CN118512712A - Implantable electrical stimulator with electromagnetic shielding function - Google Patents

Abstract

The present disclosure provides an implantable electrical stimulator with an electromagnetic shielding function. The implantable electrical stimulator includes a first shell portion, a second shell portion, a control device and at least one interactive device. The first shell portion accommodates the control device, and the second shell portion accommodates the at least one interactive device. The at least one interactive device is electrically connected to the control device. The first shell portion is configured to at least partially form an electromagnetic shielding of the control device relative to the external environment. The second shell portion is configured to allow at least one interactive device to wirelessly interact with an external device. In this way, on the basis of ensuring that the interactive 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 equipment can be effectively suppressed.

Description

Implantable electrical stimulator with electromagnetic shielding function

Technical Field

The present disclosure relates to the field of medical devices, and in particular, to an implantable electrical stimulator.

Background Art

The implantable electrical stimulator includes a control device, which is used to generate 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 the stimulation parameters to be unstable, affect the treatment effect, and may even trigger the stimulation by mistake. In addition, if the electromagnetic radiation generated by the control device itself is not properly suppressed, it may interfere with electronic equipment around the implantable electrical stimulator, such as interactive devices.

Summary of the invention

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.

The present disclosure provides an implantable electrical stimulator with an electromagnetic shielding function. The implantable electrical stimulator includes a first shell portion, a second shell portion, a control device, and at least one interactive device. The first shell portion accommodates the control device, and the second shell portion accommodates the at least one interactive device. The at least one interactive device is electrically connected to the control device. The first shell portion is configured to at least partially form an electromagnetic shielding of the control device relative to the external environment. The second shell portion is configured to allow the at least one interactive device to wirelessly interact with an external device.

According to the present disclosure, an implantable electrical stimulator with an electromagnetic shielding function is provided, wherein a control device susceptible to electromagnetic interference and prone to generating electromagnetic signals is housed in a first housing portion having an electromagnetic shielding effect, and at least one interaction device that needs to wirelessly interact with the outside is housed in a second housing portion that does not generate electromagnetic shielding. In this way, while ensuring that the interaction device can reliably interact with an external device, the influence of external electromagnetic interference on the control device and the influence of electromagnetic radiation generated by the control device itself on surrounding electronic equipment can be effectively suppressed.

As a possible implementation, the implantable electrical stimulator with electromagnetic shielding function also includes an electromagnetic shielding component, the first shell portion is provided with a through-channel, and the electromagnetic shielding component blocks the through-channel. At least one interactive device is electrically connected to the control device through at least one connecting wire. One end of each connecting wire is electrically connected to the control device, and the other end thereof is electrically connected to the corresponding interactive device through the electromagnetic shielding component.

The connection line connecting the interactive device and the control device needs to pass through the through-channel to extend between the two shell parts. Due to the presence of the electromagnetic shielding member, it will be difficult for external electromagnetic interference to enter the first shell part through the through-channel to 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 shell part. In this way, the ability of the implantable electrical stimulator to cope with electromagnetic interference can be further improved.

As a possible implementation manner, the electromagnetic shielding component includes a conductive structure and a substrate supporting the conductive structure.

The substrate can effectively support the conductive structure, and the conductive structure can play a role in electromagnetic shielding.

In one example, the conductive structure is a conductive layer arranged in stacked relationship with the substrate.

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

According to this configuration, the conductive structure will be able to provide electromagnetic shielding for the portion of the connection 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 interactive device.

As a possible implementation manner, the base body is formed by injection molding with at least one connecting line as an insert.

The connecting wires are directly wrapped inside the matrix through the injection molding process, and the matrix will support and fix the connecting wires. 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 wires with the molding of the matrix, simplifies the assembly steps, and reduces manufacturing costs. In addition, the integrated connecting wires and electromagnetic shielding parts will be assembled as a whole in the subsequent process, which helps to further reduce the manufacturing difficulty and reduce the manufacturing cost.

As a possible implementation manner, the conductive structure is insulated from the at least one connecting line and is electrically connected to the first housing portion.

The conductive structure is electrically connected to the first housing portion to form a closed shielding loop, which can more effectively block external electromagnetic interference and 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 to avoid the influence of the conductive structure on signal transmission.

