CN114947866A - Electrocardio sensor and manufacturing method thereof - Google Patents

Abstract

The application relates to an electrocardio sensor and a manufacturing method thereof, wherein the electrocardio sensor comprises an electrode, a non-woven fabric adhesive tape and conductive hydrogel; the electrode is arranged on the adhesive surface of the non-woven fabric adhesive tape and is connected with the electrocardiogram host machine through a first through hole formed in the non-woven fabric adhesive tape; the conductive hydrogel is arranged on one side of the electrode, which is far away from the non-woven fabric adhesive tape, and the adhesive surface of the conductive hydrogel and the non-woven fabric adhesive tape is used for being pasted on an object to be detected. The application provides an electrocardio sensor when being connected with electrocardio host computer and detected object, operating procedure is simple, and is difficult to drop.

Description

Electrocardio sensor and method for manufacturing electrocardio sensor

Technical Field

The application relates to the technical field of electrocardio detection, in particular to an electrocardio sensor and a manufacturing method of the electrocardio sensor.

Background

With the development of science and technology, bioelectricity (such as electroencephalogram, electromyogram, electrocardiography, etc.) measurement has been widely applied to various basic rehabilitation devices for detection diagnosis and bioelectricity feedback.

The conventional wearable electrocardiograph is equipped with a dedicated electrocardiograph sensor, which is usually applied to the skin of a subject by using skin glue. However, the conventional electrocardiograph sensor has a problem that the operation steps are complicated and the connection is easily disconnected when the electrocardiograph sensor is connected to the electrocardiograph recorder and the object to be detected.

Disclosure of Invention

In view of the above, it is necessary to provide an electrocardiograph sensor and a method of manufacturing the electrocardiograph sensor.

In one aspect, an embodiment of the present application provides an electrocardiograph sensor, including: electrodes, non-woven fabric tape and conductive hydrogel;

the electrode is arranged on the adhesive surface of the non-woven fabric adhesive tape and is connected with the electrocardiogram host machine through a first through hole formed in the non-woven fabric adhesive tape;

the conductive hydrogel is arranged on one side of the electrode, which is far away from the non-woven fabric adhesive tape, and the adhesive surface of the conductive hydrogel and the non-woven fabric adhesive tape is used for being pasted on an object to be detected.

In one embodiment, the electrocardiograph sensor further comprises an adhesive layer, and a first release liner arranged on the first surface of the adhesive layer; the second surface of the bonding layer is arranged on the non-adhesive surface of the non-woven fabric adhesive tape, and the bonding layer is used for connecting the non-adhesive surface of the non-woven fabric adhesive tape with the electrocardiogram host.

In one embodiment, an electrode includes a thin film substrate, a first conductive layer, a second conductive layer, and a conductive body;

the thin film substrate comprises a first surface and a second surface, the first conducting layer is arranged on the first surface of the thin film substrate, and the second conducting layer is arranged on the second surface of the thin film substrate;

the electric conductor penetrates through the film substrate and is used for conducting the first conducting layer and the second conducting layer.

In one embodiment, the conductive body includes a conductive hole formed in the film substrate, and a conductive ink disposed in the conductive hole.

In one embodiment, the electrode further comprises: the insulating layer is arranged between the electrode and the adhesive surface of the non-woven fabric adhesive tape, the insulating layer is provided with a second through hole, and the position of the second through hole is consistent with that of the first through hole in the preset direction.

In one embodiment, the electrocardiograph sensor further comprises a second release substrate, and the second release substrate is disposed on a side of the conductive hydrogel away from the electrode.

In another aspect, an embodiment of the present application provides a method for manufacturing an electrocardiograph sensor, where the method includes:

applying the adhesive surface of the non-woven fabric adhesive tape to the first surface of the electrode;

a conductive hydrogel is coated on the second surface of the electrode.

In one embodiment, before applying the adhesive side of the nonwoven tape to the first surface of the electrode, the method further comprises:

arranging the second surface of the electrode on the silica gel protective film;

after applying the adhesive side of the nonwoven tape to the first surface of the electrode, the method further comprises:

and removing the silica gel protective film.

