Neuroelectric signal acquisition and stimulation unit capable of shortening implantation time

Abstract

The utility model relates to the field of brain electrodes, in particular to an electroneurographic signal acquisition and stimulation unit capable of shortening implantation duration, which comprises an electrode wire, an electroneurographic signal acquisition and stimulation unit and an electroneurographic signal acquisition and stimulation unit, the curing assembly is used for wrapping and restraining the roots of the electrode wires, so that the adjacent electrode wires are kept parallel to each other; the shaping part is made of a material which can be dissolved in the process of implanting the electrode wire into the brain area and is used for being solidified at the connecting part of the solidifying assembly and the electrode wire so as to wrap and restrain the electrode wire; wherein the part, exposed on the outer side of the shaping piece, of the electrode wire is straight, the part, restrained on the inner side of the shaping piece, of the electrode wire is bent, and the electrode wire has the elastic force for restoring to be straight after being released from the inner side of the shaping piece. According to the embodiment of the utility model, on the premise that the length of the electrode wire is not shortened, the length of the shaping piece is shortened, so that the speed of completely dissolving the shaping piece is accelerated, and the total time of implanting the electrode wire is further reduced.

Description

Technical Field

[0001] This invention relates to the field of brain electrodes, specifically to a neural electrical signal acquisition and stimulation unit that can shorten the implantation time. Background Technology

[0002] The basic principle of microfilament electrodes is to use a fine electrode wire with an insulating layer. One end is connected to a back-end device with an amplifier, and the other end is directly inserted into the cell. The weak current signal of the neuron is transmitted to the back-end device for amplification and processing, thereby collecting the neuron's firing signal. Microfilament electrodes can be used in combination with optical fibers and drug delivery tubes to expand their functions.

[0003] To facilitate the implantation of soft microwire electrodes deep into the brain, existing microwire electrodes are wrapped with a soluble shaping element. This shaping element is used to constrain the shape of the microwire electrode, ensuring that the microwire electrode located on the outer side of the brain region does not bend during implantation.

[0004] However, because the microwire electrode is relatively long, while the shaping element is only slightly shorter than the microwire electrode, and the shaping element dissolves more slowly, the microwire electrode needs to wait for the shaping element to completely dissolve before it can be implanted into the brain region at the predetermined depth, resulting in a longer implantation time for the microwire electrode. Utility Model Content

[0005] The purpose of this invention is to provide a neural electrical signal acquisition and stimulation unit that can shorten the implantation time, in order to solve the problem that the slow dissolution rate of the shaping component leads to a long implantation time for the microwire electrode.

[0006] To solve the above-mentioned technical problems, this utility model specifically provides the following technical solution:

[0007] A neural electrical signal acquisition and stimulation unit capable of shortening implantation time includes: an electrode wire for insertion into the brain tissue of a test subject; a curing component for wrapping and constraining the root of the electrode wire, so that adjacent electrode wires remain parallel to each other; and a shaping member made of a material that dissolves during the implantation of the electrode wire into the brain region, for curing at the connection between the curing component and the electrode wire to wrap and constrain the electrode wire, so that the electrode wire maintains a predetermined shape during insertion into the test subject; wherein the portion of the electrode wire exposed outside the shaping member is straight, the portion of the electrode wire constrained inside the shaping member is curved, and the electrode wire has an elasticity to return to straightness after being released from the inside of the shaping member.

[0008] Furthermore, the surface of the electrode wire is covered with an insulating layer.

[0009] Furthermore, the tip of the electrode wire has an exposure point, which exposes the conductive portion of the electrode wire to the outside of the insulating layer.

[0010] Furthermore, it also includes electrode terminals for connecting each of the electrode wires to the subsequent equipment.

[0011] Furthermore, the curing assembly includes a cubic root component, with the electrode terminals embedded inside the root component and the plug portion of the electrode terminals exposed outside the root component.

[0012] Furthermore, a head component extends vertically from the center of the root component, and one end of the electrode wire passes through the head component and the root component and is connected to the electrode terminal.

[0013] Furthermore, the outer wall of the root component at the end away from the head component is covered by a housing.

[0014] Furthermore, the material of the shaping component is a material that can be cured at low temperatures and dissolved in water.

[0015] Furthermore, the electrode wire is a nickel-titanium alloy wire with a diameter of 5-100 micrometers.

[0016] Furthermore, the insulating layer is made of a biocompatible flexible thin film material.

[0017] Compared with the prior art, this application has the following advantages:

[0018] This invention provides a neural electrical signal acquisition and stimulation unit that can shorten the implantation time. The embodiment of this invention aims to shorten the length of the shaping component without shortening the length of the electrode wire, thereby accelerating the complete dissolution of the shaping component and reducing the total implantation time of the electrode wire. When the tip of the electrode wire passes through the cerebral cortex, it leaves a straight perforation. After the subsequent electrode wire is released from the inside of the shaping component, it also returns to a straight posture and is implanted deep into the brain region along the straight perforation. This allows the electrode wire to maintain a straight posture deep in the brain region, so that the shape of the electrode wire inside the shaping component does not affect the implantation position, implantation posture, and implantation depth of the electrode wire. Attached Figure Description

[0019] To more clearly illustrate the embodiments of this utility model or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings in the following description are merely exemplary, and those skilled in the art can derive other embodiments based on the provided drawings without creative effort.

