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WO2015007369A1 - Réseau de biocapteurs - Google Patents

Réseau de biocapteurs Download PDF

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Publication number
WO2015007369A1
WO2015007369A1 PCT/EP2014/001804 EP2014001804W WO2015007369A1 WO 2015007369 A1 WO2015007369 A1 WO 2015007369A1 EP 2014001804 W EP2014001804 W EP 2014001804W WO 2015007369 A1 WO2015007369 A1 WO 2015007369A1
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WO
WIPO (PCT)
Prior art keywords
biosensor
cells
biosensor array
array
cell
Prior art date
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Ceased
Application number
PCT/EP2014/001804
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English (en)
Inventor
Masaki Hasegawa
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Merck Patent GmbH
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Merck Patent GmbH
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Filing date
Publication date
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Publication of WO2015007369A1 publication Critical patent/WO2015007369A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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

Definitions

  • the invention relates to a biosensor array and to a preparation thereof.
  • the invention further relates to the use of biosensor cells specifically in biosensor arrays.
  • the invention further relates to a calibration method of a biosensor array and a method for wider and improved dynamic detection range of a biosensor array.
  • JP3969702B (Seiko Epson Co.) describes a capacitor type TFT biosensor array.
  • JP4255475B (Fujitsu Ltd.) describes a top gate type TFT biosensor array.
  • WO 2012/084077A (Agency for Science, Technology and Research) describes an FET biosensor array.
  • the inventors aimed to solve one or more of the aforementioned problems.
  • the inventors have found an inventive biosensor array comprising a plurality of biosensor cells (4) having a sensor layer (14) and receptors (13) that are immobilized on surface of the sensor layer (14), where at least one biosensor cell of the plurality of biosensor cells has a different density of receptors than the other biosensor cell of the plurality of biosensor cells.
  • the inventive biosensor array is highly suitable for detecting bioanalytes. Preferably, it solves one or both of problems 1 and 2.
  • the inventors further innovated a calibration function of a biosensor array for solving problem 1 or both of problems 1 and 2.
  • the invention therefore relates to a biosensor array which comprises:
  • a substrate (8) comprising switching field effect transistors (3), gate lines (2), drain lines (5), and source lines (1);
  • a plurality of biosensor cells which are connected to the source lines (1) via switching field effect transistors (3); where each of the biosensor cells has a source electrode (11), a drain electrode (12), a sensor layer (14) and receptors (13), which are immobilized on the surface of the sensor layer (14); with the proviso that at least one biosensor cell of the plurality of biosensor cells has a different density of receptors than the other biosensor cell of the plurality of biosensor cells and a differentiation of the receptor density between at least one biosensor cell of the plurality of biosensor cells and the other biosensor cell of the plurality of biosensor cells is in the range of 1.05 times to 1000 times.
  • differentiation of the receptor density between at least one biosensor cell of the plurality of biosensor cells and the other biosensor cell of the plurality of biosensor cells is in the range of 2 times to 15 times.
  • biosensor array of the present invention More specifically, by switching from biosensor cells with high sensitivity to biosensor cells with low sensitivity, wider and improved dynamic detection range can be realized.
  • the switching from biosensor cells with high sensitivity to biosensor cells with low sensitivity can be realized by selecting switching field effect transistors (hereafter, SWFETs) accordingly.
  • SWFETs switching field effect transistors
  • One or more of the biosensor cells of the plurality of the biosensor cells with lower receptor density than the other biosensor cell of the plurality of the biosensor cells is used as the low sensitivity biosensor cells, and the biosensor cells with higher receptor density are used as the high sensitivity biosensor cells.
  • the biosensor cells of the present invention are, at each occurrence, field effect transistors to realize higher sensitivity of the biosensor array.
  • the SWFET may or may not be present in the biosensor array. In case the SWFETs are not present, the biosensor cells function instead as SWFETs.
  • SWFETs makes the structure of the biosensor array simple and may realize cost reduction of the biosensor array.
  • the biosensor cells in the biosensor array may have, at each occurrence, a top gate electrode and / or a bottom gate electrode.
  • the biosensor cells in the biosensor array of the present invention have a top gate electrode.
