle inlet 222 is the same as the inner diameter of the channel 221. The needle inlet 222 and the channel 221 are axially aligned upwards. As a result, the needle 201 is more easily aligned with the channel 221 after passing through the needle inlet 222, which can improve the guiding effect of the needle inlet 222.

[0053] Example 2

[0054] refer to Figure 1 ,refer to Figure 5 and Figure 6 Furthermore, the base assembly 2 includes a base 21 and a testing fixture 22. The base 21 and the testing fixture 22 are connected by a detachable structure 23. The testing fixture 22 has a channel 221 and a needle inlet 222. Different testing fixtures 22 may be required to match different models or specifications of blood collection needles 200. The detachable structure 23 allows for easy replacement of the testing fixture 22 to meet the testing needs of various blood collection needles 200, thus improving the versatility of the base assembly 2.

[0055] refer to Figure 5 and Figure 6 Furthermore, the detachable structure 23 includes a latching protrusion 231 and a latching groove 232. The latching protrusion 231 is disposed on the base 21, and the latching groove 232 is disposed through the base 21. Both the latching protrusion 231 and the latching groove 232 extend along a second direction, which is perpendicular to the first direction. The test fixture 22 can be pushed along the second direction, thereby installing the test fixture 22 on the base 21 or removing the test fixture 22 from the base 21. This installation method is simple and direct, improving installation efficiency.

[0056] Optionally, the first direction is the up-down direction and the second direction is the front-back direction. The test fixture 22 can be pushed onto the base 21 from the front or rear side to achieve installation between the test fixture 22 and the base 21; or, the first direction is the up-down direction and the second direction is the left-right direction. The test fixture 22 can be pushed onto the base 21 from the left or right side to achieve installation between the test fixture 22 and the base 21.

[0057] refer to Figure 1 ,refer to Figure 5 and Figure 6Furthermore, the cross-sectional shape of the protrusion 231 and the slot 232 perpendicular to the second direction is T-shaped or cross-shaped. The T-shaped or cross-shaped cross-section has a certain guiding effect, making it easier for the operator to align the protrusion 231 with the slot 232 when installing the test fixture 22. Moreover, the unique shape allows the test fixture 22 to be positioned more accurately during installation. Once the protrusion 231 enters the slot 232, the position of the test fixture 22 can be quickly determined, reducing adjustment time during installation and improving installation efficiency.

[0058] Example 3

[0059] See Figure 1 and Figure 3 , Figure 2 and Figure 4 Furthermore, the linear conveying mechanism 1 includes a clamping assembly 11 and a driving assembly 12. The driving assembly 12 is connected to the clamping assembly 11 to drive the clamping assembly 11 to move along a first direction. A force sensor is disposed between the clamping assembly 11 and the driving assembly 12. The clamping assembly 11 is used to clamp the blood collection needle 200. When the hemostatic sheath 202 is blocked by the needle inlet 222 of the base assembly 2, and the needle tube 201 continues to extend into the channel 221 under the drive of the clamping assembly 11, the needle tube 201 will experience axial resistance due to the rebound force of the hemostatic sheath 202. The force sensor, disposed between the clamping assembly 11 and the driving assembly 12, can directly and accurately measure this axial resistance.

[0060] See Figure 1 and Figure 3 , Figure 2 and Figure 4 Furthermore, the drive assembly 12 includes a drive plate, and the clamping assembly 11 includes a three-jaw chuck disposed on the drive plate. A force sensor is located at the connection between the three-jaw chuck and the drive plate. This arrangement allows the force sensor to accurately measure the axial resistance experienced by the needle tube 201 during clamping and insertion into the channel 221.

[0061] See Figure 7 In a specific example, the blood collection needle 200 includes a needle tube 201, a needle hub 203, and a hemostatic sheath 202. The needle tube 201 is fixedly connected to the needle hub 203, and the hemostatic sheath 202 is fitted onto the needle tube 201. A three-jaw chuck is used to fix the needle hub 203 of the blood collection needle 200.

[0062] The drive board includes a drive component and a transmission plate. The output end of the drive component is connected to the transmission plate. The transmission plate is equipped with a three-jaw chuck, and a force sensor can be set between the three-jaw chuck and the transmission plate.

