【発明の詳細な説明】〔産業上の利用分野〕本発明は汗中物質の測定装置に関するものである。[Detailed description of the invention][Industrial application field]The present invention relates to a device for measuring substances in sweat.
従来、人体の皮膚表面から発せられる汗中物質は人体の
様々な状態を表すものとして知られており、該汗中物質
の濃度測定により人体の体調を把握することが試みられ
ている。2. Description of the Related Art Conventionally, substances in sweat emitted from the surface of the human skin have been known to represent various conditions of the human body, and attempts have been made to understand the physical condition of the human body by measuring the concentration of substances in sweat.
従来より、汗中物質の測定方法としては、人体の皮膚か
らまず汗を採取し、次に該汗を分析装置にて分析する方
法が一般的である。かかる方法によれば、人体からの汗
中物質をリアルタイムで、かつ連続的に測定することは
できない。Conventionally, a common method for measuring substances in sweat is to first collect sweat from the skin of a human body and then analyze the sweat using an analyzer. According to such a method, substances in sweat from the human body cannot be measured continuously in real time.
本発明は汗中物質をリアルタイムで、かつ連続的に測定
でき、更には皮膚を傷つけることなく非侵襲測定ができ
る汗中物質の測定装置を提供することを目的とするもの
である。SUMMARY OF THE INVENTION An object of the present invention is to provide a device for measuring substances in sweat that can continuously measure substances in sweat in real time and non-invasively without damaging the skin.
本発明は、上記目的を達成するため、皮膚表面に装着さ
れ、該皮膚表面の汗中物質に対して選択的に感応し、該
汗中物質に対する感応により化学量または物理量を生じ
る感応部を備え、該感応部にて生じる化学量または物理
量により前記汗中物質の濃度を測定するという技術的手
段を採用したものである。In order to achieve the above object, the present invention includes a sensitive part that is attached to the skin surface, selectively sensitive to substances in sweat on the skin surface, and generates a chemical amount or a physical amount in response to the substances in sweat. , which employs a technical means of measuring the concentration of the substance in sweat based on the chemical or physical amount generated in the sensitive area.
また、本発明では、皮膚表面の汗中物質に対して選択的
に反応する反応部と、該反応部での汗中物質の反応によ
り生成する特定成分の電気化学的反応により生じる物理
量を測定する一対の電極と、前記一対の電極間に位置し
て前記電気化学的反応を惹起せしめる電解質と、を具備
したという技術的手段によっても上記目的を達成するこ
とができる。Furthermore, in the present invention, a physical quantity generated by an electrochemical reaction between a reaction part that selectively reacts with substances in sweat on the skin surface and a specific component generated by the reaction of substances in sweat at the reaction part is measured. The above object can also be achieved by a technical means including a pair of electrodes and an electrolyte that is located between the pair of electrodes and causes the electrochemical reaction.
また、本発明では、皮膚表面の汗中乳酸を選択的に酸化
せしめる酸化剤と、該酸化剤での乳酸の酸化反応により
生成する特定成分の電気化学的反応により生じる酸化還
元電流を測定する一対の電極と、前記一対の電極間に位
置して前記電気化学的反応を惹起せしめる電解質と、を
具備したという技術的手段によっても上記目的を達成す
ることができる。In addition, in the present invention, a pair of oxidizing agents that selectively oxidize lactic acid in sweat on the skin surface and a specific component generated by the oxidation reaction of lactic acid with the oxidizing agent measure the redox current generated by the electrochemical reaction. The above object can also be achieved by a technical means including an electrode and an electrolyte located between the pair of electrodes to induce the electrochemical reaction.
本発明では、乳酸を選択的に酸化せしめる酸化剤として
は乳酸オキシダーゼがあり、この乳酸オキシダーゼを用
いる場合には電極の先端に固定すればよい。In the present invention, lactate oxidase is an oxidizing agent that selectively oxidizes lactic acid, and when this lactate oxidase is used, it may be fixed at the tip of the electrode.
本発明では、上記電気化学的反応を惹起するために、電
極間に特定の電圧を印加する電圧源を接続することが必
要である。In the present invention, in order to induce the electrochemical reaction described above, it is necessary to connect a voltage source that applies a specific voltage between the electrodes.
また、本発明では、人体の皮膚に対して装着が容易な構
成とするため、取り付け部材を有していてもよい。Further, in the present invention, an attachment member may be included in order to make it easy to attach to the skin of a human body.
