Back root ganglion stimulating electrode with lubricity

Abstract

The utility model relates to the field of implantable medical equipment, in particular to a dorsal root ganglion stimulating electrode with lubricity, which comprises a stimulating portion, a protective tube, a connecting portion and an inner tube, the inner tube penetrates through the stimulating portion, the protective tube and the connecting portion, and the stimulating electrode is further provided with a first colloidal body and a second colloidal body. The first colloid fills the gap between the stimulation part and the inner tube and extends into a part of the gap between the protection tube and the inner tube, and the second colloid fills the gap between the connection part and the inner tube and extends into a part of the gap between the protection tube and the inner tube; the first colloid and the second colloid enhance stiffness and structural strength of the stimulation part and the connection part, a coating prepared from a hydrophilic material is arranged on the peripheral side of the protection tube, and the coating improves lubricating conditions of the surface of the electrode and reduces electrode displacement and fracture risks.

Description

Technical Field

[0001] The utility model relates to the field of implantable medical devices, in particular to a dorsal root ganglion stimulating electrode with lubricity. Background Art

[0002] The dorsal root ganglion (DRG) is located on the inner side of the intervertebral foramen outside the spinal dura mater sac, near the dorsal side of the upper part of the intervertebral foramen, and belongs to the swollen nodule of the dorsal root of the spinal nerve. The cell bodies of the pseudounipolar neurons in the dorsal root ganglion can block and amplify the peripheral input signals through their own electrical activities, and have a low-pass filtering effect. By implanting a stimulator into the body, the dorsal root ganglion can be directly stimulated through the stimulating electrode. However, the stimulating electrode needs to pass through the lamina gap and the intervertebral foramen, passing through the narrow bony channels twice. The friction between the stimulating electrode in the prior art and the surrounding tissues is large, which increases the risks of electrode displacement and fracture. Content of the Utility Model

[0003] In view of this, the utility model provides a dorsal root ganglion stimulating electrode with lubricity, which includes a stimulating part, a protection tube, a connecting part and an inner tube, and the inner tube penetrates through the stimulating part, the protection tube and the connecting part;

[0004] The stimulating electrode is further provided with a first colloidal body and a second colloidal body. The first colloidal body fills the gap between the stimulating part and the inner tube and extends into part of the gap between the protection tube and the inner tube. The second colloidal body fills the gap between the connecting part and the inner tube and extends into part of the gap between the protection tube and the inner tube;

[0005] The outer peripheral side of the protection tube is further provided with a hydrophilic coating.

[0006] Further, in some embodiments of the utility model, the outer peripheral side of the protection tube is provided with micro-nano structures, and the coating maps the micro-nano structures.

[0007] Further, in some embodiments of the utility model, the thickness of the coating is 0.1mm - 0.3mm.

[0008] Further, in some embodiments of the utility model, the outer peripheral side of the protection tube is further provided with a concave cavity. The depth of the concave cavity in the radial direction is 0.1mm - 0.15mm. The size of the cavity opening of the concave cavity is smaller than the size of the cavity body of the concave cavity, and the concave cavity is filled with the coating.

[0009] Further, in some embodiments of the utility model, the stimulating part includes a plurality of contact points and isolation rings located between adjacent two of the contact points;

[0010] The contact points and the isolation rings are respectively sleeved on the inner tube and are bonded to the inner tube through the first colloidal body.

[0011] Further, in some embodiments of the present invention, the length of the stimulation electrode ranges from 400 mm to 600 mm;

[0012] The contact is ring-shaped, with a length ranging from 1mm to 2mm and an outer diameter ranging from 1mm to 1.5mm.

[0013] Furthermore, in some embodiments of the present invention, the interval between two adjacent contacts is in the range of 4 mm to 6 mm.

[0014] Furthermore, in some embodiments of the present invention, the extension length of the first colloid in the gap between the protection tube and the inner tube is in the range of 1 mm to 3 mm.

[0015] Furthermore, in some embodiments of the present invention, the connecting portion includes a positioning ring disposed adjacent to the protective tube.

[0016] Furthermore, in some embodiments of the present invention, the second colloid extends within the gap between the protection tube and the inner tube for a length less than 5 mm.