[0063] During use, the test fixture 22 is assembled to the bottom of the base 21, and the blood collection needle 200 is fixed in the three-jaw chuck. The height and position of the three-jaw chuck are adjusted so that the needle tube 201 of the blood collection needle 200 is on the same axis as the channel 221, and the bottom of the hemostatic sleeve 202 is approximately parallel to the upper plane of the test fixture 22. The parameters of the drive component are adjusted, and the drive component drives the three-jaw chuck downward through the drive transmission plate. After the needle tube 201 passes through the hemostatic sleeve 202, it enters the channel 221 through the needle tube inlet 222. The hemostatic sleeve 202 is locked on the upper plane of the test fixture 22 and specifically locked outside the channel 221. The needle tube 201 extends into the channel 221 by approximately 15mm and then stops. The force sensor is located between the three-jaw chuck and the transmission plate. The three-jaw chuck clamps the blood collection needle downwards, and the elastic force of the hemostatic sheath is fed back to the force sensor through the three-jaw chuck. That is, the force sensor detects the resistance value encountered when the transmission plate descends, obtains the elastic force of the hemostatic sheath, and sends the resistance value to the computer. The computer records the value.

[0064] Other components and operations of the hemostatic sheath rebound force detection device 100 according to embodiments of the present invention are known to those skilled in the art and will not be described in detail here. In the description of the present invention, "first feature" and "second feature" may include one or more of the features. The up-down direction, left-right direction, and front-back direction are defined as shown in the figures.

[0065] In the description of this utility model, unless otherwise expressly specified and limited, "above" or "below" the second feature can include direct contact between the first and second features, or contact between the first and second features not in direct contact but through another feature between them. Moreover, "above," "over," and "on top" of the second feature include the first feature directly above or diagonally above the second feature, or simply indicates that the first feature is at a higher horizontal level than the second feature.

[0066] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the present invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0067] Although embodiments of the present invention have been shown and described, those skilled in the art will understand that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the present invention, the scope of which is defined by the claims and their equivalents.

Claims

1. A hemostatic sleeve recoil force detection device, characterized by, include: A linear conveying mechanism (1) is used to convey blood collection needles along a first direction; The base assembly (2) defines a channel (221) extending along the first direction and a needle inlet (222) communicating with the channel (221). The inner diameter of the channel (221) is configured to be larger than the outer diameter of the needle tube of the blood collection needle and smaller than the outer diameter of the hemostatic sheath of the blood collection needle to prevent the hemostatic sheath from entering the channel (221). The inner diameter of the needle inlet (222) is configured to be larger than the outer diameter of the needle tube of the blood collection needle to allow the needle tube of the blood collection needle to pass through and enter the channel (221). A force sensor, connected to the linear delivery mechanism (1), is used to detect the axial resistance generated when the hemostatic sheath is blocked and the needle continues to extend into the channel (221).

2. The hemostat sleeve recoil force detection device of claim 1, wherein, The inner diameter of the channel (221) is 0.6mm~2.2mm.

3. The hemostat sleeve recoil force detection device of claim 1, wherein, The extension length of the channel (221) is at least 20 mm.

4. The hemostat sleeve recoil force detection device of claim 1, wherein, The needle inlet (222) is constructed as a tapered shape that tapers toward the channel (221).

5. The hemostatic sleeve recoil force detection device of claim 4, wherein, The minimum inner diameter of the needle inlet (222) is the same as the inner diameter of the channel (221) and is axially aligned.

6. The hemostat sleeve recoil force detection device of claim 1, wherein, The base assembly (2) includes a base (21) and a test fixture (22); The base (21) and the test fixture (22) are connected by a detachable structure (23); The test fixture (22) has the channel (221) and the needle inlet (222).

7. The hemostatic sleeve recoil force detection device of claim 6, wherein, The detachable structure (23) includes a latching protrusion (231) on the base (21) and a latching groove (232) through the test fixture (22). Both the card protrusion (231) and the card slot (232) extend along a second direction, which is perpendicular to the first direction.

8. The hemostat sleeve recoil force detection device of claim 7, wherein, The cross-sectional shape of the card protrusion (231) and the card slot (232) perpendicular to the second direction is T-shaped or cross-shaped.

9. The hemostat sleeve recoil force detection device of claim 1, wherein, The linear conveying mechanism (1) includes a clamping assembly (11) and a driving assembly (12). The driving assembly (12) is connected to the clamping assembly (11) to drive the clamping assembly (11) to move along the first direction. The force sensor is located between the clamping assembly (11) and the driving assembly (12). The clamping assembly (11) is used to clamp the blood collection needle.

10. The hemostatic sleeve recoil force detection device of claim 9, wherein, The drive assembly (12) includes a drive plate, and the clamping assembly (11) includes a three-jaw chuck disposed on the drive plate.

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