CN105466985A - Electrode for biological detection test piece and manufacturing method thereof - Google Patents

Abstract

The invention discloses an electrode for a biological detection test piece. The electrode for the biological detection test piece comprises a substrate, a non-conductive adhesive layer arranged on the substrate and a first metal layer arranged on the non-conductive adhesive layer. The non-conductive adhesive layer comprises a sensitizer and an activator, so that the process or the material used for manufacturing the electrode for the biological detection test piece has elasticity, and the manufactured electrode for the biological detection test piece still has good conductive property. The invention also discloses a method for manufacturing the electrode for the biological detection test piece.

Description

Electrode for bioassay test strip and manufacturing method thereof

technical field

The present invention relates to an electrode and a manufacturing method thereof, in particular to an electrode used for a biological detection test piece and a manufacturing method thereof.

Background technique

In recent years, the incidence of diabetes, hypercholesterolemia or gout in China has been increasing year by year. In addition to diet and drug control, the most important thing for diabetes and gout is self-examination. Therefore, for such diseases, there is a great demand in the market for bioassay test strips that can be easily carried and used for detecting blood sugar, cholesterol or uric acid.

At present, the electrodes of the test strips produced by most of the relevant test strip manufacturers are all made by screen printing, and the conductive material is mainly carbon or silver. However, the finished electrodes produced by the screen printing process have disadvantages such as unstable output, unstable impedance value, low accuracy, large power consumption, and slow response speed.

In order to solve the above problems, Taiwan Patent No. I396844 has disclosed an electrode for a biological detection test strip and its production method, which can effectively remedy the above-mentioned shortcomings of the general detection test strip. However, the electrode structure proposed in Taiwan Patent No. I396844 has low flexibility in process or material selection. If there is no required equipment during production or the price of raw materials on the market rises, it will be difficult to find alternatives and increase production costs.

Contents of the invention

(1) Technical problems to be solved

In view of the problems of the above-mentioned well-known technologies, the object of the present invention is to provide an electrode for biological detection test strips, so that the electrodes used for biological detection test strips can maintain high quality, and at the same time, the selection of processes or materials is extremely sensitive during production. Great elasticity.

(2) Technical solution

According to the object of the present invention, an electrode for a biological detection test piece is proposed. The electrode used for the biological detection test piece includes a substrate, a non-conductive adhesive layer arranged on the substrate and a first metal layer arranged on the non-conductive adhesive layer. The non-conductive adhesive layer contains sensitizer and activator.

Preferably, the material of the first metal layer can be palladium.

Preferably, the electrode for the biological detection test piece may further include a second metal layer disposed on the first metal layer. The material of the first metal layer can be palladium, and the material of the second metal layer can be gold.

Preferably, the electrode for the biological detection test piece may further include a second metal layer disposed on the first metal layer and a third metal layer disposed on the second metal layer. The material of the first metal layer can be palladium, the material of the second metal layer can be nickel, and the material of the third metal layer can be gold or palladium.

Preferably, the electrode for the biological detection test piece may further include a second metal layer disposed on the first metal layer, a third metal layer disposed on the second metal layer, and a fourth metal layer disposed on the third metal layer. metal layer. The material of the first metal layer can be copper, the material of the second metal layer can be palladium, the material of the third metal layer can be nickel, and the material of the fourth metal layer can be gold or palladium.

Preferably, the sensitizer may comprise glucose, hydrazine, borohydride, stannous chloride, aminoborane compounds, aldehydes, hypophosphite or tartrate, while the activator may comprise nickel, cobalt, palladium, sodium or Particles or compounds of copper.

Preferably, the non-conductive adhesive layer may further include an adhesive, and the adhesive may include polyvinyl acetate, polyvinyl alcohol or titanium isopropoxide.

Preferably, the non-conductive adhesive layer may further comprise an adhesive, and the adhesive may comprise an acrylic polymer or an alkoxide.

Preferably, the substrate may be a flexible plastic substrate, aluminum substrate, ceramic substrate, glass substrate or glass fiber (FR4) substrate.

According to another object of the present invention, a method for manufacturing an electrode for a biological test strip is proposed. The method includes providing a substrate, forming a non-conductive adhesive layer on the substrate, the non-conductive adhesive layer includes a sensitizer and an activator, and forming one or more metal layers on the non-conductive adhesive layer.