[0017] The utility model provides a dorsal root ganglion stimulation electrode with lubricity, comprising a stimulation part, a protective tube, a connecting part and an inner tube, wherein the inner tube passes through the stimulation part, the protective tube and the connecting part, and the stimulation electrode is further provided with a first colloid and a second colloid, wherein the first colloid fills the gap between the stimulation part and the inner tube and extends into part of the gap between the protective tube and the inner tube, and the second colloid fills the gap between the connecting part and the inner tube and extends into part of the gap between the protective tube and the inner tube, the first colloid and the second colloid enhance the stiffness and structural strength of the stimulation part and the connecting part, and a coating made of a hydrophilic material is provided on the outer peripheral side of the protective tube, wherein the coating improves the lubrication condition of the electrode surface and reduces the risk of electrode displacement and breakage. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] The above and other purposes, features and advantages of the present invention will become more apparent through the following description of the embodiments of the present invention with reference to the accompanying drawings, in which:

[0019] Figure 1 It is a schematic diagram of the structure of the dorsal root ganglion electrical stimulation system in an embodiment of the utility model.

[0020] Figure 2 It is a schematic diagram of the structure of the stimulator in the embodiment of the utility model.

[0021] Figure 3 This is a schematic diagram of the first extended wire structure in the embodiment of the utility model.

[0022] Figure 4This is a schematic diagram of the second extended wire structure in the embodiment of the utility model.

[0023] Figure 5 This is a schematic diagram of the third extended wire structure in the embodiment of the utility model.

[0024] Figure 6 It is a schematic block diagram of the circuit principle of the stimulator in the embodiment of the utility model.

[0025] Figure 7 It is a schematic diagram of the internal structure of the socket part of the embodiment of the utility model for extending the wire.

[0026] Figure 8 The socket part of the utility model embodiment is Figure 7 Schematic diagram of the CC direction cross section.

[0027] Fig. 9 The four socket parts of an extension wire in the embodiment of the utility model are Figure 7 Schematic diagram of the CC direction cross-sectional structure.

[0028] Fig.10 It is a schematic diagram of the structure of the stimulation electrode in the embodiment of the utility model.

[0029] Fig.11 In the utility model embodiment Fig.10 Schematic diagram of the internal structure at A in the middle.

[0030] Fig.12 yes Fig.10 Schematic diagram of the internal structure at B in the middle.

[0031] Fig.13 It is a schematic diagram of the cross-sectional structure of the protection tube in the embodiment of the utility model.

[0032] Description of reference numerals:

[0033] 1. Stimulator; 2. Extension wire; 3. Stimulating electrode;

[0034] 11. Communication channel; 12. Controller; 13. Pulse output module; 14. Channel switch selection array;

[0035] 21. Plug part; 22. Lead part; 23. Socket part; 23', Seat body; 24. Primary fork body; 25. Secondary fork body; 26. Primary line segment; 27. Secondary line segment;

[0036] 231, connecting structure; 232, locking structure; 233, annular groove; 234, operating port; 235, plug hole; 236, partition wall; 237, outer ring wall; 238, first protrusion; 239, second protrusion;

[0037] 2311, fastener; 2312, annular clamp;

[0038] 2321, locking hole; 2322, locking screw; 2323, connecting seat;

[0039] 2331, accommodating cavity;

[0040] 2371. Front seal;

[0041] 31. Stimulation part; 32. Protection tube; 33. Connection part; 34. Inner tube; 35. First colloid; 36. Second colloid; 37. Coating;

[0042] 311, contact point; 312, isolation ring;

[0043] 321, micro-nano structure; 313, cavity;

[0044] 331. Positioning ring. DETAILED DESCRIPTION

[0045] The present invention is described below based on embodiments, but the present invention is not limited to these embodiments. In the detailed description of the present invention below, some specific details are described in detail. For those skilled in the art, the present invention can be fully understood without the description of these details. In order to avoid confusing the essence of the present invention, well-known methods, processes, procedures, components and circuits are not described in detail.

[0046] In addition, it should be understood by those skilled in the art that the drawings provided herein are for illustrative purposes and are not necessarily drawn to scale. Unless the context clearly requires otherwise, the words "include", "comprise" and the like throughout the application document should be interpreted as including rather than exclusive or exhaustive; that is, "including but not limited to". In the description of the present utility model, it should be understood that the terms "first", "second", etc. are used for descriptive purposes only and cannot be understood as indicating or implying relative importance. In addition, in the description of the present utility model, unless otherwise specified, "plurality" means two or more.