  • a sensor layer of the biosensor cell is not particularly limited. Many kinds of semiconductive materials which are publicly known, can be used as materials for the sensor layer. Such as amorphous silicon, polycrystalline silicon, metal oxide material, organic semiconductor material, CNT, graphene, reduced graphene oxide (hereafter, RGO).
  • Graphene or RGO is preferable because it is highly suitable to fix linkers and / or receptors on the surface.
  • the sensor layer may be a stacked layer to enhance the electron mobility of the sensor layer.
  • the stacked layer consists of two or more of layers.
  • the stacked layer consists of two layers and one layer is a RGO layer.
  • the RGO layer is stacked onto the other sensor layer that has preferably a higher electron mobility than the RGO layer.
  • the other sensor layer of the stacked layer comprises polycrystalline silicon, or metal oxide material to increase the electron mobility of the stacked layer.
  • the biosensor array according to the present invention comprises a biosensor array area and one or more calibration cell areas.
  • the calibration cell area can be overlapping with the biosensor array area and / or can be located in a different part of the biosensor array area.
  • this configuration can be used in the calibration process.
  • All calibration process can be done in the calibration area, and the actual biosensing to detect analyte type and analyte concentration can be done in the biosensor array area.
  • a substrate of the biosensor array is not particularly limited. Any publicly known kind of substrates having good surface flatness can be used, such as a glass substrate, a silicon substrate, or a metal substrate.
  • the biosensor array may comprise a wall to keep a buffer solution.
  • a material for the wall is not particularly limited. It can be selected from publicly known ones, such as silicone rubber gel.
  • At least one of the biosensor cells in the biosensor array according to the present invention consists of different kinds of receptors compared with the receptors of the rest of the biosensor cells of the biosensor array, to detect different kinds of analytes.
  • the biosensor array of the present invention can have the ability to detect multiple analytes by one biosensor array at the same time.
  • the kind of receptor is not particularly limited. Depending on the kind of target analyte, the receptor is selected preferably from publicly known ones.
  • Publicly known antibodies, aptamers or capture DNA can be used as a receptor of the present invention.
  • the buffer solution to disperse receptors is not particularly limited.
  • the solution can be preferably selected from publicly known buffer solutions for biotechnology.
  • buffer solutions for biotechnology such as PBS, HEPES buffer, Tris buffer.
  • NaCI is added to the solution to disperse the receptors.
  • linkers can be used to fix receptors on the sensor layer stably.
  • sulfo-SSMCC cross linker 1- pyrenebutanoic acid succinimidyl ester.
  • the solvent for linker is not particularly limited. Publicly known one can be selected to make a linker solution.
  • DMF DMF
  • Methanol can be used preferably as the solvents for aforementioned linkers.
  • the invention further relates to a process for the preparation of a biosensor array of the present invention, comprising the following steps in the sequence: a) performing film formation of sensor layer;
  • a receptor density of a biosensor cell can be controlled by changing the receptor concentration in the receptor solution and the incubation time.
  • receptor density is used with the meaning, that the receptor number / ⁇ 2 is confirmed by the following method:
  • the actual receptor density of biosensor cells is confirmed by Atomic force microscopy (here after, AFM), such as SPM-9700 (Shimazu) with eyes or with software system of SPM-9700 named" MODEL Particle Analysis” (Shimazu) for particle analysis.
  • AFM image with 300 nm 2 to 500 nm 2 resolution can be used to count a receptor density by eyes or by the software system.
  • the results of AFM can be used to predetermine the receptor
  • the incubation time is 1 hour up to 15 hours.
  • a rinse solution is not particularly limited and may be selected from publicly known ones.
  • PH7 PBS solution can be used in the rinse process in step e).
  • the process for the preparation of a biosensor array of the present invention embraces following sequential steps f) to j) between step a) and step b);
  • a drying process to remove the rinse solution from the substrate may be present.
  • a buffer for a linker is saturated with a linker to make a linker solution.
  • incubation condition in step h) is 1 to 10 hours settlement at room temperature in air conditioning. More preferably, it is 4 hours settlement at room temperature in air conditioning.
  • a rinse solution is not particularly limited and may be selected from publicly known ones.
  • PH7 methanol / PBS mixed solution can be used in the rinse process in step i).
