Hemodialysis puncture needle device capable of reducing blood cell damage

Abstract

The invention discloses a hemodialysis puncture needle device capable of reducing blood cell destruction, which comprises a puncture needle and a dialysis connecting tube, and is characterized in that the puncture needle comprises a needle seat and a needle tube, and the needle seat is arranged at one end of the needle tube; the dialysis connecting tube is connected to the needle seat and is used for conveying blood to the puncture needle; wherein the surface of the needle tube is provided with a heparin nano coating with the thickness of 0.5-1 mu m, and the heparin nano coating is used for reducing platelet adhesion; the needle tube comprises a main body section, a transition section and a puncture section which are connected in sequence, the inner diameter of the main body section is smaller than that of the transition section, the inner diameter of the transition section is smaller than that of the puncture section, and the main body section is connected to the needle seat. The heparin nano coating with the thickness of 0.5-1 micron is arranged on the surface of the needle tube, and the needle tube structure with the main body section, the transition section and the puncture section which are sequentially expanded in diameter is adopted, so that blood cell damage and platelet abnormal adhesion caused by direct contact of the surface of the metal needle tube in the hemodialysis process are remarkably reduced, and the risk of microthrombus generation is reduced.

Description

Technical Field

[0001] The present invention relates to a puncture needle, in particular to a hemodialysis puncture needle device capable of reducing blood cell damage. Background Art

[0002] Hemodialysis is an important treatment method for maintaining the lives of patients with end-stage renal disease. There are many problems with the dialysis puncture needles currently used in clinical practice, mainly including mechanical damage to blood cells, abnormal platelet activation, and complications from vascular puncture. During dialysis treatment, the patient's blood flows into the dialysis system through the puncture needle. Due to the direct contact between the metal needle and the blood, red blood cells are easily subjected to large shear forces under high-speed flow conditions and rupture. At the same time, dialysis lasts for a long time, and the surface characteristics of metal materials easily lead to platelet adhesion and aggregation, especially in low-flow areas where microthrombi may form. Summary of the Invention

[0003] The present invention aims to solve one of the technical problems in the related art to at least a certain extent. To this end, the present invention aims to provide a hemodialysis puncture needle device that can reduce blood cell damage.

[0004] To achieve the above objectives, a hemodialysis puncture needle device capable of reducing blood cell damage according to an embodiment of the present invention comprises:

[0005] A puncture needle, comprising a needle seat and a needle tube, wherein the needle seat is provided at one end of the needle tube;

[0006] a dialysis connecting tube connected to the needle seat for transporting blood to the puncture needle;

[0007] The needle tube surface has a heparin nanocoating with a thickness of 0.5 to 1 μm to reduce platelet adhesion; the needle tube includes a main section, a transition section and a puncture section connected in sequence, the inner diameter of the main section is larger than the inner diameter of the transition section, the inner diameter of the transition section is larger than the inner diameter of the puncture section, and the main section is connected to the needle seat.

[0008] According to an embodiment of the present invention, a hemodialysis puncture needle device capable of reducing blood cell damage is provided. By providing a heparin nanocoating with a thickness of 0.5 to 1 μm on the surface of the needle tube and adopting a needle tube structure with a puncture section, a transition section and a main section that expand in sequence, blood cell damage and abnormal platelet adhesion caused by direct contact with the metal needle tube surface during hemodialysis are significantly reduced. The heparin nanocoating is bonded to the substrate through a covalent bond, thereby reducing platelet adhesion. The needle tube with a sequentially expanding diameter utilizes the Bernoulli effect to reduce local shear stress, thereby reducing platelet aggregation. In this way, the fluid mechanics state of the blood in the needle tube is effectively improved, the blood flows more smoothly in the needle tube, and the red blood cell rupture and platelet activation caused by local high-speed shear force are reduced, thereby reducing the risk of microthrombosis and improving the safety of the overall dialysis operation.

[0009] In addition, the hemodialysis puncture needle device capable of reducing blood cell damage according to the above embodiment of the present invention may also have the following additional technical features:

[0010] According to one embodiment of the present invention, the heparin nanocoating contains a hydrophilic polymer, and the hydrophilic polymer is PVP or polyethylene glycol.

