WO2016043402A1 - Biocapteur à microélectrodes interdigitées - Google Patents

Biocapteur à microélectrodes interdigitées Download PDF

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Publication number
WO2016043402A1
WO2016043402A1 PCT/KR2015/004697 KR2015004697W WO2016043402A1 WO 2016043402 A1 WO2016043402 A1 WO 2016043402A1 KR 2015004697 W KR2015004697 W KR 2015004697W WO 2016043402 A1 WO2016043402 A1 WO 2016043402A1
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WO
WIPO (PCT)
Prior art keywords
cross
electrode
signal
impedance
electrodes
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PCT/KR2015/004697
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English (en)
Korean (ko)
Inventor
황교선
조원우
김태송
박종배
유용경
고경옥
김혜진
이준옥
Original Assignee
한국과학기술연구원
주식회사 캔티스
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Publication of WO2016043402A1 publication Critical patent/WO2016043402A1/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
    • G01N27/02—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance
    • 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
    • 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
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing

Definitions

  • the present invention relates to a cross-electrode biosensor, and more particularly, to a cross-electrode biosensor which detects the presence and the concentration of a biomaterial such as a protein through an impedance measurement between electrodes.
  • biosensors have been developed to detect the presence and concentration of various biological materials such as genes and proteins by electrical methods.
  • One example is the use of interdigitated microelectrodes. It is evaluated that even if the concentration of the biomaterial is low, the measurement is properly performed because the region in which the receptor that specifically binds the biomaterial is fixed is substantially wide in a zigzag form.
  • the problem to be solved by the present invention is a cross-electrode capable of accurately detecting the presence and concentration of a small amount of biological material through the measurement of the impedance between the electrodes, even if the conductive particles are not used so that the current flows between the electrodes To provide a biosensor.
  • Comb-shaped two electrodes are installed on the substrate in the form of interlocking staggered spaced apart by a predetermined interval, the cross-electrode portion is installed between the two electrodes to capture the target material;
  • a driving signal applying unit applying a driving frequency between the two electrodes
  • An impedance measuring unit measuring an impedance between the two electrodes By being made, including
  • the target material is analyzed by measuring a change in impedance which appears depending on whether the target material is captured.
  • the driving frequency has a frequency range of 10 Hz to 100 Hz.
  • the gap between the two electrodes is preferably 3 ⁇ 7 ⁇ m.
  • a protective cap is installed on the cross-electrode portion so that a channel is formed on the cross-electrode portion, and an adsorption prevention layer is coated on a surface inside the channel where the receptor is not installed.
  • the adsorption prevention layer is preferably made of BSA (Bovine Serum Albumin).
  • Two electrodes having a comb shape are installed on the substrate in an interlocking manner while being spaced apart from each other by a predetermined interval, and the reference cross-electrode portion does not capture the target material;
  • a signal cross-electrode unit disposed on the substrate in a shape in which two comb-shaped electrodes are alternately engaged with each other at a predetermined interval, and the target material is captured by a receptor provided between the two electrodes;
  • a driving signal applying unit installed to apply a driving frequency to the reference crossing electrode unit and the signal crossing electrode unit, respectively;
  • a reference impedance measuring unit which measures an impedance between two electrodes of the reference cross-electrode unit as a reference impedance
  • a signal impedance measuring unit which measures an impedance between two electrodes in the signal crossing electrode unit as a signal impedance
  • a differential amplifier installed to differentially amplify the reference impedance and the signal impedance from the reference impedance measuring unit and the signal impedance measuring unit;
