KR101007788B1 - Non-contact type metal electrode patch for measuring bioelectric signals and apparatus for measuring bioelectric signals - Google Patents

Abstract

Disclosed is a non-contact metal electrode patch and a biosignal measuring apparatus for measuring a biosignal which minimizes damage to the skin and is reusable, and improves compatibility for use in a conventional electrocardiogram measuring device. To this end, an adhesive member detachable to the skin, a copper plate positioned on the adhesive member to measure a biosignal, a flexible printed circuit board formed on the copper plate, and an upper portion of the flexible printed circuit board electrically connected to the copper plate. It provides a non-contact metal electrode patch for biological signal measurement including a connector connecting member to be connected. According to the present invention can be directly applied to the electrocardiogram analyzer which is widely used in the prior art can be used to improve the compatibility and the conventional gel composition is not required, it can be expected to simplify the manufacturing process and reduce the manufacturing cost. In addition, since the non-contact type electrode is used to ensure breathability to the skin, it is possible to reduce side effects and pain, including damage to the skin when detached.

Description

NON-CONTACT TYPE METAL ELECTRODE PATCH FOR MEASURING BIOELECTRIC SIGNALS AND APPARATUS FOR MEASURING BIOELECTRIC SIGNALS

The present invention relates to a non-contact metal electrode patch and a bio-signal measuring device for measuring a bio-signal, and more particularly, to a non-contact metal electrode for measuring a bio-signal, which can minimize the effects on the skin and can be reused. The present invention relates to a patch and a biosignal measuring apparatus.

In order to precisely grasp the patient's condition for effective treatment, or to determine the abnormality of the health of the general public and to take appropriate preventive measures, a technique for accurately and efficiently measuring various biological information detected in the human body has been developed.

ElectrocardioGram (ECG), one of the representative biometric information, records the active current generated when the heart muscle contracts and expands due to the beating of the heart, and attaches an electrode to the skin of the body to measure the active current according to the contraction of the heart muscle. The graph then depicts the measured current data.

Specifically, the action potential generated when the heart muscle contracts and relaxes due to the heartbeat causes an electric current transmitted from the heart to the whole body, which generates an electric potential difference according to the position of the body, which is attached to the skin of the human body. It can be detected and recorded through the surface electrode.

Such electrocardiograms are used to check for abnormalities of the heart and are used as a basic measurement method for diagnosing cardiac diseases such as angina pectoris, myocardial infarction and arrhythmia.

In general, the electrode induction method used in the clinical practice to measure the electrical abnormality of the heart is to measure the biopotential generated when the electrical stimulation generated in the ipsilateral node of the heart is conducted to the left and right ventricles and the left and right atria. It is attached and measured.

As such, the limb electrode induction method and the two-electrode measurement method are mainly used as the measurement method using the electrode.

The limb electrode induction method uses the fact that the longer the route of shipment is, the greater the potential can be measured, and the electrode is attached to both arms and legs of the body and the cable is connected to a cardiac electrical activity measuring device. It is a method to measure. In the case of the limb electrode induction method, since the longer the route of the shipment, the larger the potential can be measured, there is a problem that it is difficult to miniaturize and is sensitive to noise.

The two-electrode measuring method is a method of measuring the electrical activity of the heart by attaching an electrode to the chest area using an elastic band. In the case of the two-electrode measurement method, there is a problem in that it is difficult to wear the elastic band for a long time because of the feeling of pressure on the chest.

In addition, there is a problem in that the quality of the heart rate signal measured when the electrode is loosely attached due to a user's mistake when the first attachment or the humidity of the electrode is reduced due to long use.

Heart rate signal measuring devices have been developed that can solve the problems occurring in the conventional device for measuring the heart rate signal.

For example, Korean Patent Publication No. 10-0695152 (registered on March 08, 2007) discloses an electrode for measuring ECG and an ECG measuring apparatus including the same.

This is an electrocardiogram measurement electrode comprising a signal detector for measuring an electrocardiogram signal, an electrolyte gel composition applied to one surface of the signal detector and having adhesiveness and electrical conductivity, and a controller connection portion electrically connected to the signal detector It relates to an electrode for ECG and an electrocardiogram measuring device including the same.

