Flexible electrode for implantable neural signal device, implantable neural signal device and preparation method of flexible electrode

Abstract

The invention provides a flexible electrode for an implantable neural signal device, the implantable neural signal device and a preparation method of the flexible electrode. The implantable neural signal device comprises a feed-through piece, the flexible electrode is electrically connected with the feed-through piece, and the flexible electrode comprises a far-end electrode part, a near-end electrode part and a lead connecting part. The near-end electrode part comprises an electrode body and a conductive contact, the conductive contact forms a hollow structure, and the hollow structure is configured to deform when the conductive contact is stressed, so that the conductive contact abuts against the feed-through piece to form electric connection. The hollow structure of the flexible electrode can enable the conductive contact to deform after being stressed, so that the deformation capability of the electrode joint is enhanced, the deformed conductive contact can be in closer contact with the feed-through piece, and the improvement of the reliability of electric connection between the conductive contact and the feed-through piece is facilitated.

Description

Technical Field

[0001] The present application relates to the technical field of flexible electrodes, and in particular to a flexible electrode for an implantable neural signal device, an implantable neural signal device, and a method for preparing the flexible electrode. Background Art

[0002] At present, neural signal systems including implantable neural signal devices have been widely used in the medical field. In this system, the implantable neural signal device is implanted into the patient's body to achieve treatment of the affected part and the collection of relevant signals of the affected part. For example, a neural stimulator regulates neural activity by sending electrical stimulation pulses to the brain or spinal cord, thereby treating neurological diseases such as Parkinson's disease, epilepsy, depression and pain. In order to achieve dynamic regulation of neural activity, the neural stimulator can also record signals from the brain and other parts, and automatically adjust the stimulation parameters according to the relevant signals.

[0003] However, the traditional implantable electrode is constructed as a rigid tubular structure, which is electrically connected to the stimulator body through a beveled coil spring. However, the implantable electrode and beveled coil spring assembly are large in size, and the electrode is not flexible enough to meet the flexibility requirements of the implantable electrode. If a flexible electrode is used to overcome the flexibility problem, the contact surface between the flexible electrode and the feedthrough is a plane, and there is a certain gap between the two, which can easily lead to the problem of low electrical connection reliability, that is, the flexible electrode is prone to sliding with the feedthrough, resulting in misalignment of the conductive contacts, affecting the stability of the electrical connection. Summary of the invention

[0004] In response to the above-mentioned technical problems existing in the prior art, the present application provides a flexible electrode for an implantable neural signal device, an implantable neural signal device and a method for preparing a flexible electrode. The hollow structure of the flexible electrode can cause the conductive contact to deform after being subjected to force, thereby enhancing the deformation capacity of the electrode connection, so that the deformed conductive contact can be in closer contact with the feedthrough, which is beneficial to improving the reliability of the electrical connection between the conductive contact and the feedthrough.

[0005] The embodiment of the present application provides a flexible electrode for an implantable neural signal device. The implantable neural signal device includes a feedthrough, the flexible electrode is electrically connected to the feedthrough, and the flexible electrode includes a distal electrode portion, a proximal electrode portion, and a lead connection portion. The distal electrode portion includes at least one electrode site, and the electrode site is used to apply electrical stimulation to the target tissue and / or collect the potential signal of the target tissue. The proximal electrode portion includes an electrode body and at least one conductive contact provided on the electrode body, the conductive contact is formed with a hollow structure, and the hollow structure is configured to deform the conductive contact when the conductive contact is subjected to force, so that the deformed conductive contact is against the feedthrough to form an electrical connection. The lead connection portion includes a lead, and the two ends of the lead are electrically connected to the conductive contact of the proximal electrode portion and the electrode site of the distal electrode portion respectively, and the distal electrode portion, the proximal electrode portion and the lead connection portion are arranged in sequence along the length direction of the flexible electrode.

[0006] In some embodiments, the conductive contact has an electrically connected contact middle portion and a contact deformation portion, wherein the contact deformation portion is arranged around the outer periphery of the contact middle portion.

[0007] In some embodiments, the hollow structure is formed on the contact deformation portion, and / or the hollow structure is formed between the contact deformation portion and the electrode body.

[0008] In some embodiments, there are multiple hollow structures, and the multiple hollow structures are arranged at intervals around the middle of the contact.

[0009] In some embodiments, there are multiple contact deformation parts, and the multiple contact deformation parts are electrically connected to the contact middle part and the lead connection part respectively.

[0010] In some embodiments, a plurality of the contact deformation portions are evenly arranged around the periphery of the middle portion of the contact.

[0011] In some embodiments, the contact deformation portion includes a plurality of bending structures connected in sequence, the hollow structure is formed between the plurality of bending structures and the electrode body, and the plurality of bending structures are configured to be stretched and deformed along the direction of force after being subjected to force.

[0012] In some embodiments, the bending directions of adjacent bending structures are opposite to each other.

[0013] In some embodiments, the contact deformation portion includes a spiral structure connected to the middle portion of the contact, the spiral structure spirals outward around the middle portion of the contact in sequence, and is electrically connected to the lead connection portion.

[0014] In some embodiments, the hollow structure is formed on the contact deformation portion, and the hollow structure has a plurality of fold line portions forming a closed cavity, and the plurality of fold line portions are arranged around the middle portion of the contact.

[0015] In some embodiments, a plurality of through holes are formed in the middle portion of the contact, and the plurality of through holes are used to provide a deformation space for the middle portion of the contact.

[0016] In some embodiments, the deformation range of the conductive contact in the thickness direction of the proximal electrode portion is not less than 10 microns.

[0017] In some embodiments, there are multiple conductive contacts, and the multiple conductive contacts are arranged linearly or in an array along the length direction of the proximal electrode portion.

[0018] In some embodiments, the thickness of the flexible electrode is no greater than 200 microns.

[0019] In some embodiments, the flexible electrode includes a first insulating layer, a first conductive layer, and a second insulating layer stacked along the thickness direction, the conductive contacts, electrode sites, and leads are all arranged in the first conductive layer, and the conductive contacts and electrode sites are exposed to the first insulating layer and / or the second insulating layer.

[0020] In some embodiments, the flexible electrode further includes a second conductive layer and a third insulating layer, the second conductive layer is disposed on a side of the second insulating layer facing away from the first conductive layer, and the third insulating layer is disposed on a side of the second conductive layer facing away from the second insulating layer.

[0021] An embodiment of the present application also provides an implantable neural signal device, comprising the above-mentioned flexible electrode for the implantable neural signal device, and also comprising an action component, the action component comprising a first shell, an action module and a feed-through, the action module being arranged in the first shell, the feed-through being arranged on the first shell, the flexible electrode being electrically connected to the action module via the feed-through; wherein the action module comprises a stimulation module and / or an acquisition module.

