WO2021003670A1 - 一种微电极及其制备方法和神经假体 - Google Patents

一种微电极及其制备方法和神经假体 Download PDF

Info

Publication number
WO2021003670A1
WO2021003670A1 PCT/CN2019/095263 CN2019095263W WO2021003670A1 WO 2021003670 A1 WO2021003670 A1 WO 2021003670A1 CN 2019095263 W CN2019095263 W CN 2019095263W WO 2021003670 A1 WO2021003670 A1 WO 2021003670A1
Authority
WO
WIPO (PCT)
Prior art keywords
microelectrode
platinum
dendritic
layer
grooves
Prior art date
Application number
PCT/CN2019/095263
Other languages
English (en)
French (fr)
Inventor
曾齐
吴天准
Original Assignee
深圳先进技术研究院
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 深圳先进技术研究院 filed Critical 深圳先进技术研究院
Priority to PCT/CN2019/095263 priority Critical patent/WO2021003670A1/zh
Priority to US17/251,002 priority patent/US20210260368A1/en
Publication of WO2021003670A1 publication Critical patent/WO2021003670A1/zh

Links

Images

Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
    • H01B1/00—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors
    • H01B1/02—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors mainly consisting of metals or alloys
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/0551—Spinal or peripheral nerve electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system

Definitions

  • the invention relates to the field of biomedical engineering, in particular to a microelectrode, a preparation method thereof and a neural prosthesis.
  • nerve electrodes are used to stimulate nerve tissue or record nerve electrical signals, and are widely used in life sciences such as neurophysiology and brain science research.
  • life sciences such as neurophysiology and brain science research.
  • the clinical requirements for the accuracy of stimulation or recording become higher and higher, the low-density, simple function of nerve electrodes can no longer meet the needs of precise control.
  • Nerve electrodes are developing in the direction of integration and miniaturization. Therefore, the reduction of the size of microelectrodes causes performance problems such as increased electrode impedance and reduced capacitance, which limit its clinical application.
  • multi-focus electrodes are designed to balance the number of electrodes and electrode spacing, breaking through the bottleneck of its spatial resolution; and, under the condition of the same electrode geometry, improve its practicality through good surface modification Area to reduce the critical stimulus charge density; at the same time, increase the number of patients' perception and produce higher resolution, which is the development direction of nerve electrodes.
  • the present invention provides a microelectrode, including a flexible layer, a conductive layer and a plurality of dendritic platinum structures.
  • the conductive layer is arranged in the flexible layer, and a plurality of grooves are arranged on the surface of the flexible layer to expose part of the conductive layer.
  • each groove is provided with a dendritic platinum structure, where multiple grooves become multiple focal electrodes, the electrode sites are small, the recording points are more, and the distribution is uniform; the modified dendritic platinum structure increases the surface area of the microelectrode, Electrical performance, biocompatibility and service life; at the same time, the use of current guidance technology to create virtual electrodes, increase the number of microelectrodes receiving stimuli during use, and improve its resolution in applications.
  • the present invention provides a microelectrode comprising a flexible layer, a conductive layer and a dendrite platinum structure.
  • the conductive layer is provided in the flexible layer, and a plurality of grooves are provided on the surface of the flexible layer to expose For part of the conductive layer, each of the grooves is provided with a dendritic platinum structure.
  • the thickness of the flexible layer is 3 ⁇ m-300 ⁇ m. Further, the thickness of the flexible layer is 10 m-260 m.
  • the material of the flexible layer can be, but is not limited to, polyimide or parylene.
  • the thickness of the conductive layer is 0.1 ⁇ m-100 ⁇ m. Further, the thickness of the conductive layer is 0.5 ⁇ m-80 ⁇ m.
  • the distance between adjacent grooves is 10 ⁇ m-1000 ⁇ m. Further, the distance between adjacent grooves is 50 ⁇ m-700 ⁇ m. Furthermore, the distance between adjacent grooves is 80 ⁇ m-500 ⁇ m.
  • the setting of the distance between adjacent grooves is beneficial to the generation of virtual electrode channels, thereby increasing the number of perceptions of the microelectrode during use and promoting resolution.
  • a plurality of the grooves are arranged in an array.
  • the array arrangement of the grooves is beneficial to the array arrangement of the dendritic platinum structure arranged in the grooves, thereby increasing the number of virtual channels generated by the microelectrode and increasing the number of stimuli.
  • the opening shape of the groove may be, but not limited to, a circle, a square, a rectangle, an ellipse, a diamond or an irregular shape.
  • the depth of the groove is 0.5 ⁇ m-80 ⁇ m. Further, the depth of the groove is 2 ⁇ m-70 ⁇ m.
  • the distribution density of the grooves in the microelectrode is 10-300 grooves/cm 2 . Further, the distribution density of the grooves in the microelectrode is 50-200 grooves/cm 2 .
  • the dendritic platinum structure is formed of multiple dendritic platinum.
  • the dendritic platinum includes at least one of platinum nanowires, platinum nanorods, platinum nanocones, and platinum nanoflowers.
  • the dendritic platinum structure can greatly increase the surface area of the microelectrode, thereby increasing its electrical performance.
  • the platinum nanowires have a diameter of 2nm-50nm and a length of 0.2 ⁇ m-5 ⁇ m. Further, the platinum nanowires have a diameter of 3nm-9nm and a length of 1.2 ⁇ m-4 ⁇ m.
  • the platinum nanorods have a diameter of 0.1 ⁇ m-1 ⁇ m and a length of 0.3 ⁇ m-5 ⁇ m. Further, the platinum nanorods have a diameter of 0.15 ⁇ m to 0.85 ⁇ m and a length of 0.8 ⁇ m to 4 ⁇ m.
  • the bottom diameter of the platinum nanocone is 0.1 ⁇ m-1 ⁇ m, and the height is 0.3 ⁇ m-5 ⁇ m. Further, the diameter of the bottom of the platinum nanocone is 0.2 ⁇ m-0.95 ⁇ m, and the length is 1.5 ⁇ m-3.5 ⁇ m.
  • the average diameter of the platinum nanoflowers is 0.2 ⁇ m-3 ⁇ m. Further, the average diameter of the platinum nanoflowers is 0.5 ⁇ m-2.6 ⁇ m. Further, each of the platinum nanoflowers includes a plurality of platinum nanosheets, and the lateral dimension of the platinum nanosheets is 0.1 ⁇ m-1 ⁇ m. Furthermore, the lateral size of the platinum nanosheets is 0.15 m-0.8 m.
  • the arrangement of the platinum nanowires, platinum nanorods, and platinum nanocones is beneficial to further increase the surface area of the microelectrode and improve its electrical performance.
  • the distribution density of the dendritic platinum in the dendritic platinum structure is 10 pcs/ ⁇ m 2 -300 pcs/ ⁇ m 2 . Further, the distribution density of the dendritic platinum in the dendritic platinum structure is 25 pcs/ ⁇ m 2 -265 pcs/ ⁇ m 2 . Furthermore, the distribution density of the dendritic platinum in the dendritic platinum structure is 50 pcs/ ⁇ m 2 -180 pcs/ ⁇ m 2 . In the present invention, the denser the distribution of dendritic platinum, the larger the surface area of the microelectrode, and the more improved the electrical performance, which is more conducive to its application.
  • the thickness of the dendritic platinum structure is 0.3 ⁇ m-70 ⁇ m. Further, the thickness of the dendritic platinum structure is 3 ⁇ m-60 ⁇ m. Furthermore, the thickness of the dendritic platinum structure is 5 ⁇ m-50 ⁇ m. In the present invention, the setting of the thickness of the dendritic platinum structure is beneficial to the generation and transmission of stimuli.
  • the thickness of the dendritic platinum structure may be equal to the depth of the groove, may be smaller than the depth of the groove, or may be greater than the depth of the groove.
  • the thickness of the dendritic platinum structure is greater than the depth of the groove, the surface area of the microelectrode is further increased, thereby improving its electrical performance.
  • a plurality of the dendritic platinum structures are arranged in an array, so that an array of dendritic platinum structures is formed on the microelectrode, that is, a microelectrode array is formed, which further improves the overall electrical performance of the microelectrode and the number of stimuli received during use , Which increases the number of virtual channels and improves their resolution in applications.
  • the dendritic platinum structure may completely cover the bottom surface of the groove (that is, the surface of the conductive layer exposed in each groove), or partially cover the bottom surface of the groove.
  • a conductive polymer layer is further provided on the dendritic platinum structure.
  • the conductive polymer layer has good electrical properties and is a soft material with excellent biocompatibility. It fits the tissues, reduces the immune response, and improves the long-term safety of the microelectrode. Therefore, a conductive polymer layer is provided on the dendritic platinum structure to "combine hard and soft" to further improve the biocompatibility and service life of the microelectrode.
  • all of the multiple dendritic platinum structures may be provided with a conductive polymer layer, or may be partially provided with a conductive polymer layer, which is not limited. Further, a conductive polymer layer is provided on a plurality of the dendritic platinum structures, which further improves the biocompatibility and stability of the microelectrode.
