JP6621734B2 - Blood concentration measurement value calibration device - Google Patents
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- 239000008280 blood Substances 0.000 title claims description 107
- 210000004369 blood Anatomy 0.000 title claims description 107
- 238000005259 measurement Methods 0.000 title claims description 46
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 41
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- 239000011347 resin Substances 0.000 description 27
- 229920005989 resin Polymers 0.000 description 27
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- 230000003287 optical effect Effects 0.000 description 6
- 239000012530 fluid Substances 0.000 description 4
- 238000001631 haemodialysis Methods 0.000 description 4
- 230000000322 hemodialysis Effects 0.000 description 4
- 239000007788 liquid Substances 0.000 description 4
- 230000005540 biological transmission Effects 0.000 description 3
- 230000017531 blood circulation Effects 0.000 description 3
- 210000001367 artery Anatomy 0.000 description 2
- 235000013405 beer Nutrition 0.000 description 2
- 238000007796 conventional method Methods 0.000 description 2
- RZTAMFZIAATZDJ-UHFFFAOYSA-N felodipine Chemical compound CCOC(=O)C1=C(C)NC(C)=C(C(=O)OC)C1C1=CC=CC(Cl)=C1Cl RZTAMFZIAATZDJ-UHFFFAOYSA-N 0.000 description 2
- 239000011521 glass Substances 0.000 description 2
- 239000012510 hollow fiber Substances 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 210000003462 vein Anatomy 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 1
- 239000012503 blood component Substances 0.000 description 1
- 238000004140 cleaning Methods 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 230000018044 dehydration Effects 0.000 description 1
- 238000006297 dehydration reaction Methods 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000011160 research Methods 0.000 description 1
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3607—Regulation parameters
- A61M1/3609—Physical characteristics of the blood, e.g. haematocrit, urea
- A61M1/3612—Physical characteristics of the blood, e.g. haematocrit, urea after treatment
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/27—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands using photo-electric detection ; circuits for computing concentration
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61M2205/00—General characteristics of the apparatus
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- A61M2205/3306—Optical measuring means
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/20—Blood composition characteristics
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- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
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Description
この発明は、光透過性の管路内を流れる血液の濃度をランベルト−ベールの法則に基づいて測定した測定値を較正する装置に関するものである。 The present invention relates to an apparatus for calibrating a measurement value obtained by measuring the concentration of blood flowing in a light-transmitting pipe line based on the Lambert-Beer law.
従来のランベルト−ベールの法則に基づく流体濃度の測定方法としては、例えば特許文献１記載のものが知られており、ここにおける測定方法は、半導体ウエハを洗浄処理する流体としての処理液の濃度を測定するもので、処理液供給配管の途中に測定体を複数設け、各測定体内に、処理液中を通過する光の光路長さを異ならせた光透過部を設け、処理液の性質に応じた光路長さの光透過部に光源からの光を供給し、その光透過部において処理液中を透過した光を光検出器で受光してその光の強度を調べ、その光の強度からランベルト−ベールの法則に基づいて処理液の濃度を求めている。
As a conventional method for measuring a fluid concentration based on the Lambert-Beer law, for example, a method described in
ところで、上記従来の流体濃度の測定方法では、各光透過部における光路長さが厳密に判明しており、それゆえあらかじめ光路長さが設定された計算式を用いて流体の濃度を容易に求めることができる。その一方で、例えば樹脂チューブやガラス管等の光透過性の管路内を流れる血液の濃度が測定できると医療等の分野において極めて役立つであろうということが予想される。 By the way, in the above conventional method for measuring fluid concentration, the optical path length in each light transmitting section is strictly determined, and therefore the fluid concentration is easily obtained using a calculation formula in which the optical path length is set in advance. be able to. On the other hand, it is expected that it will be extremely useful in the field of medicine and the like if the concentration of blood flowing in a light-transmitting conduit such as a resin tube or a glass tube can be measured.
