CN112754486A - Annular dry electrode - Google Patents
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- CN112754486A CN112754486ACN202110029866.5ACN202110029866ACN112754486ACN 112754486 ACN112754486 ACN 112754486ACN 202110029866 ACN202110029866 ACN 202110029866ACN 112754486 ACN112754486 ACN 112754486A
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Abstract
Translated fromChinese
Description
Technical Field
The invention relates to the technical field of intelligent equipment, in particular to an annular dry electrode.
Background
With the development of intelligent wearable equipment, the detection of biological electric signals becomes an important subject, body surface electric signals taking electroencephalogram (EEG) and Electrocardiogram (ECG) as mainstream are key indexes in the fields of medical health and intelligent equipment, including neuroscience, psychology, polysomnography, brain-computer interface, dynamic electrocardiogram monitoring, a series of consumer-grade products and the like, and electrodes for collecting the electric signals are a key ring for detecting the body surface electric signals.
At present, an electrode used in detection of a bioelectric signal is often to directly attach a complete attachment surface to the skin of a target object, and a long hair exists on the skin of some target objects, so that the contact between the electrode and the skin is blocked by the hair, acquisition of the bioelectric signal is interfered, and identification of the bioelectric signal is inaccurate.
Disclosure of Invention
The invention provides an annular dry electrode, which is used for solving the defects that in the prior art, the contact between the electrode and the skin is blocked due to hairs, the acquisition of bioelectric signals is interfered, and the identification of the bioelectric signals is inaccurate, reducing the interference caused by the hairs, expanding the applicable scene and improving the identification accuracy of the bioelectric signals.
The present invention provides an annular dry electrode comprising: an annular substrate having a working side for attaching to a target; the probe is arranged on the working side surface and is used for contacting with a target to detect an electric signal; a connector electrically connected with the probe.
According to the present invention there is provided an annular dry electrode, the probe comprising: a plurality of microneedles coupled to the annular substrate.
According to the annular dry electrode provided by the invention, a plurality of the micro-needles are arranged on the annular substrate at intervals, and the connecting line of the plurality of the micro-needles is annular.
According to the annular dry electrode provided by the invention, the micro-needle and the annular substrate are integrally formed.
According to the annular dry electrode provided by the invention, the length of the microneedle is 50-1000 μm; or the diameter of the bottom circle of the microneedle is 50-500 μm; alternatively, the central distance between adjacent microneedles is 100 μm to 1000 μm; alternatively, the microneedles are at a distance of 100 μm to 1000 μm from the edge of the working side.
According to the annular dry electrode provided by the invention, the annular substrate is in a shape of a regular circular ring, an elliptical ring, a rectangular ring or a diamond ring.
According to the annular dry electrode provided by the invention, the annular substrate is a flexible substrate.
According to the annular dry electrode provided by the invention, the annular substrate is a polyester resin substrate, a polyester substrate or a polymer substrate.
According to the annular dry electrode provided by the invention, at least part of the annular substrate and/or the probe is coated with the conductive layer, the joint is arranged on the annular substrate, and the joint is electrically connected with the probe through the conductive layer.
According to the present invention, there is provided an annular dry electrode, the conductive layer comprising: a metal; and/or, a conductive polymer comprising: poly 3, 4-ethylenedioxythiophene: at least one of sodium polystyrene sulfonate, polyaniline, polypyrrole and polythiophene; and/or, a nano-conductive material comprising: at least one of platinum black, graphene, carbon nanotubes, and silver nanowires.
According to the annular dry electrode provided by the invention, the annular substrate is arranged, the hair can be bypassed by the annular structure, the annular dry electrode is suitable for stably working in a hair covering area, the interference caused by the hair is reduced, the applicable scene is expanded, and the identification accuracy of the bioelectricity signal is improved.
Drawings
In order to more clearly illustrate the technical solutions of the present invention or the prior art, the drawings needed for the description of the embodiments or the prior art will be briefly described below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and those skilled in the art can also obtain other drawings according to the drawings without creative efforts.
