CN108309291B - Flexible contact brain electrode and preparation method thereof - Google Patents
Flexible contact brain electrode and preparation method thereof Download PDFInfo
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- CN108309291B CN108309291B CN201810198860.9A CN201810198860A CN108309291B CN 108309291 B CN108309291 B CN 108309291B CN 201810198860 A CN201810198860 A CN 201810198860A CN 108309291 B CN108309291 B CN 108309291B
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J5/00—Manufacture of articles or shaped materials containing macromolecular substances
- C08J5/18—Manufacture of films or sheets
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K7/00—Use of ingredients characterised by shape
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
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- C08J2353/02—Characterised by the use of block copolymers containing at least one sequence of a polymer obtained by reactions only involving carbon-to-carbon unsaturated bonds; Derivatives of such polymers of vinyl aromatic monomers and conjugated dienes
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2375/00—Characterised by the use of polyureas or polyurethanes; Derivatives of such polymers
- C08J2375/04—Polyurethanes
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2383/00—Characterised by the use of macromolecular compounds obtained by reactions forming in the main chain of the macromolecule a linkage containing silicon with or without sulfur, nitrogen, oxygen, or carbon only; Derivatives of such polymers
- C08J2383/04—Polysiloxanes
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K2201/00—Specific properties of additives
- C08K2201/001—Conductive additives
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K2201/00—Specific properties of additives
- C08K2201/011—Nanostructured additives
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L2203/00—Applications
- C08L2203/20—Applications use in electrical or conductive gadgets
Abstract
The invention belongs to the technical field of electrophysiological signal detection, and particularly relates to a flexible electroencephalogram electrode and a preparation method thereof. The brain electrode consists of a flexible silica gel electrode slice and an electrode base. The upper layer of the flexible silica gel electrode sheet is a flexible silica gel layer, the lower layer is a composite conductive layer, and the cut electrode sheet comprises a circular electrode and a connecting handle; the electrode base includes: the electrode plate outer fixing buckle comprises a fixing nut, an electrode wire, an electroencephalogram cap fixing base, an electrode plate outer fixing buckle and an electrode wire fixing buckle; the outer clamping buckles of the electrode plates fix the silica gel flexible electrode plates on the electrode base, and the outer clamping buckles fix nuts to fix the silica gel flexible electrode plates. The electrode lead and the flexible silica gel electrode plate are tightly pressed by the bulge of the inner wall of the outer buckle of the electrode plate, and are fixed on the electroencephalogram cap fixing base by the fixing buckle fixing nut. The invention has good contact, convenient and comfortable wearing, low impedance between the electrode and the skin, good conductivity and capability of collecting high-quality electroencephalogram signals.
Description
Technical Field
The invention belongs to the technical field of electrophysiological signal detection, and particularly relates to an electroencephalogram electrode and a preparation method thereof.
Background
The brain wave (EEG) signal is the synthesis of potential information generated by physiological activities of cerebral cortex or scalp surface neuron cell bodies, contains the rhythm information [1] rich in brain, and can be widely applied to the fields of brain disease diagnosis, rehabilitation, brain-computer interface (BCI), fatigue detection and the like. It is considered as the main method for detecting epileptic seizure, psychological non-epileptic seizure, migraine, encephalopathy, etc. [2], and is also an important basis for diagnosing sleeping diseases. However, the amplitude of the brain electrical signal is generally less than 100 mu V3, so the capturing of the brain electrical signal has high requirements on the brain electrical electrode and the post-conditioning circuit. Among them, the technology of the post-conditioning circuit has tended to be mature. In contrast, the research of the electroencephalogram electrode is in progress due to the complex electrical characteristics of the electrode and the special requirements of bioelectric signal acquisition.