In summary, according to the electrode for biological detection test strips of the present invention, it may have one or more of the following advantages:

(1) Electrodes used for biological detection test strips can pass through a non-conductive adhesive layer containing sensitizers and activators, thereby chemically plating metal layers with good properties on various substrates.

(2) The electrode used for the biological detection test piece can pass through the non-conductive adhesive layer containing the sensitizer and the activator, thereby making the process of making the electrode of the biological detection test piece more flexible.

Description of drawings

FIG. 1 is a schematic structural diagram of an electrode for a biological detection test strip according to a first embodiment of the present invention.

FIG. 2 is a schematic structural diagram of an electrode for a biological detection test strip according to a second embodiment of the present invention.

FIG. 3 is a schematic structural view of an electrode for a biological detection test strip according to a third embodiment of the present invention.

FIG. 4 is a schematic structural diagram of an electrode for a biological detection test strip according to a fourth embodiment of the present invention.

FIG. 5 is a flowchart of a method for manufacturing an electrode for a biological test strip according to a fifth embodiment of the present invention.

FIG. 6 is a flowchart of a method for manufacturing an electrode for a biological detection test strip according to a sixth embodiment of the present invention.

FIG. 7 is a flowchart of a method for manufacturing an electrode for a biological detection test strip according to a seventh embodiment of the present invention.

FIG. 8 is a flowchart of a method for manufacturing an electrode for a biological detection test strip according to an eighth embodiment of the present invention.

FIG. 9 is a flow chart of a method for manufacturing an electrode for a biological test strip according to a ninth embodiment of the present invention.

FIG. 10 is a flowchart of a method for manufacturing an electrode for a biological detection test strip according to a tenth embodiment of the present invention.

FIG. 11 is a flowchart of a method for manufacturing an electrode for a biological test strip according to an eleventh embodiment of the present invention.

Fig. 12 is an exploded perspective view of a biological detection test strip including electrodes for a biological detection test strip of the present invention.

FIG. 13 is a graph showing the data measured by the bioassay test strip in FIG. 12 .

FIG. 14 is a graph of data measured by a bioassay test strip containing carbon/silver (C/Ag) electrodes.

FIG. 15 is a graph showing the comparison between the data measured by the biological detection test strip in FIG. 12 and the data measured by the YSI-2300 blood glucose analyzer.

detailed description

With reference to the accompanying drawings, the detailed description is as follows in the form of the embodiment, and the drawings used therein are only for illustration and auxiliary description purposes, and may not be the true proportion and precise configuration of the present invention after implementation, so they should not The proportions and configuration relationships of the drawings are limited to the protection scope of the technical solutions in practical implementation of the present invention.

Embodiments of electrodes for biological detection test strips according to the present invention will be described below with reference to related drawings. For ease of understanding, the same components in the following embodiments are described with the same reference numerals.

Referring to FIG. 1 , it is a schematic structural diagram of an electrode for a biological detection test strip according to a first embodiment of the present invention. In the figure, the electrode used for the biological detection test strip includes a substrate 100 , a non-conductive adhesive layer 200 disposed on the substrate 100 and a first metal layer 300 disposed on the non-conductive adhesive layer 200 . The non-conductive adhesive layer 200 includes a sensitizer and an activator.

Typically, bonding or plating is used to attach the desired metal to the substrate. Among them, electroless plating usually has a more uniform thickness, and for the electrodes used for detection, it can usually also obtain better quality electrical signals. However, not all substrates can be directly attached to metals by electroless plating. For example, metals do not readily attach to plastic or ceramic substrates without the aid of external forces by the redox reactions required for electroless plating.

Therefore, in the present invention, before the electroless plating of the first metal layer 300 , a non-conductive adhesive layer 200 may be provided on the substrate 100 , and the non-conductive adhesive layer 200 contains a sensitizer and an activator. The sensitizer and activator can act together to render the surface properties of the substrate susceptible to electroless plating reactions for the intended metal. Specifically, after the sensitizer and the activator work together, a highly chemically active substance will be produced, which can effectively reduce the chemical potential energy that needs to be eliminated during electroless plating, thereby promoting the self-sustainability of the metal main agent in the electroplating solution. Catalytic reaction. It is worth mentioning that the non-conductive adhesive layer 200 can activate the surface of the substrate 100 without additional process (such as laser treatment or pickling process) to facilitate the electroless plating reaction. In this way, when the substrate 100 provided with the non-conductive adhesive layer 200 is immersed in an electroplating solution in which the main component of the metal is the material of the first metal layer 300, metal will be formed on the surface of the substrate 100 provided with the non-conductive adhesive layer 200. The self-catalyzed redox reaction forms the first metal layer 300 on the surface of the substrate 100 provided with the non-conductive adhesive layer 200 . In some embodiments, the material of the first metal layer may be copper, palladium, nickel or cobalt.

