CN107158560A - It is controllable from deformation nerve microelectrode based on swelling behavior characteristic - Google Patents
It is controllable from deformation nerve microelectrode based on swelling behavior characteristic Download PDFInfo
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- 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
- A61N1/0526—Head electrodes
- A61N1/0541—Cochlear electrodes
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- 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
- A61N1/0526—Head electrodes
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Abstract
The invention discloses a kind of controllable deformation nerve microelectrode certainly based on swelling behavior characteristic, including：Hydrogel layer, in contact liq, hydrogel water swelling in hydrogel layer；Parylene material electrode basements, Parylene materials electrode basement is interconnected and fixed with hydrogel layer, wherein, in preset time during microelectrode is implanted into human body or after completion implantation, and during hydrogel layer water swelling, so that not expanding and Parylene material electrode basements that stress situation is different deform, so that microelectrode integrally occurs bending and deformation.The microelectrode hydrogel can be used to realizing microelectrode it is overall from flexural deformation, improve the applicability of microelectrode, the reliability of microelectrode be effectively ensured, it is simple easily to realize.
Description
Technical field
It is more particularly to a kind of based on the controllable of swelling behavior characteristic the present invention relates to medicine equipment and biological technical field
From deformation nerve microelectrode.
Background technology
Perception of the people to the world is the input based on sensory nerve, and the input of sensory nerve passes through membrane potential of neurons
Change expressed, and this electric signal is all identical on all neuronal cells in human body, no matter the signal
Purposes and producing method.Electro photoluminescence can cause human body cell excited and produce action potential, and implantable nerve prosthese can utilize electricity
The patient stimulated as nerve damage builds nerve bypass, limbs or organ of the patient again with lost contact is obtained connection
System, recovers missing function.Nerve microelectrode is then the key componentses of all kinds of nerve prosthesis, and research needs to make microactrator
Technique is combined with clinical practice.
After nerve microelectrode implantation human body, the degree of engagement of itself and nerve fiber determines its effect that can be played a role,
The global shape of microelectrode should be with needing the shape facility of implant site to match.Partes corporis humani divides organ shape different, adds
There is human body otherness between patient in itself, nerve microelectrode in addition to it should can change shape according to different clinical demands,
Also medical personnel should can be allowed to be adjusted during placing human body.
For example, the cochlea of people is one is closely wound into vertical screw cone, cochlea by the long and narrow pipeline full of lymph
There are inner hair cell and external hair cell in corti's organ on pipe basilar memebrane, the mechanical energy of lymph flow can be converted into telecommunications
Number.The hair cell of the deaf patient of severe phonosensitive nerve there is damage, it is necessary to which implantable artificial cochlea, spiral shell is implanted into by array microelectrode
In the cochlea tympanic canal for revolving shape, directly impose electro photoluminescence to substitute hair cell by the auditory nerve cell of electrode pair corresponding site
Function.Hair cell has frequency topology distribution in cochlea, i.e., different basement membrane portions is dispersed with perception different frequency acoustical signal
Hair cell, therefore by be distributed in different zones multi-channel electrode encourage, the separation of sound frequency can be realized.In theory,
Electrod-array with more multichannel and number of electrodes, using the teaching of the invention it is possible to provide higher frequency resolution；Meanwhile, microelectrode is each with basilar memebrane
The laminating situation at position can also influence effect of stimulation.
The shape of existing artificial cochlea's microelectrode has two kinds of linear pattern and Curved.Linear electrode is flexible by it,
Restricted to form helical form by cochlea shape in operation implantation process.This electrode due to natural resiliency, in cochlea with outside tympanic canal
Side forms contact, and, effect of stimulation is inferior to meander electrode apart from the basilar memebrane where nerve cell farther out.Another Curved electrode
Linear is remained by a larger filament of rigidity before implantation, metal is extracted out with progressively slow in electrode implantation process
Silk, makes electrode bending for spiral shape and is close to the basilar memebrane on the inside of tympanic canal, effect of stimulation preferably, but due to wire rigidity compared with
The probability increase of basilar memebrane is damaged in height, surgical procedure.
In another example, all optic nerve fibers of eyeball optic nerve beam upper set, optic nerve prosthese is that one kind is placed in
Artificial prosthesis on eye optic nerve beam, different from the artificial prosthesis for being currently mainly used in retina, optic nerve prosthese is to view
Film occur lesion, or even Eyeball defect patient bring part recover eyesight hope.This nerve prosthesis is needed microelectrode
Winding or lock ring also have using microneedle array formula electrode on eye optic nerve beam, by the sheath on microneedle optic tract,
Directly the optic nerve fiber of deep layer is stimulated to improve resolution ratio.Therefore, such electrode needs the base of annular in shape or oversleeve
Bottom, the Kraft electrode that conventional optic nerve prosthese is typically molded using pre-production, for the ease of operation implantation, microelectrode should be
Required shape is just voluntarily deformed into during laying human body, it also can be used for pushing away micropin from driving force produced when deforming
Enter in nerve fiber.
