CN115969380A - Brain-heart electric electrode slice and preparation method thereof - Google Patents

Abstract

The application relates to the technical field of electroencephalogram sensors, and particularly discloses a brain electrocardio electrode plate and a preparation method thereof, wherein the brain electrocardio electrode plate comprises a base film and a functional surface, the functional surface is divided into a lead area, a plurality of electrode areas and an outer connection area according to the shape, and the lead area is connected between the electrode areas and extends to the outer connection area; the functional surface of the base film is sequentially provided with a basic conductive layer, a biological signal sensing layer and an anti-oxidation layer, the basic conductive layer and the biological signal sensing layer have substantially the same graph, and the biological signal sensing layer is provided with a sensing electrode and a sensing connecting lead; the sensing electrode is positioned in the electrode area, the sensing connecting lead is positioned in the lead area, the anti-oxidation layer covers the sensing connecting lead to prevent the sensing connecting lead of the biological signal sensing layer from being oxidized, and the sensing electrode of the biological signal sensing layer is exposed out of the anti-oxidation layer to realize stable signal transmission. The method and the device have the advantages of ensuring the quality of signal acquisition and improving the unstable effect of signal acquisition.

Description

Brain-heart electric electrode slice and preparation method thereof

Technical Field

The application relates to the technical field of electroencephalogram sensors, in particular to a brain electrocardio electrode plate and a preparation method thereof.

Background

Brain electrocardio electrode piece is the disposable consumables of attached human brain, can gather the biological signal of human brain, whether a certain function of people can be judged healthy through the biological signal of the brain of gathering, therefore brain electrocardio electrode piece needs the accurate biological signal of gathering human brain, the brain electricity electrode paster of general adoption uses individual layer PET or PI as the substrate on the existing market, and conductive paste and silver chloride thick liquid are printed to the single face, be regarded as the connecting lead and the contact electrode of brain electrocardio electrode piece respectively, but this brain electrocardio electrode piece easily receives external environment signal's interference at the during operation, lead to the signal of gathering inaccurate.

The quality of signal collection can be guaranteed to the brain electricity electrode sensor among the correlation technique, this brain electricity electrode sensor includes film PCB circuit layer, the adhesion layer of setting on film PCB circuit layer, contact pilotage layer and electrically conductive hydrogel, the both ends of film PCB circuit layer are grafting port and electrode core respectively, wherein the electrode core is provided with four, four through-holes have been seted up on the adhesion layer, the position of four through-holes sets up and big or small shape looks adaptation with the position of four electrode cores is corresponding, contact pilotage layer and electrically conductive hydrogel set gradually on the electrode core by supreme down, can increase the degree of contact with human skin through the contact pilotage, and electrically conductive hydrogel's electric conductive property is good, when guaranteeing this brain electricity electrode sensor simple structure, the quality of assurance signal, promote the effect of signal acquisition simultaneously low price, application cost has been reduced. However, when the electroencephalogram electrode sensor in the related art is used for collecting brain signals of the old and heavy-duty workers, the skin of the old and heavy-duty workers is rough, so that the signal collection is unstable in the signal transmission process, and even the signal is lost.

Therefore, the electroencephalogram electrode sensor in the technical scheme has the defects of unstable signal acquisition and signal loss when acquiring biological signals of the human brain.

Disclosure of Invention

In order to ensure the quality of signal acquisition and improve the problem of unstable signal acquisition, the application provides a brain electrocardio electrode plate and a preparation method thereof.

In a first aspect, the present application provides a brain heart electrode slice that adopts the following technical scheme:

an electroencephalogram electrode sheet, comprising:

the base film is provided with a functional surface, the functional surface is divided into a lead area, a plurality of electrode areas and an outer connection area according to the shape, and the lead area is connected between the electrode areas and extends to the outer connection area;

the basic conducting layer is printed and formed on the functional surface and is provided with a plurality of basic contact electrodes positioned in the electrode area and a plurality of basic connecting leads which are integrally connected with the corresponding basic contact electrodes, one end of each basic connecting lead is provided with a basic leading-out electrode, and the basic leading-out electrode is positioned on the outer connecting area;

the biological signal sensing layer is printed and formed on the basic conducting layer in the same graph, and is provided with a plurality of sensing electrodes which are positioned in the electrode area and are overlapped on the basic contact electrodes and a plurality of sensing connecting leads which are integrally connected with the corresponding sensing electrodes and are overlapped on the basic connecting leads;

and the anti-oxidation layer is arranged on the biological signal sensing layer and covers the sensing connecting lead of the biological signal sensing layer so as to prevent the sensing connecting lead of the biological signal sensing layer from being oxidized, and the sensing electrode of the biological signal sensing layer is exposed out of the anti-oxidation layer.

