JP3370746B2 - Device for measuring the amount of sample in a transparent container - Google Patents

Device for measuring the amount of sample in a transparent container

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Publication number
JP3370746B2
JP3370746B2 JP24057493A JP24057493A JP3370746B2 JP 3370746 B2 JP3370746 B2 JP 3370746B2 JP 24057493 A JP24057493 A JP 24057493A JP 24057493 A JP24057493 A JP 24057493A JP 3370746 B2 JP3370746 B2 JP 3370746B2
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JP
Japan
Prior art keywords
light
transparent container
sample
measuring
amount
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JP24057493A
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Japanese (ja)
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JPH0798239A (en
Inventor
昭 森
Original Assignee
セファテクノロジー株式会社
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Description

【発明の詳細な説明】Detailed Description of the Invention

【０００１】[0001]

【産業上の利用分野】この発明は透明容器内試料の分量
測定装置に関し、さらに詳細には、試験管等の透明容器
内に収容された液体試料を光学的に測定する技術に関す
る。This invention relates to the quantity of sample in a transparent container.
More specifically, the present invention relates to a technique for optically measuring a liquid sample contained in a transparent container such as a test tube.

【０００２】[0002]

【従来の技術】例えば、血液は遠心分離装置にかけて血
漿と血清に遠心分離された後、それぞれが種々の医学療
法に有効利用されるところ、これらの分量測定は、図１
５(a)に示すように、その分離時に用いた試験管１に収
容された状態のままでは行うことができず、血漿（沈澱
物）２と血清（上澄み液）３をそれぞれ別個の容器にと
ってから、それらの重量等を測ることにより行われてい
た。2. Description of the Related Art For example, blood is centrifuged in a centrifuge to separate it into plasma and serum, which are then effectively used for various medical therapies.
As shown in FIG. 5 (a), the test tube 1 used for the separation cannot be performed in the state of being stored in the test tube 1, and the plasma (precipitate) 2 and the serum (supernatant solution) 3 are placed in separate containers. Therefore, it was performed by measuring their weight.

【０００３】[0003]

【発明が解決しようとする課題】しかしながら、このよ
うな測定方法では、別の容器に移す際などに非常な手間
がかって迅速な処理が行えず、しかも、少量の場合には
正確な分量測定が行えないという問題もあり、その改良
技術の開発が要望されていた。However, in such a measuring method, rapid processing cannot be performed because it takes a great deal of time when transferring to another container, and moreover, in the case of a small amount, an accurate quantity measurement is not possible. There is also a problem that it cannot be done, and there has been a demand for the development of improved technology.

【０００４】この測定を、光センサを用い試験管１の試
料部分の透明度変化のみを検出することによって行なう
ことも考えられる。しかし、試料が血清３のような透明
液である場合には、試験管１の透明液の部分と、その上
方の空気の部分とで透明度の変化は少なく、この変化を
検出することは容易ではない。さらに、試験管１には試
料を識別するためのラベルが貼られているのが通例であ
り、このラベルによっても透明度変化は曖昧になる。し
たがって、透明度変化の検出のみによる測定は不適当で
ある。It is also conceivable to carry out this measurement by using an optical sensor to detect only the change in transparency of the sample portion of the test tube 1. However, when the sample is a transparent liquid such as serum 3, there is little change in transparency between the transparent liquid part of the test tube 1 and the air part above it, and it is not easy to detect this change. Absent. Further, it is usual that a label for identifying the sample is attached to the test tube 1, and this label also makes the change in transparency ambiguous. Therefore, measurement by only detecting the change in transparency is inappropriate.

【０００５】本発明にかかる従来の問題点に鑑みてなさ
れたものであって、その目的とするところは、試験管等
のラベルが貼られることがある透明容器内に収容された
液体試料について、光学的手段を用いてそのままの状態
で迅速かつ正確に分量測定を行うことができる、透明容
器内試料の分量測定装置の提供にある。The present invention has been made in view of the conventional problems of the present invention, and its purpose is to provide a liquid sample contained in a transparent container to which a label such as a test tube may be attached. Another object of the present invention is to provide a device for measuring a quantity of a sample in a transparent container, which enables rapid and accurate quantity measurement in an as-is state using optical means.

【０００６】[0006]

【課題を解決するための手段】上記目的を達成するた
め、本発明の透明容器内試料の分量測定装置は、液体試
料が収容された透明容器内側面に、光を斜め上方を向く
所定の仰角を付けて、スポット状に収束するように投射
する投光手段と、この投光手段の上記透明容器に対する
光投射位置を、透明容器深さ方向へ所定速度をもって相
対的に移動させる投光位置移動手段と、上記透明容器を
挟んで上記投光手段に対向して設けられ、この投光手段
から上記透明容器内を直線状に透過した光と全反射して
透過した光とを受光して光電変換する受光手段と、この
受光手段の出力の経時的変化を測定する光量変化測定手
段と、この光量変化測定手段および上記投光位置移動手
段を同期して制御する制御手段と、上記光量変化測定手
段の測定結果に基づいて、上記透明容器内の液体試料の
分量を演算する分量演算手段とを備えてなり、上記受光
手段の受光素子は、上記投光手段と一定の位置関係を保
って、上記直線状の透過光および全反射した透過光の双
方を受光し得る位置に配置した位置検出素子であり、上
記光量変化測定手段は、上記位置検出素子の出力から全
透過光量の変化と受光重心位置の変化を算出・測定する
ものであり、上記分量演算手段は、この光量変化測定手
段の測定結果に基づいて上記透明容器内の液体試料の分
量を演算するものであることを特徴とする。In order to achieve the above object, the apparatus for measuring the amount of a sample in a transparent container according to the present invention comprises a liquid sample.
The light is directed diagonally upward on the inner surface of the transparent container containing the ingredients.
Project with a predetermined elevation angle so that it converges in a spot shape
And a transparent container for the transparent container.
Adjust the light projection position at a predetermined speed in the depth direction of the transparent container.
The transparent position moving means for moving the pair and the transparent container
The light projecting means is provided so as to face the light projecting means by sandwiching it.
From the above, the light transmitted through the transparent container in a straight line and totally reflected
A light receiving means for receiving and photoelectrically converting the transmitted light, and
Light intensity change measuring hand that measures the change over time in the output of the light receiving means
Step, the light quantity change measuring means, and the light emitting position moving hand.
Control means for synchronously controlling the steps, and the above-mentioned light intensity change measuring hand
Based on the measurement results of the stage, the liquid sample in the transparent container
And a quantity calculation means for calculating a quantity,
The light receiving element of the means maintains a fixed positional relationship with the light projecting means.
Therefore, the linear transmission light and the total reflection transmission light
It is a position detection element placed at a position where
The measuring means for measuring the change in the amount of light recorded is
Calculate and measure changes in the amount of transmitted light and changes in the center of gravity of the received light
The light quantity change measuring means is
The liquid sample in the transparent container is
It is characterized in that it calculates a quantity .

【０００７】[0007]

【０００８】[0008]

【作用】本発明の分量測定装置においては、レーザ光等
の光を、液体試料が収容された透明容器に対し斜め上方
を向く所定の仰角をもって、スポット状に収束させて投
射するとともに、この投射位置を所定速度をもって深さ
方向へ移動させる。この投射光は、透明容器内におい
て、試料中を直線状に透過するとともに、その試料液面
の水平部とその上部空間との界面において全反射する。In the quantity measuring device of the present invention, light such as laser light is projected onto the transparent container containing the liquid sample in a spot-like manner with a predetermined elevation angle directed obliquely upward and projected. The position is moved in the depth direction at a predetermined speed. In the transparent container, the projected light linearly passes through the sample and is totally reflected at the interface between the horizontal portion of the sample liquid surface and the upper space thereof.

