JPS63135131A - Percataneous sensor - Google Patents
Percataneous sensorInfo
- Publication number
- JPS63135131A JPS63135131A JP61281786A JP28178686A JPS63135131A JP S63135131 A JPS63135131 A JP S63135131A JP 61281786 A JP61281786 A JP 61281786A JP 28178686 A JP28178686 A JP 28178686A JP S63135131 A JPS63135131 A JP S63135131A
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- glucose
- skin
- sensor
- hydrogen peroxide
- 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.)
- Pending
Links
- 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 claims description 37
- 239000008103 glucose Substances 0.000 claims description 37
- MHAJPDPJQMAIIY-UHFFFAOYSA-N Hydrogen peroxide Chemical compound OO MHAJPDPJQMAIIY-UHFFFAOYSA-N 0.000 claims description 26
- 239000001301 oxygen Substances 0.000 claims description 17
- 229910052760 oxygen Inorganic materials 0.000 claims description 17
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 claims description 16
- 210000004243 sweat Anatomy 0.000 claims description 14
- 239000000126 substance Substances 0.000 claims description 13
- 239000012528 membrane Substances 0.000 claims description 12
- 108010093096 Immobilized Enzymes Proteins 0.000 claims description 5
- 108090000790 Enzymes Proteins 0.000 claims description 4
- 102000004190 Enzymes Human genes 0.000 claims description 4
- 108010015776 Glucose oxidase Proteins 0.000 claims description 4
- 239000004366 Glucose oxidase Substances 0.000 claims description 4
- 229940088598 enzyme Drugs 0.000 claims description 4
- 229940116332 glucose oxidase Drugs 0.000 claims description 4
- 235000019420 glucose oxidase Nutrition 0.000 claims description 4
- 238000010438 heat treatment Methods 0.000 claims description 4
- 239000003638 chemical reducing agent Substances 0.000 claims description 3
- 108090000854 Oxidoreductases Proteins 0.000 claims description 2
- 102000004316 Oxidoreductases Human genes 0.000 claims description 2
- 239000013076 target substance Substances 0.000 claims 1
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 18
- 239000008280 blood Substances 0.000 description 14
- 210000004369 blood Anatomy 0.000 description 14
- 229910052697 platinum Inorganic materials 0.000 description 9
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 7
- 239000011810 insulating material Substances 0.000 description 7
- 229910052709 silver Inorganic materials 0.000 description 7
- 239000004332 silver Substances 0.000 description 7
- 238000005259 measurement Methods 0.000 description 6
- LCTONWCANYUPML-UHFFFAOYSA-N Pyruvic acid Chemical compound CC(=O)C(O)=O LCTONWCANYUPML-UHFFFAOYSA-N 0.000 description 4
- 239000007789 gas Substances 0.000 description 4
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 239000011148 porous material Substances 0.000 description 4
- 239000003792 electrolyte Substances 0.000 description 3
- 230000002452 interceptive effect Effects 0.000 description 3
- CIWBSHSKHKDKBQ-JLAZNSOCSA-N Ascorbic acid Chemical compound OC[C@H](O)[C@H]1OC(=O)C(O)=C1O CIWBSHSKHKDKBQ-JLAZNSOCSA-N 0.000 description 2
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 2
- LEHOTFFKMJEONL-UHFFFAOYSA-N Uric Acid Chemical compound N1C(=O)NC(=O)C2=C1NC(=O)N2 LEHOTFFKMJEONL-UHFFFAOYSA-N 0.000 description 2
- TVWHNULVHGKJHS-UHFFFAOYSA-N Uric acid Natural products N1C(=O)NC(=O)C2NC(=O)NC21 TVWHNULVHGKJHS-UHFFFAOYSA-N 0.000 description 2
- 210000004204 blood vessel Anatomy 0.000 description 2
- 230000006866 deterioration Effects 0.000 description 2