This technology has the advantage of being able to attach the electrocardiogram electrode to the body skin using a gel composition having electrical conductivity as well as adhesive properties, as well as measuring a good signal.

However, the gel composition having the adhesive and conductive properties mentioned above can be expected to reduce the pain on the body skin to some extent when detached from the body skin compared to the conventional adhesive portion, but such a gel composition is also in contact with the skin when used for a long time There is a problem that can cause skin damage, such as the body part is turned red.

In particular, when the electrode for ECG measurement using the gel composition is detached to a patient who has undergone cardiac surgery in addition to a healthy general person, the patient who has undergone the cardiac surgery may feel a lot of pain due to the adhesive property of the gel composition. In addition, in the case of the gel composition is used as a disposable rather than reuse, there is a problem in that it is inefficient in terms of cost.

And the Republic of Korea Patent Publication No. 10-0731676 (registered June 18, 2007) is disclosed "electrode patch for measuring heart electrical activity in the mobile environment".

It consists of a circular concentric electrode portion for sensing a biopotential signal, a conductive metal, an electrode support for supporting each electrode and transmitting a biopotential signal, and amplifying the biopotential signal received through the electrode support and wirelessly Signal processing and transmission unit for transmitting to the outside, an adhesive unit for bonding the electrode patch for measuring heart electrical activity to the human body, a buffer isolation unit for providing a buffer function to enhance the wear when wearing the human body, and signal processing and transmission The present invention relates to an electrode patch for measuring cardiac electrical activity in a mobile environment including a cover for transmitting an amplified biopotential signal generated in a negative direction to the outside.

This technique has the advantage of continuously monitoring cardiac electrical activity signals using a miniaturized wireless electrode patch compared to conventional limb electrode induction. However, by using a wireless electrode patch, it can be applied only to an electrocardiogram measuring device capable of wirelessly receiving the amplified biopotential signal generated and amplified from the signal processing and transmission unit, and thus cannot be used in a widely used electrocardiogram measuring device. There is a problem that the utility is poor.

Therefore, problems caused by the adhesion of the electrode to the skin, for example, to minimize the pain or damage of the skin when detached from the skin, the adhesive strength is maintained and reused even when detached many times, as well as the existing ECG analysis equipment The development of an electrocardiogram measurement electrode patch capable of measuring a high quality signal with excellent compatibility that can be used in connection with is required.

Accordingly, a first object of the present invention is to provide a non-contact metal electrode patch for measuring bio signals that can minimize damage to the skin to which an electrode is attached and reuse it, and improve compatibility that can be used in a conventional electrocardiogram measuring device. .

In addition, the second object of the present invention is to apply a non-contact metal electrode patch for measuring the bio-signals to minimize the damage to the skin, reusable, bio-signals that improve the compatibility that can be used in conventional ECG devices It is to provide a measuring device.

In order to achieve the first object of the present invention described above, the present invention is an adhesive member detachable to the skin; A copper plate positioned on the adhesive member to measure a biosignal; A flexible printed circuit board formed on the copper plate; And a connector connection member positioned on the flexible printed circuit board and electrically connected to the copper plate.

In addition, to achieve a second object of the present invention, a plurality of electrodes including an adhesive member and a copper plate positioned on the adhesive member; A plurality of connector connecting members electrically connected to the plurality of copper plates, respectively, corresponding to the copper plates included in the plurality of electrodes; A flexible printed circuit board connecting the plurality of electrodes to the plurality of connector connecting members; A signal line designed on a surface of the flexible printed circuit board so that the bio signal measured through the copper plate can be transmitted to the connector connecting member; And a ground line designed on a surface of the flexible printed circuit board along the signal line such that the bio signal flowing through the signal line does not interfere with an external fine signal.

When using a non-contact metal electrode patch for measuring a bio-signal according to the present invention, it can be directly applied to an electrocardiogram analyzer widely used in the prior art, thereby improving compatibility.

