JP7261634B2 - Electrode structure and biosensor device having the electrode structure - Google Patents

Description

The present invention relates to electrode structures and biosensor devices.

Conventionally, there is a biosensor using a biocompatible polymer substrate that includes a plate-like first polymer layer, a plate-like second polymer layer, electrodes, and a data acquisition module (see, for example, Patent Document 1). ).

Japanese Unexamined Patent Application Publication No. 2012-010978

By the way, the surface of the living body to which the biosensor is attached is not flat, and many of the parts are three-dimensionally curved. In particular, if the biosensor is attached to the concave surface of the living body, the electrodes may not be in sufficient contact with the concave surface of the living body, and electrical characteristics such as impedance may change, making accurate measurement impossible. Also, it takes a certain amount of time to acquire data from a living body through electrodes.

Therefore, the biosensor is required to be able to maintain a state in which the electrode is stably brought into contact with the concave surface of the living body.

Accordingly, it is an object of the present invention to provide an electrode structure capable of maintaining a state in which an electrode is stably brought into contact with a concave surface of a living body, and a biosensor device having the electrode structure.

An electrode structure according to an embodiment of the present invention includes a surface layer, a bottom layer having through holes, a conductive polymer sheet provided between the surface layer and the bottom layer, and an electric and an elastic member that is provided between the surface layer and the conductive polymer sheet and causes a part of the conductive polymer sheet to protrude through the through hole of the bottom layer, A portion of the polymer sheet protrudes from the bottom surface of the bottom layer by 0.2 mm or more and 2 mm or less .

It is possible to provide an electrode structure and a biosensor device capable of maintaining a state in which an electrode is stably brought into contact with a concave surface of a living body.

1 is a plan view showing a biosensor device 100; FIG. FIG. 2 is a diagram showing a cross section taken along line AA of FIG. 1; FIG. 2 is a view showing a cross section taken along line BB of FIG. 1; FIG. 14 is a diagram showing a structure 146 in which the probe 140 and frame portions 145A and 145B are superimposed. FIG. 5 is a view showing a cross section taken along line CC in FIG. 4; 100A is an exploded view of the electrode structure 100A; FIG. 2 is a diagram showing a circuit configuration of the biosensor device 100; FIG. 4A and 4B are diagrams for explaining the effect of the biosensor device 100; FIG. FIG. 11 is a plan view showing a plate 110M of a biosensor device of a modified example of the embodiment; It is a figure which shows the structure 146M1 of the modification of embodiment. It is a figure showing structure 146M2 of a modification of an embodiment. FIG. 10 is a diagram showing a biosensor device 100M of a modified example of the embodiment; 4A to 4C are diagrams showing a manufacturing process of the structure 146; FIG. FIG. 14 is a diagram showing pretreatment of the manufacturing process shown in FIG. 13; FIG. 14 is a diagram showing pretreatment of the manufacturing process shown in FIG. 13; FIG. 14 is a diagram showing pretreatment of the manufacturing process shown in FIG. 13; FIG. 10 illustrates an embodiment of an electrode structure;

Embodiments to which the electrode structure and the biosensor device of the present invention are applied will be described below.

<Embodiment (electrode structure)>
The electrode structure of the present invention comprises a surface layer, a bottom layer having through holes, a conductive polymer sheet provided between the surface layer and the bottom layer, and electrically connected to the ends of the conductive polymer sheet. and an elastic member provided between the surface layer and the conductive polymer sheet to allow a portion of the conductive polymer sheet to protrude through the bottom layer.

An example of an embodiment of the electrode structure of the present invention will be described below with reference to FIGS. 6 and 17, but the electrode structure of the present invention is not limited to this embodiment.

The electrode structure of the present invention has a conductive sheet 140, which will be described in detail in the biosensor device below, and the conductive sheet 140 functions as an electrode in contact with a subject, a so-called probe. As shown in FIG. 6, conductive sheet 140 is disposed between top layer 120 and bottom layer 110 . Through holes 111 are provided in the bottom layer 110 so that a part of the surface of the conductive sheet 140 can be exposed. The surface layer 120 and the bottom layer 110 may be made of any material, such as polytetrafluoroethylene.