- 206010012601 diabetes mellitus Diseases 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000001727 in vivo Methods 0.000 description 2
- 208000015181 infectious disease Diseases 0.000 description 2
- 235000014655 lactic acid Nutrition 0.000 description 2
- 239000004310 lactic acid Substances 0.000 description 2
- 229960000448 lactic acid Drugs 0.000 description 2
- 230000003340 mental effect Effects 0.000 description 2
- 210000000496 pancreas Anatomy 0.000 description 2
- 229940107700 pyruvic acid Drugs 0.000 description 2
- 230000035900 sweating Effects 0.000 description 2
- 239000002470 thermal conductor Substances 0.000 description 2
- 229940116269 uric acid Drugs 0.000 description 2
- 229920000742 Cotton Polymers 0.000 description 1
- 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
- 239000004593 Epoxy Substances 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
- XSQUKJJJFZCRTK-UHFFFAOYSA-N Urea Chemical compound NC(N)=O XSQUKJJJFZCRTK-UHFFFAOYSA-N 0.000 description 1
- 235000010323 ascorbic acid Nutrition 0.000 description 1
- 229960005070 ascorbic acid Drugs 0.000 description 1
- 239000011668 ascorbic acid Substances 0.000 description 1
- 239000004202 carbamide Substances 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 229910002092 carbon dioxide Inorganic materials 0.000 description 1
- 238000007796 conventional method Methods 0.000 description 1
- 239000000174 gluconic acid Substances 0.000 description 1
- 235000012208 gluconic acid Nutrition 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 201000001421 hyperglycemia Diseases 0.000 description 1
- 229910052741 iridium Inorganic materials 0.000 description 1
- GKOZUEZYRPOHIO-UHFFFAOYSA-N iridium atom Chemical compound [Ir] GKOZUEZYRPOHIO-UHFFFAOYSA-N 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Landscapes
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は生化学センサにかかわり、特に生体内グルコー
スを無侵襲に体表面から測定するグルコース測定装置、
あるいは人口膵臓などの糖尿病治療に好適な経皮センサ
に関するものである。[Detailed Description of the Invention] [Industrial Application Field] The present invention relates to a biochemical sensor, and particularly to a glucose measuring device that non-invasively measures in-vivo glucose from the body surface;
Alternatively, the present invention relates to a transcutaneous sensor suitable for diabetes treatment such as an artificial pancreas.
従来の生体内グルコース濃度の連続測定では。 In conventional continuous measurement of glucose concentration in vivo.
グルコースセンサを血管内あるいは組織内に挿入する（
特開昭５９−８９３９号、特開昭５９−８９６９号、特
開昭５９−１４８４３号、特開昭５９−１４８５７号）
か、血管内へ挿入したカテーテルから体外へ導いた血液
にセンサを接する（特開昭５２−１３５５９９号、特開
昭５４−８２８８５号）かの方法がとられていた。また
、間欠的なグルコース濃度の測定は、採血後センサで測
定している。Inserting the glucose sensor into a blood vessel or tissue (
JP-A-59-8939, JP-A-59-8969, JP-A-59-14843, JP-A-59-14857)
Alternatively, a method has been used in which a sensor is brought into contact with blood led outside the body from a catheter inserted into a blood vessel (Japanese Patent Laid-Open Nos. 52-135599 and 1982-82885). In addition, intermittent glucose concentration measurements are performed using a sensor after blood collection.
一方、グルコース以外では、体表面から無侵襲、すなわ
ち経皮的に血中ガス分圧を測定できることが知られてい
る（特開昭５０−１４１１８６号、特開昭５３−１３７
５９０号、特開昭５４−６０７８８号など）。On the other hand, for gases other than glucose, it is known that blood gas partial pressure can be measured non-invasively, that is, transcutaneously, from the body surface (Japanese Patent Laid-Open Nos. 50-141186, 1983-137).
No. 590, JP-A-54-60788, etc.).
上記従来技術のうちグルコース測定については。 Among the above conventional techniques, regarding glucose measurement.