In one embodiment, the method further comprises:

printing conductive ink on the first surface of the film substrate to form a first conductive layer, and printing silver/silver chloride slurry on the second surface of the film substrate to form a second conductive layer; the first conducting layer is the first surface of the electrode, and the second conducting layer is the second surface of the electrode;

and punching holes on the film substrate, and plugging the holes by using conductive ink to form a conductor.

In one embodiment, after printing the conductive ink on the first surface of the film substrate to form the first conductive layer, the method further includes:

and printing insulating oil on the first conducting layer except the area connected with the electrocardio host to form an insulating layer.

The embodiment of the application provides an electrocardio sensor and a manufacturing method thereof, wherein the electrocardio sensor comprises an electrode, a non-woven fabric adhesive tape and conductive hydrogel; the electrode is arranged on the adhesive surface of the non-woven fabric adhesive tape and is connected with the electrocardiogram host machine through a first through hole formed in the non-woven fabric adhesive tape; the conductive hydrogel is arranged on one side of the electrode, which is far away from the non-woven fabric adhesive tape, and the adhesive surface of the conductive hydrogel and the non-woven fabric adhesive tape is used for being pasted on an object to be detected. The electrocardio sensor that this embodiment provided pastes on the skin of waiting to detect the object through the area face of gluing of non-woven fabric sticky tape, and the laminating nature is good, the gas permeability is good, waterproof nature is good, can not drop from the skin when meeting water. In actual use, the adhesive surface of the non-woven fabric adhesive tape and the surface of the conductive hydrogel connected with the object to be detected are provided with release liners. When the electrocardio sensor is used, the release substrate is directly torn off and is pasted on the skin of an object to be detected, so that the electrocardio sensor is connected with the object to be detected, and the electrocardio sensor is very simple to operate.

Drawings

In order to more clearly illustrate the technical solutions in the embodiments or the conventional technologies of the present application, the drawings used in the description of the embodiments or the conventional technologies will be briefly introduced below, it is obvious that the drawings in the following description are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to these drawings without creative efforts.

Fig. 1 is a diagram illustrating an application scenario of an electrocardiograph sensor according to an embodiment;

FIG. 2 is a schematic diagram of an embodiment of an electrocardiograph sensor;

FIG. 3 is a schematic diagram of a configuration of an ECG sensor according to another embodiment;

FIG. 4 is a schematic diagram of a configuration of an ECG sensor according to another embodiment;

FIG. 5 is a schematic diagram of a configuration of an ECG sensor according to another embodiment;

FIG. 6 is a schematic flow chart illustrating steps of a method for manufacturing an electrical heart sensor, according to an exemplary embodiment;

FIG. 7 is a schematic flow chart illustrating steps of a method for manufacturing an ECG sensor according to another embodiment;

FIG. 8 is a schematic flow chart illustrating steps of a method for manufacturing an ECG sensor according to another embodiment;

FIG. 9 is a schematic diagram of a first conductive layer pattern according to one embodiment;

FIG. 10 is a schematic diagram of a second conductive layer pattern according to one embodiment;

fig. 11 is a schematic flowchart illustrating steps of a method for manufacturing an electrocardiograph sensor according to another embodiment.

Description of reference numerals:

10. an electrocardiograph sensor; 20. an electrocardio host; 100. an electrode; 101. a first through hole; 110. a thin film substrate; 111. a first surface; 112. a second surface; 120. a first conductive layer; 130. a second conductive layer; 140. an electrical conductor; 150. an insulating layer; 151. a second through hole; 200. a non-woven fabric tape; 201. a surface with glue; 202. a non-adhesive surface; 300. a conductive hydrogel; 400. an adhesive layer; 410. a first release liner; 500. a second release liner.

Detailed Description

In order to make the aforementioned objects, features and advantages of the present application more comprehensible, embodiments accompanying the present application are described in detail below with reference to the accompanying drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. This application is capable of embodiments in many different forms than those described herein and that modifications may be made by one skilled in the art without departing from the spirit and scope of the application and it is therefore not intended to be limited to the specific embodiments disclosed below.