[0020] Figure 1This is a perspective view of the concealed shaping component of this utility model;

[0021] Figure 2 This is a perspective view of the present utility model;

[0022] Figure 3 This is a side view of the present invention;

[0023] Figure 4 for Figure 3 A cross-sectional view along the AA direction;

[0024] The labels in the diagram represent the following:

[0025] 1-Electrode wire; 2-Curing component; 21-Root component; 22-Head component; 23-Housing; 3-Shaping component; 4-Electrode terminal. Detailed Implementation

[0026] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0027] Figure 1 A three-dimensional diagram of a neural electrical signal acquisition and stimulation unit that can shorten implantation time is shown. Figure 2 A three-dimensional diagram of a neural electrical signal acquisition and stimulation unit that can shorten implantation time is shown. Figure 3 Its side view, Figure 4 for Figure 3 A cross-sectional view along the AA direction.

[0028] Combination Figures 1 to 4 The neural electrical signal acquisition and stimulation unit, which can shorten the implantation time, includes:

[0029] Electrode wire 1 is used to be inserted into the brain tissue of the experimental subject;

[0030] An insulating layer covers the surface of electrode wire 1 to ensure accurate signal transmission and biocompatibility;

[0031] An exposure point is formed at the tip of electrode wire 1, exposing it to the outside of the insulation layer, which can effectively collect or transmit electrical signals.

[0032] The curing component 2 is cured at the connection between the electrode terminal 4 and the electrode wire 1, wrapping and constraining the root of the electrode wire 1, so that the adjacent electrode wires 1 are kept parallel to each other, ensuring stability during the implantation process.

[0033] The shaping component 3 is made of a material that can be cured at low temperatures and can be dissolved during the implantation of the electrode wire 1 into the brain region. It is cured at the connection between the curing component 2 and the electrode wire 1 to wrap and constrain the electrode wire 1 so that it maintains a predetermined shape during the insertion of the experimental subject.

[0034] Electrode terminal 4 is used to connect each electrode wire 1 to the subsequent equipment. The surface is also provided with an insulating layer to prevent signal interference.

[0035] The portion of the electrode wire 1 exposed on the outside of the shaping member 3 is straight, the portion of the electrode wire 1 constrained on the inside of the shaping member 3 is curved, and the electrode wire 1 has an elastic force that allows it to return to a straight position after being released from the inside of the shaping member 3.

[0036] The design of this embodiment aims to shorten the length of the shaping component 3 without shortening the length of the electrode wire 1, thereby accelerating the complete dissolution of the shaping component 3 and reducing the total implantation time of the electrode wire 1. When the tip of the electrode wire 1 passes through the cerebral cortex, it leaves a straight perforation. After the subsequent electrode wire 1 is released from the inside of the shaping component 3, it also returns to a straight posture and is implanted deep into the brain region along the straight perforation. This allows the electrode wire 1 to maintain a straight posture deep in the brain region, so that the shape of the electrode wire 1 inside the shaping component 3 does not affect the implantation position, implantation posture and implantation depth of the electrode wire 1.

[0037] Specifically:

[0038] The surface of electrode wire 1 is covered with an insulating layer, which is used to ensure accurate signal transmission and biocompatibility.

[0039] The tip of electrode wire 1 has an exposure point, which exposes the conductive part of electrode wire 1 to the outside of the insulation layer, enabling effective acquisition or transmission of electrical signals.

[0040] The curing assembly 2 includes a cubic root component 21, with electrode terminals 4 embedded inside the root component 21 and their plug portions exposed outside the root component 21 for connection to downstream devices.

[0041] A head component 22 extends vertically from the center of the root component 21. One end of the electrode wire 1 passes through the head component 22 and the root component 21 and is connected to the electrode terminal 4.

[0042] The outer wall of the root component 21, away from the head component 22, is covered by the housing 23, providing additional protection.

[0043] The shaping component 3 is water-soluble. As the electrode wire 1 gradually penetrates the brain tissue, the shaping component 3 will dissolve on its own. The electrode wire 1 located inside the brain tissue advances along the puncture channel it forms within the brain tissue, ensuring the stability of the puncture direction. The electrode wire 1 located outside the brain tissue remains wrapped and constrained by the shaping component 3 to prevent deformation. Finally, the electrode wire 1 is vertically inserted into the target brain region, the shaping component 3 completely dissolves, and only the electrode wire 1 remains inside the brain tissue.

[0044] The shaping component 3 can be made of materials that can be metabolized by the experimental body, such as collagen, chitosan, cellulose, polyethylene glycol, polyamino acids, polylactic acid, polyglycolic acid, calcium phosphate, tricalcium phosphate, lactide, glycolide, caprolactone, polyesters, or mixtures or copolymers of the above materials.

