Implantable stroke treatment stimulation device

Abstract

An implantable cerebral apoplexy treatment stimulation device disclosed by the present invention comprises a skull nail and a conductive part, the skull nail comprises a stud part, a screwing part and an electrode part, the stud part is suitable for being screwed into an implantation hole, the screwing part is connected to the top of the stud part, the electrode part is connected to the bottom of the stud part, a mounting hole is formed in the skull nail, and the conductive part is arranged in the mounting hole. The outer surface of the stud part and the outer surface of the screwing part are electric insulation surfaces, the bottom surface of the mounting hole forms a first conductive surface, the bottom surface of the conductive part is attached to the first conductive surface, the conductive part is connected with a wire, and the wire is used for being connected with a pulse generator. The device is simple in structure and more convenient to fix on the skull, the problem that current is prone to leakage can be solved, the stimulation intensity can be improved, small-range lesions can be accurately targeted, stimulation is more accurate, stimulation parameters and stimulation areas can be adjusted and controlled, the device dynamically adapts to brain injury conditions of different patients, and the stroke treatment effect is better.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of brain-computer interface, and particularly relates to an implantable stroke treatment stimulation device. BACKGROUND

[0002] Stroke (commonly known as "stroke") is a kind of acute cerebral vascular disease, and the core pathological mechanism is that the brain blood vessels suddenly occlude or rupture, leading to irreversible damage of brain tissue due to ischemia and hypoxia or blood clot compression, and then causing limb paralysis, language disorder, cognitive decline and other neurological deficits. It has the characteristics of acute onset, rapid progression, high mortality and disability, and is the leading cause of global adult disability.

[0003] At present, for the rehabilitation treatment of stroke, the main treatment methods include transcranial magnetic stimulation (TMS), transcranial direct current stimulation (tDCS) and other methods, which generate magnetic stimulation or electric stimulation through the electrodes of the stimulator, adjust the excitability of the brain area, and improve the motor and language functions. Clinical studies have shown that it has certain effectiveness. However, the existing stimulator has the electrode part fixed on the outer surface of the scalp, and the current needs to penetrate the scalp and skull, with a very high attenuation rate, and the actual generated current intensity is only 10% to 20% of the output value. Secondly, the current is "hemispherical diffusion", the stimulation target covers a large radius, and it is difficult to accurately target small lesions, which is not conducive to precise stimulation and rehabilitation. In addition, the existing stimulator not only has a complex structure, but also is fixed on the skull, and the current emitted by the electrode part is easy to leak to the non-treatment area of the patient's head, affecting the treatment effect. SUMMARY

[0004] The present application aims to at least solve one of the technical problems existing in the prior art. To this end, the present application provides an implantable stroke treatment stimulation device, which can not only improve the stimulation intensity, but also accurately target small lesions, stimulate more accurately, and solve the problem of current leakage of the traditional stimulator to the non-treatment area of the patient's head, and has better treatment effect, in addition to simple structure and convenient fixation on the skull.