【０００９】試料中を直線状に透過する光の光量は、透
過位置における透明容器の透明度（収容物の内容等に対
応する）に従って変化し、上記全反射が発生したとき０
になる。The amount of light linearly transmitted through the sample changes according to the transparency of the transparent container at the transmission position (corresponding to the contents of the contents, etc.), and when the above total reflection occurs, 0
become.

【００１０】一方、この全反射光は、投射方向に対して
大きな角度を持って透明容器を透過するので、全反射な
く直線状に透過した光と明確に区別でき、これを検出す
れば液面を確実に捉えることができる。On the other hand, since the totally reflected light transmits through the transparent container at a large angle with respect to the projection direction, it can be clearly distinguished from the light that is linearly transmitted without total reflection. Can be reliably captured.

【００１１】したがって、光の投射位置を移動させると
同時に、透明容器内を直線状に透過した光、および全反
射し所定角度をもって透過した光の光量変化を、光セン
サや位置検出素子（ＰＳＤ）等の受光素子を用いて電気
的に検出すれば、これら検出値の経時的変化から液体試
料の深さ寸法を算出できる。そして、この算出値と予め
測定した透明容器の内径寸法、液体試料の比重等から液
体試料の分量（体積や重量）を算出する。Therefore, at the same time when the light projection position is moved, the light quantity linearly transmitted through the transparent container and the light quantity change of the light totally reflected and transmitted at a predetermined angle are detected by an optical sensor or a position detecting element (PSD). If electrically detected using a light receiving element such as, the depth dimension of the liquid sample can be calculated from the change with time of these detected values. Then, the volume (volume or weight) of the liquid sample is calculated from the calculated value, the inner diameter dimension of the transparent container, the specific gravity of the liquid sample, and the like which are measured in advance.

【００１２】例えば、血液を遠心分離して得られた血漿
と血清のうち、血清の分量を測定する場合は、沈澱物で
ある血漿とその上澄み液である血清の境界で透明度が大
きく異なるため、上記直線状の透過光の光量が大きく変
化し、また、この血清の液面では、上記直線状の透過光
の光量が０になると同時に上記全反射して透過した光が
観測されるので、これら変化時および観測時の間の時間
を計測することで、血清部分の深さ寸法を算出すること
ができ、これにより、遠心分離に用いた試験管に収容し
た状態のままでの血清の分量測定を可能とする。For example, in the case of measuring the amount of serum among plasma and serum obtained by centrifuging blood, the transparency is greatly different at the boundary between plasma as a precipitate and serum as a supernatant thereof. Since the light amount of the linearly transmitted light largely changes and the light amount of the linearly transmitted light becomes 0 on the liquid surface of the serum, the light totally reflected and transmitted is observed. By measuring the time between the time of change and the time of observation, it is possible to calculate the depth dimension of the serum part, which enables the measurement of the amount of serum in the state of being housed in the test tube used for centrifugation. And

【００１３】この場合において、受光素子として、上記
位置検出素子を使用していることから、全透過光量を表
す受光信号の変化で、血漿と血清の境界を検出し、全反
射の発生に伴う受光位置信号の変化で血清の液面を検出
することになる。[0013] In this case, as the light receiving element, from the fact that using the above <br/> position detecting element, a change of the light reception signal representing the total amount of transmitted light, and detects a boundary of the plasma and serum, the total reflection The liquid level of the serum is detected by the change in the light receiving position signal accompanying the generation.

【００１４】[0014]

【実施例】以下、本発明に係る実施例を図面に基づいて
説明する。Embodiments of the present invention will be described below with reference to the drawings.

【００１５】実施例１ 本発明に係る透明容器内試料の分量測定装置を図１に示
し、この装置は具体的には図１５(a) に示すような試験
管１内に収容された血液分離後の上澄み液である血清３
の分量を測定するものであって、投光手段である投光光
学系５、受光手段である受光光学系６、透明容器である
試験管１を移動させる投光位置移動手段である駆動部
７、光量変化測定手段である信号処理部８、制御手段で
ある制御部９および分量演算手段である分量算出部１０
を主要部として構成されている。Example 1 An apparatus for measuring the amount of a sample in a transparent container according to the present invention is shown in FIG. 1, and this apparatus is specifically for separating blood contained in a test tube 1 as shown in FIG. 15 (a). Serum which is the supernatant liquid after
Is a light projecting optical system 5 which is a light projecting means, a light receiving optical system 6 which is a light receiving means, and a drive section 7 which is a light projecting position moving means for moving the test tube 1 which is a transparent container. , A signal processing section 8 which is a light quantity change measuring means, a control section 9 which is a control means, and a quantity calculating section 10 which is a quantity calculating means.
Is configured as a main part.

【００１６】投光光学系５は、サンプル（血漿，血清）
２，３が収容された試験管１に対して光（投射光）１１
ａを投射するためのもので、発光源ＬＤと、この発光源
ＬＤからの投射光１１ａを試験管１の内側面に微小なス
ポット状に収束する対物レンズＬ0 とを備え、その光軸
に所定の仰角δを与えている。The projection optical system 5 is a sample (plasma, serum)
Light (projection light) 11 is applied to the test tube 1 in which 2 and 3 are accommodated.
It is for projecting a, and includes a light emission source LD and an objective lens L0 for converging the projection light 11a from the light emission source LD on the inner surface of the test tube 1 in the form of a minute spot, and its optical axis is predetermined. The elevation angle δ is given.

【００１７】このように斜め上方に向けて光を入射する
のは、試験管１内のサンプル（血清）３液面の水平部
（周縁の表面張力による湾曲面を除いた部分）におい
て、全反射が起るようにするためである。発光源ＬＤと
しては、半導体レーザ、固体レーザ、ＬＥＤまたはラン
プ＋コンデンサレンズ＋ピンホールの組み合わせ等が使
用される。本発明ではサンプル液面の水平部で全反射さ
せることによって、反射方向が一定した大きな検出面積
を確保しているので、細く絞り込んだレーザ光のように
干渉性が少なく指向性が高い特殊光源を特に使用する必
要はなく、ランプ等の通常光源を充分使用できる。In this way, the light is incident obliquely upward because total reflection occurs in the horizontal portion of the liquid surface of the sample (serum) 3 in the test tube 1 (the portion excluding the curved surface due to the surface tension at the peripheral edge). This is so that As the light emitting source LD, a semiconductor laser, a solid-state laser, an LED or a combination of a lamp + a condenser lens + a pinhole is used. In the present invention, since a large detection area in which the reflection direction is constant is secured by total reflection at the horizontal part of the sample liquid surface, a special light source with low coherence and high directivity, such as a laser beam narrowed down, can be used. There is no particular need to use it, and ordinary light sources such as lamps can be used sufficiently.

【００１８】受光光学系６は、第１の受光器６ａおよび
第２の受光器６ｂから構成される。第１の受光器６ａ
は、試験管１内を直線状に透過した発光源ＬＤからの光
（直線状の透過光）１１ｂを受光し、第２の受光器６ｂ
は、第１の受光器６ａの下方にあって、試験管１内のサ
ンプル液（血清）３の液面（空気との境界面）で全反射
した発光源ＬＤからの光（全反射した透過光）１１ｃを
受光する。The light receiving optical system 6 comprises a first light receiver 6a and a second light receiver 6b. First light receiver 6a
Receives the light (linearly transmitted light) 11b from the light emitting source LD that has linearly transmitted through the test tube 1, and outputs the second light receiver 6b.
Is below the first light receiver 6a, and is the light from the light emitting source LD (totally reflected transmission) that is totally reflected by the liquid surface (boundary surface with air) of the sample liquid (serum) 3 in the test tube 1. (Light) 11c is received.

