【発明の詳細な説明】産業上の利用分野本発明は、医療分野および一般家庭において使用し、血
液中のブドウ糖濃度を検知するハンディタイプの血糖測
定器に関するものである。DETAILED DESCRIPTION OF THE INVENTION Field of Industrial Application The present invention relates to a hand-held blood glucose meter that is used in the medical field and at home to detect the glucose concentration in blood.
従来の技術従来この種の電極系を用いた血糖測定器においては、測
定終了後、電極表面の付着物を水あるいはアルコール等
でふき取り洗浄していた。BACKGROUND OF THE INVENTION Conventionally, in a blood glucose meter using this type of electrode system, after the measurement is completed, the electrode surface is cleaned by wiping off deposits with water, alcohol, or the like.
発明が解決しようとする問題点しかし従来の水による電極洗浄方法においては、電極表
面に強固に付着した血液中の脂質、タンパク質等が完全
に除去されず、電極表面積が除々に減少するため、前記
酸化電流の応答が変化し、血糖測定値の変動となるため
、アルコール’Ｊ ｋ 用い電極表面の付着物を完全に
除去する必要があった。Problems to be Solved by the Invention However, in the conventional electrode cleaning method using water, lipids, proteins, etc. in blood that are firmly attached to the electrode surface are not completely removed, and the electrode surface area gradually decreases. Since the response of the oxidation current changes and the blood glucose measurement value fluctuates, it was necessary to completely remove the deposits on the electrode surface using alcohol'Jk.
そこで本発明は水のみのふき取りにより、電極表面の付
着物が完全に除去される電極作用を有する血糖測定器を
提供することを目的とする。SUMMARY OF THE INVENTION An object of the present invention is to provide a blood glucose meter having an electrode function in which deposits on the electrode surface can be completely removed by wiping with only water.
問題点を解決するための手段本発明は絶縁性の基板に設けた測定極と対極及び参照極
からなる電極系を用い、酵素と酸化型の電子受容体と血
中グルコースとを反応させ、生成した還元型の電子受容
体の濃度を前記電極系で酸化電流として検知して、血液
中のブドウ糖の濃度を測定する測定器において、前記酸
化電流検知後測定極と対極間に電圧を印加し水の電気分
解を行なう構成としたものである。Means for Solving the Problems The present invention uses an electrode system consisting of a measurement electrode, a counter electrode, and a reference electrode provided on an insulating substrate to react an enzyme, an oxidized electron acceptor, and blood glucose to generate In a measuring device that measures the concentration of glucose in blood by detecting the concentration of reduced electron acceptors as an oxidation current with the electrode system, after detecting the oxidation current, a voltage is applied between the measurement electrode and the counter electrode to The structure is such that electrolysis is carried out.
作 用この構成により、１ｌｌｌｌ定極、対極に発生するガス
により、電極表面に強固に密着した付着物は、電極から
離脱され、電極は水のみのふき取りにより表面の完全洗
浄が可能となるものである。Function: With this configuration, the gas generated at the constant electrode and the counter electrode removes deposits that adhere firmly to the electrode surface from the electrode, making it possible to completely clean the surface of the electrode by wiping it with water only. be.
実施例以下、本発明の実施例について、第１図〜第２図を参照
して説明する。第１図はブドウ糖と酵素とを反応させる
センサ一部である。絶縁性の基板１に白金を埋め込み測
定極２と対極３および参照極４からなる電極系を構成し
ている。この電極系を覆うように、保液層５．血球濾過
層６．パルプの不織布にグルコースオキシダーゼとフェ
リシアン化カリウム７を担持した反応層７を設置してい
る。この反応層に血液を添加すると、血液中のブドウ糖
は、グルコースオキシダーゼにより酸化され、同時にフ
ェリシアン化カリウムはフェロシアン化カリウムに還元
される。反応した血液は、血球濾過層６により血球分が
除去され、保液層６により電極上に保持される。フェロ
シアン化カリウムは、測定極を基準に参照極の電位を陰
極側に掃引することにより酸化し、酸化電流が流れる。Embodiments Hereinafter, embodiments of the present invention will be described with reference to FIGS. 1 and 2. FIG. 1 shows a part of a sensor that causes a reaction between glucose and an enzyme. An electrode system consisting of a measuring electrode 2, a counter electrode 3, and a reference electrode 4 is constructed by embedding platinum in an insulating substrate 1. A liquid retaining layer 5. Blood cell filtration layer6. A reaction layer 7 carrying glucose oxidase and potassium ferricyanide 7 is provided on a pulp nonwoven fabric. When blood is added to this reaction layer, glucose in the blood is oxidized by glucose oxidase, and at the same time potassium ferricyanide is reduced to potassium ferrocyanide. Blood cells from the reacted blood are removed by the blood cell filtration layer 6, and the blood is retained on the electrode by the liquid retaining layer 6. Potassium ferrocyanide is oxidized by sweeping the potential of the reference electrode toward the cathode based on the measurement electrode, and an oxidation current flows.
