JP5301101B2 - Electrochemical sensor and electrochemical sensor system - Google Patents
Electrochemical sensor and electrochemical sensor system Download PDFInfo
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- JP5301101B2 JP5301101B2 JP2007050433A JP2007050433A JP5301101B2 JP 5301101 B2 JP5301101 B2 JP 5301101B2 JP 2007050433 A JP2007050433 A JP 2007050433A JP 2007050433 A JP2007050433 A JP 2007050433A JP 5301101 B2 JP5301101 B2 JP 5301101B2
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- electrochemical sensor
- oxidase
- dlc film
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- electrode
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Abstract
Description
本発明は電気化学センサ及び電気化学センサシステムに関する。 The present invention relates to an electrochemical sensor and an electrochemical sensor system.
従来、グルコース、尿酸などの生体関連物質は、酵素を用いたセンサを用いる方法により検出されるのが一般的である。酵素を用いない方法としては、ホウ素等の混入により導電性が付与されたダイヤモンド電極を用いて電気化学的にグルコース濃度を測定する方法が提案されている。
酵素やダイヤモンド電極を用いた従来のセンサは高価であり、より安価な材料を用いたセンサが望まれる。しかも、本発明者らの検討によれば、酵素やダイヤモンド電極を用いて血液のグルコース濃度を測定した場合、血液に含まれる血小板が酸素やダイヤモンド電極上で凝固してしまうため、センサを洗浄して再利用することが極めて困難である。材料が高価であることから、再利用が困難であり、改善の余地がある。 Conventional sensors using enzymes or diamond electrodes are expensive, and sensors using cheaper materials are desired. Moreover, according to the study by the present inventors, when the glucose concentration of blood is measured using an enzyme or a diamond electrode, platelets contained in the blood coagulate on the oxygen or diamond electrode, so that the sensor is washed. It is extremely difficult to reuse. Since the material is expensive, it is difficult to reuse and there is room for improvement.
そこで、本発明は、安価な材料を用いながら、グルコース、尿酸等の生体関連物質等の濃度を高い精度で測定することが可能なセンサを提供することを目的とする。 Therefore, an object of the present invention is to provide a sensor capable of measuring the concentration of biologically related substances such as glucose and uric acid with high accuracy while using an inexpensive material.
一つの側面において、本発明は電気化学センサに関する。本発明に係る電気化学センサは、支持体と、該支持体上に形成された導電性のDLC膜からなる作用電極と、対極と、を備える。 In one aspect, the invention relates to an electrochemical sensor. The electrochemical sensor according to the present invention includes a support, a working electrode made of a conductive DLC film formed on the support, and a counter electrode.
上記本発明に係る電気化学センサによれば、安価な材料を用いながら、グルコース、尿酸等の生体関連物質の濃度を高い精度で測定することが可能である。検体としての生体関連物質を含む試料に電気化学センサの作用電極及び対極を接触させながら、作用電極と対極との間の所定の電位における電流値が測定される。このとき、作用電極の電位を検体の酸化還元電流が適切に観測される電位に設定することにより、検体の酸化還元電流値が測定される。一般に検体の濃度は酸化還元電流値と相関するため、これらの相関関係を表す検量線を予め作成しておけば、測定された酸化還元電流値から、この検量線に基づいて検体の濃度を算出することができる。 According to the electrochemical sensor of the present invention, it is possible to measure the concentration of a biological substance such as glucose and uric acid with high accuracy while using an inexpensive material. A current value at a predetermined potential between the working electrode and the counter electrode is measured while the working electrode and the counter electrode of the electrochemical sensor are brought into contact with a sample containing a biological substance as a specimen. At this time, the redox current value of the specimen is measured by setting the potential of the working electrode to a potential at which the redox current of the specimen is appropriately observed. In general, the concentration of the sample correlates with the oxidation-reduction current value. If a calibration curve representing these correlations is created in advance, the concentration of the sample is calculated based on this calibration curve from the measured oxidation-reduction current value. can do.
上記DLC膜は、遷移金属元素を含有することが好ましい。また、本発明に係る電気化学センサは、DLC膜の表面に固定された生体関連物質を更に備えることが好ましい。これにより、検体の検出感度がより高められる。 The DLC film preferably contains a transition metal element. In addition, the electrochemical sensor according to the present invention preferably further includes a biological substance fixed on the surface of the DLC film. Thereby, the detection sensitivity of the specimen is further increased.
本発明に係る電気化学センサは、DLC膜の表面に固定された、検体を捕捉する化合物であって捕捉された検体の量に応じて酸化還元物質の酸化還元電流を定量的に変化させる化合物を更に備えていてもよい。これにより、電気化学反応に直接寄与しない検体であっても、その濃度を別の酸化還元物質の酸化還元電流に基づいて検出することが可能になる。 The electrochemical sensor according to the present invention includes a compound that is immobilized on the surface of a DLC film and that captures an analyte and quantitatively changes the oxidation-reduction current of the oxidation-reduction substance in accordance with the amount of the captured analyte. Furthermore, you may provide. This makes it possible to detect the concentration of a specimen that does not directly contribute to the electrochemical reaction based on the redox current of another redox substance.
上記支持体はプラスチック基板であることが好ましい。また、プラスチック基板は検体が比較的吸着し難く、測定後の洗浄が容易であるという利点もある。導電性のダイヤモンド薄膜を成膜するためには高温に加熱する必要があり、プラスチック基板上にダイヤモンド薄膜を形成することは極めて困難であったのに対して、DLC膜であれば比較的低温での成膜が可能であり、支持体としてプラスチック基板を採用することができる。 The support is preferably a plastic substrate . Also, the plastic substrate specimen is relatively hardly adsorbed, there is an advantage that cleaning after the measurement is easy. In order to form a conductive diamond thin film, it is necessary to heat to a high temperature, and it was extremely difficult to form a diamond thin film on a plastic substrate, whereas a DLC film has a relatively low temperature. A plastic substrate can be employed as the support.
電気化学センサは、作用電極及び対極を覆うゲル電解質膜を更に備えていてもよい。これにより、アンモニア、アセトン等のガスを検体としてその酸化還元電流や濃度を測定することが可能になる。 The electrochemical sensor may further include a gel electrolyte membrane covering the working electrode and the counter electrode. As a result, it becomes possible to measure the oxidation-reduction current and concentration using a gas such as ammonia or acetone as a specimen.
別の側面において、本発明は電気化学センサシステムに関する。本発明に係る電気化学センサは、上記本発明に係る電気化学センサと、該電気化学センサにおいて生じる酸化還元電流を検出する制御部と、を備える。このシステムによれば、安価な材料を用いながら、グルコース、尿酸等の生体関連物質の濃度を高い精度で測定することが可能である。 In another aspect, the present invention relates to an electrochemical sensor system. The electrochemical sensor according to the present invention includes the electrochemical sensor according to the present invention and a control unit that detects an oxidation-reduction current generated in the electrochemical sensor. According to this system, it is possible to measure the concentration of biological substances such as glucose and uric acid with high accuracy while using an inexpensive material.
本発明に係る電気化学センサによれば、安価な材料を用いながら、グルコース、尿酸等の生体関連物質の濃度を高い精度で測定することが可能である。 According to the electrochemical sensor of the present invention, it is possible to measure the concentration of a biological substance such as glucose and uric acid with high accuracy while using an inexpensive material.