  • the thickness of the conductive polymer layer is 0.1 ⁇ m-20 ⁇ m. Further, the thickness of the conductive polymer layer is 2 ⁇ m-16 ⁇ m. In the present invention, the setting of the thickness of the conductive polymer layer is more conducive to the transmission of stimulation of the conductive layer and the dendritic platinum structure.
  • the material of the conductive polymer layer includes at least one of polypyrrole, polyaniline, polythiophene and its derivatives, and conductive hydrogel. That is, the material of the conductive polymer layer includes at least one of polypyrrole, polyaniline, polythiophene, polypyrrole derivative, polyaniline derivative, polythiophene derivative, and conductive hydrogel.
  • the selection of the material of the conductive polymer layer is more conducive to the biocompatibility of the conductive polymer layer, thereby improving the biocompatibility and safety of the microelectrode.
  • the exposed conductive layer and the dendritic platinum structure become multiple electrodes, the electrode sites are small, and in a certain space, the number of electrodes increases, the recording points increase, and the distribution is even, which is very effective for nerves.
  • the stimulus is more concentrated, which overcomes the disadvantage that the fringe electric field of the ordinary planar electrode is significantly stronger than the center, which causes the electric field lines to diverge.
  • the dendritic platinum structure increases the surface area of the microelectrode and effectively improves the electrochemical performance of the microelectrode, such as reducing impedance, lowering the critical stimulating charge density, improving charge storage and charge injection capabilities, etc., and the dendritic platinum structure is combined with the conductive layer The effect is good, the shedding of the dendritic platinum structure is avoided, and the biocompatibility and service life of the microelectrode are improved.
  • the electric fields of adjacent electrodes interact in time and space to generate additional perceptible virtual stimuli between the stimuli produced by the two electrodes separately, that is, create virtual electrode channels and increase the microelectrode
  • the number of stimuli received during use increases its resolution in applications, thereby broadening the application range of microelectrodes.
  • the present invention provides a method for preparing a microelectrode, including:
  • the substrate is removed, and the dendritic platinum structure is deposited in the plurality of grooves to obtain a microelectrode.
  • the substrate may be, but not limited to, a silicon wafer, a silicon oxide wafer or a glass wafer.
  • the preparing the first flexible layer on the substrate includes preparing the first flexible layer on the substrate by spin coating or deposition.
  • the preparing a conductive layer on the first flexible layer through a mask includes disposing a mask on the first flexible layer, and forming the conductive layer on the first flexible layer by deposition,
  • the conductive layer covers part of the first flexible layer.
  • the deposition may be, but is not limited to, physical vapor deposition or chemical vapor deposition.
  • the material of the first flexible layer and the second flexible layer may be, but not limited to, polyimide or parylene.
  • the etching includes at least one of dry etching and wet etching.
  • the etching may be, but not limited to, reactive ion etching or plasma etching.
  • the depositing a dendritic platinum structure in the plurality of grooves includes: providing a platinum salt solution, and forming the dendrites in the plurality of grooves using a constant potential deposition method or a constant current deposition method Platinum structure.
  • the platinum salt includes platinum chloride, ammonium hexachloroplatinate, potassium hexachloroplatinate, sodium hexachloroplatinate, chloroplatinic acid, platinum nitrate, platinum sulfate, potassium tetrachloroplatinate and tetrachloroplatinic acid At least one of ammonium.
  • the concentration of the platinum salt solution is greater than 30 mmol/L. Furthermore, the concentration of the platinum salt solution is greater than 35 mmol/L.
  • the present invention uses high-concentration platinum salt solution (greater than 30mmol/L) to prepare dendritic platinum structure, which can further increase the surface area of the microelectrode, and at the same time greatly increase its electrochemical performance, so that it has a better increase in charge storage capacity and charge Injection capacity, etc.
  • the pH of the platinum salt solution is 7-8. Furthermore, the pH of the platinum salt solution is 7.2-7.6. The choice of the pH of the platinum salt solution is more conducive to the deposition of the dendritic platinum structure and at the same time makes the dendritic platinum structure uniform.
  • the method further includes preprocessing the grooves. Further, the pretreatment includes cleaning and roughening the groove. The pretreatment of the groove can improve the bonding force between the subsequently deposited dendritic platinum structure and the groove, so that the dendritic platinum structure and the groove are not easy to fall off and separate.
  • the voltage of the constant potential deposition method is -0.6V to -0.75V, and the deposition time is 20min-60min. Furthermore, the voltage of the constant potential deposition method is -0.7V to -0.73V, and the deposition time is 30min-60min.
  • the current of the constant current deposition is -2 ⁇ A to -5 ⁇ A, and the deposition time is 20min-60min. Furthermore, the current for the constant current deposition is -3.5 ⁇ A to -4.5 ⁇ A, and the deposition time is 30 min-60 min.
  • the conditions of the constant potential deposition method/constant current deposition method used in the present invention are beneficial to the preparation of a dendritic platinum structure with uniform structure, and at the same time, it is beneficial to increase the surface area of the dendritic platinum structure, thereby increasing the surface area of the microelectrode and increasing its electrical performance.
  • the method further includes depositing a conductive polymer layer on the dendritic platinum structure by using an in-situ method or a template method.
  • depositing the conductive polymer layer is more conducive to the biocompatibility of the conductive polymer layer, thereby improving the biocompatibility and safety of the microelectrode.
  • the preparation method of the microelectrode provided by the second aspect of the present invention has simple operation, can be prepared on a large scale, and has uniform and stable performance.
  • the present invention provides a neural prosthesis, which includes the microelectrode manufactured by the manufacturing method described in the first aspect or the second aspect.
  • the neural prosthesis can be, but is not limited to, a cochlear implant, an optic nerve prosthesis, an implantable cardiac pacemaker or an implanted deep brain stimulator, especially an optic nerve prosthesis.
  • the microelectrodes in the neural prosthesis can realize precise and dynamic nerve stimulation and improve the performance of the neural prosthesis. Specifically, when used in an optic nerve prosthesis, the microelectrodes can increase the amount of stimulation received and produce higher spatial resolution.
  • the neural prosthesis includes one or more of the microelectrodes. Specifically, but not limited to, when the neural prosthesis includes a plurality of the microelectrodes, the plurality of the microelectrodes are arranged in an array.
  • the exposed conductive layer and the dendritic platinum structure constitute multiple electrodes.
  • the electrode sites are small, and in a certain space, the number of electrodes increases, the recording points increase, and the distribution is even.
  • the stimulation is more concentrated, which overcomes the disadvantage that the fringe electric field of the ordinary planar electrode is significantly stronger than the center, which causes the electric field lines to diverge.
  • the dendritic platinum structure increases the surface area of the microelectrode and effectively improves the electrochemical performance of the microelectrode, such as reducing impedance, lowering the critical stimulating charge density, improving charge storage and charge injection capabilities, etc., and the dendritic platinum structure is combined with the conductive layer The effect is good, the shedding of the dendritic platinum structure is avoided, and the biocompatibility and service life of the microelectrode are improved.
  • the electric fields of adjacent focus electrodes interact in time and space to generate additional perceptible virtual stimuli between the stimuli produced by the two focus electrodes separately, that is, create virtual electrode channels and increase micro
  • the number of stimuli that the electrode receives during use increases its resolution in applications, thereby broadening the application range of microelectrodes;
  • the preparation method of the microelectrode provided by the present invention has simple operation, uniform and stable performance, good repeatability, and can be prepared on a large scale;
  • the neural prosthesis provided by the present invention has excellent performance and a wide range of applications, and can be widely used in the fields of life sciences such as neurophysiology and brain science research.
  • FIG. 1 is a schematic cross-sectional view of a microelectrode provided by an embodiment of the present invention
  • FIG. 2 is a flow chart of a method for preparing a microelectrode according to an embodiment of the present invention
  • step S101 in a method for manufacturing a microelectrode according to an embodiment of the present invention
  • step S102 is a schematic diagram of step S102 in a method for manufacturing a microelectrode according to an embodiment of the present invention