And since the conventional gel composition which plays a role of measuring the electrical signal of the heart is not necessary, it can be expected to simplify the manufacturing process and reduce the manufacturing cost. In addition, since the non-contact type electrode that is breathable to the skin is used, it is possible to reduce the damage or pain of the skin when detachable.

In addition, unlike the case of using a conventional gel composition can be reused, reducing the generation of waste can contribute to environmental pollution, of course, can be expected to reduce the cost. Furthermore, since the number of electrodes for measuring the electrical signal of the heart can be selectively designed from 2 to 12, the present invention provides an electrode patch for measuring bio signals that can measure electrical signals of a higher quality heart.

Hereinafter, a non-contact metal electrode patch for measuring a biosignal according to an embodiment of the present invention will be described in detail with reference to the accompanying drawings.

1 is a front perspective view illustrating a non-contact metal electrode patch for measuring a bio-signal according to an embodiment of the present invention, Figure 2 is a non-contact metal electrode patch for measuring a bio-signal according to an embodiment of the present invention It is a back perspective view for doing so.

1 and 2, the electrode patch 100 according to the present embodiment is formed with a detachable adhesive member 110 on the skin, and a copper plate 120 is formed on the adhesive member 110. The flexible printed circuit board 130 and the connector connecting member 140 are sequentially formed on the copper plate 120.

Hereinafter, each component will be described in detail with reference to the accompanying drawings.

3 is a schematic cross-sectional view for explaining a non-contact metal electrode patch for measuring a bio-signal according to an embodiment of the present invention.

Referring to Figure 3, the electrode patch 100 according to an embodiment of the present invention includes an adhesive member (110).

The adhesive member 110 serves to attach the electrode patch 100 to the skin of the body part to be measured. The adhesive member 110 is preferably detachable so that the user does not feel pain when detached to the skin, it is preferable to use a material that can be recycled because the adhesive strength does not decrease even when detached many times.

Any material having such physical properties can be used without particular limitation, but as one example, a material having a fine cilia structure can be used. The surface of the lotus leaf or the sole of the gecko lizard, which has a large number of micro or nano-sized cilia and protrusions on the surface, has superhydrophobic, antifouling, and high adhesion properties.

When the adhesive member 110 is manufactured using this principle, since the water or liquid can be water-repelled and contamination by an external material can be prevented, it is possible to manufacture a durable electrode patch that maintains its performance even after multiple uses. Can be. In addition, it is possible to produce an electrode patch excellent in adhesion without using a separate gel composition or a synthetic material.

The adhesive member of the above-mentioned form can be manufactured using a general imprint technique, a soft lithography method, or the like. Specifically, for example, after applying an ultraviolet curable polymer material on a predetermined substrate, a mold having a pattern capable of producing a cilia of a size to be produced is contacted on the polymer material.

Thereafter, pressure is applied to the mold to transfer the shape of the mold to the polymer material, or the polymer material flows by capillary action to fill the intaglio portion of the mold, thereby transferring the shape of the mold to the polymer material. Subsequently, after curing the polymer material in which the cilia are formed with ultraviolet rays, the mold is removed to obtain an adhesive member having fine cilia.

In this case, since the substrate should be attached to the body, it is preferable to use a flexible and harmless material, for example, a silicon substrate, a metal substrate, a polymer substrate, or the like. Examples of the polymer material include polyurethane acrylate (PUA), polyethylene glycol diacrylate (PEG-DA), polyester acrylate or perfluorinated polyether dimethacrylate (PFPE-DMA), and polyester (polystyrene) or poly (methyl methacrylate) (poly (methylmethacrylate)) and the like can be used. As the mold, for example, polyurethane, polydimethylsiloxane, or the like can be used.

In addition, in order to improve adhesiveness or hydrophobicity, only the lower end of the cilia is completely cured in the curing step of the polymer material, and the upper part is partially cured, and then the second step is formed in the partially cured part. It may be.

