Implantable electrical stimulator with electromagnetic shielding function

Abstract

The present disclosure provides an implantable electrical stimulator having an electromagnetic shielding function. The implantable electrical stimulator includes a first housing portion, a second housing portion, a control device, and at least one interaction device. The first housing portion houses the control device, and the second housing portion houses at least one interaction device. At least one interaction device is electrically connected to the control device. The first housing portion is configured to at least partially form an electromagnetic shield for the control device relative to the external environment. The second housing portion is configured to allow at least one interaction device to wirelessly interact with an external device. In this way, on the basis of ensuring that the interaction device can reliably interact with the external device, the influence of external electromagnetic interference on the control device and the influence of the electromagnetic radiation generated by the control device itself on surrounding electronic devices can be effectively suppressed.

Description

Technical Field

[0001] The present disclosure relates to the field of medical devices, and in particular, to an implantable electrical stimulator. Background Art

[0002] The implantable electrical stimulator includes a control device for generating stimulation pulses. The implantable electrical stimulator provided by the related art is difficult to cope with the influence of external electromagnetic interference on the control device. External electromagnetic interference may cause unstable stimulation parameters, affect the treatment effect, and even may trigger stimulation erroneously. In addition, if the electromagnetic radiation generated by the control device itself is not properly suppressed, it may interfere with electronic devices such as interaction devices around the implantable electrical stimulator. Summary of the Invention

[0003] In view of this, the present disclosure improves the implantable electrical stimulator, aiming to improve the problem that the implantable electrical stimulator provided by the related art is difficult to effectively cope with electromagnetic interference.

[0004] The present disclosure provides an implantable electrical stimulator with an electromagnetic shielding function. The implantable electrical stimulator includes a first housing part, a second housing part, a control device, and at least one interaction device. The first housing part houses the control device, and the second housing part houses at least one interaction device. At least one interaction device is electrically connected to the control device. The first housing part is configured to at least partially form an electromagnetic shield for the control device relative to the external environment. The second housing part is configured to allow at least one interaction device to wirelessly interact with an external device.

[0005] According to the implantable electrical stimulator with an electromagnetic shielding function provided by the present disclosure, the control device that is vulnerable to electromagnetic interference and prone to generate electromagnetic signals is housed in the first housing part with an electromagnetic shielding effect, and at least one interaction device that needs to wirelessly interact with the outside is housed in the second housing part without electromagnetic shielding. In this way, on the basis of ensuring that the interaction device can reliably interact with the external device, the influence of external electromagnetic interference on the control device and the influence of the electromagnetic radiation generated by the control device itself on the surrounding electronic devices can be effectively suppressed.

[0006] As a possible implementation, the implantable electrical stimulator with an electromagnetic shielding function further includes an electromagnetic shielding member. The first housing part is provided with a through channel, and the electromagnetic shielding member seals the through channel. At least one interaction device is electrically connected to the control device respectively through at least one connection line. One end of each connection line is electrically connected to the control device, and the other end thereof passes through the electromagnetic shielding member and is electrically connected to the corresponding interaction device.

[0007] The connecting line connecting the interaction device and the control device needs to pass through the through-channel to extend between the two housing parts. Due to the presence of the electromagnetic shielding member, external electromagnetic interference will be difficult to enter the interior of the first housing part through the through-channel and affect the control device. At the same time, the electromagnetic radiation generated by the control device will also be difficult to escape from the first housing part. In this way, the ability of the implantable electrical stimulator to cope with electromagnetic interference can be further improved.

[0008] As a possible implementation, the electromagnetic shielding member includes a conductive structure and a matrix supporting the conductive structure.

[0009] The matrix can effectively support the conductive structure, and the conductive structure can play an electromagnetic shielding role.

[0010] In one example, the conductive structure is a conductive layer laminated with the matrix.

[0011] In another example, the conductive structure is a conductive grid or conductive particles distributed in the matrix.

