JP3826479B2 - Blood glucose meter - Google Patents

Blood glucose meter Download PDF

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Publication number
JP3826479B2
JP3826479B2 JP06582497A JP6582497A JP3826479B2 JP 3826479 B2 JP3826479 B2 JP 3826479B2 JP 06582497 A JP06582497 A JP 06582497A JP 6582497 A JP6582497 A JP 6582497A JP 3826479 B2 JP3826479 B2 JP 3826479B2
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Japan
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light receiving
laser
detecting means
wavelength
blood
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JPH10258036A (en
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武年 佐藤
匡 三木
雅代 土師
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Panasonic Corp
Panasonic Holdings Corp
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Panasonic Corp
Matsushita Electric Industrial Co Ltd
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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)

Description

【０００１】
【発明の属する技術分野】
本発明は、血液中の糖分を簡単に測定できる血糖計に関するものである。
【０００２】
【従来の技術】
従来、血糖値は、グルコースオキシダーゼ（ＧＯＤ）によってグルコースを分解し、血糖値を測定するＧＯＤ法が広く利用されている。ＧＯＤ法による血糖測定は、比較的短時間で簡単にできるものである。
【０００３】
【発明が解決しようとする課題】
前記ＧＯＤ法は、穿刺針によって微量ではあるが血液の採取を行わなければならないものであり、患者に苦痛を与えるものである。また、グルコース糖の濃度が小さい場合は温度による影響が大きく、正確な血糖値の測定ができないという課題を有している。
【０００４】
【課題を解決するための手段】
本発明は、レーザと受光素子とを使用して、血液中に吸収されるレーザ光線の量を検出し、また２種類のピーク波長のレーザ光線を使用して温度による影響がなく、採血の必要のない血糖計としているものである。
【０００５】
【発明の実施の形態】
本発明は、第１・第２・第３のレーザによって３波長のレーザ光線を使用して、温度の検出が正確で、血液中の各種成分の濃度を測定できる血糖計としている。
【０００６】
また、本発明は、第３のレーザが照射するレーザ光線のピークを適切に設定して、血液中の赤血球の濃度や血液中のグルコース糖の濃度や血液中の脂質の濃度を正確に測定できる血糖計としている。
【０００７】
【実施例】
（参考例１）
以下本発明に関連する第１の参考例について説明する。図１は参考例１の構成を示すブロック図である。指先を挿入するプローブ１内に、第１のレーザ２・第２のレーザ３・第１の受光素子４・第２の受光素子５を配置している。第１のレーザ２は第１の波長のレーザ光線を放射し、第２のレーザ３は第２の波長のレーザ光線を放射する。本実施例では第１のレーザ２・第２のレーザ３としてガリウムアルミ砒素（GaAlAs）を使用しており、第１の波長として1300nmを第２の波長として1700nmを使用している。第１のレーザ２・第２のレーザ３が放射したレーザ光線は、プローブ１内に挿入した指先を透過するときに指先内の血液等によって吸収され減衰して、第１の受光素子４・第２の受光素子５によって受光される。第１の受光素子４・第２の受光素子５は、それぞれ第１のレーザ２・第２のレーザ３に対向して配置されている。第１の受光素子４・第２の受光素子５が受光した信号は、それぞれ第１の受光感度検知手段６・第２の受光感度検知手段７に伝達されている。第１の受光感度検知手段６は、第１の受光素子４が受けた信号から第１の波長のレーザ光線の減衰度を、つまり第１の波長のレーザ光線が血液によって吸光され減衰した吸光度を演算する。