Based on the technical scheme, the base film is used as a basic bearing body and is used for bearing the basic conducting layer, the basic conducting layer is used for conducting electricity, the basic contact electrodes of the basic conducting layer are used for transmitting signals, the basic connecting lead is used for integrally connecting the adjacent basic contact electrodes, and the signals are transmitted to external equipment from the basic leading-out electrodes so as to realize the transmission of the signals; the biological signal sensing layer realizes signal interaction with human biological signals, the sensing electrode is superposed on the basic contact electrode, and the sensing connecting lead is superposed on the basic connecting lead, so that the signal transmission is more stable; because the biological signal sensing layer can be oxidized under the action of illumination and moisture in the air, and the electric conductivity of the biological signal sensing layer is low, the anti-oxidation layer is superposed on the biological signal sensing layer and covers the biological signal sensing layer to protect the biological signal sensing layer, and the sensing electrode is exposed out of the anti-oxidation layer to realize stable signal transmission.

Preferably, the anti-oxidation layer comprises a coating layer and a transparent protective film layer, the coating layer is provided with a covering lead layer and a covering outgoing layer, the covering lead layer is integrally connected with the covering outgoing layer, the covering lead layer is positioned on the lead area, the covering outgoing layer is positioned on the outer connection area, and the transparent protective film layer covers the coating layer.

Based on the technical scheme, the covering lead layer is positioned on the lead area, the covering connection outlet layer is positioned on the outer connection area, and the coating layer covers part of the biological signal sensing layer, so that the oxidation of the part of the biological signal sensing layer is avoided, and the transparent protective film is covered on the coating layer to protect the coating layer.

Preferably, the anti-oxidation layer is an opaque protective film layer, the opaque protective film layer is located on the lead area and the outer connection area, a through hole is formed in the base film, and the basic leading-out electrode is located in the through hole.

Based on above-mentioned technical scheme, cover opaque protection film layer on biological signal sensing layer, mainly be located lead wire district and external district to avoided biological signal sensing layer's oxidation, seted up the perforation on the base film, made basic conducting layer be connected with external equipment, thereby realized the transmission of signal.

Preferably, an adhesive foam sheet is arranged on the anti-oxidation layer, is located on the electrode area and is used for being adhered to human skin, a through hole is formed in the adhesive foam sheet, corresponds to the basic contact electrode, and is filled with hydrogel, so that the sensing electrode in hydrogel conduction can sense a biological signal.

Based on the technical scheme, the viscous foam sheet is positioned on the electrode area, when the brain heart electrode plate is used, the viscous foam sheet can be used for pasting the brain heart electrode plate to human skin, through the through hole formed in the viscous foam sheet, signal interaction between the sensing electrode and a human biological signal is achieved, and meanwhile, hydrogel is filled in the through hole, so that the signal can sense the biological signal through the hydrogel and the sensing electrode, and the signal interaction is achieved.

Preferably, the through hole, the sensing electrode and the basic contact electrode are all set to be circular, the radius of the through hole is larger than that of the sensing electrode, the radius of the sensing electrode is larger than that of the basic contact electrode, and the radius of the through hole is between 0.75 cm and 1.25 cm.

Based on above-mentioned technical scheme, the radius of through-hole is greater than sensing electrode's radius to avoid viscidity bubble cotton piece to shelter from sensing electrode, avoid hindering the signal interaction between sensing electrode and the human body.

Preferably, the sticky foam sheet is provided with a reinforcing part, the reinforcing part extends into the lead wire area connected with the electrode area, two notches are formed in the periphery of the through hole, the two notches are symmetrically arranged, the opening direction of each notch is consistent with the extending direction of the reinforcing part, and the thickness of the sticky foam sheet (50) is between 0.025 cm and 0.125 cm.

Based on the technical scheme, the through holes are provided with the notches at the peripheries, so that the condition that the hydrogel overflows is reduced when the through holes are filled with the hydrogel; if the thickness of the sticky foam sheet is too small, the sticky foam sheet is easy to deform, the thickness of the sticky foam sheet is between 0.025 cm and 0.125cm, and the sticky foam sheet can be favorably in contact with the skin of a human body, so that the stability of a signal value is improved.

Preferably, the basic connecting lead consists of a plurality of lead wires, and the gap between every two adjacent lead wires is 0.05-0.1 cm.

Based on above-mentioned technical scheme, through the distance between the restriction adjacent line of leading, avoid adjacent line of leading to be apart from too closely and produce signal interference.

Preferably, before the brain electrocardio electrode plate is used, the adhesive foam cotton sheet is covered with a sticker protective film.

Based on the technical scheme, the sticker protective film covers the sticky foam sheet to protect the viscosity of the sticky foam sheet.