  • step S103 is a schematic diagram of step S103 in a method for manufacturing a microelectrode according to an embodiment of the present invention
  • step S104 is a schematic diagram of step S104 in a method for manufacturing a microelectrode according to an embodiment of the present invention
  • FIG. 7 is a schematic diagram of step S105 in a method for manufacturing a microelectrode according to an embodiment of the present invention.
  • FIG. 8 is a flowchart of a method for preparing a microelectrode according to another embodiment of the present invention.
  • Figure 9 is a schematic diagram of a microelectrode electrode channel provided by the present invention.
  • FIG. 1 is a microelectrode provided by an embodiment of the present invention, including a flexible layer 10, a conductive layer 20, and a dendritic platinum structure 30.
  • the conductive layer 20 is disposed in the flexible layer 10, and the surface of the flexible layer 10 is There are two grooves 11 to expose part of the conductive layer 20, and each groove 11 is provided with a dendritic platinum structure 30.
  • the exposed conductive layer 20 and the dendritic platinum structure 30 constitute a plurality of electrodes, the electrode sites are small, and in a certain space, the number of electrodes increases, the recording points increase, and the distribution is even, which stimulates nerves It is more concentrated and overcomes the disadvantage that the fringe electric field of the ordinary planar electrode is significantly stronger than the center, which causes the electric field lines to diverge.
  • the dendritic platinum structure 30 increases the surface area of the microelectrode and effectively improves the electrochemical performance of the microelectrode, such as lowering impedance, lowering the critical stimulating charge density, improving charge storage capacity and charge injection capacity, etc., and the dendritic platinum structure 30 is conductive
  • the layer 20 has a good bonding effect, avoids the shedding of the dendritic platinum structure 30, and improves the biocompatibility and service life of the microelectrode.
  • the electric fields of adjacent focus electrodes interact in time and space to generate additional perceptible virtual stimuli between the stimuli produced by the two focus electrodes alone, that is, create virtual electrode channels and increase micro
  • the number of stimuli that the electrode receives during use increases its resolution in applications, thereby broadening the application range of microelectrodes.
  • the thickness of the flexible layer 10 is 3 ⁇ m-300 ⁇ m. Further, the thickness of the flexible layer 10 is 10 ⁇ m-260 ⁇ m.
  • the material of the flexible layer 10 can be, but is not limited to, polyimide or parylene.
  • the thickness of the conductive layer 20 is 0.1 ⁇ m-100 ⁇ m. Further, further, the thickness of the conductive layer 20 is 0.5 ⁇ m-80 ⁇ m.
  • the spacing between the plurality of grooves 11 is 10 ⁇ m-1000 ⁇ m. Further, the spacing between the plurality of grooves 11 is 50 ⁇ m-700 ⁇ m. Furthermore, the spacing between the plurality of grooves 11 is 80 ⁇ m-500 ⁇ m. In the present invention, the arrangement of the spacing between the plurality of grooves 11 is beneficial to the generation of virtual electrode channels, thereby increasing the number of perceptions of the microelectrode during use and promoting resolution.
  • the plurality of grooves 11 are arranged in an array.
  • the array arrangement of the grooves 11 is beneficial to the array arrangement of the dendritic platinum structures 30 arranged in the grooves 11, thereby increasing the number of virtual channels generated by the microelectrodes and increasing the number of stimuli.
  • the opening shape of the groove 11 may be, but not limited to, a circle, a square, a rectangle, an ellipse, a diamond, or an irregular shape.
  • the depth of the groove 11 is 0.5 ⁇ m-80 ⁇ m. Further, the depth of the groove 11 is 2 ⁇ m-70 ⁇ m.
  • the distribution density of the grooves 11 in the microelectrode is 10-300 grooves/cm 2 . Further, the distribution density of the grooves 11 in the microelectrode is 50-200/cm 2 .
  • the dendritic platinum structure 30 is formed of a plurality of dendritic platinum. Further, the dendritic platinum includes at least one of platinum nanowires, platinum nanorods, platinum nanocones, and platinum nanoflowers. In the present invention, the dendritic platinum structure 30 can greatly increase the surface area of the microelectrode, thereby increasing its electrical performance.
  • the platinum nanowire has a diameter of 2nm-50nm and a length of 0.2 ⁇ m-5 ⁇ m. Furthermore, the platinum nanowires have a diameter of 3nm-9nm and a length of 1.2 ⁇ m-4 ⁇ m.
  • the platinum nanorods have a diameter of 0.1 ⁇ m-1 ⁇ m and a length of 0.3 ⁇ m-5 ⁇ m. Further, the platinum nanorods have a diameter of 0.15 ⁇ m to 0.85 ⁇ m and a length of 0.8 ⁇ m to 4 ⁇ m.
  • the bottom diameter of the platinum nanocone is 0.1 ⁇ m-1 ⁇ m, and the height is 0.3 ⁇ m-5 ⁇ m. Further, the diameter of the bottom of the platinum nanocone is 0.2 ⁇ m-0.95 ⁇ m, and the length is 1.5 ⁇ m-3.5 ⁇ m.
  • the average diameter of the platinum nanoflowers is 0.2 ⁇ m-3 ⁇ m. Further, the average diameter of platinum nanoflowers is 0.5 ⁇ m-2.6 ⁇ m. Further, each platinum nanoflower includes a plurality of platinum nanosheets, and the lateral size of the platinum nanosheets is 0.1 ⁇ m-1 ⁇ m. Furthermore, the lateral dimension of the platinum nanosheets is 0.15 ⁇ m-0.8 ⁇ m.
  • the arrangement of platinum nanowires, platinum nanorods, and platinum nanocones is beneficial to further increase the surface area of the microelectrode and improve its electrical performance.
  • the distribution density of dendritic platinum in the dendritic platinum structure 30 is 10 pcs/ ⁇ m 2 -200 pcs/ ⁇ m 2 . Further, the distribution density of dendritic platinum in the dendritic platinum structure 30 is 25 pcs/ ⁇ m 2 -185 pcs/ ⁇ m 2 . Furthermore, the distribution density of dendritic platinum in the dendrite platinum structure 30 is 50 pcs/ ⁇ m 2 -150 pcs/ ⁇ m 2 . In the present invention, the denser the distribution of dendritic platinum, the larger the surface area of the microelectrode, and the more improved the electrical performance, which is more conducive to its application. Specifically, the distribution density of dendritic platinum may be, but not limited to, 30 pieces/ ⁇ m 2 , 70 pieces/ ⁇ m 2 , 135 pieces/ ⁇ m 2 or 180 pieces/ ⁇ m 2 .
  • the thickness of the dendritic platinum structure 30 is 0.3 ⁇ m-70 ⁇ m. Further, the thickness of the dendritic platinum structure 30 is 3 ⁇ m-60 ⁇ m. Furthermore, the thickness of the dendritic platinum structure 30 is 5 ⁇ m-50 ⁇ m. In the present invention, the setting of the thickness of the dendritic platinum structure 30 facilitates the generation and transmission of stimuli. Specifically, the thickness of the dendritic platinum structure 30 can be, but is not limited to, 0.8 ⁇ m, 2 ⁇ m, 8 ⁇ m, 25 ⁇ m, 36 ⁇ m, or 52 ⁇ m.
  • a plurality of dendritic platinum structures 30 are arranged in an array, so that an array of dendritic platinum structures is formed on the microelectrode, that is, a microelectrode array is formed, which further improves the overall electrical performance of the microelectrode and the stimulus received during use.
  • the quantity increases the number of virtual channels and improves their resolution in applications.
  • the dendritic platinum structure 30 may completely cover the bottom surface of the groove 11 (that is, the surface of the conductive layer 20 exposed in each groove 11 ), or may partially cover the bottom surface of the groove 11.
  • the thickness of the dendritic platinum structure 30 may be equal to the depth of the groove 11, may be smaller than the depth of the groove 11, or may be greater than the depth of the groove 11.
  • the thickness of the dendritic platinum structure 30 is greater than the depth of the groove 11, the surface area of the microelectrode is further increased, thereby improving its electrical performance.
  • the exposed surface of the conductive layer 20 is a flat surface or an uneven surface.
  • a conductive polymer layer is also provided on the dendritic platinum structure 30.
  • the conductive polymer layer has good electrical properties and is a soft material with excellent biocompatibility. It fits the tissues, reduces the immune response, and improves the long-term safety of the microelectrode. Therefore, a conductive polymer layer is provided on the dendritic platinum structure 30 to "combine hard and soft" to further improve the biocompatibility and service life of the microelectrode.
  • all of the multiple dendritic platinum structures may be provided with a conductive polymer layer, or may be partially provided with a conductive polymer layer, which is not limited. Further, a conductive polymer layer is provided on a plurality of the dendritic platinum structures, which further improves the biocompatibility and stability of the microelectrode.
  • the thickness of the conductive polymer layer is 0.1 ⁇ m-20 ⁇ m. Further, the thickness of the conductive polymer layer is 2 ⁇ m-16 ⁇ m. In the present invention, the setting of the thickness of the conductive polymer layer is more conducive to the transmission of stimulation of the conductive layer 20 and the dendritic platinum structure 30. Specifically, the thickness of the conductive polymer layer may be, but not limited to, 0.5 ⁇ m, 3.6 ⁇ m, 8 ⁇ m, 14 ⁇ m, or 17 ⁇ m.
  • the material of the conductive polymer layer includes at least one of polypyrrole, polyaniline, polythiophene and its derivatives, and conductive hydrogel. That is, the material of the conductive polymer layer includes at least one of polypyrrole, polyaniline, polythiophene, polypyrrole derivative, polyaniline derivative, polythiophene derivative, and conductive hydrogel.