[0047] Unless otherwise clearly defined and limited, the terms "installed", "connected", "connected", "fixed" and the like should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be directly connected or indirectly connected through an intermediate medium, it can be the internal connection of two elements or the interaction relationship between two elements, unless otherwise clearly defined. For ordinary technicians in this field, the specific meanings of the above terms in this utility model can be understood according to specific circumstances.

[0048] The embodiment of the utility model provides a dorsal root ganglion stimulation electrode with lubricity. The stimulation electrode is provided with a hydrophilic coating, which can improve the lubrication condition of the electrode surface and keep the stimulation electrode lubricated during the implantation process, thereby reducing the resistance of the implantation, alleviating the patient's pain, and reducing the risk of electrode displacement and breakage.

[0049] It should be noted that the main content of the utility model is the innovative design of the structural direction, and the description of the main structural components does not involve implantation surgery, treatment stimulation programs and the like.

[0050] Figure 1 It is a schematic diagram of the structure of the dorsal root ganglion electrical stimulation system in an embodiment of the utility model. Figure 2 It is a schematic diagram of the structure of the stimulator in the embodiment of the utility model.

[0051] like Figure 1-2 The dorsal root ganglion electrical stimulation system includes a stimulator 1, an extension wire 2 and a stimulating electrode 3. The stimulator 1 is rechargeable or non-rechargeable, and has a communication device inside that can establish a wireless connection with an external device, so that it can be programmed by the external device to adjust the stimulation mode. The stimulator 1 has two communication channels 11. In some other examples, there can be one, three, four or more communication channels 11. Each communication channel 11 is provided with a plurality of electrical conductors connected to the internal circuit board of the stimulator 1. The extension wire 2 includes a plug part 21, a lead part 22 and a socket part 23. The plug part 21 is plug-in-fitted with the communication channel 11, and the plug part 21 is inserted into the communication channel 11 and electrically connected to the electrical conductor. The lead part 22 connects the plug part 21 and the socket part 23. When the socket part 23 is connected to the stimulating electrode 3, the stimulating electrode 3 is electrically connected to the electrical conductor in the communication channel 11 through the extension wire 2. The pulse electrical signal emitted by the stimulator 1 will be transmitted to the contact 311 of the stimulating electrode 3 through the electrical conductor, the plug part 21, the lead part 22 and the socket part 23 in sequence.

[0052] Figure 3 This is a schematic diagram of the first extended wire structure in the embodiment of the utility model.

[0053] like Figure 3 As shown, the lead portion 22 includes a primary forked body 24, a secondary forked body 25, a primary line segment 26 and a secondary line segment 27. One side of the primary forked body 24 is connected to the plug portion 21, and the other side is connected to two primary line segments 26, the two primary line segments 26 are respectively connected to the secondary forked body 25, and the secondary forked body 25 is connected to two secondary line segments 27. In this way, the plug portion 21 is connected to four secondary line segments 27, each of which is connected to a socket portion 23, and the extended wire 2 forms a plug portion 21 with four socket portions 23.

[0054] Figure 3In the example, a two-stage forked body is adopted, and two line segments are led out from each stage of the forked body, so that one plug part 21 corresponds to multiple socket parts 23. Such a structural design can ensure that the volume of the forked body is minimized, and the forked bodies at each stage are connected by line segments to form a certain distance, which is conducive to implantation in the body, and at the same time reduces the mutual influence of the forked bodies at each stage after being subjected to force in the body. For example, if the body tissue applies a pulling, squeezing, bending and other forces to a forked body, the line segments reduce the influence of the force on other forked bodies.

[0055] In some other embodiments, one of the two primary line segments 26 can be directly connected to the socket portion 23, and the other can be connected to the secondary forked body 25, and then the secondary forked body 25 is connected to the three socket portions 23 through three secondary line segments 27, and a structure in which one plug portion 21 is equipped with four socket portions 23 can also be formed. The primary forked body 24 of the utility model can also be connected to one, three, four or more primary line segments 26, and the secondary forked body 25 can also be connected to one, three, four or more secondary line segments 27.

[0056] Figure 4 This is a schematic diagram of the second extended wire structure in the embodiment of the utility model.

