JP4418435B2 - 電気化学的バイオセンサー - Google Patents
電気化学的バイオセンサー Download PDFInfo
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- JP4418435B2 JP4418435B2 JP2006027017A JP2006027017A JP4418435B2 JP 4418435 B2 JP4418435 B2 JP 4418435B2 JP 2006027017 A JP2006027017 A JP 2006027017A JP 2006027017 A JP2006027017 A JP 2006027017A JP 4418435 B2 JP4418435 B2 JP 4418435B2
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- 235000013305 food Nutrition 0.000 description 1
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- 125000002791 glucosyl group Chemical group C1([C@H](O)[C@@H](O)[C@H](O)[C@H](O1)CO)* 0.000 description 1
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- DCYOBGZUOMKFPA-UHFFFAOYSA-N iron(2+);iron(3+);octadecacyanide Chemical compound [Fe+2].[Fe+2].[Fe+2].[Fe+3].[Fe+3].[Fe+3].[Fe+3].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-] DCYOBGZUOMKFPA-UHFFFAOYSA-N 0.000 description 1
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- KHPXUQMNIQBQEV-UHFFFAOYSA-N oxaloacetic acid Chemical compound OC(=O)CC(=O)C(O)=O KHPXUQMNIQBQEV-UHFFFAOYSA-N 0.000 description 1
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- 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
- C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
- C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose
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- 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
- G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
- G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
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- G—PHYSICS
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- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
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Description
(1) ブドウ糖 + GOx-FAD →グルコン酸 + GOx-FADH2
(2) GOx-FADH2 + 電子伝達媒介体(酸化状態) →GOx-FAD + 電子伝達媒介体(還元状態)
血糖を測定するためのバイオセンサーは次のような構成を有する。
Y = -72.23 + 0.58691X - 0.00084073 X2 - 1.1211x10-6 X3 + 5.7521x10-9 X4 - 9.1172x10-12 X5
(1)ストリップが挿入された測定器に血液試料が流入する(工程1)。
[実施例]
塩化ヘキサアミンルテニウム(III)30mg(41.6重量%)とカルボキシメチルセルロース(carboxy methyl cellulose)1mg(1.4重量%)、トリトンX-100(1.4重量%)1mg、そしてグルコ−スオキシダーゼ40mg(55.6重量%)を含んだ混合物を、pH6.4の1mlPBS緩衝溶液に溶解して、溶液内に残っている微粒子は濾して除去した。前記得られた試薬溶液を空気圧縮分注器(EFD XL100)の注射器内に保管した。
