JPH0460549B2 - - Google Patents
Info
- Publication number
- JPH0460549B2 JPH0460549B2 JP60225439A JP22543985A JPH0460549B2 JP H0460549 B2 JPH0460549 B2 JP H0460549B2 JP 60225439 A JP60225439 A JP 60225439A JP 22543985 A JP22543985 A JP 22543985A JP H0460549 B2 JPH0460549 B2 JP H0460549B2
- Authority
- JP
- Japan
- Prior art keywords
- sensitive body
- substance
- substrate
- detected
- field
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 239000000126 substance Substances 0.000 claims description 33
- 239000000758 substrate Substances 0.000 claims description 23
- 239000004065 semiconductor Substances 0.000 claims description 18
- 230000005669 field effect Effects 0.000 claims description 17
- 150000001875 compounds Chemical class 0.000 claims description 3
- 229920000642 polymer Polymers 0.000 claims description 2
- 238000001514 detection method Methods 0.000 description 11
- 238000000034 method Methods 0.000 description 9
- 230000035945 sensitivity Effects 0.000 description 9
- 108090000790 Enzymes Proteins 0.000 description 8
- 102000004190 Enzymes Human genes 0.000 description 8
- 229940088598 enzyme Drugs 0.000 description 8
- 238000006243 chemical reaction Methods 0.000 description 7
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 description 6
- 239000008103 glucose Substances 0.000 description 6
- 239000012528 membrane Substances 0.000 description 5
- 230000003100 immobilizing effect Effects 0.000 description 4
- 239000000463 material Substances 0.000 description 4
- 238000003486 chemical etching Methods 0.000 description 2
- 239000013078 crystal Substances 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 238000001179 sorption measurement Methods 0.000 description 2
- 239000013076 target substance Substances 0.000 description 2
- RGHNJXZEOKUKBD-UHFFFAOYSA-N D-gluconic acid Natural products OCC(O)C(O)C(O)C(O)C(O)=O RGHNJXZEOKUKBD-UHFFFAOYSA-N 0.000 description 1
- RGHNJXZEOKUKBD-SQOUGZDYSA-N Gluconic acid Natural products OC[C@@H](O)[C@@H](O)[C@H](O)[C@@H](O)C(O)=O RGHNJXZEOKUKBD-SQOUGZDYSA-N 0.000 description 1
- 108010015776 Glucose oxidase Proteins 0.000 description 1
- 239000004366 Glucose oxidase Substances 0.000 description 1
- MHAJPDPJQMAIIY-UHFFFAOYSA-N Hydrogen peroxide Chemical compound OO MHAJPDPJQMAIIY-UHFFFAOYSA-N 0.000 description 1
- LEHOTFFKMJEONL-UHFFFAOYSA-N Uric Acid Chemical compound N1C(=O)NC(=O)C2=C1NC(=O)N2 LEHOTFFKMJEONL-UHFFFAOYSA-N 0.000 description 1
- TVWHNULVHGKJHS-UHFFFAOYSA-N Uric acid Natural products N1C(=O)NC(=O)C2NC(=O)NC21 TVWHNULVHGKJHS-UHFFFAOYSA-N 0.000 description 1
- 239000013543 active substance Substances 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 238000005530 etching Methods 0.000 description 1
- 239000007789 gas Substances 0.000 description 1
- 235000012208 gluconic acid Nutrition 0.000 description 1
- 239000000174 gluconic acid Substances 0.000 description 1
- 229940116332 glucose oxidase Drugs 0.000 description 1
- 235000019420 glucose oxidase Nutrition 0.000 description 1
- 230000020169 heat generation Effects 0.000 description 1
- 229920001600 hydrophobic polymer Polymers 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 238000004020 luminiscence type Methods 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 210000003463 organelle Anatomy 0.000 description 1
- 230000010399 physical interaction Effects 0.000 description 1
- 238000001020 plasma etching Methods 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 229920005597 polymer membrane Polymers 0.000 description 1
- 229940116269 uric acid Drugs 0.000 description 1
Classifications