FIG. 1 is a schematic diagram of a ring-shaped dry electrode according to the present invention;
FIG. 2 is one of the wearing schematics of the ring-shaped dry electrode provided by the present invention;
FIG. 3 is a second schematic view of the wearing of the annular dry electrode according to the present invention;
FIG. 4 is a third schematic view of the wearing of the annular dry electrode provided by the present invention;
FIG. 5 is a second schematic structural view of the annular dry electrode provided in the present invention;
FIG. 6 is a graph showing the difference in amplitude-frequency characteristics of contact impedances of the annular dry electrode and the annular wet electrode under different conductive materials;
fig. 7 is a graph of the phase-frequency characteristic difference of contact impedance of the annular dry electrode and the annular wet electrode provided by the invention under different conductive materials.
Reference numerals:
10: a ring-shaped substrate; 11: a hole; 12: microneedles;
13: a joint; 20: connecting a cable externally; 30: hair.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention clearer, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings, and it is obvious that the described embodiments are some, but not all embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
In the description of the embodiments of the present invention, it should be noted that the terms "upper", "lower", "inner", "outer", "top", "bottom", and the like indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings, which are only used for convenience in describing the embodiments of the present invention and simplifying the description, but do not indicate or imply that the referred devices or elements must have specific orientations, be constructed in specific orientations, and be operated, and thus, should not be construed as limiting the embodiments of the present invention.
In the description of the embodiments of the present invention, it should be noted that, unless explicitly stated or limited otherwise, the terms "connected" and "connected" are to be interpreted broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected; can be mechanically or electrically connected; may be directly connected or indirectly connected through an intermediate. Specific meanings of the above terms in the embodiments of the present invention can be understood in specific cases by those of ordinary skill in the art.
In the description herein, references to the description of the term "one embodiment," "some embodiments," "an example," "a specific example," or "some examples," etc., mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of an embodiment of the invention. In this specification, the schematic representations of the terms used above are not necessarily intended to refer to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, various embodiments or examples and features of different embodiments or examples described in this specification can be combined and combined by one skilled in the art without contradiction.
The annular dry electrode of the present invention is described below with reference to fig. 1 to 7.
As shown in fig. 1, an embodiment of the present invention provides an annular dry electrode, including: a ring-shaped substrate 10, a probe and ajoint 13.
Theannular substrate 10 has a working side surface for being attached to a target, and the working side surface may have viscosity, so that the adhesive is stably adhered and fixed to a skin position of the target in a detection process, and certainly, the working side surface may have no viscosity, and is fixed to the skin position of the target by being held by a user, which is not specifically limited herein.
It can be understood that theannular substrate 10 is in the shape of a ring, theannular substrate 10 is composed of an outer frame and ahole 11 in the middle, theannular substrate 10 can be in a sheet structure and can be attached to a target, the target can be various organisms such as a human body, and can also be other animals such as certain livestock or pets, the body surface electric signals of the organisms can be monitored to assist in judging the health condition, and the body surface electric signals of the organisms can reflect various physiological, psychological and pathological information, and have important clinical significance. And the target organism can be electrically stimulated on the body surface, and medical and man-machine interaction scenes such as nerve function regulation, touch simulation and the like can be realized.
As shown in fig. 2, 3 and 4, the ring-shaped substrate 10 is ring-shaped, and has ahole 11 in the middle, so when the ring-shaped substrate 10 is attached to the skin of a specific location of a living body, if there is along hair 30 in the location, thehair 30 can pass through thehole 11, so that the ring-shaped substrate 10 and the skin have a higher contact degree, and the interference caused by thehair 30 is reduced.
It is noted that the ring structure can bypass thehair 30, and directly avoid the interference of thehair 30 to the bioelectrical signal acquisition.
For example, theannular substrate 10 may be attached to the skin of the head of a human body, so that the hair at the position of the scalp to be detected may form a strand, and the strand of hair passes through theholes 11 of theannular substrate 10, so that the working side surface of theannular substrate 10 may be directly contacted with the scalp, and thus, the electrical signal at the position of the scalp may be directly collected, and the annular substrate may be used for monitoring brain waves or electrically stimulating the brain area in real time, and may be used for human-computer interaction.