  • the selection of the material of the conductive polymer layer is more conducive to the biocompatibility of the conductive polymer layer, thereby improving the biocompatibility and safety of the microelectrode.
  • the total thickness of the dendritic platinum structure 30 and the conductive polymer layer may be equal to the depth of the groove 11 or may be greater than the depth of the groove 11.
  • FIG. 2 is a method for preparing a microelectrode provided by an embodiment of the present invention, including:
  • Step S101 Provide a substrate, and prepare a first flexible layer on the substrate.
  • a substrate 40 is provided.
  • the substrate 40 can be, but is not limited to, a silicon wafer, a silicon oxide wafer or a glass wafer.
  • the preparation of the first flexible layer 101 on the substrate 40 includes the preparation of the first flexible layer 101 on the substrate 40 by spin coating or deposition.
  • the material of the first flexible layer 101 may be, but is not limited to, polyimide or parylene.
  • the thickness of the first flexible layer 101 is 1 ⁇ m-200 ⁇ m.
  • Step S102 preparing a conductive layer on the first flexible layer through a mask.
  • a conductive layer 20 is prepared on the first flexible layer 101 through a mask.
  • it includes setting a mask on the first flexible layer 101, and forming a conductive layer 20 on the first flexible layer 101 by deposition, and the conductive layer 20 covers a part of the first flexible layer.
  • the deposition may be, but is not limited to, physical vapor deposition or chemical vapor deposition.
  • the thickness of the conductive layer 20 is 0.1 ⁇ m-100 ⁇ m.
  • Step S103 deposit a second flexible layer on the conductive layer, the second flexible layer partially covers the surface of the conductive layer and partially covers the surface of the first flexible layer.
  • a second flexible layer 102 is deposited on the conductive layer 20, and the second flexible layer 102 partially covers the surface of the conductive layer 20 and partially covers the surface of the first flexible layer 101.
  • the second flexible layer 102 is deposited on the conductive layer 20 by spin coating or deposition.
  • the material of the second flexible layer 102 may be, but not limited to, polyimide or parylene.
  • the thickness of the second flexible layer 102 is 1 ⁇ m-200 ⁇ m.
  • Step S104 etching the second flexible layer to expose part of the conductive layer and forming a plurality of grooves.
  • the second flexible layer 102 is etched to expose a part of the conductive layer 20 and a plurality of grooves 11 are formed.
  • the etching includes at least one of dry etching and wet etching.
  • the etching may be, but not limited to, reactive ion etching or plasma etching.
  • a reactive ion etching (Reactive Ion Etching, RIE) method is used to deposit an aluminum mask on the second flexible layer 102 for an etching process to form a plurality of grooves 11, and then wet Method etching to remove the aluminum mask.
  • the thickness of the dendritic platinum structure 30 may be equal to the depth of the groove 11, may be smaller than the depth of the groove 11, or may be greater than the depth of the groove 11.
  • the surface area of the microelectrode is further increased, thereby improving its electrical performance.
  • the spacing between adjacent grooves 11 may be the same or different.
  • the distance between adjacent grooves 11 is 10 ⁇ m-1000 ⁇ m.
  • the distance between adjacent grooves 11 is 50 ⁇ m-700 ⁇ m.
  • the distance between adjacent grooves 11 is 80 ⁇ m-500 ⁇ m.
  • the arrangement of the spacing between the plurality of grooves 11 is beneficial to the generation of virtual electrode channels, thereby increasing the number of perceptions of the microelectrodes during use and promoting resolution.
  • the shape of the opening of the groove 11 can be, but is not limited to, a circle, a square, a rectangle, an oval, a diamond, or an irregular shape.
  • the exposed surface of the conductive layer 20 is a flat surface or an uneven surface.
  • part of the second flexible layer when etching the second flexible layer, part of the second flexible layer can be just etched to expose part of the conductive layer, and the exposed surface of the conductive layer is a flat surface; or part of the second flexible layer can be etched At the same time, a part of the conductive layer is etched, and a part of the conductive layer is also exposed.
  • the exposed surface of the conductive layer is an uneven surface.
  • Step S105 removing the substrate and depositing a dendritic platinum structure in a plurality of grooves to obtain a microelectrode.
  • depositing the dendritic platinum structure 30 in the plurality of grooves 11 includes: providing a platinum salt solution, and forming the dendritic platinum structure 30 in the plurality of grooves 11 by a constant potential deposition method or a constant current deposition method.
  • platinum salts include platinum chloride, ammonium hexachloroplatinate, potassium hexachloroplatinate, sodium hexachloroplatinate, chloroplatinic acid, platinum nitrate, platinum sulfate, potassium tetrachloroplatinate and ammonium tetrachloroplatinate. At least one of. Further, the concentration of the platinum salt solution is greater than 30 mmol/L. Further, the pH of the platinum salt solution is 7-8. Further, before forming the dendritic platinum structure 30 in the plurality of grooves 11 by using the constant potential deposition method or the constant current deposition method, it further includes preprocessing the grooves 11. Further, the pretreatment includes cleaning and roughening the groove 11.
  • the pretreatment of the groove 11 can improve the bonding force between the subsequently deposited platinum dendritic structure 30 and the groove 11, so that the platinum dendritic structure 30 and the groove 11 are not easy to fall off and separate.
  • the voltage of the constant potential deposition method is -0.6V ⁇ -0.75V, and the deposition time is 20min-60min.
  • the current for constant current deposition is -2 ⁇ A to -5 ⁇ A, and the deposition time is 20min-60min.
  • the first flexible layer 101 and the second flexible layer 102 are the flexible layer 10 in FIG. 1.
  • the substrate may be removed first, and then the dendritic platinum structure may be deposited, or the dendritic platinum structure may be deposited first, and then the substrate may be removed.
  • FIG. 8 is a flow chart of a method for preparing a microelectrode according to another embodiment of the present invention, wherein steps S201-S205 are the same as S101-S105 in the above-mentioned embodiment, and further includes step S206, using in-situ method or
  • the template method deposits a conductive polymer layer on the dendritic platinum structure to obtain a microelectrode.
  • the thickness of the conductive polymer layer is 0.1 ⁇ m-20 ⁇ m. Further, the thickness of the conductive polymer layer is 2 ⁇ m-16 ⁇ m.
  • the total thickness of the dendritic platinum structure 30 and the conductive polymer layer may be equal to the depth of the groove 11 or may be greater than the depth of the groove 11.
  • the setting of the thickness of the conductive polymer layer is more conducive to the transmission of stimulation of the conductive layer 20 and the dendritic platinum structure 30.
  • the material of the conductive polymer layer includes at least one of polypyrrole, polyaniline, polythiophene and its derivatives, and conductive hydrogel. That is, the material of the conductive polymer layer includes at least one of polypyrrole, polyaniline, polythiophene, polypyrrole derivative, polyaniline derivative, polythiophene derivative, and conductive hydrogel.
  • the selection of the material of the conductive polymer layer is more conducive to the biocompatibility of the conductive polymer layer, thereby improving the biocompatibility and safety of the microelectrode.
  • the conductive polymer layer has good electrical properties and is a soft material with excellent biocompatibility. It adheres to tissues, reduces immune response, and improves the long-term safety of microelectrodes. Therefore, a conductive polymer layer is arranged on the dendritic platinum structure 30 to "combine hard and soft" to further improve the biocompatibility and service life of the microelectrode.
  • the present invention also provides a neural prosthesis including the above-mentioned microelectrode.
  • the neural prosthesis can be, but is not limited to, a cochlear implant, an optic nerve prosthesis, an implantable cardiac pacemaker or an implanted deep brain stimulator.
  • a neuroprosthesis when used as an optic nerve prosthesis, on the one hand, it has good electrical performance and biocompatibility.
  • the multi-focus electrode in the microelectrode realizes the real electrode. Multiple stimulation of channels and virtual electrode channels can achieve precise nerve control, improve spatial resolution, and provide a hardware foundation for high-density nerve stimulation and neural prostheses.
  • the stimulus waveform, amplitude, and charge distribution ratio on different electrode pairs are changed through electric field control. Specifically, it can, but is not limited to, different distribution ratios of the stimulus charges of adjacent or spaced electrode points are sequentially increased from 0 to 1 in steps of 0.1, and the directional action of the current is used to realize the dynamic movement of the stimulation focus to construct a virtual channel. In the limited microelectrode space, multi-channel virtual stimulation is realized, and the stimulation effect is improved.
  • the neural prosthesis includes one or more of the above-mentioned microelectrodes.
  • the neural prosthesis includes multiple microelectrodes
  • the multiple microelectrodes are arranged in an array, which is more conducive to increasing the number of stimuli received during the use of the neural prosthesis, and significantly improving the resolution.