[0012] According to this structure, the conductive structure will be able to provide electromagnetic shielding for the part of the connecting line placed in the electromagnetic shielding member. This ensures electromagnetic compatibility on the signal transmission path, reduces signal attenuation and interference, and maintains high fidelity and low latency of data exchange between the control device and the interaction device.

[0013] As a possible implementation, the matrix is injection-molded with at least one connecting line as an insert.

[0014] By directly coating the connecting line inside the matrix through the injection molding process, the matrix will support and fix the connecting line. This integration method reduces the connection points and improves the mechanical stability of the entire system. In addition, this method integrates the fixation of the connecting line and the forming of the matrix into one, simplifies the assembly steps, and reduces the manufacturing cost. In addition, the integrated connecting line and electromagnetic shielding member will be assembled as a whole in subsequent processes, which helps to further reduce the manufacturing difficulty and reduce the manufacturing cost.

[0015] As a possible implementation, the conductive structure is insulated from at least one connecting line and electrically connected to the first housing part.

[0016] The conductive structure is electrically connected to the first housing part, forming a closed shielding loop, which can more effectively block external electromagnetic interference and at the same time reduce the impact of electromagnetic radiation generated by internal electronic components on the outside world. The conductive structure is insulated from at least one connecting line, avoiding the influence of the conductive structure on signal transmission.

[0017] As a possible implementation, the electromagnetic shielding member includes a connecting portion, and the connecting portion includes a peripheral wall portion and a flange portion. The peripheral wall portion surrounds the matrix, and the flange portion protrudes outward from the outer surface of the peripheral wall portion.

[0018] The peripheral wall portion can receive the substrate of the electromagnetic shielding member to ensure its reliable positioning. The outwardly convex structure of the flange portion provides additional mechanical support, enhancing the connection strength between the electromagnetic shielding member and the housing portion, and enabling better resistance to various mechanical stresses inside and outside the body, such as extrusion and twisting, thereby improving the stability and durability of the implant device.

[0019] As a possible implementation, the conductive structure is electrically connected to the first housing portion through the connecting portion.

[0020] In this way, this configuration ensures the formation of a continuous and low-impedance electrical connection path between the conductive structure and the first housing portion, which helps to form a complete electromagnetic shielding loop, more effectively shields external electromagnetic interference, while reducing the leakage of internally generated electromagnetic radiation, and improves the electromagnetic compatibility of the entire electrical stimulation system and the reliability of treatment. The connecting portion not only has the function of supporting and positioning the shielding member, but also has the function of conducting the electrical connection between the shielding member and the first housing portion. The same component has multiple functions, which helps to reduce the complexity of the structure and the manufacturing cost.

[0021] As a possible implementation, the substrate is injection-molded with at least one connecting wire and the connecting portion as inserts.

[0022] This method integrates the fixation of the connecting wire, the fixation of the connecting portion, and the molding of the substrate into one body, simplifies the assembly steps, and reduces the manufacturing cost. In addition, the integrated connecting wire, connecting portion, and electromagnetic shielding member will be assembled as a whole in subsequent processes, which helps to further reduce the manufacturing difficulty and reduce the manufacturing cost. The peripheral wall portion defines the flow range of the material, which helps to control the material distribution during the injection molding process.

[0023] As a possible implementation, the control device includes a first circuit board and a second circuit board that are stacked and spaced apart along the thickness direction of the first housing portion. The first circuit board has an electronic device surface and a non-electronic device surface that are opposite in the thickness direction. The electronic device surface faces the second circuit board surface, and the non-electronic device surface abuts against the inner surface of the first housing portion.

[0024] The two circuit boards stacked in the thickness direction make full use of the space in the thickness direction and avoid the overly large area of the implantable electrical stimulator. By directly abutting the non-electronic device surface against the inner surface of the first housing portion and concentrating the electronic devices between the two circuit boards, the utilization rate of the internal space of the first housing portion in the thickness direction is improved, so that more electronic components can be integrated to meet complex functional requirements without increasing the overall size of the device. Description of the Drawings

[0025] It should be understood that the following drawings only show certain embodiments of the present disclosure and should not be regarded as limiting the scope.