In a second aspect, the present application provides a method for preparing a brain heart electrode slice, which adopts the following technical scheme:

the preparation method of the brain electrocardio electrode slice comprises the following steps:

providing a base film, wherein the base film is provided with a functional surface, and the functional surface is divided into a lead area, a plurality of electrode areas and an outer connection area;

printing a basic conducting layer on the base film, wherein the basic conducting layer is provided with a plurality of basic contact electrodes and a plurality of basic connecting leads connected with the corresponding basic contact electrodes, a basic leading-out electrode is formed at one end of each basic connecting lead, the basic contact electrodes are printed in the electrode area, the basic connecting leads are printed in the lead area, and the basic leading-out electrodes are printed in the outer connection area;

printing to form a biological signal sensing layer on the basic conducting layer, wherein the printed circuit of the biological signal sensing layer is the same as that of the basic conducting layer, and the biological signal sensing layer is provided with a plurality of sensing electrodes which are positioned in the electrode area and are overlapped on the basic contact electrodes and a plurality of sensing connecting leads which are integrally connected with the corresponding sensing electrodes and are overlapped on the basic connecting leads; the biological signal sensing layer is provided with an anti-oxidation layer, the anti-oxidation layer covers the sensing connecting lead of the biological signal sensing layer and is used for isolating light and moisture in air, the sensing connecting lead of the biological signal sensing layer is prevented from being oxidized, and the sensing electrode of the biological signal sensing layer is exposed out of the anti-oxidation layer.

Based on the technical scheme, the base film is used as a bearing body, the basic conducting layer, the biological signal sensing layer and the anti-oxidation layer are sequentially printed on the base film, wherein a functional surface of the base film is divided into a lead area, a plurality of electrode areas and an outer connection area, the basic conducting layer is provided with a plurality of basic contact electrodes, a basic connecting lead and a basic leading-out electrode, the basic contact electrodes are correspondingly arranged on the electrode areas, the basic connecting lead is correspondingly arranged in the lead area, the basic leading-out electrode is correspondingly arranged in the outer connection area, the basic conducting layer is used for conducting electricity, the pattern states of the biological signal sensing layer and the basic conducting layer are completely the same and completely cover the basic conducting layer, the anti-oxidation layer covers the sensing connecting lead through printing or UV technology, the oxidation of the biological signal sensing layer is avoided, the signal interaction with a human body is realized, and meanwhile, the signal is more stable.

Preferably, the thickness of the base film is between 0.03 and 0.1mm, and the thickness of the base conductive layer, the thickness of the biological signal sensing layer and the thickness of the oxidation prevention layer are between 4 and 10 micrometers.

Based on the technical scheme, the thickness of the base film is between 0.03 and 0.1mm, and the thicknesses of the basic conducting layer, the biological signal sensing layer and the anti-oxidation layer are between 4 and 10 micrometers, so that the signal transmission effect is more stable.

In summary, the present application includes at least one of the following beneficial technical effects:

1. the sensing electrodes are overlapped on a plurality of basic contact electrodes positioned in the electrode area, the sensing connecting leads are overlapped on a plurality of basic connecting leads which are integrally connected with the corresponding sensing electrodes, so that the signal transmission is more stable, and the sensing connecting leads are provided with anti-oxidation layers, so that the oxidation of a biological signal sensing layer is avoided;

2. the coating layer covers part of the biological signal sensing layer so as to avoid oxidation of the part of the biological signal sensing layer, and the transparent protective film covers the coating layer so as to protect the coating layer;

3. the non-transparent protective film layer covers the biological signal sensing layer and is mainly positioned on the lead area and the external connection area, and the base film is provided with the through holes, so that the base conductive layer is connected with external equipment, and the signal transmission is realized.

Drawings

Fig. 1 is a schematic view illustrating an overall structure of a brain cardiac electrode pad according to embodiment 1 of the present application;

fig. 2 is a schematic diagram illustrating an exploded structure of the brain cardiac electrode pad according to embodiment 1 of the present application;

fig. 3 is a cross-sectional view of a brain cardiac electrode pad according to embodiment 1 of the present application;

fig. 4 is a rear view of the brain cardiac electrode pad according to embodiment 2 of the present application;

fig. 5 is a schematic diagram illustrating an exploded structure of the brain cardiac electrode pad according to embodiment 2 of the present application;

FIG. 6 is a cross-sectional view of the brain-heart electrode pad of embodiment 2 of the present application;

FIG. 7 is a schematic diagram illustrating an exploded structure of a electroencephalogram electrode sheet in the prior art;

FIG. 8 is a schematic diagram illustrating an exploded structure of a related art ECG electrode pad;

fig. 9 is a flowchart illustrating a process for manufacturing a brain cardiac electrode pad according to embodiment 1 of the present application.