[0011] According to one embodiment of the present invention, the front end of the needle exit section has a needle tip, and the needle tip includes a first bevel and a second bevel connected to each other, the angle of the first bevel is greater than that of the second bevel, and the second bevel is located behind the first bevel.

[0012] According to one embodiment of the present invention, the needle seat has an upwardly protruding bypass connector;

[0013] The hemodialysis puncture needle device also includes a three-way valve, which has a first interface, a second interface and a third interface. The first interface is connected to the bypass connector, the second interface is connected to a fiber optic pressure sensor for detecting the pressure inside the puncture needle, and the third interface is connected to an injection tube for injecting physiological saline.

[0014] According to one embodiment of the present invention, it also includes a liquid pump and a controller, wherein the liquid pump is connected to the injection tube, and the controller is connected to the optical fiber sensor and the liquid pump, so as to control the liquid pump to pump a predetermined amount of physiological saline into the puncture needle in a pulsed manner when the pressure detected by the optical fiber sensor is greater than a predetermined value.

[0015] According to one embodiment of the present invention, the inner wall of the puncture section is provided with a spiral guide groove, the groove depth of the spiral guide groove is 0.1 to 0.3 mm, and is used to convert the liquid laminar flow into turbulent flow.

[0016] According to one embodiment of the present invention, an ultrasonic transducer is provided between the injection tube and the liquid pump for generating a cavitation effect during flushing with physiological saline.

[0017] According to one embodiment of the present invention, a plurality of hemispherical protrusions are provided on the inner wall of the transition point between the transition section and the puncture section. The plurality of hemispherical protrusions are spaced circumferentially along the puncture needle. The height of the hemispherical protrusions is 0.05 to 0.1 mm, and is used to destroy the boundary layer flow and inhibit platelet aggregation.

[0018] According to one embodiment of the present invention, the needle tube is made of nickel-titanium alloy, the surface of the needle tube is anodic oxidized to form an oxide layer with a porous structure, the pore size is 50 to 200 nm, and the heparin nanocoating is embedded in the porous structure.

[0019] Additional aspects and advantages of the present invention will be set forth in part in the description which follows and, in part, will be obvious from the description which follows, or may be learned by practice of the present invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on the structures shown in these drawings without paying any creative work.

[0021] Figure 1 2 is a schematic structural diagram of a hemodialysis puncture needle device capable of reducing blood cell damage according to an embodiment of the present invention;

[0022] Figure 2 This is an exploded view of a hemodialysis puncture needle device capable of reducing blood cell damage according to an embodiment of the present invention;

[0023] Figure 3 yes Figure 2 A partial enlarged view of point A in the middle;

[0024] Figure 4 This is a cross-sectional view of a puncture needle in a hemodialysis puncture needle device capable of reducing blood cell damage according to an embodiment of the present invention.

[0025] Reference numerals:

[0026] 10. Puncture needle;

[0027] 101. needle;

[0028] 1011, main body paragraph;

[0029] 1012, transition section;

[0030] 1013, puncture segment;

[0031] 102, needle holder;

[0032] 1021, bypass connector;

[0033] S101, first inclined surface;

[0034] S102, second inclined surface;

[0035] H101, spiral guide groove;

[0036] 20. Dialysis connecting tube;

[0037] 30. Three-way valve;

[0038] 301, first interface;

[0039] 302, second interface;

[0040] 303, third interface;

[0041] 31. Liquid injection tube;

[0042] 40. Light pressure sensor.

[0043] The purpose, features and advantages of the present invention will be further described with reference to the accompanying drawings and in conjunction with the embodiments. DETAILED DESCRIPTION

[0044] The following describes in detail embodiments of the present invention, examples of which are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are intended to be used to explain the present invention, and are not to be construed as limiting the present invention. All other embodiments obtained by persons of ordinary skill in the art based on the embodiments of the present invention without creative effort are within the scope of protection of the present invention.

[0045] In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", "clockwise", "counterclockwise", "axial", "circumferential", "radial", etc., indicating the orientation or position relationship, are based on the orientation or position relationship shown in the accompanying drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operate in a specific orientation, and therefore cannot be understood as limiting the present invention.

