WO2016173542A1 - System and method for detection in ion fluid - Google Patents

System and method for detection in ion fluid Download PDF

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Publication number
WO2016173542A1
WO2016173542A1 PCT/CN2016/080679 CN2016080679W WO2016173542A1 WO 2016173542 A1 WO2016173542 A1 WO 2016173542A1 CN 2016080679 W CN2016080679 W CN 2016080679W WO 2016173542 A1 WO2016173542 A1 WO 2016173542A1
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Prior art keywords
target
gate
ion fluid
fet
electrode
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PCT/CN2016/080679
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French (fr)
Inventor
Le-Chang HSIUNG
Chun-Yen TAI
Yu-Lin Chen
Fang-yu LIN
Chuan Whatt Eric OU
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Winnoz Technology, Inc
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Priority to CN201680024582.4A priority Critical patent/CN107850564B/en
Priority to JP2018507764A priority patent/JP2018515792A/en
Priority to EP16785970.1A priority patent/EP3274700A4/en
Publication of WO2016173542A1 publication Critical patent/WO2016173542A1/en

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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
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    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/502753—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by bulk separation arrangements on lab-on-a-chip devices, e.g. for filtration or centrifugation
    • 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
    • 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
    • G01N27/414—Ion-sensitive or chemical field-effect transistors, i.e. ISFETS or CHEMFETS
    • G01N27/4145—Ion-sensitive or chemical field-effect transistors, i.e. ISFETS or CHEMFETS specially adapted for biomolecules, e.g. gate electrode with immobilised receptors
    • 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
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • 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
    • G01N33/68—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving proteins, peptides or amino acids
    • G01N33/6803—General methods of protein analysis not limited to specific proteins or families of proteins
    • 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
    • G01N33/72—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood pigments, e.g. haemoglobin, bilirubin or other porphyrins; involving occult blood
    • G01N33/721—Haemoglobin
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
    • B01L2200/10—Integrating sample preparation and analysis in single entity, e.g. lab-on-a-chip concept
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/06—Auxiliary integrated devices, integrated components
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/06—Auxiliary integrated devices, integrated components
    • B01L2300/0627—Sensor or part of a sensor is integrated
    • B01L2300/0636—Integrated biosensor, microarrays
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/06—Auxiliary integrated devices, integrated components
    • B01L2300/0681—Filter
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/06—Auxiliary integrated devices, integrated components
    • B01L2300/069—Absorbents; Gels to retain a fluid
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0861—Configuration of multiple channels and/or chambers in a single devices
    • B01L2300/087—Multiple sequential chambers
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0861—Configuration of multiple channels and/or chambers in a single devices
    • B01L2300/0883—Serpentine channels
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/04—Moving fluids with specific forces or mechanical means
    • B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
    • B01L2400/0406—Moving fluids with specific forces or mechanical means specific forces capillary forces
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/04—Moving fluids with specific forces or mechanical means
    • B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
    • B01L2400/043—Moving fluids with specific forces or mechanical means specific forces magnetic forces
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/08—Regulating or influencing the flow resistance
    • B01L2400/084—Passive control of flow resistance
    • B01L2400/088—Passive control of flow resistance by specific surface properties
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/68—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving nucleic acids
    • C12Q1/6806—Preparing nucleic acids for analysis, e.g. for polymerase chain reaction [PCR] assay

Definitions

  • the present disclosure relates to a field effect transistor (FET) -based biosensor, particularly a FET-based biosensor using electrochemical method to improve detection limit and sensitivity in a high-ion fluid.
  • FET field effect transistor
  • the gate 150 is modified with antibodies or some recognition elements 152 for the detection of specific biomarkers 154.
  • the recognition elements 152 the charges of the biomarkers 154 will accumulate on the gate surface to cause a potential on the gate 150, such that the biomarker concentration can be determined by the current flowing through the substrate 120 between the source 140 and the drain 130 (i.e., I DS ) in the presence of a voltage source 110.
  • the potential contributed by the charges of the biomarker will be neutralized by the ions in the sample.
  • a specific length i.e. Debye length ( ⁇ )
  • the electric potential screened out may reduce the current flowing through the substrate 120 between the source 140 and the drain 130, such that the system cannot provide desired detection limit and sensitivity to detect the concentration of biomarker.
  • FIG. 2 further shows the comparison of detection results of conventional extended-gate field effect transistor (EGFET) in 100 mM phosphate buffer solution (PBS) (ionic strength is ⁇ 400 mM; Table 1) and in 0.1 mM PBS (ionic strength is ⁇ 0.4 mM; Table 1) .
  • EGF extended-gate field effect transistor
  • Debye length can be further decreased to ⁇ 0.48 nm in 100 mM PBS, which is smaller than the diameter of hemoglobin ( ⁇ 5 nm, Biol Proced Online 2009, 11: 32-51) . Therefore, the charges carried by hemoglobin are insufficient to generate potential on the gate of EGFET to induce corresponding I DS for detection.