The numbering of the components as such, e.g., "first", "second", etc., is used herein only to distinguish the objects as described, and does not have any sequential or technical meaning. The term "connected" and "coupled" when used in this application, unless otherwise indicated, includes both direct and indirect connections (couplings). In the description of the present application, it is to be understood that the terms "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", and the like, indicate orientations or positional relationships based on those shown in the drawings, and are used only for convenience in describing the present application and for simplicity in description, and do not indicate or imply that the devices or elements referred to must have a particular orientation, be constructed in a particular orientation, and be operated, and thus, are not to be considered as limiting the present application.

In this application, unless expressly stated or limited otherwise, the first feature "on" or "under" the second feature may be directly contacting the first and second features or indirectly contacting the first and second features through intervening media. Also, a first feature "on," "over," and "above" a second feature may be directly or diagonally above the second feature, or may simply indicate that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature may be directly under or obliquely under the first feature, or may simply mean that the first feature is at a lesser elevation than the second feature.

First, before specifically describing the technical solution of the embodiment of the present disclosure, a technical background or a technical evolution context on which the embodiment of the present disclosure is based is described. The conventional wearable electrocardiograph is equipped with a dedicated electrocardiograph sensor, which is usually applied to the skin of a subject by using skin glue. Specifically, the skin adhesive selects skin dressing as a foam adhesive dressing product. However, the human body surface and the skin surface are conducted by positive and negative skin glue, so that high alternating current resistance is easily caused, and an electrocardiogram monitoring error is caused; and the skin glue has poor air permeability, complex interlayer structure and complex operation steps in the using process.

As shown in fig. 1, the electrocardiograph sensor 10 provided by the present application can be connected to an electrocardiograph host 20. The electrocardiogram host 20 is used for receiving an electrocardiogram signal of the object to be detected by the electrocardiogram sensor. The present embodiment does not limit the specific structure of the electrocardiogram host 20.

The following describes the technical solutions of the present application and how to solve the technical problems with the technical solutions of the present application in detail with specific embodiments. These several specific embodiments may be combined with each other below, and details of the same or similar concepts or processes may not be repeated in some embodiments. Embodiments of the present application will be described below with reference to the accompanying drawings.

Referring to fig. 2, an embodiment of the present application provides an ecg sensor 10. The electrocardiograph sensor 10 includes an electrode 100, a nonwoven fabric tape 200, and a conductive hydrogel 300.

The electrode 100 is a device for inputting or outputting current in the electrocardiograph sensor 10. The non-woven tape 200 includes an adhesive side 201 and a non-adhesive side 202. The conductive hydrogel 300 may be classified into an electron conductive hydrogel and an ion conductive hydrogel. The present embodiment does not limit the type of the conductive hydrogel 300 as long as the function thereof can be achieved.

The electrode 100 is arranged on the adhesive surface 201 of the non-woven fabric adhesive tape 200, and the electrode 100 is connected with the electrocardiograph main unit 20 through a first through hole 101 formed in the non-woven fabric adhesive tape 200. The non-woven fabric tape 200 is provided with a plurality of first through holes 101, and the electrode 100 is connected with the electrocardiograph host 210 through the first through holes 101 on the non-woven fabric tape on the tape surface 201 of the non-woven fabric tape 200, so as to transmit the signal detected by the electrocardiograph sensor 10 to the electrocardiograph host 20.

The conductive hydrogel 300 is disposed on a side of the electrode 100 away from the non-woven fabric tape 200, and the conductive hydrogel 300 and the adhesive surface 201 of the non-woven fabric tape 200 are used for being attached to an object to be detected. Electrode 100 includes a first side and a second side, and conductive hydrogel 300 also includes a first side and a second side. The adhesive surface 201 of the non-woven fabric adhesive tape 200 is arranged opposite to the first surface of the electrode 100, the first surface of the conductive hydrogel 300 is arranged opposite to the second surface of the electrode 100, and the adhesive surface of the non-woven fabric adhesive tape 200 and the second surface of the conductive hydrogel 300 are pasted on an object to be detected. In other words, the first surface of the electrode 100 is connected to the adhesive surface 201 of the non-woven fabric tape 200, the second surface of the electrode 100 is connected to the first surface of the conductive hydrogel 300, the second surface of the conductive hydrogel 300, and the area of the adhesive surface of the non-woven fabric tape 200 not connected to the first surface of the electrode 100 are connected to the object to be detected.