本発明では、感応部にて皮膚表面の汗中物質が選択的に
感応され、かかる感応部にて汗中物質に対応した化学量
または物理量が生じることになる。In the present invention, substances in sweat on the skin surface are selectively sensitized at the sensitive area, and chemical or physical amounts corresponding to the substances in sweat are generated at the sensitive area.
該物理量または化学量で汗中物質の濃度を測定すること
ができる。The concentration of substances in sweat can be measured using the physical quantity or chemical quantity.
また、本発明では、汗中物質が反応部と反応して特定成
分を生成し、該特定成分が電解質内部で電気化学的反応
を生成し、かかる電気化学的反応により発生ずる物理量
を一対の電極で測定するのである。Further, in the present invention, substances in sweat react with the reaction part to produce a specific component, the specific component produces an electrochemical reaction inside the electrolyte, and the physical quantity generated by the electrochemical reaction is transferred to a pair of electrodes. It is measured by
以上要するに、本発明によれば、皮膚表面の汗中物質を
リアルタイムで、かつ連続的に測定することができる。In summary, according to the present invention, substances in sweat on the skin surface can be measured continuously in real time.
また、その測定に際しては皮膚を傷付けることがないた
め、測定対象としては万人向けであり、不快感の低減に
大きく寄与する。Furthermore, since the measurement does not injure the skin, it can be measured by anyone, and greatly contributes to reducing discomfort.
以下、本発明を図に示す実施例について説明する。DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, embodiments of the present invention shown in the drawings will be described.
第１図〜第４図において、測定部の構成について説明す
る。The configuration of the measuring section will be explained with reference to FIGS. 1 to 4.
１は反応電極で、該反応電極１は断面円形の例えば直径
１ ｍｍの金線よりなる。２は補助電極で、該補助電極
２は断面円形の例えば直径０． ５１１１１１１の銀線
よりなる。Reference numeral 1 denotes a reaction electrode, and the reaction electrode 1 is made of a gold wire having a circular cross section and a diameter of 1 mm, for example. 2 is an auxiliary electrode, and the auxiliary electrode 2 has a circular cross section, for example, a diameter of 0. Made of 5111111 silver wire.
３は硬質プラスチ・ツクよりなる円筒形かつ断面凹状の
支持体である。該支持体３の中心には例えば直径３朧の
雌ねじ部３ａが設けである。3 is a cylindrical support body made of hard plastic and having a concave cross section. The center of the support 3 is provided with a female threaded portion 3a having a diameter of 3 mm, for example.
上記反応電極１の表面には該反応電極１の反応表面積を
一定とするために直径２髄の熱収縮チュブ４が該電極１
の２／３程度まで被せてあり、またそのチューブ４の表
面の２／３程度までには、反応電極１の支持体３への固
定とシールのために肉厚０． １ｍｍ、幅１３胴の伸縮
性の四フッ化エチレン樹脂よりなるシールテープ５が巻
付けである。A heat-shrinkable tube 4 with a diameter of 2 mm is placed on the surface of the reaction electrode 1 in order to keep the reaction surface area of the reaction electrode 1 constant.
The surface of the tube 4 is covered to about 2/3, and about 2/3 of the surface of the tube 4 is covered with a wall thickness of 0.5 mm for fixing and sealing the reaction electrode 1 to the support 3. A sealing tape 5 made of stretchable polytetrafluoroethylene resin and having a width of 1 mm and a width of 13 cylinders is wound.
なお、該テープ５としては例えば商品名ハルカーテープ
シール（ｍ１本ハルカー工業株式会社）がある。The tape 5 is, for example, the product name Halker Tape Seal (m1 Hon Halker Industries Co., Ltd.).
かかる構成の反応電極１の一端側は、そのテープ５の部
分を介して支持体３の雌ねじ部３ａにシール固定化され
ている。なお、電極の一端面は支持体３の外部に露出し
ている。One end of the reaction electrode 1 having such a structure is sealed and fixed to the female threaded portion 3a of the support 3 via the tape 5. Note that one end surface of the electrode is exposed to the outside of the support 3.
Ｇは硬質プラスチックよりなる反応槽であり、該反応槽
６は断面逆り字状の全体として円筒形の形態を有してお
り、該反応槽６は支持体３に対して例えばエポキシ樹脂
系の樹脂接着剤７によりシ−小接合しである。G is a reaction tank made of hard plastic, and the reaction tank 6 has an overall cylindrical shape with an inverted cross section. A small seam joint is made using a resin adhesive 7.