塩化ヘキサアミンルテニウム(III)30mg(23.6重量%)とカルボキシメチルセルロース(carboxy methyl cellulose)1mg(0.8重量%)、ポリビニルピロリドン(polyvinyl pyrrolidone; PVP)5mg(4重量%)、トリトンX-100 1mg(0.8重量%)、ラウリン酸(lauric acid)20mg(15.7重量%)、臭化ミリスチルトリメチルアンモニウム(myristyltrimethylammonium bromide)30mg(23.6重量%)、そしてグルコ−スオキシダーゼ40mg(31.5重量%)を含んだ混合物をpH6.4 の1mlPBS緩衝溶液に溶解して、溶液内に残っている微粒子は濾して除去した。前記得られた試薬溶液を空気圧縮分注器(EFD XL100)の注射器内に保管した。
図2乃至図3a、図3bの補助電極105を薄層電気化学セル形バイオセンサーの基準電極に使用した。血糖値測定用薄層電気化学セルは次のように製造する。
ストリップセンサー509が挿入された測定器500に採取した血液試料を投入すると(工程1)、作動電極104と補助電極105間及び流動感知電極107と補助電極105間に一定な電位差が与えられ(工程2)、ストリップの試料導入部を通じて流入された前記試料が作動電極104と補助電極105間に1次電気的変化を誘発し、前記電極間の電圧を同じに調整するようになり(工程3)、流動感知電極107が前記試料の流動を感知して2次電気的変化を起こして前記補助電極105と流動感知電極107間の電圧を同じに調整することにより作動電極104で1次感知された電気的変化との時間差の情報を提供し(工程4)、血液試料と作動電極104に溶解した試薬が充分に混ざると再び作動電極104と補助電極105間に200mVの電圧が印加され対面形薄層電気化学セル内循環反応(cycling reaction)を起こした後、到達した正常電流値を読んだ後(工程5)、工程4で得た時間情報と工程5で得た正常電流値を利用して試料内に存在する基質の量を測定することにより(工程6)血糖を測定した。
実施例3によって製作された対面形電極を使用してお互いに異なる走査速度による循環電圧電流度を調べてみた。
実施例3により製作された対面形電極と電極が一枚の絶縁体上に形成された平面形電極の対時間電流法的感応比較結果を下記に示す。
実施例3により製作された平均値0.5μl試料導入部100を有する対面形グルコースセンサーでのグルコース、アスコルビン酸、アセトアミノフェン及び尿酸等の妨害物質及び緩衝溶液に対する影響を測定した。
実施例3により製作された対面形グルコースセンサーを利用してグルコース標準溶液に対する検定テストを行なった。
実施例3により製作された流動感知電極が具備した対面形グルコースセンサーを利用して血液流動性測定とヘマトクリット値の影響補正テストを行なった。
Y = -72.23 + 0.58691X - 0.00084073 X2 - 1.1211x10-6 X3 + 5.7521x10-9 X4 - 9.1172x10-12 X5
実施例3によりバイオストリップセンサーを製作した。ヘパリン(heparin;血液凝固防止剤)で処理した全血試料は血漿とヘマトクリットに遠心分離機を利用して分離して、20、40、60%の三種類の異なるヘマトクリット値の血液試料を得るために再び混合した。
102:通気部 103:余裕空間部
104:作動電極 105:補助電極または基準電極
106:電極連結部 107:流動感知電極
108:バイオセンサー確認電極 200:中間基板
300:上部基板 301:試料確認窓
400:下部基板 500:血糖値測定器
501:測定器本体 503:液晶表示パネル
505:電源スイッチ 507:操作スイッチ
509:上向ストリップ 511:ストリップ挿入口
Claims (13)
- 一枚の平面絶縁板にコーティングされた作動電極と;前記作動電極と同じ平面または異なる一枚の平面絶縁板で一定間隔離隔している注入試料の流動性を感知する流動感知電極と;前記作動電極と対向する異なる一枚の平面絶縁板上にコーティングされた補助電極と;微細流路が形成された試料導入部を具備し、前記作動電極と前記補助電極を一定間隔隔離させて圧着させる粘着性隔離板と;導体物質を厚く積層構造で印刷して補助電極と次元的に連結される部位が形成され前記作動電極と補助電極を連結させる電極連結部;及び電子伝達媒介体と酸化酵素を含んだ反応試薬層からなる対面形の薄層電気化学セルを具備した電気化学的バイオセンサーを使用して、(1)ストリップセンサーが挿入された測定器に採取した血液試料を投入する工程;(2)作動電極と補助電極間及び流動感知電極と補助電極間に一定な電位差を与える工程;(3)前記試料の流入が作動電極と補助電極間に1次電気的変化を誘発して前記電極間の電圧を同じに調整する工程;(4)流動感知電極が前記試料の流動を感知して2次電気的変化を起こして前記補助電極と流動感知電極間の電圧を同じに調整することにより作動電極で1次感知された電気的変化との時間差の情報を提供する工程;(5)血液試料と作動電極に溶解した試薬が充分に混ざると再び作動電極と補助電極間に所定の電圧が印加され、対面形薄層電気化学セル内循環反応(cycling reaction)を起こした後、到達した正常電流値をよむ工程;及び(6)工程4で得た時間情報と工程5で得た正常電流値を利用して試料内に存在する基質の量を測定する工程からなることを特徴とする、電気化学的バイオセンサーを利用して血糖を測定する方法。
