WO2013062322A1 - Biocapteur et procédé de fabrication de celui-ci - Google Patents

Biocapteur et procédé de fabrication de celui-ci Download PDF

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Publication number
WO2013062322A1
WO2013062322A1 PCT/KR2012/008785 KR2012008785W WO2013062322A1 WO 2013062322 A1 WO2013062322 A1 WO 2013062322A1 KR 2012008785 W KR2012008785 W KR 2012008785W WO 2013062322 A1 WO2013062322 A1 WO 2013062322A1
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WO
WIPO (PCT)
Prior art keywords
electrode
biosensor
base substrate
signal transmission
plating
Prior art date
Application number
PCT/KR2012/008785
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English (en)
Korean (ko)
Inventor
이진우
최재규
정해광
Original Assignee
주식회사 세라젬메디시스
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Application filed by 주식회사 세라젬메디시스 filed Critical 주식회사 세라젬메디시스
Publication of WO2013062322A1 publication Critical patent/WO2013062322A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
    • G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/403—Cells and electrode assemblies
    • G01N27/406—Cells and probes with solid electrolytes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/483—Physical analysis of biological material
    • G01N33/487—Physical analysis of biological material of liquid biological material

Definitions

  • the present invention relates to a biosensor, and more particularly, to a biosensor and a method of manufacturing the same that can simplify the structure and manufacturing process.
  • Biosensor refers to a means of investigating the properties of a substance by using a function of a living organism. Since a biomaterial such as blood sugar or ketone is used as a detection device, it has excellent sensitivity and reaction specificity. Therefore, it is used in a wide range of fields such as clinical chemical analysis in the medical / medical field, process measurement in the bio industry, environmental measurement, and stability evaluation of chemicals. In particular, biosensors are widely used for various self tests such as blood sugar measurement, pregnancy diagnosis, urine test, and rapid disease diagnosis.
  • the most common electrochemical biosensor is mainly used for blood glucose measurement.
  • An electrochemical reaction occurs when a sample such as blood is introduced into the biosensor, and an electrical signal is generated and transmitted to a measuring instrument connected to or connected to the biosensor. That's the way.
  • the structure of a conventional biosensor is a structure in which a plurality of thin film layers are stacked as a structure in which a reactor plate is raised on a lower substrate, a sample introduction spacer is placed on a reactor substrate, an upper substrate is raised thereon, and a cover is placed on the top thereof. to be. Most of them are in the form of rod strips, in particular very small in size, requiring a fairly sophisticated process.
  • An object of the present invention is to provide a biosensor having a one-layer structure and a method of manufacturing the same.
  • Another object of the present invention is to provide a biosensor having a simple manufacturing process and a method of manufacturing the same.
  • Still another object of the present invention is to provide a biosensor having a low manufacturing cost and a method of manufacturing the same.
  • the present invention is a base substrate 10,
  • a working electrode 30 and a reference electrode 40 formed on the inner wall of the sample introduction path 20 and spaced apart from each other;
  • reaction reagent coated on the working electrode 30 and the reference electrode 40 A reaction reagent coated on the working electrode 30 and the reference electrode 40,
  • Signal transmission electrode 50 formed on one surface of the base substrate 10 to be electrically connected to each of the working electrode 30 and the reference electrode 40
  • biosensor characterized in that configured to include.
  • the signal transmission electrode 50 is composed of an operation signal transmission electrode 51 formed under the operation electrode 30 and a reference signal transmission electrode 52 formed under the reference electrode 40.
  • the signal transmission electrode 51 and the reference signal transmission electrode 52 may be spaced apart from each other.
  • the base substrate 10 may be formed of an insulating substrate.
  • the present invention is the process of forming two through holes 16, 17 in the base substrate 10,
  • Also provided is a method of manufacturing a biosensor which comprises applying a reaction reagent to the working electrode 30 and the reference electrode 40.
  • the first plating process may be a copper plating process
  • the second plating process may be performed by forming gold plating only on the working electrode 30, the reference electrode 40, and the signal transmission electrode 50. No gold plating is formed in the circumference.
  • the method may further include preparing a large insulating substrate, such as a PCB, as the base substrate 10.