【００１９】各受光器６ａ，６ｂはそれぞれ、到達した
透過光１１ｂ，１１ｃを収束させる対物レンズＬ1 ，Ｌ
2 と、この収束された透過光１１ｂ，１１ｃを感知する
光センサＰＳ1 ，ＰＳ2 と、これら光センサＰＳ1 ，Ｐ
Ｓ2 での受光面積を規定するスリットＳＬ1 ，ＳＬ2 と
を備える。The respective light receivers 6a and 6b respectively have objective lenses L 1 and L for converging the transmitted lights 11b and 11c which have arrived.
2 , optical sensors PS 1 and PS 2 for sensing the converged transmitted light 11b and 11c, and these optical sensors PS 1 and P
Slits SL 1 and SL 2 that define the light receiving area at S 2 are provided.

【００２０】これら第１の受光器６ａおよび第２の受光
器６ｂは、試験管１を挟んで投光光学系５に対向配置さ
れ、この位置関係は、厳密には、例えば図２に示すよう
に規定される。すなわち、第１の受光器６ａは、投光光
学系５の光軸の延長線上に配置されるとともに、第２の
受光器６ｂは、血清３の液面において、投光光学系５側
の湾曲面（液面周縁の表面張力による湾曲面）Ｃｕに近
接した部位Ｆで全反射した光１１ｃが到達する位置に配
置されている。The first light receiver 6a and the second light receiver 6b are arranged so as to face the light projecting optical system 5 with the test tube 1 interposed therebetween. The positional relationship is strictly as shown in FIG. 2, for example. Stipulated in. That is, the first light receiver 6 a is arranged on the extension line of the optical axis of the light projecting optical system 5, and the second light receiver 6 b is curved on the liquid surface of the serum 3 on the light projecting optical system 5 side. It is arranged at a position where the light 11c totally reflected at the portion F near the surface (curved surface due to the surface tension of the liquid surface edge) Cu reaches.

【００２１】この配置は、第１の受光器６ａと第２の受
光器６ｂの上下間隔を大きく取って（受光光学系６寄り
の位置で全反射した光を受光すると第１および第２の受
光器６ａ，６ｂの受光位置が近づく。）、入射光の相互
干渉によるＳ／Ｎ比の低下を防止するとともに、全反射
の検出位置Ｆを、同様に全反射が起きて検出候補となり
得る前記湾曲面Ｃｕに近接させることによって検出の信
頼性を高めるためである。In this arrangement, the first photoreceiver 6a and the second photoreceiver 6b are arranged at a large vertical distance (when the light totally reflected at the position closer to the photodetection optical system 6 is received, the first and second photodetectors are received). The light receiving positions of the devices 6a and 6b approach each other), and the S / N ratio is prevented from lowering due to the mutual interference of incident light, and the total reflection detection position F is similarly curved so that total reflection occurs and becomes a detection candidate. This is because the reliability of detection is improved by bringing the surface Cu close to the surface Cu.

【００２２】光センサＰＳ1 ，ＰＳ2 としては、フォト
ダイオード、フォトトランジスタ、または光電子増倍管
（フォトマルチプライア）等が使用される。また、スリ
ットＳＬ1 ，ＳＬ2 の開口面積は調整可能とされ、投射
光１１ａがその投射位置Ｐ0から試験管１内を進んで、
反対側内側面の透過位置Ｐ1 ，Ｐ2 におけるスポットよ
り多少大きな面積に対して感応できるように受光面積を
規定する。A photodiode, a phototransistor, a photomultiplier tube (photomultiplier), or the like is used as the photosensors PS 1 and PS 2 . Further, the opening areas of the slits SL 1 and SL 2 can be adjusted, and the projection light 11a travels from the projection position P 0 inside the test tube 1,
The light receiving area is defined so as to be sensitive to an area slightly larger than the spots at the transmission positions P 1 and P 2 on the inner surface on the opposite side.

【００２３】駆動部７は、試験管１に対する投射光１１
ａの投射位置Ｐ0 を上下方向（試験管１の深さ方向）Ｘ
へ相対的に移動させるためのもので、図示例において
は、投光光学系５と受光光学系６を固定的に保持する一
方、試験管１つまりサンプル２，３を一体的に上下方向
Ｘへ所定速度をもって昇降動作させるように構成されて
いる。この駆動部７は、制御部９により信号処理部８と
同期して駆動され、アクチュエータとしてはパルスモー
タ等が使用される。The driving unit 7 projects the projection light 11 to the test tube 1.
The projection position P 0 of “a” is set in the vertical direction (depth direction of the test tube 1) X
In the illustrated example, the light projecting optical system 5 and the light receiving optical system 6 are fixedly held, while the test tube 1, that is, the samples 2 and 3 are integrally moved in the vertical direction X. It is configured to move up and down at a predetermined speed. The drive unit 7 is driven by the control unit 9 in synchronization with the signal processing unit 8, and a pulse motor or the like is used as an actuator.

【００２４】この駆動部７は、本分量測定装置の機械的
構造部分を構成するもので、具体的には、例えば図３に
示すように構成される。The drive unit 7 constitutes a mechanical structure portion of the present quantity measuring device, and is specifically constructed as shown in FIG. 3, for example.

【００２５】この駆動部７は、２本の試験管１，１内の
血清３，３を同時に測定するためのもので、試験管１は
図示しないキャリアに、例えば１０本立てられた状態で
本装置内に導入され、測定用器材の配置スペースの制限
から、離隔した２本の試験管１，１を、最初は１本目と
６本目め、次に２本目と７本目、……、最後に５本目と
１０本目という順序で次々とチャック装置１２，１２で
取出して測定する。The drive unit 7 is for simultaneously measuring the sera 3 and 3 in the two test tubes 1 and 1. The test tube 1 is placed in a carrier (not shown), for example, 10 units of the apparatus are set up. Due to the limitation of the space for placing the measuring equipment, the two test tubes 1 and 1 separated from each other were initially the 1st and 6th tubes, then the 2nd and 7th tubes, and so on. The chuck device 12, 12 is taken out one after another in the order of the first and tenth ones and measured.

【００２６】２つのチャック装置１２，１２は、垂直移
動用アクチュエータ１３ａを備えた上下動機構１３内に
回転自在に取り付けられ、各々回転用アクチュエータ１
４，１４によって独立して回転制御される。上下動機構
１３は、水平移動用アクチュエータ１５ａを備えた水平
移動機構１５によって水平位置を制御される。The two chuck devices 12, 12 are rotatably mounted in a vertical movement mechanism 13 having a vertical movement actuator 13a.
Rotation control is independently performed by 4, 14. The vertical position of the vertical movement mechanism 13 is controlled by the horizontal movement mechanism 15 including the horizontal movement actuator 15a.

【００２７】測定開始時には、両チャック装置１２，１
２が、測定対象とする試験管１，１の位置に水平移動さ
れた後、降下されて試験管１，１の上部をそれぞれ把持
する。At the start of measurement, both chuck devices 12, 1
After being horizontally moved to the position of the test tube 1, 1 to be measured, it is lowered and holds the upper part of the test tube 1, 1 respectively.

【００２８】この場合、試験管１の上部には、誰のサン
プルであるかを識別する細帯状のＩＤラベル１６が貼ら
れているので、初めにこの自動読み取りを光学的に行な
う。すなわち、試験管１を把持した状態で、チャック装
置１２，１２を上昇させ、ＩＤ読み取り装置１７の位置
に合わせ、この状態で試験管１を回転させ読み取りを行
なう。なお、ＩＤ読み取り装置１７は、ＩＤが文字の場
合は文字読み取り装置であり、ＩＤがバーコードの場合
はバーコードリーダである。読み取り中は照明装置１７
ａ，１７ａ，１７ａが照明を行なう。In this case, since the strip-shaped ID label 16 for identifying the sample is attached to the upper part of the test tube 1, this automatic reading is first performed optically. That is, while holding the test tube 1, the chuck devices 12, 12 are moved up to match the position of the ID reading device 17, and the test tube 1 is rotated in this state for reading. The ID reading device 17 is a character reading device when the ID is a character and a bar code reader when the ID is a bar code. Lighting device 17 during reading
a, 17a, 17a perform illumination.