In correlation technique, it can be needed to be fabricated to different shape, example according to clinic in the preparation process of microelectrode
Such as a kind of preparation method of the ring-type Kraft microelectrode bent based on seif-citing rate, it is by controlling microelectrode Parylene basalises
Thickness and heat treatment condition, different Parylene layer of itself stress situation of adjustment, to realize from toroidal bend, formation Kraft
(oversleeve type) electrode.However, this method can only set the shape of microelectrode in preparation process, it is impossible to placing the process of human body
In the shape of microelectrode is adjusted, also voluntarily made a change according to local environment structure without decree microelectrode.
The content of the invention
It is contemplated that at least solving one of technical problem in correlation technique to a certain extent.
Therefore, a kind of controllable from the neural micro- electricity of deformation based on swelling behavior characteristic it is an object of the invention to propose
Pole, the microelectrode can improve the applicability of microelectrode, and the reliability of microelectrode is effectively ensured, simple easily to realize.
To reach above-mentioned purpose, the embodiment of the present invention proposes a kind of controllable from change body and the spirit based on swelling behavior characteristic
Through microelectrode, including：Hydrogel layer, in contact liq, hydrogel water swelling in the hydrogel layer；Parylene materials
Electrode basement, the Parylene materials electrode basement is interconnected and fixed with the hydrogel layer, wherein, planted in microelectrode
Enter during human body or complete in the preset time after implantation, and during the hydrogel layer water swelling so that do not expand
And the different Parylene materials electrode basement of stress situation deforms, the change so that microelectrode integrally bends
Shape.
The controllable deformation nerve microelectrode certainly based on swelling behavior characteristic of the embodiment of the present invention, people is implanted into microelectrode
During body or in the certain time of completion implantation, by hydrogel layer water swelling, so that not expanding and stress
The different Parylene material electrode basements of situation are deformed, so that microelectrode integrally occurs bending and deformation, hydrogel is used
In realize microelectrode it is overall from flexural deformation, improve the applicability of microelectrode, the reliability of microelectrode be effectively ensured, it is simple easily
Realize.
In addition, the controllable nerve microelectrode of deformation certainly according to the above embodiment of the present invention based on swelling behavior characteristic is also
There can be following additional technical characteristic：
Further, in one embodiment of the invention, according to the factors influencing deformation according to the hydrogel and institute
Particular ion concentration, acid-base value and temperature that microelectrode is implanted into environment are stated, by changing the design of material of the hydrogel, or
Species, component and synthesis condition to the hydrogel are adjusted, to obtain the hydrogel for meeting preparatory condition, to control
Make the deformation trigger condition in preset time of the microelectrode during implantation human body or after completion implantation, deflection, hold
Continuous time and the deformation velocity.
Further, in one embodiment of the invention, the thickness of the hydrogel layer is non-uniform thickness, to cause
Angle of bend, deflection, deformation direction and the shape of the microelectrode meet the first default Morph Target.
Further, in one embodiment of the invention, the thickness of the Parylene materials electrode base materials is
Non-uniform thickness, to cause angle of bend, deflection, deformation direction and the shape of the microelectrode to meet the second default Amoebida
Mark.
Further, in one embodiment of the invention, the shape and characteristic of implantation position are needed according to the microelectrode
Determine the thickness information of the hydrogel layer or/and Parylene material electrode basements so that the microelectrode be deformed into arc,
Spiral shape or circle so that the microelectrode is close to that the nerve fiber of nerve stimulation and perception need to be carried out.
Further, in one embodiment of the invention, the microelectrode according to the hydrogel layer or/and
The thickness flexure of Parylene material electrode basements is into oversleeve or annular.
Further, in one embodiment of the invention, the microelectrode by the hydrogel layer on nerve tract
Carry out grappling.
Alternatively, in one embodiment of the invention, the material of the hydrogel include polyethyleneglycol diacrylate,
Polyvinyl alcohol, bacterial fibers-polyvinyl alcohol, gelatin, sodium alginate, hyaluronic acid, agarose, chitosan, collagen, poly- methyl-prop
Olefin(e) acid hydroxyl ethyl ester, polyacrylamide, polyurethanes, polyacrylic acid, Sodium Polyacrylate, polyacrylic acid-PAA, polyoxyethylene
Alkene, Capillary electrophoresis, polyethylene glycol methacrylate-styrene polymer and polyethyleneglycol diacrylate-polyethylene glycol dimethyl
One or more in acrylate.
The additional aspect of the present invention and advantage will be set forth in part in the description, and will partly become from the following description
Obtain substantially, or recognized by the practice of the present invention.
Brief description of the drawings
Of the invention above-mentioned and/or additional aspect and advantage will become from the following description of the accompanying drawings of embodiments
Substantially and be readily appreciated that, wherein：
Fig. 1 is according to the controllable from deformation nerve microelectrode based on swelling behavior characteristic of one embodiment of the invention
Structural representation；
Fig. 2 is according to the controllable from deformation nerve microelectrode based on swelling behavior characteristic of another embodiment of the present invention
Three dimensional structure diagram；
Fig. 3 is the effect diagram of the flexural deformation according to one embodiment of the invention；
Fig. 4 is to wale nerve tract schematic diagram according to the microelectrode of one embodiment of the invention；
Fig. 5 be according to the microelectrode of one embodiment of the invention deform after can be in irregular shape schematic diagram；
The spiral shell that it can be zero in the variable pitch of radius of curvature after being deformed according to the microelectrode of one embodiment of the invention that Fig. 6, which is,
Revolve shape schematic diagram；
Fig. 7 is to be shown according to microelectrode example variations pre-structure and electrode basement the layer groove structure of one embodiment of the invention
It is intended to；
Fig. 8 is that can deform schematic diagram in the shape of a spiral after being deformed according to the microelectrode of one embodiment of the invention；
Fig. 9 is that spiral taper is presented according to the microelectrode of one embodiment of the invention to deform schematic diagram；
Figure 10 is shallow grooves or cut layout side on Parylene layers or hydrogel layer according to one embodiment of the invention
Formula schematic diagram；
Figure 11 is the Parylene electrode basements layer groove structure perspective diagram according to one embodiment of the invention；
Figure 12 is shallow grooves layout type control deformation rotation direction signal on the hydrogel layer according to one embodiment of the invention
Figure.