[0005] The implantable stroke treatment stimulation device according to the embodiments of the present application is suitable for a skull with at least two implantation holes, and comprises at least two skull nails and at least two conductive parts. The skull nail comprises a stud part, a screwing part and an electrode part. The outer peripheral wall of the stud part is formed with external threads. The at least two stud parts are suitable for being screwed into the at least two implantation holes, respectively. The screwing part is connected to the top of the stud part. The top of the screwing part is provided with an operation groove suitable for a screwdriver to be inserted to rotate the skull nail. The electrode part is connected to the bottom of the stud part. The skull nail is provided with a mounting hole. The outer surface of the stud part and the outer surface of the screwing part are electrically insulating surfaces. The bottom surface of the mounting hole forms a first conductive surface. The outer surface of the electrode part forms a second conductive surface. The first conductive surface and the second conductive surface are electrically connected. The at least two conductive parts are mounted in the at least two mounting holes, respectively. The bottom surface of the conductive part is attached to the first conductive surface. The conductive part is connected with a wire. The wire extends out of the skull nail and is used to connect a pulse generator. The implantable stroke treatment stimulation device according to the embodiments of the present application has at least the following beneficial effects: The stud part of the skull nail is screwed into the implantation hole, and then the conductive part is mounted in the mounting hole of the skull nail. The structure is simple. The stimulation device is fixed on the skull conveniently. The workload of medical staff can be reduced. In the present application, the outer surface of the stud part and the outer surface of the screwing part of the skull nail are electrically insulating surfaces. Only the electrode part at the bottom end is conductive. The wire is electrically connected with the electrode part through the conductive part inside the skull nail and the first conductive surface. In this way, the current emitted by the second conductive surface of the electrode part can be effectively prevented from leaking to the non-treatment area of the patient's head through the outer surface of the stud part and the outer surface of the screwing part. In addition, through minimally invasive surgery, the skull nail with the electrode part is implanted in the implantation hole. The electrode part as a current target point can be positioned in the preset brain area. It can accurately target small lesions. The stimulation is more accurate and the stimulation range error is small. At the same time, the electrode part penetrates into the skull. The attenuation of the scalp and the skull to the current can be avoided. The current transmission efficiency is high. The current stimulation effect is good. In addition, by adjusting the current intensity, controlling the switching time sequence of the stimulation pulse of multiple electrode parts and matching the positive and negative electrodes of the electrode parts, the stimulation parameters can be adjusted. Through the electrical connection of the pulse generator and different electrode parts, the stimulation area can be adjusted. It is dynamically adapted to the brain injury of different patients. The stroke treatment effect is better. It is especially suitable for patients who are ineffective in the treatment of existing TMS / tDCS devices.

[0006] According to some embodiments of the present application, the implantable stroke treatment stimulation device further comprises an electrically insulating column mounted in the mounting hole. The bottom of the electrically insulating column abuts against the top of the conductive part. The electrically insulating column is provided with a wiring hole for the wire to pass through.

[0007] According to some embodiments of the present application, the bottom of the electrically insulating column is provided with a positioning groove in communication with the wiring hole, the top of the electrically conductive part is formed with a protrusion, the protrusion is inserted into the positioning groove, and the wire is connected to the top of the protrusion.

[0008] According to some embodiments of the present application, the electrically insulating column is made of polyether ether ketone; and / or, the outer peripheral wall of the wire is coated with an electrically insulating layer.

[0009] According to some embodiments of the present application, the top end of the mounting hole is in communication with the operation groove, at least one outer end of the operation groove extends outwardly to form a wiring groove, the wire is threaded through the top end of the mounting hole and is wired through the wiring groove.

[0010] According to some embodiments of the present application, the skull screw is made of medical titanium alloy, and the outer surfaces of the threaded stud part and the screwing part are both formed with an electrically insulating layer through anodic oxidation.

[0011] According to some embodiments of the present application, the second electrically conductive surface is provided as an outwardly convex circular arc surface.

[0012] According to some embodiments of the present application, the implantation hole is provided as a threaded hole matched with the threaded stud part.

[0013] According to some embodiments of the present application, the pulse generator comprises a housing, a circuit board, a feedthrough connector, an energy coil and a data antenna, the circuit board is arranged in the housing, the feedthrough connector is arranged in the housing and connected to the circuit board, the wire is connected to the feedthrough connector, the energy coil is connected to the feedthrough connector, and the data antenna is connected to the feedthrough connector.

[0014] According to some embodiments of the present application, the working frequency of the energy coil is 135.6KHz, and the working frequency of the data antenna is 2.4Ghz.

[0015] Additional aspects and advantages of the present application will be given in part in the following description, and some additional aspects and advantages will become apparent from the following description, or will be learned through practice of the present application. BRIEF DESCRIPTION OF DRAWINGS

[0016] The present application will be further described below in conjunction with the drawings and embodiments, in which: Figure 1 It is a schematic view of the installation of the implantable stroke treatment stimulation device according to an embodiment of the present application; Figure 2 It is a schematic view of the structure of the skull screw according to an embodiment of the present application; Figure 1 It is a partial sectional view of the skull screw according to an embodiment of the present application; Figure 3 It is a schematic view of the structure of the skull screw according to an embodiment of the present application; Figure 4 is a sectional view of a skull screw; Figure 5 is a schematic view of the cooperation of the conductive part and the electrically insulating column; Figure 6 is a schematic view of the arrangement of multiple implantation holes; Figure 7 is a schematic view of the structure of a pulse generator; Figure 8 is a schematic view of the interaction of the pulse generator and external devices.