【００２９】ＩＤの読み取り後、試験管１はさらに引き
上げられ、この位置から一定の速度で降下して、血清３
の分量測定が開始される。After reading the ID, the test tube 1 is further pulled up and descends from this position at a constant speed, so that the serum 3
The measurement of the quantity is started.

【００３０】これに関連して、一対の反射型光センサ１
８ａ，１８ｂが、各試験管１について上記投光光学系５
の両側に配置されている。これら光センサ１８ａ，１８
ｂは、試験管１の中間部に貼られたサンプルの種類を示
すラベル１９を検出し、回転用アクチュエータ１４によ
る回転位置制御によって、投光光学系５が、試験管１に
巻き付けられたラベル１９の隙間１９ａから、試験管１
に直接投射を行なう状態を確保する。In this connection, a pair of reflective photosensors 1
8a and 18b are the projection optical system 5 for each test tube 1.
Are located on both sides of. These optical sensors 18a, 18
In b, the label 19 indicating the type of the sample attached to the intermediate portion of the test tube 1 is detected, and the projection optical system 5 is wrapped around the test tube 1 by the rotation position control by the rotation actuator 14. From the gap 19a of the test tube 1
Secure the condition of direct projection to.

【００３１】すなわち、上記両反射型光センサ１８ａ，
１８ｂの位置関係は、その双方の投射光の試験管１上投
射位置間距離が上記ラベル１９の端縁間よりも短く、か
つこれら両投射位置間に投光光学系５の投射位置Ｐ0 が
位置するように設定されている。That is, the birefringence type optical sensor 18a,
As for the positional relationship of 18b, the distance between the projected positions of the projected lights on both sides of the test tube 1 is shorter than that between the edges of the label 19, and the projected position P 0 of the projection optical system 5 is located between these projected positions. It is set to be located.

【００３２】そして、両反射型光センサ１８ａ，１８ｂ
の双方がラベル１９の隙間１９ａを検出するようなトレ
ース動作をすることによって、たとえ上記ラベル１９が
傾斜して巻かれ、ラベルの隙間１９ａが斜めになったと
しても、投光光学系５は、常に試験管１に直接スポット
光１１ａを投射することができる。Then, the both reflection type optical sensors 18a, 18b.
By performing a tracing operation such that both of them detect the gap 19a of the label 19, even if the label 19 is wound in an inclined manner and the gap 19a of the label is inclined, the projection optical system 5 is The spot light 11a can always be directly projected onto the test tube 1.

【００３３】上記反射型光センサ１８ａ，１８ｂは、設
置スペースおよび検知エリア特定の面から、投受光を光
ファイバを用いて行なう光ファイバ式センサを用いるこ
とが有利である。この光ファイバ式センサとしては、中
心に受光用の光ファイバ、その周囲に複数の投光用光フ
ァイバが配置されてなる、いわゆる同軸センサ等があ
る。As the reflection type optical sensors 18a and 18b, it is advantageous to use an optical fiber type sensor for projecting and receiving light using an optical fiber from the aspect of the installation space and the detection area specifying. As the optical fiber type sensor, there is a so-called coaxial sensor in which a light receiving optical fiber is arranged at the center and a plurality of light projecting optical fibers are arranged around the light receiving optical fiber.

【００３４】信号処理部８は、光センサＰＳ1 ，ＰＳ2
の光電変換出力Ｓ1 ，Ｓ2 を検出し、その経時的変化を
測定する。この出力変化は、例えば、図４に示すように
なり、Ｓ1 は試験管１を直線状に透過した光１１ｂの受
光量を表し、Ｓ2 はサンプルの液面Ｆで全反射し一定方
向に透過した光１１ｃの受光量を表す。The signal processing unit 8 includes optical sensors PS 1 and PS 2
The photoelectric conversion outputs S 1 and S 2 are detected and the change over time is measured. This change in output is, for example, as shown in FIG. 4, S 1 represents the amount of light 11b linearly transmitted through the test tube 1, and S 2 is totally reflected by the liquid surface F of the sample and is in a fixed direction. The amount of received light 11c is represented.

【００３５】このようにＳ1 の他にＳ2 を検出すること
は、Ｓ1 のみで測定した場合において、前記ラベル１９
の部分で受光量が低下し（特に文字が印刷された部分で
光が減衰することによる影響が大きい。）、全反射によ
って受光量が０になる場合と区別し難くなる問題を解決
することになる。[0035] detecting the S 2 is thus in addition to S 1, when measured only in S 1, the label 19
In order to solve the problem that the amount of received light is reduced in the area of (in particular, the effect of the light being attenuated in the area where the characters are printed is large), and it is difficult to distinguish it from the case where the amount of received light is 0 due to total reflection. Become.

【００３６】これらの光電変換出力Ｓ1 ，Ｓ2 は、共通
の時間軸に対する独立データとして扱って試験管１内の
血清３を測定することもできる（例えば、Ｓ1 の最初の
立ち上がりと、Ｓ2 の立ち上がりのタイミングを用い
る）。この場合、Ｓ2 における全反射光１１ｃの検出時
期と、Ｓ1 において直線状の透過光１１ｂが０になる時
期は重なるので、Ｓ1 −Ｓ2 の演算を行って、この変化
を強調し、この演算値に対して測定を行なうと、全反射
したタイミングをより明確に捉えることができ、測定の
信頼性が向上する。These photoelectric conversion outputs S 1 and S 2 can be treated as independent data with respect to a common time axis to measure the serum 3 in the test tube 1 (for example, the first rising of S 1 and S 1 ). Use the rising timing of 2 ). In this case, the detection timing of the totally reflected light 11c at S 2, since the timing of linear transmitted light 11b in the S 1 is made zero overlap, performs an operation of S 1 -S 2, highlighting the changes, When measurement is performed on this calculated value, the timing of total reflection can be grasped more clearly, and the reliability of measurement is improved.

【００３７】この演算値（Ｓ1 −Ｓ2 ）に対して測定を
行なう場合、例えば演算値（Ｓ1 −Ｓ2 ）が第１の設定
値Ｔｈ1 を越えた時間より時間計測を開始し、同演算値
（Ｓ1 −Ｓ2 ）が第２の設定値Ｔｈ2 を下回った瞬間ま
での時間、つまり、血清３における投射位置Ｐ0 の上下
方向Ｘ移動通過時間を計測する。[0037] Start the case of performing measurements on computed values (S 1 -S 2), for example, the calculated value (S 1 -S 2) is the time measured from the time that exceeds a first set value Th 1, The time until the same calculated value (S 1 -S 2 ) falls below the second set value Th 2 , that is, the vertical X movement passage time of the projection position P 0 on the serum 3 is measured.

【００３８】上記第１および第２の設定値Ｔｈ1 ，Ｔｈ
2 は、試験管１内に微小スポットとなって進入する投射
光１１ａの挙動による上記図４のＳ1 ，Ｓ2 の変化を考
慮して設定され、以下この点について説明する。The above first and second set values Th 1 and Th
2 is set in consideration of the changes in S 1 and S 2 in FIG. 4 due to the behavior of the projection light 11a that enters the test tube 1 as a minute spot, and this point will be described below.

【００３９】まず、投射光１１ａの試験管１内での挙動
に伴うＳ1 ，Ｓ2 の変化は次のようになる。なお、厳密
には空気と液体との境界では光の屈折があるが、説明の
簡便化のため図示ではこの屈折を省いている。First, changes in S 1 and S 2 due to the behavior of the projection light 11a in the test tube 1 are as follows. Strictly speaking, there is refraction of light at the boundary between air and liquid, but this refraction is omitted in the figure for simplicity of explanation.