A conductive member 145 , which is an example of a conductive member, is arranged such that a conductive member 145 is electrically contactable with the conductive sheet 140 on at least a portion or one side of the end portion (end side portion) of the conductive sheet 140 . The conductive member 145 may be laminated such that the constituent members 145A and 145B of the conductive member 145 sandwich the end portion of the conductive sheet 140 . Also, the conductive member 145 may have a configuration in which the ends of the constituent members 145A and 145B of the conductive member 145 are laminated and joined together. The ends of the adhesive sheet 140 are pinched. The conductive sheet 140 and the conductive member 145 may be laminated via an adhesive layer, and the adhesive layer may have conductivity. Conductive member 145 may have a rectangular or circular annular structure, with the inner dimensions of the annular structure generally matching the through-holes in bottom layer 110 . Note that the ring structure may be continuous or intermittent. When used as a biosensor device, the conductive member 145 transmits a signal detected by the conductive sheet to the wiring 130, and the signal is transmitted to the electronic device. The material of the conductive member 145 is not particularly limited, but is usually selected from a group including metals such as copper, alloys, conductive polymers, and mixtures of conductive polymers and nanoparticles.

An elastic member 124 is arranged between the conductive sheet 140 and the surface layer 120 . As shown in FIG. 17, the elastic member 124 allows a portion of the conductive sheet 140 to protrude beyond the bottom layer 110 through the through hole 111 . The dimensions such as the thickness of the elastic member and the area in contact with the conductive sheet 140 may be designed so that the conductive sheet 140 is pressed by the subject and is in constant contact. The Young's modulus of the elastic member is not particularly limited as long as the object of the present invention can be achieved, but it is preferably smaller than the Young's modulus of the surface layer 120, and more preferably the Shore hardness of the elastic member is 10 or more and 60 or less. preferable. By doing so, according to the electrode structure having the elastic member, when the adhesive layer is provided and attached to the subject, the electrode (probe 140) in contact with the subject is pressed against the subject. It is possible to keep contact with the sensor at all times in the form of a shape, and to stably measure biological signals and the like. As a presumed mechanism, the following can be considered. When the electrode structure of the present invention is provided with the adhesive layer 170 and attached to the subject, the cover 120 (surface layer) fixed to the subject via the adhesive layer 170 is microscopically protruded. The surface of the probe 140 is subjected to a stress that causes the surface of the probe 140 to come into the same plane as the surface of the adhesive layer 170 due to the contact with the subject and the pressure of the elastic member 124, and is elastically deformed to become convex on the side opposite to the subject. do. However, since the elastic member 124 has a Young's modulus lower than that of the cover layer 120, the stress that restores the original shape of the cover layer 120 is dominant, and the elastic member 124 is a part of the conductive sheet 140 (through the through-hole of the probe 140). exposed portion) is pressed toward the subject. Examples of such an elastic member include silicone rubber. At this time, polytetrafluoroethylene is used for the surface layer 120 .

The electrode structure of the present invention may have an adhesive layer on the side of the bottom layer 110 opposite to the surface layer 120 side. The adhesive layer is preferably arranged around the through holes of the bottom layer 110 , in other words, around the surface of the protruding conductive sheet 140 .

The electrode structure of the present invention is not particularly limited as long as a portion of the protruding conductive sheet 140 protrudes beyond the bottom layer 110, but the length of the protrusion in the thickness direction of the electrode structure is is preferably 0.2 mm or more and 2 mm or less. In addition, when an adhesive layer is provided around a part of the conductive sheet 140 that protrudes from the bottom layer 110, the electrode structure is formed with reference to the surface opposite to the bottom layer 110 formed by the adhesive layer. The length of the protrusion in the thickness direction is preferably 0.2 mm or more and 2 mm or less.

<Embodiment (biological sensor device)>
FIG. 1 is a plan view showing a biosensor device 100. FIG. FIG. 2 is a cross-sectional view taken along the line AA of FIG. 1. FIG. FIG. 3 is a cross-sectional view taken along the line BB in FIG.
FIG. 2 shows the skin 10 of a living body. The biosensor device 100 is a sheet-like device having a rectangular shape in plan view, but the thickness is exaggerated in FIG. 2 to facilitate understanding of the configuration of each part.

