Split-type fully implantable cochlear implant system

Abstract

This invention discloses a split-type fully implantable cochlear implant system, comprising a basic implant and an implantable speech processor. The basic implant receives coded signals from the implantable speech processor, decodes the coded signals, generates electrical stimulation pulses, and stimulates the auditory nerve. The implantable speech processor receives external sound signals, processes the sound signals, generates coded signals, and transmits them to the basic implant. The implantable speech processor is detachably connected to one side of the basic implant. The basic implant is provided with a connector, and the implantable speech processor is provided with a locking hole. When the implantable speech processor is connected to the basic implant, the connector is locked into the locking hole. With this split-type fully implantable cochlear implant system, when the speech processor hardware needs to be upgraded or damaged, only a minimally invasive surgery is required to remove the implantable speech processor through the connector, thereby avoiding secondary surgical damage, improving safety, and reducing user costs.

Description

Technical Field

[0001] This invention belongs to the field of medical device technology, and specifically relates to a split-type fully implantable cochlear implant system. Background Technology

[0002] Cochlear implants are crucial medical devices that help patients with severe and profound hearing loss regain their hearing. Traditional cochlear implant systems consist of an external sound processor and an implant within the body. The microphone of the external sound processor receives sound signals, which are then digitized and encoded by the processor. The encoded sound signal is then transmitted wirelessly via a transcutaneous link to the receiving coil in the implant. The implanted stimulation chip decodes the signal and converts it into a corresponding electrical signal, which is then used to send electrical impulses to the auditory nerve, stimulating the nerve and transmitting these impulses to the auditory center of the brain, thus producing hearing. With continuous technological advancements, fully implantable cochlear implants have gradually become a hot topic in research and application.

[0003] Compared to traditional cochlear implants with external devices, fully implantable cochlear implants offer better concealment and wearing comfort, significantly improving patients' quality of life. However, fully implantable cochlear implant systems face significant challenges in practical application. In integrated fully implantable designs, the speech processor is integrated with the implant itself. Upgrading the speech processor or causing malfunction requires removing the entire implanted structure, making the surgery extremely difficult. Furthermore, secondary surgeries can easily damage the cochlear structure and impair residual hearing. Therefore, there is an urgent need for a fully implantable cochlear implant system that avoids the damage caused by secondary surgeries. Summary of the Invention

[0004] To address the aforementioned problems, the technical solution of this invention is as follows: a split-type fully implantable cochlear implant system, comprising a basic implant and an implantable speech processor, wherein,

[0005] The basic implant is used to receive the encoded signal from the implantable speech processor, decode the encoded signal, generate electrical stimulation pulses, and stimulate the auditory nerve.

[0006] The implantable speech processor is used to receive external sound signals, process the sound signals, generate encoded signals, and transmit them to the basic implant.

[0007] The implantable speech processor is detachably connected to one side of the basic implant.

[0008] Preferably, the basic implant is provided with a connector, and the implantable speech processor is provided with a locking hole. When the implantable speech processor is connected to the basic implant, the connector is locked into the locking hole.

[0009] Preferably, the connector has a centerline, and the implanted speech processor has an inserted state and a final state;

[0010] When the implantable speech processor is in the inserted state, the connector is embedded in the slot and the implantable speech processor can rotate relative to the base implant about the center line of the connector.

[0011] When the implanted speech processor rotates to the final state, the connector can restrict the implanted speech processor from continuing to rotate.

[0012] Preferably, the connector has a centerline, the connector is basically T-shaped, the connector has a large head and a small head, the basic implant is provided with an installation hole, the large head is connected to the installation hole, and the small head protrudes from the installation hole and is detachably connected to the implantable speech processor.

[0013] Preferably, the small head is detachably connected to a limiting piece. When the implantable speech processor is connected to the base implant, the limiting piece can restrict the implantable speech processor from moving away from the base implant, and can also restrict the implantable speech processor from rotating relative to the base implant around the center line of the connector.

[0014] Preferably, the small head is substantially columnar and extends along the centerline of the connector; the outer diameter of the small head gradually decreases in the direction away from the large head.

[0015] Preferably, the cochlear implant system further includes an implantable cortical electrode, which is used to attach to the human cerebral cortex and is capable of collecting electroencephalogram (EEG) signals induced by stimulation of the cerebral cortex and sending the EEG signals to the implantable speech processor.

[0016] Preferably, the implantable cortical electrode is mounted on the implantable speech processor and can be removed from the base implant along with the implantable speech processor; or, the implantable cortical electrode is connected to the base implant and cannot be removed from the base implant along with the implantable speech processor.