[0022] In some embodiments, the active component also includes an electrode cover, which covers the proximal electrode portion of the flexible electrode. A pressure connector is provided on the side of the electrode cover facing the flexible electrode, and the pressure connector is used to apply a force to the conductive contacts of the proximal electrode portion to press against the feedthrough.

[0023] In some embodiments, the feedthrough component includes an insulating carrier and a feedthrough conductor, the insulating carrier is disposed on one side of the first shell, the feedthrough conductor passes through the insulating carrier, and both ends of the feedthrough conductor are electrically connected to the conductive contact and the action module respectively.

[0024] In some embodiments, there are a plurality of feed-through conductors, and a plurality of the feed-through conductors are arrayed on the insulating carrier.

[0025] In some embodiments, the pressure connector includes at least one elastic member, which is arranged in a one-to-one correspondence with the conductive contacts, and the elastic member is used to apply a force to the conductive contacts of the flexible electrode so that the conductive contacts are pressed against the feed-through member to form an electrical connection.

[0026] In some embodiments, an outer edge of the electrode cover and an outer edge of the first shell are mounted on each other, and a first sealing gasket is provided between the outer edge of the electrode cover and the outer edge of the first shell.

[0027] In some embodiments, the pressure connector also includes a seat body and a second sealing gasket, the seat body is connected to the distal side of the electrode cover, and a mounting hole is provided on the seat body, the elastic member is arranged in the mounting hole, the second sealing gasket is arranged on the seat body and surrounds the outer peripheral side of the elastic member, and the second sealing gasket is located on the inner peripheral side of the first sealing gasket.

[0028] The embodiment of the present application also provides a method for preparing a flexible electrode, which is used to prepare the above-mentioned flexible electrode for an implantable neural signal device, wherein the flexible electrode comprises a first insulating layer, a first conductive layer, and a second insulating layer stacked in a thickness direction, wherein the conductive contacts, electrode sites, and leads are all arranged in the first conductive layer, and the conductive contacts and electrode sites are exposed to the first insulating layer and / or the second insulating layer, and the method for preparing the flexible electrode comprises: Spin coating and baking the insulating slurry to form a first insulating layer; removing a portion of the first insulating layer corresponding to the electrode site to expose the electrode site through the first insulating layer; forming a first conductive layer on the first insulating layer by photolithography and coating; Spin coating and baking an insulating paste on a side of the first conductive layer facing away from the first insulating layer to form a second insulating layer; removing portions of the second insulating layer corresponding to the electrode sites and the conductive contacts to expose the electrode sites and the conductive contacts through the second insulating layer; Portions of the first insulating layer and the second insulating layer corresponding to the hollow structure are removed.

[0029] Compared with the prior art, the beneficial effects of the embodiments of the present application are: the present application can better adapt to the shape and movement of the neural tissue by using a flexible electrode, thereby reducing the mechanical pressure and damage to the surrounding tissue, and a hollow structure is formed on the conductive contact of the proximal electrode portion of the flexible electrode, which can cause the conductive contact to deform after being subjected to force, thereby enhancing the deformation ability of the electrode connection, so that the deformed conductive contact can be in closer contact with the feedthrough, which is beneficial to improving the reliability of the electrical connection between the conductive contact and the feedthrough, and ensuring the conduction effect at the contact point, and the conductive contact after being subjected to pressure is no longer in the same plane with the rest of the flexible electrode due to deformation, which enables the conductive contact to be stably limited to the position in contact with the feedthrough, which can ensure that the conductive contact is difficult to displace, and further improves the reliability of the electrical connection. In addition, after the deformed conductive contact is in closer contact with the feedthrough, the contact gap between the conductive contact and the feedthrough can be reduced as much as possible, thereby facilitating the improvement of the sealing between the conductive contact and the feedthrough, and ensuring that the implantable neural signal device can be implanted stably for a long time. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] In the drawings, which are not necessarily drawn to scale, the same reference numerals may describe similar components in different views. The drawings generally illustrate various embodiments by way of example and not limitation, and together with the description and claims, serve to illustrate the disclosed embodiments. When appropriate, the same reference numerals are used throughout the drawings to refer to the same or similar parts. Such embodiments are illustrative and are not intended to be exhaustive or exclusive embodiments of the present apparatus or method.

[0031] Figure 1 It is a cross-sectional view of an implantable neural signal device using the flexible electrode of an embodiment of the present application.

[0032] Figure 2 It is a schematic diagram of the three-dimensional structure of an implantable neural signal device using the flexible electrode of an embodiment of the present application.

[0033] Figure 3 This is a planar structural diagram of the flexible electrode according to an embodiment of the present application, and the contact deformation portion shown in the diagram includes a bending structure.

[0034] Figure 4 This is a schematic diagram of the three-dimensional structure of the flexible electrode according to an embodiment of the present application.

[0035] Figure 5 This is a planar structural diagram of the flexible electrode according to an embodiment of the present application, and the contact deformation portion shown in the diagram includes a spiral structure.

[0036] Figure 6 This is a planar structural diagram of the flexible electrode according to an embodiment of the present application. The hollow structure shown in the figure has multiple fold line portions.

[0037] Figure 7 This is a partial structural diagram of the flexible electrode according to an embodiment of the present application, in which a through hole is formed in the middle of the contact shown in the figure.

[0038] Figure 8 It is a schematic diagram of the three-dimensional structure of the electrode cover and the pressure connector of the implantable neural signal device using the flexible electrode of the embodiment of the present application.

[0039] Fig. 9 This is a flow chart of a method for preparing a flexible electrode according to an embodiment of the present application.

[0040] The components indicated by the reference numerals in the figures are: 1. Feed-through; 11. Insulating carrier; 12. Feed-through conductor; 2. Flexible electrode; 3. Distal electrode portion; 31. Electrode site; 4. Proximal electrode portion; 41. Electrode body; 42. Conductive contact; 43. Hollow structure; 44. Middle part of contact; 45. Contact deformation portion; 46. Through hole; 5. Lead connection portion; 6. Active component; 61. First shell; 62. Circuit board; 7. Electrode cover; 8. Pressure connector; 81. Elastic member; 82. Seat body; 83. Second sealing gasket; 9. First sealing gasket. DETAILED DESCRIPTION

[0041] In order to enable those skilled in the art to better understand the technical solution of the present application, the present application is described in detail below in conjunction with the accompanying drawings and specific implementation examples. The embodiments of the present application are further described in detail below in conjunction with the accompanying drawings and specific implementation examples, but are not intended to limit the present application.