An XYZ coordinate system will be defined and explained below. Also, hereinafter, for convenience of explanation, the Z-axis negative direction side is referred to as the lower side or the lower side, and the Z-axis positive direction side is referred to as the upper side or the upper side, but this does not represent a universal vertical relationship.

In the present embodiment, as an example, a biosensor device 100 that measures biometric information in contact with a living body will be described. A living body refers to a human body, a living creature other than a human body, and the like, and is applied to the skin, scalp, forehead, or the like thereof.

The biosensor device 100 includes a plate 110, a cover 120, an elastic member 124, a wire 130, a probe 140, an electronic device 150, a battery 160, and an adhesive layer 170 as main components. Among the components of biosensor device 100, plate 110, cover 120, elastic member 124, wiring 130, probe 140, and adhesive layer 170 construct electrode structure 100A. The biosensor device 100 includes two electrode structures 100A.

An embodiment using a plate 110 as an example of a bottom layer, a cover 120 as an example of a surface layer, a frame portion 145 as an example of a conductive member, and a probe 140 as an example of a conductive polymer sheet will be described below.

The plate 110 is a plate-like member and is provided on the bottom side of the biosensor device 100 (the side to be attached to the skin 10). The plate 10 has a wiring 130, an electronic device 150, and a battery 160 mounted on its upper surface. Plate 110 is a member used as a substrate of biosensor device 100 . The plate 110 may be made of elastic and flexible resin such as silicone rubber or urethane.

The plate 110 has two through holes 111 provided at both ends in the X direction. A probe 140 is provided in the through hole 111 . The details of the configuration in which the probes 140 are provided in the through holes 111 will be described together with the cover 120 .

A cover 120 covers the wiring 130 , the electronic device 150 and the battery 160 on the plate 110 . The cover 120 is adhered to the plate 110 and together with the plate 110 constructs the housing of the biosensor device 100 . Like the plate 110, the cover 120 may be made of elastic and flexible resin such as silicone rubber or urethane.

The cover 120 is provided on the surface side of the biosensor device 100 (the side opposite to the bottom side attached to the skin 10). The cover 120 has side walls 121 , a base 122 and projections 123 . The side wall 121 surrounds the cover 120 in a substantially rectangular annular shape in plan view, and the lower end thereof is adhered to the upper surface of the plate 110 by a second adhesive layer 125 . The second adhesive layer 125 may be a conductive adhesive having electrical conductivity.

The base 122 is a portion continuously provided on the side wall 121 and extending along the XY plane. A convex portion 123 is provided in the center of the base portion 122 in plan view. The convex portion 123 is a portion in which the central portion of the base portion 122 in the X direction and the Y axis direction protrudes upward.

The cover 120 having such a configuration has a storage portion 120A surrounded by the side wall 121, the base portion 122, and the projection portion 123, and the wiring 130, the electronic device 150, and the battery 160 are stored in the storage portion 120A. .

The elastic members 124 are provided on the lower surface side of the base portion 122 on both end sides in the X direction, and are pressed downward by the base portion 122 to be inserted into the through holes 111 . The Young's modulus of the elastic member 124 is smaller than the Young's modulus of the cover 120, and the hardness of the elastic member is 10 or more and 60 or less. Here, hardness is represented by shore hardness. Therefore, when the electrode structure of the present invention is provided with the adhesive layer 170 and attached to the subject, the cover 120 (surface layer) fixed to the subject through the adhesive layer 170 is microscopically , the surface of the protruding probe 140 is subjected to stress that tries to fit in the same plane as the surface of the adhesive layer 170 due to contact with the subject and pressing of the elastic member 124, and elastic deformation that becomes convex on the side opposite to the subject. try to However, since the elastic member 124 has a Young's modulus lower than that of the cover layer 120, the stress that restores the original shape of the cover layer 120 is dominant, and the elastic member 124 is a part of the conductive sheet 140 (through the through-hole of the probe 140). exposed portion) is pressed toward the subject. In this way, according to the electrode structure, when the adhesive layer is provided and adhered to the subject, the electrode (probe 140) in contact with the subject can always be in contact with the subject while being pressed. Therefore, biosignals and the like can be stably measured.