【００４０】Ａ．血漿２の部位を投射する場合：（図５
参照） 試験管１内に入った投射光１１ａは、沈殿物である血漿
２により吸収されたり散乱して遮られ、第１および第２
の受光器６ａ，６ｂの光センサＰＳ1 ，ＰＳ2へは殆ど
光が到達せず、Ｓ1 ，Ｓ2 は共に０である。A. When projecting a part of plasma 2: (Fig. 5
The projected light 11a that has entered the test tube 1 is absorbed or scattered by the plasma 2 that is a precipitate, and is blocked by the first and second
Light hardly reaches the photosensors PS 1 and PS 2 of the photodetectors 6a and 6b, and S 1 and S 2 are both 0.

【００４１】Ｂ．血清３の部位を投射する場合：（図６
参照） 試験管１内に入った投射光１１ａは、空気と試験管１の
屈折率差による屈折効果、あるいは、試験管１内の上澄
み液である血清３によるレンズ効果，多少の吸収，散乱
効果等を受けるが、おおむね直進して、入射した時（投
射位置Ｐ0 の微小スポット）よりは大きいスポットを出
口側である透過位置Ｐ1 で形成し、第１の受光器６ａの
光センサＰＳ1 へ到達する。B. When projecting a site of serum 3: (Fig. 6
The projected light 11a entering the test tube 1 has a refraction effect due to a difference in refractive index between the air and the test tube 1, or a lens effect, some absorption and a scattering effect by the serum 3 which is the supernatant liquid in the test tube 1. However, a spot larger than when it is incident (a minute spot at the projection position P 0 ) is formed at the transmission position P 1 on the exit side, and goes to the optical sensor PS 1 of the first light receiver 6 a. To reach.

【００４２】この光センサＰＳ1 の受光量は、試験管１
に貼られたラベル１９の位置を通過するとき、光の減衰
量が大きい（特に文字が印刷された部分）ため低下す
る。一方、第２受光器６ａの光センサＰＳ2 は、光の直
進方向とは角度が異なるため受光しない。The amount of light received by this optical sensor PS 1 is determined by the test tube 1
When passing through the position of the label 19 affixed to the label, the amount of light attenuation is large (particularly the part where characters are printed), and therefore the amount of light decreases. On the other hand, the optical sensor PS 2 of the second light receiver 6a does not receive light because the angle is different from the straight traveling direction of light.

【００４３】したがって、Ｓ1 はラベル１９の部分で低
下する場合を除き、一定レベル近傍で上下動する。一
方、Ｓ2 は依然として０値を保つ。Therefore, S 1 moves up and down in the vicinity of a certain level except when it drops at the label 19. On the other hand, S 2 still retains the 0 value.

【００４４】Ｃ．血清３の液面付近を通る場合：（図７
〜図１０参照） 試験管１が下降して行くと、血清３内を進行する光は、
血清３の液面において、受光器寄りの水平面位置（液面
周縁の表面張力による湾曲面Ｃｕを除いた部分）に入射
するようになる（図７）。C. When passing near the liquid surface of serum 3: (Fig. 7
(See FIG. 10) When the test tube 1 descends, the light traveling in the serum 3
On the liquid surface of the serum 3, the light enters the horizontal surface position near the light receiver (a portion excluding the curved surface Cu due to the surface tension of the liquid surface peripheral edge) (FIG. 7).

【００４５】このとき、液面の法線に対する投射光１１
ａの入射角θは、θ＞ｓｉｎ-1（１／ｎ）となり（ｎ：
血清の屈折率）、この結果投射光１１ａが全反射を起こ
す。これによって、第１の受光器６ａの光センサＰＳ1
には透過光が入射しなくなる。一方、全反射光１１ｃ
は、入射方向に対して所定の角度を持って試験管１から
出て行くが、第２受光器６ａとは光軸が一致しないた
め、光センサＰＳ2 にも入射しない。At this time, the projection light 11 with respect to the normal line of the liquid surface
The incident angle θ of a is θ> sin −1 (1 / n) (n:
(Refractive index of serum), and as a result, the projection light 11a causes total reflection. As a result, the optical sensor PS 1 of the first light receiver 6a
The transmitted light does not enter the. On the other hand, total reflection light 11c
Exits from the test tube 1 at a predetermined angle with respect to the incident direction, but does not enter the optical sensor PS 2 because its optical axis does not match the second light receiver 6a.

【００４６】続いて試験管１が下降し、全反射位置が、
液面水平部の投光光学系５寄りの位置（図２のＦ）とな
ると（図８）、この全反射光１１ｃを第２の受光器６ａ
の光センサＰＳ2 が受光するようになる。このとき第１
受光器６ａの光センサＰＳ1は依然として受光しない。Then, the test tube 1 descends, and the total reflection position becomes
When it comes to a position (F in FIG. 2) near the projection optical system 5 in the horizontal part of the liquid surface (FIG. 8), the total reflected light 11c is reflected by the second light receiver 6a.
The optical sensor PS 2 of 2 receives light. At this time the first
The optical sensor PS 1 of the light receiver 6a still does not receive light.

【００４７】さらに、試験管１が下降し、投射光１１ａ
の入射位置が、投光光学系５寄りの表面張力による湾曲
面（図２のＣｕ）に入射するようになると（図９）、入
射部分を拡大して示す図１０に示すように、入射位置は
→→と変化する。Further, the test tube 1 descends and the projected light 11a
Is incident on the curved surface (Cu in FIG. 2) due to the surface tension near the projection optical system 5 (FIG. 9), the incident position is enlarged as shown in FIG. Changes to → →.

【００４８】この場合、では投射光１１ａが全反射を
起こすものの、その反射方向は上記Ｆにおける全反射方
向とはかなり異なるため、第２の受光器６ａの光センサ
ＰＳ2 は受光しない。また全反射のため第１の受光器６
ａの光センサＰＳ1 も受光しない。一方、では投射
光１１ａの屈折方向が直進方向とはかなり異なり、第１
および第２の受光器６ａ，６ｂの光センサＰＳ1 ，ＰＳ
2 は共に受光しない。In this case, although the projection light 11a causes total reflection in this case, the reflection direction thereof is considerably different from the total reflection direction in the above F, and therefore the optical sensor PS 2 of the second light receiver 6a does not receive light. Also, because of total reflection, the first light receiver 6
The optical sensor PS 1 of a does not receive light either. On the other hand, in, the refraction direction of the projection light 11a is quite different from the straight traveling direction, and
And the optical sensors PS 1 , PS of the second light receivers 6a, 6b
2 does not receive both.

【００４９】したがって、この期間中のＳ1 は０とな
り、Ｓ2 は上記位置Ｆに入射するとき短い幅で急峻に立
ち上がる。Therefore, S 1 becomes 0 during this period, and when S 2 is incident on the position F, it rapidly rises with a short width.

【００５０】Ｄ．空気中を通る場合：（図１１参照） 試験管１内に入った投射光１１ａは、空気と試験管１の
屈折率差による屈折効果などわずかな影響は受けるもの
の、ほとんど直進して、第１の受光器６ａの光センサＰ
Ｓ1 に到達する。このとき、第２の受光器６ｂの光セン
サＰＳ2 は受光しない。したがって、Ｓ1 は血清３を検
出した場合と同レベルの大きさとなり、Ｓ2 は０とな
る。D. When passing through the air: (See FIG. 11) Although the projection light 11a entering the test tube 1 is slightly affected by the refraction effect due to the difference in refractive index between the air and the test tube 1, it almost goes straight to the first position. Optical sensor P of the light receiver 6a
Reach S 1 . At this time, the optical sensor PS 2 of the second light receiver 6b does not receive light. Therefore, S 1 has the same level as that when serum 3 is detected, and S 2 is 0.