また、DLC膜は表面にグルコース等が付着しにくく、測定後に容易に洗浄することができる。したがって、センサを容易に繰り返して使用することができる。 In addition, the DLC film hardly adheres to glucose or the like on the surface, and can be easily washed after measurement. Therefore, the sensor can be used easily and repeatedly.
以下、本発明の好適な実施形態について詳細に説明する。ただし、本発明は以下の実施形態に限定されるものではない。 Hereinafter, preferred embodiments of the present invention will be described in detail. However, the present invention is not limited to the following embodiments.
図1は、電気化学センサシステムの一実施形態の概略を示すブロック図である。図1に示す電気化学センサシステム100は、作用電極2、対極3及び参照電極5を有する電気化学センサ1と、電気化学センサ1を検体の酸化還元電流が検出されるように制御する制御部10と、を備える。作用電極2、対極3及び参照電極5はそれぞれ制御部10と電気的に接続されている。作用電極2は参照電極5を基準として所定の電位に維持されるように制御部10によって制御される。そして、作用電極2と対極3との間の電流が制御部10によって検出される。
FIG. 1 is a block diagram showing an outline of an embodiment of an electrochemical sensor system. An
本発明に係る電気化学センサシステムは、例えば図2に示す実施形態のように、参照電極を備えていなくてもよい。この場合、作用電極2の電位は対極3を基準として制御される。
The electrochemical sensor system according to the present invention may not include the reference electrode as in the embodiment shown in FIG. In this case, the potential of the working
図3は、電気化学センサの一実施形態を示す平面図である。図3に示す電気化学センサ1は、第1の基板21と、第1の基板21の一方面において一方の端部近傍に設けられた作用電極2、対極3及び参照電極5と、作用電極2、対極3及び参照電極5にそれぞれ接続されるとともに第1の基板21の他方の端部まで延在するように第1の基板21上に形成されたリード線2a,3a及び5aと、第1の基板21に接着された、作用電極2、対極3及び参照電極5が露出するような窓25が形成されている第2の基板22とから構成される。第2の基板22は、リード線2a,3a及び5aのうち第1の基板21の他方の端部近傍以外の部分を覆っている。
FIG. 3 is a plan view showing an embodiment of an electrochemical sensor. The
作用電極2は、導電性のDLC膜である。DLC膜は、一般にダイヤモンド状炭素膜、ダイヤモンド様炭素膜、ダイヤモンドライクカーボン膜、又はi−カーボン膜とも呼ばれる。DLC膜は主として炭素及び水素から構成され、sp3結合及びsp2結合が混在する非晶質炭素膜である。DLC膜の組成をCHnで表すとき、0.05≦n≦0.7である。なお、ダイヤモンド膜はダイヤモンド構造を有する結晶を含んだ膜であり、DLC膜とはその構造が異なる。DLC膜とダイヤモンド膜はラマン分光分析によって明確に区別できることが知られている。ラマンスペクトルにおいて、ダイヤモンド膜の場合1333cm−1に明確なピークが観測されるのに対して、DLC膜の場合1350cm−1付近のDisorderedバンドおよび1550cm−1付近のGraphiticバンドにブロードなピークが観測される。
The working
本発明者らの知見によれば、DLC膜を作用電極として用いた場合、アスコルビン酸のような尿中の成分の酸化電位が高電位側にシフトする。この電位シフトの結果、グルコースや尿素の酸化電流が、所定の電圧においてアスコルビン酸等の酸化電流と分離して観測される。その結果、アスコルビン酸等の混在成分が存在する血液におけるグルコースや尿素の濃度を高精度で測定することが可能になる。 According to the knowledge of the present inventors, when a DLC membrane is used as a working electrode, the oxidation potential of components in urine such as ascorbic acid is shifted to a high potential side. As a result of this potential shift, the oxidation current of glucose or urea is observed separately from the oxidation current of ascorbic acid or the like at a predetermined voltage. As a result, it becomes possible to measure the glucose and urea concentrations in blood containing mixed components such as ascorbic acid with high accuracy.
また、DLC膜の表面はダイヤモンド膜等と比較して平滑であり、検体を含む試料液に浸して測定した後に、試料液が表面に残留し難く、洗浄が容易であるという利点も有する。例えば、ダイヤモンド膜の場合、血清のグルコース濃度測定に用いられたとき、膜表面に残留した血清を充分に洗浄するのは困難である。血液の検査に用いられたときは、ダイヤモンド膜上で血しょうが凝固してしまうため、作用電極としての再使用は事実上不可能である。一方、DLC膜の場合は、試料液の残留や血しょうの凝固による固着も明らかに少なく、作用電極として容易に再使用できる。 In addition, the surface of the DLC film is smoother than that of a diamond film or the like, and has an advantage that the sample liquid does not easily remain on the surface after measurement by immersing in a sample liquid containing a specimen and is easy to clean. For example, in the case of a diamond film, when used for measuring the glucose concentration of serum, it is difficult to sufficiently wash the serum remaining on the film surface. When used for blood testing, the plasma will coagulate on the diamond membrane, making it virtually impossible to reuse as a working electrode. On the other hand, in the case of a DLC film, there is clearly little sticking due to residual sample liquid and coagulation of plasma and it can be easily reused as a working electrode.
例えばSiウエハ上に形成されたDLC膜のJIS B0601に定められた方法で測定される表面粗さRaは、0.1μm以下である。一方、ダイヤモンド膜の表面粗さRaは、通常0.5〜3μm程度である。 For example, the surface roughness Ra measured by a method defined in JIS B0601 of a DLC film formed on a Si wafer is 0.1 μm or less. On the other hand, the surface roughness Ra of the diamond film is usually about 0.5 to 3 μm.
作用電極2としてのDLC膜は、電極として機能する程度の導電性を有する。具体的には、DLC膜の抵抗率は好ましく108Ωcm以下であり、より好ましくは106Ωcm以下であり、更に好ましくは102Ωcm以下である。抵抗率の下限は特に制限はないが、通常10−4Ωcm程度である。
The DLC film as the working
DLC膜は、その導電性を高めるために、窒素、リン、ヒ素、アンチモン、ビスマス、ホウ素、アルミニウム、ガリウム、インジウム及びタリウムからなる群から選ばれる少なくとも1種の元素によってドープされる場合が多い。 The DLC film is often doped with at least one element selected from the group consisting of nitrogen, phosphorus, arsenic, antimony, bismuth, boron, aluminum, gallium, indium, and thallium in order to increase the conductivity.
