Electrically-controlled bending-adjustable nerve intervention guide wire device

Abstract

The utility model relates to an electrically-controlled bending-adjustable nerve intervention guide wire device which comprises a handle, a reducing core tube, an electroactive polymerization wire, a conductive wire and a guide sleeve, the reducing core tube is of a hollow tubular structure, the near end of the reducing core tube is installed in the handle, the far end of the reducing core tube freely extends, one end of the electroactive polymerization wire in the length direction is connected with the reducing core tube, and the other end of the electroactive polymerization wire freely extends; the conductive wire is suitable for being electrically connected with a battery pack, the conductive wire penetrates through the near end of the variable-diameter core tube and penetrates out of the side wall of the far end of the variable-diameter core tube, the conductive wire is wound outside the electroactive polymerization wire to regulate and control the temperature of the electroactive polymerization wire, and the guide sleeve is arranged outside the variable-diameter core tube, the electroactive polymerization wire and the conductive wire in a sleeving mode. After the conductive wire is electrified and heated, the temperature of the electroactive polymerization wire is regulated and controlled, so that the electroactive polymerization wire is bent or straightened, and the problem that the expected bending angle cannot be reached due to friction between the core wire and the inner wall of the guide wire after multiple parts of the guide wire are bent is solved, so that the problem that the bending angle of the far end is not in place due to the bending of the middle section of the guide wire is solved.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to an electrically controlled adjustable bendable nerve intervention guidewire device. Background Technology

[0002] In the early stages before rupture, intracranial aneurysms compress nerve tissue. Aneurysms in different locations can cause corresponding pathological symptoms; for example, compression of the optic nerve can cause shadows in the visual field, potentially leading to blindness. Subarachnoid hemorrhage caused by aneurysm rupture can lead to stroke. Current treatments for intracranial aneurysms include surgical clipping and interventional therapy. Considering the slow healing after craniotomy in elderly patients, interventional therapy is often used. Interventional devices include auxiliary stents, auxiliary coil tamponade, flow diversion devices, and woven material tamponade. Currently, guidewire tip deformation is achieved through mechanical force to create an arc. The operator uses auxiliary instruments to change the arc of the distal guidewire, which usually requires the assistance of fingers, thus prolonging the operation time and increasing the complexity of the procedure. Utility Model Content

[0003] In view of this, this application proposes an electrically controlled adjustable bending guidewire device for nerve intervention, which facilitates adjustment of the distal bending of the guidewire.

[0004] According to one aspect of this application, an electrically controllable adjustable bending nerve intervention guidewire device is provided, comprising: a handle;

[0005] The variable diameter core tube is a hollow tubular structure. The proximal end of the variable diameter core tube is installed inside the handle, and the distal end extends freely.

[0006] An electroactive polymer filament, one end of which is connected to the variable diameter core tube along its length, and the other end extends freely;

[0007] A conductive wire, suitable for electrically connecting battery packs, passes through the proximal end of the variable diameter core tube and exits through the distal sidewall of the variable diameter core tube, and the conductive wire is wound around the outside of the electroactive polymer wire to regulate the temperature of the electroactive polymer wire;

[0008] A guide sleeve is fitted over the outside of the variable diameter core tube, the electroactive polymer filament, and the conductive filament.

[0009] In one possible implementation, the conductive wire is uniformly spirally wound around the outside of the electroactive polymer wire.

[0010] In one possible implementation, the electroactive polymer filament is laser-welded or riveted to the conductive filament.

[0011] In one possible implementation, the cross-section of the conductive wire, which is bolted and wound along the axial direction of the variable diameter core tube, is annular.

[0012] In one possible implementation, the cross-section of the electroactive polymer filament is circular, rectangular, or semi-circular.