  • the present disclosure provides an electrochemical extended gate FET-based system, also referring as an electrochemical extended-gate transistor (EET) system, which is capable of avoiding Debye length issue and can be used directly to detect a target (for example, a biomarker) in high-ion fluid. Furthermore, an electrochemical method is applied in the EET system of the present disclosure, such that the concentration of a target can be determined by detecting the electrochemical signals generated by the redox in an ion fluid.
  • EET electrochemical extended-gate transistor
  • the EET system for detecting a target comprises: a field effect transistor (FET) , having a gate, a source, and a drain; a potentiostat, having a working electrode, a counter electrode, and a reference electrode; wherein the working electrode is coupled with a detection region, and the counter electrode is coupled with the gate; wherein the detection region, the gate, and the reference electrode are arranged in an ion fluid; wherein the potentiostat is configured to generate redox in the ion fluid by an electrochemical method to detect the target.
  • FET field effect transistor
  • the FET comprises a readout unit coupled thereto for quantifying signals.
  • the FET may be a n-MOS, a p-MOS FET, or any component with similar function.
  • the substances in forming the working electrode, counter electrode, and reference electrode comprise at least one substance selected from the group consisting of gold, silver, platinum, palladium, carbon, indium tin oxide (ITO) glass, any conductive inks, and any combination thereof.
  • ITO indium tin oxide
  • the ion fluid may be in gas phase or liquid phase.
  • the ion fluid may be an electrolyte, such as PBS, blood, serum, urine, saliva, sweat, or any solution having an ionic strength similar to physiological environment.
  • an electrolyte such as PBS, blood, serum, urine, saliva, sweat, or any solution having an ionic strength similar to physiological environment.
  • the target comprises at least one selected from a group consisting of small molecule, protein, enzyme, antigen, antibody, nucleic acid, DNA, RNA, miRNA, aptamer, glycolipid, ligand, exosome or any biomarker for sensing applications.
  • the detection region is modified with recognition elements having affinity or specificity to the target.
  • the recognition elements can be any molecule having affinity or specificity to the target.
  • the target may involve electrochemical (EC) activity.
  • EC electrochemical
  • the present disclosure further provides a method for detecting a target, comprising: providing a FET having a gate, a source, and a drain; providing a potentiostat including a working electrode, a counter electrode, and a reference electrode, wherein the working electrode is coupled with a detection region, wherein the counter electrode is coupled with the gate, wherein the detection region, the gate, and the reference electrode are arranged in an ion fluid; and performing an electrochemical method driven by the potentiostat to generate redox in the ion fluid to detect the target.
  • the electrochemical method includes: voltammetry method, amperometry method, conductimetric method, impedance method, or any conventional electrochemical method.
  • FIGs. 1 (A) and 1 (B) illustrate a conventional FET-based biosensor and the relationship between ionic strength and Debye length
  • FIG. 2 shows results of using conventional EGFET system for detecting hemoglobin in 100 mM PBS and 0.1 mM PBS;
  • FIG. 3 shows a schematic view of the EET system according to an embodiment of the present disclosure, wherein the arrows show an exemplary direction for illustrating the direction of redox reaction;
  • FIG. 4 shows a schematic view of the EET system according to an embodiment of the present disclosure, wherein recognition elements and mediators are introduced to the EET system;
  • FIG. 5 (A) shows a plot of time against the normalized current ratio detected by a conventional EGFET system according to an embodiment of the present disclosure for detecting hemoglobin;
  • FIG. 5 (B) shows a plot of concentration of hemoglobin against the normalized current ratio detected by a conventional EGFET system according to an embodiment of the present disclosure for detecting hemoglobin;
  • FIG. 5 (C) shows a plot of time against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting hemoglobin
  • FIG. 5 (D) shows a plot of concentration of hemoglobin against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting hemoglobin;
  • FIG. 6 (A) shows a plot of time against the normalized current ratio detected by a conventional EC system according to an embodiment of the present disclosure for detecting H 2 O 2 ;
  • FIG. 6 (B) shows a plot of concentration of H 2 O 2 against the normalized current ratio detected by a conventional EC system according to an embodiment of the present disclosure for detecting H 2 O 2 ;
  • FIG. 6 (C) shows a plot of time against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting H 2 O 2 ;
  • FIG. 6 (D) shows a plot of concentration of H 2 O 2 against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting H 2 O 2 ;
  • FIG. 7 shows a plot for comparing the industrial value of the EET system of the present disclosure with the conventional EGFET and EC systems.
  • FIG. 3 shows a schematic view of the EET system according to an embodiment of the present disclosure.
  • the system 300 includes: a field effect transistor (FET) 310, having a gate 312, a source 316, and a drain 314; a potentiostat 330, having a working electrode 332, a counter electrode 334, and a reference electrode 336; wherein the working electrode 332 is coupled with a detection region 320, and the counter electrode 334 is coupled with the gate 312; wherein the detection region 320, the gate 312, and the reference electrode 336 are arranged in an ion fluid 302; wherein the potentiostat 330 is configured to generate redox in the ion fluid 302 to redox by an electrochemical method to detect the target 324.