  • the structure is simplified, the productivity is improved, and the manufacturing cost is reduced.
  • the present invention proposes a method of forming a sample introduction path and an electrode part in one layer instead of the conventional multi-layer stacked type, thereby improving the operability of the biosensor through the simple structure, improving the productivity of the biosensor, and generating a failure rate. There is an effect of reducing the.
  • FIG. 1 is a perspective view and an internal electrode structure diagram showing a biosensor according to the present invention.
  • Figure 2 is a flow chart showing a manufacturing method of a biosensor according to the present invention.
  • 3A and 3B are schematic diagrams sequentially showing before and after the insulating substrate is drilled.
  • Figure 4 is a schematic diagram of the electroless copper plating is formed on the drilled insulating substrate of FIG.
  • FIG. 5 is a schematic view in which patterning is performed on the copper-plated insulating substrate of FIG. 4.
  • FIG. 5 is a schematic view in which patterning is performed on the copper-plated insulating substrate of FIG. 4.
  • FIG. 6 is a schematic view illustrating a connection hole connecting the through holes in the state in which the patterning of FIG. 5 is performed.
  • FIG. 7 is a schematic view showing that secondary plating is performed in the state of FIG. 6.
  • FIG. 8 is a schematic diagram illustrating an internal electrode part of FIG. 7.
  • FIG. 9 is a schematic diagram showing that the biosensor according to the present invention is introduced into the outer housing 100.
  • FIG. 1 is a perspective view and an internal electrode structural diagram showing a biosensor according to the present invention.
  • the biosensor according to the present invention includes a base substrate 10 formed of an insulating substrate such as a printed circuit board (PCB) and a sample introduction path (Capillary) formed to penetrate the base substrate 10 ( 20 and a working electrode 30 and a reference electrode 40 which are formed on the inner wall of the sample introduction path 20 and are spaced apart from each other.
  • PCB printed circuit board
  • Capillary sample introduction path
  • a reaction reagent such as an enzyme immobilized in a method such as drying after coating on the working electrode 30 and the reference electrode 40, and the working electrode 30 and the reference electrode ( 40) is configured to include a signal transmission electrode 50 formed on one surface of the base substrate 10 to be electrically connected to each.
  • the signal transmitting electrode 50 transmits a reaction signal to a measuring instrument (not shown).
  • the reaction reagent applied on the working electrode 30 and the reference electrode 40 reacts with the introduced blood to generate a reaction signal.
  • the reaction signal is transmitted to the measuring device through the signal transmission electrode 50 connected to the working electrode 30 and the reference electrode 40, the measuring device may calculate a measurement result according to the level of the reaction signal.
  • FIG. 2 is a flowchart showing a method of manufacturing a biosensor according to the present invention.
  • a second step S200 which is a preparation process of the base substrate 10, which proceeds through a first step S100, which is a starting process, and two steps performed after the second step S200, are performed.
  • the third step S300 which is a through hole forming process
  • the fourth step S400 which is a first plating process performed after the third step S300, and the patterning that is performed after the fourth step S400.
  • the second step (S500) and the second through the sixth step (S600) and the sixth step (S600) after the sixth step (S600) and the sixth step (S600) A seventh step (S700), and a ninth step (S900), which is an end process performed after the eighth step (S800) and the eighth step (S800), which are the reaction reagent application processes performed after the seventh step, and the seventh step (S800). It is configured to include).
  • a second step (S200), which is a process of preparing the base substrate 10, is a process of preparing an insulating substrate or a PC substrate as the base substrate 10 as shown in FIG. 3A.
  • the upper surface 12 and the lower surface 14 of the base substrate 10 may be formed with a copper layer.
  • step S300 of forming two through holes through holes in the vertical direction are formed such that two holes spaced apart from each of the upper surface 12 and the lower surface 14 of the base substrate 10 are formed as shown in FIG. 3B.
  • (16, 17) is a process of forming, a method such as drilling is used.
  • the base substrate 10 having the two through holes 16 and 17 is formed by electroless plating. It is the process of copper plating which is primary plating on the copper surface.