The wiring 130 is provided on the upper surface of the plate 110 and electrically connects the probe 140 , the electronic device 150 and the battery 160 . The wiring 130 should be fixed at least to the end of the probe 140 on the probe 140 side. The end portion of the probe 140 referred to here is the end portion closest to the wiring 130 among the end portions of the rectangular probe 140 in plan view.

The interconnects 130 are selected from a group including at least metals, alloys, conductive polymers, and mixtures of conductive polymers and nanoparticles.

The probe 140 is an electrode that contacts the skin 10 when the lower surface of the plate 110 touches the skin 10 and detects a biological signal. A biological signal is, for example, an electrical signal representing an electrocardiographic waveform, an electroencephalogram, a pulse, or the like.

The probe 140 is made of a polymer having conductivity and elasticity (conductive polymer). As the conductive polymer, for example, PEDOT/PSS in which poly3,4-ethylenedioxythiophene (PEDOT) is doped with polystyrene sulfonic acid (poly4-styrene sulfonate; PSS) can be used.

The probe 140 is produced by punching a conductive polymer sheet member with a mold or the like. The probe 140 has a rectangular shape in plan view and has holes 140A arranged in a matrix. Therefore, the probe 140 is mesh-like.

Here, the probe 140 will be described using FIGS. 4 to 6 in addition to FIGS. 1 and 2. FIG. FIG. 4 is a diagram showing a structure 146 in which the probe 140 and frame portions 145A and 145B are overlapped. FIG. 5 is a cross-sectional view taken along line CC in FIG. FIG. 6 is an exploded view of the electrode structure 100A. 6 also shows the structure 146 shown in FIGS. 4 and 5 in an exploded state.

As shown in FIGS. 4 and 5, the probe 140 is overlapped with rectangular ring-shaped frames 145A and 145B having the same outer size in plan view. The hole portion 140A of the probe 140 is not formed in a portion overlapping with the frame portions 145A and 145B.

A frame portion 145A is adhered to the lower side of the probe 140, and a frame portion 145B is adhered to the upper side. That is, the probe 140 is sandwiched between the frames 145A and 145B. As an example, the probe 140 is 15 mm×15 mm, the frame portions 145A and 145B are 15 mm×15 mm in outer shape, and the inner opening of the rectangular ring is 11 mm×11 mm. In addition, the thickness of the elastic member 124 in the -Z direction is, for example, 1.5 mm.

A carbon adhesive, for example, can be used to bond the probe 140 and the frames 145A and 145B. Since the carbon adhesive has conductivity, the electrical connection between the probe 140 and the frames 145A and 145B can be made more reliable. It should be noted that the probe 140 has low rigidity and it is difficult to maintain the flat plate shape by itself. Frames 145A and 145B also play a role of retaining the shape of probe 140 .

When assembling the biosensor device 100, a plate 110 on which the wiring 130, the electronic device 150, and the battery 160 are mounted, two structures 146 (see FIG. 4), and a cover 120 are prepared. The frame portion 145A of the structure 146 is fixed around the two through holes 111 of the plate 110 with the second adhesive layer 125 . At this time, the frame portion 145A is connected to the wiring 130 . The second adhesive layer 125 is applied to a rectangular annular portion in a plan view under the frame portion 145A.

In this state, when the elastic member 124 is positioned over the probe 140 and the lower end of the elastic member 124 is brought into contact with the upper surface of the probe 140 , the cover 120 is pressed downward, so that the elastic member 124 is pushed through the through hole 111 . , and the elastic member 124 enters the through hole 111 while the probe 140 is stretched. The probe 140 is pressed from a flat state as shown in FIGS. 4 to 6 by the elastic member 124 at the central portion thereof, thereby forming a rectangular annular shape sandwiched between the frame portions 145A and 145B as shown in FIG. It is stretched so that a step is formed between the portion and the central portion.

When the elastic member 124 is completely pushed into the through-hole 111 , the state shown in FIG. 2 is obtained, in which the central portion of the probe 140 in plan view protrudes below the lower surface of the plate 110 . Below, the lower surface of the central portion of the probe 140 in plan view located below the lower end of the elastic member 124 is referred to as the lower surface 140B of the probe 140 .