[0017] Reference Signs: skull screw 100; screw column part 101; screwing part 102; electrode part 103; operation slot 104; mounting hole 105; first conductive surface 106; second conductive surface 107; wiring slot 108; conductive part 200; wire 201; bump 202; electrically insulating column 300; wiring hole 301; positioning slot 302; pulse generator 400; shell 401, circuit board 402; feedthrough connector 403; energy coil 404; data antenna 405; electrode connector 406; skull 500; implantation hole 501. DETAILED DESCRIPTION

[0018] Embodiments of the present application are described below in detail, examples of which are shown in the accompanying drawings, wherein the same or similar reference signs represent the same or similar elements or elements having the same or similar functions throughout. The embodiments described below by referring to the accompanying drawings are exemplary, only for explaining the present application, and cannot be understood as limiting the present application.

[0019] Reference is made below to Figures 1 to 8 An implantable stroke treatment stimulation device according to an embodiment of the present application is described.

[0020] Reference is made to Figure 1 , Figure 2 and Figure 7 An implantable stroke treatment stimulation device according to an embodiment of the present application is adapted to a skull 500, the skull 500 being provided with at least two implantation holes 501, the number of implantation holes 501 being determined according to actual requirements, for example, referring to Figure 6 , nine implantation holes 501 can be provided.

[0021] Reference is made to Figures 1 to 5As shown, the implantable stroke treatment stimulation device comprises at least two skull pins 100 and at least two conductive parts 200. The number of skull pins 100 and conductive parts 200 is determined according to the number of implantation holes 501, and each implantation hole 501 is provided with one skull pin 100 and one conductive part 200.

[0022] The skull pin 100 comprises a threaded shank 101, a screwing part 102 and an electrode part 103. The outer peripheral wall of the threaded shank 101 is formed with external threads, and at least two threaded shanks 101 are adapted to be screwed into at least two implantation holes 501, respectively. The screwing part 102 is connected to the top of the threaded shank 101, and the top of the screwing part 102 is provided with an operating groove 104 which can be cross-shaped or linear. The operating groove 104 is adapted to be inserted by a screwdriver to rotate the skull pin 100. The screwdriver can be a common screwdriver or an electric screwdriver, which will not be described here. The electrode part 103 is connected to the bottom of the threaded shank 101, and the threaded shank 101, the screwing part 102 and the electrode part 103 can be integrally formed.

[0023] The skull pin 100 is provided with a mounting hole 105 which can extend along the axial direction of the threaded shank 101. The top end of the mounting hole 105 can be provided through, and the bottom surface of the mounting hole 105 can be the top surface of the electrode part 103. Of course, the mounting hole 105 can also extend to the inside of the electrode part 103. The outer surface of the threaded shank 101 and the outer surface of the screwing part 102 are electrically insulating surfaces. The bottom surface of the mounting hole 105 forms a first conductive surface 106, and the outer surface of the electrode part 103 forms a second conductive surface 107. The first conductive surface 106 is electrically connected to the second conductive surface 107.

[0024] At least two conductive parts 200 are mounted in at least two mounting holes 105, respectively. The bottom surface of the conductive part 200 is attached to the first conductive surface 106. The conductive part 200 is connected with a lead wire 201 which can be welded with the conductive part 200, for example. The lead wire 201 extends out of the skull pin 100 and is used to connect the pulse generator 400. In this way, the pulse generator 400 is electrically connected through the lead wire 201, the conductive part 200, the first conductive surface 106 and the electrode part 103. The pulse generator 400 generates a pulse electrical signal, the electrode part 103 receives the pulse electrical signal, and the second conductive surface 107 of the electrode part 103 emits a corresponding stimulation waveform and stimulation current, thereby performing treatment.