  • the target material may be analyzed by changing the signal impedance relative to the reference impedance.
  • the driving frequency applied by the driving signal applying unit preferably has a frequency range of 10 Hz to 100 Hz.
  • the gap between the two electrodes forming the reference cross-electrode portion is 3 to 7 ⁇ m, and the gap between the two electrodes forming the signal cross-electrode portion is 3 to 7 ⁇ m.
  • Protective caps are respectively provided on the reference cross-electrode portion and the signal cross-electrode portion so that channels are formed on the reference cross-electrode portion and the signal cross-electrode portion, respectively, and an adsorption preventing layer on the surface inside the channel where the receptor is not installed. It is preferred to be coated.
  • the adsorption prevention layer is preferably made of BSA (Bovine Serum Albumin).
  • the capture of the target material occurs only at the signal cross-electrode part or the signal cross-over part.
  • the receptor may be provided only in the electrode portion, and the target material may be provided to both the reference cross electrode portion and the signal cross electrode portion so that the capture of the target material occurs only at the signal cross electrode portion.
  • the presence or absence of a biological substance and its concentration can be accurately detected through impedance measurement without using conductive particles as in the prior art.
  • the precise detection can be made while using a low frequency of 10Hz ⁇ 100Hz so as not to denature or damage the target biomaterial.
  • the use of differential amplification has the advantage of enabling precise detection of small amounts of biomaterials.
  • FIG. 1 is a view for explaining the principle of the cross-electrode biosensor according to the present invention.
  • FIG. 2 is a graph for explaining the change in the impedance of the cross-electrode portion 20 by the reaction of the receptor 31 and the target biomaterial 32;
  • FIG. 3 is a view for explaining a cross-electrode biosensor according to the present invention to which a differential amplifier is applied;
  • FIG. 4 is a view for explaining the manufacturing process of the cross-electrode portion 20 of FIG. 1 and the specific binding of the target biomaterial 32;
  • 6 and 7 are diagrams for explaining the detection capability of the cross-electrode biosensor of FIG. 3, and look at the contribution to the specific binding of the target biomaterial 32;
  • FIG. 8 is a graph illustrating a beta amyloid detection test result at a concentration of 100 pg / mL for explaining the detection capability of the cross-electrode biosensor of FIG. 3, and looks at the contribution of the differential amplifier 300.
  • driving signal applying unit 10 substrate
  • reference cross-electrode unit 225 reference impedance measuring unit
  • FIG. 1 is a view for explaining the principle of the cross-electrode biosensor according to the present invention.
  • the cross-electrode part 20 is installed on the substrate 10.
  • the interdigitated microelectrode part (IME part) 20 is installed in a form in which two electrodes 21 and 22 having a comb shape are interlocked with each other at predetermined intervals.
  • the impedance between the two electrodes 21, 22 is arranged as follows.
  • Z is impedance
  • R is resistance
  • X reactance
  • C is capacitance
  • w angular frequency.
  • the reactance X is divided into the inductor component X L and the capacitor component X C. Since the two electrodes 21 and 22 are not electrically connected directly, the inductor component X L is ignored and only the capacitor component X C is present. It can be said that.
  • a receptor (mainly an antibody, aptamer, etc.) 31 that specifically reacts with the target biomaterial 32 is fixed in the space between the two electrodes 21, 22 and the target biomaterial 32 is the receptor 31.
  • the impedance change between the two electrodes (21, 22) is confirmed when reacting to the) it is possible to quantitatively analyze the target biomaterial (32).
  • FIG. 2 is a graph for explaining the change in the impedance of the cross-electrode portion 20 by the reaction of the receptor 31 and the target biomaterial 32.
  • the receptor 31 and the target biomaterial 32 are specifically bound, the water (or buffer solution, serum, blood, etc.) existing between the two electrodes 21 and 22 is pushed out and the target biomaterial 32 is positioned.
  • the resistance increases.