  • the copper plating is a process for effectively performing gold plating, which is a secondary plating to be performed later, and when gold plating is performed without copper plating on the base substrate 10, the gold is insulated or copper surface of the base substrate 10, Since the plastic part in which the through hole is formed is not plated, gold plating is not formed.
  • FIG. 4 illustrates the hatching in both directions to show that the copper plating film is formed on the upper surface 12 and the lower surface 14 and the through holes 16 and 17 of the base substrate 10, before the copper plating film is formed.
  • the hatching on the upper surface 12 and the lower surface 14 of the base substrate 10 is illustrated in one direction.
  • the fifth step S500 which is a patterning process, is a process of performing patterning through exposure and etching processes on the first plated substrate through the fourth step S400 as shown in FIG. 5.
  • the upper surface 12 removes the metal parts of all parts except the working electrode parts, that is, the working electrode 30 and the reference electrode 40, to be formed in the through holes 16 and 17, The metal material of the remaining portions except for the working electrode part to be formed in the through holes 16 and 17 and the signal transmission electrode 50 connected to the working electrode part is removed.
  • the metal material is removed between the portion of the signal transmission electrode 50 connected to the lower portion of the working electrode 30 and the portion of the signal transmission electrode 50 connected to the lower portion of the reference electrode 40.
  • the sixth step (S600) is the connection through hole forming process in the direction parallel to the through-holes (16, 17) of the base substrate 10, the patterning is completed through the fifth step (S500) as shown in FIG. Forming the through-holes 18, it is a process of connecting the through-holes 16, 17 as one.
  • the working electrode 30 and the reference electrode 40 are positioned to be spaced apart from each other in the same through space, and have a through hole in which the working electrode 30 and the reference electrode 40 are formed.
  • the fields 16 and 17 and the connecting through hole 18 become the sample introduction path 20.
  • gold plating which is secondary plating
  • a method such as electroless plating
  • gold plating is formed only on a portion where copper plating is formed.
  • Gold plating is formed only on the electrode 40 and the signal transmission electrode 50, and gold plating is not formed around the connection through hole.
  • the working electrode 30 and the reference electrode 40 are spaced apart from each other as shown in FIG. 8, and the working electrode 30 and the reference electrode 40 are connected to the signal transmission electrode 50, respectively.
  • the signal transmission electrode 50 formed under the working electrode 30 and connected to the working electrode 30 is called an operation signal transmission electrode 51, and is formed under the reference electrode 40 to form the reference electrode 40.
  • the signal transfer electrode 50 connected to the reference signal is called a reference signal transfer electrode 52.
  • the operation signal transmission electrode 51 and the reference signal transmission electrode 52 are formed to be spaced apart from each other.
  • the eighth step (S800), which is the reaction reagent application process, is a process of applying and drying the reaction reagents to the working electrode 30 and the reference electrode 40 formed at both sides of the through holes 16 and 17.
  • the biosensor is completed.
  • the processes of the first step (S100) to the ninth step (S900) are performed in parallel on a large insulating substrate, such as a PC, and then the cutting process is performed.
  • FIG. 9 is a schematic diagram showing that the biosensor according to the present invention is introduced into the outer housing 100.
  • an outer housing 100 having a space in which the biosensor device can be inserted may be separately provided to improve appearance or usability of the product.
  • the outer housing 100 is a synthetic resin material such as plastic, it is preferable to easily change the shape or size by injection molding.
  • the present invention proposes a method of forming a sample introduction path and an electrode part in one layer instead of the conventional multi-layer stacked type, thereby improving the operability of the biosensor through the simple structure, improving the productivity of the biosensor, and generating a failure rate. There is an effect of reducing the.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Molecular Biology (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Pathology (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Electrochemistry (AREA)
  • Biomedical Technology (AREA)
  • Biophysics (AREA)
  • Hematology (AREA)
  • Urology & Nephrology (AREA)
  • Food Science & Technology (AREA)
  • Medicinal Chemistry (AREA)
  • Apparatus Associated With Microorganisms And Enzymes (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