[0013] In one possible implementation, the guide sleeve includes: a spring guide sleeve;

[0014] The spring guide sleeve has a spiral structure;

[0015] The inner diameter of the spring guide sleeve matches the outer diameter of the variable diameter core tube;

[0016] The spring guide sleeve is fitted over the variable diameter core tube, the electroactive polymer filament, and the conductive filament.

[0017] In one possible implementation, the proximal end of the guide sleeve abuts against the distal end of the handle.

[0018] In one possible implementation, the variable diameter core tube has more than one variable diameter section in its axial direction.

[0019] In one possible implementation, the outer surface of the variable diameter core tube is coated with a PTFE coating.

[0020] In one possible implementation, the surface of the conductive wire is coated with a hydrophilic coating.

[0021] In one possible implementation, the electroactive polymer filament is a nickel-titanium filament.

[0022] In one possible implementation, a conductive through-hole is provided at the distal end of the variable diameter core tube, the diameter of the conductive through-hole being matched with the diameter of the conductive wire, and the conductive wire passing through the conductive through-hole and winding around the outside of the electroactive polymer wire.

[0023] In one possible implementation, the conductive wire is a developing ring.

[0024] In one possible implementation, the distal end of the handle has a circular cross-section that matches the cross-sectional diameter of the conductive wire.

[0025] In one possible implementation, the distal cross-sectional diameter of the conductive filament is equal to the proximal cross-sectional diameter of the electroactive polymer filament.

[0026] The beneficial effects of the electrically controlled adjustable bending guidewire device in this application embodiment are as follows: A conductive wire, sleeved outside the electroactive polymer wire, carries an electric current. After the conductive wire heats up, the temperature of the electroactive polymer wire is controlled, causing it to bend or straighten, ensuring that the length of the device's tip is not affected. Specifically, achieving bending by electrically controlling the wire's state has a significant advantage over traditional adjustable guidewires that rely on mechanical pulling of the core wire. This design avoids the problem of the core wire failing to reach the expected bending angle due to friction between the core wire and the inner wall of the guidewire after multiple bends. Therefore, the guidewire does not suffer from insufficient bending angle at the distal end due to bending in the middle section.

[0027] Other features and aspects of this application will become clear from the following detailed description of exemplary embodiments with reference to the accompanying drawings. Attached Figure Description

[0028] The accompanying drawings, which are included in and form part of this specification, illustrate exemplary embodiments, features, and aspects of this application together with the specification and serve to explain the principles of this application.

[0029] Figure 1 This is a schematic diagram of the main structure of the electrically controlled adjustable bending nerve intervention guidewire device according to an embodiment of this application;

[0030] Figure 2 This is a cross-sectional schematic diagram of an embodiment of the electrically controlled adjustable bendable nerve intervention guidewire device of this application;

[0031] Figure 3 Another cross-sectional schematic diagram of the electrically controlled adjustable bendable nerve intervention guidewire device according to an embodiment of this application is shown;

[0032] Figure 4 A schematic diagram of the main structure of the variable diameter core tube according to an embodiment of this application is shown;

[0033] Figure 5 This illustration shows another main structural diagram of the electrically controlled adjustable bending nerve intervention guidewire device according to an embodiment of this application;

[0034] Figure 6 This illustration shows another main structural diagram of the electrically controlled adjustable bending nerve intervention guidewire device according to an embodiment of this application;

[0035] Figure 7 This illustration shows another main structural diagram of the electrically controlled adjustable bending nerve intervention guidewire device according to an embodiment of this application;

[0036] Figure 8 A circuit diagram of an electrically controlled adjustable bendable nerve intervention guidewire device according to an embodiment of this application is shown. Detailed Implementation

[0037] Various exemplary embodiments, features, and aspects of this application will now be described in detail with reference to the accompanying drawings. The same reference numerals in the drawings denote elements that have the same or similar functions. Although various aspects of the embodiments are shown in the drawings, they are not necessarily drawn to scale unless specifically indicated otherwise.

[0038] It should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", and "circumferential" indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this utility model or 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. Therefore, they should not be construed as limitations on this utility model.