導電性のDLC膜は、当業者には理解されるように、イオン化蒸着法、高周波プラズマCVD法等、DLC膜の成膜方法として通常採用されている方法によって形成することができる。成膜の際、炭素源としての炭化水素ガスとともに、窒素ガス、アンモニアガス及びピリジン等の含窒素有機物、酸化ホウ素とアルコール類若しくはケト類、又はホウ素アルコキシドのようなガスを併用することにより、窒素、ホウ素等によりドープされたDLC膜が形成される。例えば、炭化水素ガスと、窒素ガスと、場合により水素、ネオン、ヘリウム、アルゴン及び酸素からなる群より選ばれる少なくとも1種の添加ガスとを含む混合ガスを真空成膜装置内に原料ガスとして導入しながら、原料ガスに13.56MHzの周波数の電圧を印加してプラズマ化させ、プラズマ化した原料ガスから生成した炭化水素を堆積させる方法により、導電性のDLC膜を形成することができる。 As understood by those skilled in the art, the conductive DLC film can be formed by a method usually employed as a method of forming a DLC film, such as an ionization vapor deposition method or a high-frequency plasma CVD method. Nitrogen gas, ammonia gas, nitrogen-containing organic substances such as pyridine, boron oxide and alcohols or keto, or a gas such as boron alkoxide, together with hydrocarbon gas as a carbon source during film formation, nitrogen is used. Then, a DLC film doped with boron or the like is formed. For example, a mixed gas containing hydrocarbon gas, nitrogen gas, and optionally at least one additive gas selected from the group consisting of hydrogen, neon, helium, argon and oxygen is introduced as a source gas into the vacuum film forming apparatus. However, the conductive DLC film can be formed by applying a voltage of 13.56 MHz to the raw material gas to form plasma and depositing hydrocarbons generated from the plasmaized raw material gas.
DLC膜の膜厚は、0.01〜20μmであることが好ましい。この膜厚が0.01μm未満であるとDLC膜の抵抗値が大きくなる傾向にあり、20μmを超えると支持体としての基板が反ったり基板にクラックが入ったりしやすくなる傾向にある。同様の観点から、DLC膜の膜厚は、より好ましくは0.05〜10μmであり、更に好ましくは0.1〜5μmである。 The thickness of the DLC film is preferably 0.01 to 20 μm. If this film thickness is less than 0.01 μm, the resistance value of the DLC film tends to increase, and if it exceeds 20 μm, the substrate as a support tends to warp or the substrate tends to crack. From the same viewpoint, the thickness of the DLC film is more preferably 0.05 to 10 μm, and further preferably 0.1 to 5 μm.
第1の基板21とDLC膜(作用電極2)の間に、密着力を向上するためのケイ素と炭素から構成される非晶質混合層などの中間層を設けてもよい。
An intermediate layer such as an amorphous mixed layer composed of silicon and carbon for improving the adhesion may be provided between the
DLC膜は、遷移金属元素を含有することが好ましい。遷移金属元素は、金属微粒子の状態でDLC膜に添加されていてもよいし、酸化物、窒化物、塩化物、臭化物、ヨウ化物、又はフタロシアニン等の有機物との金属錯体としてDLC膜に添加されていてもよい。遷移金属元素は、具体的には、スカンジウム、チタン、バナジウム、クロム、マンガン、鉄、コバルト、ニッケル、銅、イットリウム、ジルコニウム、ニオブ、モリブデン、テクネチウム、ルテニウム、ロジウム、パラジウム、銀、ハフニウム、タンタル、タングステン、レニウム、オスミウム、イリジウム、白金、金、ランタン、セリウム、ネオジム、プロメチウム、サマリウム、ユウロピウム、ガドリニウム、テルビウム、ディスプロシウム、ホルミウム、エウロピウム、ツリウム、イッテルビウム、ルテチウム、アクチニウム、トリウム、プロトアクチニウム、ウラン、ネプツニウム、アメリシウム、キュリウム、バークリウム、カルフォルニウム、アインスタイニウム、フェルミウム、メンデレビウム、ノーベリウム及びローレンシウムからなる群から選ばれる。これら遷移金属元素はd空位軌道を有していることから、検体の酸化還元反応を促進する触媒機能を有する。これにより、検体の検出感度が向上する。触媒機能としての機能を発現し易くするため、遷移金属元素はDLC膜の表面に存在していることが好ましい。 The DLC film preferably contains a transition metal element. The transition metal element may be added to the DLC film in the form of metal fine particles, or added to the DLC film as a metal complex with an organic substance such as an oxide, nitride, chloride, bromide, iodide, or phthalocyanine. It may be. Specifically, the transition metal elements are scandium, titanium, vanadium, chromium, manganese, iron, cobalt, nickel, copper, yttrium, zirconium, niobium, molybdenum, technetium, ruthenium, rhodium, palladium, silver, hafnium, tantalum, Tungsten, rhenium, osmium, iridium, platinum, gold, lanthanum, cerium, neodymium, promethium, samarium, europium, gadolinium, terbium, dysprosium, holmium, europium, thulium, ytterbium, lutetium, actinium, thorium, protactinium, uranium , Neptunium, Americium, Curium, Barium, Calfornium, Einsteinium, Fermium, Mendelevium, Nobelium and Lorenci It is selected from the group consisting of beam. Since these transition metal elements have d vacancy orbitals, they have a catalytic function to promote the redox reaction of the specimen. Thereby, the detection sensitivity of the specimen is improved. The transition metal element is preferably present on the surface of the DLC film in order to easily develop a function as a catalytic function.
遷移金属元素をDLC膜に添加する方法としては、例えば、真空蒸着、イオンプレーティング、RFスパッタリング、化学気相蒸着法(CVD)、イオン注入、電気化学的電析、メカノケミカル反応、熱拡散又は塗布による方法が挙げられる。DLC膜の成膜の際に原料ガスとして同時に導入してもよい。 Examples of the method of adding the transition metal element to the DLC film include vacuum deposition, ion plating, RF sputtering, chemical vapor deposition (CVD), ion implantation, electrochemical electrodeposition, mechanochemical reaction, thermal diffusion, or The method by application | coating is mentioned. You may introduce | transduce simultaneously as source gas in the film-forming of a DLC film.