The probe is arranged on the working side surface and is used for being in contact with the target to detect the electric signal.
It can be understood that the probe is installed on the working side of the ring-shaped substrate 10, and when the working side is attached to the target, the probe can be in contact with the target, the probe can pass through the high-impedance horny layer, and in the absence of conductive adhesive, it can provide low-impedance and stable electrical contact, and because of the absence of conductive adhesive, the user can wear the probe for a long time, thus improving the applicability of various occasions.
Theconnector 13 is electrically connected to the probe, theconnector 13 may be connected to thering substrate 10, the probe may be electrically connected to theconnector 13 through a wire, or the probe may be electrically connected to theconnector 13 through a conductive layer coated on the surface of thering substrate 10, which is not limited herein.
Theconnector 13 can be electrically connected with an external device through theexternal cable 20, and theconnector 13 can lead out the electric signal recognized by the probe through theexternal cable 20 to the external device, or receive the electric signal input by the external device, so that the external device can recognize the electric signal of the target, recognize corresponding physiological information through the electric signal, or output the electric stimulation to the corresponding position of the target.
It is noted that the wet electrode is a body surface electrical signal collecting electrode commonly used in clinical and related medical research, and can provide stable and reliable collecting capability for weak body surface electrical signals. The excellent performance of the wet electrode is mainly aided by the conductive paste or gel attached to the metal electrode sheet, the most common body surface electrode pattern is a silver/silver chloride electrode patch covered with a conductive gel coating, and the back side is connected with an external circuit through a button type connector. The button electrode patch is suitable for collecting electroencephalogram signals at the forehead and electrocardiosignals at the chest or four limbs, and needs a larger gel area to prolong the effective use time.
However, button electrode patches are not suitable for working on areas of the scalp covered with hair or on the body surface of living organisms with large body hair. In the case of a scalp area covered with hair or a body surface of a living being with much hair, a conventional solution is to apply conductive pastes to a metal electrode and a target area, respectively, to form a conductive path between hairs. Because the conductive paste has certain fluidity, the adjacent electrodes cannot be too close to avoid short circuit, which limits the electroencephalogram acquisition application targeting high resolution. After collection, the conductive paste still remains among hairs and needs to be washed by water or alcohol, so that the body surface electric signal collection process is complex, tedious and fussy. Meanwhile, the conductive paste gradually dries with time to lose conductivity, and is not friendly to long-time electric signal acquisition.
Dry electrodes, as opposed to wet electrodes, which do not require the use of conductive pastes or gels, are a class of body surface electrodes that have gradually advanced into research and market in recent years, and are commonly available in the form of stretchable flexible planar electrodes, microtip array electrodes, and the like. In the design of dry electrodes, the electrode-skin contact impedance is a key factor determining its performance, and a lower contact impedance will result in a higher signal-to-noise ratio and common mode rejection ratio for the acquisition system.
The stretchable planar dry electrode can be tightly attached to the surface of the skin, and the micro-needle-tip array electrode can penetrate through the high-impedance stratum corneum to directly acquire an electric signal from the inner layer of the skin. In contrast, the micro-tip array electrode can achieve very low contact resistance with a small contact area. However, most dry electrodes also fail to address the problem of stable operation in the hair covered area.
The inventor finds in the development process that the dry electrode in a shape of a claw or a brush can be directly contacted with the skin through hair by design, but the dry electrode is generally large in volume and not suitable for high-resolution collection, the wearing feeling is heavy, the micro-needle point structure is difficult to further design on the dry electrode, and the contact impedance characteristic has no advantage compared with a wet electrode.
Meanwhile, compared with a micro-needle dry electrode without a hole structure and with a single plane substrate, the annular substrate structure enables the dry electrode to have better flexibility and stretchability, and can be attached to a curved skin surface in a more conformal manner, so that displacement artifacts caused by user activities are reduced, and the recorded signal quality is improved.
According to the annular dry electrode provided by the embodiment of the invention, theannular substrate 10 is arranged, and the hair can be bypassed by the annular structure, so that the annular dry electrode is suitable for stable work in a hair covering area, the interference caused by the hair is reduced, the applicable scene is expanded, and the identification accuracy of the bioelectric signal is improved.