The operation principle of the electrocardiograph sensor 10 provided in this embodiment is as follows: the electrode 100 is connected with the electrocardiogram main machine 20 through the first through hole 101, and the area of the non-woven fabric adhesive tape 200, the adhesive surface of which is not connected with the first surface of the electrode 100, and the conductive hydrogel 300 are connected with the object to be detected. The electrocardiosignal of the object to be detected is transmitted to the electrocardio host 20 through the conductive hydrogel 300 and the electrode 100. The electrocardiograph 20 can process and display the received electrocardiograph signal.

The electrocardiograph sensor 10 provided by the embodiment of the present application includes an electrode 100, a non-woven fabric tape 200, and a conductive hydrogel 300. The electrode 100 is arranged on the adhesive surface 201 of the non-woven fabric adhesive tape 200, and the electrode 100 is connected with the electrocardiogram main machine 20 through a first through hole 101 formed in the non-woven fabric adhesive tape 200; the conductive hydrogel 300 is disposed on a side of the electrode 100 away from the non-woven fabric tape 200, and the conductive hydrogel 300 and the adhesive surface 201 of the non-woven fabric tape 200 are used for being attached to an object to be detected. The electrocardiograph sensor 10 provided in this embodiment is applied to the skin of the subject to be detected through the adhesive surface 201 of the nonwoven tape 200, and has good applicability, good air permeability, and good water resistance, and does not fall off from the skin when encountering water.

In one embodiment, as shown in FIG. 3, the electrocardiograph sensor 10 further includes an adhesive layer 400, and a first release substrate 410 disposed on a first side of the adhesive layer 400. The adhesive layer 400 includes a first side and a second side. The second surface of the adhesive layer 400 is disposed on the non-adhesive surface 202 of the nonwoven tape 200, and the first surface of the adhesive layer 400 is used for connecting the non-adhesive surface 202 of the nonwoven tape 200 with the electrocardiograph 20. In other words, the second surface of the adhesive layer 400 is connected to the non-adhesive surface 202 of the non-woven fabric tape 200, and the first release liner 410 disposed on the first surface of the adhesive layer 400 is peeled off, so that the first surface of the adhesive layer 400 is connected to the electrocardiograph main unit 20, that is, the electrocardiograph sensor 10 is connected to the electrocardiograph main unit 20. The present embodiment does not limit the specific material used for the adhesive layer 400 as long as the function thereof can be achieved.

In this embodiment, the adhesive layer 400 is disposed on the non-adhesive surface 202 of the non-woven adhesive tape 200, and the first release liner 410 is disposed on the first surface of the adhesive layer 400, so that the non-adhesive surface 202 of the non-woven adhesive tape 200 can be connected to the electrocardiograph main unit 20 by directly tearing off the first release liner 410 during actual use, and the electrocardiograph sensor 10 and the electrocardiograph main unit 20 can be conveniently connected. In addition, the first release liner 410 can protect the first surface of the adhesive layer 400, thereby ensuring the adhesiveness of the first surface of the adhesive layer 400. Moreover, the adhesive layer 400 with good waterproof property can ensure that the main electrocardiograph unit 20 and the electrocardiograph sensor 10 (the non-adhesive surface of the non-woven fabric tape 100) are not separated when meeting water, and can improve the sealing performance between the electrocardiograph sensor 10 and the main electrocardiograph unit 20.

In one embodiment, as shown in fig. 4, electrode 100 includes a thin film substrate 110, a first conductive layer 120, a second conductive layer 130, and an electrical conductor 140.

The film substrate 110 is the result of a combination of ceramic materials and film metallization techniques. Specifically, the film substrate 110 may be a PET polyester film, and the film substrate 110 includes a first surface 111 and a second surface 112. The first conductive layer 120, the second conductive layer 130, and the conductive body 140 may be made of the same conductive material, or may be made of different conductive materials.

The first conductive layer 120 is disposed on the first surface 111 of the film substrate 110, and the second conductive layer 130 is disposed on the second surface 112 of the film substrate 110. The conductive body 140 is disposed through the film substrate 110 for conducting the first conductive layer 120 and the second conductive layer 130. In other words, the first surface 111 and the second surface 112 of the film substrate 110 are provided with the first conductive layer 120 and the second conductive layer 130, respectively, and the conductive body 140 penetrates the film substrate 110 to make the first conductive layer 120 and the second conductive layer 130 conductive.