In the prior art, the electroencephalogram electrode can be divided into a wet electrode and a dry electrode. Wet electrodes refer to electrodes that need to be used with conductive pastes. Through the operations of preliminary skin preparation and conductive paste smearing at the acquisition position, a metal-electrolyte interface is formed between the electrode and the surface of human skin, so that the ultra-high electrical impedance of the skin is reduced, and a signal with high signal-to-noise ratio is obtained. The conventional wet electrode is represented by a gold cup electrode (Gold Cup Electrode) 4 and an Ag/AgCl electrode (5). The gold cup electrode is prepared by electroplating gold metal on the basis of a pure silver electrode, and the problem of oxidization of the pure silver electrode in long-time use is solved. When the device is used, the gold cup electrode and the skin are required to be connected by using the conductive paste, and the signal acquisition is carried out after the gold cup electrode and the skin are in full contact and the signal is stable. As a standard electrode for EEG signal acquisition, the electrode has the advantages of excellent conductivity, stable signal, high signal-to-noise ratio and the like. However, the application of the conductive paste requires a lot of time to complete with the help of medical staff, and the long-time collection will cause discomfort to the subject, and in severe cases will cause allergic red swelling reactions. In addition, cleaning after the experiment is also very cumbersome. For the Ag/AgCl electrode, the Ag/AgCl electrode is widely used in industry because of the convenient preparation, low price, stable electric signal baseline, strong anti-interference capability and other electronic characteristics. However, since the conductive gel in the electrode is dehydrated and dried, its electrical characteristics change when it is used for a long time, and large noise and errors are introduced into high-precision experiments.
In order to solve the problems of the wet electrode, various researches have been conducted to develop a dry electrode that does not require the use of conductive paste or conductive gel. The dry electrode is very suitable for being applied to the fields of future health monitoring, rehabilitation, disease diagnosis and treatment, brain-computer interface (BCI) and the like because the operations of skin preparation, conductive paste smearing and the like are not needed. The microneedle electrode [6] is the dry electrode most commonly adopted in the current electroencephalogram acquisition technology. The microneedle electrode is an electrode designed and developed by using the microneedle technology, and an array microneedle structure formed by manufacturing on the surfaces of materials such as silicon materials, metals, polymers and glass by a micro-manufacturing method directly pierces through a stratum corneum to reduce the influence of ultrahigh electrical impedance on signal acquisition. The device is convenient and reliable to use, has smaller impedance and smaller electrochemical characteristics, and is more beneficial to long-term measurement. But has the disadvantage of avoiding injury to the dermis and damage to nerves and blood vessels during use. Meanwhile, although other textile electrodes have good application in wearable electrocardio and electromyographic signal acquisition systems, when the textile electrodes are applied to electroencephalogram acquisition, contact impedance is further increased due to poor contact caused by hair and impedance effect of skin, so that acquisition of EEG signals is more difficult.
The invention provides a flexible dry electrode based on a silica gel substrate, which aims to overcome the defects that the traditional wet electrode is complex in operation, difficult to collect signals in a wearable manner for a long time, poor in signal quality of the dry electrode and the like. The electrode is combined with scalp comfortably and tightly, and simultaneously, due to the use of high-conductivity materials, the high-quality original signal can be obtained on the premise of not using conductive paste or conductive gel. The test demonstration of the electrical property of the electrode shows that the electrode has the advantages of comfortable wearing, simple and convenient operation, high sensitivity and precision and the like, and is suitable for the fields of health monitoring, wearable electroencephalogram signal acquisition and the like.
Reference to the literature
[1] Han Feng A, zhu Xianfeng A medical imaging device installation and maintenance science [ M ] Beijing, people health Press, 2008:162-172.
[2] Acharya, D., Rani, A., & Agarwal, S. （2015, September）. EEG data acquisition circuit system Based on ADS1299EEG FE. In Reliability, Infocom Technologies and Optimization （ICRITO）（Trends and Future Directions）, 2015 4th International Conference on （pp. 1-5）. IEEE.
[3] Oohashi, T., Kawai, N., Honda, M., Nakamura, S., Morimoto, M., Nishina, E., & Maekawa, T. （2002）. Electroencephalographic measurement of possession trance in the field. Clinical Neurophysiology, 113（3）, 435-445.