  • reactance is the dielectric constant of water (or buffer solutions, serum, blood, etc.) decreases the value of the capacitance (C) by the nature of the small target biological material (32) than the value X C is greater according -X value C Will decrease.
  • the frequency of the driving frequency is high, the current mainly flows through the space above the specifically coupled target biomaterial 32, that is, root A, so that detection of the target biomaterial 32 is not properly performed.
  • the frequency is high, the target biomaterial 32 may be damaged by high frequency and may not be detected properly.
  • the present invention is characterized by using a low driving frequency of 10 Hz to 100 Hz so that the current can flow through the root B. Since the frequency is low, the target biomaterial 32 is also prevented from being damaged. Of course, in this case, since the frequency is low, there is a disadvantage in that it is difficult to detect a change in the fine impedance at the root B, but this disadvantage can be overcome by using a differential amplifier as described below.
  • the gap between the two electrodes 21 and 22 is preferably 3 to 7 ⁇ m. If the gap is too small and less than 3 ⁇ m, the deviation of the detection signal is too large to perform a reliable test. If the gap is too large and larger than 7 ⁇ m, the sensitivity is insufficient to detect a small amount of the biomaterial 32. Because. Considering the deviation and sensitivity, the case of 5 ⁇ m is most preferable.
  • FIG. 3 is a view illustrating a cross-electrode biosensor according to the present invention to which a differential amplifier is applied.
  • the signal cross-electrode portion 120 and the reference cross-electrode portion 220 are installed on the substrate 1, and each of the signal cross-electrode portion 120 and the reference cross-electrode portion 220 is illustrated in FIG. 1.
  • Two electrodes 21 and 22 having a comb-like shape, such as the cross-electrode portion 20 of, are arranged in a staggered manner while being spaced apart by a predetermined interval.
  • the signal cross-electrode unit 120 captures the target biomaterial 32 by the receptor 31 disposed between the two electrodes 21 and 22, while the capture cross-electrode unit 220 does not capture the target biomaterial 32. .
  • the receiver 31 may be provided only in the unit 120, and the target biomaterial 32 may be provided to both the signal cross-electrode unit 120 and the reference cross-electrode unit 220.
  • the driving frequency is applied to the signal cross electrode unit 120 and the reference cross electrode unit 220 through the driving signal applying unit 1. Then, the impedance at the signal cross-electrode unit 120 is measured as the signal impedance in the signal impedance measuring unit 125, and the impedance at the reference cross-electrode unit 220 is measured as the reference impedance in the reference impedance measuring unit 225. .
  • the signal impedance will be the impedance between the two electrodes 21 and 22 for the case where the target biomaterial 32 is captured between the two electrodes 21 and 22, and the reference impedance will be between the two electrodes 21 and 22. Will be the impedance between the two electrodes 21, 22 for the case where the target biomaterial 32 is not captured.
  • the differential amplifier 300 receives the signal impedance and the reference impedance, respectively, and differentially amplifies the signal impedance and outputs a result signal.
  • FIG. 4 is a view for explaining the manufacturing process and the specific binding of the target biomaterial 32 of the cross-electrode portion 20 of FIG.
  • a 500 nm thick silicon oxide film SiO 2 , 11 is formed on the silicon substrate 10 by thermal oxidation, and then sputtering on the silicon oxide film 11 is performed.
  • a metal layer 20a is formed by sequentially stacking Ti 30 nm and Pt 150 nm by sputtering. The Ti layer is used as an adhesion layer for increasing the bonding force between the Pt layer and the silicon oxide film 11.
  • a photoresist film is coated on the metal layer 20a and the photoresist film is patterned by a photolithography process to form a photoresist pattern 40.
  • the metal layer 20 is etched using inductively coupled plasma reactive ion etcher (ICP-RIE) until the silicon oxide film 11 is exposed using the photoresist pattern 40 as an etch mask.
  • ICP-RIE inductively coupled plasma reactive ion etcher
  • Specific binding of the target biomaterial 32 is performed as follows.