  • a biosensor array is settled in air conditioning for 1hour at room temperature.
  • an inkjet machine, a dispenser or a nozzle printing machine can be used to pour a buffer solution selectively on a sensor layer of the biosensor cells.
  • An inkjet machine, a dispenser, or a nozzle printing machine can pour different solutions which have a different concentration of receptors and / or different kinds of receptor, selectively on different biosensor layers.
  • Mask technique is also applicable to pour a buffer solution selectively on a sensor layer of the biosensor cells.
  • Rubber masks preferably a silicone rubber mask, can be used in this way.
  • the process has the following sequential steps a), b) and k) to o), instead of present sequential steps of the process for the preparation of a biosensor array of the present invention a) to e); a) performing film formation of sensor layer;
  • a rubber mask is put onto a biosensor array to cover the sensor layers of one or more of biosensor cells of the plurality of biosensor cells selectively.
  • a solution having determined concentration of receptor is poured onto one or more of the biosensor layers of a biosensor array
  • the mask is removed and put again onto a biosensor array to cover the sensor layers of another biosensor cells of the plurality of biosensor cells selectively.
  • a solution having different concentration or different kind of receptor is poured onto the biosensor layers.
  • the mask is removed again.
  • the biosensor cells having different receptor density and / or different kinds of receptors can be fabricated.
  • the receptor density of a biosensor cell can be controlled by changing receptor concentration in a receptor solution and / or incubation time.
  • the invention further relates to the use of biosensor cells specifically in a biosensor array of the present invention, in which the biosensor array comprises:
  • a substrate (8) comprising switching field effect transistors (3), gate lines (2), drain lines (5), and source lines (1);
  • each of the biosensor cells has a source electrode (11), a drain electrode (12), a sensor layer (14) and receptors (13), which are immobilized on the surface of the sensor layer (14); with the proviso that at least one biosensor cell of the plurality of biosensor cells has a different density of receptors than the other biosensor cell of the plurality of biosensor cells and a differentiation of the receptor density between at least one biosensor cell of the plurality of biosensor cells and the other biosensor cell of the plurality of biosensor cells is in the range of 1.05 times to 1000 times.
  • the invention further relates to a calibration method of a biosensor array.
  • the term "calibration" is used with the meaning that p) making an estimate of the symbol K and A in the formula (I), and q) using the obtained values for K and A to conclude from the drain current to the analyte type and the analyte concentration.
  • the values of the symbol K and A depend on an analyte type, receptor type and receptor density.
  • the symbol K depends on the analyte type, receptor type and receptor density .
  • the symbol K represents the gradient of the calibration curves.
  • the symbol A represents the initial drain current of each biosensor cell of the biosensor array before any analyte solution is poured.
  • Y represents an analyte concentration of the poured analyte solution.
  • calibrated analyte concentration and the analyte type are determined by measured drain current and the values of K and A obtained in the calibration.
  • drain current change in the formula (I) means a value calculated as follows: detected drain current - A.
  • drain current is used with the meaning of the raw drain current value of a biosensor array.
  • the calibration method embraces determination process of calibration curves of each biosensor cell.
  • the determination process of calibration curves embraces following sequential process r) to w);
  • Measurement process of drain current and drain current change may be continuous throughout the step t) to v) and also pouring process may be continuous by changing solutions with different concentration of analyte.
  • Measurement method and equipment are not particularly limited. Publicly known techniques and / or equipment can be used, such as digital signal oscilloscope with probe(s), or a digital altimeter.
  • a biosensor array of the present invention may have one or more of publicly known amplification circuits to make the drain current larger.
  • step x) preferably follows:
  • the calibration method is applied to each biosensor cells having different receptor condition, such as kind of receptor, density of receptor.
  • the two proportional coefficients with its value A and K of the formula (I) are determined from the primary approximation lines on a receptor type and a receptor concentration basis as well as a analyte type basis by each biosensor cells of the biosensor array.
  • Determined calibration curves may be stored in a memory or an external storage on a receptor and an analyte type basis.