[0039] 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 technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this utility model, "a plurality of" means two or more, unless otherwise explicitly specified.

[0040] The term “exemplary” as used herein means “serving as an example, embodiment, or illustration.” Any embodiment illustrated herein as “exemplary” is not necessarily to be construed as superior to or better than other embodiments.

[0041] Furthermore, to better illustrate this application, numerous specific details are provided in the following detailed embodiments. Those skilled in the art should understand that this application can be implemented without certain specific details. In some instances, methods, means, components, and circuits well-known to those skilled in the art have not been described in detail in order to highlight the main points of this application.

[0042] like Figure 1 As shown, the electrically controlled adjustable bending nerve intervention guidewire device of this application embodiment includes: a handle 7, a variable diameter core tube 3, an electroactive polymer wire 2, a conductive wire 1, and a guide sleeve. The variable diameter core tube 3 is a hollow tubular structure. The proximal end of the variable diameter core tube 3 is installed in the handle 7, and the distal end extends freely. One end of the electroactive polymer wire 2 in the length direction is connected to the variable diameter core tube 3, and the other end extends freely. The conductive wire 1 is suitable for electrically connecting to the battery pack 74. The conductive wire 1 passes through the proximal end of the variable diameter core tube 3 and exits through the distal sidewall of the variable diameter core tube 3. The conductive wire 1 is wrapped around the outside of the electroactive polymer wire 2 to regulate the temperature of the electroactive polymer wire 2. The guide sleeve is fitted on the outside of the variable diameter core tube 3, the electroactive polymer wire 2, and the conductive wire 1.

[0043] In this embodiment, a current flows through the conductive wire 1, which is sleeved outside the electroactive polymer wire 2. After the conductive wire 1 is energized and heated, the temperature of the electroactive polymer wire 2 is adjusted to bend or straighten it, ensuring that the front end of the device is not affected by its length. Specifically, the bending purpose is achieved by electrically controlling the change of the wire's state. Compared with the traditional adjustable bending guide wire that uses mechanical pulling of the core wire, this design does not fail to achieve the expected bending angle due to friction between the core wire and the inner wall of the guide wire after multiple bends. Therefore, the guide wire will not have the problem of insufficient bending angle at the distal end due to bending in the middle section.

[0044] The handle 7 serves as the central operating point of the entire device, facilitating a secure grip and precise operation by medical personnel. It integrates control switches and interfaces for connection to an external power source. The proximal end of the variable-diameter core tube 3 is firmly mounted inside the handle 7, while its distal end extends freely, providing flexible guidance and support for the guidewire. The electroactive polymer wire 2 is a special alloy material with excellent shape memory effect and superelasticity, capable of automatically adjusting its shape under temperature changes, enabling the guidewire to bend and recover, thus easily traversing complex vascular pathways and accurately reaching the lesion site. The conductive wire 1, as a component of the temperature control system, passes through the proximal end of the variable-diameter core tube 3 and exits through its distal sidewall, then tightly wraps around the outside of the electroactive polymer wire 2. Connected to the external battery pack 74, the conductive wire 1 transfers electrical energy to the electroactive polymer wire 2, generating heat and precisely regulating its temperature. As a protective and insulating layer, the guide sleeve is tightly fitted around the outside of the variable diameter core tube 3, the electroactive polymer filament 2, and the conductive wire 1, effectively preventing friction and wear between the components, ensuring the sealing and insulation of the entire device, and further improving the safety of the operation.

[0045] It should be noted that this application heats the active polymer filament 2 covered by the conductive wire 1 by passing electricity through the conductive wire 1, thereby causing the active polymer filament 2 to bend or recover.