【００５１】以上のようにＳ1 ，Ｓ2 は変化し、その演
算値（Ｓ1 −Ｓ2 ）は、図４に示したようになるので、
上記第１の設定値Ｔｈ1 は、血清３中での受光量（透過
光量）レベルよりも小さく、かつ血漿２中での受光量レ
ベルよりも大きな値に設定し、上記第２の設定値Ｔｈ2
は、マイナスの所定値に設定する。なお、Ｓ1 とＳ2の
差を演算して測定対象とするこの実施例では、Ｓ1 とＳ
2 の各変化を相互に強調し合うように取り出しているの
で、各検出タイミングが明瞭に表われ、設定値Ｔｈ1 、
Ｔｈ2 を厳密に調整しなくても、確実な検出が行なえ、
取り扱いの容易化ならびに信頼性の向上が達成できる。As described above, S 1 and S 2 change, and the calculated value (S 1 -S 2 ) becomes as shown in FIG.
The first set value Th 1 is set to a value smaller than the received light amount (transmitted light amount) level in the serum 3 and larger than the received light amount level in the plasma 2, and the second set value Th 1 is set. 2
Is set to a negative predetermined value. In this embodiment, in which the difference between S 1 and S 2 is calculated to be the measurement target, S 1 and S 2
Since each change of 2 is extracted so as to emphasize each other, each detection timing clearly appears, and the set value Th 1 ,
Even if Th 2 is not strictly adjusted, reliable detection can be performed,
Ease of handling and improvement in reliability can be achieved.

【００５２】分量算出部１０は、信号処理部８の測定結
果に基づいて試験管１内の血清３の分量を演算するもの
で、具体的には、信号処理部８で測定された投射位置Ｐ
0 の上下方向Ｘ移動通過時間から、血清３の深さ寸法ｈ
を算出し、この算出値と予め測定した試験管１の内径寸
法、血清３の比重等から、血清３の分量つまり体積や重
量を算出する。The quantity calculating section 10 calculates the quantity of the serum 3 in the test tube 1 based on the measurement result of the signal processing section 8. Specifically, the projection position P measured by the signal processing section 8 is calculated.
In the vertical direction X moves transit time 0, serum 3 depth h
From the calculated value, the inner diameter of the test tube 1 measured in advance, the specific gravity of the serum 3, and the like, the amount of the serum 3, that is, the volume or weight, is calculated.

【００５３】しかして、以上のように構成された分量測
定装置において、光学系５，６に対して、遠心分離装置
により血漿２と血清３に遠心分離された試験管１を、図
３に示した駆動部７により下から上へ上昇させながら、
投射光１１ａを投射させる。FIG. 3 shows a test tube 1 obtained by centrifuging plasma 2 and serum 3 by the centrifuge with respect to the optical systems 5 and 6 in the quantity measuring apparatus configured as described above. While raising from the bottom to the top by the driving unit 7,
The projection light 11a is projected.

【００５４】このとき第１および第２の受光器６ａ，６
ｂの光センサＰＳ1 ，ＰＳ2 により、試験管１を透過す
る透過光１１ｂの光量を電気信号として検出し、信号処
理部８によりその光量の経時的変化（図４参照）を測定
するとともに、この測定結果に基づいて、分量算出部１
０により、血清３の深さ寸法ｈさらにはその分量を算出
する。At this time, the first and second photodetectors 6a, 6
The photosensors PS 1 and PS 2 of b detect the light amount of the transmitted light 11b that passes through the test tube 1 as an electric signal, and the signal processing unit 8 measures the change over time of the light amount (see FIG. 4). Based on this measurement result, the quantity calculation unit 1
From 0, the depth dimension h of the serum 3 and the amount thereof are calculated.

【００５５】この場合、血清３の深さ寸法ｈを算出する
には、投射光１１ａの投射位置Ｐ0が血清３の深さ方向
Ｘへ通過する時間を計測するが、これは図４において、
受光量（入力信号）が第１の設定値Ｔｈ1 を越えた時間
より時間計測を開始し、受光量が第２の設定値Ｔｈ2 を
下回った瞬間までの時間を、測定することで簡単になし
得る。なお、投光光学系５の投射光をラベルの隙間１９
ａに投射するための試験管１の回転補正動作中は、試験
管１の上下動作が一旦停止されており、この補正動作時
間は除かれる。In this case, in order to calculate the depth dimension h of the serum 3, the time taken for the projection position P0 of the projection light 11a to pass in the depth direction X of the serum 3 is measured.
It is easy to start the time measurement from the time when the received light amount (input signal) exceeds the first set value Th 1 and measure the time until the moment when the received light amount falls below the second set value Th 2 You can do it. In addition, the projection light of the projection optical system 5 is applied to the gap 19 of the label.
During the rotation correction operation of the test tube 1 for projecting onto a, the vertical movement of the test tube 1 is temporarily stopped, and this correction operation time is excluded.

【００５６】また、第１および第２の光センサＰＳ1 ，
ＰＳ2 の受光面積は、透過位置Ｐ1，Ｐ2 における透過
光１１ｂ，１１ｃのスポットよりも多少大きな面積に対
して感応できるように設定されているため、試験管１の
透過位置側に紙質のラベル１９があり、しかも、文字等
が印刷されていても、各透過光１１ｂ，１１ｃを確実に
検出することができ、光センサＰＳ1 ，ＰＳ2 の感度を
特に高くする必要がない。In addition, the first and second photosensors PS 1 ,
Since the light receiving area of PS 2 is set so as to be sensitive to an area slightly larger than the spots of the transmitted light 11b and 11c at the transmission positions P 1 and P 2 , the paper quality is set on the transmission position side of the test tube 1. Even if there is the label 19 and characters are printed, the transmitted lights 11b and 11c can be reliably detected, and it is not necessary to increase the sensitivity of the photosensors PS 1 and PS 2 .

【００５７】実施例２ 本例は図１５(b) に示すような沈殿物を含まず、透明ま
たは透明に近い単一の液体サンプル２０、例えば、予め
血漿から分離された血清や透明水溶液等の分量を測定す
る場合であり、このときの第１および第２の光センサＰ
Ｓ1 ，ＰＳ2 による受光量Ｓ1 、Ｓ2 および（Ｓ1 −Ｓ
2 ）の経時的変化を図１２に示す。Example 2 In this example, as shown in FIG. 15 (b), a single liquid sample 20 which does not contain a precipitate and is transparent or nearly transparent, such as serum or a transparent aqueous solution previously separated from plasma, is used. This is a case of measuring a quantity, and the first and second optical sensors P at this time
Received light amounts S 1 , S 2 and (S 1 −S 2) due to S 1 , PS 2.
FIG. 12 shows the change over time in ( 2 ).

【００５８】このように単一の液体サンプル２０におい
ては、投射光１１ａの試験管１内での挙動は実施例１に
おけるＢ（図６）→Ｃ（図７〜図９）→Ｄ（図１１）の
順番となるため、液体サンプル２０の液面のみを検出し
て、投射光１１ａが液体サンプル２０中を深さ方向Ｘへ
通過する時間を計測するようにする。その他の構成およ
び作用は実施例１と同様である。As described above, in the single liquid sample 20, the behavior of the projection light 11a in the test tube 1 is B (FIG. 6) → C (FIGS. 7 to 9) → D (FIG. 11) in the first embodiment. Therefore, only the liquid surface of the liquid sample 20 is detected, and the time for the projection light 11a to pass through the liquid sample 20 in the depth direction X is measured. Other configurations and operations are similar to those of the first embodiment.

【００５９】実施例３ 本例は図１３に示し、受光光学系６の受光素子として位
置検出素子（POSITIONSENSITIVE DETECTOR 、以下ＰＳ
Ｄ）２５が用いられたものである。Example 3 This example is shown in FIG. 13, and a position detecting element (POSITIONSENSITIVE DETECTOR, hereinafter PS) is used as a light receiving element of the light receiving optical system 6.
D) 25 was used.