Preferably, the material of the first metal layer 300 may be palladium.

Referring to FIG. 1 again, in an electrode used in a biological detection test strip, the outermost metal must have good conductivity, such as palladium or gold. In the electrode for the biological detection test strip of the present invention, due to the existence of the non-conductive adhesive layer 200 , palladium can be easily disposed on the surface with the non-conductive adhesive layer 200 through electroless plating. Therefore, the material of the first metal layer 300 can be palladium, so that the first metal layer 300 is the outermost metal layer of the electrode used in the biological test strip. That is to say, only the substrate 100 , the non-conductive adhesive layer 200 and the first metal layer 300 can constitute the main body of the electrode for the biological detection strip. As shown in FIG. 1 , the thickness of the first metal layer 300 made of palladium can be changed through the process conditions of electroless plating, and then adjusted to the optimum thickness suitable for the electrodes of the biological detection strip. The process of this embodiment can be greatly simplified due to the structure, thereby reducing the process cost.

Preferably, the electrode for the biological detection test strip may further include a second metal layer 400 disposed on the first metal layer 300 . The material of the first metal layer 300 may be palladium, and the material of the second metal layer 400 may be gold.

Referring to FIG. 2 , it is a schematic structural diagram of an electrode for a biological detection test strip according to a second embodiment of the present invention. As shown in the figure, the electrode for biological detection test strip of the present invention can make the selection of the material of the metal layer very flexible, so the second metal layer 400 can be set on the first metal layer 300, and the second metal layer 400 is the metal layer used for the outermost layer of the electrode of the biological detection test piece. At this time, the material of the first metal layer 300 can still be palladium, but compared with the first embodiment, since the first metal layer 300 is used as an intermediary layer at this time, the thickness does not need to be too thick. The material of the second metal layer 400 disposed on the first metal layer 300 can be gold, so that the electrodes used in the biological test strip have good conductivity.

Preferably, the electrode used for the biological detection test strip may further include a second metal layer 400 disposed on the first metal layer 300 and a third metal layer 500 disposed on the second metal layer 400 . The material of the first metal layer 300 may be palladium, the material of the second metal layer 400 may be nickel, and the material of the third metal layer 500 may be gold or palladium.

Referring to FIG. 3 , it is a schematic structural diagram of an electrode for a biological detection test strip according to a third embodiment of the present invention. As shown in the figure, the metal layer of the electrode used in the biological detection strip of the present invention may further include a third metal layer 500 disposed on the second metal layer 400 . Since in this embodiment, the third metal layer 500 is the outermost metal layer, the material of the third metal layer 500 can be the material palladium of the first metal layer in the first embodiment or palladium in the second embodiment. The material of the second metal layer is gold, and its conductive properties have not changed much. The material of the first metal layer 300 as the intermediary layer can still be palladium, and the thickness of the palladium can be relatively thin and be a thin layer of palladium. However, the material of the second metal layer 400 that is also used as the intermediary layer can be nickel at this time, so as to reduce the amount of noble metal used, thereby reducing the manufacturing cost of the electrode used for the biological detection test piece. The conductive property of the electrode of the test piece has not changed substantially but still has good conductivity.

Preferably, the electrode used for the biological detection test strip may further include a second metal layer 400 disposed on the first metal layer 300, a third metal layer 500 disposed on the second metal layer 400, and a third metal layer disposed on the third metal layer. 500 on the fourth metal layer 600 . The material of the first metal layer 300 can be copper, the material of the second metal layer 400 can be palladium, the material of the third metal layer 500 can be nickel, and the material of the fourth metal layer 600 can be gold or palladium.

Referring to FIG. 4 , it is a schematic structural diagram of an electrode for a biological detection test strip according to a fourth embodiment of the present invention. As mentioned above, the electrode used in the biological detection test piece of the present invention is extremely flexible in the selection of materials. Therefore, in this embodiment, the metal layer used for the electrode of the biological detection strip may have a four-layer structure. Since the outermost metal layer needs to have good electrical conductivity, the material of the fourth metal layer 600 can be the material palladium of the first metal layer in the first embodiment or the material gold of the second metal layer in the second embodiment. , and its conductive properties did not change much. At this time, the material of the first metal layer 300 as the intermediary layer may be copper. The material of the second metal layer 400 can be palladium, and the thickness of palladium can be relatively thin as a thin layer of palladium. The material of the third metal layer 500 may be nickel, and the fourth metal layer 600 is formed thereon. In this embodiment, although the process steps of electroless plating are more, the amount of precious metal used can be reduced, thereby reducing the cost of materials.