-
- 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
- C12Q1/001—Enzyme electrodes
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
- G01K7/00—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements
- G01K7/16—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements using resistive elements
- G01K7/18—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements using resistive elements the element being a linear resistance, e.g. platinum resistance thermometer
- G01K7/183—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements using resistive elements the element being a linear resistance, e.g. platinum resistance thermometer characterised by the use of the resistive element
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
- G01N27/3275—Sensing specific biomolecules, e.g. nucleic acid strands, based on an electrode surface reaction
-
- 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
Landscapes
- Life Sciences & Earth Sciences (AREA)
- Chemical & Material Sciences (AREA)
- Health & Medical Sciences (AREA)
- Physics & Mathematics (AREA)
- Molecular Biology (AREA)
- Immunology (AREA)
- General Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- General Physics & Mathematics (AREA)
- Organic Chemistry (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- Electrochemistry (AREA)
- Chemical Kinetics & Catalysis (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Pathology (AREA)
- Zoology (AREA)
- Proteomics, Peptides & Aminoacids (AREA)
- Wood Science & Technology (AREA)
- Biotechnology (AREA)
- Microbiology (AREA)
- Microelectronics & Electronic Packaging (AREA)
- Biophysics (AREA)
- Bioinformatics & Cheminformatics (AREA)
- General Engineering & Computer Science (AREA)
- Genetics & Genomics (AREA)
- Investigating Or Analyzing Materials By The Use Of Fluid Adsorption Or Reactions (AREA)
- Investigating Or Analyzing Materials By The Use Of Electric Means (AREA)
- Testing Or Calibration Of Command Recording Devices (AREA)
- Apparatus Associated With Microorganisms And Enzymes (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Description
【発明の詳細な説明】
＜産業上の利用分野＞
本発明は、尿酸、グリコース等の生理活性物質
を検知対象としたバイオセンサに関し、検知対象
物（量）と前記バイオセンサに内蔵された化学的
または物理的な相互作用を電気信号に変換するこ
とにより検知対象物（量）を検出するものであ
る。[Detailed Description of the Invention] <Industrial Application Field> The present invention relates to a biosensor that detects physiologically active substances such as uric acid and glycose. The object (quantity) to be detected is detected by converting physical interaction into an electrical signal.
＜従来の技術＞
一般にバイオセンサは酵素や抗体あるいは生体
内小器官（オルガネラ）等の生体関連物質を適当
な基体（膜）に固定化したレセプターと呼ばれる
感応体と、レセプターと測定対象物質との反応に
よつて生じたあるいは消滅したガス等の化学物質
や光、熱等の物理量を電気信号に変換するトラン
スデユーサとからなる。例えば、グルコースの検
知を行うグルコースセンサにおいては、酵素（グ
ルコースオキシダーゼ：GOD）を高分子膜に固
定化したものをレセプターとして用いる。グルコ
ースとGCD酵素とが接触すると、下記の反応式
によつて過酸化水素（H2O2）が生成される。<Conventional technology> In general, biosensors use a sensitive body called a receptor, which is a biologically related substance such as an enzyme, an antibody, or an organelle immobilized on a suitable substrate (membrane), and a link between the receptor and the substance to be measured. It consists of a transducer that converts chemical substances such as gases generated or extinguished by reactions and physical quantities such as light and heat into electrical signals. For example, in a glucose sensor that detects glucose, an enzyme (glucose oxidase: GOD) immobilized on a polymer membrane is used as a receptor. When glucose and GCD enzyme come into contact, hydrogen peroxide (H 2 O 2 ) is produced according to the reaction formula below.