DLC膜の表面に、フッ素、塩素及びヨウ素のようなハロゲンや、酸素を結合させてもよい。これにより、DLC膜のぬれ性や血しょうの付着性などを制御できる。また、DLC膜の表面に各種の化合物を結合させることにより、化学修飾することもできる。化学修飾により、例えば、水素、水酸基、カルボキシル基及びアミノ基のような官能基が表面に導入される。あるいは、フェロセン、ニッケロセン、ルテニウムカルボニル錯体、ルテニウムプルシアンブルー類似体、オスミウム2,2’−ビピリジン錯体、フタロシアニン系のコバルトポルフィリン錯体、及びそれらの誘導体(例えば4−(4−フェロセンフェニルイミノメチル)フェノール)のような錯体触媒や、シトクロームオキシターゼ、D−アミノ酸酸化酵素、ヘム酸化酵素、NADHオキシダーゼ、銅アミンオキシダーゼ、ガラクトースオキシダーゼ、HIF−1プロリン水酸化酵素、キヌレニン酸化酵素、ユビキノール酸化酵素、リポキシゲナーゼ,カタラーゼ,ペルオキシダーゼ、グルタチオンパーオキシダーゼ、グルコースオキシターゼ、フェノール酸化酵素、カウレン酸酸化酵素、スーパーオキシドディスムターゼ、キサンチンオキシダーゼ、コレステロール酸化酵素、コレステロールエステラーゼ、リパーゼ、アルカリホスファターゼ、ホスホリパーゼC、アシルCoA合成酵素、ウレアーゼ、グルタミン酸脱水水素酵素、ウリカーゼ、クレアチニナーゼ、クレアチナーゼ、ピルビン酸酸化酵素、メチオニンローリアーゼ、乳酸脱水素酵素、L−アミノ酸酸化酵素、クエン酸リアーゼ、グリコーゲンホスホリラーゼ、コリンエステラーゼ、ペニシリナーゼ、ヒポキサンチン・グアニンホスホリボシルトランスフェラーゼ、コリンエステラーゼ、アミノアシラーゼ、アミノトランスフェラーゼ、グルコースイソメラーゼ、アスパルターゼ、ペニシリンアミラーゼ、フマラーゼ、ラクターゼ、L−Asp b−脱炭酸酵素、ニトリルヒドラターゼ、a−グルコシルトランスフェラーゼ、b−フルクトフラノシダーゼ、リパーゼ、マルトオリゴ糖生成酵素、ビール酵母、ナリンジナーゼ、パパイン、脱水素酵素(菌体)、アセテートキナーゼ、ホスホジエステラーゼ、クレアチナーゼ及びザルコシンオキシダーゼ等のような検体の酸化還元反応を促進する生体関連物質をDLC膜表面に固定してもよい。 A halogen such as fluorine, chlorine and iodine, or oxygen may be bonded to the surface of the DLC film. Thereby, the wettability of a DLC film, the adhesiveness of plasma, etc. can be controlled. In addition, chemical modification can be performed by bonding various compounds to the surface of the DLC film. By chemical modification, for example, functional groups such as hydrogen, hydroxyl groups, carboxyl groups and amino groups are introduced on the surface. Alternatively, ferrocene, nickelocene, ruthenium carbonyl complex, ruthenium Prussian blue analog, osmium 2,2′-bipyridine complex, phthalocyanine-based cobalt porphyrin complex, and derivatives thereof (eg, 4- (4-ferrocenephenyliminomethyl) phenol) Complex catalysts such as, cytochrome oxidase, D-amino acid oxidase, heme oxidase, NADH oxidase, copper amine oxidase, galactose oxidase, HIF-1 proline hydroxylase, kynurenine oxidase, ubiquinol oxidase, lipoxygenase, catalase, Peroxidase, glutathione peroxidase, glucose oxidase, phenol oxidase, kaurenoic acid oxidase, superoxide dismutase, xanthine Sidase, cholesterol oxidase, cholesterol esterase, lipase, alkaline phosphatase, phospholipase C, acyl-CoA synthase, urease, glutamate dehydrase, uricase, creatininase, creatinase, pyruvate oxidase, methionine loriase, lactate dehydrogenase L-amino acid oxidase, citrate lyase, glycogen phosphorylase, cholinesterase, penicillinase, hypoxanthine guanine phosphoribosyltransferase, cholinesterase, aminoacylase, aminotransferase, glucose isomerase, aspartase, penicillin amylase, fumarase, lactase, L-Asp b-decarboxylase, nitrile hydratase, a-glucosyltransferase Redox reactions of analytes such as glycerol, b-fructofuranosidase, lipase, maltooligosaccharide-forming enzyme, brewer's yeast, naringinase, papain, dehydrogenase (cells), acetate kinase, phosphodiesterase, creatinase and sarcosine oxidase A bio-related substance that promotes may be immobilized on the surface of the DLC film.
静電力、ファンデルワールス力、配位結合、水素結合及びインサーション等により検体を捕捉する化合物であって、捕捉された検体の量に応じて酸化還元物質の酸化還元電流を定量的に変化させる化合物がDLC膜の表面に固定されていてもよい。この場合、検体を捕捉する化合物により検体が捕捉されたときに、フェロセン等の酸化還元物質の酸化還元反応が促進又は抑制される。酸化還元物質の酸化還元電流値は捕捉される検体の量に応じて定量的に変化する。そして、捕捉される検体の量は試料中の検体濃度に比例する。したがって、電気化学反応に直接的には寄与しない検体であっても、所定の酸化還元物質の酸化還元電流値と検体の濃度との相関関係を表す検量線を予め作成しておけば、所定の酸化還元物質の存在下で試料中の濃度を検出することが可能になる。 A compound that captures a sample by electrostatic force, van der Waals force, coordination bond, hydrogen bond, insertion, etc., and quantitatively changes the redox current of the redox substance according to the amount of the captured sample The compound may be fixed on the surface of the DLC film. In this case, when the sample is captured by the compound that captures the sample, the oxidation-reduction reaction of a redox substance such as ferrocene is promoted or suppressed. The oxidation-reduction current value of the oxidation-reduction substance changes quantitatively according to the amount of analyte to be captured. The amount of the sample to be captured is proportional to the concentration of the sample in the sample. Therefore, even if the specimen does not directly contribute to the electrochemical reaction, if a calibration curve representing the correlation between the oxidation-reduction current value of the predetermined redox substance and the concentration of the specimen is created in advance, It becomes possible to detect the concentration in the sample in the presence of the redox substance.
DLC膜の場合、その表面に検体を捕捉する化合物を有機化学反応によって容易に固定することができる。また、DLC膜は、残余電流が少なく、金属電極、ガラス状炭素電極や高配向熱分解炭素電極と比較して検出感度が高いという利点も有している。 In the case of a DLC film, a compound that captures a specimen can be easily fixed on the surface by an organic chemical reaction. In addition, the DLC film has an advantage that the residual current is small and the detection sensitivity is higher than that of a metal electrode, a glassy carbon electrode or a highly oriented pyrolytic carbon electrode.
検体を捕捉する化合物の具体例としては、クラウンエーテル、チオ尿素、環状ポリアミド、α,α−Bis(N’−butylthioureylene)−m−xylene、α,α−Bis(N’−1−naphthylthioureylene)−m−xylene、2,7−Di−tert−butyl−9,9−dimethyl−4,5xanthenediylbiscarbamic acid dibenzyl ester、2,7−Di−tert−butyl−9,9−dimethyl−4,5−bis(N’−butylthioureeylene)−xanthene、2,7−Di−tert−butyl−9,9−dimethyl−4,5−bis(N’−phenylthioureylene)−xanthene、及び2,7−Di−tert−butyl−9,9−dimethyl−4,5−bis(N’−phenylthioureylene)−xanthene及びDNAが挙げられる。 Specific examples of the compound that captures the specimen include crown ether, thiourea, cyclic polyamide, α, α-Bis (N′-butylthioureylene) -m-xylene, α, α-Bis (N′-1-naphthylthioylene)- m-xylene, 2,7-Di-tert-butyl-9,9-dimethyl-4,5xanthenedylbiscarbamic acid dibenzyl ester, 2,7-Di-tert-butyl-9,9-dimethyl-4,5-bis (N '-Butylthioureylene) -xanthene, 2,7-Di-tert-butyl-9,9-dimethyl-4,5-bis (N'-phenylthioureylene)- Anthene, and 2,7-Di-tert-butyl-9,9-dimethyl-4,5-bis (N'-phenylthioureylene) -xanthene and DNA and the like.