[0046] In one specific embodiment, the conductive wire 1 is uniformly spirally wound around the electroactive polymer wire 2, maximizing the contact area between the conductive wire 1 and the electroactive polymer wire 2, thereby improving the efficiency of heat transfer. When the conductive wire 1 is energized and generates heat, this heat can be quickly and evenly distributed onto the electroactive polymer wire 2, achieving the preset temperature control requirements. Furthermore, the spiral winding method allows the conductive wire 1 to be uniformly wound around the nickel-iron wire. When the conductive wire 1 is energized, it can heat the wound electroactive polymer wire 2. Because the nickel-titanium wire is heated uniformly, the electroactive polymer wire 2 can bend or recover as a whole due to heating.

[0047] In this embodiment, the uniform spiral winding also gives the entire device higher structural stability and durability. The close fit between the conductive wire 1 and the electroactive polymer wire 2 reduces relative sliding and wear caused by movement or vibration, and extends the service life of the device.

[0048] In this embodiment, a spirally wound conductive wire 1 is used, which facilitates the bending and recovery of the electroactive polymer wire 2 after being heated. Specifically, the spiral winding creates a gap between adjacent circumferential components on the axial conductive wire 1, thus facilitating the bending and recovery of the electroactive polymer wire 2.

[0049] In one specific embodiment, the electroactive polymer wire 2 and the conductive wire 1 are laser welded or riveted together. Whether it is laser welding or riveting, both technologies can effectively achieve a stable bond between the electroactive polymer wire 2 and the conductive wire 1, meeting the performance requirements of different application scenarios.

[0050] Furthermore, the conductive wire 1 and the electroactive polymer wire 2 are fixed by laser welding or riveting. Since the conductive wire 1 is spirally sleeved on the outside of the electroactive polymer wire 2, the fixation of the conductive wire 1 and the electroactive polymer wire 2 will not be affected even if the electroactive polymer wire 2 is completely fixed.

[0051] In one specific embodiment, the connection method between the electroactive polymer filament 2 and the variable diameter core filament includes adhesive bonding, laser welding, and sleeve connection.

[0052] In one specific embodiment, the material of the distal portion of the conductive wire 1 may include, but is not limited to, precious metal alloys such as platinum-iridium and platinum-tungsten, and metallic materials such as gold and silver.

[0053] In one specific embodiment, the conductive wire 1, which is bolted and wound along the axial direction of the variable-diameter core tube 3, has an annular cross-section, serving as a developing ring. The annular cross-section of the conductive wire 1 not only increases the contact area between the conductive wire 1 and its surrounding environment, facilitating uniform current distribution and transmission, but also enhances its mechanical strength, allowing it to maintain stable conductivity even under various stresses and deformations. The annular cross-section of the conductive wire 1 can enhance the developing or display effect, thereby improving image detail.

[0054] Furthermore, the cross-section of the electroactive polymer fiber 2 can be circular, rectangular, or semi-circular. A circular cross-section of the electroactive polymer fiber 2 results in uniform mechanical and thermal conductivity in all directions, facilitating uniform deformation and recovery. A rectangular cross-section of the electroactive polymer fiber 2 exhibits higher rigidity and load-bearing capacity; due to its larger cross-sectional dimensions in specific directions, it can resist greater bending and torsional forces. A semi-circular cross-section of the electroactive polymer fiber 2 combines some characteristics of both circular and rectangular cross-sections, possessing both a certain degree of rigidity and load-bearing capacity while also achieving a degree of uniform deformation and recovery.

[0055] In this embodiment, the conductive through hole at the far end of the variable diameter core tube 3 allows the conductive wire 1 to pass through and wrap around the outside of the electroactive polymer wire 2, ensuring the reliability of the electrical connection.

[0056] In one specific embodiment, the guide sleeve includes a spring guide sleeve. The spring guide sleeve has a spiral structure, and its inner diameter matches the outer diameter of the variable diameter core tube 3. The spring guide sleeve is fitted over the variable diameter core tube 3, the electroactive polymer filament 2, and the conductive filament 1. The spring-shaped conductor ensures that the guide sleeve can securely wrap around and guide the variable diameter core tube 3, and also allows both to maintain a certain degree of flexibility and adaptability during relative movement. The spring guide sleeve can closely conform to the changing shape of the variable diameter core tube 3, ensuring the stability and reliability of the entire system. It not only provides the necessary protection and support, but also ensures that they can function stably.