このため本願出願人は、ＰＣＴ／ＪＰ／２０１２／０７５０８２号およびその優先権を主張したＰＣＴ／ＪＰ／２０１３／０５４６６４号にて、樹脂チューブやガラス管等の光透過性の管路内を流れる血液の濃度を測定する装置を提案しており、この装置は、光透過性の管路の延在方向に沿ってその管路表面上に並んだ３箇所の光供給位置Ａ，Ｂ，Ｃからそれらに対し管路の反対側の表面上で管路直径方向にそれぞれ対向する３箇所の受光位置に位置する受光センサまで管路内を透過して到達する光の各受光位置での強度から、管路を直角に横切る光を受光する場合と管路を斜めに横切る光を受光する場合とのそれぞれについてランベルト−ベールの法則に基づく関係式を求めて連立させることで、管路の内径や壁厚さ等を定めることなく管路内の血液の濃度を求め得るようにしている。 For this reason, the applicant of the present application described in PCT / JP / 2012/075082 and PCT / JP / 2013/054664 which claimed the priority thereof, blood flowing in a light-transmitting conduit such as a resin tube or a glass tube. Has been proposed, and this device has three light supply positions A, B, and C arranged on the surface of the pipe along the extending direction of the light transmissive pipe. From the intensity at each light receiving position of the light passing through the pipe to the light receiving sensors located at the three light receiving positions facing each other in the diameter direction of the pipe on the surface opposite to the pipe, By obtaining the relational expression based on the Lambert-Beer law for each of the case of receiving light crossing the road at right angles and the case of receiving light crossing the pipe diagonally, the inner diameter and wall thickness of the pipe Pipe without deciding It is adapted to be determined the concentration of blood in the.
しかしながら、図３に、光透過性の管路としての４種類の樹脂チューブ（チューブＡ〜Ｄ）について受光センサの出力値をそれぞれ示すように、この濃度測定装置では、各濃度に対応するセンサ出力値が得られるものの、樹脂チューブが異なるとそのセンサ出力値の間に一定量のオフセットが生じるという問題があり、その原因として考えられるのは、光供給位置から供給する光の、チューブ壁内を通る回り込みである。 However, as shown in FIG. 3, the output values of the light receiving sensors are shown for four types of resin tubes (tubes A to D) as light-transmitting conduits. In this concentration measuring device, the sensor output corresponding to each concentration is shown. Although a value can be obtained, there is a problem that if the resin tube is different, a certain amount of offset occurs between the sensor output values. The possible cause is that the light supplied from the light supply position is inside the tube wall. It is a wraparound.
光供給位置Ａ，Ｃからそれらに対し管路の反対側の表面上で管路直径方向にそれぞれ対向する２箇所の受光位置に位置する受光センサまで管路内を透過して到達する光の経路を考え、図４に示すように、光供給位置Ａ，Ｃからそれぞれ管路を直角に横切る光の光量をＩＡＧ，ＩＣＧとするとともに、光供給位置Ａ，Ｃからそれぞれ管路を斜めに横切る光の光量をＩＡＦ，ＩＣＦとし、管路を斜めに横切る場合の光路長さの増加分をｌＡＦ，ｌＣＦとすると、上記の濃度測定装置の濃度算出の基本式は、樹脂チューブ内の血液の吸光係数をεＨ、濃度をＣＨとして、
この一方、光供給位置Ａ，Ｃからそれぞれ管路を直角方向に回り込む回り込み光量をＥＡＧ，ＥＣＧ、光供給位置Ａ，Ｃからそれぞれ管路を斜め方向に回り込む回り込み光量をＥＡＦ，ＥＣＦとすると、濃度算出の基本式は、
これら回り込み光量ＥＡＧ，ＥＣＧ，ＥＡＦ，ＥＣＦの値には、樹脂チューブの種類や製造ロット等の相違によるチューブ壁の入光率、透過率および内部反射等の相違も含まれ、回り込み光量の影響を解析的に求めるのは極めて困難で、樹脂チューブの相違によるオフセット量を計算で較正することは実際上できなかった。 These sneak light amounts EAG, ECG, EAF, and ECF values include differences in the light incident rate, transmittance, and internal reflection of the tube wall due to differences in resin tube types and production lots. It was extremely difficult to obtain analytically, and it was practically impossible to calibrate the offset amount due to the difference in the resin tube by calculation.