[4] Tallgren, P., Vanhatalo, S., Kaila, K., & Voipio, J. （2005）. Evaluation of commercially available electrodes and gels for recording of slow EEG potentials. Clinical Neurophysiology, 116（4）, 799-806.
[5] Verma, N., Shoeb, A., Bohorquez, J., Dawson, J., Guttag, J., & Chandrakasan, A. P. （2010）. A micro-power EEG acquisition SoC with integrated feature extraction processor for a chronic seizure detection system. IEEE Journal of Solid-State Circuits, 45（4）, 804-816.
[6] Liu Ran, wang Xiaohao, & Zhou Zhaoying (2004) MEMS microneedle arrays and their use in biomedical engineering journal 21 (3), 482-485.
Disclosure of Invention
The invention aims to provide a novel flexible contact brain electrode with excellent conductivity, strong anti-interference capability, convenient use, comfortable wearing and low production cost and a preparation method thereof.
The flexible contact brain electrode provided by the invention consists of a flexible silica gel electrode sheet D and an electrode base; the structure is shown in fig. 2 and 4. The flexible silica gel electrode plate D is formed by a circular electrode and a connecting handle connected with the circular electrode functionally; the electrode base includes: the electrode lead A, the fixing nut B, the electrode lead fixing buckle C, the electroencephalogram cap fixing base E and the electrode sheet external fixing buckle F; wherein:
the electroencephalogram cap fixing base E is used for accommodating the flexible silica gel electrode slice D and the electrode lead A; the shape of the electroencephalogram cap fixing base E is basically cylindrical, and a placement groove for placing a connecting handle of the flexible silica gel electrode slice D and the front end of the electrode wire A is formed in the electroencephalogram cap fixing base E; a wire fixing groove for fixing the electrode wire A is arranged at the upper part of the placement groove; the lower edge of the electroencephalogram cap fixing base E is a convex spherical curved surface; one surface of the round electrode part of the flexible silica gel electrode slice D, which is not made of conductive material, is tightly attached to the spherical curved surface at the lower part of the electroencephalogram cap fixing base E; one surface of the other end of the connecting handle of the flexible silica gel electrode sheet D, which is coated with a conductive layer, is contacted with one end of the electrode wire A and is fixed in a placement groove on the electric cap fixing base E;
the fixing nut B is used for fixing an electrode slice external fixing buckle F;
the electrode lead A is used for transmitting the electric signals acquired on the flexible silica gel electrode sheet D and is connected with an external circuit board; a part of the electrode wire A is placed in the wire fixing groove and is fixed on the electroencephalogram cap fixing base E by the electrode wire fixing buckle C;
the electrode wire fixing buckle C is used for fixing the electrode wire A on the electroencephalogram cap fixing base E;
the electrode plate external fixing buckle F is internally provided with a cavity, the shape of the cavity is matched with the shape of the electroencephalogram cap fixing base E, the upper opening of the cavity is matched with the lower opening of the fixing nut B, the inner side of the cavity is provided with a bulge G, the lower edge of the bulge G is provided with a through hole, and the electrode plate external fixing buckle F is provided with external threads matched with the internal threads of the fixing nut B; the electroencephalogram cap fixing base E is positioned in a cavity of the electrode plate outer fixing buckle F; the bulge G on the inner side of the electrode slice external fixing buckle F tightly presses and fixes the connecting handle of the sexual silica gel electrode slice D positioned in the arranging groove on the electroencephalogram cap fixing base E and the front end of the electrode wire A; the electrode slice external fixing buckle F is used for fixing the flexible silica gel electrode slice D at the bottom of the electroencephalogram cap fixing base E, and the spherical surface at the bottom of the electroencephalogram cap fixing base E pushes out part of the round electrode of the flexible silica gel electrode slice D outside the lower edge hole of the electrode slice external fixing buckle F, so that the surface of the electrode slice can be fully contacted with the scalp.
After the fixing nut B is combined with the electrode slice external fixing buckle F through threads, the electric cap fixing base E, the flexible silica gel electrode slice D and the electrode lead A are fixed in the electric cap fixing base E.