Description of reference numerals: 10. a base film; 11. a functional surface; 12. an electrode area; 13. a lead region; 14. an outer connection area; 15. perforating; 20. a base conductive layer; 21. a base contact electrode; 22. a base connection lead; 221. conducting wires; 23. a base extraction electrode; 30. a bio-signal sensing layer; 31. a sensing electrode; 32. a sensing connection lead; 33. a sensing lead-out electrode; 40. an oxidation-resistant layer; 41. coating a film layer; 411. covering the lead layer; 412. covering the receiving layer; 42. a transparent protective film layer; 43. an opaque protective film layer; 50. sticky foam sheets; 51. a reinforcing portion; 52. soaking a cotton layer; 521. a through hole; 522. a notch; 53. a sticking surface; 60. a hydrogel; 70. and sticking a protective film.

Detailed Description

The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, 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 present application, it should be noted that the terms "upper", "lower", "inner", "outer", "top/bottom", and the like indicate orientations or positional relationships based on those shown in the drawings, and are only for convenience of description and simplification of description, but do not indicate or imply that the referred device or element must have a specific orientation, be constructed in a specific orientation, and be operated, and thus should not be construed as limiting the present application.

In a first aspect, an embodiment of the application discloses a brain heart electrode slice.

Example 1:

referring to fig. 1 and 2, the brain heart electrode pad includes a base film 10, a base conductive layer 20, a bio-signal sensing layer 30, an oxidation preventing layer 40, and an adhesive foam sheet 50. The base film 10 is used as a basic carrier for carrying the base conductive layer 20, and the base conductive layer 20 is used for transmitting signals; the biological signal sensing layer 30 is printed and formed on the basic conducting layer 20, and the biological signal sensing layer 30 realizes signal interaction with human body signals; the anti-oxidation layer 40 completely covers the biological signal sensing layer 30, so that the biological signal sensing layer 30 is prevented from being exposed to sunlight and air, and the oxidation condition of the biological signal sensing layer 30 is improved; the sticky foam cotton sheet 50 is positioned on the anti-oxidation layer 40 and used for pasting and fixing the contact part for collecting the human body biological signals and placing the electroencephalogram electrode plate to fall off to cause inaccurate signal collection.

Referring to fig. 2, the base film 10 has a functional surface 11, the functional surface 11 serves as a circuit forming surface, the functional surface 11 is divided into four electrode regions 12, lead regions 13 and an external connection region 14 according to the shape, the lead regions 13 are connected between the electrode regions 12 to realize signal circulation between the electrode regions 12, the lead regions 13 extend outwards and are connected to the external connection region 14, the external connection region 14 is connected with external equipment, biological signals of a human body are transmitted to the external equipment through the electrode regions 12, the lead regions 13 and the external connection region 14 in sequence, and the signals are analyzed by the external equipment to obtain the condition of the human body. Wherein, base film 10 specifically chooses for use PET insulating film, usually opaque film, and base film 10 in this embodiment chooses for use is the non-transparent film of milk white to mark such as numeral symbol is printed on the back of this base film 10, also can choose for use other insulating film under the requirement that satisfies special properties such as ductility, dielectricity, etc. like PVC etc..

Referring to fig. 2, the basic conductive layer 20 is formed on the functional surface 11 by printing, the circuit layer has four basic contact electrodes 21 and basic connection leads 22, the four basic contact electrodes 21 are respectively connected with the four electrode regions 12, the basic contact electrodes 21 are integrally connected through the basic connection leads 22, one end of the basic connection lead 22 is integrally connected with one of the basic contact electrodes 21, the other end of the basic connection lead 22 is formed with a basic lead-out electrode 23, and the basic lead-out electrode 23 is located in the external connection region 14. The basic connection lead 22 is composed of a plurality of lead lines 221, and the gap between adjacent lead lines is between 0.05 cm and 0.1cm, so that signal interference caused by the close proximity of the adjacent lead lines 221 is avoided.

In the embodiment, the base conductive layer 20 is specifically formed by conductive silver paste, the conductive silver paste has better flexibility and toughness, the conductive silver paste is not easy to form a crease after being bent, the thickness of the conductive silver paste is between 4 μm and 10 μm, and preferably, the thickness of the conductive silver paste is 8 μm. In other embodiments, the base conductive layer 20 may also be a copper line or a conductive line formed by solidifying other conductive metals. In the present embodiment, the shape of the base contact electrode 21 is a circle, and is configured to be a circle so as to determine the center point of the base contact electrode 21, thereby reducing the amount of invalid corners of the base contact electrode 21, and in other embodiments, the shape of the base contact electrode 21 may be other shapes such as a square.