GOD
グルコース＋O2−→グルコン酸＋H2O2
生成されたH2O2を、例えば白金をアノードと
する電気化学デバイス（トランスデユーサ）で電
気信号として検知する。即ち、生成されたH2O2
の量を検知することによつて検知対象物質である
グルコースの濃度を知ることができる。上述のよ
うに生成された化学物質をトランスデユーサで検
知する以外に、酵素と検知対象物質との反応によ
つて生ずる発光や吸熱、発熱等の熱的現象を検出
する方式等が知られている。発光現象を利用する
場合にはトランスデユーサとして光検知器が、ま
た熱的現象を検知する場合にはサーミスタ等の温
度センサが用いられる。いずれの場合も、検知対
象物質の検出濃度下限は、ほとんどの場合レセプ
ターと検知対象物質との反応量に依存する。この
ため検出感度を増大させる手段として、可能な限
り高密度に酵素等の生体関連物質を固定化するこ
とと、検知対象物質との接触面積を増加すること
とがある。 GOD Glucose + O 2 − → Gluconic acid + H 2 O 2 The generated H 2 O 2 is detected as an electrical signal by an electrochemical device (transducer) using, for example, platinum as an anode. That is, the generated H 2 O 2
By detecting the amount of glucose, the concentration of glucose, which is the substance to be detected, can be determined. In addition to detecting the chemical substances produced as described above using a transducer, there are also known methods for detecting thermal phenomena such as luminescence, endotherm, and heat generation caused by the reaction between enzymes and the substance to be detected. There is. A photodetector is used as a transducer when a luminescent phenomenon is used, and a temperature sensor such as a thermistor is used when a thermal phenomenon is detected. In either case, the lower limit of the detection concentration of the substance to be detected depends in most cases on the amount of reaction between the receptor and the substance to be detected. Therefore, as a means to increase the detection sensitivity, there are two methods: immobilizing biological substances such as enzymes at the highest possible density and increasing the contact area with the detection target substance.
このようなバイオセンサとしては例えば、特開
昭51−139289に示されているような電界効果変換
器がある。この電界効果変換器は電界効果型トラ
ンジスタ（FET）のゲート電極に感応体を形成
させ、検知対象物質と前記感応体との相互作用に
より発生する電位の変化をFETのゲート電位の
変化としてとらえる構成になつている。 An example of such a biosensor is a field effect transducer as disclosed in Japanese Patent Laid-Open No. 139289/1983. This field effect converter has a structure in which a sensitive body is formed on the gate electrode of a field effect transistor (FET), and changes in potential generated by the interaction between the substance to be detected and the sensitive body are detected as changes in the gate potential of the FET. It's getting old.
又、検知対象物質と感応体との接触面積を増大
させることによつて検出感度を増大させる方法が
種々のセンサ素子において検討されている。 Furthermore, methods of increasing detection sensitivity by increasing the contact area between the substance to be detected and the sensitive body are being studied for various sensor elements.
＜解決しようとする課題＞
しかしながら、上述の従来技術には以下のよう
な問題点があつた。<Problems to be Solved> However, the above-mentioned conventional technology has the following problems.
特開昭51−139289に開示されているバイオセン
サでは、感応体表面が平坦なため、検知対象物質
と感応体との接触面積が小さくなり、検出感度が
低くなるという問題がある。 In the biosensor disclosed in JP-A-51-139289, since the surface of the sensitive body is flat, there is a problem that the contact area between the substance to be detected and the sensitive body becomes small, resulting in a low detection sensitivity.
前記接触面積を大きくするために、感応体の表
面に凹凸を付与する方法が考えられるが、感応体
は酵素や抗体等の生体関連物質を基体の上に共有
結合法、吸着法等により固定化して形成している
ため、凹凸を付与した基体に単に生体関連物質を
固定化しただけでは、微細加工した基体表面に直
接生体関連物質を固定化できない場合や固定化に
適した微細加工ができない場合があり、基体に高
密度に生体関連物質を付与することができなかつ
た。従つて検知対象物質と感応体とが相互作用す
る面積を有効に増大させることができなかつた。 In order to increase the contact area, it is possible to make the surface of the sensitive material uneven, but the sensitive material is made by immobilizing biological substances such as enzymes and antibodies on the substrate by covalent bonding, adsorption, etc. Therefore, simply immobilizing bio-related substances on a substrate with unevenness may not directly immobilize bio-related substances on the microfabricated surface of the substrate, or may not be able to perform microfabrication suitable for immobilization. Therefore, it was not possible to apply bio-related substances to the substrate at high density. Therefore, it has not been possible to effectively increase the area where the substance to be detected and the sensitive body interact.