[0017] Preferably, the implantable dermal electrode includes a plurality of electrode pads and a plurality of signal lines, wherein the signal lines correspond one-to-one with the electrode pads; the plurality of electrode pads are arranged at intervals along the length direction of the implantable dermal electrode.

[0018] Preferably, the implantable dermal electrode further includes a silicone base, a polyester mesh, and a silicone cap. The electrode pad and the signal line are arranged on the silicone base, and the silicone cap covers the side of the electrode pad away from the silicone base. The polyester mesh is clamped between the electrode pad and the silicone cap. The silicone base has a curved wire groove, and the signal line has a curved section embedded in the wire groove. The silicone base also has an electrode pad groove, in which the electrode pad is embedded. Several electrode pad grooves and several wire grooves are staggered along the length of the implantable dermal electrode, and the wire grooves connect adjacent electrode pad grooves.

[0019] The beneficial effects of this invention are as follows:

[0020] 1. The split-type fully implantable cochlear implant system of the present invention adopts a split design of the basic implant and the implantable speech processor. When the speech processor hardware needs to be upgraded or is damaged due to malfunction, only a minimally invasive surgery is required to remove the implantable speech processor through the connector, thereby avoiding secondary surgical damage, improving safety and reducing user costs.

[0021] 2. The split-type fully implantable cochlear implant system of the present invention features a connector on the basic implant. This connector allows for a detachable connection to the implantable speech processor, facilitating installation without occupying implantation space. Precise coil fit improves radio frequency transmission efficiency. The implantable speech processor can rotate relative to the basic implant around the centerline of the connector, thereby adjusting its implantation position for precise placement. Multiple connector structures are available, working in conjunction with limiting plates, allowing for the selection of a suitable connection structure for individual users, further enhancing implantation stability and user comfort.

[0022] 3. The split-type fully implantable cochlear implant system of the present invention, by setting an implantable cortical electrode attached to the human cerebral cortex, can collect the electroencephalogram (EEG) signals induced by stimulation in real time and transmit them to the implantable speech processor or the basic implant, thereby dynamically adjusting the stimulation parameters to form a precise closed-loop control and effectively improving the hearing rehabilitation effect.

[0023] 4. The split-type fully implantable cochlear implant system of the present invention includes an implantable cortical electrode comprising a silicone base, a silicone cap, and several signal lines with curved sections, possessing flexible characteristics to better adapt to the curved surface of the cerebral cortex, while avoiding component breakage under stress during implantation or human activity, effectively improving long-term implantation comfort and safety. The polyester mesh in the implantable cortical electrode serves as reinforcement and insulation, effectively improving the structural stability and biocompatibility of the implantable cortical electrode.

[0024] 5. The split-type fully implantable cochlear implant system of the present invention has a magnet-free structure that supports 3.0T MRI examination, avoiding problems such as magnet displacement, torque, and pain that may occur in traditional cochlear implant systems containing magnets due to strong magnetic fields. Attached Figure Description

[0025] Figure 1 This is a schematic diagram of the split-type fully implantable cochlear implant system after implantation, according to an embodiment of the present invention.

[0026] Figure 2 This is a schematic diagram of the overall structure of the split-type fully implantable cochlear implant system according to an embodiment of the present invention;

[0027] Figure 3 This is a schematic diagram of the overall structure of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention;

[0028] Figure 4 This is a schematic diagram of the structure of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention;

[0029] Figure 5 This is a schematic diagram of the connector and limiting plate structure of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention;

[0030] Figure 6 This is a schematic diagram of the implantable cortical electrode structure of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention;

[0031] Figure 7 This is a schematic diagram of the implantable cortical electrode structure of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention;

[0032] Figure 8 This is a partial structural diagram of the implantable cortical electrode of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention.

[0033] Figure 9 This is a partial structural diagram of the implantable cortical electrode of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention.

[0034] Figure 10 This is a schematic diagram of the implantable cortical electrode structure of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention;

[0035] Figure 11 This is a schematic diagram of the structure of the implantable cortical electrode of a split-type fully implantable cochlear implant system according to a specific embodiment of the present invention.