Referring to fig. 2, the bio-signal sensing layer 30 is printed on the base conductive layer 20, the bio-signal sensing layer 30 has four sensing electrodes 31, the four sensing electrodes 31 respectively cover the base contact electrodes 21, the base connection lead 22 is stacked with the sensing connection lead 32, the sensing connection lead 32 is integrally connected with the sensing electrodes 31, the sensing electrodes 31 and the base contact electrodes 21 have the same shape, the sensing connection lead 32 has the same shape as the base connection lead 22, the sensing connection lead 32 is extended outward to form the sensing lead electrodes 33, and the sensing lead electrodes 33 are stacked on the base lead electrodes 23. The biological signal sensing layer 30 is formed by solidifying silver chloride, wherein the thickness of the biological signal sensing layer 30 formed by solidifying the silver chloride is between 4 and 10 micrometers, preferably, the thickness of the silver chloride is 8 micrometers, the silver chloride can realize signal interaction with human biological signals, and the stability is improved when the human biological signals are collected.

Referring to fig. 2, the oxidation preventing layer 40 is disposed on the bio-signal sensing layer 30, and the oxidation preventing layer 40 can block light and moisture in the air, thereby preventing the bio-signal sensing layer 30 from being oxidized. The anti-oxidation layer 40 only covers the sensing connection lead 32, and the sensing electrode 31 and the sensing lead-out electrode 33 of the biological signal sensing layer 30 are exposed out of the anti-oxidation layer 40, so that signal interaction between the sensing electrode 31 and a human body is realized, and the stability of signal transmission is improved.

Referring to fig. 2, the oxidation preventing layer 40 includes a plated layer 41, the plated layer 41 has a covering lead layer 411, the covering lead layer 411 covers the sensing connection lead 32, a covering lead-out layer 412 is formed at one end of the covering lead layer 411, and the covering lead-out layer 412 covers the sensing lead-out electrode 33, so as to completely cover the exposed portion of the bio-signal sensing layer 30 and prevent the bio-signal sensing layer 30 from being oxidized.

Referring to fig. 2, the covering lead layer 411 is covered with a transparent protective film layer 42, so that the sensing electrode 31 is exposed out of the film coating layer 41, thereby realizing signal interaction between the sensing electrode 31 and the human body biological signal; and since the transparent protective film 42 does not cover the covering outgoing layer 412, the covering outgoing layer 412 is connected with an external device, so as to transmit signals to an external device for human body condition analysis. The plating layer 41 is formed by curing conductive silver paste, the conductive silver paste has better softness and toughness, a crease is not easy to form after bending, the thickness of the conductive silver paste is between 4 and 10 micrometers, and preferably, the thickness of the conductive silver paste is 8 micrometers. And the sheet resistance value of the silver chloride is between 1 and 200 omega, and the sheet resistance value of the conductive silver paste is about 6 omega, so that the conductivity is higher when the conductive silver paste is externally connected, and the signal transmission effect is improved.

Referring to fig. 2, the outline of the adhesive foam sheet 50 is substantially the same as the outline of the corresponding electrode region 12, the adhesive foam sheet 50 has a reinforcing portion 51, and the reinforcing portion 51 extends from the corresponding electrode region 12 to the lead region 13; the viscous foam sheet 50 has a foam layer 52, a through hole 521 is formed in the foam layer 52, a conductive area of the sensing electrode 31 is determined by an area of the through hole 521, the through hole 521 is generally circular, a radius of the through hole 521 is between 0.75 cm and 1.25cm, and the through hole 521 is filled with hydrogel 60, so that the sensing electrode 31 in the hydrogel 60 streets can detect a biological signal.

Referring to fig. 2, the thickness of the foam layer 52 is less than 0.125cm, two notches 522 are formed at the periphery of the through hole 521, the two notches 522 are arranged oppositely, when the hydrogel 60 is filled in the through hole 521, the excessive hydrogel 60 overflows into the notches 522, the overflow amount of the hydrogel 60 overflowing to the surface of the foam layer 52 is reduced, and the surface of the foam layer 52 is provided with an adhesive surface 53 so as to be convenient for adhering the brain heart electrode pad on the skin of a human body.

Referring to fig. 2, the thickness of the sticky foam sheet 50 is between 0.025 and 0.125cm, and the specific thickness is between 0.05 and 0.1cm, and if the thickness of the sticky foam sheet 50 is too small, the sticky foam sheet 50 is easy to deform, and when the thickness is between 0.05 and 0.1cm, the sticky foam sheet 50 is more beneficial to being in contact with the skin of a human body, so that the stability of a signal value is improved.

Referring to fig. 2, the adhesive surface 53 is provided with a sticker protective film 70, and when the brain heart electrode sheet is not used, the sticker protective film 70 covers the adhesive foam sheet 50 to protect the viscosity of the adhesive foam sheet 50.