Furthermore, in consideration of the fact that the difference in adhesion force occurs depending on the contact angle between the object to be contacted and the cilia, the cilia may be formed on the substrate in an oblique direction rather than a vertical direction. As such, when the cilia are formed in an oblique direction, when the electrode patches are separated in a direction in which adhesion is weak during detachment, the electrode patches can be separated from the skin without damaging the skin or causing pain to the patient.

4 is a schematic diagram illustrating an example of a contact member of an electrode patch according to an exemplary embodiment of the present invention. Referring to FIG. 4, fine cilia are formed in the contact member 110, and adhesiveness is provided by the cilia. Existing gel form or other adhesives are in close contact with the skin to provide adhesion, which causes problems such as damage to the skin, pain when detaching and skin necrosis during long-term use. However, when the adhesive member of the ciliated structure is used, it is possible to prevent problems such as skin damage because of the constant breathability is secured, and the electrode patch without pain by using the point that the adhesion strength is significantly different depending on the direction of attachment and detachment Can be removed

In addition to the hierarchical microstructure, the contact member 110 may be used as long as it has a reusable adhesive member that is easily removable. However, it may be desirable to use an adhesive member that can be easily detachable but minimizes the effect on the body skin when detaching from the skin.

In addition, the adhesive member 110 is preferably formed to have a thickness of 0.1 to 1mm. If the thickness of the adhesive member 110 is less than 0.1, there is a problem in that it is difficult to form the above-described adhesive ciliated structure. On the other hand, limiting the thickness of the adhesive member 110 to 1mm or less is to prevent the copper plate 120 to be described later does not affect the measurement of the ECG signal. If the thickness of the adhesive member 110 exceeds 1mm, the ECG signal measured through the copper plate 120 is insufficient, making accurate ECG signal measurement difficult.

In addition, the adhesive member 110 may be formed in a circular shape, in which case the diameter is preferably formed to be larger than the diameter of the copper plate 120 to be described later. In addition, the adhesive member 110 may be formed in an annular shape, in this case may be formed along the outer peripheral surface of the copper plate to be described later.

Electrode patch 100 according to an embodiment of the present invention includes a copper plate (120).

Referring to Figure 3, the copper plate 120 serves to measure the ECG signal of the body skin. In more detail, the copper plate 120 is positioned in a non-contact state by the adhesive member 110 and serves to measure an electrical signal of a body part to which the electrode patch according to the present invention is attached. To this end, the copper plate 120 is formed on the opposite side of the skin with the adhesive member 110 on top, that is, the adhesive member therebetween.

The copper plate 120 is preferably formed in a circular shape having a diameter of 25 to 40 mm in order to measure a higher quality electrocardiogram signal. The shape and size of the copper plate 120 may be an optimal condition for measuring a high quality electrocardiogram signal.

If the diameter of the copper plate 120 is less than 25mm, the weak ECG signal is measured. If the diameter is more than 40mm, the size of the copper plate 120 is too large to measure the inherent signal of the ECG to be measured. There is a problem.

And the copper plate 120 is preferably formed to a thickness of 0.7 to 0.8㎛. If the thickness is less than 0.7㎛ thickness is too thin, there is a difficulty in the manufacturing process, there is a problem that the durability is poor because the thickness is too thin.

In addition, when the thickness exceeds 0.8㎛ there is a problem that the thickness is too thick, the conductivity is poor. This means that the conductivity of the ECG signal measured through the copper plate 120 drops, which means that it is difficult to measure a high quality ECG signal.

And the copper plate 120 may form a surface thin film of gold (Au) on one surface in contact with the adhesive member 110. The surface thin film made of gold may be formed by coating gold on the copper plate. The reason for coating with gold as described above is to improve the conductivity of the copper plate 120 to measure a further improved quality electrocardiogram signal.

To this end, the copper plate 120 may be preferably coated with a gold thickness of 0.04 to 0.06㎛. Gold has better electrical conductivity than copper, but is expensive, and due to process problems, it is not desirable to fabricate the entire electrode from gold. However, by coating only one surface of the skin side that receives the bio-signal with gold, the bio-signal can be measured more effectively.