Embodiment
Embodiments of the invention are described below in detail, the example of the embodiment is shown in the drawings, wherein from beginning to end
Same or similar label represents same or similar element or the element with same or like function.Below with reference to attached
The embodiment of figure description is exemplary, it is intended to for explaining the present invention, and be not considered as limiting the invention.
The controllable deformation certainly based on swelling behavior characteristic proposed according to embodiments of the present invention is described with reference to the accompanying drawings
Nerve microelectrode.
Fig. 1 is the controllable from the structure for deforming nerve microelectrode based on swelling behavior characteristic of one embodiment of the invention
Schematic diagram.
As shown in figure 1, should be included based on the controllable of swelling behavior characteristic from deformation nerve microelectrode：Hydrogel layer 100
With Parylene materials electrode basement 200.
Wherein, in contact liq, hydrogel water swelling in hydrogel layer 100.Parylene materials electrode basement 200
Interconnected with hydrogel layer 100 and fixed, wherein, the preset time during microelectrode is implanted into human body or after completion implantation
It is interior, and during 100 water swelling of hydrogel layer so that not expand and Parylene material electrode basements that stress situation is different
200 deform, so that microelectrode integrally occurs bending and deformation.Hydrogel can be used for real by the microelectrode of the embodiment of the present invention
Existing microelectrode it is overall from flexural deformation, improve the applicability of microelectrode, the reliability of microelectrode be effectively ensured, it is simple easily real
It is existing.It should be noted that preset time can be configured according to actual conditions.
It is understood that the swelling character that hydrogel has, makes it can voluntarily to perceive context bar as one kind
Part simultaneously responds the material for changing own form and property, can be considered a kind of intellectual material.As a kind of hydrogel covering exists
Mechanical connection manner on electrode contacts, for artificial cochlea's microelectrode array, using have the hydrogel of biocompatibility as
From electrode contacts electric charge is transmitted to the material of neighbouring nerve fiber, it is to avoid metal electrode contact directly contacts shape with tissue
Into fibr tissue layer, but it mainly realizes that hydrogel coating is certainly solid on electrode contacts using the swelling character of hydrogel
It is fixed, expanded using hydrogel in the case where being acted on by i-coch perilymph strong to increase its connection with microelectrode array
Degree, not by hydrogel be used to realizing microelectrode it is overall from flexural deformation.
Specifically, hydrogel is combined during Parylene material nerve microelectrode arrays are prepared turns into combination electrode
Material, realizes that microelectrode integrally bends or deformed using the swelling character of hydrogel.The embodiment of the present invention can make nerve micro-
Electrode place human body during or implantation after the completion of certain time in have it is controllable from deformation characteristic, can be according to reality
Clinical demand, controls microelectrode from the trigger condition deformed, deflection by adjusting the influence factor of hydrogel deformation, continues
Time and deformation velocity, therefore be applied to but be not limited to following several applications：Artificial cochlea electrode deforms with implantation process
To adapt to the spiral-shaped of cochlea chamber, the grappling that the microelectrode, microelectrode of winding on the optic nerve are on nerve tract and provide
Driving force pushes microneedle array and is pierced into nerve fiber.
Further, in one embodiment of the invention, according to the factors influencing deformation according to the hydrogel and micro-
The information such as particular ion concentration, acid-base value and the temperature of electrode implantation environment, by changing the design of material of hydrogel, or it is right
Species, component and the synthesis condition of hydrogel are adjusted, to obtain the hydrogel for meeting preparatory condition, to control microelectrode to exist
It is implanted into during human body or completes deformation trigger condition, deflection, duration and deformation speed in the preset time after implantation
Degree.
Specifically, Capillary electrophoresis (NIPAAm) is a kind of all more quick to temperature, acid-base value and ion concentration
The hydrogel material of sense, can expand or shrink when above-mentioned condition changes.By using NIPAAm gels, or by itself and its
He carries out copolymerization by gel, can obtain the sensitive hydrogel material of temperature, acid-base value and ion concentration to body fluid.Use this kind
Gel is as the material of 100 layers of hydrogel, and the electrode is when entering fluid environment, due to where before above-mentioned condition and electrode
Liquid environment is different, and gel is expanded or shunk, so that microelectrode starts deformation.
Specifically, HEMA is a hydrogel material that class hydrophily is weaker, water absorption rate is relatively low.Use the HEMA of different-thickness
Hydrogel material as hydrogel layer 100 external sheath material, it is possible to the absorption speed of the overall hydrogel layer 100 of control,
The deformation velocity of overall microelectrode is controlled so as to realize.