８は支持体３と反応槽６との間に形成されたリング状の
空間部９に注入された液状の電解質であり、該電解質は
例えばリン酸水素すトリウム（Ｎ−２１１ＰＯ４）を水
中に例えば１／１５モル／ｆ溶解したものよりなる。ま
た、該リン酸水素ナトリウム溶液は使用する酵素の至適
ｐ１１を維持し、酵素活性を保持する。8 is a liquid electrolyte injected into a ring-shaped space 9 formed between the support 3 and the reaction tank 6, and the electrolyte is made by dissolving, for example, sodium hydrogen phosphate (N-211PO4) in water. Consisting of 1/15 mole/f dissolved. Moreover, the sodium hydrogen phosphate solution maintains the optimum p11 of the enzyme used and retains the enzyme activity.
上記補助電極２の一端は直線部として反応槽６の例えば
０．７ｍｍの穴６ａを貫通して外部に露出している。な
お、反応槽６の穴６ａと電極２との間は例えばエポキシ
樹脂系の樹脂接着剤１０によりシール接合しである。該
接着剤１０ならびに上記接着剤７は例えば商品名セメダ
インハイス−パー５（セメダイン株式会社）がある。One end of the auxiliary electrode 2 passes through a hole 6a of, for example, 0.7 mm in the reaction tank 6 as a straight portion and is exposed to the outside. Note that the hole 6a of the reaction tank 6 and the electrode 2 are sealed and bonded using, for example, an epoxy resin adhesive 10. The adhesive 10 and the adhesive 7 have, for example, the trade name Cemedine High Super 5 (manufactured by Cemedine Co., Ltd.).
補助電極２の他端側は反応表面積が広くなるよう、即ち
該電極２側での反応が充分行えるように、電極面積（反
応電極１に対して約２０倍以上）を増加するためにコイ
ル状に巻回しである。このような電極面積の増大は反応
電極１の反応を常に律速させるためである。The other end of the auxiliary electrode 2 is coiled in order to increase the electrode area (approximately 20 times or more compared to the reaction electrode 1) so that the reaction surface area becomes larger, that is, the reaction on the electrode 2 side is sufficiently performed. It is wrapped around. This increase in electrode area is to always rate-limit the reaction of the reaction electrode 1.
該巻回部２ａは上記空間部９、つまり電解質８内に浸漬
しである。The winding portion 2a is immersed in the space 9, that is, the electrolyte 8.
従って、外観上は一本の反応電極１と一本の補助電極２
とが各々支持体３、反応槽６から突出した態様となって
いる。Therefore, in appearance, there is one reaction electrode 1 and one auxiliary electrode 2.
and protrudes from the support 3 and the reaction tank 6, respectively.
１１は乳酸を酸化させるための乳酸オキシダーゼよりな
る酵素固定化膜である。該酵素固定化膜１１は例えば、
東洋醸造株式会社製のＰｅｄｉｏｃｏｃｕｓｓｐ由来（
酵素活性３３．０ｕｎｉｔ／ｍｇ） ４ 、 ５ ｍ
ｇを東洋合成株式会社製の光硬化性樹脂ＰＶＡ−３ｂＱ
５０．３ｍｇ、蒸留水３０ＩＣと混合し、該混合物を上
記電極１の露出端に塗布し、１時間の暗所風乾後、１５
分間蛍光灯照射することで構成されている。なお、該酵
素固定化膜１１は親水性であり、電解質８は該酵素固定
化膜１１を経て該酵素固定化膜１１と電極１との界面に
まで達することができる。11 is an enzyme-immobilized membrane composed of lactate oxidase for oxidizing lactic acid. The enzyme-immobilized membrane 11 is, for example,
Derived from Pediococus sp. manufactured by Toyo Jozo Co., Ltd. (
Enzyme activity 33.0 units/mg) 4, 5 m
g is photocurable resin PVA-3bQ manufactured by Toyo Gosei Co., Ltd.
50.3 mg and 30 IC of distilled water, the mixture was applied to the exposed end of the electrode 1, and after air-drying in the dark for 1 hour,
It consists of irradiation with fluorescent light for minutes. Note that the enzyme-immobilized membrane 11 is hydrophilic, and the electrolyte 8 can reach the interface between the enzyme-immobilized membrane 11 and the electrode 1 through the enzyme-immobilized membrane 11.
ところで、反応性を向上するために、支持体３皮膚側の
端面、反応槽６の開口端（空間部９の開口端）、および
酵素固定化膜１１の皮膚側表面は同一平面上に揃えであ
る。次に、上記測定部を組み込んだアームバンド型の取
り付け部材の構成に関して説明する。By the way, in order to improve the reactivity, the end surface of the support 3 on the skin side, the open end of the reaction tank 6 (the open end of the space 9), and the skin-side surface of the enzyme immobilization membrane 11 should be aligned on the same plane. be. Next, a description will be given of the configuration of an armband type attachment member incorporating the measurement section.