Electrode patch 100 according to an embodiment of the present invention includes a flexible printed circuit board (130).

Referring to FIG. 3, the flexible printed circuit board 130 serves to smoothly flow an ECG signal measured through the copper plate 120. To this end, the flexible printed circuit board 130 is preferably located on the copper plate 120.

The flexible printed circuit board (FPCB) 130 is a three-dimensional circuit board having a flexible film form, unlike a rigid PCB, which is generally a hard material, and has a thin copper foil on an insulating film having a very thin thickness. Thin and flexible circuit board.

The flexible printed circuit board 130 may be classified into three-layer copper clad laminate (CCL: copper clad laminate) and a circuit pattern protective adhesive tape (CL: coverlay) based on the material used.

The copper clad laminate material is a material obtained by laminating a copper foil on a flexible insulating material, the characteristics of the flexible insulating materials such as polyester film, polyimide film, liquid crystal polymer film, and fluorine resin film It is used accordingly.

Among the flexible insulating materials, a flexible printed circuit board using a double polyimide film is most in demand, and the polyimide film has excellent properties such as heat resistance, dimensional stability, solderability, and the like.

In the present invention, it is preferable to use a polyimide film among the flexible insulating materials as the material of the flexible printed circuit board 130, and in the case of the polyimide film adopted in the present invention, the electrocardiogram signal measured through the copper plate 120 It has the characteristics to make a smooth flow. The material of the flexible printed circuit board 130 is not limited to the polyimide film, but may use other kinds of films according to the initial design purpose.

 In addition, the flexible printed circuit board 130 may include a hole (not shown) on one side. The reason why the hole is formed in the flexible printed circuit board 130 is to allow the electrocardiogram signal measured through the copper plate 120 to flow to the connector connecting member which will be described later.

To this end, the copper plate 120 is preferably formed to extend through the hole formed in the flexible printed circuit board 130 to the connector connecting member to be described later.

In addition, the size of the flexible printed circuit board 130, that is, the diameter is preferably formed to be larger than the diameter of the copper plate 120, the exact size of the flexible printed circuit board 130 is selectively depending on the initial design purpose You can design it.

Electrode patch 100 according to an embodiment of the present invention includes a connector connecting member 140.

Referring to FIG. 3, the connector connecting member 140 is electrically connected to the copper plate 120 to transfer an electrocardiogram signal measured from the copper plate 120 to the connector 150 of the ECG analyzer. To this end, the connector connecting member 140 is preferably located above the flexible printed circuit board 130.

The connector connecting member 140 is preferably formed to be 3 to 7mm in height. The height of the connector connecting member 140 is to allow the electrocardiogram signal measured from the copper plate 120 to be transmitted to the connector 150 with a high quality electrocardiogram without external noise interference.

As described above, the electrode patch 100 of the present invention including the adhesive member 110, the copper plate 120, the flexible printed circuit board 130, and the connector connection member 140 is a widely used electrocardiogram measuring device. It can be used by connecting to the connector 150 of the highly compatible electrode patch.

The present invention also provides a biosignal measuring apparatus. Hereinafter, descriptions of parts common to the description of the non-contact metal electrode patch for measuring the bio-signals will be omitted or abbreviated.

5 is a schematic diagram illustrating a non-contact metal electrode patch for measuring a biosignal according to another exemplary embodiment of the present invention.

Referring to FIG. 5, the biosignal measuring apparatus 200 according to the present invention includes a plurality of electrodes 210 including an adhesive member 110 and a copper plate 120 positioned on the adhesive member 110.

The electrode 210 has the same structure as the adhesive member 110 and the copper plate 120 of the electrode patch 100 according to the present invention described above. Accordingly, the electrode 210 is attached to the body skin to be measured to serve to measure the ECG signal.

In addition, the electrode 210 may be formed of two, three, six, eight, or twelve. The number of electrodes 210 may be selectively changed to meet the initial design purpose. That is, the number of the electrodes 210 is determined to correspond to the position of each body part to be measured.