[0046] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of the technical features being referred to. Thus, a feature identified as "first" or "second" may explicitly or implicitly include one or more of the features. In the description of the present invention, "plurality" means two or more, unless otherwise specifically defined.

[0047] In the present invention, unless otherwise expressly specified or limited, the terms "mounted," "connected," "connect," "fixed," etc. should be understood broadly. For example, they may refer to fixed, detachable, or integral connections; mechanical or electrical connections; direct or indirect connections through an intermediary; or internal communication between two components. Those skilled in the art will understand the specific meanings of the above terms in the present invention based on specific circumstances.

[0048] In the present invention, unless otherwise expressly specified or limited, a first feature being "above" or "below" a second feature may include the first and second features being in direct contact, or may include the first and second features being in contact not directly but through another feature between them. Furthermore, a first feature being "above," "above," and "above" a second feature may include the first feature being directly above or obliquely above the second feature, or may simply mean that the first feature is higher in level than the second feature. A first feature being "below," "below," and "below" a second feature may include the first feature being directly below or obliquely below the second feature, or may simply mean that the first feature is lower in level than the second feature.

[0049] The hemodialysis puncture needle device capable of reducing blood cell damage according to an embodiment of the present invention will be described in detail below with reference to the accompanying drawings.

[0050] Reference Figures 1 to 4 As shown, a hemodialysis puncture needle device capable of reducing blood cell damage according to an embodiment of the present invention includes a puncture needle 10 and a dialysis connecting tube 20.

[0051] Specifically, the puncture needle 10 includes a needle seat 102 and a needle tube 101. The needle seat 102 is provided at one end of the needle tube 101. The dialysis connecting tube 20 is connected to the needle seat 102 to transport blood to the puncture needle 10.

[0052] The surface of the needle tube 101 has a heparin nanocoating with a thickness of 0.5 to 1 μm to reduce platelet adhesion. In a specific process, a plasma-enhanced chemical vapor deposition process can be used to form the heparin nanocoating on the surface of the needle tube 101. The radio frequency plasma excites active free radicals, which undergo in situ polymerization on the surface of the needle tube 101 (stainless steel / nickel-titanium alloy) to form a nanoscale film. The plasma activates the substrate surface to produce functional groups such as -OH and -COOH, which form covalent bonds with the sulfate groups of the heparin molecules, ensuring that the heparin nanocoating has a higher bonding strength on the surface of the needle tube 101.

[0053] This heparin nanocoating can release low-dose heparin. Since the heparin molecule itself has the biological activity of anti-coagulation and inhibiting platelet adhesion, the heparin nanocoating fixed by covalent bonds can significantly reduce the platelet activation and adhesion caused by direct contact between blood and metal surfaces while ensuring long-term stability, thereby reducing the risk of local microthrombosis and ensuring smooth blood flow during dialysis.

[0054] The needle tube 101 includes a main section 1011, a transition section 1012, and a puncture section 1013, which are sequentially connected. The inner diameter of the main section 1011 is larger than that of the transition section 1012, and the inner diameter of the transition section 1012 is larger than that of the puncture section 1013. The main section 1011 is connected to the needle hub 102. Exemplarily, the diameter of the main section 1011 is 0.8 to 1.2 mm, the diameter of the transition section 1012 is 0.5 to 0.8 mm, and the diameter of the puncture section 1013 is 0.3 to 0.5 mm.

[0055] In other words, the needle tube 101 adopts a variable diameter structure design, and utilizes the geometric characteristics of the diameter expansion design to improve the fluid dynamics state inside the needle tube 101. Specifically, the gradual expansion of the inner diameter from small to large can partially realize the Bernoulli effect during the fluid flow process, that is, reduce the shear stress of the fluid in the local area. For example, the diameter of the puncture section 1013 is the smallest, forming a narrow channel to reduce the initial stress of the blood impacting the needle tip. The diameter of the transition section 1012 is slightly larger, so that the blood flow rate decreases steadily to avoid stress concentration, and the diameter of the main section 1011 is the largest, ensuring that the blood passes at a low speed and reducing continuous shear force. In this way, when the blood flows in the needle tube 101, due to the reduced shear stress, the red blood cells will not rupture due to high-speed shear force. At the same time, the platelets also reduce the abnormal aggregation phenomenon caused by high-speed impact, thereby significantly reducing the cell damage and thrombosis risk caused by local non-steady-state flow.