[0026] It should be understood that the same or similar reference numerals are used in the drawings to represent the same or similar elements.

[0027] It should be understood that the drawings are only schematic, and the sizes and proportions of the elements in the drawings are not necessarily accurate.

[0028] Figure 1 A schematic diagram of a spinal cord stimulation system according to an embodiment of the present disclosure is shown.

[0029] Figure 2 is Figure 1 A structural schematic diagram of the implantable electrical stimulator.

[0030] Figure 3 is Figure 1 An internal structural schematic diagram of the implantable electrical stimulator in.

[0031] Figure 4 is Figure 1 An exploded schematic diagram of a part of the components of the implantable electrical stimulator in.

[0032] Figure 5 is Figure 1 A structural schematic diagram of a part of the components of the implantable electrical stimulator in.

[0033] Figure 6 is Figure 4 A structural schematic diagram of the electromagnetic shielding member in.

[0034] Figure 7 is Figure 3 A structural schematic diagram of the circuit board, the first housing part, and the battery in.

[0035] Figure 8 A structural schematic diagram of the electromagnetic shielding member according to a modification of the present disclosure.

[0036] Figure 9 A structural schematic diagram of the electromagnetic shielding member according to another modification of the present disclosure.

[0037] Figure 10 A structural schematic diagram of the implantable electrical stimulator according to another modification of the present disclosure. Detailed implementation manners

[0038] The embodiments of the present disclosure will be described exemplarily below in conjunction with the drawings. It should be understood that there can be various implementation manners of the present disclosure and should not be construed as being limited to the embodiments set forth herein. The embodiments set forth herein are only for a more thorough and clear understanding of the present disclosure.

[0039] For ease of understanding, the following refers to Figure 1 and first gives an example of the electrical stimulation system used by the implantable electrical stimulator 100 provided by the present disclosure. It can be understood that, on the premise of no contradiction, the implantable electrical stimulator 100 can be applied to other electrical stimulation systems.

[0040] Referring to Figure 1 , the electrical stimulation system may include an implantable electrical stimulator 100, an external programming device 50, and an external charging device 60. The external programming device 50 and the external charging device 60 may also be referred to as external devices. As Figure 1 shown, the implantable electrical stimulator 100 may be wholly or partially implanted into the patient's body. It should be noted that in Figure 1 , the reference numeral SC is used to indicate the spinal cord of the patient, and the reference numeral SK is used to indicate the skin of the patient.

[0041] The implantable electrical stimulator 100 may include an electrode lead 30. By way of example only, at least a part of the electrode lead 30 may be implanted into the epidural space of the patient's spinal cord. Of course, in other examples, the electrode lead 30 may also be implanted at other peripheral nerves. The electrode lead 30 includes a plurality of electrode contacts 40. Exemplarily, the number of electrode contacts 40 may be 2, 4, 6, or 8. Of course, in other examples, the number of electrode contacts 40 may also be other numbers, and the present disclosure does not specifically limit the number of electrode contacts 40. For example, in some embodiments, the number of electrode contacts 40 may also be odd.

[0042] The implantable electrical stimulator 100 is configured to generate electrical pulses. It should be noted that in the present disclosure, the electrical pulses may refer to current pulses or voltage pulses. The electrical pulses are transmitted via the electrode lead 30 to the electrode contacts 40 and are finally delivered to the target nerve of the patient via the electrode contacts 40 to achieve treatment purposes such as pain relief.

[0043] The implantable electrical stimulator 100 provided according to the present disclosure is placed in the patient's body and can be supplemented with electrical energy, for example, by the external charging device 60. At the same time, the implantable electrical stimulator 100 can also be configured to exchange data through the external programming device 50. If the implantable electrical stimulator 100 provided by the present disclosure is adopted, functions such as wireless charging, pulse control instruction change, and data exchange can be conveniently achieved through external devices.