  • FET field effect transistor
  • the EET system 300 may include an electrochemical (EC) method, and the voltage difference between the working electrode 332 and counter electrode 334 will drive the target 324 in the ion fluid 302 to redox.
  • the gate voltage of the FET 310 will thereby be controlled by the voltage of counter electrode 334 to induce a drain-to-source current (I DS ) , which can be detected by the readout unit 340. Therefore, the concentration of the target 324 is presented as a function of the I DS detected by readout unit 340.
  • some targets 324 may have specific electrochemical characteristic, such that when the potentiostat 330 performs an appropriate electrochemical method, the target 324 can generate corresponding faradic current and present a pair of redox peaks at a specific potential.
  • the detection region 320 of the EET system 300 may be modified with recognition elements (not shown in FIG. 3) having specificity to the target 324.
  • the characteristic signal of the target 324 e.g. peak current at redox potential
  • the signal may be further amplified by the FET 310, and the concentration of the target 324 can thereby be calculated and obtained by the readout unit 340 coupled with the FET 310.
  • FIG. 4 shows the EET system 400 according to another embodiment of the present disclosure.
  • the detection region 420 of the EET system 400 is modified with recognition elements 422 having specificity to the targets 424, and the targets 424 do not have electrochemical activity.
  • additional mediators 404 are added into the ion fluid 402 to facilitate the generation of the redox current.
  • the mediator 404 can be any kind of mediator commonly used in this technical field, such as but not limited to, potassium ferricyanide, ferrocene, and tetrathiafulvalene (TTF) .
  • the added mediators 404 are driven to generate redox current.
  • the resistance of the detection region 420 will change, and the redox current contributed by the mediator 404 will change correspondingly. Therefore, the concentration of the target 424 can be calculated by the readout unit 440 in this manner.
  • a method for detecting a target 324 with the EET system 300 comprises: providing a field effect transistor (FET) 310 having a gate 312, a source 316, and a drain 314; providing a potentiostat 330 having a working electrode 332, a counter electrode 334, and a reference electrode 336; wherein the working electrode 332 is coupled with a detection region 320, wherein the counter electrode 334 is coupled with the gate 312, wherein the detection region 320, the gate 312, and the reference electrode 336 are arranged in an ion fluid 302; and performing an electrochemical method driven by the potentiostat 330 to generate redox in the ion fluid 302 to detect the target 324.
  • FET field effect transistor
  • Embodiment 1 is a diagrammatic representation of Embodiment 1:
  • the EET system provided superior sensing performance (such as the limitation of the detection and the magnitude of the responses) even in physiological ionic strength environment.
  • the target was hemoglobin.
  • the potentiostat was CHI6192E (CHI, Austin, TX, USA) , but other conventional potentiostat or equivalents could be used, and the working electrode, the counter electrode, and the reference electrode were respectively electrically coupled to a carbon electrode, a carbon electrode, and an Ag/AgCl electrode. Any appropriate pretreatment can be applied to the electrodes in the embodiment, such as cleaning by oxygen plasma, ethanol or deionized water.
  • the ion fluid was 100 mM PBS, prepared in 100 mM Na 2 HPO 4 and 100 mM NaH 2 PO 4 , and the pH value was 7.4.
  • the EET system was used to measure the concentrations of hemoglobin solutions from 0.01 ⁇ g/ml to 100 ⁇ g/ml. During this measurement, an amperometry method was applied, and the voltage difference between the working electrode and the reference electrode was set at -0.4 V to drive corresponding redox reaction.
  • EGFET electrosenor
  • the configuration of the EGFET system and the detection condition were the same as those of the EET system mentioned above.
  • a source-measurement unit was also utilized in the EGFET system but it merely was used for applying a potential with respect to the reference electrode and measuring signal.
  • FIG. 5 The result of the measurement detected by a conventional EGFET system and the EET system of the present disclosure is shown in FIG. 5.
  • the x-axis refers to the measurement time
  • the x-axis refers to the concentration of hemoglobin.
  • the y-axis refers to current ratio, ⁇ I DS (change of the drain-to-source current) /I 0 (current detected in PBS without hemoglobin) .
  • the current ratio ( ⁇ I DS /I 0 ) shown in y-axis is used for illustrating the normalized result of the detection, such that a person having ordinary skill in the art should easily understand the advantage and efficacy brought out by the present disclosure.
  • FIGs. 5 (A) and 5 (B) clearly show when the concentration of hemoglobin was equal or lower than 1 ⁇ g/ml, the signals measured by EGFET system was unobservable. Also, the detected signal (reference to current ratio) in 100 ⁇ g/ml of hemoglobin by the conventional EGFET system was merely 2%-3% higher than that of the blank (without hemoglobin) .