[0056] According to an embodiment of the present invention, a hemodialysis puncture needle device capable of reducing blood cell damage is provided. By providing a 0.5 to 1 μm thick heparin nanocoating on the surface of the needle tube 101 and adopting a needle tube 101 structure with a puncture section 1013, a transition section 1012, and a main section 1011 that expand in sequence, blood cell damage and abnormal platelet adhesion caused by direct contact with the metal needle tube 101 surface during hemodialysis are significantly reduced. The heparin nanocoating is bonded to the substrate via a covalent bond, reducing platelet adhesion, while the sequentially expanding needle tube 101 utilizes the Bernoulli effect to reduce local shear stress, thereby reducing platelet aggregation. In this way, the fluid dynamics state of the blood in the needle tube 101 is effectively improved, making the blood flow in the needle tube 101 smoother, reducing red blood cell rupture and platelet activation caused by local high-speed shear force, thereby reducing the risk of microthrombosis and improving the safety of the overall dialysis operation.

[0057] In some embodiments of the present invention, the heparin nanocoating comprises a hydrophilic polymer, such as PVP or polyethylene glycol. To prepare the coating solution, heparin and a predetermined proportion of the hydrophilic polymer are dissolved in a compatible solvent, and a uniformly dispersed nanoparticle solution is obtained by ultrasonication or stirring. Using the aforementioned plasma-enhanced chemical vapor deposition process, the heparin and hydrophilic polymer form a uniform, continuous, and stable nanocoating on the surface of the needle tube 101 substrate.

[0058] On the one hand, heparin, as a natural polysaccharide with strong anticoagulant and platelet aggregation inhibitory effects, can form a firm connection with the surface of the needle tube 101 through covalent bonds, thereby forming an anticoagulant protective effect on the internal surface of the needle tube 101; on the other hand, PVP or polyethylene glycol, as a hydrophilic polymer, has a good hydration ability determined by its molecular structure, can form a hydrophilic effect on the coating surface, can quickly adsorb water molecules, and form a stable water molecule barrier, further reducing the chance of direct contact between blood and metal surfaces, thereby reducing the damage to red blood cells and platelets caused by mechanical shear or charge, and at the same time, it also reduces the resistance during needle insertion.

[0059] In one embodiment of the present invention, the front end of the needle exit section has a needle tip, which includes a first bevel S101 and a second bevel S102 connected to each other. The angle of the first bevel S101 is greater than that of the second bevel S102, and the second bevel S102 is located behind the first bevel S101.

[0060] Specifically, the first bevel S101, located at the front of the needle tip and having a larger angle, provides a stronger cutting force during puncture, allowing for rapid penetration of skin and other tissue obstacles. The second bevel S102, located behind the first bevel S101 and having a smaller angle, provides smooth guidance and mitigates tissue damage. Preferably, the junction between the first bevel S101 and the second bevel S102 utilizes a smoothly transitioning curved surface.

[0061] This embodiment provides a needle tip structure with a first bevel S101 and a second bevel S102 at the front end of the puncture section 1013, so as to achieve rapid puncture with a larger angle of the first bevel S101 and achieve a smooth transition and reduce stress concentration with a smaller angle of the second bevel S102, thereby effectively optimizing the cutting performance and biocompatibility during the puncture process, and reducing the risk of tissue damage caused by puncture.

[0062] In some embodiments of the present invention, the needle hub 102 has an upwardly protruding bypass connector 1021. The hemodialysis puncture needle 10 device further includes a three-way valve 30 having a first interface 301, a second interface 302, and a third interface 303. The first interface 301 is connected to the bypass connector 1021. The bypass interface can be a standard medical interface, such as a Luer interface, for quick connection.

[0063] The second port 302 is connected to a fiber optic pressure sensor 40, which detects the pressure within the puncture needle 10. By detecting the fluid pressure within the needle, it provides real-time monitoring of pressure changes that may occur during dialysis. The third port 303 is connected to an infusion tube 31, which is used to inject saline. If excessive pressure is detected within the needle 101, saline can be injected through the infusion tube 31 to clear the blood and prevent thrombosis.