第1の基板21は、作用電極2、対極3及び参照電極5を支持する支持体である。第1の基板21は、電気化学センサとしての使用に耐え得る物理的強度を有していればよい。具体的には、例えば、金属、プラスチック、セラミックス、及び紙等から形成された基板を第1の基板21(支持体)として用いることができる。プラスチックから形成されたプラスチック基板を用いることが好ましい。プラスチック基板の中でも、ポリエチレン及びポリプロピレンのようなオレフィン系高分子、ポリカーボネート、並びにポリエチレンテレフタレートから選ばれるプラスチックからなるプラスチック基板が好ましい。プラスチック基板はフィルムであってもよいし、不織布であってもよい。
The
対極3は、電気化学反応において通常用いられる電極用の導電性材料から構成される。好ましくは、対極3は、白金及び金のような貴金属、銀−塩化銀、又は水銀−塩化水銀から構成される。
The
参照電極5は、典型的には、銀−塩化銀、又は水銀−塩化水銀から構成される。参照電極5はペーストを用いる方法により形成することができる。
The
リード線2a,3a,5aは、銅等の導電性材料から構成され、メタルマスクを用いた通常の方法により形成することができる。
The
第2の基板22は、第1の基板21と同様の基板が用いられる。第1の基板21と第2の基板22は作用電極2等を間に挟んで接着剤により接着される。
As the
図4は、参照電極を備えていない電気化学センサの一実施形態を示す平面図である。図4に示す電気化学センサ1は、参照電極5及びこれに接続されるリード線5aが形成されていないことの他は、図3の電気化学センサ1と同様の構成を有する。
FIG. 4 is a plan view illustrating an embodiment of an electrochemical sensor that does not include a reference electrode. The
本発明に係る電気化学センサは以上説明したような実施形態に限定されるものではない。例えば、作用電極、対極及び参照電極を覆うゲル電解質膜が形成されていてもよい。これにより、アセトン、アンモニア等のガスを検体としてその酸化還元電流や濃度を測定することが可能になる。この場合、ゲル電解質は、検体を溶解すものであればよく、例えば、リン酸水素ニナトリウム−リン酸ニ水素カリウムによるpH7.4の緩衝溶液、又はホウ酸−ホウ砂によるpH8.4の緩衝溶液に寒天又はゼラチンを加えたものが挙げられる。ゲル電解質膜の厚みは、0.1〜20μm程度が好ましい。 The electrochemical sensor according to the present invention is not limited to the embodiment described above. For example, a gel electrolyte membrane that covers the working electrode, the counter electrode, and the reference electrode may be formed. As a result, it becomes possible to measure the oxidation-reduction current and concentration using a gas such as acetone or ammonia as a specimen. In this case, the gel electrolyte only needs to dissolve the specimen. For example, a buffer solution of pH 7.4 with disodium hydrogen phosphate-potassium dihydrogen phosphate, or a buffer of pH 8.4 with boric acid-borax. What added agar or gelatin to the solution is mentioned. The thickness of the gel electrolyte membrane is preferably about 0.1 to 20 μm.
電気化学センサシステム100を構成する制御部10は、例えば、作用電極2の参照電極5に対する電位を制御するポテンシオスタットと、作用電極2と対極3との間に流れる電流を計測する電流計と、ポテンシオスタット及び電流計を制御するプロセッサとから構成される。プロセッサ(CPU=中央演算装置)は、所定のソフトウエアを実行することにより、ポテンシオスタット及び電流計を制御する。ポテンシオスタットは、作用電極2の電位を検体固有の酸化還元電流が適切に検出されるような所定の電位に維持するように制御される。また、プロセッサは、所定の電位における検体の濃度と酸化電流値との関係に関する検量線を読み込んでこの検量線に基づいて検体の濃度を算出する。
The
図5は、検体の濃度を測定する方法の一実施形態を示すフロー図である。ステップS1では予め作成された検量線データがプロセッサに読み込まれる。ステップS2で作用電極を所定の電位Enに保持し、ステップS3で作用電極−対極間の電流値Inを電圧印加の開始から所定の時間tn秒後に測定する。ステップS4で電流値Inを読み込み、ステップS5で検量線からの内挿に基づいて検体の濃度Cが算出される。ステップS6で算出結果の妥当性を判断し、妥当であればステップS7で結果が表示される。算出結果が妥当でないと判断された場合、ステップS2に戻る。 FIG. 5 is a flow diagram illustrating one embodiment of a method for measuring the concentration of an analyte. In step S1, calibration curve data created in advance is read into the processor. The working electrode in step S2 is held at a predetermined potential E n, the working electrode in the step S3 - measuring a current value I n at a given time t n seconds after the start of the voltage application between the counter electrode. Reads the current value I n in step S4, the concentration C of the analyte is calculated based on interpolation from the calibration curve in step S5. In step S6, the validity of the calculation result is determined. If it is valid, the result is displayed in step S7. If it is determined that the calculation result is not valid, the process returns to step S2.
このような電気化学センサシステムによれば、検体固有の酸化還元電位を利用した電位設定により、複数の検体を分離して検出することが可能である。この点で本実施形態に係るシステムは、複数の検体を区別して検出することができない半導体式センサよりも優れる。 According to such an electrochemical sensor system, a plurality of specimens can be separated and detected by potential setting using a redox potential unique to the specimen. In this respect, the system according to this embodiment is superior to a semiconductor sensor that cannot distinguish and detect a plurality of specimens.
本実施形態に係るシステムによって検出される検体は、酸化還元反応を生じる化学物質であれば特に限定されないが、生体試料、環境試料、農工業試料又は食品試料中の多様な有機物又は無機物などを検体とすることができる。検体の具体例としては、グルコース、コレステロール、乳酸、クレアチニン、蛋白質、過酸化水素、アルコール、コレステロール、グルタミン酸、アルコールアミノ酸、アンモニア、トリメチルアミン、アセトン、エタン、ペンタン、水素、酸素、メタン、プロパン、ブタン、イソプレン、メルカプタン類、フェロセン、シトクローム、D−アミノ酸、ヘム、アミン、ガラクトース、HIF−1プロリン、キヌレニン、ユビキノール、リノール酸などの不飽和脂肪酸、グルタチオン、フェノール、カウレン、過酸化水素、コレステロール、コレステロールエステル、中性脂肪、尿素、アンモニア、尿酸、クレアチニン、クレアチン、ビリルビン、メチオニン、乳酸、ピルビン酸、クエン酸、キサンチン、ヒポキサンチン・グアニンホスホリボシルトランスフェラーゼ、コリンエステラーゼ、アセチル−DL−アミノ酸、フマル酸、ペニシリンG、L-アスパラギン、アクリロニトリル、ショ糖、DL−アスパラギン酸、液化デンプン、ADP及びザルコシンが挙げられる。これらの中でも、本実施形態に係るシステムは血液又は血清中のグルコース等の生体関連物質の濃度を決定するために用いられるときに特に有用である。 The specimen detected by the system according to the present embodiment is not particularly limited as long as it is a chemical substance that causes an oxidation-reduction reaction, but various organic or inorganic substances in biological samples, environmental samples, agricultural and industrial samples, or food samples are specimens. It can be. Specific examples of the sample include glucose, cholesterol, lactic acid, creatinine, protein, hydrogen peroxide, alcohol, cholesterol, glutamic acid, alcohol amino acid, ammonia, trimethylamine, acetone, ethane, pentane, hydrogen, oxygen, methane, propane, butane, Isoprene, mercaptans, ferrocene, cytochrome, D-amino acid, heme, amine, galactose, HIF-1 proline, quinurenin, ubiquinol, linoleic acid and other unsaturated fatty acids, glutathione, phenol, kaurene, hydrogen peroxide, cholesterol, cholesterol ester , Triglycerides, urea, ammonia, uric acid, creatinine, creatine, bilirubin, methionine, lactic acid, pyruvate, citric acid, xanthine, hypoxanthine and guanine phosphoribo Transferases, cholinesterase, acetyl -DL- amino, fumaric acid, penicillin G, L-asparagine, acrylonitrile, sucrose, DL-aspartic acid, liquefied starch, ADP and sarcosine. Among these, the system according to the present embodiment is particularly useful when used to determine the concentration of a biological substance such as glucose in blood or serum.