The electrode 100 provided in this embodiment includes a thin film substrate 110, a first conductive layer 120, a second conductive layer 130, and a conductive body 140. The electrode 100 is simple in structure and easy to manufacture.

In one embodiment, the conductive body 140 includes a conductive hole formed in the film substrate 110 and a conductive ink disposed in the conductive hole. In other words, the conductive body 140 in the electrode 100 includes a conductive hole and a conductive ink, wherein the conductive hole is a through hole opened in the film substrate 100. The conductive ink is made of a conductive material and has a certain conductive property. The conductive ink fills the conductive hole to form the conductive body 140. The conductive material used in the conductive ink is not limited in this embodiment as long as the function thereof can be achieved.

In the present embodiment, the conductive body 140 has a simple structure and is easy to manufacture.

In one embodiment, the conductive body 140 is formed by forming a through hole in the film substrate 100 and filling the through hole with conductive ink.

Referring to fig. 5, in an embodiment, the electrode 100 further includes an insulating layer 150, the insulating layer 150 is disposed between the electrode 100 and the adhesive surface 201 of the non-woven fabric adhesive tape 200, the insulating layer 150 is provided with a second through hole 151, and the second through hole 151 is consistent with the first through hole 101 in a predetermined direction. If the non-woven fabric tape 200 and the electrode 100 are horizontally disposed and the first through-hole 101 is formed in the non-woven fabric tape 200 in the vertical direction, the second through-hole 151 is formed in the insulating layer 150 in the vertical direction at the same position as the first through-hole 101 of the non-woven fabric tape 200.

In other words, the insulating layer 150 is provided between the electrode 100 and the tape surface 201 of the nonwoven tape 200. The insulating layer 150 is provided with a second through hole 151, and the second through hole 151 formed in the insulating layer 150 is arranged opposite to the first through hole 101 formed in the non-woven fabric tape 200, so that the electrode 100 can be connected with the electrocardiograph 20 through the second through hole 151 in the insulating layer 150 and the first through hole 101 in the non-woven fabric tape 200.

In this embodiment, the insulating layer is provided between the electrode 100 and the adhesive surface 201 of the non-woven adhesive tape 200, so that leakage of the electrocardiographic signal on the electrode 100 is avoided, and the stability and reliability of the electrocardiographic signal detection by the electrocardiographic sensor 10 can be improved.

In one embodiment, the second conductive layer 130 includes silver/silver chloride paste. That is, the conductive material used for the second conductive layer 130 includes silver/silver chloride slurry. The materials used for the first conductive layer 120 and the second conductive layer 130 may be the same, and the conductive material used for the first conductive layer 120 may also include silver/silver chloride slurry.

In this embodiment, the second conductive layer 130 and the first conductive layer 120 made of conductive materials of silver/silver chloride paste can better realize the transmission of the electrocardiograph signal, and provide the reliability of the electrocardiograph sensor 10 in detecting the electrocardiograph signal.

With continued reference to fig. 5, in one embodiment, the electrocardiograph sensor 10 further includes a second release substrate 500, and the second release substrate 500 is disposed on a side of the conductive hydrogel 300 away from the electrode 100. Meanwhile, the second release liner 500 is also connected to a region where the adhesive surface of the non-woven fabric tape 200 is not connected to the electrode 100. That is, the second release liner 500 can completely cover the adhesive surfaces of the conductive hydrogel 300 and the nonwoven fabric tape 200.

In this embodiment, the second release liner 500 is used to cover the adhesive surfaces of the conductive hydrogel 300 and the non-woven fabric tape 200, so as to ensure the adhesive surfaces of the non-woven fabric tape 200 and the conductive hydrogel 300, so that the electrocardiograph sensor 10 is more closely attached to the skin of the object to be detected and is not easy to fall off. In addition, when the mask is actually used, the second release liner 500 is directly torn off and is pasted on the skin of the object to be detected, so that the connection with the object to be detected is realized, and the operation is very simple.