As shown in fig. 1 and 5, in some embodiments, the probe comprises: a plurality ofmicroneedles 12.
A plurality ofmicroneedles 12 are attached to thering substrate 10, the plurality ofmicroneedles 12 may extend outwardly from the working side of thering substrate 10, and in use, themicroneedles 12 may be in contact with the skin of a subject and may be capable of detecting an electrical signal from the subject or applying an electrical stimulus to the subject.
Themicroneedles 12 have good electrical conductivity, and may be made of a metal material, such as titanium, nickel, gold, platinum, or stainless steel, with good biocompatibility, or an insulating substrate with a surface plated with a conductive material, and have good mechanical properties.
Electrode-skin contact impedance is a key factor affecting bioelectrical signal acquisition and electrical stimulation, and high electrode-skin impedance causes attenuation of the electric signal, in other words, low electrode-skin impedance is a necessary prerequisite for obtaining high quality electric signals.
In a traditional bioelectrical signal research system, there is a certain limitation in acquiring signals by using a wet electrode or a traditional dry electrode. Before the wet electrode is used, skin preparation and conductive adhesive application are needed, the skin preparation is time-consuming and inconvenient, and the application of the conductive adhesive is easy to stimulate the skin and cause allergy. Some conventional dry electrodes have high impedance and need to be equipped with on-site high impedance amplifiers. Other conventional dry electrodes, particularly rigid electrodes, do not fully conform to rough skin surfaces and have poor skin contact. Therefore, the electrode-skin impedance of the traditional dry electrode is high, the monitored bioelectric signals are not accurate enough, and the transmitted electric stimulation signals are not stable enough.
Themicroneedles 12 may be 50 μm to 1000 μm in length, for example 500 μm.
In order to ensure that themicroneedles 12 can smoothly penetrate through the stratum corneum and cause no bleeding or severe pain, the length of themicroneedles 12 is particularly critical, and according to the skin structure, the length of themicroneedles 12 is theoretically appropriate to be 50-1000 μm, so that bleeding spots on the skin are avoided while smooth transmission of electric signals is ensured, and severe stabbing pain is avoided.
The micro-needles 12 do not need to use conductive adhesive or polish the skin, the micro-needles 12 can directly penetrate through the stratum corneum with high impedance characteristic to penetrate into the conductive epidermis layer, so as to reduce the impedance of the electrode and the skin, the size of the micro-needles 12 is small, the diameter of the bottom circle of the micro-needles 12 can be 50 μm-500 μm, such as 300 μm, the center distance between the adjacent micro-needles 12 can be 100 μm-1000 μm, that is, the distance between the center points of theadjacent micro-needles 12, such as 500 μm, the required skin surface area is small when the micro-needles are used, so that the medical damage to a user is small, the distance between the micro-needles 12 and the edge of the working side is 100 μm-1000 μm, such as 500 μm, so that the micro-needles 12 can be prevented from being too close to the edge of.
As shown in fig. 1 and 5, in some embodiments, a plurality ofmicroneedles 12 are spaced apart on a ring-shapedsubstrate 10, and a line connecting the plurality ofmicroneedles 12 is in a ring shape.
It is understood that the plurality ofmicroneedles 12 may be spaced apart on thering substrate 10, a connection line of the plurality ofmicroneedles 12 may be a circle along thering substrate 10, may also be multiple circles along thering substrate 10, may also be an incomplete circle, or themicroneedles 12 may also be arranged in other arrangements, which is not specifically limited in this embodiment of the present invention.
As shown in fig. 1 and 5, in some embodiments, themicroneedles 12 are integrally formed with theannular substrate 10, that is, theannular substrate 10 and themicroneedles 12 may be integrally formed using the same mold during production, and themicroneedles 12 and theannular substrate 10 may be made of the same material.
As shown in fig. 1 and 5, in some embodiments, the ring-shapedsubstrate 10 has a shape of a perfect circle ring, an elliptical ring, a rectangular ring, or a diamond ring.