  • FIGs. 5 (C) and 5 (D) it shows a concentration-dependent correlation between the current ratio and concentration of hemoglobin.
  • the detection limit of the EET system was at least 30 times greater than that of the EGFET system and the detection range extended from 100 ⁇ g/ml to ⁇ 0.3 ⁇ g/ml of hemoglobin.
  • the detected signal (reference to current ratio) increased ⁇ 3% with outstanding linearity, when the concentration of hemoglobin increased 10 times.
  • Embodiment 2 is a diagrammatic representation of Embodiment 1:
  • the EET system provided superior sensing performance comparing to a conventional EC system.
  • the sensing target was H 2 O 2 .
  • a commercial strip (DEP-ER-P, BioDevice, Japan) was used in the embodiment, wherein the working, counter, and reference electrodes of the strip were of gold, carbon, and Ag/AgCl, respectively.
  • the potentiostat was CHI6192E (CHI, Austin, TX, USA) .
  • the ion fluid in this embodiment was PBS (100 mM Na 2 HPO 4 and 100 mM NaH 2 PO 4 ; pH 7.4) .
  • the electrode strip was cleaned by ethanol and deionized water and further dried by nitrogen gas.
  • the EET system was used to measure the concentrations of H 2 O 2 solutions from 1 nM H 2 O 2 to 100 ⁇ M H 2 O 2 . During this measurement, the amperometry method was applied, and the voltage difference between the working electrode and the reference electrode was set at 0.25 V to drive corresponding redox reaction.
  • the detection environment of the EC system was similar to that of the EET system mentioned above.
  • FIG. 6 The results of the measurement obtained by using a conventional EC system and the EET system of the present disclosure are shown in FIG. 6.
  • ⁇ I CW represents change of the counter-to-working current.
  • the results show that the detected signals were undistinguishable when the concentration of H 2 O 2 was equal or lower than 1 ⁇ M. To be more specific, the detection limit was 10 ⁇ M.
  • the results show a concentration dependent correlation between the current ratio and concentration of H 2 O 2 .
  • the detection limit of the EET system was at least 100 times greater than that of the EC system and the detection range extended from 100 ⁇ M to 0.1 ⁇ M of H 2 O 2 .
  • the description and the embodiments clearly illustrate the advantage and efficacy brought out by the EET system of the present disclosure. More specifically, the EET system of the present disclosure can further amplify the detected signal utilizing the FET configuration within the EET system. As shown in Table 2, the present disclosure demonstrates that the EET system of the present disclosure can not only improve EGFET’s limit of Debye length in a high-ion fluid, but also increase EC measurement’s sensitivity in a lower concentration scenario. In addition, with the utilization of mediator, the EET system of the present disclosure can measure the concentration of the target no matter it has electrochemical activity or not, such that more flexibility for detection is provided.
  • the present disclosure successfully provides a EET detection system which provides outstanding sensitivity and performs well in a high-ion fluid.
  • the EET system of the present disclosure has higher value in sensing applications comparing to the EGFET and EC systems.

Abstract

A system (300) for detecting a target (324) and a method for detecting a target (324) are provided. The system (300) includes a field effect transistor (310), having a gate (312), a source (316), and a drain (314); a potentiostat (330), having a working electrode (332), a counter electrode (334), and a reference electrode (336); wherein the working electrode (332) is coupled with a detection region (320), and the counter electrode (334) is coupled with the gate (312); wherein the detection region (320), the gate (312), and the reference electrode (336) are arranged in an ion fluid (302); wherein the potentiostat (330) is configured to generate redox in the ion fluid (302) by an electrochemical method to detect the target (324).

Description

SYSTEM AND METHOD FOR DETECTION IN ION FLUID
BACKGROUND OF THE DISCLOSURE
1. Field of the Disclosure
The present disclosure relates to a field effect transistor (FET) -based biosensor, particularly a FET-based biosensor using electrochemical method to improve detection limit and sensitivity in a high-ion fluid.
2. Description of the Related Art
The determination of the presence of substances, such as proteins or some specific targets, in a blood or serum sample is important in diagnosis. For example, in an ordinary FET-based biosensor 100 as shown in FIG. 1 (A) , the gate 150 is modified with antibodies or some recognition elements 152 for the detection of specific biomarkers 154. When the biomarkers 154 are caught by the recognition elements 152, the charges of the biomarkers 154 will accumulate on the gate surface to cause a potential on the gate 150, such that the biomarker concentration can be determined by the current flowing through the substrate 120 between the source 140 and the drain 130 (i.e., IDS) in the presence of a voltage source 110.
However, if the test sample has a high ionic strength, the potential contributed by the charges of the biomarker will be neutralized by the ions in the sample. As such, once the distance (r) between the gate surface and the caught biomarker exceeds a specific length (FIG. 1 (B) ) , i.e. Debye length (λ) ， over which the ions in the sample screen out electric potential of caught biomarkers. The electric potential screened out may reduce the current flowing through the substrate 120 between the source 140 and the drain 130, such that the system cannot provide desired detection limit and sensitivity to detect the concentration of biomarker.