In a specific embodiment, the thickness of the non-conductive adhesive layer 200 may be about 1 to 20u" (microinch); the material of the first metal layer 300 may be copper, and the thickness may be about 1 to 30u"; the second metal layer The material of 400 can be palladium, and the thickness can be about 1 to 10u "; The material of the third metal layer 500 can be nickel, and the thickness can be about 20 to 200u "; And the material of the fourth metal layer 600 can be gold, and the thickness can be It is about 0.5 to 10u". Or in another specific embodiment, the non-conductive adhesive layer 200, the first metal layer 300, the second metal layer 400 and the third metal layer 500 are the same as the above, but the fourth metal layer 600 The material can be palladium, and the thickness can be about 1 to 20 u".

For example, in the case where the material of the first metal layer 300 grown on the substrate 100 is copper, the thickness of the non-conductive adhesive layer 200 between the first metal layer 300 and the substrate 100 can be 2u", and the first metal layer 300 may be 4u" thick. If you want to use commercially available copper foil to form the first metal layer 300, because the general thickness of commercially available copper foil is 12u", and the thickness of 4u" copper foil is a special specification, so use commercially available copper foil to form The first metal layer 300 with a thickness of 4u" will greatly increase the cost. In contrast, the method for forming the first metal layer 300 made of copper in the present invention is electroless plating, and the first metal layer can be easily controlled only by adjusting process parameters. The thickness of the layer 300, so a thin (eg, 4u") first metal layer 300 can be formed at a relatively low cost. In the electrode used for biological detection test strips, since the thickness of the intermediate metal layer does not need to be too thick, the structure and method disclosed in the present invention can easily control the intermediate metal layer to the required thickness, thereby reducing the amount of materials used and the manufacturing cost .

To sum up, since the electrode used in the biological detection test piece of the present invention has flexibility in the selection of technology and materials, it can freely choose a lower-cost production method according to the conditions of existing equipment and materials during production, so that The produced electrodes for biological detection test strips still maintain good electrical conductivity. Embodiments of the non-conductive adhesive layer 200 and detailed processes used in the present invention will be described later.

Preferably, the sensitizer may comprise glucose, hydrazine, borohydride, stannous chloride, aminoborane compounds, aldehydes, hypophosphite or tartrate, while the activator may comprise nickel, cobalt, palladium, sodium or Particles or compounds of copper.

The non-conductive adhesive forming the non-conductive adhesive layer 200 contains sensitizers and activators capable of changing the surface properties of the substrate 100 . Specifically, sensitizers can include glucose, hydrazine, borohydride, stannous chloride, aminoborane compounds, aldehydes, hypophosphite or tartrate, and can be combined with activators added to non-conductive adhesives, such as Particles or compounds of nickel, cobalt, palladium, steel or copper, resulting in highly chemically active substances. For example, the non-conductive adhesive of the non-conductive adhesive layer 200 may comprise stannous chloride, palladium chloride, hydrochloric acid, water and a paste corresponding to the process used, wherein the stannous chloride as a sensitizer reacts with palladium chloride to produce Palladium metal particles or coordination compounds, and such substances have high chemical activity so that the metal main agent in the electroplating solution can be plated on the non-conductive adhesive layer 200 to form a predetermined metal layer by a self-catalyzed reaction during electroless plating. The above-mentioned paste may correspond to the type of process used when disposing the non-conductive adhesive on the substrate 100 , for example, when using screen printing, the paste may be a colloidal paste of titanium oxide. Of course, the present invention is not limited thereto, and any sensitizers and activators that make the surface of the substrate 100 easy to electroless plating should be included in the present invention.

Preferably, the non-conductive adhesive layer 200 may further include an adhesive, and the adhesive may include polyvinyl acetate, polyvinyl alcohol or titanium isopropoxide. Alternatively, the binder may comprise acrylic polymers or alkoxides.