[0036] Explanation of reference numerals in the attached figures:

[0037] 1. Basic implant; 2. Implantable speech processor; 3. Connector; 11. Receiving coil; 12. Mounting hole; 13. Extracochlear planar electrode; 14. Stimulator; 15. Extracochlear tubular electrode; 16. Electrode array; 21. Transmission coil; 22. Clip; 23. Processor; 231. Battery; 232. Circuit board; 233. Electrical connection feedthrough; 24. Second fully implantable microphone; 25. First connecting wire; 26. First fully implantable microphone; 27. Second connecting line; 28. Implantable dermal electrode; 281. Silicone base; 282. Dermal electrode assembly; 283. Polyester mesh; 284. Silicone cap; 2811. Electrode slot; 2812. Through hole; 2813. Wire slot; 2814. Inclined part; 2815. Outlet slot; 2816. Semi-cylinder; 2817. Rounded corner; 2821. Electrode piece; 2822. Bending section; 2823. Signal line; 31. Large head; 32. Small head. Detailed Implementation

[0038] The preferred embodiments of the present invention will now be described in detail with reference to the accompanying drawings.

[0039] See Figures 1-3 The split-type fully implantable cochlear implant system includes a basic implant 1 and an implantable speech processor 2. The implantable speech processor 2 is used to receive external sound signals, process the sound signals, generate encoded signals, and transmit them to the basic implant 1. The basic implant 1 is used to receive the encoded signals from the implantable speech processor 2, decode the encoded signals, generate electrical stimulation pulses, and stimulate the auditory nerve. The implantable speech processor 2 is detachably connected to one side of the basic implant 1.

[0040] The device adopts a split design of basic implant 1 and implantable speech processor 2. When implantable speech processor 2 needs to be upgraded or is damaged due to malfunction, it can be removed by minimally invasive surgery, thereby avoiding secondary surgical damage, improving safety and reducing user costs.

[0041] Specifically, the implantable speech processor 2 includes a transmission coil 21, a processor 23, a first fully implantable microphone 26, and a second fully implantable microphone 24. Both the first and second fully implantable microphones 26 and 24 are connected to the processor 23. The first fully implantable microphone 26 is connected to the processor 23 via a first connecting cable 25, and the second fully implantable microphone 24 is mounted on the processor 23. The first fully implantable microphone 26 receives and transmits a first external sound signal to the processor 23. The first external sound signal mainly includes external sound information, specifically valuable external sound information and non-valued external noise information. The second fully implantable microphone 24 collects and transmits internal noise signals to the processor 23. Internal noise signals include internal sound information, such as sounds caused by internal organs, bones, or muscle activity. See also... Figure 4 The processor 23 includes a battery 231 and a circuit board 232. The battery 231 provides power to the system and is an independent power supply module that can be replaced separately. The circuit board 232, as the core circuit component of the implantable speech processor 2, receives the first external sound signal and the internal noise signal, processes the sound, and generates an encoded signal. The transmission coil 21 is connected to the processor 23 to transmit the encoded signal and energy to the basic implant 1. The implantable speech processor 2 also includes an electrical connection feedthrough 233, which is connected to the circuit board 232, the implantable cortical electrode 28, the first fully implantable microphone 26, and the second fully implantable microphone 24, respectively, serving as the electrical signal transmission interface between the components and ensuring signal connectivity between them. The implantable speech processor 2 is encapsulated in silicone to ensure the implant is safe and reliable within the human body.

[0042] After implantation, the basic implant 1 is fixed in the cochlea and corresponding position in the skull. It includes a stimulator 14, an extracochlear flat electrode 13, an extracochlear tubular electrode 15, an electrode array 16, and a receiving coil 11. The receiving coil 11 is used to receive the encoded signals and energy from the implanted speech processor 2. The stimulator 14 is connected to the receiving coil 11 and is used to decode the encoded signals to generate electrical stimulation pulses. The electrode array 16 is connected to the stimulator 14 and is the main electrical stimulation component, used to stimulate the auditory nerve by inserting it into the scala tympani of the cochlea. The extracochlear tubular electrode 15 and the extracochlear flat electrode 13 are also connected to the stimulator 14 respectively, and their main function is to form a circuit with the electrode array 16 when the cochlear implant system is working. The basic implant 1 is usually encapsulated in silicone to ensure that the implant can work safely and reliably in the human body.

[0043] See Figures 2-4The basic implant 1 is provided with a connector 3, and the implantable speech processor 2 is provided with a slot 22. When the implantable speech processor 2 is connected to the basic implant 1, the connector 3 is snapped into the slot 22. The receiving coil 11 and the transmitting coil 21 are precisely fitted together, which improves the radio frequency transmission efficiency.