The biosignal measuring apparatus 200 of the present invention includes a plurality of connector connecting members 230 and a flexible printed circuit board 220.

The connector connecting member 230 is electrically connected to the plurality of copper plates, respectively, in a one-to-one correspondence with the copper plates included in the plurality of electrodes. In more detail, the connector connecting member 230 is formed on the surface of the flexible printed circuit board 220 and is formed to be connected to each other with the two or more electrodes 210.

The flexible circuit board 220 connects the plurality of electrodes 210 and the plurality of connector connection members 230.

The flexible printed circuit board 220 is positioned above the copper plate 120 of each of the two or more electrodes 210 to serve to connect the electrodes 210 and the plurality of connector connecting members to each other. In addition, a signal line and a ground line to be described below are designed on the surface of the flexible printed circuit board 220 to allow an electrocardiogram signal between the two or more electrodes 210 and the connector connecting member 230 to flow.

The biosignal measuring apparatus 200 of the present invention includes a signal line 240.

6 is a schematic diagram illustrating a signal line and a ground line of a non-contact metal electrode patch for measuring a bio signal according to another embodiment of the present invention.

Referring to FIG. 6, the signal line 240 includes the copper plate 120 and the connector so that an ECG signal measured through the copper plate 120 of the electrode 210 can be transmitted to the connector connecting member 230. It serves to connect the connection member 230.

To this end, the signal line 240 is preferably designed on the surface of the flexible printed circuit board 220 to connect the copper plate 120 and the connector connecting member 230. For example, the signal line 240 may be designed to match a line impedance of 50 (Ω) with a width of 1 to 3 mm.

The biosignal measuring apparatus 200 according to another exemplary embodiment of the present invention includes a ground line 250.

Referring to FIG. 6, the ground line 250 serves to prevent an electrocardiogram signal flowing through the signal line 240 from being interfered with by an external microsignal. To this end, the ground line 250 is preferably designed on the surface of the flexible printed circuit board 220 along the signal line 240.

For example, the ground line 250 is designed on the surface of the flexible printed circuit board 220 along the signal line 240, and both ends thereof are formed from the copper plate 120 and the connector connecting member 230 of the electrode 210. It is preferable to design 3 to 7 mm apart.

The ground line 250 is designed to be spaced apart from the copper plate 120 and the connector connecting member 230. The ground line 250 is spaced apart from the copper plate 120 and the connector connecting member 230 by less than 3 mm. If designed, there is a problem in that the ECG signal measured by the ground line 250 may disappear.

In addition, when the ground line 250 is spaced apart from the copper plate 120 and the connector connecting member 230 by more than 7 mm, the electrocardiogram signal flowing through the signal line 240 may be interfered with by external noise to measure a high quality electrocardiogram signal. This is a difficult problem.

The biological signal measuring apparatus 200 of the present invention may selectively design two, three, six, eight, or twelve electrodes 210 for measuring a biosignal such as an electrocardiogram. The distance between the electrodes 210 is not limited, but for example, when the electrodes 210 are designed in three, the distance between the electrodes 210 may be 200 mm.

The above-described biosignal measuring apparatus 200 of the present invention may also be connected to a connector of an electrocardiogram measuring apparatus and used to improve compatibility.

The biosignal data measured through the non-contact metal electrode patch for the biosignal measurement of the present invention configured as described above was measured.

FIG. 7 is a graph illustrating biosignal data measured through an electrode patch according to an embodiment of the present invention, and FIG. 8 is a graph illustrating biosignal data measured through a conventional contact patch.

Specifically, the biosignal data shown in FIG. 7 is a graph showing a biosignal output through an electrocardiogram measuring device by applying the electrode patch of the present invention to a conventional electrocardiogram measuring device, and the biosignal data shown in FIG. This is a graph showing the bio signals output through ECG using 'skintact', 'SkinTac'.

As can be seen from FIG. 7 and FIG. 8, the biosignal experimental data measured through the non-contact metal electrode patch and measuring apparatus of the present invention is not different from the biosignal experimental data measured through the conventional contact skin tag product. I could confirm it.