Therefore, the conventional FET biosensor is unable to provide desire detection limit and sensitivity to detect a target biomarker in a high-ion fluid (ionic strength is ～150 mM； Table 1) . FIG. 2 further shows the comparison of detection results of conventional extended-gate field effect transistor (EGFET) in 100 mM phosphate buffer solution (PBS) (ionic strength is ～400 mM； Table 1) and in 0.1 mM PBS (ionic strength is ～0.4 mM； Table 1) . As a result, the detection limit in high-ion fluid is lower than that in low-ion fluid, which can be attributed to the reduction of Debye length. Referring to Table 1, Debye length can be  further decreased to ～0.48 nm in 100 mM PBS, which is smaller than the diameter of hemoglobin (～ 5 nm, Biol Proced Online 2009, 11: 32-51) . Therefore, the charges carried by hemoglobin are insufficient to generate potential on the gate of EGFET to induce corresponding IDS for detection.
Figure PCTCN2016080679-appb-000001
Various approaches for such detection have been reported in the literatures. For example, regarding the sample in high-ion fluid as shown in FIG. 1 (B) , some methods are performed by diluting the test sample to obtain low ionic strength condition to extend Debye length. However, in this manner, the measurement condition is substantially limited and cannot be employed in practical applications, such as a limitation due to a further dilution of a low concentration of target biomarkers. In another approach, to remove the ions in the test sample, the test sample must be pretreated with multiple and complicated processes which consume more time and cost. An electrochemical (EC) system can serve as a solution to resolve the issue of Debye length by providing EC signal for detection. However, a conventional EC system shows poor sensitivity when the concentration of target is low.
Hence, there is a need in the industry to overcome these problems of the conventional techniques.
SUMMARY OF THE DISCLOSURE
The present disclosure provides an electrochemical extended gate FET-based system, also referring as an electrochemical extended-gate transistor (EET) system, which is capable of avoiding Debye length issue and can be used directly to detect a target (for example, a biomarker) in high-ion fluid. Furthermore, an electrochemical method is applied in the EET system of the present disclosure, such that the concentration of a target can be determined by detecting the electrochemical signals generated by the redox in an ion fluid.
According the present disclosure, the EET system for detecting a target is provided, the EET system comprises: a field effect transistor (FET) , having a gate, a source, and a drain； a potentiostat, having a working electrode, a counter electrode, and a reference electrode； wherein the working electrode is coupled with a detection region, and the counter electrode is coupled with the gate； wherein the detection region, the gate, and the reference electrode are arranged in an ion fluid； wherein the potentiostat is configured to generate redox in the ion fluid by an electrochemical method to detect the target.
In an embodiment, the FET comprises a readout unit coupled thereto for quantifying signals.
In an embodiment, the FET may be a n-MOS, a p-MOS FET, or any component with similar function.
In an embodiment, the substances in forming the working electrode, counter electrode, and reference electrode comprise at least one substance selected from the group consisting of gold, silver, platinum, palladium, carbon, indium tin oxide (ITO) glass, any conductive inks, and any combination thereof.
In an embodiment, the ion fluid may be in gas phase or liquid phase.
In an embodiment, the ion fluid may be an electrolyte, such as PBS, blood, serum, urine, saliva, sweat, or any solution having an ionic strength similar to physiological environment.
In an embodiment, the target comprises at least one selected from a group consisting of small molecule, protein, enzyme, antigen, antibody, nucleic acid, DNA, RNA, miRNA, aptamer, glycolipid, ligand, exosome or any biomarker for sensing applications.
In an embodiment, the detection region is modified with recognition elements having affinity or specificity to the target.
In an embodiment, the recognition elements can be any molecule having affinity or specificity to the target.
In an embodiment, the target may involve electrochemical (EC) activity.
Moreover, the present disclosure further provides a method for detecting a target, comprising: providing a FET having a gate, a source, and a drain； providing a potentiostat including a working electrode, a counter electrode, and a reference electrode, wherein the working electrode is coupled with a detection region, wherein the counter electrode is coupled with the gate, wherein the detection region, the gate, and the reference electrode are arranged in an ion fluid； and performing an electrochemical method driven by the potentiostat to generate redox in the ion fluid to detect the target.
In the present disclosure, the electrochemical method includes: voltammetry method, amperometry method, conductimetric method, impedance method, or any conventional electrochemical method.