Also, in this state, the lower surface of the base portion 122 around the elastic member 124 is in contact with the upper surface of the frame portion 145B. Also, in this state, the lower ends of the side walls 121 of the cover 120 are adhered to the upper surface of the plate 110 by the second adhesive layer 125 . Accordingly, the lower portion of the housing portion 120A of the cover 120 is sealed by the plate 110 adhered by the second adhesive layer 125. As shown in FIG.

In addition, although the form in which the structure 146 includes the frame portion 145B has been described here, the structure 146 may not include the frame portion 145B. Also, the probe 140 may not be mesh-like. Moreover, the probe 140 is not limited to being made of a conductive polymer, and may be an electrode that does not have stretchability. For example, an electrode obtained by forming a metal foil such as a copper foil on a wiring board may be used as the probe 140 . Also, the probe 140 is preferably of a dry type rather than a wet type such as polymer gel from the standpoint of impedance stabilization. Further, the elastic member 124 is not limited to a rectangular parallelepiped shape protruding from the lower surface of the base portion 122, and may be hemispherical or the like.

The electronic device 150 includes, for example, an ASIC (application specific integrated circuit), an MPU (Micro Processing Unit), and a memory. The electronic device 150 is connected to the wiring 130 via the terminal 151 and is connected to the probe 140 and the battery 160 via the wiring 130 .

The ASIC includes an A/D (Analog to digital) converter. Electronic device 150 is driven by power supplied from battery 160 and acquires biosignals measured by probe 140 . The electronic device 150 performs processing such as filtering and digital conversion on the biological signal, and the MPU obtains an average value of the biological signal acquired over a plurality of times and stores it in the memory. The electronic device 150 can continuously acquire biosignals for 24 hours or more, as an example. Since the electronic device 150 may measure biological signals over a long period of time, it is devised to reduce power consumption.

A battery 160 is provided on the upper surface of the plate 110 . As the battery 160, a lead-acid battery, a lithium-ion secondary battery, or the like can be used. Battery 160 may be of the button cell type. Battery 160 is an example of a battery. Battery 160 has two terminals (not shown) provided on the bottom surface. Two terminals of battery 160 are electrically connected to wiring 130 via two terminals 161, respectively. The capacity of the battery 160 is set, for example, so that the electronic device 150 can measure biosignals for 24 hours or longer.

The adhesive layer 170 is provided on the lower surface of the plate 110 around the through holes 111 . As the adhesive layer 170, for example, an acrylic adhesive, a rubber diameter adhesive, a silicone adhesive, or the like can be used. be provided. The thickness of the adhesive layer 170 is preferably thinner than the amount by which the probes 140 protrude in the −Z direction from the bottom surface of the plate 110 .

Next, the connection relationship among the probe 140, the electronic device 150, and the battery 160 in the biosensor device 100 will be described with reference to FIG.

FIG. 7 is a diagram showing the circuit configuration of the biosensor device 100. As shown in FIG. Each probe 140 is connected to electronic device 150 and battery 160 via wiring 130 . Two probes 140 are connected in parallel to the electronic device 150 and the battery 160 .

Here, the effects of the biosensor device 100 will be described with reference to FIG. FIG. 8 is a diagram explaining the effect of the biosensor device 100. FIG.

For example, when the biosensor device 100 is attached to the chest of a living body with the adhesive layer 170 to measure an electrocardiographic waveform, the concave curvature of the skin 10 of the chest causes the plate 110 to move in the X direction. Suppose that a bending force is applied so that the upper surface of the center becomes a valley and the lower surface becomes a mountain.

In this case, the plate 110 tries to return to its original flat shape, but since the adhesive layer 170 is attached to the skin 10, the force in the direction (indicated by arrow A) that presses the elastic member 124 against the skin 10 directional force) is applied. The lower surface 140B of the probe 140 is pressed against the skin 10 by the force in the direction of the arrow A, and the entire lower surface 140B of the probe 140 is in sufficient contact with the skin 10 .

Therefore, it is possible to provide the electrode structure and the biosensor device 100 that can keep the lower surface 140B of the probe 140 in stable contact with the concave surface of the skin 10 of the living body.

Note that this is the same even when the probe 140 does not protrude from the bottom surface of the plate 110 in the −Z direction and the position in the Z direction is equal to the bottom surface of the plate 110 .