[0057] In another specific embodiment, the guide sleeve includes a keyway guide sleeve, which is a tubular structure with keyways on its outer wall. The keyways are arranged along the axial direction of the keyway conductor, enhancing the flexibility of the keyway guide sleeve. Specifically, the keyways on the keyway guide sleeve are not only for structural strength and positioning accuracy but also significantly improve its flexibility. The presence of the keyways allows the keyway guide sleeve to bend and deform more smoothly when subjected to external forces, thus making it easier to pass through or adapt to various irregular spaces and shapes, such as the vascular network in the human body. Multiple keyways are provided, spaced apart from one end of the keyway guide sleeve's length direction to the other end, with the spacing between adjacent keyways following a specific mathematical relationship.

[0058] In one specific embodiment, the variable diameter core tube 3 has one or more variable diameter segments along its axial direction. The axial direction of the variable diameter core tube 3 is divided into one or more variable diameter segments, and the diameter of each variable diameter segment is different from that of its adjacent segments. This change in diameter can be gradual or abrupt, and the number, position, and magnitude of the diameter change of the variable diameter segments are also variable. Furthermore, the multi-segment variable diameter design of the variable diameter core tube 3 enhances its structural flexibility and adaptability. Segments with different diameters can withstand different loads and stresses, thereby optimizing the overall structural strength and stiffness.

[0059] In this embodiment, because the circumferential diameters of each segment of the variable-diameter core tube 3 are different, they serve different functions at different positions. The proximal end of the variable-diameter core tube 3 is embedded in the handle 7, while the distal end extends freely. Therefore, the proximal end of the variable-diameter core tube 3 is used to fix it to the handle 7, while the distal end is connected to the electroactive polymer fiber 2. The different circumferential diameters enable different functions. A larger circumferential diameter at the proximal end of the variable-diameter core tube 3 improves its stability and firmness, while a smaller circumferential diameter at the proximal end improves its flexibility, facilitating bending or repositioning within tortuous blood vessels.

[0060] In one specific embodiment, the variable diameter tube 3 is coated with a PTFE coating, which helps reduce resistance during the procedure. Furthermore, it improves the corrosion resistance, abrasion resistance, insulation, and ease of cleaning of the variable diameter tube 3, and ensures stable and efficient use of the variable diameter tube 3 within tortuous blood vessels.

[0061] In one specific embodiment, the electroactive polymer can be a nickel-titanium wire, which can automatically bend or return to its original shape according to temperature changes. Thus, when the conductive wire 1 is wrapped around the outside of the nickel-titanium wire, the conductive wire 1 is energized and the temperature rises, causing the nickel-titanium wire to bend and change shape, and when the conductive wire 1 is de-energized, the nickel-titanium wire will return to its original shape.

[0062] In one specific embodiment, the distal end of the handle 7 body is tapered, which facilitates the doctor's control of the handle 7 and ensures the stability of the guidewire during the operation.

[0063] In this embodiment, the distal cross-section of the handle 7 is circular, matching the cross-sectional diameter of the conductive wire 1. Furthermore, the distal cross-sectional diameter of the conductive wire 1 is equal to the proximal cross-sectional diameter of the electroactive polymerized wire 2, thereby reducing the gap between the inner wall of the distal opening of the handle 7 and the outer wall of the variable diameter core tube 3, and ensuring the connection stability between the variable diameter core tube 3 and the handle 7.

[0064] In one specific embodiment, the handle 7 includes: a handle body, a sliding rheostat 75, a battery pack 74, a current fuse 72, a nickel-titanium wire 76, a control chip 73, and a temperature sensor 71, used to turn on and control the magnitude of the current, thereby regulating the degree of bending and recovery of the nickel-titanium wire.