検体の他の具体例としては、上記以外の生体関連物質である、カフェイン及びテオフィリンのようなアルカロイド系物質、セロトニン、ヒスタミン、グルタチオン、テオフィリン(喘息治療薬)、ホモシステイン、グルタチオン、2-メルカプトエタンスルホン酸、セファレキシン、ナプロセン、NADH及びそれらの誘導体が挙げられる。更に、環境ホルモンとされるビスフェノールA、ダイオキシン前駆体であるクロロフェノール、めっき液添加剤であるポリエチレングリコール(PEG)及びビス3−スルホプロピルジスルフィド(SPS)、サッカリン、ブチンジオール等のジオール類が挙げられる。 Other specific examples of the specimen include biological related substances other than the above, alkaloid substances such as caffeine and theophylline, serotonin, histamine, glutathione, theophylline (asthma drug), homocysteine, glutathione, 2-mercapto Examples include ethanesulfonic acid, cephalexin, naprocene, NADH and derivatives thereof. Furthermore, diols such as bisphenol A, which is an environmental hormone, chlorophenol, which is a dioxin precursor, polyethylene glycol (PEG) and bis3-sulfopropyl disulfide (SPS), which are plating solution additives, saccharin, and butynediol. It is done.
以下、実施例を挙げて本発明についてより具体的に説明する。ただし、本発明は以下の実施例に限定されるものではない。 Hereinafter, the present invention will be described more specifically with reference to examples. However, the present invention is not limited to the following examples.
1.電気化学センサの作製とこれを用いた検体濃度の測定
実施例1
原料ガスとしてSi2H6及びCH4を用い、イオン化蒸着装置を使用してケイ素と炭素から構成される非晶質層(厚さ3μm)を0.25cm2のアルミニウム板上に形成させた。これを、対向して配置された1対の電極を備える真空成膜装置内に入れ、原料ガスとしてエタン及びピリジンを供給しながら電極間に13.56MHzの周波数を有する電圧を印加し、原料ガスをプラズマ化させた。プラズマ化された原料ガスから生成した炭素が非晶質層上に堆積し、作用電極としての導電性のDLC膜が形成された。ピリジンは水素ガスをキャリアガスとして用いて導入した。形成された作用電極の抵抗率は0.3Ωcm−1であった。作用電極と同様の条件で対極としてのDLC膜も形成させた。また、参照電極としての銀−塩化銀電極も形成させた。以上のようにして電気化学センサを作製した。
1. Example 1 Production of electrochemical sensor and measurement of analyte concentration using the same
Using Si 2 H 6 and CH 4 as source gases, an amorphous layer (
上記で作製した電気化学センサを、駆動用ソフトウェアが読み込まれたプロセッサにより制御されるポテンシオスタットに接続し、作用電極−対極間に流れる電流値が計測されるように電気化学センサシステムを構成した。 The electrochemical sensor system constructed as described above was connected to a potentiostat controlled by a processor loaded with driving software, and the current value flowing between the working electrode and the counter electrode was measured. .
尿酸及びアスコルビン酸を0.05Mリン酸水素ニナトリウム−リン酸ニ水素カリウムによるpH7.4の緩衝溶液に溶解して、尿酸の濃度が0.500mM、アスコルビン酸の濃度が1.0mMである試料溶液を調製した。ポテンシオスタットが接続された電気化学センサの作用電極、参照電極及び対極を試料溶液に浸し、参照電極に対する作用電極の電位を0.8Vに設定した。そのときの作用電極−対極間の電流を尿酸の酸化電流とみなしてその電流値を測定した。測定された尿酸の酸化電流値は0.080mA・cm−1であった。この酸化電流値から、尿酸濃度と酸化電流値との関係に関する検量線を読み込んだプロセッサにより、試料溶液の尿酸濃度は0.501mMと計算された。計算された濃度の実際の濃度に対する誤差は0.2%であった。 A sample in which uric acid and ascorbic acid are dissolved in a buffer solution of pH 7.4 with 0.05M disodium hydrogen phosphate-potassium dihydrogen phosphate, the concentration of uric acid is 0.500 mM, and the concentration of ascorbic acid is 1.0 mM A solution was prepared. The working electrode, reference electrode, and counter electrode of the electrochemical sensor to which the potentiostat was connected were immersed in the sample solution, and the potential of the working electrode with respect to the reference electrode was set to 0.8V. The current between the working electrode and the counter electrode at that time was regarded as the oxidation current of uric acid, and the current value was measured. The measured oxidation current value of uric acid was 0.080 mA · cm −1 . From this oxidation current value, the uric acid concentration of the sample solution was calculated to be 0.501 mM by a processor reading a calibration curve regarding the relationship between the uric acid concentration and the oxidation current value. The error of the calculated density with respect to the actual density was 0.2%.
比較例1
作用電極として白金板を用いたことの他は実施例1と同様の方法で尿酸の酸化電流値を測定したところ0.1322mA・cm−1であり、尿酸濃度は0.8248mMと計算された。誤差は64.8%であった。
Comparative Example 1
The oxidation current value of uric acid was measured by the same method as in Example 1 except that a platinum plate was used as the working electrode. As a result, it was 0.1322 mA · cm −1 and the uric acid concentration was calculated to be 0.8248 mM. The error was 64.8%.
比較例1のように作用電極として白金板を用いた場合、尿酸とアスコルビン酸の酸化電位が近接しており、これらの酸化電流に基づく電流ピークが重なって観測される。そのため、観測される酸化電流は尿酸だけでなくアスコルビン酸の酸化電流も含んでおり、これから求められる濃度も大きな誤差を含んでいた。これに対して、DLC膜を作用電極として用いた実施例1の場合、アスコルビン酸の酸化電位が高電位側にシフトし、尿酸の酸化電流を単独で観測可能であることから、尿酸濃度が高い精度で定量された。 When a platinum plate is used as the working electrode as in Comparative Example 1, the oxidation potentials of uric acid and ascorbic acid are close to each other, and current peaks based on these oxidation currents are observed to overlap. Therefore, the observed oxidation current includes not only uric acid but also ascorbic acid, and the concentration required from this also includes a large error. On the other hand, in the case of Example 1 using the DLC membrane as the working electrode, the oxidation potential of ascorbic acid shifts to the high potential side, and the oxidation current of uric acid can be observed alone, so the uric acid concentration is high. Quantified with accuracy.
実施例2
試料溶液にアスコルビン酸を投入しなかったこと以外は実施例1と同様にして測定を行ったところ、尿酸濃度は0.501mMと計算された。計算された濃度の実際の濃度に対する誤差は0.2%であった。
Example 2
When measurement was performed in the same manner as in Example 1 except that ascorbic acid was not added to the sample solution, the uric acid concentration was calculated to be 0.501 mM. The error of the calculated density with respect to the actual density was 0.2%.