[0042] The words "first", "second" and similar words used in this application do not indicate any order, quantity or importance, but are only used to distinguish different parts. The words "include" or "comprise" and similar words mean that the elements before the word include the elements listed after the word, and do not exclude the possibility of including other elements. "Up", "down", "left", "right" and the like are only used to indicate relative positional relationships. When the absolute position of the described object changes, the relative positional relationship may also change accordingly.

[0043] In the present application, when a specific device is described as being located between a first device and a second device, there may or may not be an intermediate device between the specific device and the first device or the second device. When a specific device is described as being connected to other devices, the specific device may be directly connected to the other device without an intermediate device, or may not be directly connected to the other device but have an intermediate device.

[0044] All terms (including technical terms or scientific terms) used in this application have the same meaning as those understood by ordinary technicians in the field to which this application belongs, unless otherwise specifically defined. It should also be understood that terms defined in general dictionaries should be interpreted as having a meaning consistent with their meaning in the context of the relevant technology, and should not be interpreted in an idealized or extremely formal sense, unless explicitly defined herein.

[0045] Technologies, methods, and equipment known to ordinary technicians in the relevant art may not be discussed in detail, but where appropriate, the technologies, methods, and equipment should be considered as part of the specification.

[0046] In the present application, the term "proximal" is intended to mean a side close to an operator (e.g., a doctor) performing an implantation operation, and the term "distal" is intended to mean a side close to a target area of ​​an implantable neural signal device to be implanted. Similarly, the term "proximal end" is intended to mean an end close to an operator (e.g., a doctor) performing an implantation operation, and the term "distal end" is intended to mean a side close to a target area of ​​an implantable neural signal device to be implanted.

[0047] All terms (including technical terms or scientific terms) used in this application have the same meaning as those understood by ordinary technicians in the field to which this application belongs, unless otherwise specifically defined. It should also be understood that terms defined in general dictionaries should be interpreted as having a meaning consistent with their meaning in the context of the relevant technology, and should not be interpreted in an idealized or extremely formal sense, unless explicitly defined as such here. Techniques, methods and equipment known to ordinary technicians in the relevant field may not be discussed in detail, but where appropriate, they should be considered as part of the specification.

[0048] The present application embodiment provides a flexible electrode for an implantable neural signal device. Figures 1 to 4 As shown, the implantable neural signal device includes a feedthrough 1, a flexible electrode 2 is electrically connected to the feedthrough 1, and the flexible electrode 2 includes a distal electrode portion 3, a proximal electrode portion 4, and a lead connection portion 5. The distal electrode portion 3 includes at least one electrode site 31, and the electrode site 31 is used to apply electrical stimulation to the target tissue and / or collect the potential signal of the target tissue. The proximal electrode portion 4 includes an electrode body 41 and at least one conductive contact 42 provided on the electrode body 41, and the conductive contact 42 is formed with a hollow structure 43, and the hollow structure 43 is configured to deform the conductive contact 42 when the conductive contact 42 is subjected to force, so that the deformed conductive contact 42 is against the feedthrough 1 to form an electrical connection. The lead connection portion 5 includes a lead, and the two ends of the lead are electrically connected to the conductive contact 42 of the proximal electrode portion 4 and the electrode site 31 of the distal electrode portion 3 respectively, and the distal electrode portion 3, the proximal electrode portion 4 and the lead connection portion 5 are sequentially arranged along the length direction of the flexible electrode 2.

[0049] In the case where the above-mentioned implantable neural signal device includes a stimulator, the stimulator may be electrically connected to the electrode site 31 of the distal electrode portion 3 to apply electrical stimulation to the target tissue through the electrode site 31 .

[0050] In the case where the implantable neural signal device includes a collector, the collector may be electrically connected to the electrode site 31 of the distal electrode portion 3 to collect the potential signal of the target tissue through the electrode site 31 .

[0051] The flexible electrode 2 can be made of a flexible material. The flexible material can make the flexible electrode 2 have good flexibility and biocompatibility so as to better adapt to the shape and movement of nerve tissue, thereby reducing mechanical pressure and damage to surrounding tissues.

[0052] The flexible electrode 2 may be constructed as a sheet-like structure.

[0053] When the flexible electrode 2 is in a static state, ie, when not subjected to external force, the conductive contact 42 can be understood as being non-deformable or freely deformable.

[0054] The force acting on the above-mentioned conductive contact 42 may come from the pressure connector 8 of the implantable neural signal device (the specific structure of the pressure connector 8 is described below and will not be described here), or from other components of the implantable neural signal device. It only needs to be able to stabilize the conductive contact 42, and this application does not make any specific limitations on this.

[0055] The hollow structure 43 can provide sufficient deformation space for the conductive contact 42 in the thickness direction of the flexible electrode 2 after the conductive contact 42 is subjected to force, so that the conductive contact 42 and the feed-through 1 can be stably abutted against each other to form an electrical connection.

[0056] The conductive contact 42 may be partially or completely made of elastic material to further increase the deformable space of the conductive contact 42 so that the conductive contact 42 can be offset against the feed-through 1 through deformation.

[0057] There may be a plurality of the hollow structures 43 , and the plurality of hollow structures 43 may be arranged at intervals from each other, so as to facilitate more uniform deformation of the conductive contact 42 after being subjected to force.

[0058] The deformation of the conductive contact 42 can be understood as the deformation of the conductive contact 42 arching away from the plane where the electrode body 41 is located. Specifically, the shape of the conductive contact 42 before deformation can be planar, and it can be in the same plane as the electrode body 41. The shape of the conductive contact 42 after deformation can be arched, and the conductive contact 42 and the electrode body 41 are in different planes. For example, Figure 3 and Figure 4As shown, Figure 3 The conductive contact 42 shown in FIG. 1 is in a state before deformation. Figure 4 The conductive contact 42 is shown in a deformed state.

[0059] The cross-sectional area of ​​the hollow structure 43 is less than or equal to 90% of the cross-sectional area of ​​the conductive contact 42 where the hollow structure 43 is located. In this way, the conductive contact 42 can form a larger current passing area to meet the effective electrical connection area between the conductive contact 42 and the feed-through 1.

[0060] The above-mentioned hollow structures 43 can be arranged in an axisymmetric or centrosymmetric manner, or in an array manner. The present application does not specifically limit the arrangement of the hollow structures 43, as long as the deformed conductive contacts 42 and the feed-through 1 can be stably offset.

[0061] The shape of the hollow structure 43 may be one or more of the following: circular, elliptical, arc-shaped and polygonal, or a combination of one or more irregular polygonal shapes. The shape of the hollow structure 43 may be specifically designed according to the deformation range required by the conductive contact 42.