In order to make the non-conductive adhesive layer 200 clearly form the required circuit pattern in the process, or can be directly shaped in the process, the non-conductive adhesive used to form the non-conductive adhesive layer 200 can contain an adhesive, so that it It has a certain viscosity. According to the type of adhesive, after the non-conductive adhesive is disposed to form the non-conductive adhesive layer 200, it can be cured by laser process or thermal process. In addition, the adhesive helps to enhance the adhesion between the first metal layer 300 and the substrate 100 , so that the electrodes used in the biological test strips have better structural strength.

Preferably, the substrate 100 may be a flexible plastic substrate, an aluminum substrate, a ceramic substrate, a glass substrate or a glass fiber (FR4) substrate.

Since the non-conductive adhesive layer 200 used in the present invention has the property of activating the surface of the substrate, almost all kinds of substrates can be used to make the substrate 100 for the electrode of the biological detection strip. Due to the non-conductive property, a metal substrate such as an aluminum substrate can also be used as the substrate 100 used in the present invention. In an embodiment, the substrate 100 used in the present invention may be a polyethylene terephthalate (PET) substrate, and its thickness may be about 0.01 to 1 cm. In another embodiment, the substrate 100 may be a ceramic/glass/aluminum substrate, and its thickness may be about 0.1 to 2 cm.

In addition, when the substrate 100 used in the present invention is a flexible plastic substrate, the flexible plastic substrate used may include a polyethylene terephthalate (PET) substrate, a polyimide (PI) substrate, Polyvinyl chloride (PVC) substrate or polypropylene (PP) substrate.

Next, the process of making the electrode for the biological detection test strip of the present invention will be described in detail in conjunction with the accompanying drawings, so as to show that the electrode for the biological detection test strip of the present invention can be formed by various processes, so there are advantages in the selection of the process. elasticity. It should be noted that the present invention is not limited thereto, and any electrodes for biological detection test strips manufactured by other processes and having the same or similar functional structure as the electrodes for biological detection test strips disclosed in the present invention should also be included in the scope of the present invention.

Referring to FIG. 5 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to a fifth embodiment of the present invention.

In step S11 , a screen can be made according to the metal circuit pattern to be formed later. And in step S12, the non-conductive offset can be printed on the substrate 100 using a screen plate, and the thickness of the non-conductive adhesive layer 200 formed at this time can be about 1 to 20u", and has a predetermined circuit pattern. In step S13, can Carry out heat treatment to the substrate 100 provided with the non-conductive adhesive layer 200. The heat treatment can be carried out in an oven, the temperature can be about 30 to 150 degrees Celsius, and the time can be about 10 to 120 minutes. Afterwards, sandbags can be used to treat the substrate 100 and the non-conductive adhesive. After the surface of layer 200 is ground, carry out follow-up steps again, to improve the quality of electroless plating.In step S14, the electroplating solution used in metallization process can comprise different metal main agents according to the metal layer that is predetermined to grow into, and Corresponding chelating agent, alkali, formaldehyde and stabilizer.At this moment, because the substrate 100 surface that is provided with non-conductive glue layer 200 is suitable for carrying out electroless plating, so metal can only be arranged on the surface with non-conductive glue through oxidation-reduction reaction layer 200 on the substrate 100 surface. That is to say, the first metal layer 300 generated will directly have a predetermined circuit pattern. At this time, according to the required electrode structure, the electroless plating process of other metal layers will be carried out in sequence, such as The aforementioned second embodiment, the third embodiment or the fourth embodiment. The mode of generating other metal layers is basically the same as the mode of generating the first metal layer 300, and the difference is only the metal main agent in the electroplating solution. This implementation The characteristic of the example is that the process steps are few and simple, which can reduce the time and cost required for the process.

Referring to FIG. 6 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to a sixth embodiment of the present invention.