BRIEF DESCRIPTION OF THE DRAWINGS
FIGs. 1 (A) and 1 (B) illustrate a conventional FET-based biosensor and the relationship between ionic strength and Debye length；
FIG. 2 shows results of using conventional EGFET system for detecting hemoglobin in 100 mM PBS and 0.1 mM PBS；
FIG. 3 shows a schematic view of the EET system according to an embodiment of the present disclosure, wherein the arrows show an exemplary direction for illustrating the direction of redox reaction；
FIG. 4 shows a schematic view of the EET system according to an embodiment of the present disclosure, wherein recognition elements and mediators are introduced to the EET system；
FIG. 5 (A) shows a plot of time against the normalized current ratio detected by a conventional EGFET system according to an embodiment of the present disclosure for detecting hemoglobin；
FIG. 5 (B) shows a plot of concentration of hemoglobin against the normalized current ratio detected by a conventional EGFET system according to an embodiment of the present disclosure for detecting hemoglobin；
FIG. 5 (C) shows a plot of time against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting hemoglobin；
FIG. 5 (D) shows a plot of concentration of hemoglobin against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting hemoglobin；
FIG. 6 (A) shows a plot of time against the normalized current ratio detected by a conventional EC system according to an embodiment of the present disclosure for detecting H2O2；
FIG. 6 (B) shows a plot of concentration of H2O2 against the normalized current ratio detected by a conventional EC system according to an embodiment of the present disclosure for detecting H2O2；
FIG. 6 (C) shows a plot of time against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting H2O2；
FIG. 6 (D) shows a plot of concentration of H2O2 against the normalized current ratio detected by the EET system according to an embodiment of the present disclosure for detecting H2O2；
FIG. 7 shows a plot for comparing the industrial value of the EET system of the present disclosure with the conventional EGFET and EC systems.
Reference Sign List
100  Ordinary FET-based biosensor  334  Counter electrode
110  Voltage source                336  Reference electrode
120  Substrate                     340  Readout unit
130  Drain                         400  EET system
140  Source                        402  Ion fluid
150  Gate                          404  Mediator
152  Recognition element           410  FET
154  Biomarker                     412  Gate
300  EET system                    414  Drain
302  Ion fluid                     416  Source
310  FET                           420  Detection region
312  Gate                          422  Recognition element
314  Drain                         424  Target
316  Source                        430  Potentiostat
320  Detection region              432  Working electrode
324  Target                        434  Counter electrode
330  Potentiostat                  436  Reference electrode
332  Working electrode             440  Readout unit
DETAILED DESCRIPTION OF THE DISCLOSURE
The following specific embodiments are provided to illustrate the disclosure of the present disclosure, the advantages and effects can be apparently understood by those skilled in the art after reading the disclosure of this specification.
It should be understood, The accompanying drawings depicted structure, proportion, size, etc., are disclosed only to match the content of the specification, to facilitate the understanding and reading of those skilled in the art, but not intend to limit the present disclosure in specific conditions, and do not have technical substantial meaning. Any modification of the structure, change of the ratio relation, or adjustment of the size should be involved in the scope of disclosures in this specification without influencing the producible efficacy and the achievable objective of this specification. Those changes or adjustments of relative relationship without substantial change of technical content should also be considered within the category of implementation.
FIG. 3 shows a schematic view of the EET system according to an embodiment of the present disclosure. The system 300 includes: a field effect transistor (FET) 310, having a gate 312, a source 316, and a drain 314； a potentiostat 330, having a working electrode 332, a counter electrode 334, and a reference electrode 336； wherein the working electrode 332 is coupled with a detection region 320, and the counter electrode 334 is coupled with the gate 312； wherein the detection region 320, the gate 312, and the reference electrode 336 are arranged in an ion fluid 302； wherein the potentiostat 330 is configured to generate redox in the ion fluid 302 to redox by an electrochemical method to detect the target 324.
The detection mechanism of the EET system according to an embodiment of the present disclosure is described in FIG. 3. For detecting the targets, the EET system 300 may include an electrochemical (EC) method, and the voltage difference between the working electrode 332 and counter electrode 334 will drive the target 324 in the ion fluid 302 to redox. In this way, the gate voltage of the FET 310 will thereby be controlled by the voltage of counter  electrode 334 to induce a drain-to-source current (IDS) , which can be detected by the readout unit 340. Therefore, the concentration of the target 324 is presented as a function of the IDS detected by readout unit 340. Furthermore, some targets 324 may have specific electrochemical characteristic, such that when the potentiostat 330 performs an appropriate electrochemical method, the target 324 can generate corresponding faradic current and present a pair of redox peaks at a specific potential. Preferably, the detection region 320 of the EET system 300 may be modified with recognition elements (not shown in FIG. 3) having specificity to the target 324. When more recognition elements are combined with the target 324, the characteristic signal of the target 324 (e.g. peak current at redox potential) will also be measured. Besides, the signal may be further amplified by the FET 310, and the concentration of the target 324 can thereby be calculated and obtained by the readout unit 340 coupled with the FET 310.