[0044] For ease of understanding, the following gives an example of the structure of the implantable electrical stimulator 100. It should be understood that the structure of the implantable electrical stimulator 100 should not be limited to the following description. For example, one or several of the following elements may be omitted or replaced, and the layout relationship between them may be replaced.

[0045] For example, the implantable electrical stimulator 100 may mainly consist of a housing part, a control device, an interaction device, and leads and electrode contacts. The main function of the housing part is to provide a strong protective layer for the internal components of the implantable electrical stimulator 100, such as the rechargeable battery 103, the control device, etc. This helps prevent damage to the internal components caused by physical impacts from the external environment, chemical substance erosion, and natural reactions of organisms such as rejection reactions, ensuring the stable and safe operation of the electrical stimulator. The control device is the core part of the electrical stimulator. This module generates electrical stimulation pulses with a certain frequency, waveform, pulse width, and intensity. These pulse parameters can be adjusted according to the treatment needs. The interaction device usually includes a communication device 202 and a wireless charging device 203, etc. The communication device 202 is responsible for receiving instructions from the external controller, transmitting the instructions to the control device, and the control device generates a stimulation pulse control signal according to the preset parameters. Some communication devices 202 also provide a system on / off control interface, a stimulation signal generation module interface, and a program writing interface to ensure the normal operation of the entire system. Through the communication device 202, a doctor or a patient can remotely adjust the stimulation parameters of the electrical stimulator, such as frequency, pulse width, stimulation intensity, etc., according to needs, for example. This helps to achieve personalized treatment plans and make real-time adjustments according to the treatment effects. Some communication devices 202 can also enable medical staff to record information such as the usage data and treatment effects of the electrical stimulator by sending messages, and store them on relevant devices or cloud servers. The leads and stimulating physiological electrodes are the parts of the electrical stimulator that directly contact the nerves or muscles, and are responsible for conducting the electrical stimulation pulses to the target nerve or muscle tissue, thereby realizing the electrical stimulation treatment of the nerves or muscles.

[0046] Reference Figure 2 and Figure 3 , in one embodiment, the housing part divides the stimulator implanted in the body into two parts, a first housing part 10 and a second housing part 20. The first housing part 10 houses the control device and the battery 103. The control device includes, for example, a first circuit board 101 and a second circuit board 102 that are stacked and spaced along the thickness direction of the first housing part 10, and a battery 103 arranged beside the first circuit board 101 and the second circuit board 102. The battery 103 is connected to the second circuit board 102 to supply electrical energy to the control device. The second housing part 20 is located in the direction away from the battery 103 of the first housing part 10 and houses the interaction device. The interaction device includes, for example, a communication device 202 and a wireless charging device 203. The communication device 202 is, for example, a helically wound antenna and is connected to the control device through a connection line 205. The wireless charging device 203 is, for example, an induction coil and can be connected to the control device through the connection line 205. The induction coil can be, for example, adjacent to the inner surface of the second housing part 20.

[0047] As an embodiment, the first housing part 10 is configured to at least partially form an electromagnetic shield for the control device with respect to the external environment, and the second housing part 20 is configured to allow at least one interaction device to interact wirelessly with an external device.

[0048] The first housing part 10 can be made of metal, such as a titanium alloy. As an electromagnetic shielding layer, the main purpose of the first housing part 10 is to protect internal electronic components such as electronic elements like the pulse generator from external electromagnetic interference (EMI). This is particularly important in modern society where wireless communication devices are increasing and the electromagnetic environment is complex, which can ensure the stable operation of the device and avoid misoperation or functional failure.

[0049] Furthermore, as Figure 3 , the implantable electrical stimulator 100 further includes an electromagnetic shield 204. The first housing part 10 is provided with a through-channel 1001 (not shown in the figure). The electromagnetic shield 204 seals the through-channel 1001. At least one interaction device is electrically connected to the control device through at least one connection line 205 respectively; one end of each connection line 205 is electrically connected to the control device, and the other end thereof passes through the electromagnetic shield 204 and is electrically connected to the corresponding interaction device.