第５図〜第７図において、第５図は取り付け部材の平面
（表）を、第６図は側面を、第７図は裏面を示している
。5 to 7, FIG. 5 shows the plane (front) of the attachment member, FIG. 6 shows the side, and FIG. 7 shows the back.
即ち、腕時計の時計装着部に、時計の代わりに上記測定
部１２がカートリッジ方式で取り付けられるものである
。その取り付け構成は測定部１２の反応槽６の外周を、
断面凹状（図示なし）の時旧装着部１３の内側に、所謂
しまりばめ状態を利用して着脱自在に固定しである。な
お、図中、１４．１５は人体の腕部に巻付け固定される
一対のアームバンドを示している。That is, the measuring section 12 is attached to the watch mounting section of the wristwatch in place of the watch using a cartridge method. The mounting configuration is such that the outer periphery of the reaction tank 6 of the measuring section 12 is
When the cross section is concave (not shown), it is removably fixed to the inside of the old mounting part 13 using a so-called interference fit. In the figure, reference numerals 14 and 15 indicate a pair of arm bands that are wrapped around and fixed to the arms of a human body.
次に、上記構成の所謂アームバンド型ノ＼イオセンリ・
を用いた測定装置の全体構成について説明する。Next, the so-called armband type of the above configuration
The overall configuration of the measuring device using the following will be explained.
第８図において、１６は上記構成からなるアムバンド型
バイオセンサ、１７は被測定者、１８】 ３は測定補助装置、１９は遠隔測定用送信機、２０は受信
機、２１は記録計、２２は分析計、２３はリード線をそ
れぞれ示している。なお、測定補助袋Ｗ１ Ｂと遠隔測
定用送信機１９はそれぞれ被測定者に保持されている。In FIG. 8, 16 is an amband type biosensor having the above configuration, 17 is a subject, 18] 3 is a measurement auxiliary device, 19 is a remote measurement transmitter, 20 is a receiver, 21 is a recorder, and 22 is a In the analyzer, 23 indicates a lead wire. Note that the measurement auxiliary bag W1B and the remote measurement transmitter 19 are each held by the person to be measured.
また、測定補助装置１８はボテンシオスタッ１−と称さ
れるもので、該測定補助装置１８からはリード線２３を
介して反応電極１と補助電極２との間に一定電圧、例え
ば７００ｍＶが印加されており、その結果として得られ
る電流を測定補助装置１８で測定する。The measurement auxiliary device 18 is called a potentiostat 1-, and a constant voltage, for example 700 mV, is applied between the reaction electrode 1 and the auxiliary electrode 2 from the measurement auxiliary device 18 via a lead wire 23. and the resulting current is measured by the measurement auxiliary device 18.
上記構成において、次に作動を説明する。In the above configuration, the operation will be explained next.
被測定者１７の腕部に対してバイオセンサ１６を取り付
ける。その取り付け方法は、反応槽６内部の電解質８が
溢れないようにした状態、つまり反応槽６の空間部９の
開口端を上にした状態として腕にバイオセンサ１６をア
ームバンド１４．１５を介して取り付ける。The biosensor 16 is attached to the arm of the person 17 to be measured. The method for attaching the biosensor 16 is to attach the biosensor 16 to the arm via the arm band 14, 15 while ensuring that the electrolyte 8 inside the reaction tank 6 does not overflow, that is, with the open end of the space 9 of the reaction tank 6 facing upward. Attach it.
そして、反応槽６をアームバンドを使い、皮膚の弾性変
形を利用して該皮膚表面に密着させる。Then, the reaction tank 6 is brought into close contact with the skin surface using an armband and utilizing the elastic deformation of the skin.
この際、反応槽６と皮膚とは密着状態にあり、電解質８
は漏れない。また、反応槽６を皮膚に密着させることに
より、皮膚の表面と酵素固定化膜１１との間に電解質８
が薄膜状に介在することになる。このため、見掛は上の
反応槽６の容積を極少とした状態となり、その分皮膚表
面Ｓからの汗中の乳酸を直接的かつ効率よく電極反応せ
しめることができる。At this time, the reaction tank 6 and the skin are in close contact, and the electrolyte 8
does not leak. In addition, by bringing the reaction tank 6 into close contact with the skin, electrolyte 8 can be formed between the skin surface and the enzyme-immobilized membrane 11.
will be present in the form of a thin film. Therefore, the apparent volume of the upper reaction tank 6 is minimized, and the lactic acid in the sweat from the skin surface S can be directly and efficiently reacted with the electrodes.