感染、精神的・肉体的苦痛、失血、生体成分付着による
センサの性能劣化、間欠的測定による情報不足などの問
題があった。また、無侵襲測定においては、対象が酸素
や炭酸ガスなどの気体、揮発性物質のみという問題があ
った。There were problems such as infection, mental and physical pain, blood loss, deterioration of sensor performance due to adhesion of biological components, and lack of information due to intermittent measurements. Another problem with non-invasive measurement is that it targets only gases and volatile substances such as oxygen and carbon dioxide.
本発明の目的は、ガス以外の生化学物質２例えばグルコ
ースを無侵襲に測定する経皮センサを提供し、患者に与
える負担を軽減することにある。An object of the present invention is to provide a transdermal sensor that noninvasively measures biochemical substances other than gases, such as glucose, and to reduce the burden on patients.
上記目的は、酸素あるいは過酸化水素を測定するポーラ
ログラフ電極とオキシダーゼ系の固定化酵素を含む酵素
電極において、該ｆｆｔ極が皮膚に装着できるような構
造を有し、発汗の手段として皮膚を加温する加温機構を
有し、浸出する汗に含まれる測定対象物質と反応する前
記固定化酵素膜の面積が０．５〜１００ａｊであり、酸
素電極の陰極あるいは過酸化水素電極の陽極を蛇行状と
して、陽極、陰極、絶縁物質から成るポーラログラフ電
極面全体に分布するような形状とすることにより、達成
される。なお、熱源が経皮センサの外部にある時は、加
温機構は不要である。The above purpose is to provide a polarographic electrode for measuring oxygen or hydrogen peroxide and an enzyme electrode containing an oxidase-based immobilized enzyme, with the fft electrode having a structure that can be attached to the skin, and heating the skin as a means of sweating. The immobilized enzyme membrane has an area of 0.5 to 100 aj and reacts with the substance to be measured contained in the exuded sweat, and the cathode of the oxygen electrode or the anode of the hydrogen peroxide electrode is connected in a meandering manner. This is achieved by creating a shape that is distributed over the entire surface of a polarographic electrode consisting of an anode, a cathode, and an insulating material. Note that when the heat source is outside the transcutaneous sensor, no heating mechanism is required.
汗のグルコース濃度と血糖値が類似の変化を示すことが
知られており、これは雑誌「糖尿病」第２８巻第１１号
（１９８５）の第１２７１頁から１２７３頁の論文に詳
しい。It is known that sweat glucose concentration and blood sugar level show similar changes, and this is detailed in the article in the journal "Diabetes", Vol. 28, No. 11 (1985), pages 1271 to 1273.
汗のグルコース濃度を測定すれば、体内のグルコース濃
度を経皮的に測定できるが、汗のグルコース濃度は血糖
と比べると極めて低い、従って、従来のグルコース電極
を体表面に装着できるようにするだけでは、血糖値の約
千分の３のグルコース濃度を検出できない、そこで、発
汗により排出されるグルコースを広い領域にわたって採
取し。Measuring the glucose concentration in sweat allows transdermal measurement of the glucose concentration in the body, but the glucose concentration in sweat is extremely low compared to blood sugar, so conventional glucose electrodes can only be attached to the body surface. However, this method cannot detect a glucose concentration that is approximately three thousandths of the blood sugar level, so glucose excreted through sweat was collected over a wide area.
高効率に電流に交換するために、電極の反応面を体表面
に装着できる範囲内でできる限り広面積化し、かつポー
ラログラフ電極面の物質を消費する電極、すなわち酸素
電極では陰極、過酸化水素電極では陽極を広域設置する
。また、前記の陰極あるいは陽極の総面積に比例する暗
電流による雑音を少なくし、Ｓ／Ｎ比を向上することも
必要である。このため、前記の陰極あるいは陽極を線幅
が２１！Ｉ１１以下の蛇行状としてポーラログラフ電極
面全体に形成した。In order to exchange current with high efficiency, the reaction surface of the electrode should be made as wide as possible within the range that can be attached to the body surface, and the electrode that consumes the substance on the polarographic electrode surface, that is, the cathode for the oxygen electrode, and the cathode for the hydrogen peroxide electrode. Now we will install anodes over a wide area. It is also necessary to reduce noise due to dark current, which is proportional to the total area of the cathode or anode, and to improve the S/N ratio. For this reason, the line width of the above-mentioned cathode or anode is 21! A meandering shape of I11 or less was formed over the entire surface of the polarographic electrode.