In the invention, the electroencephalogram cap fixing base E is provided with a groove, and the size of the groove is as follows: 4mm long, 5mm wide and 1mm deep.
In the invention, the width of the bulge G measured in the electrode wire fixing buckle C is 5mm, and the height of the vertex of the bulge from the inner surface of the electrode plate outer fixing buckle F is 0.5mm.
In the invention, the diameter of the round part of the flexible silica gel electrode plate is slightly larger than the inner aperture of the lower bottom surface of the electrode plate outer fixing buckle F. The inner diameter of the through hole on the lower bottom surface of the electrode plate external fixing buckle F is 12-14mm.
In the invention, the vertex of the circular electrode part of the flexible silica gel electrode slice D protrudes out of the lower edge hole of the electrode slice outer fixing buckle F by 1.5mm-2mm so as to ensure that the surface of the electrode slice is fully contacted with the scalp.
When the electrode is used, the electrode is tightly attached to the scalp, the electrode is soft, the signal is good, and the attribute of long-term repeated wearing is ensured.
The invention provides a preparation method of a flexible contact brain electrode, which comprises the following specific steps:
preparing a flexible silica gel electrode plate:
(1) Coating the metal nanowire dispersion liquid on the surface of a smooth substrate, heating at 60-100 ℃, and drying to form a three-dimensional conductive network film; here, the metal nanowire may be silver nanowire, copper nanowire, gold nanowire, etc., and the concentration of the metal nanowire dispersion may be 1-10 wt%; the substrate can be glass, silicon wafer, ceramic and the like;
(2) Pouring a silica gel solution on the surface of the three-dimensional conductive network film prepared in the step (1), standing for 0.5-5h, heating for 2-12h at 60-100 ℃ until the solution completely permeates into the gaps of the three-dimensional conductive network, and carefully stripping from the surface of the substrate after the silica gel is completely solidified to obtain a flexible silica gel electrode material; here, the silica gel solution may be selected from Polydimethylsiloxane (PDMS), styrene-butadiene-styrene block copolymer (SBS), polyurethane (PU), or the like;
(3) Cutting the prepared flexible silica gel electrode material into an electrode shape: comprises a circular part and a connecting handle; as shown in fig. 3;
typically, the diameter a of the circular portion of the electrode sheet is 12mm-14mm. The length b of the connecting handle is 4mm, and the width c is 5mm. Wherein the thickness e of the conductive layer is 1-10 μm, and the thickness d of the silica gel layer is 100-500 μm.
(II) assembling a dry flexible electroencephalogram electrode:
(1) Penetrating an electrode lead (B) from a gap between an electroencephalogram cap fixing base E and a fixing nut B;
(2) The front section (length is about 4 mm) of the electrode lead A is arranged in a arranging groove on the electroencephalogram cap fixing base E; the electrode wire adopts FPC;
(3) Inserting an electrode wire fixing buckle C into a wire fixing groove on an electroencephalogram cap fixing base E, fixing an electrode wire A placed in the groove on the electroencephalogram cap fixing base E, and placing the front end (4 mm in length) part of the electrode wire A into a placement groove;
(4) Inserting the connecting handle of the cut flexible silica gel electrode slice D into a gap between the electrode lead A and the inner wall of the placement groove;
(5) Aligning the bulge (G) on the inner wall of the electrode slice external fixing buckle F with the placement groove, sleeving the electrode slice external fixing buckle F outside the electroencephalogram cap fixing base E, and ensuring that the flexible silica gel electrode slice D is 1.5mm-2mm higher than the ground below the electrode slice external fixing buckle F due to extrusion of a spherical curved surface at the lower part of the electroencephalogram cap fixing base;
(6) And (3) rotating the fixing nut B to fix the electrode plate external fixing buckle F.
The flexible electroencephalogram electrode has good contact, convenient wearing mode, comfortable wearing experience, good body surface skin fit, low electrode-skin impedance and good conductivity, and can acquire high-quality electroencephalogram signals. In addition, the flexible silica gel electrode plate has extremely low generation cost, and can greatly reduce the use cost. The invention has simple operation and short manufacturing period, and is easy for mass production.