[0057] like Figure 4 As shown, the lead portion 22 includes a primary forked body 24, a secondary forked body 25, a primary line segment 26 and a secondary line segment 27. One side of the primary forked body 24 is connected to the plug portion 21, and the other side is connected to three primary line segments 26, two of the three primary line segments 26 are respectively connected to the socket portion 23, and the other primary line segment 26 is connected to the secondary forked body 25, and the secondary forked body 25 is further connected to two secondary line segments 27, and the two secondary line segments 27 are respectively connected to the socket portion 23, so that the extended wire can be configured with four socket portions 23 for one plug portion 21.

[0058] Figure 5 This is a schematic diagram of the third extension wire structure of the utility model.

[0059] like Figure 5 As shown, the lead portion 22 has only a primary forked body 24 and a primary line segment 26. One side of the primary forked body 24 is connected to the socket portion 23, and the other side is connected to four primary line segments 26, each of which is connected to the socket portion 23. Figure 3-5 The structure of the middle extension wire 2 is conducive to grouping multiple stimulation electrodes 3, such as: the stimulation electrodes 3 directly connected to the same secondary forked body 25 can be used as a group of stimulation electrodes, and the stimulation electrodes 3 directly connected to the same primary forked body 24 can be used as a group of stimulation electrodes, which is convenient for implanting the same group of stimulation electrodes in adjacent or close parts.

[0060] Figure 6It is a schematic block diagram of the circuit principle of the stimulator in the embodiment of the utility model.

[0061] like Figure 6 As shown, the circuit board of the stimulator 1 includes a controller 12, a pulse output module 13, a channel switch selection array 14, a power module and a communication module, etc., and the power module and the communication module are respectively connected to the controller 12. The pulse output module 13 is used to generate a set voltage or current pulse, and is mainly composed of a DC-DC circuit, an output control circuit, a charge balance circuit, etc. The channel switch selection array 14 takes the stimulator 1 with 8×4 contacts 311 as an example, including a positive gating switch (SEL2 / SEL4 / SEL6 / …… / SEL32, a total of 16) and a negative gating switch (SEL1 / SEL3 / SEL5 / SEL7 / …… / SEL31, a total of 16), which controls the contact 311 of each stimulation electrode 3 to be positively conductive or negatively conductive. In the utility model, a positive gating switch and a negative gating switch form a switch group, and the positive gating switch and the negative gating switch in the same switch group correspond to two identical contacts 311.

[0062] The pulse output module 13 is provided with four forward circuits, and each forward circuit controls the conduction of two electrodes through two conduction switches. Figure 6 Among them, L1, L2, L3, L4, L5, L6, L7 and L8 respectively control the forward conduction of eight stimulation electrodes 3. By controlling the stimulation electrodes 3 that need to be turned on through L1-L8, and then selecting the positive and negative polarities of the contacts 311 through SEL1-SEL32, it helps to achieve a more flexible electrical stimulation mode.

[0063] Figure 7 1 is a schematic diagram of the internal structure of the socket portion 23 of the extended wire 2 in the embodiment of the utility model. Figure 8 The socket part 23 in the embodiment of the utility model is Figure 7 Schematic diagram of the CC direction cross section.

[0064] like Figure 7The socket part 23 is columnar, and the two ends of the axial direction are provided with a conical surface structure to reduce the friction between the socket part 23 and the human body when implanted. The socket part 23 includes a seat body 23', and the seat body 23' is provided with a socket 235 and a locking structure 232. The socket 235 is for inserting the stimulation electrode 3, and the locking structure 232 is used to electrically connect with the stimulation electrode 3 and lock the stimulation electrode 3. The seat body 23' is also provided with a locking hole 2321 in the radial direction of the socket 235. The locking structure 232 includes a locking screw 2322 and a connecting seat 2323. Part of the locking screw 2322 is located in the locking hole 2321, and the connecting seat 2323 is set in the socket 235. By inserting a rotating tool (such as a screwdriver) into the locking hole 2321 and rotating the locking screw 2322, the locking screw 2322 can be squeezed through the stimulation electrode 3 of the connecting seat 2323 to fix the stimulation electrode 3 in the socket 235 and electrically connect the stimulation electrode 3 to the connecting seat 2323.