[0062] The present application can better adapt to the shape and movement of neural tissue by adopting a flexible electrode 2, thereby reducing mechanical pressure and damage to surrounding tissues. In addition, a hollow structure 43 is formed on the conductive contact 42 of the proximal electrode portion 4 of the flexible electrode 2. The hollow structure 43 can cause the conductive contact 42 to deform after being subjected to force, thereby enhancing the deformation ability of the electrode connection, so that the deformed conductive contact 42 can be in closer contact with the feedthrough 1, which is beneficial to improving the electrical connection reliability between the conductive contact 42 and the feedthrough 1, ensuring the conduction effect at the contact point, and the conductive contact 42 after being pressed is no longer in the same plane with the rest of the flexible electrode 2 due to deformation, which enables the conductive contact 42 to be stably confined in a position in contact with the feedthrough 1, which can ensure that the conductive contact 42 is difficult to displace, further improving the electrical connection reliability. In addition, after the deformed conductive contact 42 is in closer contact with the feedthrough 1, the contact gap between the conductive contact 42 and the feedthrough 1 can be reduced as much as possible, thereby facilitating the improvement of the sealing between the conductive contact 42 and the feedthrough 1, and ensuring that the implantable neural signal device can be implanted stably for a long time.

[0063] In some embodiments, Figures 3 to 7 As shown, the conductive contact 42 has an electrically connected contact middle portion 44 and a contact deforming portion 45 , and the contact deforming portion 45 is disposed around the outer circumference of the contact middle portion 44 .

[0064] In this way, the contact deformation portion 45 disposed outside the contact middle portion 44 can be used to deform and displace the contact middle portion 44 after being subjected to force, so as to achieve stable contact between the contact middle portion 44 and the feed-through 1, thereby improving the reliability of electrical connection.

[0065] The contact middle portion 44 may be located at the center of the conductive contact 42 , and there may be a plurality of contact deformation portions 45 , each of which is electrically connected to the contact middle portion 44 and the lead wire.

[0066] The contact deformation portions 45 may be arranged in a centrally symmetrical manner relative to the contact middle portion 44 .

[0067] The contact middle part 44 may have a conductive layer and an insulating layer stacked in layers, the conductive layer of the contact middle part 44 is in contact with the feed-through 1, and the insulating layer of the contact middle part 44 is arranged away from the feed-through 1 relative to the conductive layer. The insulating layer may be understood as a layer structure subjected to stress, and the external force acts on the insulating layer of the contact middle part 44, and then acts on the conductive layer of the contact middle part 44 through the insulating layer of the contact middle part 44, so that the conductive layer can be deformed and resist the feed-through 1. The external force applied to the insulating layer of the contact middle part 44 may be realized by the pressure connector 8 of the implantable neural signal device.

[0068] The contact deformation portion 45 and the electrode body 41 may also have conductive layers and insulating layers stacked together. The arrangements of the conductive layers and insulating layers of the contact deformation portion 45, the contact middle portion 44 and the electrode body 41 may be the same or different, and this application does not make any specific limitation on this.

[0069] The shape of the contact middle portion 44 after being deformed by force may be a spherical arc shape. Figure 4 , Figure 4 The state of the contact middle part 44 after being deformed by force is shown in FIG. The convex surface of the spherical arc-shaped contact middle part 44 can be understood as a side surface in contact with the feed-through 1, and the concave surface of the spherical arc-shaped contact middle part 44 can be understood as a force-bearing surface of the contact middle part 44. The contact middle part 44 is deformed after the concave surface is subjected to force. Specifically, the concave surface is a side surface in contact with the pressure connector 8.

[0070] The shape of the contact middle portion 44 can be one of the following: circular, elliptical and polygonal. Specifically, the shape of the contact middle portion 44 can be adapted to the shape of the feedthrough 1, so that the contact middle portion 44 and the feedthrough 1 have better fit when electrically connected, and the electrical connection is more stable.

[0071] In some embodiments, the hollow structure 43 is formed on the contact deformation portion 45; and / or, the hollow structure 43 is formed between the contact deformation portion 45 and the electrode body 41. In this way, the hollow structure 43 can be combined with the contact deformation portion 45 to make the structural design of the conductive contact 42 more compact and reasonable.

[0072] For example, Figure 3 and Figure 5 As shown, Figure 3 and Figure 5 The hollow structure 43 shown in FIG. 4 is formed between the contact deformation portion 45 and the electrode body 41; Figure 6 As shown, Figure 6 The hollow structure 43 shown in FIG. 4 can be understood as being formed on the contact deformation portion 45 .

[0073] In some embodiments, there are multiple hollow structures 43, and the multiple hollow structures 43 are arranged at intervals around the contact middle portion 44. In this way, the multiple hollow structures 43 can make the conductive contact 42 deform more uniformly after being stressed.

[0074] Specific combination Figure 6 , Figure 6 There are three hollow structures 43 shown in FIG. 4 , and the three hollow structures 43 are spaced and evenly arranged around the contact middle portion 44 .

[0075] In some embodiments, Figures 3 to 7 As shown, there are multiple contact deformation parts 45, and the multiple contact deformation parts 45 are respectively electrically connected to the contact middle part 44 and the lead connection part 5. In this way, the contact middle part 44 can be stably deformed by the contact deformation part 45, and the contact middle part 44 and the lead connection part 5 can be stably electrically connected through the contact deformation part 45.

[0076] The above-mentioned multiple contact deformation parts 45 can be distributed on both sides of the contact middle part 44 in an axially symmetrical manner, or can be distributed around the contact middle part 44 in a centrally symmetrical manner. The present application does not specifically limit the distribution method of the contact deformation parts 45.

[0077] In some embodiments, a plurality of contact deformation portions 45 are evenly arranged around the outer periphery of the contact middle portion 44. In this way, the contact middle portion 44 can be deformed more evenly after being subjected to force, thereby preventing the deflection problem caused by unbalanced force on the contact middle portion 44 after being subjected to force.

[0078] In some embodiments, Figure 3 and Figure 7 As shown, the contact deformation portion 45 includes a plurality of bending structures connected in sequence, a hollow structure 43 is formed between the plurality of bending structures and the electrode body 41, and the plurality of bending structures are configured to be stretched and deformed along the direction of force after being subjected to force.

[0079] The shape of the bending structure can be one of the following: S-shape and M-shape. Of course, the bending structure can also be an irregular bending shape, as long as the bending structure can be electrically connected to the contact middle portion 44 and the lead connection portion 5 respectively.