これにつき本願発明者がさらに研究を進めたところ、上記の濃度測定装置の適用対象の一つである血液透析においては正確な量の除水が可能であることを知見し、これを利用することに想到した。 As a result of further research by the inventor of the present application, it has been found that an accurate amount of water can be removed in hemodialysis, which is one of the application targets of the above-described concentration measuring device. I came up with it.
この発明は、本発明者が先に提案した血液濃度測定装置の課題を上述の知見に基づいて有利に解決するものであり、この発明の血液濃度測定値較正装置は、光透過性の管壁を持つ管路内を流れる血液の濃度を血液濃度測定装置がランベルト−ベールの法則に基づいて測定した測定値を較正する装置において、
前記管路の途中に設けられた除水装置が前記管路内を流れる血液からの徐水を行っている間に、前記管路の前記徐水装置の上流部分に設けられた前記血液濃度測定装置および下流部分に設けられた前記血液濃度測定装置がそれぞれ測定した、互いに同一のオフセット量をそれぞれ含む前記徐水装置による徐水前および徐水後の血液濃度の測定値の差を求める除水前後測定値差演算手段と、
前記徐水前および徐水後の血液濃度の測定値の差と、前記管路内を流れる血液の、前記徐水装置による徐水前の単位時間当たり流量および前記徐水装置による単位時間当たりの徐水量とに基づいて、前記血液濃度測定装置の測定値を、前記オフセット量を除いた値に較正する測定値較正手段と、
を具えることを特徴とするものである。
The present invention advantageously solves the problem of the blood concentration measuring apparatus previously proposed by the present inventor based on the above-mentioned knowledge, and the blood concentration measurement value calibration apparatus according to the present invention has a light-transmitting tube wall. In the apparatus for calibrating the measured value of the blood concentration measuring device based on the Lambert-Beer law, the concentration of blood flowing in the pipe line having
The blood concentration measurement provided in the upstream portion of the slow water device in the pipe while the dewatering device provided in the middle of the pipe performs slow water from the blood flowing in the pipe Measurement before and after dehydration to determine the difference between blood concentration measurement values before and after slow water measurement by the slow water device respectively including the same offset amount respectively measured by the blood concentration measurement device provided in the device and downstream part A value difference calculation means;
And the difference between the measured values of the blood concentration after the Jomizu before and Jomizu, blood flowing through the conduit, and Xu water per unit time by the Jomizu device the Jomizu device volume flow per unit of time and before Jomizu by Based on the measurement value calibration means for calibrating the measurement value of the blood concentration measurement device to a value excluding the offset amount ,
It is characterized by comprising .
かかるこの発明の血液濃度測定値較正装置によれば、光透過性の管壁を持つ管路内を流れる血液の濃度を血液濃度測定装置が測定した測定値を較正するに際し、前記管路内を流れる血液をその管路の途中に設けられた徐水装置に通し、その徐水装置による徐水前の血液濃度および徐水後の血液濃度の、互いに同一のオフセット量をそれぞれ含む測定値の間の差と、前記管路内を流れる血液の、前記徐水装置による徐水前の単位時間当たり流量および前記徐水装置による単位時間当たりの徐水量と、に基づいて前記測定値を、前記オフセット量を除いた値に較正するので、測定値から管路固有のオフセット量の影響を除去して実際の血液濃度を高精度に求めることができる。 According to the blood concentration measurement value calibration device of the present invention, when calibrating the measurement value measured by the blood concentration measurement device with respect to the concentration of blood flowing in the pipeline having a light-transmitting tube wall, through blood flowing through the Jomizu device provided in the middle of the line, the difference between the Jomizu device of the blood concentration after the blood concentration and Jomizu before Jomizu by the measured values including the same offset amounts respectively to each other If, blood flowing through the conduit, and Xu water per unit time by the Jomizu device per unit time flow amount before Jomizu by and the Jomizu device, the measured values based on, except for the offset amount since calibration values can be obtained the actual blood concentration from the measured value to remove the influence of the pipe-specific offset amount with high accuracy.