[0025] It should be noted that when the number of implantation holes 501 is two, the electrode part 103 in one of the implantation holes 501 is a negative electrode, and the electrode part 103 in the other implantation hole 501 is a positive electrode. When the number of implantation holes 501 is three or more, a part of the electrode parts 103 in the implantation holes 501 can be negative electrodes, and the remaining electrode parts 103 in the implantation holes 501 can be positive electrodes. For example, referring toFigure 1 and Figure 7 As shown, when there are nine implantation holes 501, the nine implantation holes 501 can be arranged in an array. The electrode portion 103 in the middle implantation hole 501 can be a negative electrode, and the electrode portions 103 in the remaining implantation holes 501 are positive electrodes, surrounding the middle negative electrode. A current stimulation region is formed between the positive and negative electrodes. The number of implantation holes 501 and the positive and negative electrode arrangement of the electrode portions 103 can have various possible combinations, and the present invention is not limited thereto.

[0026] It should be noted that the reference Figure 2 As shown, the implantation hole 501 can be a blind hole structure, meaning that the bottom end of the implantation hole 501 is not penetrated. In this case, the electrode part 103 does not adhere to the patient's dura mater. As another embodiment, the implantation hole 501 can also be a through hole structure, meaning that the bottom end of the implantation hole 501 is penetrated. In this case, the bottom surface of the electrode part 103 can adhere to the patient's dura mater.

[0027] During treatment, at least two implantation holes 501 are made on the patient's skull 500. A screwdriver is inserted into the operating groove 104 of the screwing part 102 of the skull nail 100. The screwdriver is operated to screw the stud part 101 of the skull nail 100 into the implantation hole 501. Then, the conductive part 200 is installed in the mounting hole 105 of the skull nail 100, wherein the bottom surface of the conductive part 200 is in contact with the first conductive surface 106. The wire 201 connected to the conductive part 200 is connected to the pulse generator 400.

[0028] The implantable stroke treatment stimulation device according to embodiments of the present invention is not only simple in structure, but also features an external thread on the stud portion 101 of the skull nail 100. By screwing the skull nail 100 into the implantation hole 501, the entire stimulation device can be installed and fixed, making operation simple and convenient and significantly reducing the workload of medical personnel. Furthermore, the outer surfaces of the stud portion 101 and the screwing portion 102 of the skull nail 100 are electrically insulating surfaces; only the electrode portion 103 at the bottom is conductive. The wire 201 is electrically connected to the electrode portion 103 through the conductive portion 200 and the first conductive surface 106 inside the skull nail 100. This effectively prevents the current emitted from the second conductive surface 107 of the electrode portion 103 from leaking to the non-treatment area of ​​the patient's head through the outer surfaces of the stud portion 101 and the screwing portion 102.

[0029] Furthermore, through minimally invasive surgery, a skull nail 100 with an electrode portion 103 is implanted into the implantation hole 501 of the skull 500. The electrode portion 103 serves as a current target, which can be precisely located to a preset brain region, enabling precise targeting of small lesions (such as directly acting on the penumbra area after large vessel occlusion in ischemic stroke, damaged neurons around hematoma in hemorrhagic stroke, or specific functional areas such as the inferior frontal gyrus and motor cortex), resulting in more precise stimulation and smaller stimulation range errors. Simultaneously, the electrode portion 103 penetrates deep into the skull 500, avoiding the attenuation of current by the scalp and skull 500, resulting in high current transmission efficiency and good current stimulation effect. As one embodiment, the electrode portion 103 of this invention can also be used to collect electroencephalographic signals.

[0030] Furthermore, multiple cranial nails 100 with electrode sections 103 can be implanted first. Postoperatively, based on the patient's brain injury CT / MRI images, different stimulation waveforms and stimulation currents can be generated by adjusting the current intensity of the pulse generator 400, controlling the switching sequence of stimulation pulses from multiple electrode sections 103, and matching the positive and negative poles of the electrode sections 103, thereby improving the effectiveness of stimulation therapy. Additionally, the pulse generator 400 can be electrically connected to electrode sections 103 at different locations; for example, only some electrode sections 103 can be discharged for stimulation, i.e., at least one electrode section 103 can be set to an off-state, to control the stimulation area.