Landscapes

  • Health & Medical Sciences (AREA)
  • Neurology (AREA)
  • Neurosurgery (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Cardiology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Electrotherapy Devices (AREA)

Abstract

一种微电极，包括柔性层（10）、导电层（20）和多个枝晶铂结构（30），导电层（20）设置在柔性层（10）中，柔性层（10）表面上设置有多个凹槽（11）以暴露部分导电层（20），每一凹槽（11）内设置有一枝晶铂结构（30），其中多个凹槽（11）成为多个焦点电极，电极位点小、记录点多，分布均匀；修饰的枝晶铂结构（30）提高了微电极的表面积、电学性能、生物相容性和使用寿命；同时，利用电流导引技术创建虚拟电极，增加微电极在使用过程中接收刺激的数量，提高其在应用中的分辨率。

Description

一种微电极及其制备方法和神经假体 技术领域
本发明涉及生物医学工程领域，具体涉及一种微电极及其制备方法和神经假体。
背景技术
神经电极作为最重要的植入式微器件之一，用以刺激神经组织或记录神经电信号，广泛用于神经生理、脑科学研究等生命科学领域。但随着临床对刺激或记录的精度要求越来越高，低密度、简单功能的神经电极已经无法满足精准调控的需求。神经电极正朝着集成化和微型化的化方向发展，因此，微电极的尺寸减小造成电极阻抗增加、电容降低等性能问题，限制了其临床应用。因此，在有限的空间内，设计多焦点电极，使电极数目与电极间距达到平衡，突破其空间分辨率的瓶颈；并且，在电极几何尺寸不变的情况下，通过良好的表面修饰提高其实际面积来降低临界刺激电荷密度；同时，增加患者的感知数量，产生更高的分辨率，是神经电极的发展方向。
发明内容
为解决上述问题，本发明提供了一种微电极，包括柔性层、导电层和多个枝晶铂结构，导电层设置在柔性层中，柔性层表面上设置有多个凹槽以暴露部分导电层，每一凹槽内设置有一枝晶铂结构，其中多个凹槽成为多个焦点电极，电极位点小、记录点多，分布均匀；修饰的枝晶铂结构提高了微电极的表面积、电学性能、生物相容性和使用寿命；同时，利用电流导引技术创建虚拟电极，增加微电极在使用过程中接收刺激的数量，提高其在应用中的分辨率。
第一方面，本发明提供了一种微电极，包括柔性层、导电层和枝晶铂结构，所述导电层设置在所述柔性层中，所述柔性层表面上设置有多个凹槽以暴露部分所述导电层，每一所述凹槽内设置有一所述枝晶铂结构。
可选的，所述柔性层的厚度为3μm-300μm。进一步的，所述柔性层的厚 度为10μm-260μm。在本发明中，所述柔性层的材质可以但不限于为聚酰亚胺或聚对二甲苯。
可选的，所述导电层的厚度为0.1μm-100μm。进一步的，所述导电层的厚度为0.5μm-80μm。
可选的，相邻所述凹槽之间的间距为10μm-1000μm。进一步的，相邻所述凹槽之间的间距为50μm-700μm。更进一步的，相邻所述凹槽之间的间距为80μm-500μm。在本发明中，相邻所述凹槽之间间距的设置有利于虚拟电极通道的产生，进而提高微电极在使用过程中的感知数量，促进分辨率。
可选的，多个所述凹槽呈阵列排布。凹槽的阵列排布有利于设置在凹槽中的枝晶铂结构的阵列排布，进而提高微电极产生虚拟通道的数量，提高刺激数量。
在本发明中，所述凹槽的开口形状可以但不限于为圆形、正方形、长方形、椭圆形、菱形或不规则形状。
可选的，所述凹槽的深度为0.5μm-80μm。进一步的，所述凹槽的深度为2μm-70μm。
可选的，所述微电极中所述凹槽的分布密度为10-300个/cm 2。进一步的，所述微电极中所述凹槽的分布密度为50-200个/cm 2。
可选的，所述枝晶铂结构由多个枝晶铂形成。进一步的，所述枝晶铂包括铂纳米线、铂纳米棒、铂纳米锥和铂纳米花中的至少一种。在本发明中，所述枝晶铂结构可以大大提高微电极的表面积，进而增加其电学性能。
可选的，所述铂纳米线的直径为2nm-50nm，长度为0.2μm-5μm。进一步的，所述铂纳米线的直径为3nm-9nm，长度为1.2μm-4μm。
可选的，所述铂纳米棒的直径为0.1μm-1μm，长度为0.3μm-5μm。进一步的，所述铂纳米棒的直径为0.15μm-0.85μm，长度为0.8μm-4μm。
可选的，所述铂纳米锥的底部直径为0.1μm-1μm，高度为0.3μm-5μm。进一步的，所述铂纳米锥的底部直径为0.2μm-0.95μm，长度为1.5μm-3.5μm。
可选的，所述铂纳米花的平均直径为0.2μm-3μm。进一步的，所述铂纳米花的平均直径为0.5μm-2.6μm。进一步的，每个所述铂纳米花包括多个铂纳米片，所述铂纳米片的横向尺寸为0.1μm-1μm。更进一步的，所述铂纳米片的横 向尺寸为0.15μm-0.8μm。
在本发明中，所述铂纳米线、铂纳米棒、铂纳米锥的设置有利于进一步提高微电极的表面积，提高其电学性能。
可选的，所述枝晶铂结构中所述枝晶铂的分布密度为10个/μm 2-300个/μm 2。进一步的，所述枝晶铂结构中所述枝晶铂的分布密度为25个/μm 2-265个/μm 2。更进一步的，所述枝晶铂结构中所述枝晶铂的分布密度为50个/μm 2-180个/μm 2。在本发明中，枝晶铂的分布越密集，微电极的表面积越大，电学性能提高越多，更有利于其应用。
可选的，所述枝晶铂结构的厚度为0.3μm-70μm。进一步的，所述枝晶铂结构的厚度为3μm-60μm。更进一步的，所述枝晶铂结构的厚度为5μm-50μm。在本发明中，所述枝晶铂结构厚度的设置有利于刺激的产生和传递。
在本发明中，所述枝晶铂结构的厚度可以等于所述凹槽的深度、可以小于所述凹槽的深度或可以大于所述凹槽的深度。当所述枝晶铂结构的厚度大于所述凹槽的深度时，更加提高微电极的表面积，进而提高其电学性能。
可选的，多个所述枝晶铂结构呈阵列排布，使得微电极上形成枝晶铂结构阵列，即形成微电极阵列，进一步提高微电极整体的电学性能和使用过程中接收刺激的数量，使得虚拟通道的数量增加，提高其在应用中的分辨率。
在本发明中，所述枝晶铂结构可以完全覆盖所述凹槽的底面(即每个凹槽中暴露的导电层表面)，也可以部分覆盖所述凹槽的底面。
可选的，所述枝晶铂结构上还设置有导电聚合物层。导电聚合物层具有良好电学性能，是生物相容性优异的软性材料，其贴合组织，降低免疫反应，提高微电极的长期安全性。因此，在枝晶铂结构上设置导电聚合物层，“软硬结合”，进一步提高微电极的生物相容性和使用寿命。在本发明中，多个枝晶铂结构可以全部设置有导电聚合物层，也可以部分设置有导电聚合物层，对此不作限定。进一步的，多个所述枝晶铂结构上均设置有导电聚合物层，更加提高微电极的生物相容性和稳定性。
可选的，所述导电聚合物层的厚度为0.1μm-20μm。进一步的，所述导电聚合物层的厚度为2μm-16μm。在本发明中，所述导电聚合物层的厚度的设置更有利于导电层和枝晶铂结构的刺激的传递。
可选的，所述导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩及其衍生物和导电水凝胶中的至少一种。即所述导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩、聚吡咯衍生物、聚苯胺衍生物、聚噻吩衍生物和导电水凝胶中的至少一种。在本发明中，所述导电聚合物层材质的选择更有利于导电聚合物层的生物相容性，进而提高微电极的生物相容性和安全性。
本发明第一方面提供的微电极中，暴露的导电层以及枝晶铂结构成为多个电极，电极位点小，且在一定的空间内，电极数量增多，记录点增多，分布均匀，对神经的刺激更为集中，克服了普通平面电极的边缘电场显著强于中央，导致电场线发散的缺点。枝晶铂结构提高了微电极的表面积，有效改善了微电极的电化学性能，如降低阻抗、降低临界刺激电荷密度、提高电荷存储能力和电荷注入能力等，且枝晶铂结构与导电层结合效果好，避免了枝晶铂结构的脱落，提高微电极的生物相容性和使用寿命。同时，利用电流导引技术，相邻电极电场在时间空间上相互作用，产生额外的介于两个电极单独产生的刺激之间的可感知的虚拟刺激，即创建虚拟电极通道，增加微电极在使用过程中接收刺激的数量，提高其在应用中的分辨率，从而拓宽微电极的应用范围。
第二方面，本发明提供了一种微电极的制备方法，包括：
提供基底，在所述基底上制备第一柔性层；
通过掩膜在所述第一柔性层上制备导电层；
在所述导电层上沉积第二柔性层，所述第二柔性层部分覆盖在所述导电层表面，部分覆盖在所述第一柔性层表面；
刻蚀所述第二柔性层以暴露部分所述导电层，并形成多个凹槽；
去除所述基底，并在多个所述凹槽中沉积枝晶铂结构，即可得到微电极。
可选的，所述基底可以但不限于为硅片、氧化硅片或玻璃片。
可选的，所述在所述基底上制备第一柔性层，包括采用旋涂或沉积的方式在所述基底上制备所述第一柔性层。
可选的，所述通过掩膜在所述第一柔性层上制备导电层，包括在所述第一柔性层上方设置掩膜，通过沉积在所述第一柔性层上形成所述导电层，所述导电层覆盖部分所述第一柔性层。进一步的，所述沉积可以但不限于为物理气相沉积、化学气相沉积。