As a possible implementation manner, the electromagnetic shielding component includes a connecting portion, the connecting portion includes a peripheral wall portion and a flange portion, the peripheral wall portion surrounds the base body, and the flange portion protrudes outward from an outer surface of the peripheral wall portion.

The peripheral wall portion can receive the base of the electromagnetic shielding component to ensure that it is reliably positioned. The convex structure of the flange portion provides additional mechanical support, enhances the connection strength between the electromagnetic shielding component and the shell portion, and can better resist various mechanical stresses inside and outside the body, such as extrusion, twisting, etc., thereby improving the stability and durability of the implant device.

As a possible implementation manner, the conductive structure is electrically connected to the first shell portion via a connecting portion.

In this way, this structure ensures that a continuous and low-impedance electrical connection path is formed between the conductive structure and the first shell part, which helps to form a complete electromagnetic shielding loop, more effectively shielding external electromagnetic interference, while reducing the leakage of electromagnetic radiation generated internally, and improving the electromagnetic compatibility and treatment reliability of the entire electrical stimulation system. The connecting part has the function of supporting and positioning the shielding member, and has the function of conducting the electrical connection between the shielding member and the first shell part. The same component has multiple functions, which helps to reduce the complexity of the structure and the manufacturing cost.

As a possible implementation manner, the base body is formed by insert injection molding with at least one connecting line and a connecting portion.

This method integrates the fixing of the connecting wire, the fixing of the connecting part and the molding of the base, simplifies the assembly steps and reduces the manufacturing cost. In addition, the integrated connecting wire, connecting part and electromagnetic shielding part will be assembled as a whole in the subsequent process, which helps to further reduce the manufacturing difficulty and reduce the manufacturing cost. The peripheral wall defines the flow range of the material, which helps to control the material distribution during the injection molding process.

As a possible implementation, the control device includes a first circuit board and a second circuit board stacked and spaced apart in the thickness direction of the first housing portion. The first circuit board has an electronic device surface and an electronic device-free surface opposite to each other in the thickness direction, the electronic device surface is opposite to the second circuit board surface, and the electronic device-free surface is in contact with the inner surface of the first housing portion.

The two layers of circuit boards stacked in the thickness direction make full use of the space in the thickness direction to avoid the implantable electrical stimulator being too large. The surface without electronic components directly contacts the inner surface of the first shell part, and the electronic components are concentrated between the two circuit boards, which improves the utilization rate of the internal space of the first shell part in the thickness direction, so that more electronic components can be integrated to meet complex functional requirements without increasing the overall size of the device.

BRIEF DESCRIPTION OF THE DRAWINGS

It should be understood that the following drawings only illustrate certain embodiments of the present disclosure and should not be viewed as limiting the scope.

It should be understood that the same or similar reference numerals are used in the drawings to indicate the same or similar elements.

It should be understood that the drawings are merely schematic and that the sizes and proportions of elements in the drawings are not necessarily accurate.

FIG. 1 shows a schematic diagram of a spinal cord stimulation system according to an embodiment of the present disclosure.

FIG. 2 is a schematic structural diagram of the implantable electrical stimulator of FIG. 1 .

FIG. 3 is a schematic diagram of the internal structure of the implantable electrical stimulator in FIG. 1 .

FIG. 4 is an exploded schematic diagram of a portion of components of the implantable electrical stimulator in FIG. 1 .

FIG. 5 is a schematic structural diagram of a portion of components of the implantable electrical stimulator in FIG. 1 .

FIG. 6 is a schematic structural diagram of the electromagnetic shielding component in FIG. 4 .

FIG. 7 is a schematic structural diagram of the circuit board, the first housing portion, and the battery in FIG. 3 .

FIG. 8 is a schematic structural diagram of an electromagnetic shielding component according to a modified example of the present disclosure.

FIG. 9 is a schematic structural diagram of an electromagnetic shielding component according to another variation of the present disclosure.

FIG. 10 is a schematic diagram of the structure of an implantable electrical stimulator according to another variation of the present disclosure.

DETAILED DESCRIPTION

The following is an exemplary description of the embodiments of the present disclosure in conjunction with the accompanying drawings. It should be understood that the present disclosure can be implemented in a variety of ways and should not be construed as being limited to the embodiments described herein, which are only for a more thorough and clear understanding of the present disclosure.

For ease of understanding, the electrical stimulation system used by the implantable electrical stimulator 100 provided by the present disclosure is first illustrated with reference to Fig. 1. It is understandable that the implantable electrical stimulator 100 can be applied to other electrical stimulation systems under the premise that there is no contradiction.