バイオセンサ１６を上記のようにして腕に装着後、被測
定者の腕に、バイオセンサ１６の外面を覆うようにして
手袋を被着し、かつ被測定者に厚着させ、そして電気ス
トーブを利用して被測定者の発汗を促した。なお、バイ
オセンサ１６部の温度は３８°Ｃであった。After the biosensor 16 is attached to the arm as described above, gloves are placed on the arm of the person to be measured so as to cover the outer surface of the biosensor 16, and the person is made to wear the gloves, and an electric heater is used. This caused the subject to sweat. Note that the temperature of 16 parts of the biosensor was 38°C.
被測定者の腕の表面に発生した汗中の乳酸は反応電極１
の先端に固定した酵素固定膜１１の乳酸オキシダーゼに
より酸化され、下記の反応を生成する。The lactic acid in the sweat generated on the surface of the subject's arm is detected by the reaction electrode 1.
is oxidized by lactate oxidase on the enzyme-immobilized membrane 11 fixed to the tip of the membrane, producing the following reaction.
Ｃ，、Ｉｔ６０：ｌ＋Ｏ□ −＞ Ｃ：＋ １１４０
ｚ ＋ＩＩ□０□該反応で生酸反応Ｈ２０□は電解質８
の内部にて電極１．２の間で次の電気化学的反応を引き
起こす。C,, It60:l+O□ -> C:+ 1140
z +II□0□In this reaction, the raw acid reaction H20□ is electrolyte 8
The following electrochemical reaction occurs between the electrodes 1.2 within the .
＋＋ ２０２ →２ｔｌ’ｌＯｚ＋２ｅＨ，Ｏｚ
→２Ｈ”＋Ｏｚ＋２ｅ２Ｈ’＋Ｐ０．３−→Ｈ２ＰＯ４１１□ＰＯ４−→２１１＋＋ＰＯ４３０゜＋２Ｈ”＋２ｅ−−＋）Ｉ２ｏ□八ｇ２へ＋２Ｈ”＋２ｅ−−＋２Ａｇ＋Ｉ（ｚ。++ 202 →2tl'lOz+2eH,Oz
→2H"+Oz+2e 2H'+P0.3-→H2PO4 11□PO4-→211+++PO43 0°+2H"+2e--+)I2o□ To 8g2+2H"+2e--+2Ag+I(z.
かかる電気化学的反応により、両電極間１．２で物理量
としての酸化還元電流が発生し、該電流はり一ド線２３
を経て測定補助装置１８に導かれる。該測定補助装置１
８で測定された電流は遠隔測定用送信機１９を介して受
信機２０に受信され、記録計２１にて記録され、分析計
２２でその結果が分析される。Due to this electrochemical reaction, an oxidation-reduction current as a physical quantity is generated between the two electrodes 1.2, and the current is
It is guided to the measurement auxiliary device 18 via. The measurement auxiliary device 1
The current measured at 8 is received by a receiver 20 via a telemetry transmitter 19, recorded by a recorder 21, and analyzed by an analyzer 22.
その電流測定結果を第９図に示す。横軸に出力応答（μ
Ａ）を、縦軸に測定時間（分）を示す。The current measurement results are shown in FIG. The horizontal axis shows the output response (μ
A), the vertical axis shows the measurement time (minutes).
ところで、汗中の乳酸は疲労度と相関関係を有しており
、例えば高温発汗と、運動発汗とでは汗中の乳酸の濃度
が異なることがわかった。このことを第１０図で示す。By the way, it has been found that lactic acid in sweat has a correlation with the degree of fatigue, and for example, the concentration of lactic acid in sweat is different between high temperature sweating and exercise sweating. This is illustrated in FIG.
第１０図は４人の成人男子に関して高温発汗と運動発汗
との汗中の乳酸の濃度を測定した結果を示す。高温発汗
とは４５°Ｃの温水への５分間の入浴後の発汗を意味し
、運動発汗とは階段昇降運動（酸素過少運動）後の発汗
を意味している。そして、測定方法としては人体の皮膚
表面より採取した汗を緩衝液が循環している反応セル（
乳酸オキシダーゼ、電極等を有する）中に導き、ここで
の電気化学的反応により生じる酸化還元電流を測定した
ものである。FIG. 10 shows the results of measuring the concentration of lactic acid in the sweat of four adult males during high-temperature sweating and exercise sweating. High-temperature sweating refers to sweating after a 5-minute bath in 45°C warm water, and exercise sweating refers to sweating after stair-climbing exercise (hypoxic exercise). As a measurement method, sweat collected from the surface of the human skin is collected in a reaction cell in which a buffer solution is circulated (
lactate oxidase, electrodes, etc.), and the redox current generated by the electrochemical reaction there is measured.