It is understood that the covering material of hydrogel layer 100 is not necessarily a kind of hydrogel material or other
Material, such as can be with materials such as the gelatin of degradation in vivo, chitosan, collagen, PLAs.External sheath material can be both
Play a part of slowing down or prevent hydrogel layer 100 from absorbing water, can keep overall microelectrode rigidity value moderate before being degraded again,
It is easy to the progress of implant surgery.After implant surgery is completed, as cladding material is degraded, electrode gradually starts deformation.If bag
The water suction of hydrogel layer 100 can be slowed down by covering material, then can be by the deformation of the thickness control microelectrode for controlling covering material
Speed., can be by controlling the thickness of covering material accurately to adjust if covering material can obstruct the water suction of hydrogel layer 100
Time needed for its whole degraded, so that the time that accurate coordination electrode deforms.
Specifically, PEGDA is the conventional hydrogel material of a class.The water imbibition and modulus of elasticity of PEGDA hydrogel materials
It is relevant with the molecular weight of gel performed polymer material.Performed polymer molecular weight is bigger, and the hydrogel material water imbibition after copolymerization is stronger, together
When elasticity modulus of materials it is smaller.Therefore it can be controlled by adjusting ratio of the performed polymer material of different molecular weight in performed polymer
The water imbibition and modulus of elasticity of hydrogel material after copolymerization processed.
Specifically, using two kinds of gel performed polymer material copolymerization of HEMA and PEGDA it is the conventional side that manufactures hydrogel material
Method.Wherein HEMA water imbibitions are weak and PEGDA water imbibitions are strong, therefore by adjusting group of two kinds of materials in copolymer hydrogel material
The method of point ratio can just be realized deforms the duration and deformation velocity is entered to the absorption speed of newly-generated hydrogel material
Row control.
It should be noted that because HEMA is weak compared with PEGDA water imbibitions, modulus of elasticity is low, therefore with reference to above two method,
I.e. while ratio of the PEGDA performed polymers of adjustment HEMA performed polymers and different molecular weight in overall performed polymer material, just energy is real
Now the water imbibition and modulus of elasticity to final hydrogel material are individually controlled.For example increase HEMA and macromolecule simultaneously
The ratio of PEGDA performed polymers, can reduce the modulus of elasticity of final hydrogel material while keeping water imbibition constant.
Further, in one embodiment of the invention, the thickness of hydrogel layer 100 is non-uniform thickness, to cause
Angle of bend, deflection, deformation direction and the shape of microelectrode meet the first default Morph Target.It should be noted that first
Default Morph Target can be configured by those skilled in the art according to actual conditions, be not specifically limited herein.
It is understood that hydrogel thickness is non-homogeneous layout, thus make the angle of bend, deflection, deformation of electrode
Direction, shape can be adjusted according to clinical demand.
In addition, in one embodiment of the invention, the thickness of Parylene materials electrode basement 200 is non-homogeneous thickness
Degree, to cause angle of bend, deflection, deformation direction and the shape of microelectrode to meet the second default Morph Target.Need explanation
, second, which presets Morph Target, to be configured by those skilled in the art according to actual conditions, do not make specific limit herein
System.
It should be noted that default Morph Target can be configured according to actual conditions, it is not specifically limited herein, and
And Parylene layers of non-uniform thickness are identical with hydrogel layer non-uniform thickness mechanism, and the change of overall microelectrode can be implemented separately
Shape, both approaches can also be used simultaneously.
Further, in one embodiment of the invention, the shape and characteristic for needing implantation position according to microelectrode are determined
The thickness information of hydrogel layer 100 or/and Parylene materials electrode basement 200, so that microelectrode is deformed into arc, spiral shape
Or it is circular so that microelectrode is close to that the nerve fiber of nerve stimulation and perception need to be carried out.
That is, institute can be obtained by changing thickness, shape and the layout designs of Parylene substrates and electrode etc.
The deformation needed.
Specifically, it can be in irregular shape to be laid out containing non-uniform thickness after the deformation of the microelectrode of hydrogel layer 100, including arc
Shape, spiral shape and circle, the shape and characteristic for needing implantation position according to microelectrode are designed, and microelectrode can be made to be close to need to carry out
Nerve stimulation and the nerve fiber of perception.
Further, in one embodiment of the invention, microelectrode is according to hydrogel layer 100 or/and Parylene materials
The thickness flexure of matter electrode basement 200 is into oversleeve or annular.
It is understood that the microelectrode of aqueous gel layer 100 is flexible into oversleeve or annular, be suitable for needing lock ring or
Wind the nerve stimulation or perception of nerve tract.
Further, in one embodiment of the invention, microelectrode carries out anchor by hydrogel layer 100 on nerve tract
It is fixed.Say, the hydrogel layer 100 of microelectrode could be applicable to grappling of the microelectrode on nerve tract, not be described in detail herein.
Alternatively, in one embodiment of the invention, the material of hydrogel includes polyethyleneglycol diacrylate, poly- second
Enol, bacterial fibers-polyvinyl alcohol, gelatin, sodium alginate, hyaluronic acid, agarose, chitosan, collagen, polymethylacrylic acid
Hydroxyl ethyl ester, polyacrylamide, polyurethanes, polyacrylic acid, Sodium Polyacrylate, polyacrylic acid-PAA, polyethylene glycol oxide,
Capillary electrophoresis, polyethylene glycol methacrylate-styrene polymer and polyethyleneglycol diacrylate-polyethylene glycol dimethyl allene
One or more in acid esters.