[0050] Integrating the sealing of the electromagnetic shield 204 and the through-channel 1001 shows a high degree of integration and space utilization efficiency, which is beneficial to reducing the volume of the implanted device and reducing the physiological and psychological burdens on the patient.

[0051] Furthermore, the electromagnetic shield includes a conductive structure and a matrix 2042 that supports the conductive structure.

[0052] As the core part of the shield, the conductive structure can reflect or absorb external electromagnetic waves, forming a barrier to effectively block interference signals from penetrating into the internal circuit or wire. Good electrical conductivity ensures the high efficiency of electromagnetic shielding. This combined structure allows for flexible adjustment of the shape, size, and layout of the shield according to actual needs, enabling it to closely fit the specific structure of the implantable electrode and be integrated into the entire device without affecting other functions and operations of the electrode.

[0053] Furthermore, the conductive structure is a conductive grid distributed in the matrix 2042 (such as Figure 6 ).

[0054] In an implantable electrode structure, the conductive structure employs a conductive grid distributed in the substrate 2042. The conductive grid is composed of fine conductive lines, which may be woven from microfilaments of silver, copper, or other highly conductive metals to form a regular or irregular grid pattern. The grid structure is designed to maximize the surface area to more effectively reflect or absorb external electromagnetic waves. When external electromagnetic radiation encounters the conductive grid, due to the high conductivity of the grid, induced currents are generated on the grid surface. These currents produce a reverse electromagnetic field that cancels out the original incident wave, thereby achieving effective shielding against external electromagnetic interference. In addition, the grid structure also allows a certain degree of flexibility and ductility, enabling the entire implantable electrode to adapt to the dynamic changes of the body without affecting its shielding effectiveness.

[0055] Furthermore, the substrate 2042 is injection-molded with at least one connecting wire 205 as an insert.

[0056] Insert injection molding is an efficient integrated molding technology that can integrally form multiple components, namely the substrate 2042 material and the connecting wire 205, in one go. Compared with traditional assembly methods, it greatly simplifies the production process, reduces manufacturing costs, and improves production efficiency and product consistency. Insert injection molding allows for highly customized structures. According to the specific structural and functional requirements of the implantable electrode, the path and distribution of the connecting wire 205 can be precisely positioned and shaped, optimizing the structural compactness and functionality of the electrode.

[0057] Furthermore, the conductive structure is insulated from the connecting wire 205 and electrically connected to the first housing part 10.

[0058] By electrically connecting the conductive structure to the first housing part 10, a closed shielding body is formed. This means that the first housing part 10 of the entire implantable electrode becomes a large Faraday cage, effectively preventing the penetration of external electromagnetic waves and protecting the internal circuit and the connecting wire 205 from interference. This structure ensures the continuity and integrity of the shielding, improving the shielding efficiency. The electrical connection provides a low-impedance grounding path, which helps to quickly guide and dissipate any induced currents generated by the shielding effect, reducing the possibility of forming a closed loop inside the system, and thus avoiding interference problems caused by grounding loops. The connecting wire 205 is usually used to transmit signals. Keeping it insulated from the conductive structure can effectively prevent external electromagnetic fields from coupling to the connecting wire 205 through the conductive structure and interfering with the originally transmitted signals, which is crucial for the accuracy of data acquisition, etc.

[0059] Furthermore, the electromagnetic shielding member includes a connecting portion 2041. The connecting portion 2041 includes a peripheral wall portion 2041a and a flange portion 2041b. The peripheral wall portion 2041a surrounds the substrate 2042, and the flange portion 2041b protrudes outward from the outer surface of the peripheral wall portion.