The implementation principle of a brain electrocardio electrode piece of this application embodiment 1 does: the basal membrane 10 is used as a bearing body for bearing a basal conducting layer 20, a lead area 13 of the basal membrane 10 corresponds to a basal connecting lead 22 of the basal conducting layer 20, a basal leading-out electrode 23 corresponds to an outer connecting area 14, a basal contact electrode 21 corresponds to an electrode area 12 to realize the input and output of signals, a sensing electrode 31 is arranged on the basal contact electrode 21, a sensing connecting lead 32 is arranged on the basal connecting lead 22, a sensing leading-out electrode 33 is arranged on the basal leading-out electrode 23, a biological signal sensing layer 30 completely covers the basal conducting layer 20, the biological signal sensing layer 30 interacts with human body signals to improve the stability of the signals, coating layers 41 are arranged on the sensing connecting lead 32 and the sensing leading-out electrode 33 to avoid the oxidation of the biological signal sensing layer 30, and meanwhile, the electric conductivity of the coating layers 41 is higher than that of the biological signal sensing layer 30, so that the transmission of the signals is more stable.

Example 2

The embodiment of the present application differs from embodiment 1 in that: the anti-oxidation layer 40 is an opaque protective film layer 43, which reduces the film coating layer 41 of the conductive silver paste, and the phenomenon that the biological signal sensing layer 30 is oxidized in sunlight and air is avoided by covering the opaque protective film layer 43.

Referring to fig. 3 and 4, the opaque protective film 43 covers the sensing connection lead 32 and the sensing lead-out electrode 33, the bio-signal sensing layer 30 is protected by the opaque protective film 43, the base film 10 is provided with a through hole 15, and the base conductive layer 20 is exposed through the through hole 15 so as to be connected to an external device for signal transmission.

The principle is implemented to a brain electrocardio electrode piece of this application embodiment 2: cover sensing connection lead 32 through opaque protection rete 43, avoid the oxidation of sensing connection lead 32, realize the signal interaction with human biosignal, because the electric conductivity of biosignal sensing layer 30 is lower, consequently through having seted up perforation 15 on base film 10 to make things convenient for basic conducting layer 20 to be connected with external equipment, realize the stable transmission of signal.

Silver chloride can take place the oxidation under the illumination, also can take place the oxidation because of the influence of the humidity in the air simultaneously, consequently under the irradiation of 30W ultraviolet lamp, the control temperature is 20 ℃, and humidity is 60RH, carries out resistance change test to different brain heart electrode slice, and the test result is as follows:

referring to fig. 7, the electroencephalogram electrode plate in the prior art includes a base film 10, and a base conductive layer 20 and a bio-signal sensing layer 30 that are sequentially disposed on the base film 10, the bio-signal sensing layer 30 is only disposed in the electrode region 12, and is not provided with an oxidation prevention layer 40, and at this time, the electroencephalogram electrode plate is tested to obtain resistance changes within five weeks:

sample number	1	2	3	4	5
						Original resistance/omega	350	346	351	347	349
One cycle resistance/omega	355	352	356	352	355
						Two-week resistance/omega	359	357	360	357	360
Three cycle resistance/omega	365	363	366	363	364
						Resistance/omega all around	372	369	373	371	372
Five-cycle resistance/omega	380	375	381	378	380
						Difference/omega	30	29	30	31	31
Rate of change	8.6％	8.4％	8.5％	8.9％	8.9％

Referring to fig. 8, the related art brain heart electrode slice includes a base film 10, and a base conductive layer 20 and a biological signal sensing layer 30 sequentially disposed on the base film 10, the biological signal sensing layer 30 is printed on the base conductive layer 20 with substantially the same pattern, but is not provided with an oxidation preventing layer 40, and at this time, the brain heart electrode slice is tested to obtain a resistance change within five weeks:

sample number	1	2	3	4	5
						Initial resistance/omega	160	159	161	160	158
One cycle resistance/omega	171	169	171	170	169
						Two-week resistance/omega	183	181	180	181	179
Three cycle resistance/omega	195	193	196	194	189
						Resistance/omega all around	206	205	206	205	203
Five-cycle resistance/omega	218	217	220	217	215
						Difference/omega	58	58	59	57	57
Rate of change	36.3％	36.5％	36.6％	35.6％	36.1％

Resistance change in example 1 of the present application over five weeks:

sample number	1	2	3	4	5
						Original resistance/omega	89	90	86	85	87
One cycle resistance/omega	90	91	87	86	88
						Two-week resistance/omega	91	92	88	87	89
Three cycle resistance/omega	92	93	89	88	90
						Resistance/omega all around	93	9	90	89	91
Five-cycle resistance/omega	94	95	90	89	91
						Difference/omega	5	5	4	4	4
Rate of change	5.6％	5.6％	4.7％	4.7％	4.6％

Resistance change in five weeks of example 2 of the present application:

sample number	1	2	3	4	5
						Original resistance/omega	184	186	186	185	187
One cycle resistance/omega	186	188	188	186	189
						Two-cycle resistance/omega	188	190	190	189	191
Three cycle resistance/omega	190	192	192	191	193
						Resistance/omega all around	193	195	195	194	196
Resistance/omega five cycles	198	200	201	199	202
						Difference/omega	14	14	15	14	15
Rate of change	7.6％	7.5％	8.1％	7.6％	8.0％