La présente invention concerne un biocapteur comprenant : un substrat de base (10) ; un trajet d'introduction d'échantillon (20) formé pour passer à travers le substrat de base (10) ; une électrode de fonctionnement (30) et une électrode de référence (40) formées sur la paroi intérieure du trajet d'introduction d'échantillon (20), espacées l'une de l'autre ; un réactif appliqué en revêtement sur l'électrode de fonctionnement (30) et l'électrode de référence (40) ; une électrode de transfert de signal (50) formée sur une surface du substrat de base (10) pour être électriquement reliée à l'électrode de fonctionnement (30) et l'électrode de référence (40). Selon la présente invention, lorsqu'un biocapteur est fabriqué, uniquement une couche est utilisée, simplifiant ainsi la structure de celui-ci, améliorant la productivité et réduisant les coûts de fabrication.
PCT/KR2012/008785 2011-10-25 2012-10-24 Biocapteur et procédé de fabrication de celui-ci WO2013062322A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
KR1020110109078A KR101298772B1 (ko) 2011-10-25 2011-10-25 바이오센서 및 그 제조 방법
KR10-2011-0109078 2011-10-25

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WO2013062322A1 true WO2013062322A1 (fr) 2013-05-02

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Publication number Priority date Publication date Assignee Title
KR20220116633A (ko) * 2021-02-15 2022-08-23 주식회사 더도니 바이오 센서용 스트립과 그 제작방법 및 이를 이용한 채혈 측정 장치

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH11352094A (ja) * 1998-06-11 1999-12-24 Matsushita Electric Ind Co Ltd 電気化学分析素子
KR100700713B1 (ko) * 2006-02-27 2007-03-28 한국표준과학연구원 신규한 폴리전해질 참조전극을 포함하는 소형화된 전기화학시스템 및 이것의 박층 전기분석으로의 응용
US20080063566A1 (en) * 2004-09-03 2008-03-13 Mitsubishi Chemical Corporation Sensor Unit and Reaction Field Cell Unit and Analyzer
US20090071824A1 (en) * 2004-10-14 2009-03-19 Hibbs Andrew D Integrated Sensing Array for Producing a BioFingerprint of an Analyte
JP2010119864A (ja) * 2010-02-03 2010-06-03 National Institute Of Advanced Industrial Science & Technology 穿刺器具一体型バイオセンサーの製造法

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH11352094A (ja) * 1998-06-11 1999-12-24 Matsushita Electric Ind Co Ltd 電気化学分析素子
US20080063566A1 (en) * 2004-09-03 2008-03-13 Mitsubishi Chemical Corporation Sensor Unit and Reaction Field Cell Unit and Analyzer
US20090071824A1 (en) * 2004-10-14 2009-03-19 Hibbs Andrew D Integrated Sensing Array for Producing a BioFingerprint of an Analyte
KR100700713B1 (ko) * 2006-02-27 2007-03-28 한국표준과학연구원 신규한 폴리전해질 참조전극을 포함하는 소형화된 전기화학시스템 및 이것의 박층 전기분석으로의 응용
JP2010119864A (ja) * 2010-02-03 2010-06-03 National Institute Of Advanced Industrial Science & Technology 穿刺器具一体型バイオセンサーの製造法

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KR20130044817A (ko) 2013-05-03

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