[0064] This embodiment provides an upwardly protruding bypass connector 1021 on the needle seat 102 and connects it to the interfaces of the three-way valve 30, and connects the optical fiber pressure sensor 40 to the injection tube 31, thereby achieving real-time monitoring and timely processing of the pressure in the needle tube 101, significantly improving the safety, reliability and ease of operation of the hemodialysis puncture needle 10 device.

[0065] In one embodiment of the present invention, the hemodialysis puncture needle device that can reduce blood cell damage also includes a liquid pump and a controller. The liquid pump is connected to the injection tube 31, and the controller is connected to the optical fiber sensor and the liquid pump, so as to control the liquid pump to pump a predetermined amount of physiological saline into the puncture needle 10 in a pulsed manner when the pressure detected by the optical fiber sensor is greater than a predetermined value.

[0066] During actual use, the fiber optic pressure sensor 40 monitors pressure changes within the needle tube 101 in real time. When the detected pressure exceeds a predetermined threshold, the controller, receiving a signal from the fiber optic pressure sensor 40, actively controls the liquid pump to pulse-inject saline into the puncture needle 10. Driven by the controller's pulse signal, the liquid pump delivers a predetermined amount of saline at a preset injection volume and pulse frequency, ensuring timely and effective flushing of the needle tube 101 and helping to eliminate potential fluid blockages or blood clotting.

[0067] This embodiment realizes real-time monitoring and feedback control of the pressure inside the puncture needle 10 through the cooperation of a liquid pump and a controller, and injects a predetermined amount of normal saline in a pulse manner when abnormal pressure is detected, which can effectively alleviate local pressure abnormalities, prevent blood coagulation, and significantly improve the safety and stability of hemodialysis.

[0068] In one embodiment of the present invention, the inner wall of the puncture section 1013 is provided with a spiral guide groove H101, the spiral guide groove having a depth of 0.1 to 0.3 mm, for converting the liquid laminar flow into turbulent flow. For example, the spiral angle is 15° to 30°.

[0069] When blood in a laminar flow state enters the puncture section 1013 with the spiral guide groove H101, the fluid undergoes three-dimensional spiral motion under the guidance of the spiral guide groove H101, forming a stable weak turbulence state. This turbulence has a low eddy current intensity, which can not only destroy the local concentration gradient in the blood and prevent platelets and coagulation factors from enriching near the tube wall, but also does not produce high shear stress that damages red blood cells. At the same time, the centrifugal effect generated by the spiral flow prompts blood cells to migrate toward the center of the lumen, further reducing the probability of direct contact between blood cells and the metal surface. In addition, the weak turbulence effect of the spiral guide groove H101 can inhibit the formation of a pre-thrombotic state. Compared with the puncture section 1013 with a smooth inner wall, the structure of the spiral guide groove H101 reduces the release of platelet activation markers and reduces fibrinogen deposition.

[0070] In one embodiment of the present invention, an ultrasonic transducer is provided between the injection tube 31 and the liquid pump for generating a cavitation effect during flushing with physiological saline.

[0071] In a specific application, when the controller controls the liquid pump to inject physiological saline into the puncture needle 10, at the same time, it controls the ultrasonic transducer to start, so that it generates an axially propagating ultrasonic field in the injection tube 31, which can induce a stable cavitation effect in the flowing physiological saline. The cavitation effect can improve the flushing effect of the physiological saline.

[0072] Preferably, the operating frequency of the ultrasonic transducer is 28±2kHz, the sound pressure amplitude is 0.4-0.8MPa, and the power density is 3-5W / cm2 The single action time is less than 100ms. Under these working parameters, the device not only ensures the function of clearing and preventing blood clots, but also ensures the integrity of blood cells. The red blood cell rupture rate is less than 0.1%, which is far lower than the 0.5% standard allowed by dialysis.

[0073] In one embodiment of the present invention, the inner wall of the transition between the transition section 1012 and the puncture section 1013 is provided with a plurality of hemispherical protrusions, and the plurality of hemispherical protrusions are spaced circumferentially along the puncture needle 10. The height of the hemispherical protrusions is 0.05-0.1 mm, which is used to destroy the boundary layer flow and inhibit platelet aggregation.