The resistance in the data is an alternating current resistance for simulating bioelectricity after hydrogel is added, the electroencephalogram bioelectricity is weak and complicated, so that the lower the value of an alternating current signal is, the better the performance of the acquired signal is, the resistance change rate after five weeks is less than 10% and stable, and the smaller the change rate is, the more stable the electroencephalogram electrode plate is to signal acquisition is, through the comparison of the data, the lower the change rate of the embodiment 1 and the embodiment 2 in the application is, and therefore the stability of the acquisition of the human body biological signals is improved.

In the embodiment of the present application, the lower the ac resistance of the material is, the more stable the acquired signal is, and the lower the degree of external interference is, so by comparing the standard deviation ratios of the above 12 groups of material ratios, it can be obtained that the ac resistance of the material obtained by mixing 40% silver and 60% silver chloride is the most optimal, and therefore, the material obtained by mixing 40% silver and 60% silver chloride is selected in the embodiment of the present application.

In a second aspect, the embodiment of the application discloses a preparation method of a brain heart electrode slice.

The preparation method of the brain electrocardio electrode slice comprises the following steps:

step S1: providing a base film 10, wherein the base film 10 is provided with a functional surface 11, and the functional surface 11 is divided into a lead area 13, a plurality of electrode areas 12 and an outer connecting area 14;

step S2: printing a basic conducting layer 20 on the base film 10, wherein the basic conducting layer 20 comprises a plurality of basic contact electrodes 21 and a plurality of basic connecting leads 22 connected with the corresponding basic contact electrodes 21, a basic leading-out electrode 23 is formed at one end of each basic connecting lead 22, the basic contact electrodes 21 are printed in the electrode area 12, the basic connecting leads 22 are printed in the lead area 13, and the basic leading-out electrodes 23 are printed in the outer connecting area 14;

and step S3: printing to form a biological signal sensing layer 30 on the base conducting layer 20, wherein the biological signal sensing layer 30 is provided with a sensing electrode 31, a sensing connecting lead 32 and a sensing leading-out electrode 33, the sensing electrode 31 is superposed on the base contact electrode 21, the sensing connecting lead 32 is superposed on the base connecting lead 22, and the sensing leading-out electrode 33 is superposed on the base leading-out electrode 23;

and step S4: the anti-oxidation layer 40 is arranged on the biological signal sensing layer 30, the anti-oxidation layer 40 covers the sensing connection lead 32 of the biological signal sensing layer 30, and the sensing electrode 31 of the biological signal sensing layer 30 is exposed out of the anti-oxidation layer 40.

Specifically, the thickness of the base film 10 is between 0.03 mm and 0.1mm, the base conductive layer 20 is formed by curing conductive silver paste, the bio-signal sensing layer 30 is formed by curing silver chloride, the oxidation-preventing layer 40 is formed by curing conductive silver paste and then plating a transparent protective film 42, the oxidation-preventing layer 40 can also be only an opaque protective film 43, wherein the thicknesses of the base conductive layer 20, the bio-signal sensing layer 30 and the oxidation-preventing layer 40 are all between 4 μm and 10 μm, and preferably, the thicknesses of the base conductive layer 20, the bio-signal sensing layer 30 and the oxidation-preventing layer 40 in the embodiment are 8 μm.

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; such modifications and substitutions do not substantially depart from the spirit and scope of the embodiments of the present invention, and are intended to be included within the scope of the present invention.

Claims (10)

1. A brain electrocardio electrode slice, characterized by comprising:

a base film (10) having a functional surface (11), wherein the functional surface (11) is divided into a lead region (13), a plurality of electrode regions (12) and an outer connection region (14) according to the shape, and the lead region (13) is connected between the electrode regions (12) and extends to be connected to the outer connection region (14);

a basic conductive layer (20) printed on the functional surface (11), wherein the basic conductive layer (20) is provided with a plurality of basic contact electrodes (21) positioned in the electrode area (12) and a plurality of basic connecting leads (22) integrally connected with the corresponding basic contact electrodes (21), one end of each basic connecting lead (22) is provided with a basic leading-out electrode (23), and the basic leading-out electrodes (23) are positioned on the outer connecting area (14);

a biological signal sensing layer (30) printed with substantially the same pattern on the base conductive layer (20), wherein the biological signal sensing layer (30) has a plurality of sensing electrodes (31) which are positioned in the electrode regions (12) and are superposed on the base contact electrodes (21) and a plurality of sensing connection leads (32) which are integrally connected with the corresponding sensing electrodes (31) and are superposed on the base connection leads (22);

the anti-oxidation layer (40) is arranged on the biological signal sensing layer (30), the anti-oxidation layer (40) covers the sensing connecting lead (32) of the biological signal sensing layer (30) to prevent the sensing connecting lead (32) of the biological signal sensing layer (30) from being oxidized, and the sensing electrode (31) of the biological signal sensing layer (30) is exposed out of the anti-oxidation layer (40).