Referring to FIG1 , 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 shown in FIG1 , the implantable electrical stimulator 100 may be implanted in whole or in part into the patient's body. It should be noted that in FIG1 , the reference numeral SC is used to indicate the patient's spinal cord, and the reference numeral SK is used to indicate the patient's skin.

The implantable electrical stimulator 100 may include an electrode lead 30. By way of example only, at least a portion of the electrode lead 30 may be implanted into the patient's spinal epidural space. Of course, in other examples, the electrode lead 30 may also be implanted into 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 an odd number.

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

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

For ease of understanding, the structure of the implantable electrical stimulator 100 is illustrated below. 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 more of the elements cited below can be omitted or replaced, and the layout relationship between them can be replaced.

For example, the implantable electrical stimulator 100 may be mainly composed of a shell part, a control device, an interactive device, and leads and electrode contacts. The main function of the shell part is to provide a solid protective layer for the internal components of the implantable electrical stimulator 100, such as the rechargeable battery 103, the control device, etc. This helps to prevent the physical impact of the external environment, the erosion of chemical substances, and the natural reaction of the organism, such as rejection, from damaging the internal components, and ensure the stable and safe operation of the electrical stimulator. The control device is the core part of the electrical stimulator. This module can generate electrical stimulation pulses with a certain frequency, waveform, pulse width, and intensity. These pulse parameters can be adjusted according to treatment needs. The interactive 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 and transmitting the instructions to the control device, and the control device generates a stimulation pulse control signal according to preset parameters. Some communication devices 202 also provide a system start-up and shutdown 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, doctors or patients can, for example, remotely adjust the stimulation parameters of the electrical stimulator, such as frequency, pulse width, stimulation intensity, etc., as needed. This helps to implement personalized treatment plans and make real-time adjustments based on the treatment effect. Some communication devices 202 can also send information so that medical staff can record the use data, treatment effects and other information of the electrical stimulator, and store them on related equipment or cloud servers. The leads and stimulating physiological electrodes are the parts of the electrical stimulator that are in direct contact with the nerves or muscles, and are responsible for transmitting electrical stimulation pulses to the target nerves or muscle tissues, thereby achieving electrical stimulation treatment of the nerves or muscles.

Referring to FIG. 2 and FIG. 3 , in one embodiment, the housing portion divides the implanted stimulator into two parts, a first housing portion 10 and a second housing portion 20. The first housing portion 10 accommodates a control device and a battery 103. The control device includes, for example, a first circuit board 101 and a second circuit board 102 stacked and arranged at intervals along the thickness direction of the first housing portion 10, and, for example, 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 provide power to the control device. The second housing portion 20 is located in the first housing portion 10 away from the battery 103 and accommodates an interactive device. The interactive device includes, for example, a communication device 202 and a wireless charging device 203. The communication device 202 is, for example, a spirally wound antenna connected to the control device via a connecting line 205. The wireless charging device 203 is, for example, an induction coil that can be connected to the control device via a connecting line 205. The induction coil can, for example, be attached to the inner surface of the second housing portion 20.

As an embodiment, the first housing portion 10 is configured to at least partially form an electromagnetic shielding of the control device relative to the external environment, and the second housing portion 20 is configured to allow at least one interaction device to wirelessly interact with the external device.

The first housing portion 10 may be made of metal, such as titanium alloy. As an electromagnetic shielding layer, the first housing portion 10 is mainly used to protect internal electronic components such as pulse generators from external electromagnetic interference EMI. This is particularly important in the modern society where wireless communication devices are increasing and the electromagnetic environment is complex, and can ensure stable operation of the device and avoid misoperation or functional failure.

Furthermore, as shown in FIG3 , the implantable electrical stimulator 100 also includes an electromagnetic shielding component 204 , the first shell portion 10 is provided with a through channel 1001 (not shown in the figure), the electromagnetic shielding component 204 blocks the through channel 1001 , and at least one interactive device is electrically connected to the control device via at least one connecting wire 205 ; one end of each connecting wire 205 is electrically connected to the control device, and the other end thereof is electrically connected to the corresponding interactive device via the electromagnetic shielding component 204 .