Features of the invention
The flexible contact brain electrode has good contact flexibility.
The silica gel flexible electrode has good flexibility, and can be bent at will within any angle range without affecting the conductivity.
The electrode base is of a detachable structural design, and the design ensures the simplicity of the replacement operation of the silica gel flexible electrode slice.
The silica gel flexible electrode plate and the lead are pressed through the conductive buckle fixed on the outer buckle of the electrode plate, no welding is needed, and the adhesive has good conductivity.
The contact surface of the electrode base and the silica gel flexible electrode sheet is provided with the silica gel base, so that the flexible contact between the scalp of a user and the silica gel flexible electrode sheet is further ensured.
The flexible contact brain electrode has good conductivity and can collect high-quality brain electrical signals.
Drawings
FIG. 1 is a schematic diagram of an electrode.
Fig. 2 is a schematic diagram of the internal structure of the novel flexible electroencephalogram electrode.
Fig. 3. Flexible silicone electrode pad dimensions.
Fig. 4 is a schematic diagram of a flexible electrode mounting step.
FIG. 5 is an electron micrograph of a cross section of a flexible silica gel electrode and a surface of a conductive layer.
FIG. 6. Impedance contrast between skin and electrodes of flexible electroencephalogram electrode and Ag/AgCl electrode, gold cup electrode in Fp1 region.
FIG. 7. Impedance contrast between skin and electrodes of flexible electroencephalogram electrode and Ag/AgCl electrode, gold cup electrode in F3 region.
FIG. 8. Brain electrical signals collected by the flexible brain electrical electrodes and the Ag/AgCl electrodes and the gold cup electrodes in the Fp1 region are compared.
FIG. 9 shows frequency domain comparison of the brain electrical signals collected by the flexible brain electrical electrodes, the Ag/AgCl electrodes, the flexible silica gel motor and the gold cup electrodes in the Fp1 region.
Fig. 10. Brain electrical signals collected by the flexible brain electrical electrodes and the gold cup electrodes in the F3 region are compared.
FIG. 11. Frequency domain comparison of brain electrical signals acquired by the flexible brain electrical electrodes and the gold cup electrodes in the F3 region.
Reference numerals in the drawings: a is an electrode wire, B is a buckle fixing nut, C is a fixing buckle, D is a flexible silica gel electrode plate, E is an electroencephalogram cap fixing base, F is an electrode plate external fixing buckle, and G is an inner side bulge.
Detailed Description
The novel flexible electroencephalogram electrode is prepared according to the steps:
preparation of flexible silica gel electrode slice:
(1) Dispersing silver nanowires (Ag NWs) with the concentration of 2 ml of 5 wt% on the surface of a glass substrate with the concentration of 5cm multiplied by 5cm, and heating and drying at 60 ℃ for 10min to obtain a three-dimensional silver nanowire conductive network film;
(2) Pouring 1ml of PDMS solution on the surface of the silver nanowire conductive network film prepared in the step (1), standing for 1h, then heating and curing for 5h at 60 ℃, and carefully peeling off the PDMS from the surface of the glass substrate after the PDMS is completely cured to obtain the flexible silica gel electrode, wherein the specific structure is shown in figure 2, the pure PDMS silica gel layer is used as the flexible substrate, the thickness is 100 mu m, and the Ag NWs/PDMS composite layer is used as the conductive layer, and the thickness is 10 mu m. It should be noted that the Ag NWs three-dimensional conductive network is embedded in the PDMS surface, not just simply covered on the surface, so that the Ag NWs three-dimensional conductive network has good adhesion under the condition of satisfying conductivity, and does not fall off under the conditions of bending, twisting and even stretching, thereby completely satisfying the application requirements of the electroencephalogram electrode.