FIG. 4 shows the EET system 400 according to another embodiment of the present disclosure. In the following, like numbers refer to like elements throughout this embodiment and the explanations that duplicate one another will be omitted. In this embodiment, the detection region 420 of the EET system 400 is modified with recognition elements 422 having specificity to the targets 424, and the targets 424 do not have electrochemical activity. Because the target 424 cannot generate enough redox current for target detection, in this embodiment, additional mediators 404 are added into the ion fluid 402 to facilitate the generation of the redox current. The mediator 404 can be any kind of mediator commonly used in this technical field, such as but not limited to, potassium ferricyanide, ferrocene, and tetrathiafulvalene (TTF) . When an EC method is applied, the added mediators 404 are driven to generate redox current. In this way, when more recognition elements 422 are combined with targets 424, the resistance of the detection region 420 will change, and the redox current contributed by the mediator 404 will change correspondingly. Therefore, the concentration of the target 424 can be calculated by the readout unit 440 in this manner.
According to an embodiment of the present disclosure, a method for detecting a target 324 with the EET system 300 is provided and illustrated in FIG. 3. The method comprises: providing a field effect transistor (FET) 310 having a gate 312, a source 316, and a drain 314； providing a potentiostat 330 having a working electrode 332, a counter electrode 334, and a reference electrode 336； wherein the working electrode 332 is coupled with a detection region 320, wherein the counter electrode 334 is coupled with the gate 312, wherein the detection region 320, the gate 312, and the reference electrode 336 are arranged in an ion fluid 302； and performing an electrochemical method driven by the potentiostat 330 to generate redox in the ion fluid 302 to detect the target 324.
The present disclosure describes details with exemplarily embodiments. The present disclosure, however, should not be construed as being limited to the embodiments set forth herein.
Embodiment 1:
The following experiment was carried out to illustrate that the EET system provided superior sensing performance (such as the limitation of the detection and the magnitude of the responses) even in physiological ionic strength environment. In this embodiment, the target was hemoglobin. The potentiostat was CHI6192E (CHI, Austin, TX, USA) , but other conventional potentiostat or equivalents could be used, and the working electrode, the counter electrode, and the reference electrode were respectively electrically coupled to a carbon electrode, a carbon electrode, and an Ag/AgCl electrode. Any appropriate pretreatment can be applied to the electrodes in the embodiment, such as cleaning by oxygen plasma, ethanol or deionized water. In addition, a person having ordinary skill in the art should understand that PBS is commonly used for simulating physiological environment in the technical field. The ion fluid was 100 mM PBS, prepared in 100 mM Na2HPO4 and 100 mM NaH2PO4, and the pH value was 7.4.
Afterwards, the EET system was used to measure the concentrations of hemoglobin  solutions from 0.01 μg/ml to 100 μg/ml. During this measurement, an amperometry method was applied, and the voltage difference between the working electrode and the reference electrode was set at -0.4 V to drive corresponding redox reaction.
By comparison, a conventional EGFET system was used to detect hemoglobin. The configuration of the EGFET system and the detection condition were the same as those of the EET system mentioned above. A source-measurement unit was also utilized in the EGFET system but it merely was used for applying a potential with respect to the reference electrode and measuring signal.
The result of the measurement detected by a conventional EGFET system and the EET system of the present disclosure is shown in FIG. 5. In FIGs. 5 (A) and 5 (C) , the x-axis refers to the measurement time, while in FIGs. 5 (B) and 5 (D) , the x-axis refers to the concentration of hemoglobin. The y-axis refers to current ratio, ΔIDS (change of the drain-to-source current) /I0 (current detected in PBS without hemoglobin) . The current ratio (ΔIDS/I0) shown in y-axis is used for illustrating the normalized result of the detection, such that a person having ordinary skill in the art should easily understand the advantage and efficacy brought out by the present disclosure.
FIGs. 5 (A) and 5 (B) clearly show when the concentration of hemoglobin was equal or lower than 1 μg/ml, the signals measured by EGFET system was unobservable. Also, the detected signal (reference to current ratio) in 100 μg/ml of hemoglobin by the conventional EGFET system was merely 2％-3％ higher than that of the blank (without hemoglobin) .
In contrast, according to FIGs. 5 (C) and 5 (D) , it shows a concentration-dependent correlation between the current ratio and concentration of hemoglobin. Also, the detection limit of the EET system was at least 30 times greater than that of the EGFET system and the detection range extended from 100 μg/ml to ～0.3 μg/ml of hemoglobin. Furthermore, the detected signal (reference to current ratio) increased ～3％ with outstanding linearity, when the concentration of hemoglobin increased 10 times.
Embodiment 2:
The experiment was carried out to illustrate that the EET system provided superior sensing performance comparing to a conventional EC system. In this embodiment, the sensing target was H2O2. A commercial strip (DEP-ER-P, BioDevice, Japan) was used in the embodiment, wherein the working, counter, and reference electrodes of the strip were of gold, carbon, and Ag/AgCl, respectively. The potentiostat was CHI6192E (CHI, Austin, TX, USA) . The ion fluid in this embodiment was PBS (100 mM Na2HPO4 and 100 mM NaH2PO4； pH 7.4) . Before the measurement, the electrode strip was cleaned by ethanol and deionized water and further dried by nitrogen gas.