比較例2
作用電極として白金板を用いたことの他は実施例2と同様にして測定を行ったところ、尿酸濃度は0.462mMと計算された。計算された濃度の実際の濃度に対する誤差は7.6%であった。白金板の場合、水の吸着による電気化学反応が起こり、これが残余電流として検出されたために誤差が大きくなったと考えられる。これに対して実施例2のようにDLC膜の場合は、白金板と比較して残余電流が少ないため高い検出精度が達成された。ガラス状炭素電極又は高配向熱分解炭素電極を用いて同様の実験を行った場合も、DLC膜と比較して誤差が大きかった。
Comparative Example 2
Measurement was performed in the same manner as in Example 2 except that a platinum plate was used as the working electrode, and the uric acid concentration was calculated to be 0.462 mM. The error of the calculated concentration with respect to the actual concentration was 7.6%. In the case of a platinum plate, an electrochemical reaction due to the adsorption of water occurred, and this was detected as a residual current. On the other hand, in the case of the DLC film as in Example 2, since the residual current is smaller than that of the platinum plate, high detection accuracy is achieved. When a similar experiment was performed using a glassy carbon electrode or a highly oriented pyrolytic carbon electrode, the error was larger than that of the DLC film.
実施例3
実施例1と同様の条件で、作用電極又は対極としてのDLC膜をポリカーボネート基板上に形成した。形成されたDLC膜上に、RFスパッタによりナノメータスケールの粒径を有する銅微粒子を堆積させた。銀及び塩化銀を含むペーストの印刷により参照電極を形成させた。また、リード線としての3本の銅配線パターンを、作用電極、対極又は参照電極にそれぞれ接続されるようにメタルマスクを用いて形成させた。そして、作用電極、対極及び参照電極と銅配線パターンの端部が露出するような窓が形成されたポリカーボネートフィルムを接着して、図3と同様の構成を有する電気化学センサを作製した。これに実施例1と同様にポテンシオスタットを接続して、電気化学センサシステムを構成した。
Example 3
Under the same conditions as in Example 1, a DLC film as a working electrode or a counter electrode was formed on a polycarbonate substrate. Copper fine particles having a nanometer-scale particle size were deposited on the formed DLC film by RF sputtering. A reference electrode was formed by printing a paste containing silver and silver chloride. Further, three copper wiring patterns as lead wires were formed using a metal mask so as to be connected to the working electrode, the counter electrode, or the reference electrode, respectively. And the electrochemical film which has the structure similar to FIG. 3 was adhere | attached by adhere | attaching the polycarbonate film in which the window in which the edge part of a working electrode, a counter electrode, a reference electrode, and a copper wiring pattern was exposed was adhere | attached. A potentiostat was connected to this in the same manner as in Example 1 to constitute an electrochemical sensor system.
グルコースを0.05Mリン酸水素ニナトリウム−リン酸ニ水素カリウムによるpH7.4の緩衝溶液に溶解して、グルコース濃度が5mMである試料溶液を調製した。試料溶液に上記で作成した電気化学センサの作用電極、対極及び参照電極を浸し、参照電極に対する作用電極の電位を0.7Vに設定した。そのときの作用電極−対極間の電流をグルコースの酸化電流とみなしてその電流値を測定した。測定されたグルコースの酸化電流値は14.2mA・cm−1であった。この酸化電流値から、グルコース濃度と酸化電流値との関係に関する検量線を読み込んだプロセッサにより、試料溶液のグルコース濃度は4.98mと計算された。計算された濃度の実際の濃度に対する誤差は0.4%であった。 Glucose was dissolved in a buffer solution of pH 7.4 with 0.05 M disodium hydrogen phosphate-potassium dihydrogen phosphate to prepare a sample solution having a glucose concentration of 5 mM. The working electrode, counter electrode, and reference electrode of the electrochemical sensor prepared above were immersed in the sample solution, and the potential of the working electrode with respect to the reference electrode was set to 0.7V. The current between the working electrode and the counter electrode at that time was regarded as the oxidation current of glucose, and the current value was measured. The measured glucose oxidation current value was 14.2 mA · cm −1 . From this oxidation current value, the glucose concentration of the sample solution was calculated to be 4.98 m by a processor reading a calibration curve relating to the relationship between the glucose concentration and the oxidation current value. The error of the calculated density with respect to the actual density was 0.4%.
比較例3
作用極に銅板を用いたこと以外は実施例3と同様に試料溶液におけるグルコースの酸化電流を測定したところ3.2mAであった。この酸化電流値からはグルコースの濃度は4.69mMと計算され、誤差は6.2%であった。
Comparative Example 3
The glucose oxidation current in the sample solution was measured in the same manner as in Example 3 except that a copper plate was used as the working electrode, and it was 3.2 mA. From this oxidation current value, the glucose concentration was calculated to be 4.69 mM, and the error was 6.2%.
実施例4
ポリカーボネート基板上にプラズマCVDによって導電性のDLC膜(厚さ0.5μm)を成膜し、そこにナノメータスケールの粒径を有する銅微粒子をRFスパッタによって付与した。その他は実施例3と同様にしてグルコース濃度が5mMである試料溶液について酸化電流を測定し、グルコース濃度を計算したところ4.99mMであり、誤差は0.3%であった。
Example 4
A conductive DLC film (thickness 0.5 μm) was formed on a polycarbonate substrate by plasma CVD, and copper fine particles having a nanometer-scale particle size were applied thereto by RF sputtering. Otherwise, the oxidation current was measured for the sample solution having a glucose concentration of 5 mM in the same manner as in Example 3, and the glucose concentration was calculated to be 4.99 mM with an error of 0.3%.
比較例4
メタノール:アセトン=1:9(体積比)の混合溶媒に酸化ホウ素を溶解させて調製した蒸発原料を水素キャリアガスとともに反応器内に導入し、13.56MHzの周波数で電圧を印加してプラズマ化させ、導電性ホウ素ドープダイヤモンド薄膜をポリカーボネート基板上に成膜することを試みた。しかし、ポリカーボネート基板の温度をポリカーボネートの融点である230℃以下では導電性ホウ素ドープダイヤモンド薄膜を成膜することができなかった。
Comparative Example 4
A vaporized raw material prepared by dissolving boron oxide in a mixed solvent of methanol: acetone = 1: 9 (volume ratio) is introduced into the reactor together with a hydrogen carrier gas, and a voltage is applied at a frequency of 13.56 MHz to form plasma. Thus, an attempt was made to form a conductive boron-doped diamond thin film on a polycarbonate substrate. However, when the temperature of the polycarbonate substrate is 230 ° C. or lower, which is the melting point of polycarbonate, a conductive boron-doped diamond thin film cannot be formed.
比較例5
ポリカーボネート基板に代えてp型(111)面Siウエハを使用したこと以外は比較例4と同様の方法でに導電性ホウ素ドープダイヤモンド薄膜(厚さ0.5μm)を成膜し、そこにナノメータスケールの粒径を有する銅微粒子をRFスパッタによって付与した。。これ以外は実施例3と同様にしてグルコース濃度が5mMである試料溶液について酸化電流を測定し、グルコース濃度を算出したところ4.98mMであり、誤差は0.5%であった。
Comparative Example 5
A conductive boron-doped diamond thin film (thickness 0.5 μm) was formed in the same manner as in Comparative Example 4 except that a p-type (111) plane Si wafer was used instead of the polycarbonate substrate, and the nanometer scale was formed there. Copper fine particles having a particle size of 5 mm were applied by RF sputtering. . Otherwise, the oxidation current was measured for the sample solution having a glucose concentration of 5 mM in the same manner as in Example 3, and the glucose concentration was calculated to be 4.98 mM with an error of 0.5%.