[0080] like Figure 3As shown, the above-mentioned bending structure can be located on opposite sides of the contact middle part 44, so that the contact middle part 44 can apply tension to the bending structures on both sides after being subjected to force, and achieve uniform deformation through the deformation of the bending structures on both sides to ensure stable abutment against the feed-through 1.

[0081] The bending structure may stretch after being subjected to force based on the design of size and shape, or may stretch after being subjected to force based on the design of material. For example, the bending structure may be partially or completely made of elastic material.

[0082] In some embodiments, Figure 3 and Figure 7 As shown, the bending directions of adjacent bending structures are opposite to each other.

[0083] In some embodiments, Figure 5 As shown, the contact deformation portion 45 includes a spiral structure connected to the contact middle portion 44, which spirals outwards around the contact middle portion 44 in sequence and is electrically connected to the lead connection portion 5. In this way, the spiral structure can make the contact middle portion 44 more evenly stressed, so as to stably deform and abut against the feed-through 1.

[0084] like Figure 5 As shown, the spiral structure can extend outwardly along the outer circumference of the contact middle portion 44 until it forms an electrical connection with the lead connecting portion 5 .

[0085] The spiral structure may include spiral segments connected to opposite sides of the contact middle portion 44 to further increase the force uniformity of the contact middle portion 44 .

[0086] In some embodiments, Figure 6 As shown, the hollow structure 43 is formed on the contact deformation portion 45, and the hollow structure 43 has a plurality of folded line portions forming a closed cavity, and the plurality of folded line portions are arranged around the contact middle portion 44. The design of the hollow structure 43 can make the contact middle portion 44 more uniformly stressed, so as to stably deform and abut against the feed-through 1.

[0087] The fold line portion may extend outward in a fold line shape along the outer peripheral side of the contact middle portion 44 .

[0088] The closed cavity formed by the above-mentioned fold line portion may have multiple acute-angle structures, such as a V-shaped acute-angle structure. The shapes of the multiple fold line portions may be the same, and the multiple fold line portions may be evenly arranged around the contact middle portion 44 to further increase the uniformity of force on the contact middle portion 44.

[0089] In some embodiments, Figure 7 As shown, a plurality of through holes 46 are formed on the contact middle portion 44 , and the plurality of through holes 46 are used to provide deformation space for the contact middle portion 44 , so as to facilitate the contact middle portion 44 to deform and abut against the feed-through 1 after being subjected to force.

[0090] The through holes 46 on the contact middle portion 44 may be arranged in an array.

[0091] When the through holes 46 are arranged in an array, it is beneficial for gas to be discharged after the contact middle portion 44 is deformed, thereby avoiding wrinkles in the contact middle portion 44 and making the conductive contact 42 fit more closely to the feed-through 1, thereby improving the stability of the electrical connection.

[0092] In some embodiments, the deformation range of the conductive contact 42 in the thickness direction of the proximal electrode portion 4 is not less than 10 microns. The above deformation range can cause the conductive contact 42 to produce a large deformation, which can not only make the conductive contact 42 adapt to the contact surface for electrical connection with the feed-through 1, but also cooperate with the pressure connector 8 of the implantable neural signal device, thereby achieving a better positioning effect.

[0093] In some embodiments, Figures 3 to 6 As shown, there are multiple conductive contacts 42 , and the multiple conductive contacts 42 are arranged linearly or in an array along the length direction of the proximal electrode portion 4 .

[0094] The arrangement of the conductive contacts 42 described above fully utilizes the space of the proximal electrode portion 4, ensuring that the conductive contacts 42 and the feed-through 1 have a larger contact area, thereby ensuring electrical connection reliability.

[0095] The above-mentioned conductive contact 42 can be connected to one feedthrough 1, or can be connected to multiple feedthroughs 1 in a one-to-one correspondence. The present application does not make any specific limitation on this, and it is sufficient to achieve a stable electrical connection between the conductive contact 42 and the feedthrough 1.

[0096] In some embodiments, the thickness of the flexible electrode 2 is not greater than 200 microns. In this way, a relatively thin flexible electrode 2 can produce a relatively large flexible deformation to better adapt to the shape and movement of the neural tissue, and the relatively thin flexible electrode 2 can better fit the feedthrough 1, thereby avoiding an excessively large gap, and effectively ensuring the installation sealing of the flexible electrode 2.

[0097] In some embodiments, the flexible electrode 2 includes a first insulating layer, a first conductive layer, and a second insulating layer stacked in the thickness direction, the conductive contacts 42, the electrode sites 31, and the leads are all arranged in the first conductive layer, and the conductive contacts 42 and the electrode sites 31 are exposed to the first insulating layer and / or the second insulating layer.

[0098] The first insulating layer may be made of one or more of the following materials: polyimide, parylene and high molecular fluoride.

[0099] The second insulating layer may be made of one or more of the following materials: polyimide, parylene, fluororesin and fluororubber.

[0100] The first conductive layer may be made of one or more of the following materials: gold, platinum, titanium, chromium and iridium, which have good conductive effects and good anti-corrosion effects.

[0101] In some embodiments, the flexible electrode 2 further includes a second conductive layer and a third insulating layer, the second conductive layer is disposed on a side of the second insulating layer facing away from the first conductive layer, and the third insulating layer is disposed on a side of the second conductive layer facing away from the second insulating layer.

[0102] The second conductive layer can be made of one or more of the following materials: gold, platinum, titanium, chromium and iridium, which have good conductivity and good corrosion resistance. Specifically, the second conductive layer can be made of the same or different material as the first conductive layer, and this application does not make specific restrictions on this.

[0103] The third insulating layer may be made of the same or different material as the first insulating layer and / or the second insulating layer, and this application does not impose any specific limitation on this.

[0104] The present application also provides an implantable neural signal device. Figure 1 and Figure 2 As shown, the implantable neural signal device includes the above-mentioned flexible electrode for the implantable neural signal device, and also includes an action component 6, the action component 6 includes a first shell 61, an action module and a feedthrough 1, the action module is arranged in the first shell 61, the feedthrough 1 is arranged on the first shell 61, and the flexible electrode 2 is electrically connected to the action module through the feedthrough 1; wherein the action module includes a stimulation module and / or a collection module. A circuit board 62 electrically connected to the stimulation module and / or the collection module may also be arranged in the above-mentioned first shell 61.

[0105] The first shell 61 can be made of metal material. The metal material used in the first shell 61 can be titanium alloy, or other metal materials, such as stainless steel, aluminum alloy, etc., which have excellent strength, rigidity and biocompatibility. The present application does not specifically limit the metal material used in the first shell 61, as long as it can be implanted in a living body.