第２図は経皮グルコースセンサの構成を示す概略断面図
の一例であるが、グルコースを例にとつ−て経皮センサ
の動作を説明する。経皮グルコースセンサは白金電極１
．銀電極２．絶縁物質３．多孔質物ｇＩｔ４、固定化グ
ルコースオキシダーゼ膜５、還元性物質除去膜６．電解
液７、温度センサ８゜ヒータ９、熱の良導体１０．゛断
熱材１１、リード線１２，１３．１４から構成され、皮
膚１５の上に装着される。サーミスタなどの温度センサ
８、ヒータ９．熱の良導体１０、リード線１３と１４は
皮膚１５の加温機構を構成して発汗を生じさせるが、全
身加温や運動などによる全身の温熱性発汗時にはこれら
は不要である。浸出する汗を多孔質物［４に吸収・還流
させ、常に新しい汗をグルコースセンサ表面に維持する
ことができる。この結果、血糖値と対応して変化する汗
のグルコース濃度を体表面上のグルコースセンサで測定
し、無侵襲に血糖値を知ることができる。上記グルコー
スセンサは白金電極１、銀電極２．エポキシ樹脂などの
絶縁物質３．固定化グルコースオキシダーゼ膜５．還元
性物質除去膜６、電解液７．リード綿１２から成るが、
以下の手順によりグルコースが電流に変換される。まず
、多孔質物質４に含有される汗のグルコース（ＣＢＨｉ
ｘ Ｏｓ ） ：、酸素、水は固定化グルコースオキシ
ダーゼ膜５の中で、酵素の働きで１次の化学反応により
グルコン酸ＣＣｅＨ１ｔ Ｏ７）と過酸化水素（Ｈｘ
Ｏｚ ）を生ずる。FIG. 2 is an example of a schematic sectional view showing the configuration of a transcutaneous glucose sensor, and the operation of the transcutaneous sensor will be explained using glucose as an example. Transcutaneous glucose sensor has platinum electrode 1
．． Silver electrode 2. Insulating material 3. Porous material gIt4, immobilized glucose oxidase membrane 5, reducing substance removal membrane 6. Electrolyte 7, temperature sensor 8° heater 9, good thermal conductor 10. ``It is composed of a heat insulating material 11, lead wires 12, 13, and 14, and is worn on the skin 15. Temperature sensor 8 such as a thermistor, heater 9. The thermal conductor 10 and the lead wires 13 and 14 constitute a heating mechanism for the skin 15 and cause sweating, but they are not necessary when the whole body is heated and sweats due to exercise. The leached sweat is absorbed and refluxed into the porous material [4], and new sweat can be constantly maintained on the surface of the glucose sensor. As a result, the glucose concentration in sweat, which changes in accordance with the blood sugar level, can be measured with a glucose sensor on the body surface, and the blood sugar level can be determined non-invasively. The glucose sensor has a platinum electrode 1, a silver electrode 2. Insulating materials such as epoxy resin3. Immobilized glucose oxidase membrane5. Reducing substance removal membrane 6, electrolyte 7. Consists of 12 lead cotton,
Glucose is converted into electrical current by the following procedure. First, sweat glucose (CBHi) contained in the porous material 4
xOs): Oxygen and water are converted into gluconic acid CCeH1tO7) and hydrogen peroxide (Hx
oz).
Ｃ５ＨｔｚＣ）ａ＋ｏｚ＋Ｈｚｏ→ＣｅＨｘｚＯ７＋Ｈ
ｚＯｚ （１）ポーラログラフ電極では、発生する過酸
化水素か、消費される酸素を測定することでグルコース
濃度を知ることができる。妨害物質除去膜６は尿素、ア
スコルビン酸などの妨害物質を除去する反面、測定対象
となる物質を通す。C5HtzC) a+oz+Hzo→CeHxzO7+H
(1) With a polarographic electrode, the glucose concentration can be determined by measuring the hydrogen peroxide generated or the oxygen consumed. The interfering substance removal membrane 6 removes interfering substances such as urea and ascorbic acid, while allowing the substance to be measured to pass through.