本発明は、微細な凹凸が形成された基体表面に
高密度に生体関連物質を固定化することにより、
高い検出感度の電界効果型半導体センサを提供す
ることを目的とする。 The present invention achieves the following by immobilizing bio-related substances at high density on the surface of a substrate on which fine irregularities are formed.
The purpose of the present invention is to provide a field-effect semiconductor sensor with high detection sensitivity.
＜課題を解決するための手段＞
本発明の電界効果型半導体センサは、半導体基
板にソース領域とドレイン領域とを形成し、更に
前記半導体基板上にソース電極とドレイン電極を
形成すると共に、前記ソース領域とドレイン領域
の間のチヤンネル層の上に感応体を形成し、この
感応体と対向する位置に被検知物が通過するため
の空間をあけて参照電極を形成した電界効果型半
導体センサにおいて、
前記感応体が微細な凹凸形状をなしている高分
子化合物からなる基体と、該基体上に形成された
LB（ラングミユア・ブロジエツト）膜と、該LB
膜に固定化された生体関連物質とからなることを
特徴とする。<Means for Solving the Problems> A field effect semiconductor sensor of the present invention includes forming a source region and a drain region on a semiconductor substrate, further forming a source electrode and a drain electrode on the semiconductor substrate, and forming a source region and a drain region on the semiconductor substrate. In a field-effect semiconductor sensor, a sensitive body is formed on a channel layer between a region and a drain region, and a reference electrode is formed at a position facing the sensitive body with a space for the object to be detected to pass through. A substrate made of a polymer compound in which the sensitive material has a fine uneven shape, and a substrate formed on the substrate.
LB (Langmiur Blosget) membrane and the LB
It is characterized by consisting of a biologically related substance immobilized on a membrane.
＜作用＞
疎水性の高分子化合物からなる基体に、親水性
の酵素等の生体関連物質を固体化する場合、前記
基体表面が微細な凹凸形状であると、高密度に生
体関連物質を固定化することが困難である。<Function> When solidifying a biological substance such as a hydrophilic enzyme on a substrate made of a hydrophobic polymer compound, if the surface of the substrate has minute irregularities, the biological substance can be immobilized at high density. difficult to do.
本発明では、LB法により成膜されたLB膜を、
上記微細な凹凸が付与された基体表面に形成する
ことにより、基体表面を親水性化しているため、
生体関連物質を高密度に固定化することができ、
検知対象物質と感応体との反応量を多くすること
ができ、高い検出感度の電界効果型半導体センサ
を得ることができる。 In the present invention, the LB film formed by the LB method is
By forming the above-mentioned fine irregularities on the substrate surface, the substrate surface is made hydrophilic.
Bio-related substances can be immobilized at high density,
The amount of reaction between the substance to be detected and the sensitive body can be increased, and a field-effect semiconductor sensor with high detection sensitivity can be obtained.
＜実施例＞
本実施例は、酵素やその他の生体関連物質から
なるレセプター（感応体）と測定対象物質問の反
応に基づいて測定対象物質を検出する半導体バイ
オセンサに関する。<Example> This example relates to a semiconductor biosensor that detects a substance to be measured based on a reaction between a receptor (sensor) made of an enzyme or other biologically related substance and a question of the substance to be measured.