In step S21 , a screen can be produced by widening the metal circuit pattern to be formed by about 0.1 to 0.5 cm. That is to say, at this time, the pattern on the screen will be about 0.1 to 0.5 cm wider than the predetermined line width. In step S22, the non-conductive offset can be printed on the substrate 100 by using a screen plate, and the thickness of the non-conductive adhesive layer 200 formed at this time can be about 1 to 20 u", and has a predetermined widening circuit pattern. In step S23, The substrate 100 provided with the non-conductive adhesive layer 200 can be heat-treated, and the heat treatment can be performed in an oven at a temperature of about 30 to 150 degrees Celsius and for about 10 to 120 minutes. Afterwards, a sandbag can be used to treat the substrate 100 and the non-conductive After the surface of adhesive layer 200 is ground, carry out follow-up steps again, to improve the quality of electroless plating.In step S24, will utilize optical photolithography process, on non-conductive adhesive layer 200, predetermined circuit patterns are attached The upper shielding layer, that is, the shielding layer on the non-conductive adhesive layer 200 has a width of about 0.1 to 0.5 cm on the side of the non-conductive adhesive layer 200, and an opening of a predetermined circuit pattern is formed in the middle of the shielding layer. Shielding layer can be photosensitive film or printing ink.In step S25, use metallization process to form the metal layer of monolayer or multilayer on the non-conductive adhesive layer 200 that is not covered by shielding layer, metallization process and aforementioned step S14 The metallization process is the same or similar, so it will not be described in detail. At this time, the metal will only be formed on the surface of the non-conductive adhesive layer 200 not covered by the shielding layer, thereby forming a predetermined circuit pattern. In step S26, the alkaline liquid is first used Or the corresponding liquid removes the shielding layer, and then uses a volatile liquid such as alcohol or butanone or a corresponding liquid to remove the redundant non-conductive adhesive layer 200. The characteristics of this embodiment are required compared to the fifth embodiment Less non-conductive glue can save material cost. In addition, the resolution of circuit pattern formed by optical lithography process is better, and it will have better signal transmission quality when used as an electrode for biological detection test strips.

Referring to FIG. 7 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to a seventh embodiment of the present invention.

Steps S31 , S32 and S33 in this embodiment are the same as steps S21 , S22 and S23 in the sixth embodiment respectively, so they will not be described in detail. Afterwards, sandbags can be used to grind the surfaces of the substrate 100 and the non-conductive adhesive layer 200 before performing subsequent steps to improve the quality of the electroless plating. In S34, the shielding layer is placed on the non-conductive adhesive layer 200 with a predetermined circuit pattern by using an optical lithography process, that is to say, the pattern width of the shielding layer will be about 0.1 to 0.5 cm. The shielding layer can be a photosensitive film or ink. In step S35 , the shielding layer is first removed with an alkaline chemical solution or a corresponding chemical solution, and then the redundant non-conductive adhesive layer 200 is removed with a volatile chemical solution such as alcohol or methyl ethyl ketone or a corresponding chemical solution. In step S36, a single-layer or multi-layer metal layer is formed on the non-conductive adhesive layer 200 with a predetermined circuit pattern by using a metallization process. The metallization process is basically the same as the metallization process in step S14 of the fifth embodiment. or similar, so no further details are given. Compared with the fifth embodiment, this embodiment requires less non-conductive glue, which can save material cost. In addition, the resolution of the circuit pattern formed by the optical lithography process is better, and it will have better signal transmission quality when used as an electrode for a biological detection test strip.

Referring to FIG. 8 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to an eighth embodiment of the present invention.

In step S41 , a non-conductive adhesive having a predetermined circuit pattern and thickness is disposed on the substrate 100 by 3D printing to form the non-conductive adhesive layer 200 . Steps S42 and S43 are basically the same as or similar to steps S13 and S14 of the fifth embodiment respectively, so details are not repeated. The feature of this embodiment is that after the circuit is designed, the finished product can be produced quickly by 3D printing, which can reduce the time required from design to manufacture, and is convenient for quickly verifying the effect of the finished product.

Referring to FIG. 9 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to a ninth embodiment of the present invention.

In step S51 , the non-conductive glue is disposed on the entire surface of the substrate 100 , and the manner of disposing the non-conductive glue may be spraying, coating or printing. In step S52, heat treatment may be performed on the substrate 100 provided with the non-conductive adhesive layer 200, and the parameters of the heat treatment may be the same as those in step S13 of the fifth embodiment, so details will not be repeated. In step S53 , the first metal layer 300 is formed on the non-conductive adhesive layer 200 by a metallization process, and at this time the first metal layer 300 covers the entire surface of the non-conductive adhesive layer 200 . In step S54 , a shielding layer forming a predetermined circuit pattern is disposed on the first metal layer 300 by using an optical lithography process. In step S55, the first metal layer 300 not covered by the shielding layer is etched, so that the remaining first metal layer 300 has a predetermined circuit pattern. After removing the shielding layer and the non-conductive adhesive layer outside the predetermined circuit pattern, the subsequent metallization process of step S56 is performed to dispose other metal layers on the first metal layer 300 . It should be noted that, if the manufactured electrode structure for the biological detection test strip is the same as that of the first embodiment, step S56 of this embodiment can be omitted.