過酸化水素電極として働かせるには、白金電極１を陽極
とし、銀電極２を陰極として、両極間に０．６〜０．８
ｖの電圧を印加する。陽極上では。In order to work as a hydrogen peroxide electrode, the platinum electrode 1 is used as an anode and the silver electrode 2 is used as a cathode, with a gap of 0.6 to 0.8 between the two electrodes.
Apply a voltage of v. on the anode.
過酸化水素が次式により酸化され。Hydrogen peroxide is oxidized according to the following equation.
２ＨｘＯｘ→４Ｈ＋＋２０ｘ＋４ｅ−（２）となり、陰
極上では。酸素が次式により還元され。2HxOx→4H++20x+4e-(2) on the cathode. Oxygen is reduced by the following equation.
４Ｈ＋＋Ｏｚ→２ＨｔＯ−４ｇ−（３）となる。4H++Oz→2HtO-4g-(3).
酸素電極として働かせるには、白金電極１を陰極、銀電
極２を陽極として、両極間に０．６〜０．８ｖの電圧を
印加する。陽極上では、銀が次式により酸化され、
４Ａｇ＋４ＣＭ−−＋４ＡｇＣＩ２＋４ｓ−（４）とな
り、陰極上では、酸素が次式により還元され、Ｏｘ＋４
Ｈ＋→２ＨｚＯ４ｅ″″（酸素）−（５）Ｏｚ＋２Ｈｚ
Ｏ−＋４０Ｉ−Ｉ−−４ｅ−（アルカリ性）（６）とな
る。In order to function as an oxygen electrode, platinum electrode 1 is used as a cathode, silver electrode 2 is used as an anode, and a voltage of 0.6 to 0.8 V is applied between the two electrodes. On the anode, silver is oxidized according to the following formula to become 4Ag+4CM--+4AgCI2+4s-(4), and on the cathode, oxygen is reduced according to the following formula to become Ox+4
H+→2HzO4e″″(oxygen)-(5)Oz+2Hz
O-+40I-I-4e- (alkaline) (6).
これにより、過酸化水素型のグルコースセンサでも、酸
素型のグルコースセンサでも、汗のグルコース濃度に比
例した電流値が得られる。なお、酸素型のグルコースセ
ンサでは、生体内の酸素分圧の変動が誤差を与えるので
、これを除去する必要がある。As a result, a current value proportional to the glucose concentration of sweat can be obtained with both the hydrogen peroxide type glucose sensor and the oxygen type glucose sensor. Note that in an oxygen-type glucose sensor, fluctuations in the oxygen partial pressure within the body cause errors, which must be removed.
また、グルコース以外の有機物、すなわち乳酸、ピルビ
ン酸、尿酸なども汗の値と血液の値が対応して変化する
ことが考えられるため、グルコースと同様に酵素電極に
より経皮的に測定できよう。Furthermore, organic substances other than glucose, such as lactic acid, pyruvic acid, and uric acid, can be measured transcutaneously using enzyme electrodes in the same way as glucose, since sweat values and blood values may change in a corresponding manner.
以下、本発明の実施例を第１図に基づいて詳説するが、
本実施例は第２図の面Ｓでの経皮センサの断面を体表面
側から見たものである。Hereinafter, embodiments of the present invention will be explained in detail based on FIG.
This embodiment shows a cross section of the transcutaneous sensor taken along plane S in FIG. 2, viewed from the body surface side.