Referring to fig. 6, an embodiment of the present application provides a method for manufacturing an electrocardiograph sensor, which is used to manufacture the electrocardiograph sensor 10 according to the above embodiment. The method comprises the following steps:

step 600, pasting the adhesive surface of the non-woven fabric adhesive tape on the first surface of the electrode.

And obtaining the manufactured electrode and the non-woven fabric adhesive tape. Generally, the adhesive side of the nonwoven fabric tape has a release liner. Before the electrode is horizontally placed and the adhesive surface of the non-woven fabric adhesive tape is attached to the first surface of the electrode, the release liner on the adhesive surface of the non-woven fabric adhesive tape is torn off, and then the adhesive surface of the non-woven fabric adhesive tape is attached to the upper surface or the lower surface (the first surface) of the electrode.

Step 610, covering the second surface of the electrode with a conductive hydrogel.

And (3) obtaining conductive hydrogel, covering the conductive hydrogel on the second surface of the electrode, wherein when the electrode is horizontally placed, the second surface of the electrode is the upper surface or the lower surface of the electrode. If the adhesive surface of the non-woven fabric adhesive tape is on the upper surface of the electrode, the conductive hydrogel is on the lower surface of the electrode; if the adhesive surface of the non-woven fabric adhesive tape is on the lower surface of the electrode, the conductive hydrogel is on the upper surface of the electrode.

The conductive hydrogel can cover only the area where the electrode is located, or can cover the area larger than the area where the electrode is located, as long as the conductive hydrogel can cover the electrode.

The manufacturing method of the electrocardio sensor provided by the embodiment of the application is simple and easy to understand and easy to realize. Moreover, the electrocardio sensor can be manufactured by the method provided by the embodiment, so that all beneficial effects of the electrocardio sensor are achieved, and the details are not repeated.

Referring to fig. 7, in one embodiment, before the applying the adhesive surface of the non-woven adhesive tape to the first surface of the electrode, the method for manufacturing the electrocardiograph sensor further includes the steps of:

and 700, arranging the second surface of the electrode on the silica gel protective film.

After applying the adhesive side of the nonwoven tape to the first surface of the electrode, the method further comprises:

and step 710, removing the silica gel protective film.

Before the adhesive surface of the non-woven fabric adhesive tape is arranged on the first surface of the electrode, the second surface of the electrode is arranged on the silica gel protective film, namely, the bottom of the electrode is supported by the silica gel protective film. In other words, the second surface of the electrode was placed on the silicone protective mold, and the adhesive side of the nonwoven tape was applied to the first surface of the electrode. The area of the electrode is smaller than the area of the adhesive surface of the non-woven fabric adhesive tape, and the area of the adhesive surface of the non-woven fabric adhesive tape, which is not pasted with the electrode, is pasted on the silica gel protection mold.

After the adhesive surface of the non-woven fabric adhesive tape is attached to the first surface of the electrode, the conductive hydrogel needs to be covered on the second surface of the electrode, and then the silica gel protective mold arranged on the second surface of the electrode needs to be torn off, so that the next manufacturing step can be conveniently carried out.

In this embodiment, through the second surface at the electrode set up the silica gel protection mould for after the area face of gluing of non-woven fabrics sticky tape applies the first surface of electrode, the silica gel protection film can avoid not applying in the area face of gluing of non-woven fabrics sticky tape and causing the pollution in the electrode area, thereby can guarantee that the area face of gluing of non-woven fabrics sticky tape can be better the subsides apply on detected object's skin, can not follow and drop on the skin.

Referring to FIG. 8, in one embodiment, the electrodes of the ECG sensor may be pre-fabricated. The manufacturing method of the electrode in the electrocardio sensor comprises the following steps:

step 800, printing conductive ink on a first surface of a film substrate to form a first conductive layer, and printing silver/silver chloride slurry on a second surface of the film substrate to form a second conductive layer; the first conducting layer is the first surface of the electrode, and the second conducting layer is the second surface of the electrode;

obtaining a film substrate, and printing a conductive material on a first surface of the film substrate to form a first conductive layer; and printing a conductive material on the second surface of the film substrate to form a second conductive layer. The first conductive layer is used as the first surface of the electrode, and the second conductive layer is used as the second surface of the electrode. The conductive material printed on the first surface and the second surface of the film substrate may be the same or different. In this embodiment, the conductive material printed on the first surface of the film substrate is conductive ink, and the conductive material printed on the second surface of the film substrate is silver/silver chloride slurry.