[0044] In one specific embodiment, the connector 3 has a centerline, and the implantable speech processor 2 has a snap-in state and a final state. When the implantable speech processor 2 is in the snap-in state, the connector 3 is embedded in the slot 22, and the implantable speech processor 2 can rotate relative to the base implant 1 around the centerline of the connector 3. When the implantable speech processor 2 rotates to the final state, the connector 3 can restrict the implantable speech processor 2 from continuing to rotate. By setting an adjustable angle structure, it is convenient for doctors to adjust the implantation angle according to the surgical situation.

[0045] See Figure 4 and Figure 5 In another specific embodiment, the connector 3 has a center line, the connector 3 is basically T-shaped, the connector 3 has a large head 31 and a small head 32, the receiving coil 11 of the basic implant 1 is provided with a mounting hole 12 at the center position, the large head 31 is connected to the mounting hole 12, and the small head 32 extends out of the mounting hole 12 and is detachably connected to the implanted speech processor 2.

[0046] The small head 32 is detachably connected to a limiting plate. When the implantable speech processor 2 is connected to the base implant 1, the limiting plate can restrict the implantable speech processor 2 from moving away from the base implant 1, and can also restrict the implantable speech processor 2 from rotating relative to the base implant 1 around the center line of the connector 3. Furthermore, the small head 32 is basically cylindrical and extends along the center line of the connector 3; the outer diameter of the small head 32 is gradually reduced in the direction away from the large head 31.

[0047] This application incorporates a connector 3 on the basic implant 1, enabling a detachable connection between the connector 3 and the implantable speech processor 2. This facilitates installation without occupying implantation space, and the precise coil fit improves radio frequency transmission efficiency. The implantable speech processor 2 can rotate relative to the basic implant 1 around the centerline of the connector 3, thereby adjusting the implantation position and angle for precise implantation. Multiple connector 3 structures are available, which, in conjunction with limiting plates, allow for the selection of suitable connection structures based on individual user needs, further enhancing implantation stability and user comfort.

[0048] See Figure 2 and Figure 3 The cochlear implant system also includes an implantable cortical electrode 28, which is attached to the human cerebral cortex and can collect the electroencephalogram (EEG) signals induced by stimulation of the cerebral cortex and send the EEG signals to the implantable speech processor 2.

[0049] By setting up implantable cortical electrodes 28 attached to the human cerebral cortex, the electroencephalogram (EEG) signals induced by stimulation can be collected in real time and transmitted to the implantable speech processor 2 or the basic implant 1. The processor 23 adjusts the electrical signal parameters (such as frequency and intensity) of the stimulator 14 in real time, forming a closed-loop control process of sound input, electrical stimulation, and feedback from the implantable cortical electrodes 28 to parameter optimization. This dynamically adjusts the stimulation parameters to form precise closed-loop control, effectively improving the hearing rehabilitation effect.

[0050] Furthermore, the implantable cortical electrode 28 is mounted on the implantable speech processor 2 and can be removed from the base implant 1 along with the implantable speech processor 2; or, the implantable cortical electrode 28 is connected to the base implant 1 and cannot be removed from the base implant 1 along with the implantable speech processor 2.

[0051] See Figure 3 In one specific embodiment, the implantable cortical electrode 28 is mounted on the implantable speech processor 2, and the implantable speech processor 2 is provided with a second connecting line 27. The implantable cortical electrode 28 and the implantable speech processor 2 are connected through the second connecting line 27.

[0052] See Figure 6 and Figure 7 The implantable dermal electrode 28 includes a dermal electrode assembly 282, which includes a plurality of electrode pads 2821 and a plurality of signal lines 2823. The signal lines 2823 correspond one-to-one with the electrode pads 2821; the plurality of electrode pads 2821 are arranged at intervals along the length of the implantable dermal electrode 28.

[0053] See Figures 6-11The implantable cortical electrode 28 also includes a silicone base 281, a polyester mesh 283, and a silicone cap 284. The electrode sheet 2821 and the signal line 2823 are arranged on the silicone base 281. The silicone cap 284 covers the side of the electrode sheet 2821 away from the silicone base 281. The polyester mesh 283 is clamped between the electrode sheet 2821 and the silicone cap 284, which can enhance the structural strength of the implantable cortical electrode 28. The silicone base 281 is provided with a bent wire groove 2813. The signal line 2823 has a bent section 2822, which is embedded in the wire groove 2813. The bent section 2822 is used to improve the tensile strength of the signal line 2823. The silicone base 281 is also provided with electrode slots 2811, and electrode pads 2821 are embedded in the electrode slots 2811. Several electrode slots 2811 and several wire slots 2813 are arranged alternately along the length of the implanted cortical electrode 28, and the wire slots 2813 connect two adjacent electrode slots 2811. Through holes 2812 are provided in the electrode slots 2811 for the electrode pads 2821 to collect electroencephalogram (EEG) signals induced by stimulation of the cerebral cortex.