[0065] In this embodiment, the plug portion 21 is provided with a plurality of conductive rings, and the number of conductive rings is the same as the number of electrical conductors in the communication channel 11. The number of conductive rings of the extension wire can be the same as the number of locking structures 232, or it can be a multiple relationship, for example: a conductive ring can be connected to a locking structure 232 through the lead portion 22, or it can be connected to two, four or more locking structures 232, the number of locking structures 232 connected to each conductive ring can be the same or different, and the plurality of locking structures 232 of a socket portion 23 are fixedly connected to at least two conductive rings. In one embodiment, the stimulator 1 can transmit stimulation signals to thirty-two contacts 311. The stimulator 1 has two communication channels 11, each of which has sixteen electrical conductors, and the extension wire 2 has four socket portions 23, forming an electrical stimulation system with 8×4 contacts 311. The plug portion 21 has sixteen conductive rings, each of which has four locking structures 232, and one conductive ring is connected to one locking structure 232 through the lead portion 22.

[0066] like Figure 7-8 The seat body 23' is provided with an annular groove 233 surrounding the insertion hole 235 and a receiving cavity 2331 communicating with the annular groove 233. The annular groove 233 is provided near the insertion end of the insertion hole 235 for cooperating with the stimulation electrode 3. The socket part 23 is provided with a connecting structure 231, which is sleeved in the annular groove 233. The connecting structure 231 includes an operating part for controlling the tightness of the connection between the seat body 23' and the stimulation electrode 3. The operating parts on each socket part 23 have different directions (different). Based on the direction of the operating part relative to the locking structure 232, each socket part 23 is distinguished, so as to avoid the stimulation electrodes 3 implanted in different parts from being mixed with the socket part 23, which affects the stimulation effect.

[0067] The electrical stimulation system of the embodiment of the utility model has multiple stimulation electrodes, which can achieve synchronous stimulation of the dorsal root ganglia at multiple parts of the spine. In order to achieve a better stimulation effect, different parts require different stimulation modes, and there are differences in frequency, amplitude, pulse width and / or positive and negative polarity combinations between multiple contacts 311. Figure 6 The contact 311 of each stimulation electrode 3 can be controlled by a different switch circuit respectively. During the implantation of the stimulation electrode 3, the operating parts on each socket part 23 are oriented in different directions (different), and the socket parts 23 are accurately distinguished to avoid mixing of stimulation electrodes 3 implanted in different parts with the socket parts 23, thereby ensuring that the stimulation mode matches the electrode implantation position.

[0068] A partition wall 236 (or inner ring wall) is provided between the annular groove 233 and the plug hole 235, and the partition wall 236 separates the annular groove 233 and the plug hole 235. The partition wall 236 is provided with a first protrusion 238 on the side facing the annular groove 233, and a second protrusion 239 on the side facing the plug hole 235. The first protrusion 238 and the second protrusion 239 are respectively annular, and preferably, the second protrusion 239 is coaxial with the plug hole 235. The first protrusion 238 is staggered on the side of the second protrusion 239 facing the insertion end of the plug hole 235, and the first protrusion 238 is used to limit the connection structure 231 from escaping from the annular groove 233, and the second protrusion 239 is used to enhance the sealing performance between the seat body 23' and the stimulation electrode 3.

[0069] The outer peripheral side of the annular groove 233 is an outer annular wall 237, and the outer annular wall 237 includes a front sealing portion 2371, which extends to the front of the annular groove 233 (toward the insertion end of the socket), and the front sealing portion 2371 is arranged around, and the hole surrounded by the front sealing portion 2371 serves as a part of the insertion hole 235. Preferably, the hole surrounded by the front sealing portion 2371 is smaller than or equal to the aperture of other parts of the insertion hole 235.

[0070] In the present invention, the stimulation electrode 3 in the jack 235 and the socket part 23 have at least two seals, the first seal is the sealed connection between the front seal part 2371 and the stimulation electrode 3, and the second seal is the sealed connection between the second protrusion 239 and the stimulation electrode 3. The connection structure 231 squeezes the second protrusion 239 to enhance its tightness with the stimulation electrode 3, and at the same time, the socket parts 23 can be distinguished by the direction of the operating part of the connection structure 231, so as to avoid mixing the stimulation electrodes 3 implanted in different parts with the socket part 23, which affects the stimulation effect.