第１０図のハーグラフの上は高温発汗、下は運動発汗を
示している。第１０圀から理解されるように、運動発汗
中の乳酸濃度の方が高いことがわかる。The upper half of the graph in Figure 10 shows high temperature sweating, and the lower half shows sweating due to exercise. As understood from Section 10, the concentration of lactic acid during sweating during exercise is higher.
従って、汗中の乳酸の濃度の測定により、人体の肉体疲
労度を客観的に把握することができるのである。Therefore, by measuring the concentration of lactic acid in sweat, it is possible to objectively understand the degree of physical fatigue of the human body.
本発明では人体の汗中の乳酸を人体を傷付Ｃノることな
く、非侵襲で測定できる。According to the present invention, lactic acid in human sweat can be measured non-invasively without causing any damage to the human body.
本発明は上記の実施例に限定されるものではなく、次の
ように種々の変形が可能である。The present invention is not limited to the embodiments described above, and various modifications can be made as follows.
（１）バイオセンサの皮膚側の面に、汗ならびに電解質
８が透過可能な透過膜を設置しても勿論よい。(1) Of course, a permeable membrane through which sweat and the electrolyte 8 can permeate may be provided on the skin-side surface of the biosensor.
該透過膜は反応（汗中の乳酸と酵素固定化膜１１の乳酸
オキシダーゼとの反応）の緩衝化と、電解質８の漏洩防
止とに寄与することができる。The permeable membrane can contribute to buffering the reaction (the reaction between lactic acid in sweat and lactic acid oxidase in the enzyme-immobilized membrane 11) and preventing leakage of the electrolyte 8.
該透過膜の材質は例えばＳａｍｅｌｅｓｓ ｃｅｌｌｕ
ｌｏｓｅｔｕｂｉｎｇ（孔径２４人、膜厚２０ ｕ ｍ
：ＶＩｓＫＡｓＥ ５ＡＬＥＳＣＯＲＰ、）、 ５ＴＡ
ＮＤＡＲＤ Ｄｒ八へＹＺＩＮＧ ＭＥＭＢＩ？Ａ
ＮＥ（孔径２４人、膜厚１５μｍ：ＴＥＣＨＮＩＣＯＮ
ＣＨＥＭＩＣＡＬ Ｃｏ Ｓ、Ａ）、ニュークリポア
ーメンブレン ポリカーボネイト膜（孔径０．０１５〜
１２μｍ＝奥村マイクロ・ザイエンス株式会社）等を使
用することができる。The material of the permeable membrane is, for example, Sameless cellu.
losetubing (pore size 24 mm, film thickness 20 μm
:VIsKAsE 5ALESCORP, ), 5TA
YZING MEMBI to NDARD Dr.8? A
NE (pore diameter 24, film thickness 15μm: TECHNICON
CHEMICAL Co S, A), Nuclepore membrane polycarbonate membrane (pore size 0.015~
12 μm=Okumura Micro Science Co., Ltd.), etc. can be used.
（２）上記反応式から理解されるように、乳酸が乳酸オ
キシダーゼにより酸化されるとピルビン酸が生成される
。これは一種の妨害物質となり、該妨害物質の影響を排
除するために、上記実施例において、」二記反応電極の
他に乳酸オキシダーゼを固定化していない別の反応電極
を設置し、該反応電極にてピルビン酸に係わる電流を測
定し、乳酸に係わる電流とピルビン酸に係わる電流との
差を検出し、乳酸による酵素反応分だけをモニタリング
するようにすればよい。(2) As understood from the above reaction formula, pyruvic acid is produced when lactic acid is oxidized by lactate oxidase. This becomes a kind of interfering substance, and in order to eliminate the influence of this interfering substance, in the above example, another reaction electrode on which lactate oxidase is not immobilized is installed in addition to the reaction electrode described in 2. It is sufficient to measure the current related to pyruvic acid, detect the difference between the current related to lactic acid and the current related to pyruvic acid, and monitor only the enzyme reaction due to lactic acid.