第２の受光感度検知手段７は、第２の受光素子５が受けた信号から第２の波長のレーザ光線の減衰度を、つまり第２の波長のレーザ光線が血液によって吸光され減衰した吸光度を演算する。第１の受光感度検知手段６・第２の受光感度検知手段７の信号は、温度検出手段８に伝達される。温度検出手段８は、第１の波長のレーザ光線の吸光度と第２の波長のレーザ光線の吸光度との差ΔＡと、温度Ｔとの関係を図４のグラフに示すように予め記憶している。温度検出手段８が検出した温度信号と、第１の受光感度検知手段６・第２の受光感度検知手段７の信号とは、血糖値検出手段９に伝達される。血糖値検出手段９は、前記２つの波長のレーザ光線の吸光度の差ΔＡを温度信号によって補正し、指先の血液によって吸光された真の吸光度の差を演算する。またこの真の吸光度の差から血糖値Ｃを演算し、演算した血糖値を表示手段１１に表示する。
【０００８】
以下参考例１の動作について説明する。プローブ１内に指先を挿入して、図示していないスイッチをオンすると、血糖値の測定が開始される。第１のレーザ２・第２のレーザ３が放射する第１の波長のレーザ光線と第２の波長のレーザ光線は、指先を透過して減衰した状態で第１の受光素子３と第２の受光素子４に受光される。第１の受光素子４と第２の受光素子５は、受光量に応じた電気信号を発生し、それぞれ第１の受光感度検知手段６と第２の受光感度検知手段７にこの電気信号を伝達する。第１の受光感度検知手段６と第２の受光感度検知手段７は、第１のレーザ２・第２のレーザ３が放射したレーザ光線の出力と第１の受光素子４・第２の受光素子５が受けた受光量との比を採ることによって、指先を流れる血液によって吸収され減衰した第１の波長と第２の波長での吸光度を求めるものである。この吸光度の情報は温度検出手段８に伝達される。
【０００９】
次に温度検出手段８の温度検出動作について説明する。図２は、温度をＴ1とした状態で、ある血糖値を有する血液によって吸光され減衰される様子を、波長を変えて示している。この実験では、波長λmaxの吸光度がＡ1でピークとなっており、波長がλmaxからずれるに従って吸光度は低下しておりλminで最低の吸光度Ａ2となっている。また図３は、温度をＴ2とした状態で、ある血糖値を有する血液によって吸光され減衰される様子を、波長を変えて示している。この実験では、波長λminの吸光度がＡ3でピークとなっており、波長がλminからずれるに従って吸光度は低下しておりλmaxで最低の吸光度Ａ4となっている。この結果から、波長λmaxでの吸光度と波長λminでの吸光度との差ΔＡは、温度の上昇に応じて減少することが分かるものである。この様子を図４に示している。図４は、横軸が血液の温度を、縦軸は吸光度の差ΔＡを示している。従ってΔＡが決まると、温度Ｔは決定されるものである。前記λmin・λmaxは、それぞれ第２の波長・第１の波長に合致させている。従って温度検出手段８は、第１の受光感度検知手段６・第２の受光感度検知手段７の信号から、血液の温度Ｔを演算できるものである。
【００１０】
温度検出手段８がこのようにして演算した血液の温度Ｔは、第１の受光感度検知手段６・第２の受光感度検知手段７の信号と共に、血糖値検出手段９に伝達される。
【００１１】
第１の受光感度検知手段６と第２の受光感度検知手段７が出力する吸光度の差ΔＡは、数１に示すように、血糖値Ｃによって決定されるものである。
【００１２】
ΔＡ＝Ｋ1＊Ｃ＋Ｂ Ｋ1：比例定数 （数１）
数１中の比例定数Ｋ1は血液の温度によって変化するものである。そこで発明者らは実験を繰り返して、図５に示しているような温度Ｔと見かけの吸光度の差ΔＡ0と真の吸光度の差ΔＡ1との間の関係を見い出しているものである。例えば、温度がＴ1で見かけの吸光度の差がΔＡ01であれば真の吸光度の差はΔＡ11であり、温度がＴ2で見かけの吸光度の差がΔＡ02であれば真の吸光度の差はΔＡ12であり、温度がＴ3で見かけの吸光度の差がΔＡ03であれば真の吸光度の差はΔＡ13である。また図６は、前記数１に示した関係を表したグラフで、真の吸光度の差ΔＡ1と血糖値Ｃとの関係を示している。例えば真の吸光度の差がΔＡ11であれば血糖値はＣ0であり、真の吸光度の差がΔＡ12であれば血糖値はＣ1である。血糖値検出手段９は、前記図５・図６に示すデータを備えている。こうして、温度検出手段８から受けた温度データＴと、第１の受光感度検知手段６・第２の受光感度検知手段７の信号とから、血糖値Ｃを演算するものである。またこの血糖値Ｃを表示手段１０に表示させている。
【００１３】
以上のように参考例１によれば、血液中に吸収されるレーザ光線の量を検出し、また２種類のピーク波長のレーザ光線を使用して温度による影響のない、採血の必要のない血糖計を実現できるものである。
【００１４】