[0071] In order to better illustrate the connection structure 231, Figure 8 The first protrusion 238 and the second protrusion 239 are hidden. Figure 8As shown, the connection structure 231 includes a fastener 2311 and an annular clamp 2312. The annular clamp 2312 is an open structure, which is enclosed in an annular shape and is sleeved in the annular groove 233. One end of the annular clamp 2312 is fixed, and the other end of the annular clamp 2312 is in transmission connection with the fastener 2311. The size of the space enclosed by the annular clamp 2312 is controlled by rotating the fastener 2311, thereby squeezing the partition wall 236, increasing the squeezing force of the seat body 23' on the stimulation electrode 3, and improving the sealing. In this embodiment, the connection structure 231 can be similar to or the same as the structural principle of the existing throat clamp.

[0072] The fastener 2311 is located in the accommodating cavity 2331, and the seat body 23' is further provided with an operating port 234 in the radial direction of the annular groove 233. One end of the operating port 234 is connected to the accommodating cavity 2331, and the other end is connected to the outside of the seat body 23'. Part of the fastener 2311 is located in the operating port 234, and the operating portion includes an operating end of the fastener 2311 exposed through the operating port 234. The operating end can be provided with a groove such as a straight groove or a cross groove, and a screwdriver can be used to extend into the operating port 234 to cooperate with the operating end, and the fastener 2311 can be controlled to rotate by rotating the screwdriver. It can be understood that the direction of the operating portion refers to the direction of the operating port 234 or the direction of the operating end.

[0073] Fig. 9 The four socket parts of an extension wire in the embodiment of the utility model are Figure 7 Schematic diagram of the cross-sectional structure in CC direction. Fig. 9 The first protrusion 238 and the second protrusion 239 are hidden.

[0074] like Fig. 9 As shown, the locking structures 232 of the four socket parts 23 have the same orientation, and the operating ports 234 and the operating parts of the socket parts 23 have different orientations relative to the locking structures 232, thereby distinguishing the socket parts 23. The socket parts 23 of the utility model can be made of polyvinyl chloride (PVC) or polytetrafluoroethylene (PTFE), which has a certain degree of transparency, which helps to quickly distinguish the orientation of the operating part.

[0075] Furthermore, in the present invention, a sealing design is provided between the locking screw 2322 and the locking hole 2321 , and between the fastener 2311 and the operating port 234 , such as a sealing rubber ring is provided on the locking screw 2322 and the fastener 2311 .

[0076] Fig.10 It is a schematic diagram of the structure of the stimulation electrode 3 in the embodiment of the utility model. Fig.11 In the present utility model embodiment Fig.10 Schematic diagram of the internal structure of the stimulation electrode at point A. Fig.12 yes Fig.10 Schematic diagram of the internal structure of the stimulation electrode at point B. Fig.13It is a schematic diagram of the cross-sectional structure of the protection tube 32 in the embodiment of the utility model.

[0077] The present invention provides a lubricating dorsal root ganglion stimulation electrode 3. Figure 10-13 The stimulation electrode 3 includes a stimulation part 31, a protective tube 32, a connecting part 33 and an inner tube 34. The protective tube 32 is located between the stimulation part 31 and the connecting part 33. The inner tube 34 passes through the stimulation part 31, the protective tube 32 and the connecting part 33, and there is a gap between the inner tube 34 and the stimulation part 31, the protective tube 32 and the connecting part 33.

[0078] Preferably, the material of the protection tube 32 and the inner tube 34 may be polyurethane.

[0079] The connecting part 33 is electrically connected to the stimulation part 31 through a guide wire, which has an insulating coating. The guide wire is arranged in a spiral structure around the inner tube 34 between the protection tube 32 and the inner tube 34 to improve the elasticity of the stimulation electrode 3 and reduce the probability of the guide wire breaking.

[0080] The stimulation electrode 3 has a glue injection area I and a glue injection area II. The first colloid 35 is provided in the glue injection area I. The first colloid 35 fills the gap between the stimulation part 31 and the inner tube 34 and extends to a part of the gap between the protection tube 32 and the inner tube 34. The stimulation part 31 is bonded to the inner tube 34 through the first colloid 35. The second colloid 36 is provided in the glue injection area II. The second colloid 36 fills the gap between the connection part 33 and the inner tube 34 and extends to a part of the gap between the protection tube 32 and the inner tube 34. The connection part 33 is bonded to the inner tube 34 through the second colloid 36. The first colloid 35 and the second colloid 36 improve the stiffness and structural strength of the stimulation part 31 and the connection part 33.