実施例5
銅微粒子に代えて酸化ルテニウム微粒子をRFスパッタによりDLC膜に付与したこと以外は実施例3と同様にして試料溶液のグルコース濃度を算出したところ、4.99mMであった。
Example 5
The glucose concentration of the sample solution was calculated in the same manner as in Example 3 except that ruthenium oxide fine particles were applied to the DLC film by RF sputtering instead of the copper fine particles.
実施例6
参照電極を形成せず、図4と同様の構成を有する電気化学センサを作製し、参照電極に代えて対極に対する電位によって作用電極を制御したこと以外は実施例3と同様の方法で試料溶液のグルコース濃度を測定したところ4.98mMであり、誤差は0.4%であった。
Example 6
An electrochemical sensor having the same configuration as in FIG. 4 was prepared without forming the reference electrode, and the sample solution was prepared in the same manner as in Example 3 except that the working electrode was controlled by the potential with respect to the counter electrode instead of the reference electrode. The glucose concentration was measured and found to be 4.98 mM, with an error of 0.4%.
実施例7
DLC膜を酸素プラズマ処理し、更に、アミノプロピルトリエトキシシランを80℃で反応させて、フタロシアニン修飾コバルトをDLC膜上に固定したことの他は実施例3と同様の電気化学センサシステムを構成した。これを用いて試料溶液のグルコース濃度を測定したところ、5.01mMであった。
Example 7
An electrochemical sensor system similar to that of Example 3 was configured except that the DLC film was treated with oxygen plasma and further aminopropyltriethoxysilane was reacted at 80 ° C. to fix the phthalocyanine-modified cobalt on the DLC film. . It was 5.01 mM when the glucose concentration of the sample solution was measured using this.
実施例8
DLC膜上にグルコースオキシターゼを固定したことの他は実施例3と同様にして、電気化学センサシステムを構成した。これを用いて試料溶液のグルコース濃度を測定したところ、5.00mMであった。
Example 8
An electrochemical sensor system was constructed in the same manner as in Example 3 except that glucose oxidase was immobilized on the DLC film. It was 5.00 mM when the glucose concentration of the sample solution was measured using this.
実施例9
実施例1と同様にして形成させたDLC膜の表面に、混酸(濃硝酸+濃硫酸)で処理してニトロ基を導入し、そのニトロ基を塩化錫を触媒としてエタノール中でアミノ基に還元した。次いで、アミノ基に2,7−Di−tert−butyl−9,9−dimethyl−4,5−bis)N’−phenylthioureylene)−xantheneを結合させて、検体を捕捉する機能が付加されたDLC膜が得られた。その後、0.05Mリン酸水素ニナトリウム−リン酸ニ水素カリウムによるpH7.4の緩衝溶液にゼラチン及びフェロセンを溶解させて溶解液を調製し、加熱された溶解液DLC膜の表面に厚さ50μmに塗布した。冷却後、酸化還元物質であるフェロセンを含有するゲル電解質膜がDLC膜上に形成された。
Example 9
The surface of the DLC film formed in the same manner as in Example 1 is treated with a mixed acid (concentrated nitric acid + concentrated sulfuric acid) to introduce a nitro group, and the nitro group is reduced to an amino group in ethanol using tin chloride as a catalyst. did. Subsequently, 2,7-Di-tert-butyl-9,9-dimethyl-4,5-bis) N'-phenylthiourelene) -xanthene is bound to the amino group, and a DLC film having a function of capturing the sample is added. was gotten. Thereafter, gelatin and ferrocene were dissolved in a buffer solution of pH 7.4 using 0.05 M disodium hydrogen phosphate-potassium dihydrogen phosphate to prepare a solution, and a thickness of 50 μm was formed on the surface of the heated solution DLC film. It was applied to. After cooling, a gel electrolyte film containing ferrocene as a redox substance was formed on the DLC film.
得られたDLC膜を用いて実施例1と同様の電気化学システムを構成した。DLC膜に10〜100ppmの濃度でアセトンガスを含む空気を接触させ、フェロセンの酸化電流を測定したところ、アセトンガスの濃度に比例してフェロセンの酸化還元電流値が低下した。すなわち、アセトンガスの濃度とフェロセンの酸化還元電流値との相関を示す検量線を作成すればアセトンガスの濃度を定量できることが確認された。 The electrochemical system similar to Example 1 was comprised using the obtained DLC film. When the DLC film was brought into contact with air containing acetone gas at a concentration of 10 to 100 ppm and the oxidation current of ferrocene was measured, the oxidation-reduction current value of ferrocene decreased in proportion to the concentration of acetone gas. That is, it was confirmed that the concentration of acetone gas could be quantified by creating a calibration curve showing the correlation between the concentration of acetone gas and the oxidation-reduction current value of ferrocene.
2.電気化学センサの洗浄性の検討
実施例4と比較例5でそれぞれ作製した電気化学センサを用い、グルコース濃度の測定と測定後の純水による洗浄を4回繰り返して行った。実施例4の場合、グルコース濃度の測定値は順に4.99、5.01、4.98及び5.02mMであり、安定していた。これに対して、ダイヤモンド薄膜を用いた比較例5の場合は順に5.02、5.03、5.05及び5.06mMであり、測定と洗浄を繰り返すのにしたがって測定誤差が明らかに大きくなる傾向が認められた。これは、ダイヤモンド薄膜の表面から洗浄により充分に試料溶液が除去できなかったことに起因すると考えられる。
2. Examination of Washability of Electrochemical Sensor Using the electrochemical sensors produced in Example 4 and Comparative Example 5, respectively, measurement of glucose concentration and washing with pure water after measurement were repeated four times. In the case of Example 4, the measured values of glucose concentration were 4.99, 5.01, 4.98, and 5.02 mM in order, and were stable. On the other hand, in the case of the comparative example 5 using a diamond thin film, it is 5.02, 5.03, 5.05, and 5.06 mM in order, and a measurement error becomes large clearly as measurement and washing are repeated. A trend was observed. This is considered to be because the sample solution could not be sufficiently removed from the surface of the diamond thin film by washing.
1…電気化学センサ、2…作用電極、3…対極、5…参照電極、10…制御部、21…第1の基板(支持体)、22…第2の基板、100…電気化学センサシステム。
DESCRIPTION OF
Claims (8)
該支持体上に形成された導電性のDLC膜からなる作用電極と、
対極と、を備え、
前記DLC膜のラマンスペクトルにおいて、1350cm−1付近のDisorderedバンドにピークが観測され、前記DLC膜の抵抗率が10−4Ωcm〜102Ωcmであり、
前記DLC膜が、イオン化蒸着法又は高周波プラズマCVD法によって形成されたDLC膜であり、
前記支持体がプラスチック基板であり、
測定後に洗浄して繰り返し使用される、電気化学センサ。 A support;
A working electrode made of a conductive DLC film formed on the support;
A counter electrode, and
In the Raman spectrum of the DLC film, a peak is observed in the Disordered band near 1350 cm −1 , and the resistivity of the DLC film is 10 −4 Ωcm to 10 2 Ωcm,
The DLC film is a DLC film formed by ionized vapor deposition or high-frequency plasma CVD,
Said support Ri plastic substrate der,
An electrochemical sensor that is cleaned and used repeatedly after measurement .
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