[0065] In this embodiment, the sliding rheostat 75, the nickel-titanium wire 76, the battery pack 74, and the control chip 73 are connected in series to form a closed circuit, and the temperature sensor 71, the nickel-titanium wire 76, and the control chip 73 are also connected in series to form a closed circuit. The nickel-titanium wire 76 is connected in series with the sliding rheostat 75. By adjusting the resistance of the sliding rheostat 75, the current flowing through the nickel-titanium wire 76 is adjusted, thereby obtaining the temperature of the nickel-titanium wire 76 during adjustment. Since the nickel-titanium wire 76 and the nickel-titanium wire are made of the same material, the temperature sensor 71, connected in series with the nickel-titanium wire 76, can obtain the temperature of the nickel-titanium wire 76 at this time, and thus obtain the temperature and bending status of the nickel-titanium wire. Specifically, the sliding rheostat 75, the nickel-titanium wire 76, the battery pack 74, and the control chip 73 form a closed-loop control circuit, and the temperature sensor 71, the nickel-titanium wire 76, and the control chip 73 are connected in series to monitor and provide feedback on the temperature status of the nickel-titanium wire 76 in real time. The nickel-titanium wire 76 is directly connected in series with the sliding rheostat 75 in the circuit provided by the battery pack 74. The current flowing through the nickel-titanium wire 76 can be precisely controlled by adjusting the resistance of the sliding rheostat 75. Changes in current directly cause changes in the wire's temperature. The nickel-titanium wire 76 and the nickel-titanium wire are made of the same material and exhibit similar temperature change characteristics under the same current and environment. Therefore, a temperature sensor 71 is connected in series with the nickel-titanium wire 76. The sensor can capture and convert the temperature information of the nickel-titanium wire 76 into an electrical signal in real time, and then transmit these signals to the control chip 73 for processing. The control chip 73 receives the temperature data from the temperature sensor 71 to correct the degree of bending, greatly improving the overall response speed and adjustment accuracy. The degree of bending can be directly seen by the doctor under DSA, allowing the doctor to control the nickel-titanium wire more flexibly and accurately in complex medical procedures.

[0066] In this embodiment, the temperature of the nickel-titanium wire 76 is the same as that of the nickel-titanium wire. The temperature information is transmitted to the control chip 73. The doctor adjusts the sliding rheostat 75 according to the degree of tortuosity of the blood vessel and the degree of bending of the nickel-titanium wire.

[0067] In this embodiment, it should be noted that the current flowing through the electroactive polymer wire 2 is changed by altering the current through the proximal handle 7, causing the electroactive polymer wire 2 to heat up and the nickel-titanium wire to shrink, thereby changing its length and achieving the purpose of bending the guide wire. The phase transition temperature of the electroactive polymer wire 2 is selected and controlled; its phase transition temperature should be higher than normal human body temperature but lower than safe human body temperature. When the electroactive polymer wire 2 is a nickel-titanium wire, reference materials show that the phase transition temperatures of shrinkable TiNi materials include 20~40℃, 45~90℃, and 5~15℃. Theoretically, the temperature of the electroactive polymer wire 2 can be controlled by adjusting the current, thereby controlling the amount of shrinkage of the electroactive polymer wire 2. Therefore, temperature detection is particularly important. The temperature of the nickel-titanium wire is theoretically calculated and the data measured by the temperature sensor 71 is fitted in real time to form a closed-loop feedback control current. The theoretical heat generation can be obtained using the power formula: W=I^2RT (I is the current, R is the resistance of the nickel-titanium wire, and T is the time). Because the guide wire is too small, the temperature sensor 71 cannot be installed at the distal end of the guide wire. Therefore, a proportionally shortened nickel-titanium wire of the same type is placed in the handle 7 and energized with the same current to replace the distal end for real-time temperature monitoring. Based on the thermal energy Q=CMΔt and the power formula, the current value at a given temperature and time can be calculated. Applying the current to the nickel-titanium wire yields the actual measured temperature. When the measured temperature is higher than the given temperature, the control current is automatically reduced to ensure the actual temperature dynamically approaches the given temperature, and the guide wire returns to its original state, cooling down through its own heat dissipation.