[0081] Preferably, the first colloid 35 is made of silicone rubber.

[0082] Preferably, the second colloid 36 is made of epoxy resin.

[0083] In this embodiment, the length of the stimulation electrode 3 is L1, and the value range of L1 is between 400mm-1000mm. The implantation surgery needs to determine the lead length required from the intervertebral foramen to the implantation site of the stimulator. Using a stimulation electrode 3 longer than 1000mm may make it difficult to curl the excess lead, and using a stimulation electrode 3 shorter than 400mm may not be long enough. Preferably, the stimulation electrode 3 is 500mm long. The stimulation portion 31 includes a plurality of contacts 311 and an isolation ring 312 located between two adjacent contacts 311. The isolation ring 312 is made of polyurethane. The length of the isolation ring 312 (the distance between two adjacent contacts 311) is L2, and the value of L2 is between 4mm-6mm. The distance between the contacts 311 is too large, and the contacts 311 are sparsely distributed, so it is impossible to form targeted stimulation of the desired nerve root; the distance between the contacts 311 is too small, and the contacts 311 are closely spaced, the stimulation range is small, and the stimulation areas between adjacent contacts 311 overlap, affecting the stimulation effect. The contact 311 is annular, with an outer diameter of D, which is between 1mm-1.5mm, and the preferred outer diameter of the contact 311 is 1.3mm. The length of the contact 311 is L3, which is between 1mm-2mm, and the preferred length of the contact 311 is 1.5mm. If the contact 311 is too large, it will encounter more resistance during the implantation process, which is likely to cause greater damage to the surrounding neural structures, increasing the difficulty and risk of the operation; if the contact 311 is too small, the conductive performance will deteriorate, the stimulation range will be limited, and it will be difficult to cover the area that needs to be treated, affecting the stimulation effect.

[0084] The stimulation part 31 also includes a plug, which is used to seal the end of the inner tube 34 on one side of the stimulation part 31 to prevent the contact 311 from falling off. Preferably, the plug is made of polyurethane, the outer diameter of the plug is the same as the outer diameter of the contact 311, and the length of the plug is less than 2 mm.

[0085] The first colloid 35 extends in the gap between the protective tube 32 and the inner tube 34 to a length of L4, and the range of L4 is 1mm-3mm. The first colloid 35 ensures the connection strength among the stimulation part 31, the protective tube 32 and the inner tube 34. If L4 is too short, it will affect the structural stability, and if it is too long, it will affect the flexibility of the protective tube 32. The connecting part 33 includes a positioning ring 331 arranged adjacent to the protective tube 32. The second colloid 36 extends in the gap between the protective tube 32 and the inner tube 34 to a length of L5, and L5 is less than 5mm. After the stimulation electrode 3 is implanted in the body, the connecting part 33 is relatively far away from the nerve stimulation area, and most of the connecting part 33 is plugged into the socket part 23 of the extension wire 2. The accuracy of the extension length L5 of the second colloid 36 is not high. Therefore, it is sufficient to limit the length L5 of the second colloid 36 after extending out of the positioning ring 331 to be less than 5mm.

[0086] The outer circumference of the protection tube 32 is provided with a hydrophilic coating 37, and the material of the coating 37 is preferably polyvinyl pyrrolidone (PVP) or acrylic polymer. The coating 37 improves the lubricity of the surface of the stimulation electrode 3, reduces the friction between the stimulation electrode 3 and the body tissue, and thus reduces the risk of electrode displacement and breakage.

[0087] like Fig.10 As shown, a micro-nano structure 321 is also provided on the outer peripheral side of the protection tube 32 to increase the contact area between the coating 37 and the protection tube 32, thereby improving the bonding force of the coating 37. The coating 37 reflects the micro-nano structure 321, and the micro-nano structure 321 improves the wettability of the coating 37 and improves the hydrophilicity of the protection tube 32. A concave cavity 313 is also provided on the outer peripheral side of the protection tube 32 of the utility model, and the radial depth of the concave cavity 313 is between 0.1mm and 0.15mm. The cavity size of the concave cavity 313 is smaller than the cavity size of the concave cavity 313. The concave cavity 313 is filled with the coating 37, which further improves the bonding force between the coating 37 and the protection tube 32 and prevents the coating 37 from falling off.