[0060] In the structure of the electromagnetic shielding component, the structure of the connecting portion 2041 includes a peripheral wall portion 2041a and a flange portion 2041b. The flange portion 2041b specifically functions to provide an efficient and reliable connection method to cover and protect the through-channel 1001 provided in the first shell portion 10 of the implantable electrode, while enhancing the overall electromagnetic shielding effectiveness. The peripheral wall portion 2041a forms a groove structure, so that during the one-piece injection molding process, the liquid matrix 2042 material can fully flow into and fill these grooves, and after cooling and solidification, a strong mechanical interlocking structure is formed. This structure significantly enhances the bonding strength between the electromagnetic shielding component and the matrix 2042 material, ensuring the stability and durability of long-term implantation. The groove structure simplifies the process flow of one-piece injection molding, reduces additional assembly steps and the use of adhesives through natural flow filling, improves production efficiency, and also reduces manufacturing costs. Through the carefully constructed groove structure, the possible complex and changeable geometric shapes of the interactive device when passing through the substrate 2042 can be adapted, and even tiny or irregular areas can be effectively covered and protected, which increases the flexibility of the structure and enables the interactive device to better fit the specific needs of the electrode.

[0061] Figure 3 , Figure 4 and Figure 5 The relative positional relationship between the interactive device and the connecting portion 2041 , the substrate 2042 , the through channel 1001 , and the signal line 2010 is shown.

[0062] On the other hand, Figure 7 The control device includes a first circuit board 101 and a second circuit board 102 stacked and spaced apart in the thickness direction of the first shell portion 10. The first circuit board 101 has a relative surface with electronic components and a surface without electronic components in the thickness direction. The surface with electronic components is opposite to the surface of the second circuit board 102, and the surface without electronic components is in contact with the inner surface of the first shell portion 10.

[0063] The surface of the first circuit board 101 without electronic components directly contacts the inner surface of the first housing portion 10. Figure 7 The figure shows only part of the housing, which means there are no additional components or protrusions on the back of the circuit board, and the circuit boards are stacked in the thickness direction instead of the traditional parallel placement, which greatly saves space inside the implantable electrode. This structure makes the device more compact and reduces the implant volume, thereby reducing the burden on the patient's body and facilitating implantation in a small in vivo environment.

[0064] Optionally, the at least one interaction device includes a communication device 202 and / or a wireless charging device 203 .

[0065] Other possible variant embodiments are introduced next.

[0066] As Figure 8 shown, in a variant, the conductive structure is conductive particles distributed in the substrate 2042.

[0067] In another implantable electrode structure, the conductive structure employs conductive particles distributed in the substrate 2042. This structure forms a conductive composite material by uniformly doping tiny conductive particles in the substrate 2042, which not only retains the mechanical properties of the substrate 2042 material but also endows the overall structure with electromagnetic shielding ability. The conductive particles are usually metal powders such as silver, copper, nickel powders or carbon-based materials such as graphene, carbon nanotubes, which have excellent electrical conductivity. The particle size is generally in the micron or nanometer range to better disperse in the substrate 2042 while minimizing the impact on the overall flexibility of the material.

[0068] As Figure 9 shown, in another variant, the conductive structure is a conductive layer 2043 stacked with the substrate 2042.

[0069] The conductive layer 2043 is usually composed of a thin metal foil such as copper foil, aluminum foil or a thin film coated with a conductive material such as silver paste, carbon ink, and has high electrical conductivity and good electromagnetic wave reflection ability.

[0070] As Figure 10 shown, in another variant, the wireless charging device 203 and the conductive part in the substrate 2042 are jointly connected to the conversion circuit 105, and at the same time, the conversion circuit 105 is electrically connected to the battery 103, the first circuit board 101, and the first housing part 10. The specially constructed conversion circuit 105 plays a crucial role, enabling the wireless charging device 203 to also provide partial shielding function in the working mode. In the charging mode, the implantable stimulator is in a wireless charging state. Once the charging is completed, the conversion circuit 105 receives the charging completion signal or according to the preset time / electricity threshold, and at the same time turns on the electrical connection between the wireless charging device 203 and the first housing part 10, making the wireless charging device 203 serve as part of the electromagnetic shielding. This configuration further improves the signal shielding process, enabling the lead connection device 201 to be further electromagnetically shielded while the shielding does not interfere with the interaction device.