[0068] In this embodiment, the sliding rheostat 75, battery pack 74, current fuse 72, nickel-titanium wire 76, control chip 73 and temperature sensor 71 are all located inside the handle 7 body.

[0069] The various embodiments of this application have been described above. These descriptions are exemplary and not exhaustive, nor are they limited to the disclosed embodiments. Many modifications and variations will be apparent to those skilled in the art without departing from the scope and spirit of the described embodiments. The terminology used herein is chosen to best explain the principles, practical application, or improvement of the technology in the market, or to enable others skilled in the art to understand the embodiments disclosed herein.

Claims

1. An electrically controlled adjustable bendable nerve intervention guidewire device, characterized in that, include: handle; The variable diameter core tube is a hollow tubular structure. The proximal end of the variable diameter core tube is installed inside the handle, and the distal end extends freely. An electroactive polymer filament, one end of which is connected to the variable diameter core tube along its length, and the other end extends freely; A conductive wire passes through the proximal end of the variable diameter core tube and exits through the distal sidewall of the variable diameter core tube, and the conductive wire is wound around the outside of the electroactive polymer filament; the conductive wire can regulate the temperature of the electroactive polymer filament by connecting to a power source. A guide sleeve is fitted over the outside of the variable diameter core tube, the electroactive polymer filament, and the conductive filament.

2. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The conductive wire is uniformly spirally wound around the outside of the electroactive polymer wire.

3. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 2, characterized in that, The electroactive polymer filament is laser-welded or riveted to the conductive filament.

4. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 2, characterized in that, Along the axial direction of the variable diameter core tube, the cross-section of the conductive wire, which is bolted and wound, is annular.

5. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The cross-section of the electroactive polymer filament is circular, rectangular, or semi-circular.

6. The electrically controlled adjustable bendable nerve intervention guidewire device according to any one of claims 1 to 5, characterized in that, The guide sleeve is a spring guide sleeve; The spring guide sleeve has a spiral structure; The inner diameter of the spring guide sleeve matches the outer diameter of the variable diameter core tube; The spring guide sleeve is fitted over the variable diameter core tube, the electroactive polymer filament, and the conductive filament.

7. The electrically controlled adjustable bendable nerve intervention guidewire device according to any one of claims 1 to 5, characterized in that, The proximal end of the guide sleeve abuts against the distal end of the handle.

8. The electrically controlled adjustable bendable nerve intervention guidewire device according to any one of claims 1 to 5, characterized in that, The variable diameter core tube has one or more variable diameter sections in its axial direction.

9. The electrically controlled adjustable bending nerve intervention guidewire device according to claim 8, characterized in that, The variable diameter core tube is coated with a PTFE coating.

10. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The surface of the conductive wire is coated with a hydrophilic coating.

11. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The electroactive polymerized wire is a nickel-titanium wire.

12. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The distal end of the variable diameter core tube is provided with a conductive through hole, the diameter of which matches the diameter of the conductive wire, and the conductive wire passes through the conductive through hole and winds around the outside of the electroactive polymer wire.

13. The electrically controlled adjustable bending nerve intervention guidewire device according to claim 4, characterized in that, The conductive wire is a developing ring.

14. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The distal end of the handle has a circular cross-section, which matches the cross-sectional diameter of the conductive wire.

15. The electrically controlled adjustable bendable nerve intervention guidewire device according to claim 1, characterized in that, The distal cross-sectional diameter of the conductive wire is equal to the proximal cross-sectional diameter of the electroactive polymer wire.

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