  • a Calixcrown Self-Assembled Monolayer is formed as a connecting molecule layer 33 for selectively fixing the beta amyloid antibody on the surface of the silicon oxide film 11 between the two electrodes 21 and 22.
  • the beta amyloid antibody is fixed to the linking molecule layer 33 as the receptor 31.
  • the beta amyloid which is the target biomaterial 32, is selectively bound to the receptor 31.
  • FIG. 5 is a diagram for describing the channel 55.
  • the protective cap 50 is installed on the two electrodes 21 and 22 so that the two electrodes 21 and 22 are placed in the channel 55.
  • the channel 55 by the protective cap 50 also serves to help the sample enter the specific binding region.
  • the protective cap 50 is preferably made of a polydimethylsiloxane (PDMS) material.
  • the target biomaterial 32 When a sample containing various components is introduced into the channel 55, only the target biomaterial 32 that specifically reacts with the receptor 31 is bound to the receptor 31.
  • the target biomaterial 32 will be beta amyloid.
  • the adsorption preventing layer 51 is preferably made of BSA (Bovine Serum Albumin).
  • FIG. 6 and 7 illustrate the detection capability of the cross-electrode biosensor of FIG. 3 and illustrate the contribution to specific binding of the target biomaterial 32.
  • the test unit 100 and the control unit 200 are divided into the test unit 100 and the control unit 200, respectively, as shown in FIG. 3.
  • the electrode portions 220 were formed in pairs.
  • the beta amyloid antibody is fixed to the signal cross-electrode unit 120 of the experiment unit 100, and the PSA (prostate-specific antigen) for selectivity control (negative control) to the signal cross-electrode unit 120 of the control unit 200.
  • Antibodies were fixed.
  • a PDMS chip having two microchannels was attached to each of the experiment unit 100 and the control unit 200.
  • 0.1X PBS buffer solution was injected into both channels, and the stabilization was performed by observing the signal until the impedance signal output from each electrode part remained stable and stable.
  • the beta amyloid was injected into the channel to observe the change in the impedance signal to confirm the antigen-antibody reaction of the beta amyloid.
  • FIG. 7 is a graph showing impedance changes in the test unit 100 and the control unit 200 when 10, 100, and 1000 pg / mL of beta amyloid was sequentially injected.
  • the impedance change amount of the experiment unit 100 increases as the beta amyloid concentration increases (green), but in the case of the control unit 200 in which the non-specific antibody is immobilized, the beta amyloid is injected. It can be seen that the signal change is very insignificant (blue). This is a result reflecting that the specific binding of the beta amyloid that is the target biomaterial 32 is made in the experiment unit 100, while the control unit 200 does not perform such specific binding.
  • FIG. 8 is a graph illustrating a beta amyloid detection test result at a concentration of 100 pg / mL for explaining the detection capability of the cross-electrode biosensor of FIG. 3, and looks at the contribution of the differential amplifier 300.
  • FIG. 8A illustrates the impedance output from the signal cross electrode unit 120 and the reference cross electrode unit 220 without being differentially amplified. As can be seen in FIG. 8A, it is very difficult to quantitatively detect the amount of the target biomaterial 32 because impedance changes of the signal cross-electrode portion 120 and the reference cross-electrode portion 220 are not properly distinguished.
  • FIG. 8B differentially amplifies the signal impedance (red) output from the signal cross electrode unit 120 with respect to the reference impedance (blue) output from the reference cross electrode unit 220 and outputs the result.
  • Figure 8b it can be seen that even if a small amount of 100pg / mL can be properly measured because the distinction between the signal impedance and the reference impedance.
  • the presence or absence of a biological substance and its concentration can be accurately detected through impedance measurement without using conductive particles as in the prior art.
  • the precise detection can be made while using a low frequency of 10Hz ⁇ 100Hz so that the target biomaterial 32 is not denatured or damaged.
  • the use of differential amplification has the advantage of enabling precise detection of small amounts of biomaterials.