（３）酵素反応は温度に対してその反応速度が変化する
ので、その反応を一定にするためにも温度補償を行って
もよい。(3) Since the reaction rate of an enzyme reaction changes with temperature, temperature compensation may be performed to keep the reaction constant.
（４）反応槽６の内部には未酵素反応の乳酸、反応生成
物たるピルビン酸、過酸化水素が溜まることが考えられ
るので、これら物質を反応槽６内から排除するために反
応槽６内の電解質８の循環を行うようにしてもよい。こ
のような循環により、電解質８中において乳酸が飽和す
ることがなく連続的に測定が可能となる。(4) Since unenzymatic reaction lactic acid, reaction products pyruvic acid, and hydrogen peroxide may accumulate inside the reaction tank 6, in order to remove these substances from the reaction tank 6, The electrolyte 8 may be circulated. Such circulation allows continuous measurement without saturation of lactic acid in the electrolyte 8.
（５）電解質８は液状に限らず、ゲル状としてもよいし
、またその成分もリン酸水素ナトリウムに限らず、要は
イオン導電体を生成するものであればよい。(5) The electrolyte 8 is not limited to a liquid state, but may be a gel state, and its components are not limited to sodium hydrogen phosphate, but may be any material that generates an ionic conductor.
（６）汗中物質としては乳酸に限らず、グルコース、ピ
ルビン酸、フェノール、脂質、尿酸、グルタミン酸、尿
素、アルギニン、リジン、フェニルアラニン、クレアチ
ニン、アミノ酸、あるいはナトリウム、アンモニウム、
塩素、カルシウム、マグネシウム、銅、ビタミンＢ６、
臭素、フッ素、沃素、亜鉛等のイオンが知られている。(6) Substances in sweat include not only lactic acid but also glucose, pyruvic acid, phenol, lipids, uric acid, glutamic acid, urea, arginine, lysine, phenylalanine, creatinine, amino acids, sodium, ammonium,
Chlorine, calcium, magnesium, copper, vitamin B6,
Ions such as bromine, fluorine, iodine, and zinc are known.
本発明はかかる汗中物質の濃度を測定するものにも適用
できることは言うまでもない。そして、惑応部、酵素セ
ンサとしては、例えばグルコースに対してはグルコース
オキシクーゼ、ピルビン酸に対してはピルビン酸オギシ
ターゼ、フェノールに対してはチロシナーゼ、脂質に対
してはコレステロールオキシターゼ、尿酸に対してはウ
リカーゼ、等々、各汗中物質を酸化せしめる酵素を用い
ればよい。It goes without saying that the present invention can also be applied to measuring the concentration of such substances in sweat. For example, the enzyme sensor is glucose oxidase for glucose, pyruvate oxidase for pyruvic acid, tyrosinase for phenol, cholesterol oxidase for lipids, and cholesterol oxidase for uric acid. Enzymes that oxidize each substance in sweat, such as uricase, may be used.
また、例えば上記イオンに対しては公知のイオン選択膜
にて汗中のイオンを選択的に検出し、そのイオン濃度に
より発生ずる一対の電極間の電位差を物理量として検知
すればよく、例えばナトリウムイオンに対してはイオン
選択膜として公知のＮａｚＯ−ＣａＯ−５ｔＯｚ−Ｌｔ
Ｊ−ＣｓｚＯ−ＬｚＯ３−Ｓ；Ｏｚを用いればよい。For example, for the above-mentioned ions, it is sufficient to selectively detect the ions in sweat using a known ion-selective membrane, and detect the potential difference between a pair of electrodes generated depending on the ion concentration as a physical quantity. For example, sodium ion NazO-CaO-5tOz-Lt, which is known as an ion selective membrane for
J-CszO-LzO3-S;Oz may be used.
なお、汗中のアンモニウムイオン（ＮＨ４＋）は、本実
施例における乳酸と同様、疲労度と相関関係を有してお
り、高温発汗と運動発汗とでは運動発汗の方がアンモニ
ウムイオンの濃度が高いことを確認している。In addition, ammonium ions (NH4+) in sweat have a correlation with the degree of fatigue, similar to lactic acid in this example, and the concentration of ammonium ions is higher in sweating at high temperatures and sweating during exercise. has been confirmed.
（７）本発明の用途としては、運動生理学、医療分野、
日常生活における高齢者管理等に適用することができる
他、自動車の運転者の体調把握にも適用することができ
る。(7) Applications of the present invention include exercise physiology, medical fields,
In addition to being applicable to the management of elderly people in daily life, it can also be applied to monitoring the physical condition of car drivers.