The integrated structure of the electromagnetic shielding component 204 and the plugging of the through channel 1001 demonstrates high integration and space utilization efficiency, which is conducive to reducing the size of the implanted device and reducing the physiological and psychological burden on the patient.

Furthermore, the electromagnetic shielding component includes a conductive structure and a substrate 2042 supporting the conductive structure.

As the core part of the shield, the conductive structure can reflect or absorb external electromagnetic waves to form a barrier, effectively blocking interference signals from penetrating into internal circuits or wires. Good conductivity ensures the high efficiency of electromagnetic shielding. This combined structure allows the shape, size and layout of the shield to be flexibly adjusted according to actual needs, so that it can fit the specific structure of the implantable electrode closely and be integrated into the entire device without affecting other functions and operations of the electrode.

Furthermore, the conductive structure is a conductive grid distributed in the substrate 2042 (as shown in FIG. 6 ).

In an implantable electrode structure, the conductive structure uses a conductive grid distributed in the matrix 2042. The conductive grid is composed of fine conductive lines, which may be woven from fine filaments 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, the electromagnetic waves will generate induced currents on the surface of the grid. These currents will generate reverse electromagnetic fields, which will cancel each other out with the original incident waves, thereby achieving effective shielding of external electromagnetic interference. In addition, the grid structure also allows a certain degree of flexibility and ductility, so that the entire implantable electrode can adapt to the dynamic changes of the body without affecting its shielding effectiveness.

Furthermore, the base body 2042 is formed by injection molding with at least one connecting line 205 as an insert.

Insert molding is an efficient integrated molding technology that can integrate multiple component substrates 2042 materials and connecting wires 205 into a one-time molding process. Compared with traditional assembly methods, it greatly simplifies the production process, reduces manufacturing costs, and improves production efficiency and product consistency. Insert molding allows for highly customized construction, and can accurately locate and shape the path and distribution of the connecting wires 205 according to the specific structure and functional requirements of the implanted electrode, thereby optimizing the structural compactness and functionality of the electrode.

Furthermore, the conductive structure is insulated from the connecting wire 205 and is electrically connected to the first housing portion 10 .

By electrically connecting the conductive structure to the first shell portion 10, a closed shielding body is formed. This means that the first shell portion 10 of the entire implantable electrode becomes a large Faraday cage, which effectively prevents the penetration of external electromagnetic waves and protects the internal circuit and the connecting wire 205 from interference. This structure ensures the continuity and integrity of the shielding and improves the shielding efficiency. The electrical connection provides a low-impedance grounding path, which helps to quickly guide and dissipate any induced current generated by the shielding effect, reduce the possibility of forming a closed loop within the system, and thus avoid interference problems caused by the grounding loop. The connecting wire 205 is usually used to transmit signals, and keeping it insulated from the conductive structure can effectively prevent the external electromagnetic field from coupling to the connecting wire 205 through the conductive structure and interfering with the originally transmitted signal, which is crucial for the accuracy of data acquisition, etc.

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

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.

3 , 4 and 5 show the relative positional relationship between the interactive device and the connecting portion 2041 , the base 2042 , the through channel 1001 and the signal line 2010 .

On the other hand, as shown in 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.

The non-electronic device surface of the first circuit board 101 directly contacts the inner surface of the first housing portion 10. As shown in FIG. 7, only part of the housing portion is shown in the figure, which means that 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 the space inside the implantable electrode. This structure makes the device more compact, reduces the implant volume, thereby reducing the burden on the patient's body, and is also convenient for implantation in a narrow in vivo environment.

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

Other possible variant embodiments are introduced next.

As shown in FIG. 8 , in a variation, the conductive structure is conductive particles distributed in the matrix 2042 .

In another implantable electrode structure, the conductive structure uses conductive particles distributed in the matrix 2042. This structure forms a conductive composite material by uniformly doping tiny conductive particles in the matrix 2042, which not only retains the mechanical properties of the matrix 2042 material, but also gives the overall structure the ability of electromagnetic shielding. The conductive particles are usually metal powders such as silver, copper, nickel powder or carbon-based materials such as graphene and carbon nanotubes, which have excellent conductive properties. The particle size is generally at the micrometer or nanometer level, so that it can be better dispersed in the matrix 2042 while reducing the impact on the overall flexibility of the material.

As shown in FIG. 9 , in another variation, the conductive structure is a conductive layer 2043 stacked with a substrate 2042 .