The novel flexible silica gel brain electrode was installed and tested according to fig. 4. Firstly, penetrating an FPC electrode lead A from a gap between an electroencephalogram cap fixing base E and an electrode plate external fixing buckle fixing nut B; then, the front section of the FPC electrode lead A is arranged in a placement groove on the electroencephalogram cap fixing base E, wherein the length of the front section of the FPC electrode lead A is about 4mm; the electrode lead fixing buckle F is inserted into a clamping groove above the placement groove on the electroencephalogram cap fixing base; then inserting the connecting handle of the flexible silica gel electrode slice D cut according to the figure 3 into a gap between the FPC electrode wire A and the inner wall of the placement groove; in addition, after the bulge on the inner wall of the electrode slice external fixing buckle F is aligned with the mounting groove, the electrode slice external fixing buckle F is sleeved outside the electroencephalogram cap fixing base, and the lower edge of the flexible silica gel electrode higher than the electrode slice external fixing buckle F by about 1.5mm due to extrusion of the spherical surface at the lower part of the electroencephalogram cap fixing base is ensured; and finally, fixing the outer fixing buckle F of the electrode plate by the outer fixing buckle fixing nut B of the rotary electrode plate.
At present, the brain electrode widely used in clinic is a gold cup electrode or an Ag/AgCl electrode, and conductive gel is often attached to the contact part of the electrode and skin to improve the bonding degree and the conductivity and reduce the impedance between the skin and the electrode. However, as the service time increases, the conductive gel tends to harden and the related properties significantly decrease.
The flexible electroencephalogram electrode provided by the invention does not need conductive gel, and the mechanical property of the material can keep good contact with skin for a long time. Electrochemical workstation test results showed that the skin-to-electrode impedance of the proposed electrode was comparable to that of the gold cup electrode and the Ag/AgCl electrode in the range of 0.1 Hz-100 khz, while the frequencies of almost all physiological signals (e.g. brain, heart, muscle, etc.) were distributed in the range of 0.1Hz to 1 khz. The characteristics of no need of conductive gel enable the electrode to have obvious advantages compared with Ag/AgCl electrodes in application scenes of wearable equipment, and compared with gold cup electrodes, the electrode is suitable for long-term monitoring, and the acquired quality is not divided into upper and lower parts. Figures 6 and 7 show the skin-to-electrode impedance of the proposed electrode versus the gold cup electrode, ag/AgCl electrode, respectively, in the Fp1 (left frontal pole, no hair attachment) and F3 (left frontal, with hair attachment) positions within the range of 0.1 Hz-100 khz. The flexible silicone electrode has minimum skin electrode interface impedance in the frequency range of 0.1Hz to 200KHz, and is about half (about 15 Kohm) of the gold cup electrode near the DC frequency range, and the impedance distribution is similar to that of EEG standard gold cup electrode. The smaller interface impedance of the skin electrode enables the internal resistance of the equivalent signal source to be smaller, so that the signal distortion problem caused by the larger internal resistance of the signal source is reduced. The Ag/AgCl electrode in the three electrodes has the largest impedance, and the Ag/AgCl electrode is difficult to collect EEG signals in practical application.
Furthermore, it is the ultimate goal for the electrodes to be able to collect an effective signal in addition to having good electrical performance. Signal acquisition verification is therefore performed using medical grade commercial polysomnography PSG (Compumedics Grael) equipment. The experimental conditions were as follows: to ensure tight variable control, the subject requires that the wash be performed prior to the experiment to ensure that the test is not disturbed by perspiration, oil stains, etc., and that the test ends within one hour, assuming that the subject's physical state remains unchanged (skin contact and impedance state do not change significantly over time, resulting in test failure), the sampling frequency is 256Hz. A comparative test was performed using three electrodes in the Fp1 region. In the F3 area, the quality of signals acquired by the Ag/AgCl electrode is poor due to the interference of hair, so that the comparison test of the novel flexible electroencephalogram electrode and the gold cup electrode is only carried out in the F3 area. The experiment analyzes the time domain and the frequency domain of the acquired original signals, and demonstrates the feasibility of electrode design according to the characteristics of the time domain and the frequency domain. Fig. 8 and 9 show the electroencephalogram signals collected by the novel flexible electroencephalogram electrode, the Ag/AgCl electrode and the gold cup electrode in the Fp1 region and the comparison diagram of frequency domain analysis respectively. Fig. 10 and 11 are diagrams showing the comparison of the electroencephalogram signals collected by the novel flexible electroencephalogram electrode and the gold cup electrode in the F3 region and the frequency domain analysis. From the time domain, the two have the same waveform, which indicates the effectiveness of the signal acquisition of the two. From the frequency domain, the frequency spectrum structures of the two acquired signals are completely consistent, and the rationality of the electrode design is demonstrated again.