そして、この発明の血液濃度測定値較正装置においては、前記徐水装置による徐水前および徐水後の血液濃度は、前記管路の、徐水装置の上流部分および下流部分に設けた２台の血液濃度測定装置で、徐水装置が徐水を行っている間に測定する。 In the blood concentration measurement value calibration apparatus according to the present invention, the blood concentrations before and after the slow watering by the slow water device are the two blood provided in the upstream portion and the downstream portion of the slow water device in the conduit. a concentration measuring device is measured during Jomizu terminal is performing Jomizu.
以下、本発明の実施の形態を実施例によって、図面に基づき詳細に説明する。ここに、図１は、この発明の血液濃度測定値較正装置の一実施形態を実施するランベルト−ベールの法則に基づく血液濃度測定装置を用いた血液透析システムを例示する説明図である。 Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. FIG. 1 is an explanatory view illustrating a hemodialysis system using a blood concentration measuring device based on the Lambert-Beer law, which implements one embodiment of the blood concentration measurement value calibration device of the present invention.
この実施形態の血液濃度測定値較正装置は、光透過性の管壁を持つ管路としての実質的に透明な樹脂チューブ内を流れる血液の濃度をランベルト−ベールの法則に基づいて測定する血液濃度測定装置での測定値を較正するものであり、ここでは、人工透析対象患者の腕の動脈に接続した樹脂チューブとその患者の腕の静脈に接続した樹脂チューブとを徐水装置としてのダイアライザーの血液流入口と血液流出口とにそれぞれ接続するとともに、それらの樹脂チューブを血液濃度測定装置１と血液濃度測定装置２とにそれぞれ装着し、動脈側の樹脂チューブを血液ポンプに装着して単位時間当たり流量Ｑの血液を患者の腕の動脈からダイアライザーに圧送可能とし、ダイアライザーの透析液流入口に透析液を供給することで、ダイアライザー内の中空糸内を通る血液からダイアライザー内でその中空糸を囲んで流れる透析液に濃度差により水を単位時間当たり所定量ｑだけ抽出除去し、単位時間当たり流量Ｑから所定量ｑの水を除去した血液を患者の腕の静脈に戻すとともに、除去した所定量ｑの水を含む透析液をダイアライザーの透析液流出口から流出させる。
Blood Concentration measurements calibration apparatus of this embodiment, substantially the concentration of the blood flowing through the transparent resin in the tube as a conduit having a light permeable tube wall Lambert - blood concentration measured based on Beer's Law The measurement value in the measuring device is calibrated. Here, the resin tube connected to the artery of the arm of the patient to be artificially dialyzed and the resin tube connected to the vein of the arm of the patient are connected to the dialyzer as a slow water device. Connected to the blood inlet and the blood outlet, respectively, the resin tubes are attached to the blood concentration measuring
ここで、血液濃度測定装置１および血液濃度測定装置２ではそれぞれ、光源としての例えば３つの発光ダイオードから出力された光が、樹脂チューブの延在方向に沿って互いに隣接して並ぶその樹脂チューブの表面上の例えば３箇所に位置する光供給箇所で樹脂チューブ内に供給され、樹脂チューブのそれらの発光ダイオードに近い側のチューブ壁と、樹脂チューブ内の血液と、それらの発光ダイオードから遠い側（反対側）のチューブ壁とを通過して、それらの光供給箇所に対しその樹脂チューブの直径方向の反対側に位置する樹脂チューブの表面上の例えば３箇所の受光箇所で例えば３つの光センサに、血液流を直角に横切る経路および血液流を斜めに横切る経路を通って到達し、光経路長さおよび樹脂チューブ内の血液の濃度の影響で減衰した光を受光したそれらの光センサの出力信号を入力されたコンピュータが、ランベルトベールの法則に基づく演算を行って、樹脂チューブ内の血液濃度に対応する測定値（表示血液濃度）ＣＨＡ，ＣＨＢを出力する（詳細は前述のＰＣＴ／ＪＰ／２０１２／０７５０８２号およびその優先権を主張したＰＣＴ／ＪＰ／２０１３／０５４６６４号の明細書を参照のこと）。