[0031] In this way, by adjusting the stimulation parameters and stimulation area, it is possible to dynamically adapt to the different brain injury conditions of different patients (such as adapting to different infarct sizes and different hemorrhage absorption), resulting in better stroke treatment and rehabilitation effects. It can effectively improve the motor, language and cognitive functions of stroke patients, and is especially suitable for patients who have not responded to existing TMS / tDCS equipment treatment. refer to Figure 2 and Figure 5 As shown, in some embodiments of the present invention, the implantable stroke treatment stimulation device further includes an electrically insulating column 300, which is installed within a mounting hole 105. The bottom of the electrically insulating column 300 abuts against the top of the conductive part 200. The electrically insulating column 300 is provided with a wiring hole 301 for the wire 201 to pass through. For example, a small gap may exist between the outer peripheral wall of the electrically insulating column 300 and the wall of the mounting hole 105, the gap being 0.05-0.12 mm, thus facilitating the installation or removal of the electrically insulating column 300 from the mounting hole 105. The wiring hole 301 may be coaxial with the electrically insulating column 300. After the wire 201 passes through the wiring hole 301, the wire 201 can be bonded to the electrically insulating column 300 using silicone adhesive.

[0032] In the embodiment, the electrically insulating column 300 is installed in the mounting hole 105. The electrically insulating column 300 can not only limit the conductive part 200 in cooperation with the mounting hole 105 to avoid the conductive part 200 from moving randomly to affect the conductive effect, but also can play an electrically insulating role to reduce the electric leakage. In addition, the electrically insulating column 300 can facilitate the wire 201 to be routed and reduce the winding of the wire 201.

[0033] Referring to Figure 2 and Figure 5 In some embodiments of the present application, the bottom of the electrically insulating column 300 is provided with a positioning groove 302 communicating with a wire routing hole 301, the top of the conductive part 200 is formed with a protrusion 202, and the protrusion 202 is inserted into the positioning groove 302, and the wire 201 is connected to the top of the protrusion 202.

[0034] In the embodiment, the positioning groove 302 and the protrusion 202 can limit the conductive part 200 in the vertical direction and the horizontal direction, thereby further avoiding the conductive part 200 from moving randomly to affect the conductive effect. In addition, the welding position of the wire 201 and the conductive part 200 is located in the positioning groove 302, which can protect the welding point, so that the welding of the wire 201 and the conductive part 200 is more stable, and the conductive stability is better.

[0035] In some embodiments of the present application, the electrically insulating column 300 is made of polyether ether ketone. In the embodiment, the electrically insulating column 300 is made of polyether ether ketone, which has reliable biocompatibility, is non-toxic and non-sensitizing to human tissues, and has excellent electrically insulating performance.

[0036] In some embodiments of the present application, the outer peripheral wall of the wire 201 is covered with an electrically insulating layer. For example, the electrically insulating layer covering the outer peripheral wall of the wire 201 can be made of polyimide or other suitable electrically insulating material. In this way, the electric leakage of the wire 201 can be avoided.

[0037] In some embodiments of the present application, the conductive part 200 and the wire 201 can be made of platinum-iridium alloy, and the conductive part 200 and the wire 201 can be connected by welding, such as laser welding.

[0038] Referring to Figure 3 and Figure 4 In some embodiments of the present application, the top end of the mounting hole 105 communicates with an operation groove 104, at least one outer end of the operation groove 104 extends outward to form a wire routing groove 108, for example, one outer end of the operation groove 104 extends outward to form the wire routing groove 108, and the wire 201 is routed through the top end of the mounting hole 105 and the wire routing groove 108.

[0039] In this embodiment, the top end of the mounting hole 105 is connected to the operating groove 104, which facilitates the wire 201 to extend from the top end of the mounting hole 105 into the skull nail 100. Moreover, the operating groove 104 is not only used for inserting a screwdriver to rotate the skull nail 100, but at least one outer end of the operating groove 104 also extends outward to form a wiring groove 108, which facilitates the wiring of the wire 201 after it extends out of the skull nail 100, making the surgical process more convenient.

[0040] In some embodiments of the present invention, the skull nail 100 is made of medical-grade titanium alloy, and the outer surfaces of the stud portion 101 and the screwing portion 102 are both anodized to form an electrically insulating layer. For example, the skull nail 100 can be made of medical-grade titanium alloy Ti 6Al4V-ELI or other suitable types of medical-grade titanium alloy.

[0041] In this embodiment, the skull nail 100 is made of medical-grade titanium alloy. Titanium alloy has reliable biocompatibility, is non-toxic and non-allergenic to human tissue, and is lightweight and has good corrosion resistance. The outer surfaces of the stud portion 101 and the screw portion 102 are both anodized to form an electrically insulating layer, which can prevent the current emitted from the outer surface of the electrode portion 103, that is, the second conductive surface 107, from leaking to the non-treatment area of ​​the patient's head through the outer surfaces of the stud portion 101 and the screw portion 102.