[0106] The implantable neural signal device using the above-mentioned flexible electrode 2 can better adapt to the shape and movement of neural tissue by using the flexible electrode 2, thereby reducing mechanical pressure and damage to surrounding tissues. In addition, a hollow structure 43 is formed on the conductive contact 42 of the proximal electrode portion 4 of the flexible electrode 2. The hollow structure 43 can cause the conductive contact 42 to deform after being subjected to force, thereby enhancing the deformation ability of the electrode connection, so that the deformed conductive contact 42 can be in closer contact with the feedthrough 1, which is beneficial to improving the electrical connection reliability between the conductive contact 42 and the feedthrough 1, ensuring the conduction effect at the contact point, and the conductive contact 42 after being pressed is no longer in the same plane with the rest of the flexible electrode 2 due to deformation, which enables the conductive contact 42 to be stably confined in a position in contact with the feedthrough 1, which can ensure that the conductive contact 42 is difficult to displace, further improving the electrical connection reliability. In addition, after the deformed conductive contact 42 is in closer contact with the feedthrough 1, the contact gap between the conductive contact 42 and the feedthrough 1 can be reduced as much as possible, thereby facilitating the improvement of the sealing between the conductive contact 42 and the feedthrough 1, and ensuring that the implantable neural signal device can be implanted stably for a long time.

[0107] In some embodiments, Figure 1 and Figure 8 As shown, the action component 6 also includes an electrode cover 7, which covers the proximal electrode portion 4 of the flexible electrode 2. A pressure connector 8 is provided on the side of the electrode cover 7 facing the flexible electrode 2. The pressure connector 8 is used to apply a force to the conductive contact 42 of the proximal electrode portion 4 to make it press against the feed-through 1.

[0108] In this way, a stable force can be applied to the conductive contact 42 through the above-mentioned pressure connector 8, so that the conductive contact 42 can stably abut against the feedthrough 1, effectively improving the conduction effect at the contact point between the conductive contact 42 and the feedthrough 1, thereby ensuring that the flexible electrode 2 can be stably electrically connected to the action module through the feedthrough 1.

[0109] The pressure connector 8 and the feedthrough 1 can be respectively arranged on opposite sides of the flexible electrode 2 , specifically on both sides in the thickness direction of the flexible electrode 2 , so that the conductive contacts 42 of the flexible electrode 2 can be deformed and pressed against the feedthrough 1 under the action of the pressure connector 8 .

[0110] In the case where the action module includes a stimulation module, since a simulator will be first used to electrically connect the flexible electrode 2 for a simulation operation, and after the simulation operation confirms various parameters, an implantable neural signal device will be used to perform a formal implantation operation. Therefore, the flexible electrode 2 and the action component 6 will be installed before the formal implantation operation. By using the above-mentioned pressure connector 8, when the flexible electrode 2 is installed on the action component 6, a force can be applied to the conductive contact 42 of the flexible electrode 2 to make it press against the feedthrough 1, so that the conductive contact 42 can be deformed by the force, thereby ensuring that the conductive contact 42 can achieve a stable electrical connection relationship with the action module through the feedthrough 1.

[0111] In some embodiments, the pressure connector 8 can be used to apply an elastic force to the conductive contact 42, so that the conductive contact 42 can stably press against the feedthrough 1. In some other embodiments, the pressure connector 8 can move under the control of a control signal to act on the conductive contact 42, so as to apply a force to the conductive contact 42 to press against the feedthrough 1, such as the pressure connector 8 includes a retractable structure, which can perform a retractable movement to act on the conductive contact 42 after receiving the control signal.

[0112] The electrode cover 7 can be mounted on the distal side of the first shell 61. Specifically, the electrode cover 7 can be connected to the first shell 61 in a detachable connection manner, such as the electrode cover 7 is connected to the first shell 61 in a pivot connection manner, or the electrode cover 7 is provided with a mounting hole, and a mounting screw can be installed in the mounting hole to achieve disassembly and assembly with the first shell 61. In some other embodiments, the electrode cover 7 can be connected to the first shell 61 in a sliding connection manner, and the present application does not specifically limit the connection method between the electrode cover 7 and the first shell 61.

[0113] The electrode cover 7 can be made of one or more of the following materials: polyetheretherketone, epoxy resin.

[0114] In some embodiments, Figure 1 As shown, the feed-through 1 includes an insulating carrier 11 and a feed-through conductor 12. The insulating carrier 11 is disposed on one side of the first housing 61. The feed-through conductor 12 passes through the insulating carrier 11, and the two ends of the feed-through conductor 12 are electrically connected to the conductive contact 42 and the action module, respectively. In this way, the electrical connection between the conductive contact 42 and the action module can be achieved through the feed-through conductor 12.

[0115] The feed-through conductor 12 may pass through the insulating carrier 11, and the insulating carrier 11 may be in surface-to-surface contact with the proximal electrode portion 4 of the flexible electrode 2, so as to provide support for the flexible electrode 2 through the insulating carrier 11. One or both ends of the feed-through conductor 12 may protrude from the surface of the insulating carrier 11, so that the feed-through conductor 12 may be more easily in contact with the conductive contact 42, thereby improving the stability of the electrical connection.

[0116] The shape of the insulating carrier 11 may be adapted to the shape of the proximal electrode portion 4, so that the proximal electrode portion 4 can be better supported by the insulating carrier 11. Exemplarily, the shape of the insulating carrier 11 may be one of the following: circular, elliptical, and polygonal.

[0117] The insulating carrier 11 may be made of insulating material, such as ceramic.

[0118] The feed-through conductor 12 may be made of metal material, such as at least one of gold, platinum and iridium.

[0119] In some embodiments, Figure 1 As shown, there are a plurality of feed-through conductors 12 , and the plurality of feed-through conductors 12 are arranged in an array on the insulating carrier 11 .

[0120] There are also a plurality of the conductive contacts 42 , which are arranged one-to-one with the feed-through conductors 12 to form a larger current conduction area, thereby ensuring the reliability of the electrical connection between the feed-through 1 and the conductive contacts 42 .

[0121] In some embodiments, Figure 1 and Figure 8 As shown, the pressure connector 8 includes at least one elastic member 81, which is arranged one by one with the conductive contact 42, and the elastic member 81 is used to apply a force to the conductive contact 42 of the flexible electrode 2 so that the conductive contact 42 is pressed against the feed-through member 1 to form an electrical connection.

[0122] In this way, the elastic member 81 can apply a stable elastic force to the conductive contact 42, so that the conductive contact 42 can stably abut against the feedthrough 1, effectively improving the conduction effect at the contact point between the conductive contact 42 and the feedthrough 1. In addition, the elastic member 81 has a simple structural design, which can reduce the manufacturing cost of the implantable neural signal device while applying a stable force to the conductive contact 42.