It should be noted that electrode base materials are not limited to parylene materials, it is any being capable of phase with hydrogel material
The fixed material of fixed can.
That is, being included but is not limited to using hydrogel material：Polyethyleneglycol diacrylate (PEGDA), polyethylene
Alcohol (PVA), bacterial fibers-polyvinyl alcohol (BC-PVA), gelatin, sodium alginate, hyaluronic acid, agarose, chitosan, collagen,
Poly hydroxy ethyl acrylate (PHEMA/HEMA), polyacrylamide (PAAM/PAM), polyurethanes (PU), polyacrylic acid
(PAAc), Sodium Polyacrylate (PAAs/PAA-Na), polyacrylic acid-PAA, polyethylene glycol oxide (PEO), poly- N isopropyls third
Acrylamide (NIPAAm/PNIPA), polyethylene glycol methacrylate-styrene polymer (PEGMA), polyethyleneglycol diacrylate-polyethylene glycol
Dimethylacrylate (PEGMA-co-PEGDMA).Using above-mentioned material by being mutually mixed or entering as matrix with other materials
Row scion grafting is modified the hydrogel material to be formed from contained by deformation poll.
Specifically, hydrogel layer 100 as whole electrode bottom, Parylene materials as nerve microelectrode base
Bottom materials are located on hydrogel, and both interconnect and fixed, and form implantable nerve micro- electricity of the tool from flexural deformation characteristic
The substrate of pole.Context and the characteristic responded can be perceived using hydrogel, the hydrogel layer 100 of tool biocompatibility exists
The masterpiece produced in meeting water swelling when contacting body fluid during microelectrode implantation human body, expansion process is driving force, and order is not
Expand and Parylene materials electrode basement 200 that stress situation is different deforms, so that microelectrode is overall in spy
Determine voluntarily bend under environment.
In an embodiment of the present invention, make use of swelling behavior characteristic, by according to around microelectrode it is extra it is specific from
Sub- concentration, acid-base value, temperature isoconcentration situation, are pre-designed water-setting and compose and deform trigger condition, utilize the change of hydrogel
Shape responds factor to control the shape and property of hydrogel layer 100, during implantation human body or can complete certain after implantation
Trigger condition, deflection, duration and the speed of expansion of control hydrogel expansion process in time.Microelectrode contains hydrogel
With Parylene, wherein stress of the hydrogel during moisture expantion can change, and utilize the stress variation of two kinds of materials
The difference of situation, is deformed microelectrode overall structure.Hydrogel thickness is non-homogeneous layout, thus makes the angle of bend of electrode
Degree, deflection, deformation direction, shape can be adjusted according to clinical demand.Non-uniform thickness is laid out micro- electricity of hydrogel layer 100
Irregular shape, including arc, spiral shape and circle can be presented after the deformation of pole, shape and the spy of implantation position are needed according to microelectrode
Property is designed, and microelectrode can be made to be close to that the nerve fiber of nerve stimulation and perception need to be carried out.Meanwhile, also avoid prebuckling electrode
Complicated implantation require.The thickness proportion of Parylene layers or hydrogel layer 100 is not necessarily by 1:1 arrangement, according to deformation institute
The direction and deflection needed can have the layout of different proportion in horizontal or vertical direction, by changing Parylene substrates and electrode
Deng thickness, shape and layout designs obtain required for deformation.
The embodiment of the present invention can be used in the microelectrode array of artificial cochlea, can be according to residing spiral after implantation cochlear duct
Taper pipeline environment voluntarily adjusts shape, to improve effect of being fitted with each position of nerve fiber.According to the shape that need to be bent, micro- electricity
The Parylene layers or hydrogel layer 100 of pole are present on multiple shallow grooves or cut, microelectrode on along the longitudinal direction along longitudinal side
Deflection to each position is different, so as to produce the shape of helix-coil；And Parylene layers or/and hydrogel layer
100 is uneven along the thickness layout in the vertical or horizontal direction of microelectrode, thus makes microelectrode from can present and do not advise when deforming
Then bend, such as thus vertical helicon is suitable for the shape that cochlear duct is long and narrow and is closely wound.
When in the microneedle array formula electrode for optic nerve prosthese, the embodiment of the present invention can be used as microneedle array electrode
Substrate, from deformation after winding or lock ring on eye optic nerve beam, by the sheath on microneedle optic tract, directly to depth
The optic nerve fiber of layer is stimulated.Not pre-production is molded the microelectrode shape of the embodiment of the present invention, can be in implant
During make the substrate of microelectrode voluntarily deform annular in shape or oversleeve, lock ring or can be wrapped on nerve tract, meanwhile, it is from becoming
Produced driving force also can be used for micropin being pushed into nerve fiber during shape.And when the microelectrode of ring-type or oversleeve is with water-setting
The expansion of glue and bend, gradually banding is on nerve tract for the tensile force that can be produced, and the deflection of hydrogel is bigger, then lock ring
Power it is also bigger, so as to form the effect from grappling.