  • an external storage preferably a laptop computer or a desktop computer may be used.
  • the biosensor array of the present invention may have a memory to store determined calibration curves and / or the memory may be an external memory.
  • the determined values of the symbols K and A in the earlier mentioned formula (I) may be stored in the memory or the external storage as mentioned above on a receptor type and receptor concentration basis as well as an analyte type basis.
  • calibrated analyte concentration and the analyte type are determined by measured drain current and the values of K and A obtained in the calibration.
  • a memory and the external storage that has a calibration data, calibration curves, the values of the symbols K and A, may be used for the calibration of another biosensor cell and / or biosensor array.
  • the stored calibration data may be used for the same biosensor array that was used in calibration process due to the products quality varies widely caused by variation of fabrication conditions.
  • the invention further relates to a method of wider and improved dynamic detection range and high sensitivity of a biosensor array.
  • the biosensor array has at least two types of biosensor cells, one is a biosensor cell with higher receptor density and another one is a biosensor cell with lower receptor density than the higher one.
  • the biosensor cell with low receptor density is used to low sensitivity biosensor and the biosensor cell with high receptor density is used as high sensitivity biosensor.
  • the value of the saturation point of each biosensor cell can be determined as follows;
  • concentration such as 100 pico Mol / 10 mM buffer, 1 nano, 10 nano, 100 nano, 1 micro, 0 micro, 20 micro, 30 micro and 50micro Mol / 10 mM buffer and measure drain currents of each biosensor cell of the biosensor array.
  • B) by using the value of the last three drain current changes, 2 nd primary approximation line is determined.
  • C) extend both 1 st and 2 nd primary approximation lines to figure out the crossing point.
  • the crossing point can be defined as the saturation point.
  • the value of the saturation point of each biosensor cell of the biosensor array may be stored in a memory or an external storage.
  • field effect transistor means a transistor in which the current path from source to drain is modulated by applying a transverse electric field between grid or gate electrodes.
  • the term embraces thin film transistor (hereafter, TFT) and Metal Oxide Semiconductor Field Effect Transistor (hereafter, MOSFET).
  • Amorphous Si:H (hereafter a-Si:H) thin film transistor (hereafter TFT) arrays are fabricated by using conventional plasma CVD and
  • the array consists of 2 rows and 2 columns, and the source electrodes made of gold are connected to each switching TFT.
  • the drain electrodes made of gold are connected to each drain line.
  • the source and drain electrodes are fabricated by using lift off deposition method.
  • the source and drain electrodes pattern is made with photoresist by photolithography, then Au is fabricated as the source and drain electrodes by using vapour deposition method. After Au is deposited, photoresist pattern is removed by solvent.
  • ink jet printing method can be used to fabricate Au pattern.
  • the source and drain electrodes are coated by graphene oxide (hereafter, GO) that is dispersed in methanol, by using an inkjet printer.
  • GO graphene oxide
  • the GO is prepared as follows:
  • graphite is mixed with the strong acid solution comprising NaNO3, H2SO4, and KMnO 4 . Then the mixture is stirred for 50 hours. After stirring, the mixture is diluted in pure water, and it is centrifuged to separate exfoliated graphite. Then it is decanted off and dispersed in methanol.
  • the GO is coated on the source and drain electrodes as the sensor layer, methanol is evaporated at room temperature, then the GO is reduced by ascorbic acid to a RGO, and RGO works as sensor layer. After reduction has been obtained, the silicone rubber mask is placed on the biosensor array to keep the solutions.
  • succinimidyl ester and methanol is poured onto the RGO surface.
  • Methanol as a buffer solution of the linker solution is saturated with 1- pyrenebutanoic acid succinimidyl ester to make the linker solution.
  • the pouring condition is 4 hours settle at room temperature to fix the linker on the RGO surface.
  • PH7 methanol / PBS mixed solution is used to rinse. After 1 hour settled, the biosensor array having 2 * 2 biosensor cells with linker is obtained. Then, IgE aptamer solution is poured onto one biosensor cell surface to fix the IgE aptamer on the linker as the receptor of the biosensor array.
  • the four types of IgE aptamer solutions are prepared with following conditions; 10 nM, 30 nM ,50 nM and 100 nM IgE aptamer, as the receptor, are dispersed each independently in the buffer solution.
  • the four types of IgE aptamer solutions are poured each independently onto the four biosensor cells of the biosensor array.