なお参考例１によれば、第１の受光素子４・第２の受光素子５が受光するレーザ光線を、指先を透過したものとしているが、指先によって反射したレーザ光線を受光する構成としても良いものである。すなわち、第１の受光素子４・第２の受光素子５を第１のレーザ２・第２のレーザ３と同一側に配置するようにしても良いものである。この場合、レーザ光線は指先の表面で反射されるものと指先内部の血液によって散乱され反射されるものとが存在する。いずれにしても、指先によって反射されるレーザ光線を受光する構成としても、参考例１の思想を適用することは可能である。
【００１５】
また参考例１ではレーザ光線を使用する構成としているため、吸光度を精度良く測定できるものである。つまり、レーザ光線は波長分布が極めて狭く、必要な波長に集中することが出来るものである。
【００１６】
また参考例１では、第１のレーザ１・第２のレーザ２として半導体レーザであるガリウム・アルミ・砒素（GaAlAs）を使用しているものである。このため、装置を小型に構成できるものである。
【００１７】
また参考例１では、第１のレーザ１または第２のレーザ２が照射するレーザ光線の波長を、1300nmまたは1700nmに設定しているものである。このため、血液に吸収される量が多く、温度の測定が正確にでき、従って正確な血糖値の表示が出来る血糖計を実現するものである。
【００１８】
（参考例２）
次に本発明に関連する第２の参考例について説明する。参考例２では第１の受光素子４と第２の受光素子５とを、インジゥム・ガリウム・砒素（InGaAs）を使用した１つの受光素子で兼用しているものである。インジゥム・ガリウム・砒素（InGaAs）は、受光感度が1300nmから1700nmまでの範囲で高くなっており、血糖計に使用する場合に適しているものである。
【００１９】
従って参考例２とした場合には、第１の受光素子４と第２の受光素子５とを１つの受光素子で構成でき、簡単な構成で正確な血糖値を測定できる血糖計を実現できるものである。
【００２０】
（参考例３）
次に本発明に関連する第３の参考例について説明する。参考例３では、第１のレーザ２・第２のレーザ３を半導体レーザであるガリウム・アルミ・砒素（GaAlAs）を使用した１つのレーザによって構成しているものである。つまり、半導体レーザは流れる電流を制御したり或いはレーザ素子の温度を制御することにより発振波長が変わるものである。また血液による吸光度のピーク波長は、1450nm付近を中心に±20nm程度で変わるものである。この範囲は、半導体レーザを電流制御や温度制御することによって充分実現できるものである。
【００２１】
つまり、第１の波長のレーザ光線を放射した後、電流や温度を変えることによって、第２の波長のレーザ光線を放射するようにするものである。またこの場合には、第１の受光素子４の受光タイミングと第２の受光素子５の受光タイミングとを前記レーザの放射タイミングに合わせて変えるものである。
【００２２】
このようにすれば、１つのレーザを使用することによって参考例１で説明したと、ほぼ同様に動作する血糖計を実現できるものである。つまり参考例１に比べると精度は若干低下するが、簡単な構成で正確な血糖値を測定できる血糖計を実現できるものである。
【００２３】
（実施例）
次に本発明の一実施例について説明する。図７は本発明の実施例の構成を示すブロック図である。本実施例では、第１のレーザ２・第２のレーザ３に加えて第３のレーザ１５を、また、第１の受光素子４・第２の受光素子５に加えて第３の受光素子１６を使用している。第３のレーザ１５は第３の波長を有するレーザ光線を放射するものであり、第３の受光素子１６はこの第３のレーザが放射したレーザ光線を、指先を介して受光するものである。第１の受光素子４が受光した信号は第１の受光感度検知手段８に、第２の受光素子５が受光した信号は第２の受光感度検知手段９に、第３の受光素子１６が受光した信号は第３の受光感度検知手段１７にそれぞれ伝達されている。また第１の受光感度検知手段６・第２の受光感度検知手段７の信号は、上記参考例１で説明したとおり、温度検出手段８・血糖値検出手段９に伝達されている。第３の受光感度検知手段１７の信号は、血糖値検出手段９に伝達されている。また１０は表示手段である。
【００２４】
以下本実施例の動作について説明する。本実施例では、上記参考例１と同様に、温度検知手段８が第１の受光感度検知手段６・第２の受光感度検知手段７からの信号によって血液の温度を検知している。また血糖値検出手段９は、この検知した温度によって補正した真の吸光度を演算しているものである。
【００２５】
このとき、本実施例では第１のレーザ２・第２のレーザ３と第３のレーザ１５とを使用している。つまり、レーザ光線の波長を３種類設定できるものである。従って、例えば第１のレーザと第２のレーザが放射するレーザ光線の波長を血液中の水分に良く吸収される1400nmを含んだ形として、温度を推定し、第３のレーザが放射するレーザ光線の波長を自由に設定することが出来る。つまり、1800nm付近に設定するようにすれば血液中の脂質の濃度を精度良く検出でき、660nm付近に設定すれば赤血球の濃度を精度良く検出でき、1680nm付近とすればグルコース糖の濃度を精度良き検知できるものである。