Claims (9)
1. The flexible contact brain electrode is characterized by comprising a flexible silica gel electrode plate (D) and an electrode base; the flexible silica gel electrode plate (D) is functionally composed of a circular electrode and a connecting handle connected with the circular electrode; the electrode base includes: an electrode wire (A), a fixing nut (B), an electrode wire fixing buckle (C), an electroencephalogram cap fixing base (E) and an electrode sheet external fixing buckle (F); wherein:
the electroencephalogram cap fixing base (E) is used for accommodating a flexible silica gel electrode plate (D) and an electrode lead (A); the shape of the electroencephalogram cap fixing base (E) is basically cylindrical, and a placement groove for placing a connecting handle of the flexible silica gel electrode plate (D) and the front end of the electrode lead (A) is formed in the fixing base; a wire fixing groove for fixing the electrode wire (A) is arranged at the upper part of the placement groove; the lower edge of the electroencephalogram cap fixing base (E) is a convex spherical curved surface; one surface of the round electrode part of the flexible silica gel electrode sheet (D) which is not made of conductive material is tightly attached to the spherical curved surface at the lower part of the electroencephalogram cap fixing base (E); one surface of the other end of the connecting handle of the flexible silica gel electrode sheet (D) coated with the conductive layer is contacted with one end of the electrode wire (A) and is fixed in a placement groove on the electric cap fixing base (E);
the electrode lead (A) is used for transmitting the electric signals acquired on the flexible silica gel electrode sheet (D) and is connected with an external circuit board; a part of the electrode wire (A) is placed in the wire fixing groove and is fixed on the electroencephalogram cap fixing base (E) by the electrode wire fixing buckle (C);
the electrode wire fixing buckle (C) is used for fixing the electrode wire (A) on the electroencephalogram cap fixing base (E);
the electrode plate external fixing buckle (F) is internally provided with a cavity, the shape of the cavity is matched with the shape of the electroencephalogram cap fixing base (E), the upper opening of the cavity is matched with the lower opening of the fixing nut (B), the inner side of the cavity is provided with a bulge (G), the lower edge of the bulge (G) is a through hole, and the electrode plate external fixing buckle (F) is provided with external threads matched with the internal threads of the fixing nut (B); the electroencephalogram cap fixing base (E) is positioned in a cavity of the electrode plate outer fixing buckle (F); a bulge (G) at the inner side of the electrode slice external fixing buckle (F) tightly presses and fixes a connecting handle of the sexual silica gel electrode slice (D) positioned in the arranging groove on the electroencephalogram cap fixing base (E) and the front end of the electrode wire (A); the electrode plate external fixing buckle (F) is used for fixing the flexible silica gel electrode plate (D) at the bottom of the electroencephalogram cap fixing base (E), and a spherical surface at the bottom of the electroencephalogram cap fixing base (E) pushes out a part of a round electrode of the flexible silica gel electrode plate (D) outside a lower edge hole of the electrode plate external fixing buckle (F), so that the surface of the electrode plate can be fully contacted with the scalp;
after the fixing nut (B) is combined with the electrode plate external fixing buckle (F) through threads, the electric cap fixing base (E), the flexible silica gel electrode plate (D) and the electrode lead (A) are fixed in the electric cap fixing base.
2. The flexible contact electroencephalogram electrode according to claim 1, wherein the electroencephalogram cap fixing base (E) is provided with a groove having a size of: 4mm long, 5mm wide and 1mm deep.