第１図は、本発明の電界効果型半導体センサに
使用する感応体局部の模式説明図である。予め、
合成高分子材料などからなる基体４１の少なくと
も表面に化学エツチングやプラズマエツチング等
の方法によつて図のような一定周期の微細な凹凸
を形成しておく、その後、酵素等の生体関連物質
４３を共有結合法あるいは吸着法によつてその表
面に固定化した感応膜４２を形成してレセプター
（感応体）とする。このような構造とすることに
よつて、従来の表面が平坦なレセプターと比べ、
基体の単位面積当たりの固定化した生体関連物質
の数が増加しかつ検知対象物質との接触面積も増
大することとなる。この結果、検出感度の増大あ
るいは、従来と同一感度で良い場合には、センサ
ー全体の小型化が可能となるなどの利点が得られ
る。 FIG. 1 is a schematic explanatory diagram of a local part of a sensitive body used in a field-effect semiconductor sensor of the present invention. In advance,
At least the surface of a substrate 41 made of a synthetic polymeric material or the like is formed with fine irregularities at a constant period as shown in the figure by a method such as chemical etching or plasma etching, and then a biologically related substance 43 such as an enzyme is applied. A sensitive film 42 fixed on the surface is formed by a covalent bond method or an adsorption method to serve as a receptor (sensor). With this structure, compared to conventional receptors with flat surfaces,
The number of immobilized biological substances per unit area of the substrate increases, and the contact area with the detection target substance also increases. As a result, there are advantages such as an increase in detection sensitivity or, if the same sensitivity as in the past, it is possible to downsize the entire sensor.
感応膜４２を基体４１上に形成する方法の一つ
として、ラングミユア・プロジエツト（LB）法
による成膜が有効である。また、基体４１に単結
晶を用いることが可能な場合には、化学エツチン
グ速度の結晶方位依存性、即ち異方性エツチング
技術を用いて微細加工することができる。上記感
応体は、電気化学デバイスや光検知器あるいは温
度センサなどのトランスデユーサと物理的に結合
してセンサを作成すれば従来にものに比べて検出
感度の高いバイオ・センサとすることができる。 As one method for forming the sensitive film 42 on the substrate 41, film formation by the Langmire-Prodget (LB) method is effective. Further, if it is possible to use a single crystal for the substrate 41, microfabrication can be performed using the crystal orientation dependence of the chemical etching rate, that is, anisotropic etching technology. If the above-mentioned sensitive body is physically combined with a transducer such as an electrochemical device, a photodetector, or a temperature sensor to create a sensor, it can be made into a biosensor with higher detection sensitivity than conventional ones. .
第２図に示すように、上記感応体を電界効果ト
ランジスタ（FET）のゲート部上な形成するこ
とによつて、本願発明のFET型のバイオ・セン
サを得ることができる。FET５１のゲート絶縁
膜５２上に感応体５３を形成し、溶液中で参照電
極５４との間で一定の電位を形成する。検知対象
物質と感応体との反応による僅かな電位変化を
FETのゲート電位の変化としてとらえ、FETの
増幅作用を利用してドレイン電流IDの大きな変化
として出力することができる。 As shown in FIG. 2, the FET type biosensor of the present invention can be obtained by forming the above-mentioned sensitive body on the gate portion of a field effect transistor (FET). A sensitive body 53 is formed on the gate insulating film 52 of the FET 51, and a constant potential is formed between it and a reference electrode 54 in a solution. Detects slight potential changes due to the reaction between the substance to be detected and the sensitive body.
This can be interpreted as a change in the gate potential of the FET, and can be output as a large change in the drain current ID by using the amplification effect of the FET.
以上のごとく本実施例の感応体は、従来から知
られているあらゆる種類のトランスデユーサと、
電気的又は物理的に結合して用いることができ、
バイオ・センサとしての性能の向上を図ることが
できる。 As described above, the sensitive body of this embodiment can be used with all kinds of conventionally known transducers.
Can be used electrically or physically coupled,
It is possible to improve the performance as a biosensor.