Moreover, the probe 140 is composed only of a conductive polymer, and the probe 140 itself is not provided with an adhesive or the like. Some adhesives contain moisture, and when such an adhesive is injected into the hole 140A of the probe 140, for example, the impedance of the probe 140 fluctuates due to fluctuations in the water content of the adhesive, resulting in the generation of biosignals. Measurement may be affected.

However, in the present embodiment, the probe 140 is composed only of the conductive polymer, so that the biosignal can be stably measured without being affected by moisture in the adhesive.

Also, by making the probe 140 itself a dry type that does not contain moisture, the biological signal can be stably measured.

Further, the adhesive layer 170 is not necessary on the entire bottom surface of the plate 110, but only around the through holes 111 where the probes 140 are exposed. In the case of attaching biosensor device 100 to the concave surface of skin 10 , adhesive layer 170 is provided in through-hole 111 of plate 110 in order to efficiently generate a force that presses lower surface 140B of probe 140 against skin 10 . It is preferably provided on the periphery and not provided on the central portion of the lower surface of the plate 110 in the X direction. With such a configuration, the amount of adhesive layer 170 can be reduced.

In the above description, the elastic member 124 of the cover 120 is inserted into the through hole 111 of the plate 110, but the plate 110 may include the following structure instead of the through hole 111. FIG. 9 is a plan view showing the plate 110M of the biosensor device of the modified example of the embodiment.

The plate 110M has cutouts 111M instead of the through holes 111 of the plate 110 shown in FIG. The notch portions 111M are portions cut out from both ends of the plate 110 in the X direction toward the center of the plate 110M in the X direction. A structure 146 (see FIG. 4) may be attached to the notch 111M.

In the above description, as shown in FIGS. 4 and 5, the mode in which the probe 140 is overlapped with the rectangular ring-shaped frames 145A and 145B having the same outer size in plan view has been described. However, the probe 140 may be configured as shown in FIG. FIG. 10 is a diagram showing a structure 146M1 of a modification of the embodiment.

The structural body 146M1 is obtained by overlapping the probe 140M1 and the frame portions 145A and 145B. The probe 140M1 has a smaller outer size in plan view than the frame portions 145A and 145B. Therefore, both ends of the frame portions 145A and 145B are overlapped at both ends of the structure 146M1.

FIG. 11 is a diagram showing a structure 146M2 of a modified example of the embodiment. In the structure 146M2, the frame portions 145MA and 145MB are annular in plan view, and the probe 140M1 is circular in plan view. When using such a structure 146M2, the opening shape of the through hole 111 of the plate 110 may be circular.

FIG. 12 is a diagram showing a biosensor device 100M of a modified example of the embodiment. In the biosensor device 100M, the lower surface 140B of the probe 140 protrudes from the lower surface of the plate 110 by 0.2 mm to 2 mm.
Thus, when the lower surface 140B of the probe 140 protrudes from the lower surface of the plate 110, when the biosensor device 100M is attached to the skin 10, the lower surface 140B of the probe 140 is strongly pressed by the skin 10. .

Next, a method for manufacturing the structure 146 (see FIGS. 4 and 5) will be described with reference to FIGS. 13 and 14. FIG. 13A and 13B are diagrams showing the manufacturing process of the structure 146. FIG. 14 to 16 are diagrams showing the pretreatment of the manufacturing process shown in FIG. 13. FIG.

FIG. 13 shows a process of making a tape 146R using rollers 11 to 15 before separating the structure 146 into pieces. Here, a tape-like probe tape 140R and copper tapes 145AR and 145BR before being singulated like the probe 140 and frame portions 145A and 145B are used. Both surfaces of the probe tape 140R are protected by PET (polyethylene terephthalate) films 141R and 142R before being overlapped with the copper tapes 145AR and 145BR.

The probe tape 140R, both sides of which are protected by the PET films 141R, 142R, and the copper tapes 145AR, 145BR can be rolled up and stored.

As shown in FIG. 13, the probe tape 140R and the PET films 141R and 142R are fed by the rollers 11 and 12 in MD (Machine Direction) 1 while the probe tape 140R and the PET films 141R and 142R are protected on both sides by the PET films 141R and 142R. The PET film 141R is peeled off by the roller 11 from the superimposed tapes. Thereby, the lower surface side of the probe tape 140R is exposed.