[0054] In one specific embodiment, a semi-cylinder 2816 is fixed to both the end of the silicone base 281 near the processor 23 and the end of the silicone cover 284 near the processor 23. The two semi-cylinders 2816 can close together to form a complete cylindrical structure, which enhances structural strength and improves adaptability to human tissue. A wire exit groove 2815 is formed on the facing surfaces of the two semi-cylinders 2816. One end of one wire exit groove 2815 extends to the silicone base 281, and the other end extends to the silicone cover 284. Signal lines 2823 converge and are embedded within the wire exit groove 2815, forming a bundle that extends outward from the implanted cortical electrode 28 and connects to the second connecting line 27. The wire exit groove 2815 serves to organize the routing of the signal lines 2823, preventing tangling or damage from stress. The width of the semi-cylinder 2816 is smaller than the width of the silicone base 281. Along the direction from the silicone base 281 to the semi-cylinder 2816, the width of the silicone base 281 near the end of the semi-cylinder 2816 gradually decreases until it is equal to the width of the semi-cylinder 2816, and an inclined portion 2814 is formed on the side wall of the silicone base 281. Similarly, the width of the semi-cylinder 2816 is smaller than the width of the silicone cap 284. Along the direction from the silicone cap 284 to the semi-cylinder 2816, the width of the silicone cap 284 near the end of the semi-cylinder 2816 gradually decreases until it is equal to the width of the semi-cylinder 2816, and an inclined portion 2814 is also formed on the side wall of the silicone cap 284. This design optimizes the fit of the implanted dermal electrode 28, adapts to the physiological curvature of human tissue, and reduces the foreign body sensation after implantation. Both the end of the silicone base 281 away from the semi-cylinder 2816 and the end of the silicone cap 284 away from the semi-cylinder 2816 are provided with rounded corners 2817 to avoid damage to human tissue from sharp edge structures, thereby further improving biocompatibility and implantation safety.

[0055] It should be noted that the silicone base 281 and the silicone cover 284 can be bonded with medical-grade silicone adhesive (such as silicone room temperature curing adhesive); the adhesive must meet biocompatibility requirements and have good flexibility and sealing properties after curing, so as to achieve stable encapsulation and fixation of the skin electrode assembly 282 and the polyester mesh 283; the electrode welding components are mutually insulated.

[0056] In terms of size, the split-type fully implantable cochlear implant system has an ultra-thin, non-magnetic structure with no protrusion on the body surface after implantation. The thickness of the transmission coil 21 is ≤1mm, and the thickness of the implantable cortical electrode 28 is ≤0.8mm.

[0057] The implantable cortical electrode 28 of this application includes a silicone base 281, a silicone cap 284, and several signal lines 2823 with curved sections 2822. Its flexibility allows it to better adapt to the curved surface of the cerebral cortex, while preventing component breakage under stress during implantation or human activity, effectively improving long-term implantation comfort and safety. The polyester mesh 283 in the implantable cortical electrode 28 provides reinforcement and insulation, effectively improving the structural stability and biocompatibility of the implantable cortical electrode 28. Furthermore, the magnet-free structure supports 3.0T MRI examinations, avoiding problems such as magnet displacement, torque, and pain that may occur in traditional magnetic cochlear implant systems due to strong magnetic fields.

[0058] The implantation procedure for a split cochlear implant system is as follows:

[0059] S1: The electrode array 16 is implanted into the cochlear scala tympani, and the receiving coil 11 is fixed to the surface of the skull.

[0060] S2: Then, attach the silicone base 281 to the corresponding area of ​​the cerebral cortex and fix the electrode pad 2821;

[0061] S3: Connect and fix the implantable speech processor 2 to the basic implant 1 via connector 3. The first fully implantable microphone 26 is fixed near the ear canal, and the battery 231 is located in the subcutaneous pre-reserved cavity. The system assembly is completed and the closed-loop parameters are adjusted.

[0062] The maintenance and upgrade process is as follows:

[0063] Speech processor 23 upgrade: The implanted speech processor 2 was removed by minimally invasive surgery, replaced with a new module, and then reconnected and the closed-loop parameters were calibrated.