＜発明の効果＞
以上詳述したように、本発明の電界効果型半導
体センサは、感応体が微細な凹凸形状をなしてい
る基体とこの基体上に形成された感応膜とからな
り、さらに感応膜には生体関連物質が固定化され
た構成であるため、表面積が大きく、高密度に生
体関連物質が固定化された感応体を有する電界効
果型半導体センサが得られる。従つて、検出感度
が高い電界効果型半導体センサを得ることができ
る。<Effects of the Invention> As detailed above, the field-effect semiconductor sensor of the present invention includes a base body in which the sensitive body has a fine uneven shape and a sensitive film formed on the base body. Since the membrane has a structure in which a biological substance is immobilized, a field-effect semiconductor sensor having a large surface area and a sensitive body on which a biological substance is immobilized at a high density can be obtained. Therefore, a field effect semiconductor sensor with high detection sensitivity can be obtained.
第１図は本発明の電界効果型半導体センサに用
いる感応体の一実施例の要部の模式説明図、第２
図は感応体を電界効果トランジスタに組み込んだ
電界効果型半導体センサの一実施例を示す模式断
面図である。
４１……基体、４３……生体関連物質、４２…
…感応膜、５３……感応体、５１……FET、５
２……ゲート絶縁膜、５４……参照電極。
FIG. 1 is a schematic explanatory diagram of a main part of an embodiment of a sensitive body used in a field-effect semiconductor sensor of the present invention, and FIG.
The figure is a schematic cross-sectional view showing an embodiment of a field-effect semiconductor sensor in which a sensitive body is incorporated into a field-effect transistor. 41...Substrate, 43...Bio-related substance, 42...
...Sensitive membrane, 53...Sensitive body, 51...FET, 5
2... Gate insulating film, 54... Reference electrode.
Claims (1)
形成し、更に前記半導体基板上にソース電極とド
レイン電極を形成すると共に、前記ソース領域と
ドレイン領域の間のチヤンネル層の上に感応体を
形成し、この感応体と対向する位置に被検知物が
通過するための空間をあけて参照電極を形成した
電界効果型半導体センサにおいて、 前記感応体が微細な凹凸形状をなしている高分
子化合物からなる基体と、該基体上に形成された
LB膜と、該LB膜に固定化された生体関連物質と
からなることを特徴とする電界効果型半導体セン
サ。[Claims] 1. A source region and a drain region are formed on a semiconductor substrate, a source electrode and a drain electrode are further formed on the semiconductor substrate, and a channel layer is formed on a channel layer between the source region and the drain region. In a field effect semiconductor sensor in which a sensitive body is formed and a reference electrode is formed at a position facing the sensitive body with a space for a detected object to pass through, the sensitive body has a fine uneven shape. A base made of a polymer compound, and a base formed on the base.
A field-effect semiconductor sensor comprising an LB film and a biologically related substance immobilized on the LB film.
Priority Applications (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60225439A JPS6283641A (en) | 1985-10-08 | 1985-10-08 | Sensor element |
| DE19863634132 DE3634132C2 (en) | 1985-10-08 | 1986-10-07 | Biosensor device |
| GB8624094A GB2183344B (en) | 1985-10-08 | 1986-10-08 | Sensor |
| US07/579,195 US5140393A (en) | 1985-10-08 | 1990-09-05 | Sensor device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60225439A JPS6283641A (en) | 1985-10-08 | 1985-10-08 | Sensor element |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS6283641A JPS6283641A (en) | 1987-04-17 |
| JPH0460549B2 true JPH0460549B2 (en) | 1992-09-28 |
Family
ID=16829380
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP60225439A Granted JPS6283641A (en) | 1985-10-08 | 1985-10-08 | Sensor element |
Country Status (3)
| Country | Link |
|---|---|
| JP (1) | JPS6283641A (en) |
| DE (1) | DE3634132C2 (en) |
| GB (1) | GB2183344B (en) |
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Also Published As
| Publication number | Publication date |
|---|---|
| JPS6283641A (en) | 1987-04-17 |
| GB8624094D0 (en) | 1986-11-12 |
| DE3634132C2 (en) | 1993-10-14 |
| GB2183344B (en) | 1990-03-14 |
| GB2183344A (en) | 1987-06-03 |
| DE3634132A1 (en) | 1987-04-16 |
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