Triggered time, duration and the speed of expansion of microelectrode can be according to actual clinical demands, in the mistake of implantation human body
Its shape is voluntarily adjusted in journey, the structure of local environment is adapted to, it is ensured that the compactness with nerve fiber need to be stimulated；Has bio-compatible
Property hydrogel layer 100 microelectrode implantation human body during contact body fluid when occur water swelling, with that will not expand
Parylene layers be connected in the state of, under both different stress situations effects, make microelectrode integrally bend change
Shape；The shape and property of hydrogel layer 100 are controlled by adjusting the deformation response factor of hydrogel, microelectrode is can control overall
Deflection and deforming depth.The situations such as particular ion concentration, acid-base value, the temperature of environment are implanted into according to electrode, by changing
The design of material of hydrogel, or hydrogel species, component and synthesis condition are adjusted, the hydrogel of performance needed for obtaining,
Deformation triggered time, duration and deformation velocity that can be with coordination electrode during implantation human body.
Microelectrode containing hydrogel can be during microelectrode places human body to its angle of bend, deforming depth, change
Shape direction, shape, deformation triggered time, duration and speed etc. are adjusted.Microelectrode is flexible into oversleeve or annular, its
Not pre-production is molded shape, but the nerve fiber that need to be stimulated voluntarily is wound in placement process, is suitable for needing lock ring
The nerve stimulation or perception of nerve tract.The embodiment of the present invention is applied to meet the nerve stimulation of implantation human body or perceives demand, also
Grappling of the microelectrode on nerve tract is applicable to, and driving force push microneedle array piercing nerve fiber is provided.
The hydrogel layer 100 of microelectrode possesses good bio-compatibility and is difficult to be degraded or absorbed by human body, makes micro- electricity
Pole implantation human body after can long-term role, use hydrogel material to include but is not limited to：Polyethyleneglycol diacrylate
(PEGDA), polyvinyl alcohol (PVA), bacterial fibers-polyvinyl alcohol (BC-PVA), gelatin, sodium alginate, hyaluronic acid, agar
Sugar, chitosan, collagen, poly hydroxy ethyl acrylate (PHEMA/HEMA), polyacrylamide (PAAM/PAM), polyurethanes
(PU), polyacrylic acid (PAAc), Sodium Polyacrylate (PAAs/PAA-Na), polyacrylic acid-PAA, polyethylene glycol oxide
(PEO), Capillary electrophoresis (NIPAAm/PNIPA), polyethylene glycol methacrylate-styrene polymer (PEGMA), polyethylene glycol two
Acrylate-polyethylene glycol dimethacrylate (PEGMA-co-PEGDMA).Passed through with above-mentioned material mutual with other materials
Mixing carries out scion grafting modification as matrix, is formed from the hydrogel material contained by deformation poll.
In one particular embodiment of the present invention, by hydrogel layer 100 and Parylene materials microelectrode substrates 200 with
A variety of different concrete modes are laminated, and the linear structure represented in Fig. 1 is one of which embodiment, hydrogel layer
100 are closely attached and fixed with Parylene layers, when the microelectrode of aqueous gel is implanted into human body and exposes to the open air in body fluid, water
Moisture expantion phenomenon will occur for gel layer 100, and its shape and itself stress situation change, as shown in Figures 2 and 3.By
It will not be deformed in the Parylene layers for being closely attached and fixing with hydrogel, microelectrode integrally can not equably expand,
Hydrogel basad top will promote Parylene layers to bend when expanding, so as to make microelectrode overall in implantation human body
During deform, by changing thickness, shape and the layout designs of Parylene substrates and electrode etc., oversleeve shape can be obtained
Or the microelectrode array of different shapes such as ring-type, as shown in Figure 4.Resulting microelectrode can be used for waling or being wrapped in nerve tract
On, to be stimulated or to be perceived, when the microelectrode of ring-type or oversleeve bends with the expansion of hydrogel, it can produce
Gradually banding is on nerve tract for tensile force, and the deflection of hydrogel is bigger, and the power of this lock ring is also bigger, therefore hydrogel layer
100 could be applicable to grappling of the microelectrode on nerve tract, and provide driving force push microneedle array piercing nerve fiber, such as
Shown in Fig. 5.
In implementation process, microelectrode adapts to the shape that microelectrode lays space from that can be presented irregular curved when deforming,
Such as arc, spiral shape and circle.As shown in fig. 6, the width and thickness of hydrogel layer 100 are uniformly distributed along y direction, electrode
Basalis is symmetrical on y direction, and is become narrow gradually along y direction width, makes after microelectrode deformation along y direction
The helical form that the pitch tapered into radius of curvature is zero.Further, in Parylene electrode basements layer or hydrogel layer
Shallow grooves or cut can be processed on 100, angle between each shallow grooves or the depth and transverse axis of cut, is distributed along the longitudinal axis
Density can be also designed as needed.As shown in the upper figures of Fig. 7, the angle and density of the groove on electrode basement layer are along longitudinal axis side
To being uniformly distributed, microelectrode is as shown in Fig. 7 figure below before deformation.As shown in figure 8, being in after microelectrode deformation as shown in Fig. 7 figure below
Radius of curvature and the equally distributed helical form of pitch, including electrode contacts, electrode basement layer groove structure end face, electrode base
Bottom and water-setting material layer.According to the shape of cochlea cavity body structure in the appropriate groove structure of electrode basement layer design, it can make micro-
Electrode can be curled into vertical spiral cone structure, adapt to the shape that cochlea cavity is long and narrow and is closely wound, as shown in Figure 9.Wherein
Structure after electrode basement layer deformation and the transparent effect in microelectrode entirety are as shown in Figure 10 and Figure 11.Utilize hydrogel layer
Upper shallow grooves layout type realizes the artificial cochlea electrode of conical helix shape and controls implementation such as Figure 12 institutes of the hand of spiral
Show.