Step 810, punching holes on the film substrate, and plugging the holes by using conductive ink to form a conductor.

After the first conducting layer and the second conducting layer are printed, holes are punched in the film substrate, and the holes are plugged by using a conducting material to form a conductor, wherein the conductor can conduct the first conducting layer on the first surface of the film substrate and the second conducting layer on the second surface of the film substrate. The conductive material used in this example is a conductive ink.

The method for manufacturing the electrode is simple and easy to implement. In addition, the electrode provided by the embodiment is prepared by adopting a printing mode, the acquired electrocardiosignals are stable and reliable, the alternating current impedance is small, and the alternating current impedance can be controlled within 200 ohms.

In an alternative embodiment, the conductive material printed on the first surface and the second surface of the thin film substrate, respectively, may be printed in a specific pattern. Specifically, the pattern printed on the first surface is shown in fig. 9, and the pattern printed on the second surface is shown in fig. 10.

In one embodiment, after printing the conductive ink on the first surface of the film substrate to form the first conductive layer, the method for manufacturing the electrocardiograph sensor further includes:

and printing insulating oil on the first conducting layer except the area connected with the electrocardio host to form an insulating layer.

The insulating layer may be formed during or after the electrode is formed. If the insulating oil is printed in the process of manufacturing the electrode, the conductive ink is printed on the first surface of the film substrate to form a first conductive layer, and then the insulating oil is printed on the first conductive layer to form an insulating layer. When the insulating oil is printed, the area connected with the electrocardio host on the conducting layer is not required to be printed, so that the normal connection between the electrode and the electrocardio host is ensured. If the insulating oil is printed after the electrode is manufactured, namely, the electrode is obtained, and the insulating oil is printed on the first surface of the electrode except the area connected with the electrocardio host to form an insulating layer.

In this embodiment, the insulating layer is disposed on the first surface of the electrode 100, so that the leakage of the electrocardiographic signal on the electrode 100 can be avoided, and the stability and reliability of the electrocardiographic signal detection by the electrocardiographic sensor 10 can be improved.

In one embodiment, the method for manufacturing the electrocardiograph sensor further comprises:

an adhesive layer is arranged on the non-adhesive surface of the non-woven adhesive tape except the area connected with the electrocardiogram main machine, and the electrode is connected with the electrocardiogram main machine through a first through hole arranged on the non-woven adhesive tape by the adhesive layer.

In this embodiment, the use of the adhesive layer 400 simplifies the connection between the non-adhesive surface 202 of the non-woven adhesive tape 200 and the electrocardiograph main unit 20, and simplifies the operation steps when using the electrocardiograph sensor.

Referring to fig. 11, an embodiment of the present application provides a method for manufacturing an electrocardiograph sensor, the method includes:

step 110, printing conductive ink on the first surface of the film substrate to form a first conductive layer, and printing silver/silver chloride slurry on the second surface of the film substrate to form a second conductive layer; the first conducting layer is the first surface of the electrode, and the second conducting layer is the second surface of the electrode;

step 111, printing insulating oil on the first conducting layer except an area connected with the electrocardio host to form an insulating layer;

112, punching holes on the film substrate, plugging the holes by using conductive ink to form a conductor, and obtaining an electrode;

step 113, arranging the second surface of the electrode on the silica gel protective film;

step 114, pasting the adhesive surface of the non-woven fabric adhesive tape on the first surface of the electrode, and removing the silica gel protection mold;

step 115, mounting a silica gel protective film on the chopped release layer surface on one side of the conductive hydrogel, tearing off the release liner on the other side of the conductive hydrogel, and covering the release liner on the second surface of the electrode;

step 116, removing the silica gel protective film, and arranging a second release liner on the adhesive surface of the non-woven fabric adhesive tape and the surface of the conductive hydrogel, which is far away from the electrode;

step 117, arranging the bonding layer on the non-adhesive surface of the non-woven fabric adhesive tape;

and step 118, arranging a first release liner on one side of the bonding layer, which is far away from the non-woven fabric adhesive tape.