【００２６】
つまり、本実施例によれば３波長のレーザ光線を使用することによって、血液中の脂質や、赤血球の濃度や、グルコース糖の濃度つまり血糖値等を測定できる使い勝手の良い血糖計としている。
【００２７】
なお前記各実施例は血糖計に関するものとしているが、本実施例の思想を例えば半導体等の洗浄装置に適用することもできる。つまり、半導体は洗浄水の清浄度が品質に対して非常に影響するものであり、不純物を構成する物質の濃度管理が重要なものである。そこで本実施例の思想を適用して、レーザ光線と受光素子を使用して洗浄水の濃度測定を実施すれば、サンプルを採取する必要なく濃度管理が実行できるものである。なおこの場合には、第１のレーザ２または第２のレーザ３が照射するレーザ光線は、1300nmまたは1700nmにピークを有するようにすると効果的に測定が出来るものである。すなわち、1300nmから1700nmの波長付近は水溶液の成分と水の分子とが結合して形成した成分の濃度による光の吸光度の変化が大きく出るところである。
【００２８】
【発明の効果】
本発明は、第１の波長のレーザ光線を照射する第１のレーザと、第２の波長のレーザ光線を照射する第２のレーザと、第３の波長のレーザ光線を照射する第３のレーザと、指先を透過したあるいは指先内の組織で散乱し反射したレーザ光線を受光する第１・第２・第３の受光素子と、第１の受光素子の受光信号から第１の波長の吸光度を感知する第１の受光感度検知手段と、第２の受光素子の受光信号から第２の波長の吸光度を感知する第２の受光感度検知手段と、第３の受光素子の受光信号から第３の波長の吸光度を感知する第３の受光感度検知手段と、第１の受光感度検知手段と第２の受光感度検知手段の信号から血液の温度を検出する温度検出手段と、温度検出手段が検出した温度によって第１の受光感度検知手段・第２の受光感度検知手段・第３の受光感度検知手段が検知した吸光度を補正し血液中の成分の濃度を演算すると共に、演算した成分の濃度を表示手段に表示する血糖値検出手段とを備えた構成として、血液中の各種成分の濃度を測定できる血糖計を実現するものである。
【００２９】
また、本発明は、第１のレーザまたは第２のレーザが照射するレーザ光線は、1400nmを含んだピークを有し、第３のレーザが照射するレーザ光線は660nmまたは1680nmまたは1800nmにピークを設定した構成として、血液中の赤血球の濃度や血液中のグルコース糖の濃度や血液中の脂質の濃度を正確に測定できる血糖計を実現できるものである。
【図面の簡単な説明】
【図１】 本発明に関連する第１の参考例である血糖計の構成を示すブロック図
【図２】 同、温度Ｔ１で波長を変えた場合の吸光度の変化を示す特性図
【図３】 同、温度をＴ２としたときの波長毎の吸光度を示す特性図
【図４】 同、温度と吸光度の差の関係を示す特性図
【図５】 同、温度と見かけの吸光度の差と真の吸光度の差の関係を示す特性図
【図６】 同、真の吸光度の差と血糖値との関係を示す特性図
【図７】 本発明の一実施例である血糖計の構成を示すブロック図
【符号の説明】
２ 第１のレーザ
３ 第２のレーザ
４ 第１の受光素子
５ 第２の受光素子
６ 第１受光感度検知手段
７ 第２受光感度検知手段
８ 温度検出手段
９ 血糖値検出手段
１０ 表示手段[0001]
BACKGROUND OF THE INVENTION
The present invention relates to a blood glucose meter that can easily measure sugar in blood.
[0002]
[Prior art]
Conventionally, as a blood glucose level, a GOD method for measuring glucose level by degrading glucose with glucose oxidase (GOD) has been widely used. Blood glucose measurement by the GOD method can be easily performed in a relatively short time.
[0003]
[Problems to be solved by the invention]
The GOD method is a method in which blood must be collected with a puncture needle, but is painful to the patient. Further, when the concentration of glucose sugar is small, there is a problem that the influence of temperature is large and the blood sugar level cannot be measured accurately.