[0042] It should be noted that the conductivity of the first conductive surface 106 and the second conductive surface 107 can be formed by covering it with a protective layer during the anodizing process, or by removing the surface oxide layer of the first conductive surface 106 and the second conductive surface 107.

[0043] Understandably, the hole wall of mounting hole 105 can also be anodized to form an electrically insulating layer, thus improving the leakage prevention effect.

[0044] In some embodiments of the present invention, the thickness of the electrically insulating layer formed by anodizing the outer surface of the stud portion 101 and the outer surface of the screw portion 102 is 4 to 6 μm. This not only improves the leakage protection effect on the outer surfaces of the stud portion 101 and the screw portion 102, but also avoids the electrical insulating layer being too thick and affecting the use of the skull nail 100.

[0045] refer to Figures 2 to 4 As shown, in some embodiments of the present invention, the second conductive surface 107 is configured as a convex arc surface. In this embodiment, configuring the second conductive surface 107 as a convex arc surface not only avoids the electrode portion 103 from being too sharp and causing damage to the patient's skull 500, but also makes the conductive area of ​​the second conductive surface 107 larger, thereby making the electrical stimulation treatment effect better.

[0046] In some embodiments of the present invention, the implantation hole 501 is configured as a threaded hole adapted to the stud portion 101. Since the skull screw 100 is a hollow structure, it may be damaged due to insufficient structural strength when it is tapped and screwed into the implantation hole 501. In this application, the implantation hole 501 is first processed into a threaded hole using a tapping device, which can avoid damage to the skull screw 100.

[0047] In some embodiments of the present invention, the length of the stud portion 101 is set at 4mm-7mm, which is just right to fit the thickness of an adult's skull.

[0048] In some embodiments of the present invention, the pulse generator 400 may be an implantable pulse generator (IPG) that can be implanted in the skull 500, chest, or other locations. When the pulse generator 400 is implantable, it can be powered by wireless charging or a built-in battery. Of course, the pulse generator 400 may also be disposed externally, as long as it can be electrically connected to the electrode part 103.

[0049] refer to Figure 7 As shown, in some embodiments of the present invention, the pulse generator 400 includes a housing 401, a circuit board 402, a feedthrough connector 403, an energy coil 404, and a data antenna 405.

[0050] The circuit board 402 is located inside the housing 401. The feedthrough connector 403 is located in the housing 401 and connected to the circuit board 402. The wire 201 is connected to the feedthrough connector 403. The energy coil 404 is connected to the feedthrough connector 403, and the data antenna 405 is connected to the feedthrough connector 403. For example, the feedthrough connector 403 can be a ceramic feedthrough connector 403. The feedthrough connector 403 can be located at the opening of the housing 401 and seal the housing 401. The feedthrough connector 403 is connected to the circuit board 402 inside the housing 401. The wire 201 can be directly connected to the feedthrough connector 403, or it can be connected to the feedthrough connector 403 through an electrode connector 406. The energy coil 404 and the data antenna 405 can be located on the outside of the housing 401 and covered by a protective structure. The energy coil 404 receives electrical energy from a power source, such as a portable power supply, through electromagnetic induction to achieve wireless power supply. Of course, the pulse generator 400 can also have a built-in battery, which will not be elaborated further here. The data antenna 405 is used to exchange signals with external devices, providing bidirectional signal transmission.

[0051] In this embodiment, the pulse generator 400 can be implanted in the human body and can transmit data and energy wirelessly, making it more convenient to use.

[0052] The following is for reference. Figure 8As shown, taking the implantable pulse generator (IPG) as an example, the interaction between the pulse generator 400 and the external device is simply described. It should be noted that the following description is only illustrative and does not limit the scheme of the present application.