Meanwhile, the shape of the ring-shapedsubstrate 10 may be other shapes as long as it is suitable for hair to pass through, and a person skilled in the art may select a specific shape of the ring-shapedsubstrate 10 according to the actual situation of the process.
In some embodiments, the ring-shapedsubstrate 10 is a flexible substrate, and the ring-shapedsubstrate 10 made of a flexible material can adapt to the shape of the skin surface of the target, can be stably attached to almost any skin surface, and reduces discomfort to the target.
In some embodiments, theannular substrate 10 is a polyester resin substrate, a polyester substrate, or a polymer substrate, and the polyester resin substrate, the polyester substrate, or the polymer substrate is a flexible non-toxic material suitable for direct contact with a human body.
In some embodiments, at least a portion of thering substrate 10 and/or the probe is coated with a conductive layer, thecontact 13 is provided on thering substrate 10, and thecontact 13 is electrically connected to the probe through the conductive layer.
It is understood that the conductive layer may include a conductive metal, and the conductive layer may be covered on the surface of themicroneedles 12, the ring-shapedsubstrate 10, and a portion of theconnector 13, and theconnector 13 may be electrically connected to themicroneedles 12 through the conductive layer, and the conductive layer may transmit an electrical signal recognized by themicroneedles 12.
In some embodiments, the conductive layer comprises: a metal; and/or, a conductive polymer comprising: poly 3, 4-ethylenedioxythiophene: at least one of sodium polystyrene sulfonate, polyaniline, polypyrrole and polythiophene; and/or, a nano-conductive material comprising: at least one of platinum black, graphene, carbon nanotubes, and silver nanowires.
It is understood that the conductive layer may include a metal material and/or poly 3, 4-ethylenedioxythiophene: and (3) biocompatible conductive polymers such as sodium polystyrene sulfonate (PEDOT: PSS), polyaniline, polypyrrole and polythiophene and/or nano conductive materials such as platinum black, graphene, carbon nano tubes and silver nano wires, preferably PEDOT: PSS.
PSS is a conductive polymer material with high conductivity, high biocompatibility and low sensitization, and is suitable for being used as a surface conductive coating of a biomedical device applied to the body surface or in vivo. The electric signal in the organism is generally conducted in the form of ionic current, when the bioelectric signal is collected by the electrode on the body surface, the ionic current in the organism tissue fluid is converted into the electronic current on the electrode, and the conversion of the two current types generates the effect of 'double electric layer' parasitic capacitance, so that the contact impedance of the electrode and the skin is higher. The conversion of ionic current and electronic current is transferred from the skin-electrode interface to the interface of the PEDOT and PSS inside the electrode due to the unique proton conducting property of the PEDOT and PSS, the double electric layer capacitance effect is shielded, and the contact impedance can be obviously reduced.
And in the process of manufacturing the conductive layer, uniformly growing PEDOT (PSS) on the surface of the conductive layer by a constant-current electrochemical deposition process. The electrochemical deposition adopts a three-electrode system (a working electrode is the annular dry electrode provided by the invention, a counter electrode is a platinum electrode, and a reference electrode is a silver-silver chloride electrode) or a two-electrode system (the working electrode is the annular dry electrode provided by the invention, and the counter electrode is a platinum electrode), and an electrochemical workstation is connected in a mixed aqueous solution of 3, 4-Ethylenedioxythiophene (EDOT) and sodium polystyrene sulfonate (PSS) to apply constant current.
As shown in fig. 6 and 7, the amplitude-frequency characteristics and the phase-frequency characteristics of the contact impedance of various electrodes are compared, and four electrodes are involved: a commercial gel wet electrode, a ring-shaped dry electrode (microneedle length 400 μm) having gold as a conductive surface, a ring-shaped dry electrode (microneedle length 400 μm) having PEDOT: PSS as a conductive surface, and a ring-shaped dry electrode (microneedle length 700 μm) having PEDOT: PSS as a conductive surface.
As shown in fig. 6, the impedance level of the circular dry electrode with gold as the conductive surface is slightly lower than that of the wet electrode, while the impedance level of the circular dry electrode with PEDOT: PSS as the conductive surface is significantly better than the first two, and thelonger microneedle 12 has a larger contact area with the skin, so that lower contact impedance can be obtained.