[0074] As blood flows through transition section 1012 and into puncture section 1013, the hemispherical protrusions generate periodic vortices within the boundary layer of the tube wall, disrupting any low-speed retention zones that might otherwise form and making it difficult for platelets to stably adhere to the tube wall. Furthermore, these tiny hemispherical protrusions inhibit thrombosis while protecting blood cell integrity.

[0075] In one embodiment of the present invention, the needle tube 101 is made of nickel-titanium alloy, and the surface of the needle tube 101 is anodized to form an oxide layer with a porous structure, with a pore size of 50-200 nm, and the heparin nanocoating is embedded in the porous structure.

[0076] A porous oxide layer is formed on the surface of the nickel-titanium alloy needle tube 101 by anodizing, and a heparin nanocoating is embedded therein to increase the local concentration of heparin molecules and form an anticoagulant sustained-release zone. When blood flows through, the heparin in the pores is continuously released at a lower rate. In this way, the local utilization rate and duration of the anticoagulant are greatly improved through the nano-confinement effect.

[0077] In the description of this specification, the reference terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" mean that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner. In addition, those skilled in the art can combine and combine different embodiments or examples described in this specification and features of different embodiments or examples without contradiction.

[0078] The above description is only a preferred embodiment of the present invention and does not limit the patent scope of the present invention. All equivalent structural transformations made by using the contents of the present invention description and drawings under the inventive concept of the present invention, or direct / indirect application in other related technical fields are included in the patent protection scope of the present invention.

Claims

1. A hemodialysis puncture needle device capable of reducing blood cell damage, characterized in that: include: A puncture needle, comprising a needle seat and a needle tube, wherein the needle seat is provided at one end of the needle tube; a dialysis connecting tube connected to the needle seat for transporting blood to the puncture needle; The needle tube surface has a heparin nanocoating with a thickness of 0.5 to 1 μm to reduce platelet adhesion; the needle tube includes a main section, a transition section and a puncture section connected in sequence, the inner diameter of the main section is larger than the inner diameter of the transition section, the inner diameter of the transition section is larger than the inner diameter of the puncture section, and the main section is connected to the needle seat.

2. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 1, characterized in that: The heparin nano coating contains a hydrophilic polymer, and the hydrophilic polymer is PVP or polyethylene glycol.

3. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 1, characterized in that: The front end of the puncture section has a needle tip, and the needle tip includes a first inclined surface and a second inclined surface connected to each other. The angle of the first inclined surface is greater than that of the second inclined surface, and the second inclined surface is located behind the first inclined surface.

4. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 1, characterized in that: The needle seat is provided with a bypass connector protruding upward; The hemodialysis puncture needle device also includes a three-way valve, which has a first interface, a second interface and a third interface. The first interface is connected to the bypass connector, the second interface is connected to a fiber optic pressure sensor for detecting the pressure inside the puncture needle, and the third interface is connected to an injection tube for injecting physiological saline.

5. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 4, characterized in that: It also includes a liquid pump and a controller, wherein the liquid pump is connected to the injection tube, and the controller is connected to the optical fiber sensor and the liquid pump, so as to control the liquid pump to pump a predetermined amount of physiological saline into the puncture needle in a pulsed manner when the pressure detected by the optical fiber sensor is greater than a predetermined value.

6. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 1, characterized in that: The inner wall of the puncture section is provided with a spiral guide groove, the groove depth of the spiral guide groove is 0.1 to 0.3 mm, and is used to convert the liquid laminar flow into turbulent flow.

7. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 5, characterized in that: An ultrasonic transducer is provided between the liquid injection tube and the liquid pump for generating a cavitation effect during flushing with physiological saline.

8. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 1, characterized in that: The inner wall of the transition between the transition section and the puncture section is provided with a plurality of hemispherical protrusions, which are spaced circumferentially along the puncture needle. The height of the hemispherical protrusions is 0.05 to 0.1 mm, and is used to destroy the boundary layer flow and inhibit platelet aggregation.

9. The hemodialysis puncture needle device capable of reducing blood cell damage according to claim 1, characterized in that: The needle tube is made of nickel-titanium alloy, and the surface of the needle tube is anodic oxidized to form an oxide layer with a porous structure, with a pore size of 50 to 200 nm, and the heparin nanocoating is embedded in the porous structure.

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