[0004]
[Means for Solving the Problems]
The present invention uses a laser and a light-receiving element to detect the amount of laser light absorbed in blood, and uses two types of peak wavelength laser light to avoid the influence of temperature, requiring blood collection. This is a blood glucose meter without the above.
[0005]
DETAILED DESCRIPTION OF THE INVENTION
The present invention is a blood glucose meter that uses three-wavelength laser beams by the first, second, and third lasers, can accurately detect the temperature, and can measure the concentration of various components in the blood.
[0006]
In addition, the present invention can accurately set the peak of the laser beam irradiated by the third laser to accurately measure the concentration of erythrocytes in blood, the concentration of glucose sugars in blood, and the concentration of lipids in blood. It is a blood glucose meter.
[0007]
【Example】
(Reference Example 1)
A first reference example related to the present invention will be described below. FIG. 1 is a block diagram showing the configuration of Reference Example 1 . The probe 1 to inserting the fingertip, and the first laser 2-second laser 3-first light-receiving element 4, the second light receiving element 5 is arranged. The first laser 2 emits a laser beam having a first wavelength, and the second laser 3 emits a laser beam having a second wavelength. In this embodiment, gallium aluminum arsenide (GaAlAs) is used as the first laser 2 and the second laser 3, and 1300 nm is used as the first wavelength and 1700 nm is used as the second wavelength. The laser beams emitted by the first laser 2 and the second laser 3 are absorbed and attenuated by the blood in the fingertip when passing through the fingertip inserted into the probe 1, and the first light receiving element 4. Two light receiving elements 5 receive the light. The first light receiving element 4 and the second light receiving element 5 are disposed so as to face the first laser 2 and the second laser 3, respectively. Signals received by the first light receiving element 4 and the second light receiving element 5 are transmitted to the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7, respectively. The first light receiving sensitivity detecting means 6 calculates the attenuation of the laser beam having the first wavelength from the signal received by the first light receiving element 4, that is, the absorbance of the laser beam having the first wavelength absorbed by the blood and attenuated. Calculate. The second light receiving sensitivity detecting means 7 calculates the attenuation of the laser beam having the second wavelength from the signal received by the second light receiving element 5, that is, the absorbance of the laser beam having the second wavelength absorbed by the blood and attenuated. Calculate. Signals from the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7 are transmitted to the temperature detecting means 8. The temperature detecting means 8 stores in advance the relationship between the temperature T and the difference ΔA between the absorbance of the laser beam of the first wavelength and the absorbance of the laser beam of the second wavelength as shown in the graph of FIG. . The temperature signal detected by the temperature detecting means 8 and the signals of the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7 are transmitted to the blood sugar level detecting means 9. The blood sugar level detection means 9 corrects the difference ΔA in the absorbance of the laser beams of the two wavelengths with the temperature signal, and calculates the difference in the true absorbance absorbed by the blood of the fingertip. Further, the blood glucose level C is calculated from the difference in true absorbance, and the calculated blood glucose level is displayed on the display means 11.
[0008]
The operation of Reference Example 1 will be described below. When a fingertip is inserted into the probe 1 and a switch (not shown) is turned on, blood glucose level measurement is started. The first wavelength laser beam and the second wavelength laser beam emitted by the first laser 2 and the second laser 3 are transmitted through the fingertip and attenuated in a state where the first light receiving element 3 and the second laser beam are attenuated. Light is received by the light receiving element 4. The first light receiving element 4 and the second light receiving element 5 generate an electric signal corresponding to the amount of received light, and transmit this electric signal to the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7, respectively. To do. The first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7 are configured to output the laser beam emitted by the first laser 2 and the second laser 3 and the first light receiving element 4 and the second light receiving element. The absorbance at the first wavelength and the second wavelength, which is absorbed and attenuated by blood flowing through the fingertip, is obtained by taking the ratio of the received light amount received by 5. This absorbance information is transmitted to the temperature detecting means 8.
[0009]
Next, the temperature detection operation of the temperature detection means 8 will be described. FIG. 2 shows a state in which light is absorbed and attenuated by blood having a certain blood glucose level with the wavelength being changed at a temperature of T 1 . In this experiment, the absorbance at the wavelength λmax has a peak at A 1 , the absorbance decreases as the wavelength deviates from λmax, and becomes the lowest absorbance A 2 at λmin. The Figure 3 is a state where the temperature was T 2, a state that is being absorbance by the blood with a certain blood glucose attenuation is shown by changing the wavelength. In this experiment, the absorbance at the wavelength λmin has a peak at A 3 , and the absorbance decreases as the wavelength deviates from λmin, with the lowest absorbance A 4 at λmax. From this result, it can be seen that the difference ΔA between the absorbance at the wavelength λmax and the absorbance at the wavelength λmin decreases as the temperature increases. This is shown in FIG. In FIG. 4, the horizontal axis represents the blood temperature, and the vertical axis represents the absorbance difference ΔA. Therefore, when ΔA is determined, the temperature T is determined. The λmin and λmax are matched with the second wavelength and the first wavelength, respectively. Therefore, the temperature detecting means 8 can calculate the blood temperature T from the signals of the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7.