Further, the copper tape 145AR is fed in the MD2 direction by the rollers 13 and 14, and the copper tape 145AR is attached to the lower surface of the probe tape 140R in the section between the rollers 14 and 12. FIG. When the copper tape 145AR is sent out by the roller 13, the carbon adhesive 144A is applied to the upper surface of the copper tape 145AR, so that the copper tape 145AR is carbon-bonded to the lower surface of the probe tape 140R in the section between the roller 14 and the roller 12. It can be pasted with an agent 144A.

The roller 12 peels off the copper tape 145BR on the probe tape 140R while sending out the tape in which the copper tape 145AR, the probe tape 140R and the PET film 142R are overlapped in the MD3 direction.

Then, the roller 15 downstream of the roller 12 in the direction of MD3 feeds the copper tape 145BR in the direction of MD4, onto the tape in which the copper tape 145AR and the probe tape 140R are overlapped, and onto the probe tape 140R. Apply copper tape 145BR.

When the copper tape 145BR is sent out by the roller 15, the carbon adhesive 144B is applied to the lower surface of the copper tape 145BR, so that the copper tape 145BR can be attached to the upper surface of the probe tape 140R by the roller 15 with the carbon adhesive 144B. .

Further, as shown in FIG. 14, the probe tape 140R may be provided with holes 140A by laser processing or punching while both surfaces are protected by PET films 141R and 142R. The hole portion 140A may be formed in an area corresponding to the mesh-like area of the probe 140 in consideration of the separation into pieces later. The interval in the MD1 direction of the mesh-like regions is, for example, 2 mm. It should be noted that the processing of the hole portion 140A may be performed before feeding in the MD1 direction by the rollers 11 of FIG. 13. As shown in FIG. It is sufficient to form the opening 145AR1 in advance. The opening 145AR1 may be prepared by laser processing, punching processing, etching processing, or the like. Incidentally, this also applies to the copper tape 145BR.

In addition, by separating the tape 146R along the solid lines shown in FIG. 16, the structure 146 (see FIG. 4) in which the probe 140 and the frame portions 145A and 145B are overlapped can be produced.

As described above, the tape 146R can be produced by laminating the copper tape 145AR, the probe tape 140R, and the copper tape 145BR. The tape 146R can be rolled up and stored. Thus, the tape 146R can be produced by roll-to-roll.

Although the electrode structures and biosensor devices of the exemplary embodiments of the present invention have been described above, the present invention is not limited to the specifically disclosed embodiments, but rather the scope of the claims. Various modifications and changes may be made without departing from the scope of the invention.

REFERENCE SIGNS LIST 100 biosensor device 110 plate 111 through hole 120 cover 124 convex portion 130 wiring 140 probe 150 electronic device 160 battery 170 adhesive layer

Claims (8)

a surface layer;
a bottom layer having through holes;
a conductive polymer sheet provided between the surface layer and the bottom layer;
a conductive member electrically connected to an end of the conductive polymer sheet;
an elastic member that is provided between the surface layer and the conductive polymer sheet and causes a portion of the conductive polymer sheet to protrude through the through hole of the bottom layer;
The electrode structure , wherein a part of the conductive polymer sheet protrudes from the bottom surface of the bottom layer by 0.2 mm or more and 2 mm or less . 2. The electrode structure as claimed in claim 1, wherein the conductive member is electrically connected to the edge of the conductive polymer sheet through an adhesive layer. 3. The electrode structure as claimed in claim 2, wherein said adhesive layer is electrically conductive. 4. The electrode structure according to any one of claims 1 to 3, further comprising an adhesive layer provided on the side of the bottom layer opposite to the surface layer side. The electrode structure according to any one of claims 1 to 4, wherein the Young's modulus of the elastic member is smaller than that of the surface layer, and the Shore hardness of the elastic member is 10 or more and 60 or less. 6. The electrode structure according to any one of claims 1 to 5 , wherein said conductive member grips at least one edge of said conductive polymer sheet. 7. The electrode structure of any one of claims 1-6 , wherein the conductive member is selected from at least the group comprising metals, alloys, conductive polymers, and mixtures of conductive polymers and nanoparticles. an electrode structure according to any one of claims 1 to 7 ;
and electronics for processing bio-signals acquired through said electrode structure.

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