[0045] Polyethylene glycol is preferred as the material for the shaping component 3 because it has good biocompatibility and its degradation products have no toxic side effects.

[0046] The working principle of the neural electrical signal acquisition and stimulation unit that can shorten the implantation time:

[0047] Electrode wire 1 is inserted into the brain tissue of the experimental subject, with its exposed tip contacting neurons. Electrode terminals 4 and the curing assembly 2 remain outside the experimental subject.

[0048] After the subsequent equipment is activated, electrode wire 1 transmits the collected electrical signals to the subsequent equipment to record neuronal activity; or, electrode wire 1 transmits the electrical signals generated by the subsequent equipment to the neurons to regulate the action potential of individual neurons and the field potential of neuronal groups.

[0049] The electrode wires 1 are arranged in a circular or rectangular array, and the shape of the head component 22 is designed according to the arrangement of the electrode wires 1: when the electrode wires 1 are arranged in a circular array, the head component 22 is cylindrical; when the electrode wires 1 are arranged in a rectangular array, the head component 22 is square columnar.

[0050] The tip of electrode wire 1 can be flat or ground into a cone shape, and all tips should be kept at the same angle and on the same horizontal plane to reduce damage to biological tissue when inserted into the brain tissue of the experimental subject.

[0051] The electrode wire 1 is made of corrosion-resistant metals such as platinum, titanium, gold, platinum-iridium, tungsten, or iridium oxide, which have good mechanical properties and conductivity. It is not easy to break during puncture and has high biocompatibility, which reduces the stimulation and toxicity to biological tissues, and realizes continuous, long-term, and efficient physiological electrical signal acquisition and transmission.

[0052] Among them, nickel-titanium alloy wire with a diameter of 5-100 micrometers is preferred. Nickel-titanium alloy wire has shape memory function and super elasticity, good biocompatibility, and minimal damage to tissues in the body.

[0053] The insulation layer is made of flexible materials, including biocompatible flexible film materials such as polyimide (PI), parylene, polydimethylsiloxane (PDMS), polyurethane (PU), silicone, and silicone rubber.

[0054] There are two methods for forming the exposure point: one is to expose the tip of the electrode wire 1 by cutting or grinding it after the insulating layer covers the electrode wire 1; the other is to cover the tip of the electrode wire 1 in advance before the insulating layer is covered to prevent the insulating layer from covering it, so that the electrode wire 1 can accurately collect the electrical signal of the designated neuron and avoid interfering with non-target neurons.

[0055] The curing component 2 can be made of medical-grade, non-degradable materials such as silicone or polyimide to ensure structural stability and biosafety.

[0056] The above embodiments are merely exemplary embodiments of this utility model and are not intended to limit this utility model. The scope of protection of this utility model is defined by the claims. Those skilled in the art can make various modifications or equivalent substitutions to this utility model within its substance and scope of protection, and such modifications or equivalent substitutions should also be considered as falling within the scope of protection of this utility model.

Claims

1. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time, characterized in that, include: Electrode wires are used to be inserted into the brain tissue of experimental subjects. A curing component is used to wrap and constrain the root of the electrode wire, so that adjacent electrode wires remain parallel to each other. The shaping component, made of a material that can dissolve during the implantation of the electrode wire into the brain region, is used to solidify at the connection between the solidification component and the electrode wire to wrap and constrain the electrode wire, so that the electrode wire maintains a predetermined shape during the insertion of the experimental subject. The portion of the electrode wire exposed on the outside of the shaping member is straight, the portion of the electrode wire constrained on the inside of the shaping member is curved, and the electrode wire has an elastic force that allows it to return to a straight position after being released from the inside of the shaping member.

2. The neural electrical signal acquisition and stimulation unit according to claim 1, characterized in that, The surface of the electrode wire is covered with an insulating layer.

3. The neural electrical signal acquisition and stimulation unit according to claim 2, characterized in that, The tip of the electrode wire has an exposure point, which exposes the conductive part of the electrode wire to the outside of the insulating layer.

4. The neural electrical signal acquisition and stimulation unit according to claim 1, characterized in that, It also includes electrode terminals for connecting each of the electrode wires to the subsequent equipment.

5. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time according to claim 4, characterized in that, The curing assembly includes a cubic root component, with electrode terminals embedded inside the root component and plug portions of the electrode terminals exposed outside the root component.

6. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time according to claim 5, characterized in that, A head component extends vertically from the center of the root component, and one end of the electrode wire passes through the head component and the root component and is connected to the electrode terminal.

7. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time according to claim 6, characterized in that, The outer wall of the root component at the end away from the head component is covered by a housing.

8. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time according to claim 1, characterized in that, The material of the shaping component is a material that can be cured at low temperatures and dissolves in water.

9. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time according to claim 1, characterized in that, The electrode wire is a nickel-titanium alloy wire with a diameter of 5-100 micrometers.

10. A neural electrical signal acquisition and stimulation unit capable of shortening implantation time according to claim 1, characterized in that, The insulating layer is made of a biocompatible flexible thin film material.

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