この断面は白金電極１、銀電極２、絶縁物質３がポーラ
ログラフ電極面１６に配置され、該電極面１６の周辺を
断熱材１１が囲んでいる。電極面１６に皮膚側から到達
した消費される物質は、ポーラログラフ電極が過酸化水
素型であろうが、酸素型であろうが、白金電極１で消費
される６本実施例では、白金電極１を線幅２ｍｍ以下の
蛇行状として電極面１６に広範囲に設置しているため、
高効率、高Ｓ／Ｎ比で測定対象物質を電流に変換できる
。In this cross section, a platinum electrode 1, a silver electrode 2, and an insulating material 3 are arranged on a polarographic electrode surface 16, and a heat insulating material 11 surrounds the electrode surface 16. The substances to be consumed that reach the electrode surface 16 from the skin side are consumed at the platinum electrode 1, regardless of whether the polarographic electrode is of hydrogen peroxide type or oxygen type. are installed over a wide area on the electrode surface 16 in a meandering shape with a line width of 2 mm or less,
The substance to be measured can be converted into electric current with high efficiency and high S/N ratio.
この実施例において、白金電極１の材質は白金に限らず
、金、イリジウムでも可能である。また。In this embodiment, the material of the platinum electrode 1 is not limited to platinum, but may also be gold or iridium. Also.
生化学センサの種類もグルコース以外の有機物、すなわ
ち乳酸、ピルビン酸、尿酸などを測定対象とするもので
もよく、さらに生化学センサの数も１個のみならず複数
個を集積化して一つの経皮センサに内蔵することもでき
る。The type of biochemical sensor may be one that measures organic substances other than glucose, such as lactic acid, pyruvic acid, uric acid, etc. Furthermore, the number of biochemical sensors is not limited to one, but multiple sensors can be integrated into one transdermal sensor. It can also be built into the sensor.
本発明によれば、簡便な方法により体内のグルコース濃
度を体表面から無侵襲に測定できるので、感染、患者の
精神的・肉体的苦痛、失血を除くことができ、また、セ
ンサに血液や組織の生体成分が付着しないので性能劣化
が少なく、長期に亘りグルコースを安定に測定できる。According to the present invention, the glucose concentration in the body can be measured non-invasively from the body surface using a simple method, thereby eliminating infection, mental and physical pain of the patient, and blood loss. Since biological components do not adhere, there is little performance deterioration and glucose can be measured stably over a long period of time.
また、グルコース濃度を常に知ることにより血糖値を生
理的に正常な値に保てるので、高血糖による合併症や低
直糖の事故を防ぐことができ、血糖測定装置や人工膵臓
のセンサとして利用できる。In addition, by constantly knowing the glucose concentration, it is possible to maintain the blood sugar level at a physiologically normal value, which prevents complications caused by hyperglycemia and accidents due to low blood sugar levels, and can be used as a sensor for blood sugar measuring devices and artificial pancreas. .
第１図は本発明による経皮センサの実施例を示すポーラ
ログラフ電極の横断面図、第２図は経皮グルコースセン
サの構成を示す縦断面図である。
１・・・白金電極、２・・・銀電極、３・・・絶縁物質
、４・・・多孔質物質、５・・・固定化グルコースオキ
シダーゼ膜、６・・・妨害物質除去膜、７・・・電解液
、１６・・・ボ、Ｃ′−５FIG. 1 is a cross-sectional view of a polarographic electrode showing an embodiment of the transcutaneous sensor according to the present invention, and FIG. 2 is a longitudinal cross-sectional view showing the configuration of the transcutaneous glucose sensor. DESCRIPTION OF SYMBOLS 1... Platinum electrode, 2... Silver electrode, 3... Insulating material, 4... Porous material, 5... Immobilized glucose oxidase membrane, 6... Interfering substance removal membrane, 7... ... Electrolyte, 16...Bo, C'-5
Claims (1)
電極とオキシダーゼ系の固定化酵素を含む酵素電極にお
いて、該電極が皮膚に装着できるような構造を有し、皮
膚より浸出する汗に含まれる測定対象物質と反応する前
記固定化酵素膜の面積が０．５〜１００ｃｍ＾２であり
、酸素電極の陰極あるいは過酸化水素電極の陽極を線幅
が２ｍｍ以下の蛇行状としたことを特徴とする経皮セン
サ。 ２、特許請求の範囲第１項において、該電極が皮膚に装
着できるような構造を有し、発汗の手段として皮膚を加
温する加温機構を有し、皮膚より浸出する汗に含まれる
測定対象物質と反応する前記固定化酵素膜の面積が０．
５〜１００ｃｍ＾２であり、酸素電極の陰極あるいは過
酸化水素電極の陽極を線幅が２ｍｍ以下の蛇行状とした
ことを特徴とする経皮センサ。 ３、特許請求の範囲第１項ないし第２項において、酵素
電極が酸素あるいは過酸化水素を測定するポーラログラ
フ電極、固定化グルコースオキシダーゼ膜、還元性物質
除去膜で構成されたグルコースセンサであることを特徴