【００６０】ＰＳＤ２５は、前記投光光学系５と一定の
位置関係を保って、前記直線状の透過光１１ｂおよび全
反射した透過光１１ｃの双方を受光し得る位置に配置さ
れる。The PSD 25 is arranged at a position capable of receiving both the linear transmitted light 11b and the totally reflected transmitted light 11c while maintaining a fixed positional relationship with the light projecting optical system 5.

【００６１】ＰＳＤ２５は、その受光面２５ａ全体に入
光した透過光の全受光量と、この受光面２５ａで受光し
た透過光の重心位置とを得るもので、単一のＰＳＤ２５
に、上記第１および第２の受光器６ａ，６ｂと同等の機
能を持たせることができ、受光光学系６を著しく簡素化
することができる。The PSD 25 obtains the total amount of received transmitted light entering the entire light-receiving surface 25a and the position of the center of gravity of the transmitted light received by the light-receiving surface 25a.
In addition, it is possible to provide the same function as the first and second light receivers 6a and 6b, and it is possible to significantly simplify the light receiving optical system 6.

【００６２】このＰＳＤ２５を使用した場合、信号処理
部８である光量変化測定手段は、ＰＳＤの出力から全透
過光量と受光重心位置を算出・測定する構成とする。When the PSD 25 is used, the light amount change measuring means, which is the signal processing unit 8, is configured to calculate and measure the total transmitted light amount and the light receiving center of gravity position from the output of the PSD.

【００６３】すなわち、ＰＳＤ２５は、平板状シリコン
にＰ層、Ｉ層、Ｎ層の三層を形成し、Ｐ層上の両端に出
力電極２６，２７、Ｎ層にバイアス電極２８を付けた構
造を有するもので、この受光面２５ａであるＰ層に光ス
ポットが入射すると、入射位置に光エネルギーに比例し
た電荷が発生し、この電荷は抵抗層であるＰ層を通って
出力電極２６，２７に流れる。That is, the PSD 25 has a structure in which three layers of a P-layer, an I-layer and an N-layer are formed on a plate-like silicon, and output electrodes 26 and 27 on both ends of the P-layer and a bias electrode 28 on the N-layer are attached. When a light spot is incident on the P layer, which is the light receiving surface 25a, charges proportional to the light energy are generated at the incident position, and the charges pass through the P layer, which is a resistance layer, to the output electrodes 26 and 27. Flowing.

【００６４】この光電流Ｉ0 は、総受光量に比例するも
のであり、出力電極２６，２７までの距離（抵抗値）に
逆比例して分割され、各出力電極から取出される。各電
流をＩ1 ，Ｉ2 、電極間距離をＬ、ＰＳＤ中心から入射
点までの距離をＸA とすれば、Ｉ1 ／Ｉ2 ＝（Ｌ−２Ｘ
A ）／（Ｌ＋２ＸA ）の関係がある。したがって、光量
変化測定手段８で、光電流Ｉ0 （＝Ｉ1 ＋Ｉ2 ）を求め
て全透過光量を表す受光信号を求め、出力電極２６，２
７の電流比Ｉ1 ／Ｉ2 から、受光重心位置を表す位置信
号を求める。This photocurrent I 0 is proportional to the total amount of received light, is divided in inverse proportion to the distance (resistance value) to the output electrodes 26 and 27, and is taken out from each output electrode. I 1 / I 2 = (L-2X) where I 1 and I 2 are currents, L is the distance between electrodes, and X A is the distance from the PSD center to the incident point.
There is a relationship of A ) / (L + 2X A ). Therefore, the light amount change measuring means 8 obtains the photocurrent I 0 (= I 1 + I 2 ) to obtain the light receiving signal representing the total transmitted light amount, and the output electrodes 26, 2
From the current ratio I 1 / I 2 of 7, the position signal representing the position of the center of gravity of the received light is obtained.

【００６５】ＰＳＤ２５を用い、遠心分離器等により分
離された沈澱物２および上澄み液３が入った試験管１を
測定した場合において、上記光量変化測定手段出力の経
時的変化は、例えば図１４に示すようになる。When the test tube 1 containing the precipitate 2 and the supernatant 3 separated by a centrifuge or the like is measured using the PSD 25, the change with time in the output of the light quantity change measuring means is shown in FIG. 14, for example. As shown.

【００６６】受光信号Ｓa は、前述した実施例１におけ
る第１の受光器の光センサＰＳ2 のものＳ1 に近似して
いるが、直線状の透過光１１ｂの他に全反射した透過光
１１ｃをも検出するので、血清３の液面において全反射
光１１ｃが起きる際にも一定の値を持つ。位置信号Ｓp
は、全反射を起こしたとき光１１ｃの到達位置が急変す
るので、センタ位置での受光を表す基準レベルに対して
パルス状に変化する。The received light signal S a is similar to S 1 of the optical sensor PS 2 of the first light receiver in the first embodiment described above, but the transmitted light which is totally reflected in addition to the linearly transmitted light 11b. Since 11c is also detected, it has a constant value even when the total reflected light 11c is generated on the liquid surface of the serum 3. Position signal S p
When the total reflection occurs, the arrival position of the light 11c changes abruptly, so that it changes like a pulse with respect to the reference level representing the light reception at the center position.

【００６７】したがって、分量算出部１０である分量演
算手段は、この受光信号Ｓa の立ち上がりから、位置信
号ＳP の立ち上がりまでの時間を計測することにより、
血清の高さｈを算出して血清３の分量を求める。その他
の構成および作用は実施例１と同様である。Therefore, the quantity calculating means, which is the quantity calculating unit 10, measures the time from the rising of the received light signal S a to the rising of the position signal S P.
The height h of the serum is calculated to obtain the amount of the serum 3. Other configurations and operations are similar to those of the first embodiment.

【００６８】なお、上述した実施例１〜３はあくまでも
本発明の好適な実施態様を示すもので、本発明はこれに
限定されることなく、本発明の範囲内で種々設計変更可
能である。The first to third embodiments described above are merely preferred embodiments of the present invention, and the present invention is not limited to this, and various design changes can be made within the scope of the present invention.

【００６９】例えば、図示例と逆に、試験管１を固定的
に保持し、投光光学系５と受光光学系６の方を昇降動作
させるようにしてもよい。For example, contrary to the illustrated example, the test tube 1 may be fixedly held and the light projecting optical system 5 and the light receiving optical system 6 may be moved up and down.

【００７０】また、図示例においては血漿２と分離され
た血清３の分量測定について説明しているが、他の沈澱
物と上澄み液における分量測定にも同様に適用可能なこ
とは言うまでもない。Further, in the illustrated example, the amount measurement of the serum 3 separated from the plasma 2 is described, but it goes without saying that the same can be applied to the amount measurement of other precipitates and supernatant.