[0088] Preferably, the thickness of the coating 37 is between 0.1 mm and 0.3 mm. If the coating 37 is too thin, it is easy to be damaged, which affects its own structural strength and stability. If the coating 37 is too thick, it is easy to cause the protective tube 32 to be too large, which is not conducive to implantation in the body.

[0089] In summary, the utility model provides an implantable dorsal root ganglion stimulation electrode with lubricity. The stimulation electrode 3 has a hydrophilic coating 37 to improve the lubricity of the surface of the stimulation electrode 3 and reduce the friction between the stimulation electrode 3 and the body tissue, thereby reducing the risk of electrode displacement and breakage.

[0090] In the present invention, spatially related terms such as "inside", "outside", "below", "below", "lower", "above", "upper", etc. are used to describe the relationship between one element or feature illustrated in the figure and another element or feature. It will be understood that spatially related terms may be intended to include different orientations of the device in use or operation other than the orientation depicted in the figure. For example, if the device in the figure is turned over, the element described as being "below" or "below" other elements or features will then be positioned as being "above" the other elements or features. Thus, the example term "below" can include both the orientations of above and below. The device can be oriented in other ways (rotated 90 degrees or in other orientations), and the spatially related descriptors used herein should be interpreted accordingly.

[0091] The above description is only a preferred embodiment of the utility model and is not intended to limit the utility model. For those skilled in the art, the utility model may have various modifications and changes. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the utility model shall be included in the protection scope of the utility model.

Claims

1. A lubricating dorsal root ganglion stimulation electrode, characterized in that: It comprises a stimulation part (31), a protective tube (32), a connecting part (33) and an inner tube (34), wherein the inner tube (34) passes through the stimulation part (31), the protective tube (32) and the connecting part (33); The stimulation electrode is also provided with a first colloid (35) and a second colloid (36), wherein the first colloid (35) fills the gap between the stimulation portion (31) and the inner tube (34), and extends to a portion of the gap between the protection tube (32) and the inner tube (34), and the second colloid (36) fills the gap between the connection portion (33) and the inner tube (34), and extends to a portion of the gap between the protection tube (32) and the inner tube (34); The outer peripheral side of the protection tube (32) is also provided with a hydrophilic coating (37).

2. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: A micro-nano structure (321) is provided on the outer peripheral side of the protection tube (32), and the coating (37) reflects the micro-nano structure (321).

3. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: The thickness of the coating (37) is between 0.1 mm and 0.3 mm.

4. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: A concave cavity (313) is also provided on the outer peripheral side of the protection tube (32); the radial depth of the concave cavity (313) is 0.1 mm-0.15 mm; the size of the cavity opening of the concave cavity (313) is smaller than the size of the cavity body of the concave cavity (313); and the coating (37) is filled in the concave cavity (313).

5. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: The stimulation part (31) comprises a plurality of contact points (311) and an isolation ring (312) located between two adjacent contact points (311); The contact (311) and the isolation ring (312) are respectively sleeved on the inner tube (34) and bonded to the inner tube (34) via the first colloid (35).

6. The lubricating dorsal root ganglion stimulation electrode according to claim 5, characterized in that: The length of the stimulation electrode ranges from 400 mm to 600 mm; The contact (311) is ring-shaped, with a length ranging from 1 mm to 2 mm and an outer diameter ranging from 1 mm to 1.5 mm.

7. The lubricating dorsal root ganglion stimulation electrode according to claim 5, characterized in that: The interval between two adjacent contact points (311) is in the range of 4 mm to 6 mm.

8. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: The extension length of the first colloid (35) in the gap between the protection tube (32) and the inner tube (34) is in the range of 1 mm to 3 mm.

9. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: The connecting portion (33) comprises a positioning ring (331) arranged adjacent to the protection tube (32).

10. The lubricating dorsal root ganglion stimulation electrode according to claim 1, characterized in that: The second colloid (36) extends in a gap between the protection tube (32) and the inner tube (34) to a length less than 5 mm.

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