  • the biosensor cells are rinsed by PH7 PBS solution to wash out the buffer solution of the receptor and receptors which do not immobilize on the sensor layer.
  • biosensor array having 2 * 2 biosensor cells is obtained.
  • Receptor density of each biosensor cell of the biosensor array is 3000 / m 2 , 4800 / prn 2 , 9000 / Mm 2 and 17,000/ ⁇ 2 confirmed by AFM, and the AFM image with 300 nm 2 resolution is used to count the receptor density by eyes.
  • the AFM image with 300 nm 2 resolution is used to count the receptor density of the biosensor cells of the biosensor array of example 1. It is counted by eyes.
  • Receptor density of each biosensor cell of the biosensor array fabricated in the example 1 is 3000 / ⁇ 2 , 4800 / ⁇ 2 , 9000 / m 2 and 17,000/ ⁇ 2 .
  • the measurement results of the biosensor cells of the biosensor array fabricated in the example 1 and relation between receptor concentration and receptor density in the fabrication condition in example 1 are shown in figure 12.
  • Analyte solutions with 1 pM, 5 nM, 20 nM, 25nM, 130 nM, 220nM, 500 nM and 1 ⁇ IgE / 10 mM buffer are prepared.
  • As the buffer solution 10mM PBS with 140mM NaCI is used.
  • the biosensor array fabricated in the Example 1 is used in the calibration process.
  • drain current of the biosensor cells are each independently measured with the digital signal oscilloscope Agilent DSO3202A is used to determine the value A of each biosensor cell of the biosensor array.
  • analyte solutions 1 pM, 5 nM, 20 nM, 25nM, 130 nM, 220nM, 500 nM and 1 ⁇ IgE / 10 mM buffer with 10mM PBS and 140mM NaCI are poured according to the analyte concentration of the solutions and the drain current changes of the biosensor cell of the biosensor array are measured sequentially with the digital signal oscilloscope named Agilent DSO3202A.
  • the primary approximation lines are calculated with the values of the first three drain current changes.
  • the two proportional coefficients with its value A and K of the formula (I) are determined from the primary approximation lines by each biosensor cells of the biosensor array.
  • Fig. 13 shows the results.
  • diamond shapes represent drain current changes of the biosensor cell having 17,000/ ⁇ 2 IgE receptor density
  • square shapes represent drain current changes of the biosensor cell having 9,000/ ⁇ 2 IgE receptor density
  • triangle shapes represent drain current changes of the biosensor cell having 4,800/ ⁇ 2 IgE receptor density
  • cross shapes represent drain current changes of the biosensor cell having 3,000/ ⁇ 2 IgE receptor density.
  • Example 4 Specificity check of the antibody detection of the receptor IgE antibody solutions with 10 nM, 100 nM, and 200 nM IgE / 10 mM buffer with 10mM PBS and 140mM NaCI are prepared each independently. Furthermore BSA antibody solutions with 10 nM, 100 nM, and 200 nM BSA / 10 mM buffer with 10mM PBS and 140mM NaCI are prepared each independently.
  • Drain current changes are observed when the IgE antibody solutions are poured. On the other hand, the drain current change does not occur when the BSA antibody solutions are poured.
  • the results show the selectivity of receptor against target antibody.
  • the biosensor cell specificity can detect antibody.
  • the biosensor array has multiple detection function of antibodies.
  • Fig.14 shows the drain current change of the biosensor array fabricated in the example 1.
  • Fig. 1 shows a biosensor array according to the present invention
  • Fig. 2 shows a biosensor array according to the present invention, in which the biosensor cells have a gate electrode and function as FETs.
  • Fig. 3 shows a biosensor array according to the present invention, in which the switching FETs are not present and instead, the biosensor cells function as FETs.
  • Fig. 4 shows a biosensor array according to the present invention, in which the biosensor array area and the calibration cell area are located in different parts of the biosensor array.
  • Fig. 5 shows a biosensor array according to the present invention, characterized that the calibration cell area overlaps with the biosensor array area.
  • Fig. 6 shows a biosensor cell structure according to the present invention that does not have a gate electrode.
  • Fig. 7 shows a biosensor cell structure according to the present invention that comprises a reference electrode as a top gate electrode .
  • Fig. 8 shows a biosensor cell structure according to the present invention that comprises a top gate electrode.
  • Fig. 9 shows the A - A' cross section of the biosensor cell according to the present invention disclosed in Fig. 8.
  • Fig. 10 shows the B - B' cross section of the biosensor cell according to the present invention disclosed in Fig.8.
  • Fig. 11 shows a biosensor cell structure according to the present invention that comprises a bottom gate electrode.
  • Fig. 12 shows the relation between receptor concentration and receptor density in the condition of working example 3.
  • Fig. 13 shows the calibration curves of the biosensor array in working example 4.
  • Fiq.14 shows the drain current changes of the biosensor array in working example 4.