2. The brain-heart electrode slice of claim 1, wherein the oxidation prevention layer (40) comprises a coating layer (41) and a transparent protective film layer (42), the coating layer (41) has a covering lead layer (411) and a covering lead-out layer (412), the covering lead layer (411) and the covering lead-out layer (412) are integrally connected, the covering lead layer (411) is located on the lead area (13), the covering lead-out layer (412) is located on the outer connection area (14), and the transparent protective film layer (42) covers the coating layer (41).

3. The brain-heart electrode sheet according to claim 1, wherein the oxidation preventing layer (40) is an opaque protective film layer (43), the opaque protective film layer (43) is located on the lead region (13) and the outer connection region (14), a through hole (15) is formed in the base film (10), and the base lead-out electrode (23) is located in the through hole (15).

4. The brain-heart electrode slice according to claim 1, wherein an adhesive foam sheet (50) is arranged on the oxidation-resistant layer (40), the adhesive foam sheet (50) is located on the electrode area (12) and used for being adhered to the skin of a human body, a through hole (521) is formed in the adhesive foam sheet (50), the through hole (521) corresponds to the basic contact electrode (21), and hydrogel (60) is filled in the through hole (521) so that the sensing electrode (31) guided by the hydrogel (60) can sense a biological signal.

5. The brain electrocardio electrode pad of claim 4, wherein the through hole (521), the sensing electrode (31) and the base contact electrode (21) are all provided in a circular shape, the radius of the through hole (521) is larger than that of the sensing electrode (31), the radius of the sensing electrode (31) is larger than that of the base contact electrode (21), and the radius of the through hole (521) is between 0.75 cm and 1.25 cm.

6. The brain-heart electrode pad according to claim 4, wherein the viscous foam sheet (50) has a reinforcing portion (51), the reinforcing portion (51) extends into the lead region (13) connected to the electrode region (12), two notches (522) are formed in the periphery of the through hole (521), the two notches (522) are symmetrically arranged, the opening direction of the notches (522) is consistent with the extending direction of the reinforcing portion (51), and the thickness of the viscous foam sheet (50) is 0.025-0.125 cm.

7. The brain-heart electrode pad according to claim 1, wherein the basic connection lead (22) is composed of a plurality of lead wires (221), and a gap between adjacent lead wires (221) is between 0.05 and 0.1 cm.

8. The brain electrocardiac electrode sheet according to claim 4, wherein said adhesive foam sheet (50) is covered with a sticker protective film (70) before use.

9. The preparation method of the brain electrocardio electrode plate is characterized by comprising the following steps of:

providing a base film (10), wherein the base film (10) is provided with a functional surface (11), and the functional surface (11) is divided into a lead area (13), a plurality of electrode areas (12) and an external connection area (14);

printing a basic conductive layer (20) on the base film (10), wherein the basic conductive layer (20) is provided with a plurality of basic contact electrodes (21) and a plurality of basic connecting leads (22) connected with the corresponding basic contact electrodes (21), one end of each basic connecting lead (22) is provided with a basic leading-out electrode (23), the basic contact electrodes (21) are printed in the electrode area (12), the basic connecting leads (22) are printed in the lead area (13), and the basic leading-out electrodes (23) are printed in the outer connecting area (14);

printing a biological signal sensing layer (30) on the base conducting layer (20), wherein the printed circuit of the biological signal sensing layer (30) is the same as that of the base conducting layer (20), and the biological signal sensing layer (30) is provided with a plurality of sensing electrodes (31) which are positioned in the electrode area (12) and are overlapped on the base contact electrodes (21) and a plurality of sensing connecting leads (32) which are integrally connected with the corresponding sensing electrodes (31) and are overlapped on the base connecting leads (22);

an anti-oxidation layer (40) is arranged on the biological signal sensing layer (30), the anti-oxidation layer (40) covers the sensing connecting lead (32) of the biological signal sensing layer (30) to isolate light and moisture in air, the sensing connecting lead (32) of the biological signal sensing layer (30) is prevented from being oxidized, and the sensing electrode (31) of the biological signal sensing layer (30) is exposed out of the anti-oxidation layer (40).

10. The method for preparing the brain electrocardio-electrode sheet according to the claim 7, wherein the thickness of the base film (10) is between 0.03 and 0.1mm, and the thicknesses of the base conductive layer (20), the biological signal sensing layer (30) and the oxidation preventing layer (40) are between 4 and 10 μm.

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