[0053] The external device can include a computer, a programmable instrument, etc., and the software in the computer, such as the DAC software, performs system setting and parameter configuration on the programmable instrument through a Bluetooth module. The portable power supply provides working power for the programmable instrument and performs parameter fine adjustment through a button; The programmable instrument provides system working power and bidirectional data communication for the implantable pulse generator through a wireless transmission mode. The energy coil 404 provides working power for the implantable pulse generator through wireless power transmission; and the data antenna 405 adopts wireless communication to provide stable bidirectional data transmission for the system. The implantable pulse generator sends corresponding stimulation waveforms and stimulation currents to the brain tissue through the electrode part 103 according to the stimulation parameter configuration sent by the programmable instrument and processed by the MCU on the circuit board 402.

[0054] In some embodiments of the present application, the working frequency of the energy coil 404 is 135.6 KHz, and the working frequency of the data antenna 405 is 2.4 GHz. In this way, the mutual interference between the energy coil 404 and the data antenna 405 can be prevented.

[0055] The embodiments of the present application are described in detail above in combination with the drawings, but the present application is not limited to the above-described embodiments, and various changes can be made within the knowledge of those skilled in the art without departing from the purpose of the present application.

Claims

1. An implantable stimulation device for stroke treatment, adapted to the skull, wherein the skull has at least two implantation holes, characterized in that, include: At least two cranial screws, each cranial screw comprising a stud portion, a screwing portion, and an electrode portion, wherein the outer peripheral wall of the stud portion is formed with external threads, and the at least two stud portions are adapted to be screwed into at least two implantation holes respectively, the screwing portion being connected to the top of the stud portion, the top of the screwing portion being provided with an operating groove, the operating groove being adapted to allow a screwdriver to be inserted to rotate the cranial screw, the electrode portion being connected to the bottom of the stud portion, and the cranial screw having an installation hole, the outer surfaces of the stud portion and the screwing portion being electrically insulating surfaces, the bottom surface of the installation hole forming a first conductive surface, and the outer surface of the electrode portion forming a second conductive surface, the first conductive surface and the second conductive surface being electrically connected; At least two conductive parts are respectively installed in at least two of the mounting holes, the bottom surface of the conductive parts is in contact with the first conductive surface, the conductive parts are connected to wires, the wires extend out of the skull nail and are used to connect to a pulse generator.

2. The implantable stroke treatment stimulation device according to claim 1, characterized in that, The implantable stroke treatment stimulation device also includes: An electrically insulating post is installed in the mounting hole, with the bottom of the electrically insulating post abutting against the top of the conductive part, and the electrically insulating post having a wiring hole for the wire to pass through.

3. The implantable stroke treatment stimulation device according to claim 2, characterized in that, The bottom of the electrically insulating post is provided with a positioning groove that connects to the wiring hole, and the top of the conductive part is formed with a protrusion. The protrusion is inserted into the positioning groove, and the wire is connected to the top of the protrusion.

4. The implantable stroke treatment stimulation device according to claim 2, characterized in that, The electrically insulating post is made of polyetheretherketone; and / or, the outer peripheral wall of the conductor is covered with an electrically insulating layer.

5. The implantable stroke treatment stimulation device according to any one of claims 1 to 4, characterized in that, The top of the mounting hole is connected to the operating groove, and at least one outer end of the operating groove extends outward to form a wiring groove. The wire passes through the top of the mounting hole and is routed through the wiring groove.

6. The implantable stroke treatment stimulation device according to any one of claims 1 to 4, characterized in that, The skull nail is made of medical titanium alloy, and the outer surfaces of the stud and the screwing part are both anodized to form an electrically insulating layer.

7. The implantable stroke treatment stimulation device according to any one of claims 1 to 4, characterized in that, The second conductive surface is configured as a convex arc surface.

8. The implantable stroke treatment stimulation device according to any one of claims 1 to 4, characterized in that, The implantation hole is configured as a threaded hole that is adapted to the stud portion.

9. The implantable stroke treatment stimulation device according to any one of claims 1 to 4, characterized in that, The pulse generator includes: case; The circuit board is disposed within the housing; A feedthrough connector is disposed in the housing and connected to the circuit board, and the wire is connected to the feedthrough connector; An energy coil, connected to the feedthrough connector, is used for wireless charging; The data antenna is connected to the feedthrough connector.

10. The implantable stroke treatment stimulation device according to claim 9, characterized in that, The energy coil operates at a frequency of 135.6 kHz, and the data antenna operates at a frequency of 2.4 GHz.

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