この酸化電流は生成したフェロシアン化カリウムの濃度
および血液中のブドウ糖濃度に対応している。This oxidation current corresponds to the concentration of potassium ferrocyanide produced and the glucose concentration in the blood.
第２図は本発明の測定器の回路図である。８は第１図の
センサ一部である。参照極は演算増巾器１００反転入力
端子に接続し、対極は演算増巾器１０の出力端子に接続
している。また測定極は演算増巾器１１の反転入力端子
に接続の後、抵抗１２を通し、演算増巾器１１の出力端
子１４と接続しポテンショスタットを構成している。セ
ンサ一部８に血液を添加の後、酵素と血液中のブドウ糖
との反応を行なった後、演算増巾器１０の非反転入力端
子９にＯ〜０．１ｖの間で鋸歯状に−ｏ、１Ｖ／秒の掃
引電圧を印加すると、測定極には前記酸化電流が流れる
。演算増巾器１１は抵抗１２により酸化電流値を電圧に
変換し出力端子１４に出力する。FIG. 2 is a circuit diagram of the measuring instrument of the present invention. 8 is a part of the sensor shown in FIG. The reference pole is connected to the inverting input terminal of the operational amplifier 100, and the counter electrode is connected to the output terminal of the operational amplifier 10. Further, the measurement pole is connected to the inverting input terminal of the operational amplifier 11, and then connected to the output terminal 14 of the operational amplifier 11 through the resistor 12 to form a potentiostat. After blood is added to the sensor part 8 and the enzyme reacts with glucose in the blood, a voltage of -o is applied to the non-inverting input terminal 9 of the operational amplifier 10 in a sawtooth manner between O and 0.1V. When a sweep voltage of 1 V/sec is applied, the oxidation current flows through the measurement electrode. The operational amplifier 11 converts the oxidation current value into a voltage using the resistor 12 and outputs it to the output terminal 14 .
酸化電流のピーク値は、生成したフェロシアン化カリウ
ムの濃度および血液中のブドウ糖濃度に対応シている。The peak value of the oxidation current corresponds to the concentration of the generated potassium ferrocyanide and the glucose concentration in the blood.
センサ一部８の洗浄は入力端子９の入力電圧をＯＶとし
た後、トランジスタ等で構成されたスイッチ１３を閉じ
、対極と測定極間に水が電気分解しつる電圧を印加する
。この結果陽極側の対極からは酸素ガスが、陰極側の測
定極からは水素ガスが発生し、電極表面の強固な付着物
を離脱させることができる。The sensor part 8 is cleaned by setting the input voltage of the input terminal 9 to OV, then closing the switch 13 made of a transistor or the like, and applying a voltage that causes water to electrolyze between the counter electrode and the measurement electrode. As a result, oxygen gas is generated from the counter electrode on the anode side, and hydrogen gas is generated from the measurement electrode on the cathode side, making it possible to remove stubborn deposits from the electrode surface.
なお上記実施例では測定極にスイッチ１３を入れ、水が
電気分解しうる電圧を印加したが、対極の電位を変化さ
せてもよく、要は対極と測定極間に水が電気分解しつる
電圧を印加し、発生するガスにより電極表面を洗浄しう
扛は良いものである。In the above example, the switch 13 was turned on to the measurement electrode to apply a voltage that would cause water to electrolyze. However, the potential of the counter electrode may be changed, and the point is to set the voltage that causes water to electrolyze between the counter electrode and the measurement electrode. It is a good idea to apply the gas and clean the electrode surface with the generated gas.
発明の効果以上のように本発明によれば、電極表面に強固に付着し
た血液中の脂質、タンパク質等の洗浄においてアルコー
ル等を必要とせず、水のみで簡単にふきとることができ
るものであり簡易操作の血糖測定器を提供することがで
きるものである。Effects of the Invention As described above, according to the present invention, there is no need for alcohol to clean lipids, proteins, etc. in blood that are firmly attached to the electrode surface, and it can be easily wiped off with water only. It is possible to provide an operable blood glucose meter.
第１図は本発明の一実施例による血糖測定器のセンサ一
部の断面図、第２図は同血糖測定器の回路図である。１・・・・基板、２・・・・・・測定極、３・・・・・
・対極、４・・・・・・参照極、７・・・・・・反応層
。FIG. 1 is a sectional view of a part of a sensor of a blood glucose meter according to an embodiment of the present invention, and FIG. 2 is a circuit diagram of the same blood glucose meter. 1... Board, 2... Measuring pole, 3...
- Counter electrode, 4...Reference electrode, 7...Reaction layer.
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60224538AJPS6283649A (en) | 1985-10-08 | 1985-10-08 | blood sugar meter |
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60224538AJPS6283649A (en) | 1985-10-08 | 1985-10-08 | blood sugar meter |
| Publication Number | Publication Date |
|---|---|
| JPS6283649Atrue JPS6283649A (en) | 1987-04-17 |
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP60224538APendingJPS6283649A (en) | 1985-10-08 | 1985-10-08 | blood sugar meter |
| Country | Link |
|---|---|
| JP (1) | JPS6283649A (en) |
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