可选的，所述第一柔性层和所述第二柔性层的材质可以但不限于为聚酰亚胺或聚对二甲苯。
可选的，所述刻蚀包括干法刻蚀和湿法刻蚀中的至少一种。具体的，所述刻蚀可以但不限于为反应离子刻蚀、等离子刻蚀。
可选的，所述在多个所述凹槽中沉积枝晶铂结构，包括：提供铂盐溶液，采用恒电位沉积法或恒电流沉积法在多个所述凹槽中形成所述枝晶铂结构。
进一步的，所述铂盐包括氯化铂、六氯铂酸铵、六氯铂酸钾、六氯铂酸钠、氯铂酸、硝酸铂、硫酸铂、四氯铂酸钾和四氯铂酸铵中的至少一种。
进一步的，所述铂盐溶液的浓度大于30mmol/L。更进一步的，所述铂盐溶液的浓度大于35mmol/L。本发明采用高浓度的铂盐溶液(大于30mmol/L)制备枝晶铂结构，可以进一步提高微电极的表面积，同时大幅度增加其电化学性能，使其具有更好的增加电荷存储能力和电荷注入能力等。
进一步的，所述铂盐溶液的pH为7-8。更进一步的，所述铂盐溶液的pH为7.2-7.6。铂盐溶液pH的选择更有利于枝晶铂结构的沉积，同时使得枝晶铂结构均匀一致。
进一步的，所述采用恒电位沉积法或恒电流沉积法在多个所述凹槽中形成所述枝晶铂结构之前，还包括对所述凹槽进行预处理。进一步的，所述预处理包括对所述凹槽进行清洗和粗糙化处理。对凹槽进行预处理可以提高后续沉积的枝晶铂结构与凹槽的结合力，使得枝晶铂结构与凹槽不易脱落分离。
进一步的，所述恒电位沉积法的电压为-0.6V～-0.75V，沉积时间为20min-60min。更进一步的，所述恒电位沉积法的电压为-0.7V～-0.73V，沉积时间为30min-60min。
进一步的，所述恒电流沉积的电流为-2μA～-5μA，沉积时间为20min-60min。更进一步的，所述恒电流沉积的电流为-3.5μA～-4.5μA，沉积时间为30min-60min。
本发明采用的上述恒电位沉积法/恒电流沉积法的条件，有利于制备结构均匀一致的枝晶铂结构，同时有利于增加枝晶铂结构的表面积，进而提高微电极的表面积，增加其电学性能。
可选的，所述在所述凹槽中沉积枝晶铂结构后，还包括采用原位法或模板 法在所述枝晶铂结构上沉积导电聚合物层。在本发明中，沉积所述导电聚合物层更有利于导电聚合物层的生物相容性，进而提高微电极的生物相容性和安全性。
本发明第二方面提供的微电极的制备方法，操作简单，可以进行大规模制备，性能均一稳定。
第三方面，本发明提供了一种神经假体，包括第一方面所述的或第二方面所述的制备方法制得的微电极。
在本发明中，所述神经假体可以但不限于为人工耳蜗、视神经假体、植入式心脏起博器或植入式深脑刺激器，尤其是视神经假体。所述神经假体中的微电极可以实现精准、动态的神经刺激，提高神经假体的性能。具体的，当用于视神经假体时，微电极可以增加刺激接收量，产生更高的空间分辨率。
在本发明中，所述神经假体包括一个或多个所述微电极。具体的，可以但不限于为当所述神经假体包括多个所述微电极时，多个所述微电极呈阵列排布。
综上，本发明有益效果包括以下几个方面：
1、本发明提供的微电极中，暴露的导电层以及枝晶铂结构构成多个电极，电极位点小，且在一定的空间内，电极数量增多，记录点增多，分布均匀，对神经的刺激更为集中，克服了普通平面电极的边缘电场显著强于中央，导致电场线发散的缺点。枝晶铂结构提高了微电极的表面积，有效改善了微电极的电化学性能，如降低阻抗、降低临界刺激电荷密度、提高电荷存储能力和电荷注入能力等，且枝晶铂结构与导电层结合效果好，避免了枝晶铂结构的脱落，提高微电极的生物相容性和使用寿命。同时，利用电流导引技术，相邻焦点电极电场在时间空间上相互作用，产生额外的介于两个焦点电极单独产生的刺激之间的可感知的虚拟刺激，即创建虚拟电极通道，增加微电极在使用过程中接收刺激的数量，提高其在应用中的分辨率，从而拓宽微电极的应用范围；
2、本发明提供的微电极的制备方法，操作简单、性能均一稳定、重复性好，可以进行大规模制备；
3、本发明提供的神经假体性能优异，应用范围广，可以广泛用于神经生理、脑科学研究等生命科学领域。
附图说明
为了更清楚地说明本发明实施例或现有技术中的技术方案，下面将对实施例或现有技术描述中所需要使用的附图作简单地介绍。此处所描述的具体实施例仅仅用以解释本发明，并不用于限定本发明。
图1为本发明一实施例提供的一种微电极截面示意图；
图2为本发明一实施例提供的一种微电极的制备方法流程图；
图3为本发明一实施例提供的一种微电极的制备方法中步骤S101示意图；
图4为本发明一实施例提供的一种微电极的制备方法中步骤S102示意图；
图5为本发明一实施例提供的一种微电极的制备方法中步骤S103示意图；
图6为本发明一实施例提供的一种微电极的制备方法中步骤S104示意图；
图7为本发明一实施例提供的一种微电极的制备方法中步骤S105示意图；
图8为本发明另一实施例提供的一种微电极的制备方法流程图；
图9为本发明提供的一种微电极电极通道示意图。
具体实施方式
以下所述是本发明的优选实施方式，应当指出，对于本技术领域的普通技术人员来说，在不脱离本发明原理的前提下，还可以做出若干改进和润饰，这些改进和润饰也视为本发明的保护范围。
请参阅图1，为本发明一实施例提供的一种微电极，包括柔性层10、导电层20和枝晶铂结构30，导电层20设置在柔性层10中，柔性层10表面上设置有多个凹槽11以暴露部分导电层20，每一凹槽11内设置有一枝晶铂结构30。
本发明的微电极中，暴露的导电层20以及枝晶铂结构30构成多个电极，电极位点小，且在一定的空间内，电极数量增多，记录点增多，分布均匀，对神经的刺激更为集中，克服了普通平面电极的边缘电场显著强于中央，导致电场线发散的缺点。枝晶铂结构30提高了微电极的表面积，有效改善了微电极的电化学性能，如降低阻抗、降低临界刺激电荷密度、提高电荷存储能力和电荷注入能力等，且枝晶铂结构30与导电层20结合效果好，避免了枝晶铂结构30的脱落，提高微电极的生物相容性和使用寿命。同时，利用电流导引技术， 相邻焦点电极电场在时间空间上相互作用，产生额外的介于两个焦点电极单独产生的刺激之间的可感知的虚拟刺激，即创建虚拟电极通道，增加微电极在使用过程中接收刺激的数量，提高其在应用中的分辨率，从而拓宽微电极的应用范围。
本发明实施方式中，柔性层10的厚度为3μm-300μm。进一步的，柔性层10的厚度为10μm-260μm。在本发明中，柔性层10的材质可以但不限于为聚酰亚胺或聚对二甲苯。
本发明实施方式中，导电层20的厚度为0.1μm-100μm。进一步的，进一步的，导电层20的厚度为0.5μm-80μm。
本发明实施方式中，多个凹槽11之间的间距为10μm-1000μm。进一步的，多个凹槽11之间的间距为50μm-700μm。更进一步的，多个凹槽11之间的间距为80μm-500μm。在本发明中，多个凹槽11之间间距的设置有利于虚拟电极通道的产生，进而提高微电极在使用过程中的感知数量，促进分辨率。
本发明实施方式中，多个凹槽11呈阵列排布。凹槽11的阵列排布有利于设置在凹槽11中的枝晶铂结构30的阵列排布，进而提高微电极产生虚拟通道的数量，提高刺激数量。
本发明实施方式中，凹槽11的开口形状可以但不限于为圆形、正方形、长方形、椭圆形、菱形或不规则形状。
本发明实施方式中，凹槽11的深度为0.5μm-80μm。进一步的，凹槽11深度为2μm-70μm。
本发明实施方式中，微电极中凹槽11的分布密度为10-300个/cm 2。进一步的，微电极中凹槽11的分布密度为50-200个/cm 2。
本发明实施方式中，枝晶铂结构30由多个枝晶铂形成。进一步的，枝晶铂包括铂纳米线、铂纳米棒、铂纳米锥和铂纳米花中的至少一种。在本发明中，枝晶铂结构30可以大大提高微电极的表面积，进而增加其电学性能。
本发明实施方式中，铂纳米线的直径为2nm-50nm，长度为0.2μm-5μm。进一步的，铂纳米线的直径为3nm-9nm，长度为1.2μm-4μm。
本发明实施方式中，铂纳米棒的直径为0.1μm-1μm，长度为0.3μm-5μm。进一步的，铂纳米棒的直径为0.15μm-0.85μm，长度为0.8μm-4μm。
本发明实施方式中，铂纳米锥的底部直径为0.1μm-1μm，高度为0.3μm-5μm。进一步的，铂纳米锥的底部直径为0.2μm-0.95μm，长度为1.5μm-3.5μm。
本发明实施方式中，铂纳米花的平均直径为0.2μm-3μm。进一步的，铂纳米花的平均直径为0.5μm-2.6μm。进一步的，每个铂纳米花包括多个铂纳米片，铂纳米片的横向尺寸为0.1μm-1μm。更进一步的，铂纳米片的横向尺寸为0.15μm-0.8μm。
本发明实施方式中，铂纳米线、铂纳米棒、铂纳米锥的设置有利于进一步提高微电极的表面积，提高其电学性能。
本发明实施方式中，枝晶铂结构30中枝晶铂的分布密度为10个/μm 2-200个/μm 2。进一步的，枝晶铂结构30中枝晶铂的分布密度为25个/μm 2-185个/μm 2。更进一步的，枝晶铂结构30中枝晶铂的分布密度为50个/μm 2-150个/μm 2。在本发明中，枝晶铂的分布越密集，微电极的表面积越大，电学性能提高越多，更有利于其应用。具体的，枝晶铂的分布密度可以但不限于为30个/μm 2、70个/μm 2、135个/μm 2或180个/μm 2。