It should be understood that, although the steps in the flowcharts in the figures are shown in order as indicated by the arrows, the steps are not necessarily performed in order as indicated by the arrows. The steps are not performed in the exact order shown and described, and may be performed in other orders, unless explicitly stated otherwise. Moreover, at least some of the steps in the figures may include multiple sub-steps or multiple stages that are not necessarily performed at the same time, but may be performed at different times, and the order of performance of the sub-steps or stages is not necessarily sequential, but may be performed in turn or alternately with other steps or at least some of the sub-steps or stages of other steps.

All possible combinations of the technical features in the above embodiments may not be described for the sake of brevity, but should be considered as being within the scope of the present disclosure as long as there is no contradiction between the combinations of the technical features.

The above-mentioned embodiments only express several embodiments of the present application, and the description thereof is more specific and detailed, but not construed as limiting the scope of the present application. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the concept of the present application, which falls within the scope of protection of the present application. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims (10)

1. An electrocardiograph sensor, comprising: electrodes, non-woven fabric tape and conductive hydrogel;

the electrode is arranged on the adhesive surface of the non-woven fabric adhesive tape and is connected with the electrocardiogram host machine through a first through hole formed in the non-woven fabric adhesive tape;

the conductive hydrogel is arranged on one side of the electrode, which is far away from the non-woven fabric adhesive tape, and the adhesive surfaces of the conductive hydrogel and the non-woven fabric adhesive tape are used for being pasted on an object to be detected.

2. The electrocardiograph sensor according to claim 1, further comprising an adhesive layer, and a first release liner disposed on a first surface of the adhesive layer;

the second surface of the bonding layer is arranged on the non-adhesive surface of the non-woven fabric adhesive tape, and the bonding layer is used for connecting the non-adhesive surface of the non-woven fabric adhesive tape with the electrocardiogram host machine.

3. The electrocardiograph sensor of claim 1 wherein the electrodes comprise a thin film substrate, a first conductive layer, a second conductive layer, and a conductor;

the thin film substrate comprises a first surface and a second surface, the first conducting layer is arranged on the first surface of the thin film substrate, and the second conducting layer is arranged on the second surface of the thin film substrate;

the electric conductor penetrates through the film substrate and is used for conducting the first conducting layer and the second conducting layer.

4. The ecg sensor of claim 3, wherein the conductive body comprises a conductive via formed in the film substrate and a conductive ink disposed in the conductive via.

5. The electrocardiograph sensor of claim 3 wherein the electrodes further comprise: the insulating layer is arranged between the electrode and the adhesive surface of the non-woven fabric adhesive tape, a second through hole is formed in the insulating layer, and the position of the second through hole is consistent with that of the first through hole in the preset direction.

6. The ecg sensor of claim 1, further comprising a second release liner disposed on a side of the conductive hydrogel remote from the electrodes.

7. A method of manufacturing an electrocardiograph sensor according to any one of claims 1 to 6, comprising:

applying the adhesive surface of the non-woven fabric adhesive tape to the first surface of the electrode;

covering the second surface of the electrode with a conductive hydrogel.

8. The method of claim 7, wherein prior to applying the adhesive side of the non-woven adhesive tape to the first surface of the electrode, the method further comprises:

arranging the second surface of the electrode on a silica gel protective film;

after the applying the adhesive side of the non-woven fabric adhesive tape to the first surface of the electrode, the method further comprises:

and removing the silica gel protective film.

9. The method of manufacturing according to claim 7, further comprising:

printing conductive ink on a first surface of a film substrate to form a first conductive layer, and printing silver/silver chloride slurry on a second surface of the film substrate to form a second conductive layer; the first conductive layer is a first surface of the electrode, and the second conductive layer is a second surface of the electrode;

and punching holes on the film substrate, and plugging the holes by using the conductive ink to form a conductor.

10. The method of manufacturing according to claim 9, wherein after printing the conductive ink on the first surface of the film substrate to form the first conductive layer, the method further comprises:

and printing insulating oil on the first conducting layer except the area connected with the electrocardio host to form an insulating layer.

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