The situation such as the particular ion concentration of context, acid-base value, temperature after being implanted into according to microelectrode, can be by changing water
The design of material of gel, or hydrogel species, component, synthesis and deformation trigger condition are adjusted, performance needed for obtaining
Hydrogel, then deformation triggered time, duration and deformation velocity that can be with coordination electrode during implantation human body, utilizes water
The deformation response factor of gel controls the shape and property of hydrogel coating.
According to embodiments of the present invention is controllable from deformation nerve microelectrode based on swelling behavior characteristic, is planted in microelectrode
Enter during human body or complete in the certain time after implantation, by hydrogel layer water swelling, so that not expanding
And the different Parylene material electrode basements of stress situation deform, so that microelectrode integrally occurs bending and deformation, by water
Gel be used to realizing microelectrode it is overall from flexural deformation, improve the applicability of microelectrode, the reliability of microelectrode be effectively ensured,
It is simple easily to realize.
In the description of the invention, it is to be understood that term " " center ", " longitudinal direction ", " transverse direction ", " length ", " width ",
" thickness ", " on ", " under ", "front", "rear", "left", "right", " vertical ", " level ", " top ", " bottom " " interior ", " outer ", " up time
The orientation or position relationship of the instruction such as pin ", " counterclockwise ", " axial direction ", " radial direction ", " circumference " be based on orientation shown in the drawings or
Position relationship, is for only for ease of the description present invention and simplifies description, rather than indicate or imply that the device or element of meaning must
There must be specific orientation, with specific azimuth configuration and operation, therefore be not considered as limiting the invention.
In addition, term " first ", " second " are only used for describing purpose, and it is not intended that indicating or implying relative importance
Or the implicit quantity for indicating indicated technical characteristic.Thus, define " first ", the feature of " second " can express or
Implicitly include at least one this feature.In the description of the invention, " multiple " are meant that at least two, such as two, three
It is individual etc., unless otherwise specifically defined.
In the present invention, unless otherwise clearly defined and limited, term " installation ", " connected ", " connection ", " fixation " etc.
Term should be interpreted broadly, for example, it may be fixedly connected or be detachably connected, or integrally；Can be that machinery connects
Connect or electrically connect；Can be joined directly together, can also be indirectly connected to by intermediary, can be in two elements
The connection in portion or the interaction relationship of two elements, unless otherwise clear and definite restriction.For one of ordinary skill in the art
For, the concrete meaning of above-mentioned term in the present invention can be understood as the case may be.
In the present invention, unless otherwise clearly defined and limited, fisrt feature can be with "above" or "below" second feature
It is that the first and second features are directly contacted, or the first and second features pass through intermediary mediate contact.Moreover, fisrt feature exists
Second feature " on ", " top " and " above " but fisrt feature are directly over second feature or oblique upper, or be merely representative of
Fisrt feature level height is higher than second feature.Fisrt feature second feature " under ", " lower section " and " below " can be
One feature is immediately below second feature or obliquely downward, or is merely representative of fisrt feature level height less than second feature.
In the description of this specification, reference term " one embodiment ", " some embodiments ", " example ", " specifically show
The description of example " or " some examples " etc. means to combine specific features, structure, material or the spy that the embodiment or example are described
Point is contained at least one embodiment of the present invention or example.In this manual, to the schematic representation of above-mentioned term not
Identical embodiment or example must be directed to.Moreover, specific features, structure, material or the feature of description can be with office
Combined in an appropriate manner in one or more embodiments or example.In addition, in the case of not conflicting, the skill of this area
Art personnel can be tied the not be the same as Example or the feature of example and non-be the same as Example or example described in this specification
Close and combine.
Although embodiments of the invention have been shown and described above, it is to be understood that above-described embodiment is example
Property, it is impossible to limitation of the present invention is interpreted as, one of ordinary skill in the art within the scope of the invention can be to above-mentioned
Embodiment is changed, changed, replacing and modification.
Claims (8)
1. it is a kind of controllable from deformation nerve microelectrode based on swelling behavior characteristic, it is characterised in that including：
Hydrogel layer, in contact liq, hydrogel water swelling in the hydrogel layer；
Parylene material electrode basements, the Parylene materials electrode basement is interconnected and consolidated with the hydrogel layer
It is fixed, wherein, in the preset time during microelectrode is implanted into human body or after completion implantation, and the hydrogel layer water swelling
When so that do not expand and the Parylene materials electrode basement that stress situation is different deforms, so that described micro-
Electrode integrally occurs bending and deformation.