本发明实施方式中，枝晶铂结构30的厚度为0.3μm-70μm。进一步的，枝晶铂结构30的厚度为3μm-60μm。更进一步的，枝晶铂结构30的厚度为5μm-50μm。在本发明中，枝晶铂结构30厚度的设置有利于刺激的产生和传递。具体的，枝晶铂结构30的厚度为可以但不限于为0.8μm、2μm、8μm、25μm、36μm或52μm。
本发明实施方式中，多个枝晶铂结构30呈阵列排布，使得微电极上形成枝晶铂结构阵列，即形成微电极阵列，进一步提高微电极整体的电学性能和使用过程中接收刺激的数量，使得虚拟通道的数量增加，提高其在应用中的分辨率。
本发明实施方式中，枝晶铂结构30可以完全覆盖凹槽11的底面(即每个凹槽11中暴露的导电层20表面)，也可以部分覆盖凹槽11的底面。
本发明实施方式中，枝晶铂结构30的厚度可以等于凹槽11的深度、可以小于凹槽11的深度或可以大于凹槽11的深度。当枝晶铂结构30的厚度大于凹槽11的深度时，更加提高微电极的表面积，进而提高其电学性能。
本发明实施方式中，导电层20暴露的一侧表面为平整表面或凹凸表面。
本发明实施方式中，枝晶铂结构30上还设置有导电聚合物层。导电聚合物层具有良好电学性能，是生物相容性优异的软性材料，其贴合组织，降低免疫反应，提高微电极的长期安全性。因此，在枝晶铂结构30上设置导电聚合物层，“软硬结合”，进一步提高微电极的生物相容性和使用寿命。在本发明中，多个枝晶铂结构可以全部设置有导电聚合物层，也可以部分设置有导电聚合物层，对此不作限定。进一步的，多个所述枝晶铂结构上均设置有导电聚合物层，更加提高微电极的生物相容性和稳定性。
本发明实施方式中，导电聚合物层的厚度为0.1μm-20μm。进一步的，导电聚合物层的厚度为2μm-16μm。在本发明中，导电聚合物层的厚度的设置更有利于导电层20和枝晶铂结构30的刺激的传递。具体的，导电聚合物层的厚度可以但不限于为0.5μm、3.6μm、8μm、14μm或17μm。
本发明实施方式中，导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩及其衍生物和导电水凝胶中的至少一种。即导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩、聚吡咯衍生物、聚苯胺衍生物、聚噻吩衍生物和导电水凝胶中的至少一种。在本发明中，导电聚合物层材质的选择更有利于导电聚合物层的生物相容性，进而提高微电极的生物相容性和安全性。
本发明实施方式中，枝晶铂结构30和导电聚合物层的总厚度可以等于凹槽11的深度或可以大于凹槽11的深度。
请参阅图2，为本发明一实施例提供的一种微电极的制备方法，包括：
步骤S101：提供基底，在基底上制备第一柔性层。
参阅图3，提供基底40，基底40可以但不限于为硅片、氧化硅片或玻璃片。在基底40上制备第一柔性层101，包括采用旋涂或沉积的方式在基底40上制备第一柔性层101。可选的，第一柔性层101的材质可以但不限于为聚酰亚胺或聚对二甲苯。可选的，第一柔性层101的厚度为1μm-200μm。
步骤S102：通过掩膜在第一柔性层上制备导电层。
参阅图4，通过掩膜在第一柔性层101上制备导电层20。可选的，包括在第一柔性层101上方设置掩膜，通过沉积在第一柔性层101上形成导电层20，导电层20覆盖部分第一柔性层。进一步的，沉积可以但不限于为物理气相沉 积、化学气相沉积。可选的，导电层20的厚度为0.1μm-100μm。
步骤S103：在导电层上沉积第二柔性层，第二柔性层部分覆盖在导电层表面，部分覆盖在第一柔性层表面。
参阅图5，在导电层20上沉积第二柔性层102，第二柔性层102部分覆盖在导电层20表面，部分覆盖在第一柔性层101表面。可选的，采用旋涂或沉积的方式在导电层20上沉积第二柔性层102。可选的，第二柔性层102的材质可以但不限于为聚酰亚胺或聚对二甲苯。可选的，第二柔性层102的厚度为1μm-200μm。
步骤S104：刻蚀第二柔性层以暴露部分导电层，并形成多个凹槽。
参阅图6，刻蚀第二柔性层102以暴露部分导电层20，并形成多个凹槽11。可选的，刻蚀包括干法刻蚀和湿法刻蚀中的至少一种。具体的，刻蚀可以但不限于为反应离子刻蚀、等离子刻蚀。在本发明一具体实施方式中，采用反应离子刻蚀(Reactive Ion Etching，RIE)方式，在第二柔性层102上沉积铝掩膜进行刻蚀工艺，以形成多个凹槽11，再通过湿法刻蚀去除铝掩膜。在本发明中，枝晶铂结构30的厚度可以等于凹槽11的深度、可以小于凹槽11的深度或可以大于凹槽11的深度。当枝晶铂结构30的厚度大于凹槽11的深度时，更加提高微电极的表面积，进而提高其电学性能。相邻凹槽11之间的间距可以相同也可以不同。可选的，相邻凹槽11之间的间距为10μm-1000μm。进一步的，相邻凹槽11之间的间距为50μm-700μm。更进一步的，相邻凹槽11之间的间距为80μm-500μm。在本发明中，多个凹槽11之间间距的设置有利于虚拟电极通道的产生，进而提高微电极在使用过程中的感知数量，促进分辨率。在本发明中，凹槽11的开口形状可以但不限于为圆形、正方形、长方形、椭圆形、菱形或不规则形状。在本发明中，导电层20暴露的一侧表面为平整表面或凹凸表面。也就是说刻蚀第二柔性层时，可以将部分第二柔性层刚好刻蚀完，以暴露部分导电层，导电层暴露的一侧表面为平整表面；或可以将部分第二柔性层刻蚀，同时刻蚀部分导电层，同样暴露部分导电层，导电层暴露的一侧表面为凹凸表面。
步骤S105：去除基底，并在多个凹槽中沉积枝晶铂结构，即可得到微电极。
参阅图7，去除基底40，并在多个凹槽11中沉积枝晶铂结构30，即可得到微电极。可选的，在多个凹槽11中沉积枝晶铂结构30，包括：提供铂盐溶液，采用恒电位沉积法或恒电流沉积法在多个凹槽11中形成枝晶铂结构30。进一步的，铂盐包括氯化铂、六氯铂酸铵、六氯铂酸钾、六氯铂酸钠、氯铂酸、硝酸铂、硫酸铂、四氯铂酸钾和四氯铂酸铵中的至少一种。进一步的，铂盐溶液的浓度大于30mmol/L。进一步的，铂盐溶液的pH为7-8。进一步的，采用恒电位沉积法或恒电流沉积法在多个凹槽11中形成枝晶铂结构30之前，还包括对凹槽11进行预处理。进一步的，预处理包括对凹槽11进行清洗和粗糙化处理。对凹槽11进行预处理可以提高后续沉积的枝晶铂结构30与凹槽11的结合力，使得枝晶铂结构30与凹槽11不易脱落分离。进一步的，恒电位沉积法的电压为-0.6V～-0.75V，沉积时间为20min-60min。进一步的，恒电流沉积的电流为-2μA～-5μA，沉积时间为20min-60min。其中，第一柔性层101和第二柔性层102为图1中的柔性层10。在本发明中，可以先去除基底，再沉积枝晶铂结构，也可以先沉积枝晶铂结构，再去除基底。
请参阅图8，为本发明另一实施例提供的一种微电极的制备方法流程图，其中步骤S201-S205与上述实施例中S101-S105相同，并且还包括步骤S206，采用原位法或模板法在枝晶铂结构上沉积导电聚合物层，即可得到微电极。可选的，导电聚合物层的厚度为0.1μm-20μm。进一步的，导电聚合物层的厚度为2μm-16μm。枝晶铂结构30和导电聚合物层的总厚度可以等于凹槽11的深度或可以大于凹槽11的深度。在本发明中，导电聚合物层的厚度的设置更有利于导电层20和枝晶铂结构30刺激的传递。可选的，导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩及其衍生物和导电水凝胶中的至少一种。即导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩、聚吡咯衍生物、聚苯胺衍生物、聚噻吩衍生物和导电水凝胶中的至少一种。在本发明中，导电聚合物层材质的选择更有利于导电聚合物层的生物相容性，进而提高微电极的生物相容性和安全性。导电聚合物层具有良好电学性能，是生物相容性优异的软性材料，其贴合组织，降低免疫反应，提高微电极的长期安全性。因此，在枝晶铂结构30上设置导电聚合物层，“软硬结合”，进一步提高微电极的生物相容性和使用寿命。
本发明还提供了包括上述微电极的神经假体。在本发明中，神经假体可以但不限于为人工耳蜗、视神经假体、植入式心脏起博器或植入式深脑刺激器。具体的，可以但不限于为神经假体作为视神经假体时，一方面自身电学性能和生物相容性好，另一方面，如图9所示，微电极中的多焦点电极实现了真实电极通道和虚拟电极通道的多重刺激，可实现精准的神经调控，提高空间的分辨率，为高密度神经刺激和神经假体提供硬件基础。对于本发明提供的微电极，通过电场调控改变通过不同电极对上的刺激波形、幅值和电荷分配的比例。具体的，可以但不限于通过对相邻或间隔电极点的刺激电荷进行不同的分配比从0～1以0.1步长依次递增，利用电流的定向作用实现刺激焦点的动态移动，构建虚拟通道，在有限的微电极空间内，实现多通道的虚拟刺激，提高刺激效果。在本发明中，神经假体包括一个或多个上述的微电极。具体的，可以但不限于为当神经假体包括多个微电极时，多个微电极呈阵列排布，更有利于神经假体在使用过程中增加接收刺激的数量，更明显地提高分辨率。
以上所述实施例仅表达了本发明的几种实施方式，其描述较为具体和详细，但并不能因此而理解为对本发明专利范围的限制。应当指出的是，对于本领域的普通技术人员来说，在不脱离本发明构思的前提下，还可以做出若干变形和改进，这些都属于本发明的保护范围。因此，本发明专利的保护范围应以所附权利要求为准。