[0071] The basic principles of the present disclosure have been described above in conjunction with specific embodiments. However, it should be noted that the advantages, advantages, effects, etc. mentioned in the present disclosure are only examples and not limitations, and it cannot be considered that these advantages, advantages, effects, etc. are essential for each embodiment of the present disclosure. In addition, the above-mentioned specific details are only for illustrative and easy-to-understand purposes, rather than limitations, and the above details do not limit the present disclosure to necessarily adopt the above specific details to implement.

[0072] The foregoing description has been presented for purposes of illustration and description. In addition, this description is not intended to limit embodiments of the present disclosure to the forms disclosed herein. Although several example aspects and embodiments have been discussed above, those skilled in the art will recognize some variations, modifications, alterations, additions, and sub-combinations thereof.

[0073] The components and devices involved in the present disclosure are only illustrative examples and are not intended to require or imply that they must be connected, arranged, and configured in the manner shown in the drawings. As those skilled in the art will recognize, these components and devices can be connected, arranged, and configured in any manner.

[0074] The above is only the specific implementation manner of the present disclosure, but the protection scope of the present disclosure is not limited thereto. Any person skilled in the art can easily think of changes or substitutions within the technical scope disclosed by the present disclosure, and all of them should be covered by the protection scope of the present disclosure. Therefore, the protection scope of the present disclosure should be based on the protection scope of the claims.

Claims

1. An implantable electrical stimulator with electromagnetic shielding function, comprising a first housing part, a second housing part, a control device and at least one interaction device. The first housing part houses the control device, the second housing part houses the at least one interaction device, the at least one interaction device is electrically connected to the control device, the first housing part is configured to at least partially form electromagnetic shielding of the control device relative to the external environment, and the second housing part is configured to allow the at least one interaction device to interact wirelessly with an external device. The implantable electrical stimulator further includes an electromagnetic shielding member. The first housing part is provided with a through channel, and the electromagnetic shielding member seals the through channel. The electromagnetic shielding member includes a conductive structure and a matrix supporting the conductive structure. The electromagnetic shielding member includes a connecting part, the connecting part includes a peripheral wall part and a flange part. The peripheral wall part surrounds the matrix, the flange part protrudes outward from the outer surface of the peripheral wall part, and the peripheral wall part forms a groove structure so that the matrix in a liquid state fully fills the groove structure and cools.

2. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, characterized in that, The at least one interaction device is electrically connected to the control device through at least one connecting wire respectively; one end of each connecting wire is electrically connected to the control device, and the other end thereof passes through the electromagnetic shielding member and is electrically connected to the corresponding interaction device.

3. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, wherein, The conductive structure is a conductive grid or conductive particles distributed in the matrix.

4. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, characterized in that, The conductive structure is a conductive layer laminated with the matrix.

5. The implantable electrical stimulator with electromagnetic shielding function according to claim 2, characterized in that, The matrix is injection molded with the at least one connecting wire as an insert.

6. The implantable electrical stimulator with electromagnetic shielding function according to claim 5, characterized in that, The conductive structure is insulated from the connecting wire and electrically connected to the first housing part.

7. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, wherein, The conductive structure is electrically connected to the first housing part through the connecting part.

8. The implantable electrical stimulator with electromagnetic shielding function according to claim 2, wherein The matrix is injection molded with the at least one connecting wire and the connecting part as inserts.

9. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, wherein The control device includes a first circuit board and a second circuit board that are laminated and spaced along the thickness direction of the first housing part. The first circuit board has an electronic device surface and a non - electronic device surface opposite to each other in the thickness direction. The electronic device surface faces the second circuit board surface, and the non - electronic device surface abuts against the inner surface of the first housing part.

10. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, characterized in that, The at least one interaction device includes a communication device and / or a wireless charging device.

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