2. it is according to claim 1 controllable from deformation nerve microelectrode based on swelling behavior characteristic, it is characterised in that
Particular ion concentration, acid-base value and the temperature of environment are implanted into according to the factors influencing deformation of the hydrogel and the microelectrode
Degree, is adjusted by changing the design of material of the hydrogel, or to the species, component and synthesis condition of the hydrogel,
To obtain the hydrogel for meeting preparatory condition, after controlling the microelectrode during implantation human body or complete implantation
Deformation trigger condition, deflection, duration and the deformation velocity in preset time.
3. it is according to claim 1 controllable from deformation nerve microelectrode based on swelling behavior characteristic, it is characterised in that
The thickness of the hydrogel layer is non-uniform thickness, to cause angle of bend, deflection, deformation direction and the shape of the microelectrode
Shape meets the first default Morph Target.
4. it is according to claim 1 controllable from deformation nerve microelectrode based on swelling behavior characteristic, it is characterised in that
The thickness of the Parylene materials electrode basement is non-uniform thickness, with cause the angle of bend of the microelectrode, deflection,
Deformation direction and shape meet the second default Morph Target.
5. controllable from deformation nerve microelectrode based on swelling behavior characteristic according to claim 3 or 4, its feature exists
In needing the shape and characteristic of implantation position to determine the hydrogel layer or/and Parylene material electrodes according to the microelectrode
The thickness information of substrate, so that the microelectrode is deformed into arc, spiral shape or circle so that the microelectrode is close to need to carry out
Nerve stimulation and the nerve fiber of perception.
6. controllable from deformation nerve microelectrode based on swelling behavior characteristic according to claim 3 or 4, its feature exists
In, the microelectrode according to the hydrogel layer or/and the thickness flexure of Parylene material electrode basements into oversleeve or annular.
7. it is according to claim 1 controllable from deformation nerve microelectrode based on swelling behavior characteristic, it is characterised in that
The microelectrode carries out grappling by the hydrogel layer on nerve tract.
8. it is according to claim 1 controllable from deformation nerve microelectrode based on swelling behavior characteristic, it is characterised in that
The material of the hydrogel includes polyethyleneglycol diacrylate, polyvinyl alcohol, bacterial fibers-polyvinyl alcohol, gelatin, alginic acid
Sodium, hyaluronic acid, agarose, chitosan, collagen, poly hydroxy ethyl acrylate, polyacrylamide, polyurethanes, polypropylene
Acid, Sodium Polyacrylate, polyacrylic acid-PAA, polyethylene glycol oxide, Capillary electrophoresis, polyethylene glycol metering system
One or more in acid esters and polyethyleneglycol diacrylate-polyethylene glycol dimethacrylate.
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| CN107670120A (en) * | 2017-11-20 | 2018-02-09 | 中南大学 | A kind of implanted neural microelectrode wire and preparation method thereof |
| CN110819183A (en) * | 2019-12-02 | 2020-02-21 | 苏州凝智新材料发展有限公司 | Hydrophilic lubricating coating for medical equipment and preparation method thereof |
| CN111657937A (en) * | 2020-06-12 | 2020-09-15 | 西北工业大学 | Three-dimensional flexible neural microelectrode based on self-expanding hydrogel and preparation method thereof |
| CN112537095A (en) * | 2020-11-26 | 2021-03-23 | 北京工业大学 | Water absorption negative expansion lattice of hydrogel-based composite material structure beam based on solution driving and deformation method thereof |
| CN112869747A (en) * | 2019-11-29 | 2021-06-01 | 清华大学 | Microelectrode, manufacturing method and using method thereof, plug device and microelectrode system |
| CN115227869A (en) * | 2022-08-15 | 2022-10-25 | 浙江大学 | Cochlear implant electrode with functions of neural stem cell transplantation and signal conduction enhancement and preparation method thereof |
| WO2022228366A1 (en) * | 2021-04-30 | 2022-11-03 | 微创投资控股有限公司 | Cochlear implantation device and cochlea implant |
| WO2023186052A1 (en) * | 2022-04-02 | 2023-10-05 | 北京智冉医疗科技有限公司 | Implantable stretchable flexible neural electrode, electrode group, and electrode array |
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| CN107670120A (en) * | 2017-11-20 | 2018-02-09 | 中南大学 | A kind of implanted neural microelectrode wire and preparation method thereof |
| CN112869747A (en) * | 2019-11-29 | 2021-06-01 | 清华大学 | Microelectrode, manufacturing method and using method thereof, plug device and microelectrode system |
| CN110819183A (en) * | 2019-12-02 | 2020-02-21 | 苏州凝智新材料发展有限公司 | Hydrophilic lubricating coating for medical equipment and preparation method thereof |
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| CN112537095A (en) * | 2020-11-26 | 2021-03-23 | 北京工业大学 | Water absorption negative expansion lattice of hydrogel-based composite material structure beam based on solution driving and deformation method thereof |
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| WO2022228366A1 (en) * | 2021-04-30 | 2022-11-03 | 微创投资控股有限公司 | Cochlear implantation device and cochlea implant |
| WO2023186052A1 (en) * | 2022-04-02 | 2023-10-05 | 北京智冉医疗科技有限公司 | Implantable stretchable flexible neural electrode, electrode group, and electrode array |
| CN115227869A (en) * | 2022-08-15 | 2022-10-25 | 浙江大学 | Cochlear implant electrode with functions of neural stem cell transplantation and signal conduction enhancement and preparation method thereof |
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