[0010]
The blood temperature T calculated by the temperature detecting means 8 in this way is transmitted to the blood sugar level detecting means 9 together with the signals of the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7.
[0011]
The absorbance difference ΔA output from the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7 is determined by the blood glucose level C as shown in Equation 1.
[0012]
ΔA = K 1 * C + B K 1 : proportionality constant (Equation 1)
The proportionality constant K 1 in Equation 1 changes depending on the blood temperature. Thus, the inventors have repeated experiments to find the relationship between the temperature T and the apparent absorbance difference ΔA 0 and the true absorbance difference ΔA 1 as shown in FIG. For example, if the difference in apparent absorbance is ΔA 01 at temperature T 1 , the difference in true absorbance is ΔA 11 , and if the difference in apparent absorbance at temperature T 2 is ΔA 02 , the difference in true absorbance Is ΔA 12 and if the temperature is T 3 and the apparent absorbance difference is ΔA 03 , the true absorbance difference is ΔA 13 . FIG. 6 is a graph showing the relationship shown in Equation 1, and shows the relationship between the true absorbance difference ΔA 1 and the blood glucose level C. For example, if the true absorbance difference is ΔA 11 , the blood glucose level is C 0 , and if the true absorbance difference is ΔA 12 , the blood glucose level is C 1 . The blood glucose level detection means 9 includes the data shown in FIGS. Thus, the blood glucose level C is calculated from the temperature data T received from the temperature detecting means 8 and the signals of the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7. The blood glucose level C is displayed on the display means 10.
[0013]
As described above, according to Reference Example 1 , the amount of laser beam absorbed in blood is detected, and blood glucose that is not affected by temperature and that does not require blood collection using two types of peak wavelength laser beams. The total can be realized.
[0014]
According to Reference Example 1 , the laser beam received by the first light receiving element 4 and the second light receiving element 5 is transmitted through the fingertip. However, the laser beam reflected by the fingertip may be received. Is. That is, the first light receiving element 4 and the second light receiving element 5 may be arranged on the same side as the first laser 2 and the second laser 3. In this case, there are laser beams that are reflected by the surface of the fingertip and those that are scattered and reflected by blood inside the fingertip. In any case, the idea of Reference Example 1 can be applied even if the laser beam reflected by the fingertip is received.
[0015]
In Reference Example 1 , since the laser beam is used, the absorbance can be measured with high accuracy. That is, the laser beam has a very narrow wavelength distribution and can be concentrated at a required wavelength.
[0016]
In Reference Example 1 , gallium, aluminum, and arsenic (GaAlAs), which are semiconductor lasers, are used as the first laser 1 and the second laser 2. For this reason, an apparatus can be comprised small.
[0017]
In Reference Example 1 , the wavelength of the laser beam irradiated by the first laser 1 or the second laser 2 is set to 1300 nm or 1700 nm. For this reason, a blood glucose meter that can absorb a large amount of blood, can accurately measure temperature, and can display an accurate blood glucose level is realized.
[0018]
(Reference Example 2)
Next , a second reference example related to the present invention will be described. In Reference Example 2 , the first light receiving element 4 and the second light receiving element 5 are combined with one light receiving element using indium gallium arsenide (InGaAs). Indium gallium arsenide (InGaAs) has high photosensitivity in the range from 1300 nm to 1700 nm, and is suitable for use in a blood glucose meter.
[0019]
Therefore, in the case of Reference Example 2 , the first light receiving element 4 and the second light receiving element 5 can be configured by one light receiving element, and a blood glucose meter capable of measuring an accurate blood glucose level with a simple configuration can be realized. It is.
[0020]
(Reference Example 3)
Next , a third reference example related to the present invention will be described. In Reference Example 3 , the first laser 2 and the second laser 3 are configured by one laser using semiconductor lasers such as gallium, aluminum, and arsenic (GaAlAs). That is, the oscillation wavelength of the semiconductor laser is changed by controlling the flowing current or controlling the temperature of the laser element. In addition, the peak wavelength of absorbance due to blood varies about ± 20 nm, centered around 1450 nm. This range can be sufficiently realized by controlling the current and temperature of the semiconductor laser.