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Abstract

La présente invention concerne un réseau de biocapteurs et sa préparation. L'invention concerne en outre l'utilisation de cellules de biocapteur spécifiquement dans des réseaux de biocapteurs. L'invention concerne également un procédé d'étalonnage d'un réseau de biocapteurs et un procédé permettant d'élargir et d'améliorer la plage de détection dynamique d'un réseau de biocapteurs.
PCT/EP2014/001804 2013-07-19 2014-07-01 Réseau de biocapteurs Ceased WO2015007369A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP13003636.1 2013-07-19
EP13003636 2013-07-19

Publications (1)

Publication Number Publication Date
WO2015007369A1 true WO2015007369A1 (fr) 2015-01-22

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PCT/EP2014/001804 Ceased WO2015007369A1 (fr) 2013-07-19 2014-07-01 Réseau de biocapteurs

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN114364976A (zh) * 2019-07-12 2022-04-15 曲莱博医疗有限公司 电化学fet传感器
JP2022137192A (ja) * 2016-10-27 2022-09-21 コニク インコーポレイテッド 匂い物質受容体を発現する細胞のアレイを用いた検出のためのシステム
US20220390413A1 (en) * 2020-03-09 2022-12-08 Murata Manufacturing Co., Ltd. Semiconductor device and method of manufacturing semiconductor device

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1217364A2 (fr) * 2000-12-22 2002-06-26 Seiko Epson Corporation Cellule détectrice
WO2004106891A2 (fr) * 2003-05-22 2004-12-09 University Of Hawaii Capteur biochimique ultrasensible
WO2005043160A2 (fr) * 2003-10-31 2005-05-12 University Of Hawaii Plate-forme de detection ultrasensible d'agents biochimiques
WO2006041224A1 (fr) * 2004-10-14 2006-04-20 Kabushiki Kaisha Toshiba Capteur de detection d'acide nucleique a base de transistor a effet de champ
EP1811300A1 (fr) * 2005-12-23 2007-07-25 Micronas GmbH Puce de capteur avec des récepteurs inclus dans un réseau polymérique
WO2007084077A1 (fr) 2006-01-20 2007-07-26 Agency For Science, Technology And Research Cellule de biocapteur et réseau de biocapteurs
US20080179187A1 (en) * 2007-01-31 2008-07-31 Tianmei Ouyang Heterocyclic nitrogen containing polymers coated analyte monitoring device and methods of use
JP4255475B2 (ja) 2006-01-04 2009-04-15 シャープ株式会社 データ駆動型情報処理装置
WO2012084077A1 (fr) 2010-12-23 2012-06-28 Daimler Ag Empilement de piles à combustible

Patent Citations (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1217364A2 (fr) * 2000-12-22 2002-06-26 Seiko Epson Corporation Cellule détectrice
JP3969702B2 (ja) 2000-12-22 2007-09-05 セイコーエプソン株式会社 センサ・セル、センサ、サンプルを同定する方法、化学センサ、指紋認識装置、バイオセンサの操作方法、及び指紋認識装置の操作方法
WO2004106891A2 (fr) * 2003-05-22 2004-12-09 University Of Hawaii Capteur biochimique ultrasensible
WO2005043160A2 (fr) * 2003-10-31 2005-05-12 University Of Hawaii Plate-forme de detection ultrasensible d'agents biochimiques
WO2006041224A1 (fr) * 2004-10-14 2006-04-20 Kabushiki Kaisha Toshiba Capteur de detection d'acide nucleique a base de transistor a effet de champ
EP1811300A1 (fr) * 2005-12-23 2007-07-25 Micronas GmbH Puce de capteur avec des récepteurs inclus dans un réseau polymérique
JP4255475B2 (ja) 2006-01-04 2009-04-15 シャープ株式会社 データ駆動型情報処理装置
WO2007084077A1 (fr) 2006-01-20 2007-07-26 Agency For Science, Technology And Research Cellule de biocapteur et réseau de biocapteurs
US20080179187A1 (en) * 2007-01-31 2008-07-31 Tianmei Ouyang Heterocyclic nitrogen containing polymers coated analyte monitoring device and methods of use
WO2012084077A1 (fr) 2010-12-23 2012-06-28 Daimler Ag Empilement de piles à combustible

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2022137192A (ja) * 2016-10-27 2022-09-21 コニク インコーポレイテッド 匂い物質受容体を発現する細胞のアレイを用いた検出のためのシステム
CN114364976A (zh) * 2019-07-12 2022-04-15 曲莱博医疗有限公司 电化学fet传感器
US20220390413A1 (en) * 2020-03-09 2022-12-08 Murata Manufacturing Co., Ltd. Semiconductor device and method of manufacturing semiconductor device

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