As shown in fig. 7, the cause of the impedance reduction can be analyzed visually: since the electric double layer capacitor is shielded, the phase characteristics of the annular dry electrode with the PEDOT: PSS as the conductive surface in the middle frequency band approach to 0 (resistance), and the phases of the other two electrodes have very deep capacitance. As shown in fig. 6, the low capacitance characteristic in the middle frequency band makes the impedance amplitude hardly increase with the decrease of the frequency, and the impedance characteristic of the annular dry electrode with PEDOT: PSS as the conductive surface is greatly optimized.
The above-described embodiments of the apparatus are merely illustrative, and the units described as separate parts may or may not be physically separate, and parts displayed as units may or may not be physical units, may be located in one place, or may be distributed on a plurality of network units. Some or all of the modules may be selected according to actual needs to achieve the purpose of the solution of the present embodiment. One of ordinary skill in the art can understand and implement it without inventive effort.
Through the above description of the embodiments, those skilled in the art will clearly understand that each embodiment can be implemented by software plus a necessary general hardware platform, and certainly can also be implemented by hardware. With this understanding in mind, the above-described technical solutions may be embodied in the form of a software product, which can be stored in a computer-readable storage medium such as ROM/RAM, magnetic disk, optical disk, etc., and includes instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to execute the methods described in the embodiments or some parts of the embodiments.
Finally, it should be noted that: the above examples are only intended to illustrate the technical solution of the present invention, but not to limit it; although the present invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the corresponding technical solutions of the embodiments of the present invention.
Claims (10)
1. An annular dry electrode, comprising:
an annular substrate having a working side for attaching to a target;
the probe is arranged on the working side surface and is used for contacting with a target to detect an electric signal;
a connector electrically connected with the probe.
2. The annular dry electrode of claim 1, wherein the probe comprises:
a plurality of microneedles coupled to the annular substrate.
3. The annular dry electrode of claim 2, wherein a plurality of the microneedles are spaced apart on the annular substrate, and a line of the plurality of the microneedles is annular.
4. The annular dry electrode of claim 2, wherein the microneedles are integrally formed with the annular substrate.
5. The annular dry electrode of claim 2, wherein the microneedle has a length of 50-1000 μ ι η;
or the diameter of the bottom circle of the microneedle is 50-500 μm;
alternatively, the central distance between adjacent microneedles is 100 μm to 1000 μm;
alternatively, the microneedles are at a distance of 100 μm to 1000 μm from the edge of the working side.
6. The annular dry electrode according to any one of claims 1 to 5, wherein the annular substrate has a shape of a perfect circle, an elliptical circle, a rectangular circle, or a diamond-shaped circle.
7. The annular dry electrode of any of claims 1-5, wherein the annular substrate is a flexible substrate.
8. The annular dry electrode of claim 7, wherein the annular substrate is a polyester resin substrate, a polyester substrate, or a polymer substrate.
9. The annular dry electrode according to any of claims 1 to 5, wherein at least a portion of the annular substrate and/or the probe is coated with an electrically conductive layer, the contact being provided on the annular substrate, the contact being electrically connected to the probe through the electrically conductive layer.
10. The annular dry electrode of claim 9, wherein the conductive layer comprises:
a metal;
and/or, a conductive polymer comprising: poly 3, 4-ethylenedioxythiophene: at least one of sodium polystyrene sulfonate, polyaniline, polypyrrole and polythiophene;
and/or, a nano-conductive material comprising: at least one of platinum black, graphene, carbon nanotubes, and silver nanowires.
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| CN113261964A (en)* | 2021-05-28 | 2021-08-17 | 北京脑陆科技有限公司 | Cup-shaped electrode |
| CN114129889A (en)* | 2021-11-30 | 2022-03-04 | 温州医科大学 | An ophthalmic annular microneedle |
| CN116616776A (en)* | 2023-06-02 | 2023-08-22 | 大连理工大学 | Design and processing method and special tooling of a ring-shaped stepped metal microneedle electrode |
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