[0021]
That is, after the laser beam having the first wavelength is emitted, the laser beam having the second wavelength is emitted by changing the current and the temperature. In this case, the light receiving timing of the first light receiving element 4 and the light receiving timing of the second light receiving element 5 are changed in accordance with the emission timing of the laser.
[0022]
In this way, a blood glucose meter that operates in substantially the same manner as described in Reference Example 1 can be realized by using one laser. That is, although the accuracy is slightly lower than that of Reference Example 1 , a blood glucose meter capable of measuring an accurate blood glucose level with a simple configuration can be realized.
[0023]
(Example)
Next, an embodiment of the present invention will be described. FIG. 7 is a block diagram showing the configuration of the embodiment of the present invention . In this embodiment, a third laser 15 is added in addition to the first laser 2 and the second laser 3, and a third light receiving element 16 is added in addition to the first light receiving element 4 and the second light receiving element 5. Is used. The third laser 15 emits a laser beam having a third wavelength, and the third light receiving element 16 receives the laser beam emitted by the third laser via a fingertip. The signal received by the first light receiving element 4 is received by the first light receiving sensitivity detecting means 8, the signal received by the second light receiving element 5 is received by the second light receiving sensitivity detecting means 9, and the third light receiving element 16 is received by the third light receiving element 16. The transmitted signals are transmitted to the third light receiving sensitivity detecting means 17, respectively. The signals of the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7 are transmitted to the temperature detecting means 8 and the blood sugar level detecting means 9 as described in the first reference example . The signal of the third light receiving sensitivity detecting means 17 is transmitted to the blood sugar level detecting means 9. Reference numeral 10 denotes display means.
[0024]
The operation of this embodiment will be described below. In the present embodiment, the temperature detecting means 8 detects the blood temperature based on signals from the first light receiving sensitivity detecting means 6 and the second light receiving sensitivity detecting means 7 as in the first reference example . The blood glucose level detection means 9 calculates the true absorbance corrected by the detected temperature.
[0025]
At this time, in the present embodiment, the first laser 2, the second laser 3, and the third laser 15 are used. That is, three types of laser beam wavelengths can be set. Therefore, for example, assuming that the wavelength of the laser beam emitted by the first laser and the second laser includes 1400 nm that is well absorbed by moisture in blood, the temperature is estimated, and the laser beam emitted by the third laser. The wavelength can be freely set. In other words, if it is set near 1800 nm, the lipid concentration in the blood can be detected with high accuracy, if it is set near 660 nm, the concentration of red blood cells can be detected with high accuracy, and if it is set near 1680 nm, the glucose sugar concentration can be detected with high accuracy. It can be detected.
[0026]
That is, according to the present embodiment, by using a laser beam of three wavelengths, the blood glucose meter is easy to use and can measure the concentration of lipids in blood, red blood cells, glucose sugar concentration, that is, blood sugar level and the like.
[0027]
Although each of the above embodiments relates to a blood glucose meter, the idea of this embodiment can be applied to a cleaning device such as a semiconductor. In other words, the cleanliness of the cleaning water has a great influence on the quality of the semiconductor, and the concentration management of the substances constituting the impurities is important. Therefore, by applying the idea of the present embodiment and measuring the concentration of cleaning water using a laser beam and a light receiving element, concentration management can be performed without the need to collect a sample. In this case, the laser beam irradiated by the first laser 2 or the second laser 3 can be effectively measured by having a peak at 1300 nm or 1700 nm. That is, in the vicinity of the wavelength from 1300 nm to 1700 nm, the change in light absorbance largely depends on the concentration of the component formed by combining the components of the aqueous solution and the water molecules.
[0028]
【The invention's effect】
The present invention includes a first laser that irradiates a laser beam having a first wavelength, a second laser that irradiates a laser beam having a second wavelength, and a third laser that irradiates a laser beam having a third wavelength. The first, second, and third light receiving elements that receive the laser beam that has passed through the fingertip or scattered and reflected by the tissue in the fingertip, and the absorbance at the first wavelength from the light reception signal of the first light receiving element. A first light receiving sensitivity detecting means for sensing; a second light receiving sensitivity detecting means for detecting the absorbance of the second wavelength from the light receiving signal of the second light receiving element; and a third light receiving signal from the light receiving signal of the third light receiving element. A third light receiving sensitivity detecting means for detecting the absorbance of the wavelength, a temperature detecting means for detecting the blood temperature from the signals of the first light receiving sensitivity detecting means and the second light receiving sensitivity detecting means, and the temperature detecting means First light sensitivity detection means and second light sensitivity detection according to temperature A blood glucose level detecting means for correcting the absorbance detected by the third light receiving sensitivity detecting means and calculating the concentration of the component in the blood, and displaying the calculated concentration of the component on the display means; A blood glucose meter capable of measuring the concentration of various components therein is realized.