[0123] The elastic member 81 may be deformed based on the structural design to exert a force on the conductive contact 42, such as a spring, a spring, etc. The elastic member 81 may also be deformed based on the material design to exert a force on the conductive contact 42, such as silicone, rubber, etc.

[0124] The above-mentioned elastic member 81 can be multiple, and the multiple elastic members 81 are arranged along the length direction of the flexible electrode 2 and are arranged one by one with the conductive contacts 42, so as to apply elastic force to each conductive contact 42 respectively, so that the conductive contact 42 can be deformed along the thickness direction of the flexible electrode 2, so that each conductive contact 42 can form an electrical connection with the feed-through member 1, thereby achieving a better electrical connection effect.

[0125] In some embodiments, Figure 1 As shown, the outer edge of the electrode cover 7 and the outer edge of the first shell 61 are mounted on each other, and a first sealing gasket 9 is provided between the outer edge of the electrode cover 7 and the outer edge of the first shell 61. The first sealing gasket 9 can prevent body fluid from flowing into the first shell 61 through the gap between the first shell 61 and the electrode cover 7 after the implantable neural signal device is implanted into the target tissue, thereby improving the sealing performance and safety of the implantable neural signal device.

[0126] In some embodiments, Figure 1 and Figure 8 As shown, the pressure connector 8 also includes a seat body 82 and a second sealing gasket 83. The seat body 82 is connected to the distal side of the electrode cover 7, and a mounting hole is provided on the seat body 82. The elastic member 81 is provided in the mounting hole. The second sealing gasket is provided on the seat body 82 and surrounds the outer peripheral side of the elastic member 81, and the second sealing gasket is located on the inner peripheral side of the first sealing gasket 9.

[0127] In this way, the installation sealing between the pressure connector 8, the flexible electrode 2 and the feed-through 1 can be ensured by the second sealing gasket.

[0128] The second sealing pad can surround the outer edge of the pressure connector 8 and be located on the outer peripheral side of the conductive contact 42, thereby achieving a better sealing effect and further preventing body fluids from contacting the conductive contact 42 of the flexible electrode 2 after the implantable neural signal device is implanted into the target tissue.

[0129] The embodiment of the present application also provides a method for preparing a flexible electrode 2, which is used to prepare the above-mentioned flexible electrode for an implantable neural signal device, wherein the flexible electrode 2 includes a first insulating layer, a first conductive layer, and a second insulating layer stacked in a thickness direction, wherein the conductive contact 42, the electrode site 31, and the lead are all arranged in the first conductive layer, and the conductive contact 42 and the electrode site 31 are exposed to the first insulating layer and / or the second insulating layer. Fig. 9 As shown, the method for preparing the flexible electrode 2 includes steps S101 to S106.

[0130] Step S101: spin coating and baking the insulating paste to form a first insulating layer.

[0131] Step S102: removing the portion of the first insulating layer corresponding to the electrode site 31 to expose the electrode site 31 through the first insulating layer.

[0132] Step S103: forming a first conductive layer on the first insulating layer by photolithography and coating.

[0133] Step S104: spin coating and baking an insulating paste on a side of the first conductive layer facing away from the first insulating layer to form a second insulating layer.

[0134] Step S105: removing portions of the second insulating layer corresponding to the electrode sites 31 and the conductive contacts 42 to expose the electrode sites 31 and the conductive contacts 42 through the second insulating layer.

[0135] Step S106: removing the portions of the first insulating layer and the second insulating layer corresponding to the hollow structure 43 .

[0136] The above-mentioned method for preparing the flexible electrode 2 can prepare a flexible electrode 2 having the advantages of easy positioning, good sealing effect, and high electrical connection stability.

[0137] After obtaining the second insulating layer in step S104, step S105 and step S106 can be performed simultaneously, that is, the first insulating layer, the first conductive layer and the second insulating layer are etched synchronously to simultaneously remove the patterns corresponding to the electrode sites 31 of the second insulating layer and the conductive contacts 42 and the hollow structures 43 on the conductive contacts 42, so as to reduce the operation steps for preparing the flexible electrode 2.

[0138] The above-mentioned coating can be understood as physical vapor deposition coating or electroplating. Specifically, the coating method can be selected according to the materials of the first insulating layer, the first conductive layer and the second insulating layer.

[0139] In addition, although exemplary embodiments have been described herein, the scope includes any and all embodiments based on the present application with equivalent elements, modifications, omissions, combinations (e.g., schemes that cross various embodiments), adaptations or changes. The elements in the claims will be interpreted broadly based on the language used in the claims, and are not limited to the examples described in this specification or during the practice of the present application, and the examples will be interpreted as non-exclusive.

[0140] The above description is intended to be illustrative rather than restrictive. For example, the above examples (or one or more schemes thereof) may be used in combination with each other. For example, a person of ordinary skill in the art may use other embodiments when reading the above description. In addition, in the above-mentioned specific embodiments, various features may be grouped together to simplify the present application. This should not be interpreted as an intention that a disclosed feature that is not required to be protected is necessary for any claim. On the contrary, the subject matter of the present application may be less than all the features of a particular disclosed embodiment. Thus, the claims are incorporated herein as examples or embodiments in the specific embodiments, wherein each claim is independently a separate embodiment, and it is considered that these embodiments may be combined with each other in various combinations or arrangements. The scope of the present application should be determined with reference to the attached claims and the full scope of equivalent forms granted by these claims.

[0141] The above embodiments are only exemplary embodiments of the present application and are not intended to limit the present application. The protection scope of the present application is defined by the claims. Those skilled in the art may make various modifications or equivalent substitutions to the present application within the essence and protection scope of the present application, and such modifications or equivalent substitutions shall also be deemed to fall within the protection scope of the present application.

Claims

1. A flexible electrode for an implantable neural signal device, characterized in that: The implantable neural signal device comprises a feedthrough, the flexible electrode is electrically connected to the feedthrough, and the flexible electrode comprises: A distal electrode portion, comprising at least one electrode site, wherein the electrode site is used to apply electrical stimulation to a target tissue and / or collect a potential signal of the target tissue; A proximal electrode portion, comprising an electrode body and at least one conductive contact disposed on the electrode body, wherein the conductive contact is formed with a hollow structure, and the hollow structure is configured to deform the conductive contact when a force is applied to the conductive contact, so that the deformed conductive contact abuts against the feed-through to form an electrical connection; The lead connection part includes a lead, wherein both ends of the lead are electrically connected to the conductive contact of the proximal electrode part and the electrode site of the distal electrode part respectively, and the distal electrode part, the proximal electrode part and the lead connection part are arranged in sequence along the length direction of the flexible electrode.