That is, without affecting the signal quality, the non-contact metal electrode patch and measuring device of the invention has the effect of minimizing the damage of the skin to which the electrode is attached to the non-contact and improve the compatibility that can be used in the conventional ECG device.

While the above has been described with reference to a preferred embodiment of the present invention, those skilled in the art will be able to variously modify and change the present invention without departing from the spirit and scope of the invention as set forth in the claims below. It will be appreciated.

 1 is a front perspective view for explaining a non-contact metal electrode patch for measuring a biological signal according to an embodiment of the present invention.

2 is a rear perspective view for explaining a non-contact metal electrode patch for measuring a bio-signal according to an embodiment of the present invention.

3 is a schematic cross-sectional view for explaining a non-contact metal electrode patch for measuring a bio-signal according to an embodiment of the present invention.

4 is a schematic configuration diagram illustrating a contact member of a non-contact metal electrode patch for measuring a biological signal according to an embodiment of the present invention.

5 is a schematic diagram illustrating a biosignal measuring apparatus according to an exemplary embodiment of the present invention.

6 is a schematic diagram illustrating a signal line and a ground line of a biosignal measuring apparatus according to an exemplary embodiment of the present invention.

7 is a graph illustrating biosignal data measured by a non-contact metal electrode patch and a biosignal measuring apparatus for measuring a biosignal according to an embodiment of the present invention.

8 is a graph illustrating biosignal data measured through a conventional contact skin tag.

Brief description of the main parts of the drawing

100, 200: electrode patch 110: adhesive member

120: copper plate 130, 220: flexible printed circuit board

140, 230: connector connecting member 150: connector

210: electrode 240: signal line

250: ground line

Claims (13)

Adhesive member detachable to the skin; A copper plate positioned on the adhesive member to measure a biosignal; A flexible printed circuit board formed on the copper plate; And The non-contact metal electrode patch for bio-signal measurement including a connector connecting member positioned on the flexible printed circuit board and electrically connected to the copper plate. The non-contact metal electrode patch of claim 1, wherein the adhesive member comprises a fine cilia structure. 2. The non-contact metal electrode patch of claim 1, wherein the adhesive member has a thickness of 0.1 to 1 mm. The non-contact metal electrode patch of claim 1, wherein the biosignal is an electrocardiogram signal. The non-contact metal electrode patch of claim 1, wherein the copper plate has a circular diameter of 25 to 40 mm and a thickness of 0.7 to 0.8 μm. The non-contact metal electrode patch of claim 1, further comprising a surface thin film having a thickness of 0.04 to 0.06 μm including gold formed on the copper plate in contact with the adhesive member. The non-contact metal electrode patch of claim 1, wherein the copper plate is not in contact with the skin. The method of claim 1, The flexible printed circuit board includes a hole, And the copper plate extends through the hole formed in the flexible printed circuit board to the connector connection member. The non-contact metal electrode patch of claim 1, wherein the flexible printed circuit board comprises a polyimide film. A plurality of electrodes including an adhesive member and a copper plate positioned on the adhesive member; A plurality of connector connecting members electrically connected to the copper plates in correspondence with the copper plates included in the electrodes forming the plurality of electrodes; A flexible printed circuit board connecting the plurality of electrodes to the plurality of connector connecting members; Signal lines designed on the surface of the flexible printed circuit board so that the bio-signals measured through the copper plate included in each electrode forming the plurality of electrodes can be transmitted to the plurality of connector connecting members electrically connected to the copper plate, respectively. ; And And a ground line designed on a surface of the flexible printed circuit board along the signal line such that the biological signal flowing through the signal line does not interfere with an external fine signal. The apparatus of claim 10, wherein the signal line has a width of 1 to 3 mm. 11. The biosignal measuring apparatus of claim 10, wherein both ends of the ground line are separated from each other by 3 to 7 mm from each connector connecting member forming the copper plate and the plurality of connector connecting members. The biosignal measuring apparatus of claim 10, wherein the plurality of connector connecting members are connected to a connector of an ECG analyzer.

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