とする経皮センサ。[Claims] 1. In a polarographic electrode for measuring oxygen or hydrogen peroxide and an enzyme electrode containing an oxidase-based immobilized enzyme, the electrode has a structure such that it can be attached to the skin, and the electrode has a structure that allows it to be attached to the skin, and the sweat exuded from the skin. The area of the immobilized enzyme membrane that reacts with the substance to be measured contained in the membrane is 0.5 to 100 cm^2, and the cathode of the oxygen electrode or the anode of the hydrogen peroxide electrode has a meandering shape with a line width of 2 mm or less. A transcutaneous sensor featuring: 2. In claim 1, the electrode has a structure that allows it to be attached to the skin, has a heating mechanism that heats the skin as a means of perspiration, and measures the amount contained in sweat exuded from the skin. The area of the immobilized enzyme membrane that reacts with the target substance is 0.
5 to 100 cm^2, and the cathode of the oxygen electrode or the anode of the hydrogen peroxide electrode has a meandering shape with a line width of 2 mm or less. 3. Claims 1 and 2 state that the enzyme electrode is a glucose sensor composed of a polarographic electrode for measuring oxygen or hydrogen peroxide, an immobilized glucose oxidase membrane, and a reducing substance removal membrane. Features of transcutaneous sensor.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61281786A JPS63135131A (en) | 1986-11-28 | 1986-11-28 | Percataneous sensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61281786A JPS63135131A (en) | 1986-11-28 | 1986-11-28 | Percataneous sensor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPS63135131A true JPS63135131A (en) | 1988-06-07 |
Family
ID=17643953
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP61281786A Pending JPS63135131A (en) | 1986-11-28 | 1986-11-28 | Percataneous sensor |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS63135131A (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2006077750A1 (en) * | 2005-01-19 | 2006-07-27 | Sysmex Corporation | Analyzer and cartridge for extracting analyte |
| JP2009521705A (en) * | 2005-12-27 | 2009-06-04 | バイエル・ヘルスケア・エルエルシー | Electrochemical sensor system using substrate having at least one electrode and method of forming the same |
| JP2010172588A (en) * | 2009-01-30 | 2010-08-12 | Omron Healthcare Co Ltd | Blood component concentration change measuring instrument |
| CN101833239A (en) * | 2009-03-10 | 2010-09-15 | 东京毅力科创株式会社 | Substrate processing method using same |
-
1986
- 1986-11-28 JP JP61281786A patent/JPS63135131A/en active Pending
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2006077750A1 (en) * | 2005-01-19 | 2006-07-27 | Sysmex Corporation | Analyzer and cartridge for extracting analyte |
| JP2009521705A (en) * | 2005-12-27 | 2009-06-04 | バイエル・ヘルスケア・エルエルシー | Electrochemical sensor system using substrate having at least one electrode and method of forming the same |
| US9668683B2 (en) | 2005-12-27 | 2017-06-06 | Ascensia Diabetes Care Holdings Ag | Electrochemical sensor system using a substrate with at least one aperture and method of making the same |
| US10010279B2 (en) | 2005-12-27 | 2018-07-03 | Ascensia Diabetes Care Holdings Ag | Method of determining an analyte concentration of a fluid |
| JP2010172588A (en) * | 2009-01-30 | 2010-08-12 | Omron Healthcare Co Ltd | Blood component concentration change measuring instrument |
| CN101833239A (en) * | 2009-03-10 | 2010-09-15 | 东京毅力科创株式会社 | Substrate processing method using same |
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