２入団平面図、第３図は第２図の底面図、第４図は外観斜視図
、第５図〜第７図は第１図〜第４図のものをアームバン
ド型構成とした例を示すもので、第５図は平面図、第６
図は側面図、第７図は底面図、第８図は本発明の実施に
用いた計測装置の概要を模式的に示す図、第９図は第８
図の計測装置による計測結果を示す特性図、第１０図は
人体の疲労度による乳酸濃度の関係を示す特性図である
。１・・・反応電極、２・・・補助電極、３・・・支持体
、６・・・反応槽、８・・・電解質、９・・・空間部、
１１・・・酵素固定化膜、１２・・・測定部、１４．１
５・・・アームノ＼゛ンド、１６・・・バイオセンサ。2. Figure 3 is a bottom view of Figure 2, Figure 4 is an external perspective view, and Figures 5 to 7 are examples of the armband type configuration of Figures 1 to 4. Figure 5 is a plan view and Figure 6 is a plan view.
The figure is a side view, FIG. 7 is a bottom view, FIG.
FIG. 10 is a characteristic diagram showing the measurement results by the measuring device shown in the figure, and FIG. 10 is a characteristic diagram showing the relationship between the lactic acid concentration and the degree of fatigue of the human body. DESCRIPTION OF SYMBOLS 1... Reaction electrode, 2... Auxiliary electrode, 3... Support body, 6... Reaction tank, 8... Electrolyte, 9... Space part,
11... Enzyme immobilization membrane, 12... Measuring section, 14.1
5...Arm node, 16...Biosensor.
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP11245690AJPH0428343A (en) | 1990-04-27 | 1990-04-27 | Measuring device for substance in sweat |
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP11245690AJPH0428343A (en) | 1990-04-27 | 1990-04-27 | Measuring device for substance in sweat |
| Publication Number | Publication Date |
|---|---|
| JPH0428343Atrue JPH0428343A (en) | 1992-01-30 |
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP11245690APendingJPH0428343A (en) | 1990-04-27 | 1990-04-27 | Measuring device for substance in sweat |
| Country | Link |
|---|---|
| JP (1) | JPH0428343A (en) |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0947433A (en)* | 1995-08-10 | 1997-02-18 | Suzuken:Kk | Sweating amount consecutively measuring device |
| JP2002513602A (en)* | 1998-04-30 | 2002-05-14 | セラセンス、インク． | Analyte monitoring system and method of use |
| US6479015B1 (en) | 1998-03-03 | 2002-11-12 | Pepex Biomedical, Llc | Apparatus for monitoring a level of a chemical species in a body fluid |
| JP2003521953A (en)* | 1998-09-10 | 2003-07-22 | アルテア テクノロジーズ，インコーポレイティド | Compensation of attributes for analyte detection and / or continuous monitoring |
| WO2009060823A1 (en)* | 2007-11-09 | 2009-05-14 | Omron Healthcare Co., Ltd. | System for accurately measuring blood component concentration and method of controlling the system |
| CN104545817A (en)* | 2015-01-29 | 2015-04-29 | 长沙一卫医疗科技有限公司 | Sensor for detecting conditions of ions of sweat of sweat glands in non-intervention manner |
| CN111134401A (en)* | 2018-11-02 | 2020-05-12 | 国家纳米科学中心 | High-elasticity intelligent clothes based on liquid metal, and preparation method and application thereof |
| JP2021077514A (en)* | 2019-11-08 | 2021-05-20 | 東洋インキＳｃホールディングス株式会社 | Dynamic analysis system |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0947433A (en)* | 1995-08-10 | 1997-02-18 | Suzuken:Kk | Sweating amount consecutively measuring device |
| US6479015B1 (en) | 1998-03-03 | 2002-11-12 | Pepex Biomedical, Llc | Apparatus for monitoring a level of a chemical species in a body fluid |
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| WO2009060823A1 (en)* | 2007-11-09 | 2009-05-14 | Omron Healthcare Co., Ltd. | System for accurately measuring blood component concentration and method of controlling the system |
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| CN104545817A (en)* | 2015-01-29 | 2015-04-29 | 长沙一卫医疗科技有限公司 | Sensor for detecting conditions of ions of sweat of sweat glands in non-intervention manner |
| CN111134401A (en)* | 2018-11-02 | 2020-05-12 | 国家纳米科学中心 | High-elasticity intelligent clothes based on liquid metal, and preparation method and application thereof |
| JP2021077514A (en)* | 2019-11-08 | 2021-05-20 | 東洋インキＳｃホールディングス株式会社 | Dynamic analysis system |
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