- 工程1の血液試料が、前処理過程なしに0.1〜0.7μlの少量試料がストリップセンサーに導入されることを特徴とする、請求項1記載の測定方法。
- 工程1の電位差が、作動電極と補助電極、流動感知電極と補助電極間に直流、低周波交流または高周波交流、高インピーダンスまたは矩形波、三角波、半正弦波及びガウス波の中から選択されたパルスの変化で誘発されることを特徴とする、請求項1記載の測定方法。
- 前記電気的変化が、電圧、電流、インピーダンスまたはキャパシタンスの変化によるものであることを特徴とする、請求項1記載の測定方法。
- 前記バイオセンサー中の試料導入部には、幅0.5〜2mmで高さ50〜250μmを有する流路が形成され、試料の導入を容易にしたことを特徴とする、請求項1記載の測定方法。
- 工程3の電極間の電圧を同じに調整することにより、前記試料と反応試薬層間の酸化還元反応を数秒間抑制することを特徴とする、請求項1記載の測定方法。
- 前記バイオセンサー内酵素と電子伝達媒介体を含んだ反応試薬層が、作動電極及び補助電極中のいずれか一方の電極にだけ形成して、速い反応が起きるようにしたことを特徴とする、請求項1記載の測定方法。
- 前記酵素が、グルコ−スオキシダーゼまたは糖脱水素化酵素であることを特徴とする、請求項7記載の測定方法。
- 前記電子伝達媒介体が、塩化ヘキサアミンルテニウム(III)で電子伝達を容易にしたことを特徴とする、請求項7記載の測定方法。
- 前記反応試薬層が、脂肪酸及び4級アンモニウム塩を付加的に含んでヘマトクリット値差による依存性向をさらに減少させたことを特徴とする、請求項7記載の測定方法。
- 前記脂肪酸が、C4〜C20の鎖を有する塩として、カプロン酸、ヘプタン酸、カプリル酸、ノナン酸、カプリン酸、ウンデカン酸、ラウリン酸、トリデカン酸、ミリスチン酸、ペンタデカン酸、パルミチン酸、ヘプタデカン酸、ステアリン酸、ノナデカン酸及びアラキジン酸からなる群から選択され、固体状態の組成物に対して、0.1〜20重量%含まれることを特徴とする、請求項10記載の測定方法。
- 前記4級アンモニウム塩が、ドデシルトリメチルアンモニウム、エシルトリメチルアンモニウム、マイリスチルトリメチルアンモニウム、セチルトリメチルアンモニウム、オクタデシルトリメチルアンモニウム及びテトラヘキシルアンモニウム等のハロゲン化合物からなる群から選択され、固体状態の組成物に対して0.1〜30重量%含むことを特徴とする、請求項10記載の測定方法。
- 前記バイオセンサー内感応膜組成物が、作動電極及び流動感知電極中のいずれか一方の電極または前記すべての電極に形成され、前記電極間間隔が正常電流時間常数が0.05乃至8.0の範囲で調節され速い反応を助けるよう配列されることを特徴とする、請求項1記載の測定方法。
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US8057404B2 (en) * | 2005-10-12 | 2011-11-15 | Panasonic Corporation | Blood sensor, blood testing apparatus, and method for controlling blood testing apparatus |
US8114269B2 (en) * | 2005-12-30 | 2012-02-14 | Medtronic Minimed, Inc. | System and method for determining the point of hydration and proper time to apply potential to a glucose sensor |
TW200813429A (en) * | 2006-09-01 | 2008-03-16 | Gen Life Biotechnology Co Ltd | Sensor for inspecting the total cholesterol in blood sample |
EP2058651B1 (en) * | 2006-10-19 | 2015-09-02 | Panasonic Healthcare Holdings Co., Ltd. | Method for measuring hematocrit value of blood sample, method for measuring concentration of analyte in blood sample, sensor chip and sensor unit |
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