[0064] Replacement of implanted dermal electrode 28: Remove the implanted dermal electrode 28 from the subcutaneous tissue, replace it, and then reposition it. This does not affect other components.

[0065] Battery 231 replacement: Remove the subcutaneous battery 231 module separately, replace it, and then reset.

[0066] In summary, this invention employs a modular, split-type design and a closed-loop control architecture with implantable cortical electrodes 28. The system is divided into a basic implant 1, an implantable speech processor 2, and implantable cortical electrodes 28. A special connector 3 structure enables the components to be detachable and coordinated. Simultaneously, the EEG signals collected by the implantable cortical electrodes 28 provide feedback to optimize the auditory experience, ensuring comfort and discreetness. The ultra-thin components do not protrude from the body surface after implantation, and the flexible carrier of the implantable cortical electrodes 28 provides high conformity, improving long-term implantation comfort. The modular components can be replaced individually, effectively reducing user costs.

[0067] Finally, it should be noted that the above preferred embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit it. Although the present invention has been described in detail through the above preferred embodiments, those skilled in the art should understand that various changes can be made to it in form and detail without departing from the scope defined by the claims of the present invention.

Claims

1. A split-type fully implantable cochlear implant system, characterized in that, This includes basic implants and implantable speech processors, among which, The basic implant is used to receive the encoded signal from the implantable speech processor, decode the encoded signal, generate electrical stimulation pulses, and stimulate the auditory nerve. The implantable speech processor is used to receive external sound signals, process the sound signals, generate encoded signals, and transmit them to the basic implant. The implantable speech processor is detachably connected to one side of the basic implant; The basic implant is provided with a connector, and the implantable speech processor is provided with a slot. When the implantable speech processor is connected to the basic implant, the connector is snapped into the slot. The connector has a center line, and the implanted speech processor has an inserted state and a final state; When the implantable speech processor is in the inserted state, the connector is embedded in the slot and the implantable speech processor can rotate relative to the base implant about the center line of the connector. When the implanted speech processor rotates to the final state, the connector can restrict the implanted speech processor from continuing to rotate.

2. The split-type fully implantable cochlear implant system according to claim 1, characterized in that, The connector is basically T-shaped, with a large head and a small head. The basic implant has an installation hole, the large head is connected to the installation hole, and the small head protrudes from the installation hole and is detachably connected to the implanted speech processor.

3. The split-type fully implantable cochlear implant system according to claim 2, characterized in that, The small head is detachably connected to a limiting plate. When the implantable speech processor is connected to the base implant, the limiting plate can restrict the implantable speech processor from moving away from the base implant, and can also restrict the implantable speech processor from rotating relative to the base implant around the center line of the connector.

4. The split-type fully implantable cochlear implant system according to claim 2, characterized in that, The small head is basically columnar and extends along the center line of the connector; the outer diameter of the small head gradually decreases in the direction away from the large head.

5. The split-type fully implantable cochlear implant system according to claim 1, characterized in that, The cochlear implant system also includes an implantable cortical electrode, which is attached to the human cerebral cortex and can collect electroencephalogram (EEG) signals induced by stimulation of the cerebral cortex and send the EEG signals to the implantable speech processor.

6. The split-type fully implantable cochlear implant system according to claim 5, characterized in that, The implantable cortical electrode is mounted on the implantable speech processor and can be removed from the base implant along with the implantable speech processor; or, the implantable cortical electrode is connected to the base implant and cannot be removed from the base implant along with the implantable speech processor.

7. The split-type fully implantable cochlear implant system according to claim 6, characterized in that, The implantable dermal electrode includes several electrode pads and several signal lines, with each signal line corresponding to one of the electrode pads; the several electrode pads are arranged at intervals along the length of the implantable dermal electrode.

8. The split-type fully implantable cochlear implant system according to claim 7, characterized in that, The implantable dermal electrode further includes a silicone base, a polyester mesh, and a silicone cap. The electrode pad and the signal line are arranged on the silicone base, and the silicone cap covers the side of the electrode pad away from the silicone base. The polyester mesh is clamped between the electrode pad and the silicone cap. The silicone base has a curved wire groove, and the signal line has a curved section embedded in the wire groove. The silicone base also has an electrode pad groove, in which the electrode pad is embedded. Several electrode pad grooves and several wire grooves are staggered along the length of the implantable dermal electrode, and the wire grooves connect adjacent electrode pad grooves.

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