Here, in each of the blood concentration measuring
ところで、樹脂チューブのチューブ壁に供給された光は、樹脂チューブ内の血液を横切るだけでなくそのチューブ壁内をチューブ壁に沿って回りこんでも光センサに到達する。このため、血液濃度測定装置１および血液濃度測定装置２の徐水後表示血液濃度ＣＨＡおよび徐水前表示血液濃度ＣＨＢは、種類や製造ロット等によって厚さや材質等が異なるチューブ壁に応じたオフセット量を含んだものとなる。そこで、この実施形態の較正装置では、血液濃度測定装置１および血液濃度測定装置２の基準点および濃度勾配は互いに同一に調整されているものとして、以下の計算により、オフセット量をそれぞれ除いた徐水後実血液濃度ＨＣＨＡおよび徐水前実血液濃度ＨＣＨＢを求める。
By the way, the light supplied to the tube wall of the resin tube reaches the optical sensor not only across the blood in the resin tube but also around the tube wall along the tube wall. Therefore, the post-slow water display blood concentration C HA and the pre-slow water display blood concentration C HB of the blood
血液濃度測定装置１および血液濃度測定装置２の感度は正しいので、測定値の差は正しいことから、
(1)式よりＨＣＨＢを右辺に移項して、
例えば、単位時間当たり血液流量Ｑ＝２００ｍｌ／ｍｉｎ
単位時間当たり徐水量 ｑ＝ ２０ｍｌ／ｍｉｎ
のとき、除水前表示血液濃度Ｃ ＨＢ ＝２３％
徐水後表示血液濃度Ｃ ＨＡ ＝２５％
であったとすると、(4)式にこれらの数値を代入して、
徐水前実血液濃度ＨＣＨＢ＝１８．００％
これを(3)式に代入して、
徐水後実血液濃度ＨＣＨＡ＝２０．００％
となり、オフセット量を除いた実血液濃度は、徐水前１８．００％、徐水後２０．００％と較正される。
これらの演算および処理は上記血液濃度測定装置１，２の上記コンピュータにより行われる。従ってそれらのコンピュータは、除水前後測定値差演算手段と、測定値較正手段とを構成する。
For example, blood flow rate per unit time Q = 200 ml / min
Slow water volume per unit time q = 20ml / min
At the time of display, blood concentration displayed before water removal C HB = 23%
Displayed blood concentration after slow watering C HA = 25%
If these values are substituted into equation (4),
Real blood concentration before slow water HC HB = 18.00%
Substituting this into equation (3)
Real blood concentration after slow watering HC HA = 20.00%
Thus, the actual blood concentration excluding the offset amount is calibrated to 18.00% before slow water and 20.00% after slow water.
These calculations and processing are performed by the computer of the blood
また、血液透析時には別途に血液成分の検査が行われて、正確な血液濃度も知ることができる。この正確な血液濃度を用いることで、オフセット量の較正だけでなく濃度勾配の較正も行うことができる。すなわち、この正確な血液濃度は徐水前実血液濃度ＨＣＨＢそのものであり、(2)式より、徐水後実血液濃度ＨＣＨＡは、
図２は、上記実施形態の血液濃度測定値較正装置としての演算および処理を実施する血液濃度測定装置１，２による血液濃度の測定結果を、別途の正規測定装置による血液濃度の測定結果と対比して経時的に示す説明図であり、この結果からも明らかなように、この実施形態の血液濃度測定値較正装置によれば、樹脂チューブ内を流れる血液の濃度の測定値を較正するに際し、樹脂チューブ内を流れる血液を途中でダイアライザーに通し、そのダイアライザーによる徐水前および徐水後の血液濃度のオフセット量を含む測定値の間の差と、樹脂チューブ内を流れる血液のダイアライザーによる徐水前の流量および徐水量と、に基づいて測定値を較正するので、測定値からオフセット量の影響を除去して実際の血液濃度を高精度に求めることができる。
FIG. 2 compares the blood concentration measurement results obtained by the blood
以上、図示例に基づき説明したが、この発明は上述の例に限定されるものでなく特許請求の範囲の記載範囲内で適宜変更し得るものである。 Has been described above based on the illustrated embodiment, the present invention is Ru der what may appropriately changed within the claimed scope of the Not claims be limited to the above example.