[0029]
In the present invention, the laser beam irradiated by the first laser or the second laser has a peak including 1400 nm, and the laser beam irradiated by the third laser sets a peak at 660 nm, 1680 nm, or 1800 nm. Thus, a blood glucose meter capable of accurately measuring the concentration of red blood cells in blood, the concentration of glucose sugars in blood, and the concentration of lipids in blood can be realized.
[Brief description of the drawings]
FIG. 1 is a block diagram showing the configuration of a blood glucose meter as a first reference example related to the present invention . FIG. 2 is a characteristic diagram showing changes in absorbance when the wavelength is changed at temperature T1. Fig. 4 is a characteristic diagram showing the absorbance at each wavelength when the temperature is T2. Fig. 5 is a characteristic diagram showing the relationship between the temperature and the absorbance. Fig. 5 is the true difference between the temperature and the apparent absorbance. FIG. 6 is a characteristic diagram showing the relationship between true absorbance difference and blood glucose level. FIG. 7 is a block diagram showing the configuration of a blood glucose meter according to one embodiment of the present invention. [Explanation of symbols]
2 1st laser 3 2nd laser 4 1st light receiving element 5 2nd light receiving element 6 1st light reception sensitivity detection means 7 2nd light reception sensitivity detection means 8 Temperature detection means 9 Blood glucose level detection means 10 Display means

Claims (2)

第１の波長のレーザ光線を照射する第１のレーザと、第２の波長のレーザ光線を照射する第２のレーザと、第３の波長のレーザ光線を照射する第３のレーザと、指先を透過したあるいは指先内の組織で散乱し反射したレーザ光線を受光する第１・第２・第３の受光素子と、第１の受光素子の受光信号から第１の波長の吸光度を感知する第１の受光感度検知手段と、第２の受光素子の受光信号から第２の波長の吸光度を感知する第２の受光感度検知手段と、第３の受光素子の受光信号から第３の波長の吸光度を感知する第３の受光感度検知手段と、第１の受光感度検知手段と第２の受光感度検知手段の信号から血液の温度を検出する温度検出手段と、温度検出手段が検出した温度によって第１の受光感度検知手段・第２の受光感度検知手段・第３の受光感度検知手段が検知した吸光度を補正し血液中の成分の濃度を演算すると共に、演算した成分の濃度を表示手段に表示する血糖値検出手段とを備えた血糖計。  A first laser that irradiates a laser beam of a first wavelength, a second laser that irradiates a laser beam of a second wavelength, a third laser that irradiates a laser beam of a third wavelength, and a fingertip First, second, and third light receiving elements that receive the laser beam that has been transmitted or scattered and reflected by the tissue in the fingertip, and a first that senses the absorbance at the first wavelength from the light reception signal of the first light receiving element. Light receiving sensitivity detecting means, second light receiving sensitivity detecting means for sensing the absorbance of the second wavelength from the light receiving signal of the second light receiving element, and absorbance of the third wavelength from the light receiving signal of the third light receiving element. A first light receiving sensitivity detecting means for sensing, a temperature detecting means for detecting a blood temperature from signals of the first light receiving sensitivity detecting means and the second light receiving sensitivity detecting means, and a temperature detected by the temperature detecting means. Light receiving sensitivity detecting means, second light receiving sensitivity detecting means, second Light-receiving sensitivity with detection means for calculating the concentrations of the components of the corrected blood absorbance was detected, the blood glucose meter and a blood glucose level detecting means for displaying on the display means the concentration of computed components. 第１のレーザまたは第２のレーザが照射するレーザ光線は、1400nmを含んだピークを有し、第３のレーザが照射するレーザ光線は660nmまたは1680nmまたは1800nmにピークを設定した請求項１記載の血糖計。The laser beam first laser or the second laser irradiation has a peak containing 1400 nm, according to claim 1, wherein the laser beam third laser is irradiated is set to peak at 660nm or 1680nm or 1800nm Blood glucose meter.
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