Referring to FIG. 10 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to a tenth embodiment of the present invention.

Steps S61 and S62 of this embodiment are respectively the same as S51 and S52 of the ninth embodiment, so details are not repeated. In step S63, a shielding layer with a predetermined circuit pattern is placed on the non-conductive adhesive layer 200 using an optical lithography process, and then a volatile liquid such as alcohol or methyl ethyl ketone or a corresponding liquid is used to remove the shielding layer. The non-conductive adhesive layer 200 is removed, and then the shielding layer is removed by using an alkaline chemical solution or a corresponding chemical solution, so as to leave the non-conductive adhesive layer 200 with a predetermined circuit pattern. In step S64, a single-layer or multi-layer metal layer is formed on the non-conductive adhesive layer 200 with a predetermined circuit pattern using a metallization process, the metallization process is basically the same as the metallization process in step S14 of the fifth embodiment or similar, so no further details are given.

Referring to FIG. 11 , it is a flowchart of a method for manufacturing an electrode for a biological test strip according to an eleventh embodiment of the present invention.

Steps S71 and S72 of this embodiment are respectively the same as S51 and S52 of the ninth embodiment, and thus will not be repeated. In step S73 , the shielding layer is covered on the portion of the non-conductive adhesive layer 200 other than the predetermined circuit pattern by using an optical lithography process. In step S74, a single-layer or multi-layer metal layer is formed on the non-conductive adhesive layer 200 not covered by the shielding layer using a metallization process. The metallization process is basically the same as the metallization process in step S14 of the fifth embodiment. The same or similar, so no more details. That is to say, after step S74 , the single-layer or multi-layer metal layer formed on the non-conductive adhesive layer has a predetermined circuit pattern. In step S75 , the shielding layer is firstly removed with an alkaline chemical solution or a corresponding chemical solution, and then a volatile chemical solution such as alcohol or methyl ethyl ketone or a corresponding chemical solution is used to remove the non-conductive adhesive layer 200 of an unpredetermined circuit pattern.

Referring to FIG. 12 , it is a three-dimensional exploded view of a biological detection test strip including an electrode for a biological detection test strip of the present invention. The biological detection test piece may include a substrate 10 , an electrode layer 20 , a biologically active substance 30 , a middle spacer 40 and a top cover 50 . When in use, the substrate 10, the electrode layer 20, the biologically active material 30, the middle spacer 40 and the upper cover 50 are combined to form an integral biological detection test piece.

The electrode used for the biological detection test strip of the present invention can be directly used in the manufacture of the biological detection test strip to detect the biological parameters of blood sugar, cholesterol, uric acid and hemoglobin (Hb), and what is shown in Fig. 12 is an example Unique bioassay test strip structure. The electrode layer 20 may include one or more layers of the first metal layer 300 to the fourth metal layer 600 , and the non-conductive adhesive layer 200 . More precisely, the electrode layer 20 may include the electrode structures shown in the first to fourth embodiments in addition to the substrate 10 . The biologically active substance 30 disposed on the electrode layer 20 may correspond to the biological parameter to be detected. For example, when the biological parameter to be detected is blood glucose concentration, the biologically active substance 30 may include glucose oxidase. In some embodiments, the biologically active substance 30 may include enzymes, antigens or antibodies corresponding to the biological parameters to be detected. In case the bioactive substance 30 comprises an enzyme, the enzyme may comprise glucose oxidase, cholesterol esterase or uricase.

Referring to Fig. 13 to Fig. 15, it is the chart showing the data measured by the biological detection test strip of Fig. 12 respectively, the chart showing the data measured by the biological detection test strip comprising carbon/silver (C/Ag) electrode and A chart showing the correspondence between the data measured by the biological detection test strip in FIG. 12 and the data measured by the blood glucose tester YSI-2300. In the test results of FIG. 13 and FIG. 15 , the electrode layer 20 includes the electrode structure shown in the aforementioned fourth embodiment.