2. The flexible electrode for an implantable neural signal device according to claim 1, characterized in that: The conductive contact has an electrically connected contact middle portion and a contact deformation portion, wherein the contact deformation portion is arranged around the outer periphery of the contact middle portion.

3. The flexible electrode for an implantable neural signal device according to claim 2, characterized in that: The hollow structure is formed on the contact deformation portion; and / or, The hollow structure is formed between the contact deformation portion and the electrode body.

4. The flexible electrode for an implantable neural signal device according to claim 3, characterized in that: There are multiple hollow structures, and the multiple hollow structures are arranged at intervals around the middle of the contact.

5. The flexible electrode for an implantable neural signal device according to claim 2 or 3, characterized in that: There are a plurality of contact deformation parts, and the plurality of contact deformation parts are electrically connected to the contact middle part and the lead connection part respectively.

6. The flexible electrode for an implantable neural signal device according to claim 5, characterized in that: A plurality of contact deformation portions are evenly arranged around the periphery of the middle portion of the contact.

7. The flexible electrode for an implantable neural signal device according to claim 3, characterized in that: The contact deformation portion includes a plurality of bending structures connected in sequence, the hollow structure is formed between the plurality of bending structures and the electrode body, and the plurality of bending structures are configured to be stretched and deformed along the direction of force after being subjected to force.

8. The flexible electrode for an implantable neural signal device according to claim 7, characterized in that: The bending directions of the adjacent bending structures are opposite to each other.

9. The flexible electrode for an implantable neural signal device according to claim 2, characterized in that: The contact deformation portion includes a spiral structure connected to the middle portion of the contact, the spiral structure spirals outwards around the middle portion of the contact in sequence, and is electrically connected to the lead connection portion.

10. The flexible electrode for an implantable neural signal device according to claim 3, characterized in that: The hollow structure is formed on the contact deformation portion, and the hollow structure has a plurality of fold line portions forming a closed cavity, and the plurality of fold line portions are arranged around the middle portion of the contact.

11. The flexible electrode for an implantable neural signal device according to claim 2, characterized in that: A plurality of through holes are formed on the middle portion of the contact, and the plurality of through holes are used to provide a deformation space for the middle portion of the contact.

12. The flexible electrode for an implantable neural signal device according to claim 1, characterized in that: The deformation range of the conductive contact in the thickness direction of the proximal electrode portion is not less than 10 microns.

13. The flexible electrode for an implantable neural signal device according to claim 1, characterized in that: There are multiple conductive contacts, and the multiple conductive contacts are arranged linearly or in an array along the length direction of the proximal electrode portion.

14. The flexible electrode for an implantable neural signal device according to claim 1, characterized in that: The thickness of the flexible electrode is no more than 200 microns.

15. The flexible electrode for an implantable neural signal device according to claim 1, characterized in that: The flexible electrode includes a first insulating layer, a first conductive layer, and a second insulating layer stacked in a thickness direction, the conductive contacts, electrode sites, and leads are all arranged in the first conductive layer, and the conductive contacts and electrode sites are exposed to the first insulating layer and / or the second insulating layer.

16. The flexible electrode for an implantable neural signal device according to claim 15, characterized in that: The flexible electrode further includes a second conductive layer and a third insulating layer. The second conductive layer is disposed on a side of the second insulating layer facing away from the first conductive layer. The third insulating layer is disposed on a side of the second conductive layer facing away from the second insulating layer.

17. An implantable neural signal device, characterized in that: It comprises a flexible electrode for an implantable neural signal device as described in any one of claims 1 to 16, and also comprises an action component, the action component comprises a first shell, an action module and a feed-through, the action module is arranged in the first shell, the feed-through is arranged on the first shell, and the flexible electrode is electrically connected to the action module through the feed-through; wherein the action module comprises a stimulation module and / or an acquisition module.

18. The implantable neural signal device according to claim 17, characterized in that: The action component also includes an electrode cover, which covers the proximal electrode part of the flexible electrode. A pressure connector is provided on the side of the electrode cover facing the flexible electrode, and the pressure connector is used to apply a force to the conductive contact of the proximal electrode part to make it press against the feedthrough.

19. The implantable neural signal device according to claim 17, characterized in that: The feed-through component includes an insulating carrier and a feed-through conductor. The insulating carrier is disposed on one side of the first shell. The feed-through conductor passes through the insulating carrier, and two ends of the feed-through conductor are electrically connected to the conductive contact and the action module respectively.

20. The implantable neural signal device according to claim 19, characterized in that: There are a plurality of feed-through conductors, and a plurality of the feed-through conductor arrays are arranged on the insulating carrier.

21. The implantable neural signal device according to claim 18, characterized in that: The pressure connector includes at least one elastic member, which is arranged in one-to-one correspondence with the conductive contacts, and the elastic member is used to apply a force to the conductive contacts of the flexible electrode so that the conductive contacts are pressed against the feed-through member to form an electrical connection.

22. The implantable neural signal device according to claim 21, characterized in that: The outer edge of the electrode cover and the outer edge of the first shell are mounted on each other, and a first sealing gasket is arranged between the outer edge of the electrode cover and the outer edge of the first shell.

23. The implantable neural signal device according to claim 22, characterized in that: The pressure connector also includes a seat body and a second sealing gasket. The seat body is connected to the distal side of the electrode cover, and a mounting hole is provided on the seat body. The elastic member is arranged in the mounting hole. The second sealing gasket is arranged on the seat body and surrounds the outer peripheral side of the elastic member, and the second sealing gasket is located on the inner peripheral side of the first sealing gasket.

24. A method for preparing a flexible electrode, characterized in that: Used to prepare a flexible electrode for an implantable neural signal device according to any one of claims 1 to 16, the flexible electrode comprising a first insulating layer, a first conductive layer, and a second insulating layer stacked in a thickness direction, the conductive contacts, electrode sites, and leads are all arranged in the first conductive layer, and the conductive contacts and electrode sites are exposed to the first insulating layer and / or the second insulating layer, the method for preparing the flexible electrode comprising: Spin coating and baking the insulating slurry to form a first insulating layer; removing a portion of the first insulating layer corresponding to the electrode site to expose the electrode site through the first insulating layer; forming a first conductive layer on the first insulating layer by photolithography and coating; Spin coating and baking an insulating paste on a side of the first conductive layer facing away from the first insulating layer to form a second insulating layer; removing portions of the second insulating layer corresponding to the electrode sites and the conductive contacts to expose the electrode sites and the conductive contacts through the second insulating layer; Portions of the first insulating layer and the second insulating layer corresponding to the hollow structure are removed.

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