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

As shown in FIG. 10 , in another variation, the wireless charging device 203 and the conductive part in the substrate 2042 are connected to the conversion circuit 105, and the conversion circuit 105 is electrically connected to the battery 103, the first circuit board 101, and the first shell part 10. The specially constructed conversion circuit 105 plays a crucial role, so that the wireless charging device 203 can also provide a 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 a charging completion signal or according to a preset time/power threshold, and simultaneously opens the electrical connection between the wireless charging device 203 and the first shell part 10, so that the wireless charging device 203 serves as part of the electromagnetic shielding. This structure further improves the signal shielding process, so that the lead connection device 201 is further electromagnetically shielded, and the shielding does not interfere with the interactive device.

The basic principles of the present disclosure are described above in conjunction with specific embodiments. However, it should be noted that the advantages, strengths, effects, etc. mentioned in the present disclosure are only examples and not limitations, and it cannot be considered that these advantages, strengths, effects, etc. must be possessed by each embodiment of the present disclosure. In addition, the specific details disclosed above are only for the purpose of illustration and ease of understanding, rather than limitation, and the above details do not limit the present disclosure to the necessity of adopting the above specific details to be implemented.

The above description has been given for the purpose of illustration and description. In addition, this description is not intended to limit the embodiments of the present disclosure to the forms disclosed herein. Although multiple example aspects and embodiments have been discussed above, those skilled in the art will recognize certain variations, modifications, changes, additions and sub-combinations thereof.

The components and devices involved in this disclosure are only illustrative examples and are not intended to require or imply that they must be connected, arranged, or configured in the manner shown in the drawings. As will be appreciated by those skilled in the art, these components and devices may be connected, arranged, or configured in any manner.

The above are only specific embodiments of the present disclosure, but the protection scope of the present disclosure is not limited thereto. Any technician familiar with the technical field can easily think of changes or substitutions within the technical scope disclosed in the present disclosure, which should be included in 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 (12)

1. An implantable electrical stimulator with electromagnetic shielding function, comprising a first housing part housing the control device, a second housing part housing the at least one interaction device, a control device and at least one interaction device electrically connected with the control device, the first housing part being configured to at least partially form an electromagnetic shielding of the control device with respect to an external environment, the second housing part being configured to allow the at least one interaction device to interact wirelessly with an extracorporeal device.

2. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, further comprising an electromagnetic shield, the first housing part being provided with a through passage, the electromagnetic shield blocking the through passage, the at least one interaction device being electrically connected to the control device by at least one connection wire, respectively; one end of each connecting wire is electrically connected with the control device, and the other end of each connecting wire is electrically connected with the corresponding interaction device through the electromagnetic shielding piece.

3. The implantable electrical stimulator with electromagnetic shielding function according to claim 2, wherein the electromagnetic shield includes a conductive structure and a base body supporting the conductive structure.

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

5. An implantable electrical stimulator with electromagnetic shielding function according to claim 3, wherein the conductive structure is a conductive layer arranged in a layered manner with the base body.

6. The implantable electrical stimulator with electromagnetic shielding function according to claim 3, wherein the base body is insert-molded with the at least one connecting wire.

7. An implantable electrical stimulator with electromagnetic shielding function according to any one of claims 3 to 6, wherein the conductive structure is insulated from the connection line and electrically connected to the first housing portion.

8. An implantable electrical stimulator with electromagnetic shielding function according to claim 3, wherein the electromagnetic shielding member includes a connection portion including a peripheral wall portion surrounding the base body and a flange portion protruding outward from an outer surface of the peripheral wall portion.

9. The implantable electrical stimulator with electromagnetic shielding function according to claim 8, wherein the conductive structure is electrically connected to the first housing portion through the connection portion.

10. The implantable electrical stimulator with electromagnetic shielding function according to claim 8, wherein the base body is insert-molded with the at least one connecting wire and the connecting portion.

11. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, wherein the control means includes a first circuit board and a second circuit board laminated and arranged at intervals in a thickness direction of the first housing portion, the first circuit board having opposite electronic-device-present faces and electronic-device-free faces in the thickness direction, the electronic-device-present faces being opposed to the second circuit board faces, the electronic-device-free faces being in contact with an inner surface of the first housing portion.

12. The implantable electrical stimulator with electromagnetic shielding function according to claim 1, wherein the at least one interaction device comprises a communication device and/or a wireless charging device.