As shown in FIG. 13 , the application of the electrode used in the biological detection test strip of the present invention has a good effect on the detection of blood sugar concentration. Specifically, as shown in the detection results in the figure, whether it is in a high glucose concentration (greater than 300mg/dl) or a low glucose concentration (less than 100mg/dl), the electrode for the biological detection test strip of the present invention can provide Good linear detection results. Referring to FIG. 14 , it is a chart of data measured by a bioassay test strip containing conventional carbon/silver (C/Ag) electrodes. After comparing Fig. 13 with Fig. 14, it shows that the electrode for biological detection test strip of the present invention is relative to the traditional biological detection test strip comprising carbon/silver (C/Ag) electrode, the electrode for biological detection of the present invention The detection results provided by the electrodes of the test strip are consistent, and there will be no inconsistency between the detection results of high glucose concentration and low glucose concentration that will occur when the carbon/silver (C/Ag) electrode is used to detect. Fig. 15 shows a chart corresponding to the data measured by the blood glucose tester YSI-2300. The blood glucose concentration measured by the test paper in Fig. 15 is the blood glucose concentration using the electrode for the biological detection test strip of the present invention. Under the standard calculation of ISO15197; 2013, the electrode used for the biological detection test strip of the present invention can have a detection result with an error much less than 15%, and the error at each blood glucose concentration test point is close to 5% or below 5%, It is further proved that the electrode for biological detection test strips of the present invention can provide good detection results consistent with instrument test results.

The above description is for illustration only, not limitation. Any equivalent modification or change made without departing from the scope of the present invention shall be included in the scope of protection of the appended rights.

Explanation of reference signs

100, 10: Substrate

200: Non-conductive adhesive layer

300: first metal layer

400: second metal layer

500: third metal layer

600: fourth metal layer

20: electrode layer

30: Biologically active substances

40: septum

50: top cover

S11, S12, S13, S14, S21, S22, S23, S24, S25, S26, S31, S32, S33, S34, S35, S36, S41, S42, S43, S51, S52, S53, S54, S55, S61, S62, S63, S64, S65, S71, S72, S73, S74, S75: steps.

Claims (10)

1., for an electrode for biological detecting test piece, it comprises:

Substrate,

Non-conductive glue layer, it is arranged on described substrate, and

The first metal layer, it is arranged on described non-conductive glue layer;

Wherein said non-conductive glue layer comprises sensitizer and activator.

2., as claimed in claim 1 for the electrode of biological detecting test piece, it is characterized in that, the material of described the first metal layer is palladium.

3., as claimed in claim 1 for the electrode of biological detecting test piece, it is characterized in that, also comprise:

Second metal level, it is arranged on described the first metal layer,

The material of wherein said the first metal layer is palladium, and the material of described second metal level is gold.

4., as claimed in claim 1 for the electrode of biological detecting test piece, it is characterized in that, also comprise:

Second metal level, it is arranged on described the first metal layer, and

3rd metal level, it is arranged on described second metal level;

The material of wherein said the first metal layer is palladium, and the material of described second metal level is nickel, and the material of described 3rd metal level is gold or palladium.

5., as claimed in claim 1 for the electrode of biological detecting test piece, it is characterized in that, also comprise:

Second metal level, it is arranged on described the first metal layer,

3rd metal level, it is arranged on described second metal level, and

4th metal level, it is arranged on described 3rd metal level;

The material of wherein said the first metal layer is copper, and the material of described second metal level is palladium, and the material of described 3rd metal level is nickel, and the material of described 4th metal level is gold or palladium.

6. as claimed in claim 1 for the electrode of biological detecting test piece; it is characterized in that; described sensitizer comprises glucose, diamine, hydroborate, stannous chloride, amino borane compound, aldehydes, hypophosphites or tartrate, and described activator comprises particulate or the compound of nickel, cobalt, palladium, steel or copper.

7., as claimed in claim 1 for the electrode of biological detecting test piece, it is characterized in that, described non-conductive glue layer also comprises bonding agent, and described bonding agent comprises polyvinyl acetate, polyvinyl alcohol (PVA) or isopropyl titanate.

8., as claimed in claim 1 for the electrode of biological detecting test piece, it is characterized in that, described non-conductive glue layer also comprises bonding agent, and described bonding agent comprises acrylate copolymer or alkoxide.

9. manufacture a method for the electrode being used for biological detecting test piece, it comprises:

Substrate is provided;

Form non-conductive glue layer on the substrate, described non-conductive glue layer comprises sensitizer and activator; And

Described non-conductive glue layer is formed one or more layers metal level.

10. the method manufacturing the electrode being used for biological detecting test piece as claimed in claim 9; it is characterized in that; described sensitizer comprises glucose, diamine, hydroborate, stannous chloride, amino borane compound, aldehydes, hypophosphites or tartrate, and described activator comprises particulate or the compound of nickel, cobalt, palladium, steel or copper.