3. The flexible contact brain electrode according to claim 1, wherein the protrusion (G) measured inside the electrode lead fixing button (C) has a width of 5mm and the apex of the protrusion has a height of 0.5mm from the inner surface of the electrode sheet outer fixing button (F).
4. The flexible contact brain electrode according to claim 1, wherein the diameter of the circular part of the flexible silica gel electrode sheet is larger than the inner aperture of the lower bottom surface of the electrode sheet outer fixing buckle (F); the inner diameter of the through hole at the lower bottom surface of the electrode plate external fixing buckle (F) is 12-14mm.
5. The flexible contact brain electrode according to claim 1, wherein the apex of the circular electrode portion of the flexible silicone electrode sheet (D) protrudes 1.5mm-2mm outside the lower edge hole of the electrode sheet outer fixing buckle (F) to ensure that the electrode sheet surface is sufficiently contacted with the scalp.
6. A method for preparing a flexible contact brain electrode according to any one of claims 1 to 5, comprising the specific steps of:
preparing a flexible silica gel electrode plate:
(1) Coating the metal nanowire dispersion liquid on the surface of a smooth substrate, heating at 60-100 ℃, and drying to form a three-dimensional conductive network film;
(2) Pouring a silica gel solution on the surface of the three-dimensional conductive network film prepared in the step (1), standing for 0.5-5h, heating for 2-12h at 60-100 ℃ until the solution completely permeates into the gaps of the three-dimensional conductive network, and stripping from the surface of the substrate after the silica gel is completely solidified to obtain a flexible silica gel electrode material;
(3) Cutting the prepared flexible silica gel electrode material into an electrode shape: comprises a circular part and a connecting handle;
(II) assembling a dry flexible electroencephalogram electrode:
(1) Penetrating an electrode lead (A) from a gap between an electroencephalogram cap fixing base (E) and a fixing nut (B);
(2) The front end part of the electrode lead (A) is arranged in a arranging groove on the electroencephalogram cap fixing base (E);
(3) Inserting an electrode wire fixing buckle (C) into a wire fixing groove on an electroencephalogram cap fixing base (E), fixing an electrode wire (A) placed in the groove on the electroencephalogram cap fixing base (E), and placing the front end part of the electrode wire (A) into a placement groove;
(4) Inserting a connecting handle of the cut flexible silica gel electrode slice (D) into a gap between the electrode lead (A) and the inner wall of the placement groove;
(5) Aligning the bulge (G) on the inner wall of the electrode slice external fixing buckle (F) with the placement groove, sleeving the electrode slice external fixing buckle (F) outside the electroencephalogram cap fixing base (E), and ensuring that the flexible silica gel electrode slice (D) is higher than the ground 1.5mm-2mm below the electrode slice external fixing buckle (F) due to extrusion of a spherical curved surface at the lower part of the electroencephalogram cap fixing base;
(6) And (3) rotating the fixing nut (B) to fix the electrode slice external fixing buckle (F).
7. The method according to claim 6, wherein in the step (1), the metal nanowire is silver nanowire, copper nanowire or gold nanowire, and the concentration of the metal nanowire dispersion is 1-10 wt%.
8. The method according to claim 6, wherein in the step (2), the silica gel solution is selected from the group consisting of polydimethylsiloxane, styrene-butadiene-styrene block copolymer and polyurethane.
9. The method according to claim 6, wherein in the step (3), the diameter a of the circular portion of the electrode sheet is 12mm to 14mm; the length b of the connecting handle is 4mm, and the width c is 5mm; wherein the thickness e of the conductive layer is 1-10 μm, and the thickness d of the silica gel layer is 100-500 μm.
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| CN109171715B (en) * | 2018-09-20 | 2019-11-22 | 清华大学 | Use the wearable device of flexible extending electrode acquisition EEG signals |
| CN110236517A (en) * | 2019-04-02 | 2019-09-17 | 复旦大学 | The perception of cardiopulmonary signal and acquisition system for sleep monitor |
| CN116138762A (en) * | 2021-11-22 | 2023-05-23 | 深圳先进技术研究院 | Capacitive bioelectrode internal resistance testing system and testing method thereof |
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