Afterwards, the EET system was used to measure the concentrations of H2O2 solutions from 1 nM H2O2 to 100 μM H2O2. During this measurement, the amperometry method was applied, and the voltage difference between the working electrode and the reference electrode was set at 0.25 V to drive corresponding redox reaction. The detection environment of the EC system was similar to that of the EET system mentioned above.
The results of the measurement obtained by using a conventional EC system and the EET system of the present disclosure are shown in FIG. 6. In FIGs. 6 (A) and 6 (B) , ΔICW represents change of the counter-to-working current. The results show that the detected signals were undistinguishable when the concentration of H2O2 was equal or lower than 1 μM. To be more specific, the detection limit was 10 μM.
In contrast, according to FIGs. 6 (C) and 6 (D) , the results show a concentration dependent correlation between the current ratio and concentration of H2O2. Also, the detection limit of the EET system was at least 100 times greater than that of the EC system and the detection range extended from 100 μM to 0.1 μM of H2O2.
From the foregoing, the description and the embodiments clearly illustrate the advantage and efficacy brought out by the EET system of the present disclosure. More specifically, the EET system of the present disclosure can further amplify the detected signal utilizing the FET  configuration within the EET system. As shown in Table 2, the present disclosure demonstrates that the EET system of the present disclosure can not only improve EGFET’s limit of Debye length in a high-ion fluid, but also increase EC measurement’s sensitivity in a lower concentration scenario. In addition, with the utilization of mediator, the EET system of the present disclosure can measure the concentration of the target no matter it has electrochemical activity or not, such that more flexibility for detection is provided. In summary, the present disclosure successfully provides a EET detection system which provides outstanding sensitivity and performs well in a high-ion fluid. As shown in FIG. 7, the EET system of the present disclosure has higher value in sensing applications comparing to the EGFET and EC systems.
Figure PCTCN2016080679-appb-000002
The present disclosure has been described using exemplary embodiments to illustrate the principles and the effects of the present disclosure, but not intend to limit the present disclosure. The present disclosure without departing from the spirit and scope of the premise can make various changes and modifications by persons skilled in the art. Therefore, the scope of protection of the rights of the disclosure, the claims should be listed in the book. Therefore, the scope of the disclosure should be defined by the appended claims.

Claims (20)

  1. A system for detecting a target, comprising:
    a field effect transistor (FET) , having a gate, a source, and a drain；
    a potentiostat, having a working electrode, a counter electrode, and a reference electrode；
    wherein the working electrode is coupled with a detection region, and the counter electrode is coupled with the gate；
    wherein the detection region, the gate, and the reference electrode are arranged in an ion fluid；
    wherein the potentiostat is configured to generate redox in the ion fluid by an electrochemical method to detect the target.
  2. The system of claim 1, wherein the FET comprises a readout unit coupled thereto for quantifying signals.
  3. The system of claim 1, wherein the FET is an extended gate FET.
  4. The system of claim 1, wherein the target involves an electrochemical activity.
  5. The system of claim 1, wherein the target comprises at least one selected from a group consisting of small molecule, protein, nucleic acid, and glycolipid, and any combination thereof.
  6. The system of claim 1, wherein the ion fluid is in gas phase or liquid phase.
  7. The system of claim 6, wherein the liquid phase of the ion fluid is an electrolyte.
  8. The system of claim 1, wherein the ion fluid comprises a mediator.
  9. The system of claim 1, wherein the detection region is modified with recognition elements having affinity or specificity to the target.
  10. The system of claim 1, wherein the electrochemical method is at least one selected from the group consisting of a voltammetry method, an amperometry method, a conductimetric method, an impedance method, and any combination thereof.
  11. A method for detecting a target, comprising:
    providing a field effect transistor (FET) having a gate, a source, and a drain；
    providing a potentiostat having a working electrode, a counter electrode, and a reference electrode, wherein the working electrode is coupled with a detection region, wherein the counter electrode is coupled with the gate, wherein the detection region, the gate, and the reference electrode are arranged in an ion fluid； and
    performing an electrochemical method driven by the potentiostat to generate redox in the ion fluid to detect the target.
  12. The method of claim 11, further comprising quantifying signals produced by the redox of the target by a readout unit coupled to the FET.
  13. The method of claim 11, wherein the FET is an extended gate FET.
  14. The method of claim 11, wherein the target involves an electrochemical activity.
  15. The method of claim 11, wherein the target comprises at least one selected from a group consisting of small molecule, protein, nucleic acid, and glycolipid, and any combination thereof.
  16. The method of claim 11, wherein the ion fluid is in gas phase or liquid phase.
  17. The method of claim 16, wherein the liquid phase of the ion fluid is an electrolyte.
  18. The method of claim 11, wherein the ion fluid further comprises a mediator.
  19. The method of claim 11, wherein the detection region is modified with recognition elements having affinity or specificity to the target.
  20. The method of claim 11, wherein the electrochemical method is at least one selected from the group consisting of a voltammetry method, an amperometry method, a conductimetric method, an impedance method, and any combination thereof.
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