かくしてこの発明の血液濃度測定値較正装置によれば、光透過性の管壁を持つ管路内を流れる血液の濃度を血液濃度測定装置が測定した測定値を較正するに際し、前記管路内を流れる血液を徐水装置に通し、その徐水装置による徐水前および徐水後の血液濃度の、互いに同一のオフセット量を含む測定値の間の差と、前記管路内を流れる血液の、前記徐水装置による徐水前の単位時間当たり流量および前記徐水装置による単位時間当たりの徐水量と、に基づいて前記測定値を、前記オフセット量を除いた値に較正するので、測定値から管路固有のオフセット量の影響を除去して実際の血液濃度を高精度に求めることができる。 Thus, according to the blood concentration measurement value calibration device of the present invention, when calibrating the measurement value measured by the blood concentration measurement device with respect to the concentration of blood flowing in the pipeline having the light transmissive tube wall, The flowing blood is passed through the slow water device, and the difference between the measured values including the same offset amount of the blood concentration before and after the slow water by the slow water device and the slow flow of the blood flowing in the conduit The measured value is calibrated to a value excluding the offset amount based on the flow rate per unit time before slow watering by the water device and the slow water amount per unit time by the slow water device . The actual blood concentration can be obtained with high accuracy by removing the influence of the offset amount.
１，２ 血液濃度測定装置 1, 2 Blood concentration measuring device
Claims (1)
前記管路の途中に設けられた除水装置が前記管路内を流れる血液からの徐水を行っている間に、前記管路の前記徐水装置の上流部分に設けられた前記血液濃度測定装置（２）および下流部分に設けられた前記血液濃度測定装置（１）がそれぞれ測定した、互いに同一のオフセット量をそれぞれ含む前記徐水装置による徐水前および徐水後の血液濃度の測定値の差（Ｃ ＨＡ −Ｃ ＨＢ ）を求める除水前後測定値差演算手段と、
前記徐水前および徐水後の血液濃度の測定値の差（Ｃ ＨＡ −Ｃ ＨＢ ）と、前記管路内を流れる血液の、前記徐水装置による徐水前の単位時間当たり流量（Ｑ）および前記徐水装置による単位時間当たりの徐水量（ｑ）とに基づいて、前記血液濃度測定装置（１，２）の測定値（Ｃ ＨＡ ，Ｃ ＨＢ ）を、前記オフセット量を除いた値（ＨＣ ＨＡ ，ＨＣ ＨＢ ）に較正する測定値較正手段と、
を具えることを特徴とする血液濃度測定値較正装置。 In a device for calibrating a measurement value measured by a blood concentration measurement device based on Lambert-Beer's law, the concentration of blood flowing in a pipe line having a light-transmissive tube wall,
The blood concentration measurement provided in the upstream portion of the slow water device in the pipe while the dewatering device provided in the middle of the pipe performs slow water from the blood flowing in the pipe Difference in measured values of blood concentration before and after slow watering by the slow water device each including the same offset amount respectively measured by the blood concentration measuring device (1) provided in the device (2) and the downstream part. A measured value difference calculating means before and after water removal to obtain (C HA -C HB );
Wherein the Jomizu difference before and measurements of blood concentration after Jomizu (C HA -C HB), of the blood flowing through the conduit, flow amount per unit of time before Jomizu by the Jomizu device (Q) and said Xu Based on the slow water amount (q) per unit time by the water device, the measured value (C HA , C HB ) of the blood concentration measuring device (1, 2) is a value (HC HA , Measurement value calibrating means for calibrating to HC HB ) ,
Blood Concentration measurements calibration apparatus characterized by comprising a.
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