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Abstract

L'impédance de signal est l'impédance entre deux électrodes (21, 22) lorsqu'un biomatériau cible (32) est capturé entre les deux électrodes (21, 22), et l'impédance de référence est l'impédance entre deux électrodes (21, 22) lorsqu'un biomatériau cible (32) n'est pas capturé entre les deux électrodes (21, 22). Un amplificateur différentiel (300) reçoit une entrée de chacune parmi l'impédance de signal et l'impédance de référence et délivre en sortie un signal résultant tout en amplifiant de manière différentielle l'impédance de signal. Si l'impédance de signal est amplifiée différemment sur la base de l'impédance de référence, la différence d'impédance entre celles-ci est définitivement présentée et, par conséquent, même une petite quantité de biomatériau cible (32) peut être détectée de manière quantitative et précise.
PCT/KR2015/004697 2014-09-19 2015-05-11 Biocapteur à microélectrodes interdigitées WO2016043402A1 (fr)

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3399305A4 (fr) * 2015-12-28 2019-08-28 Korea Institute of Science and Technology Bio-capteur à électrode inter-digitée utilisant une réaction entre un récepteur et un biomatériau cible

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KR101912890B1 (ko) * 2016-10-04 2018-10-29 한국과학기술연구원 표적 생체물질과 수용체의 반응을 개선한 교차 전극 바이오센서
KR102048987B1 (ko) 2017-02-22 2019-11-27 한국과학기술연구원 신경퇴행성 장애의 진단을 위한 정보 제공 방법
KR102102534B1 (ko) * 2018-07-11 2020-04-23 주식회사 엑스와이지플랫폼 유전 전기 영동을 이용한 마이크로 전극 바이오 센서, 및 이를 이용한 생체물질 검출 방법
DE102019108921A1 (de) * 2019-04-04 2020-10-08 Bayerische Motoren Werke Aktiengesellschaft Zweiteilige Referenzelektrode
KR102350449B1 (ko) * 2019-11-15 2022-01-11 광운대학교 산학협력단 정전용량을 기반한 바이오센서 및 그의 제조방법
KR102436003B1 (ko) * 2020-03-19 2022-08-25 성균관대학교산학협력단 전도도 및 주파수 변화 측정을 위한 바이오 센서 어레이 및 제조 방법
KR102488871B1 (ko) * 2020-05-04 2023-01-17 광운대학교 산학협력단 바이오 센서 및 이를 이용한 전립선암의 진단 방법
KR102512759B1 (ko) * 2020-06-02 2023-03-23 주식회사 셀앤바이오 재사용 가능한 바이러스 신속 검출용 dna 바이오 센서
KR102515752B1 (ko) * 2020-12-31 2023-03-30 주식회사 바이오소닉스 다중 주파수를 이용한 바이오 센서 장치의 항원 검출 방법
KR102449459B1 (ko) * 2021-01-12 2022-09-29 서울대학교산학협력단 나노필터를 이용한 단백질 분석 장치
KR102376338B1 (ko) * 2021-01-27 2022-03-17 광운대학교 산학협력단 이중 인터디지털 커패시터 센서 칩을 탑재한 코로나 바이러스 탐지 키트
KR102376333B1 (ko) * 2021-01-27 2022-03-17 광운대학교 산학협력단 코로나바이러스 검출을 위한 이중 인터디지털 커패시터 센서 칩

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6835552B2 (en) * 2000-12-14 2004-12-28 The Regents Of The University Of California Impedance measurements for detecting pathogens attached to antibodies
US20070151848A1 (en) * 2006-01-05 2007-07-05 Nano-Proprietary, Inc. Capacitance based biosensor
US20090117571A1 (en) * 2007-08-15 2009-05-07 State of Oregon by and through the State Board of Higher Education on behalf of Portland State Univ. Impedance spectroscopy of biomolecules using functionalized nanoparticles
KR20090062591A (ko) * 2007-12-13 2009-06-17 중앙대학교 산학협력단 유전영동 임피던스를 이용한 센싱장치 및 센싱방법
US20110025348A1 (en) * 2007-11-05 2011-02-03 Impedimed Limited Impedance determination

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR100777973B1 (ko) 2006-07-13 2007-11-29 한국표준과학연구원 다중선형전극 센서 유닛으로 이루어진 바이오센서

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6835552B2 (en) * 2000-12-14 2004-12-28 The Regents Of The University Of California Impedance measurements for detecting pathogens attached to antibodies
US20070151848A1 (en) * 2006-01-05 2007-07-05 Nano-Proprietary, Inc. Capacitance based biosensor
US20090117571A1 (en) * 2007-08-15 2009-05-07 State of Oregon by and through the State Board of Higher Education on behalf of Portland State Univ. Impedance spectroscopy of biomolecules using functionalized nanoparticles
US20110025348A1 (en) * 2007-11-05 2011-02-03 Impedimed Limited Impedance determination
KR20090062591A (ko) * 2007-12-13 2009-06-17 중앙대학교 산학협력단 유전영동 임피던스를 이용한 센싱장치 및 센싱방법

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3399305A4 (fr) * 2015-12-28 2019-08-28 Korea Institute of Science and Technology Bio-capteur à électrode inter-digitée utilisant une réaction entre un récepteur et un biomatériau cible

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