Claims (16)

  1. 一种微电极，其特征在于，包括柔性层、导电层和多个枝晶铂结构，所述导电层设置在所述柔性层中，所述柔性层表面上设置有多个凹槽以暴露部分所述导电层，每一所述凹槽内设置有一所述枝晶铂结构。
  2. 如权利要求1所述的微电极，其特征在于，所述枝晶铂结构上还设置有导电聚合物层，所述导电聚合物层的厚度为0.1μm-20μm。
  3. 如权利要求2所述的微电极，其特征在于，所述导电聚合物层的材质包括聚吡咯、聚苯胺、聚噻吩及其衍生物和导电水凝胶中的至少一种。
  4. 如权利要求1所述的微电极，其特征在于，相邻所述凹槽之间的间距为10μm-1000μm。
  5. 如权利要求4所述的微电极，其特征在于，相邻所述凹槽之间的间距为50μm-700μm。
  6. 如权利要求1所述的微电极，其特征在于，多个所述枝晶铂结构呈阵列排布。
  7. 如权利要求1所述的微电极，其特征在于，所述枝晶铂结构由多个枝晶铂形成，所述枝晶铂包括铂纳米线、铂纳米棒、铂纳米锥和铂纳米花中的至少一种。
  8. 如权利要求7所述的微电极，其特征在于，所述枝晶铂结构中所述枝晶铂的分布密度为10个/μm 2-300个/μm 2。
  9. 如权利要求1所述的微电极，其特征在于，所述枝晶铂结构的厚度为 0.3μm-70μm。
  10. 如权利要求1所述的微电极，其特征在于，所述导电层的厚度为0.1μm-100μm。
  11. 一种微电极的制备方法，其特征在于，包括：
    提供基底，在所述基底上制备第一柔性层；
    通过掩膜在所述第一柔性层上制备导电层；
    在所述导电层上沉积第二柔性层，所述第二柔性层部分覆盖在所述导电层表面，部分覆盖在所述第一柔性层表面；
    刻蚀所述第二柔性层以暴露部分所述导电层，并形成多个凹槽；
    去除所述基底，并在多个所述凹槽中沉积枝晶铂结构，即可得到微电极。
  12. 如权利要求11所述的微电极的制备方法，其特征在于，所述在多个所述凹槽中沉积枝晶铂结构后，还包括采用原位法或模板法在所述枝晶铂结构上沉积导电聚合物层。
  13. 如权利要求11所述的微电极的制备方法，其特征在于，所述在多个所述凹槽中沉积枝晶铂结构，包括：提供铂盐溶液，采用恒电位沉积法或恒电流沉积法在多个所述凹槽中形成所述枝晶铂结构。
  14. 如权利要求13所述的微电极的制备方法，其特征在于，所述铂盐包括氯化铂、六氯铂酸铵、六氯铂酸钾、六氯铂酸钠、氯铂酸、硝酸铂、硫酸铂、四氯铂酸钾和四氯铂酸铵中的至少一种。
  15. 如权利要求13所述的微电极的制备方法，其特征在于，所述铂盐溶液的浓度大于30mmol/L。
  16. 一种神经假体，包括如权利要求1-10任一项所述的或权利要求11-15 任一项所述的制备方法制得的微电极。
PCT/CN2019/095263 2019-07-09 2019-07-09 一种微电极及其制备方法和神经假体 WO2021003670A1 (zh)

Priority Applications (2)

Application Number Priority Date Filing Date Title
PCT/CN2019/095263 WO2021003670A1 (zh) 2019-07-09 2019-07-09 一种微电极及其制备方法和神经假体
US17/251,002 US20210260368A1 (en) 2019-07-09 2019-07-09 Microelectrode, preparation method thereof and neural prosthesis

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2019/095263 WO2021003670A1 (zh) 2019-07-09 2019-07-09 一种微电极及其制备方法和神经假体

Publications (1)

Publication Number Publication Date
WO2021003670A1 true WO2021003670A1 (zh) 2021-01-14

Family

ID=74114487

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2019/095263 WO2021003670A1 (zh) 2019-07-09 2019-07-09 一种微电极及其制备方法和神经假体

Country Status (2)

Country Link
US (1) US20210260368A1 (zh)
WO (1) WO2021003670A1 (zh)

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023187526A1 (en) * 2022-03-29 2023-10-05 Rochford Amy Elizabeth Implantable bioelectronic device and method of using same
GB2617100A (en) * 2022-03-29 2023-10-04 Elizabeth Rochford Amy Implantable bioelectronic device and method of using same
WO2024092750A1 (zh) * 2022-11-04 2024-05-10 深圳先进技术研究院 复合材料、微电极及其制备方法和应用
CN115813399A (zh) * 2022-12-08 2023-03-21 天津大学 一种纳米材料修饰的神经电极及制备方法

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101172184A (zh) * 2007-10-10 2008-05-07 中国科学院上海微系统与信息技术研究所 一种三维柔性神经微电极及制作方法
CN104548335A (zh) * 2014-12-26 2015-04-29 武汉格林泰克科技有限公司 用于生物体的植入式柔性阵列电极及其制备方法
US20170232251A1 (en) * 2005-04-28 2017-08-17 Second Sight Medical Products, Inc. Flexible Circuit Electrode Array
CN108853717A (zh) * 2018-06-19 2018-11-23 国家纳米科学中心 一种柔性神经电极以及柔性神经电极的植入方法
CN109205551A (zh) * 2018-11-01 2019-01-15 深圳先进技术研究院 一种锥形阵列柔性电极及其制备方法
CN109700453A (zh) * 2018-12-15 2019-05-03 深圳先进技术研究院 一种复合阵列电极及其制备方法和应用

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU2002305357A1 (en) * 2001-05-01 2002-11-11 Second Sight, Llc High-density array of micro-machined electrodes for neural stimulation
US20070224244A1 (en) * 2006-03-22 2007-09-27 Jan Weber Corrosion resistant coatings for biodegradable metallic implants
US8765323B2 (en) * 2007-06-12 2014-07-01 Canon Kabushiki Kaisha Membrane electrode assembly and fuel cell with dendritic shape catalyst layer
US8355768B2 (en) * 2007-12-17 2013-01-15 California Institute Of Technology Micromachined neural probes
EP3958241A1 (en) * 2013-03-12 2022-02-23 Arizona Board of Regents, a Body Corporate of the State of Arizona acting for and on behalf of Arizona State University Dendritic structures and tags
CA2996870C (en) * 2015-08-27 2019-05-07 Nissan Motor Co., Ltd. Catalyst particles, and electrode catalyst, electrolyte membrane-electrode assembly, and fuel cell using catalyst particles

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20170232251A1 (en) * 2005-04-28 2017-08-17 Second Sight Medical Products, Inc. Flexible Circuit Electrode Array
CN101172184A (zh) * 2007-10-10 2008-05-07 中国科学院上海微系统与信息技术研究所 一种三维柔性神经微电极及制作方法
CN104548335A (zh) * 2014-12-26 2015-04-29 武汉格林泰克科技有限公司 用于生物体的植入式柔性阵列电极及其制备方法
CN108853717A (zh) * 2018-06-19 2018-11-23 国家纳米科学中心 一种柔性神经电极以及柔性神经电极的植入方法
CN109205551A (zh) * 2018-11-01 2019-01-15 深圳先进技术研究院 一种锥形阵列柔性电极及其制备方法
CN109700453A (zh) * 2018-12-15 2019-05-03 深圳先进技术研究院 一种复合阵列电极及其制备方法和应用

Also Published As

Publication number Publication date
US20210260368A1 (en) 2021-08-26

Similar Documents

Publication Publication Date Title
WO2021003670A1 (zh) 一种微电极及其制备方法和神经假体
CN101172184B (zh) 一种三维柔性神经微电极及制作方法
US8010208B2 (en) Microelectrode, applications thereof and method of manufacturing
Green et al. Variation in performance of platinum electrodes with size and surface roughness
WO2009062114A2 (en) Cochlear stimulation device comprising a flexible electrode array
CN110314279A (zh) 一种微电极及其制备方法和神经假体
CN108125677A (zh) 一种微电极及其制备方法
WO2007010441A2 (en) Apparatus and method for coupling implanted electrodes to nervous tissue
Leccardi et al. Multilayer 3D electrodes for neural implants
US20230133153A1 (en) Composite array electrode, preparation method thereof and use thereof
Khudhair et al. Microelectrode arrays: architecture, challenges and engineering solutions
JP2012179333A (ja) 電極
Muguet et al. Combining PEDOT: PSS Polymer Coating with Metallic 3D Nanowires Electrodes to Achieve High Electrochemical Performances for Neuronal Interfacing Applications
CN103301576A (zh) 基于光电技术的多模态植入式神经调控电极及制作方法
Borda et al. Three-dimensional multilayer concentric bipolar electrodes restrict spatial activation in optic nerve stimulation
CN103118739B (zh) 用于电刺激神经结构的具有三维布局的植入物
US10058698B2 (en) Asymmetric cochlear implant electrodes and method
EP2394696A1 (en) Device to stimulate or record a signal to or from a living tissue
Wang et al. Flexible cylindrical neural probe with graphene enhanced conductive polymer for multi-mode BCI applications
CN218187546U (zh) 一种生物神经调控电极
CN215653437U (zh) 电极结构、人工耳蜗电极以及人工耳蜗设备
de Asis et al. Electrical stimulation of brain tissue with carbon nanofiber microbrush arrays
CN117322884A (zh) 用于癫痫疾病的长期在体双向微纳电极阵列及其制备方法
CN116271534A (zh) 用于非人灵长类动物脑深部核团双模功能定位和精准电刺激的神经微探针
CN114870247A (zh) 一种用于耳蜗核精准刺激的拟神经电极

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 19936958

Country of ref document: EP

Kind code of ref document: A1

122 Ep: pct application non-entry in european phase

Ref document number: 19936958

Country of ref document: EP

Kind code of ref document: A1

122 Ep: pct application non-entry in european phase

Ref document number: 19936958

Country of ref document: EP

Kind code of ref document: A1

32PN Ep: public notification in the ep bulletin as address of the adressee cannot be established

Free format text: NOTING OF LOSS OF RIGHTS PURSUANT TO RULE 112(1) EPC (EPO FORM 1205A DATED 05/08/2022)

122 Ep: pct application non-entry in european phase

Ref document number: 19936958

Country of ref document: EP

Kind code of ref document: A1