【００７１】[0071]

【発明の効果】以上詳述したように、本発明によれば、
液体試料が収容された透明容器内側面に、光を斜め上方
を向く所定の仰角を付けて、スポット状に収束するよう
に投射する投光手段と、この投光手段の上記透明容器に
対する光投射位置を、透明容器深さ方向へ所定速度をも
って相対的に移動させる投光位置移動手段と、上記透明
容器を挟んで上記投光手段に対向して設けられ、この投
光手段から上記透明容器内を直線状に透過した光と全反
射して透過した光とを受光して光電変換する受光手段
と、この受光手段の出力の経時的変化を測定する光量変
化測定手段と、この光量変化測定手段および上記投光位
置移動手段を同期して制御する制御手段と、上記光量変
化測定手段の測定結果に基づいて、上記透明容器内の液
体試料の分量を演算する分量演算手段とを備えてなり、
上記受光手段の受光素子は、上記投光手段と一定の位置
関係を保って、上記直線状の透過光および全反射した透
過光の双方を受光し得る位置に配置した位置検出素子で
あり、上記光量変化測定手段は、上記位置検出素子の出
力から全透過光量の変化と受光重心位置の変化を算出・
測定するものであり、上記分量演算手段は、この光量変
化測定手段の測定結果に基づいて上記透明容器内の液体
試料の分量を演算するものであるから、試験管等のラベ
ルが貼られることがある透明容器内に収容された液体試
料について、光学的手段を用いてそのままの状態で迅速
かつ正確に分量測定を行うことができる。すなわち、本
発明の分量測定装置においては、液体試料が収容された
透明容器に対して、試料液面で全反射が起こるように上
向きに傾けたレーザ光等を、所定速度で深さ方向へ移動
させながらスポット状に収束させて投射し、このとき透
明容器に対して、直線状に透過する光と、全反射により
方向を変化させて透過する光を区別して検出し、これら
の光電変換出力の経時的変化から、液体試料の深さ寸法
さらにはその分量を算出することにより、透明容器内に
収容された液体試料について、そのままの状態での分量
測定が迅速かつ正確に行うことができる。As described in detail above, according to the present invention,
Light is obliquely upward on the inner surface of the transparent container containing the liquid sample.
Make a spot-like convergence with a predetermined elevation angle facing
To the transparent container of the light projecting means for projecting onto the
The light projection position to the transparent container is controlled at a predetermined speed in the depth direction.
The relative position of the projection position moving means, and the transparent
It is provided so as to face the light projecting means with a container sandwiched between
The light and the light transmitted linearly through the transparent container from the light means
Light receiving means for receiving and photoelectrically converting light that has been emitted and transmitted
And the change in light quantity that measures the change over time in the output of this light receiving means.
Measuring means, the light quantity change measuring means, and the projection position
Control means for synchronously controlling the position moving means, and the light amount changing means.
Based on the measurement result of the liquefaction measuring means, the liquid in the transparent container
And a volume calculation means for calculating the volume of the body sample,
The light receiving element of the light receiving means has a fixed position with the light emitting means.
In keeping with the relationship, the linear transmitted light and the totally reflected light are transmitted.
With a position detection element placed at a position that can receive both of the excess light
Yes, the light quantity change measuring means is
Calculates the change in total transmitted light amount and the change in light-receiving center of gravity position from the force.
The quantity calculation means described above is used to measure the light quantity.
Liquid in the transparent container based on the measurement result of
Since the sample volume is calculated, the liquid sample contained in a transparent container where labels such as test tubes may be attached can be used to measure the volume quickly and accurately using optical means. It can be carried out. I.e. the book
In the quantity measuring device of the invention, with respect to a transparent container containing a liquid sample , a laser beam or the like tilted upward so that total reflection occurs on the sample liquid surface, while moving in the depth direction at a predetermined speed The light that is transmitted in a straight line and the light that is transmitted by changing the direction by total reflection are separately detected and detected with respect to the transparent container. from the liquid sample depth further by calculating the quantity, the liquid sample contained in a transparent container can be content measurements as it is carried out quickly and accurately.

【００７２】これにより、例えば、従来不可能とされて
いた血液遠心分離後の血清についても、遠心分離に用い
た試験管に血漿，血清の両者が収容されたままの状態
で、その分量測定が可能となる。As a result, for example, the serum after blood centrifugation, which has been considered impossible in the past, can be measured in quantity with both the plasma and the serum contained in the test tube used for centrifugation. It will be possible.

【００７３】特に、全反射光を区別して検出する構成に
より、液面を確実に検出できるようになり、透明容器に
ラベルが貼られていて、直線状の透過光の検出のみで
は、測定が不確実になる問題が解消される。In particular, the configuration in which the total reflected light is detected separately allows the liquid surface to be detected reliably, and the label is attached to the transparent container, and the measurement cannot be performed only by detecting the linear transmitted light. The problem that becomes certain is solved.

【図面の簡単な説明】[Brief description of drawings]

【図１】本発明に係る実施例１である透明容器内試料の
分量測定装置の概略を示す構成ブロック図である。FIG. 1 is a configuration block diagram showing an outline of an apparatus for measuring the amount of a sample in a transparent container, which is Embodiment 1 according to the present invention.

【図２】実施例１における投光光学系、透明容器および
受光光学系の相対位置関係の一例を示す図である。FIG. 2 is a diagram showing an example of a relative positional relationship between a light projecting optical system, a transparent container, and a light receiving optical system in Embodiment 1.

【図３】実施例１における駆動手段の具体的な構成例を
示す概略図である。FIG. 3 is a schematic diagram showing a specific configuration example of a driving unit in the first embodiment.

【図４】実施例１において、投射光が試験管内の血漿，
血清および空気中を順次透過する場合の直線状の透過光
および全反射による透過光の光量の経時的変化を示す線
図である。[Fig. 4] In Example 1, the projected light was plasma in a test tube,
FIG. 3 is a diagram showing changes over time in the amount of linearly transmitted light and the amount of transmitted light due to total reflection when sequentially passing through serum and air.

【図５】同分量測定装置における投射光が試験管内の血
漿中を透過する場合の挙動を示す側面断面図である。FIG. 5 is a side cross-sectional view showing the behavior when the projected light in the aliquot measuring device passes through the plasma in the test tube.

【図６】同分量測定装置における投射光が試験管内の血
清中を透過する場合の挙動を示す側面断面図である。FIG. 6 is a side cross-sectional view showing the behavior when the projected light in the aliquot measuring device passes through the serum in the test tube.

【図７】同分量測定装置における投射光が試験管内の血
清の（受光光学系寄りの）水平液面を透過する場合の挙
動を示す側面断面図である。FIG. 7 is a side cross-sectional view showing the behavior in the case where projected light in the aliquot measuring device passes through a horizontal liquid surface (close to the light receiving optical system) of serum in a test tube.

【図８】同分量測定装置における投射光が試験管内の血
清の（投光光学系寄りの）水平液面を透過する場合の挙
動を示す側面断面図である。FIG. 8 is a side cross-sectional view showing the behavior when the projected light in the aliquot measuring device transmits the horizontal liquid surface (close to the light projecting optical system) of serum in the test tube.

【図９】同分量測定装置における投射光が試験管内の血
清の（投光光学系寄りの）液面周縁を透過する場合の挙
動を示す側面断面図である。FIG. 9 is a side cross-sectional view showing the behavior in the case where projected light in the aliquot measuring device passes through the liquid surface peripheral edge of the serum in the test tube (close to the light projecting optical system).

【図１０】投射光が、図９に示した位置を透過する場合
の挙動を説明するための拡大側面断面図である。FIG. 10 is an enlarged side cross-sectional view for explaining the behavior when the projection light passes through the position shown in FIG.

【図１１】同分量測定装置における投射光が試験管内の
空気中を透過する場合の挙動を示す側面断面図である。FIG. 11 is a side cross-sectional view showing the behavior of the same quantity measuring device when projected light passes through the air in the test tube.

【図１２】本発明に係る実施例２である、単一の液体試
料の分量を測定する場合の直線状の透過光および全反射
による透過光の光量の経時的変化を示す線図である。FIG. 12 is a diagram showing a time-dependent change in the amount of linear transmitted light and the amount of transmitted light due to total reflection when measuring the amount of a single liquid sample, which is Example 2 according to the present invention.

【図１３】本発明に係る実施例３であるＰＳＤを用いた
透明容器内試料の分量測定装置の概略を示す構成ブロッ
ク図である。FIG. 13 is a configuration block diagram showing an outline of an apparatus for measuring a quantity of a sample in a transparent container using a PSD which is Embodiment 3 according to the present invention.

【図１４】同分量測定装置の投射光が試験管内の血漿，
血清および空気中を順次透過する場合において、ＰＳＤ
出力から取り出された受光信号および位置信号の経時的
変化を示す線図である。FIG. 14: Projection light of the same amount measurement device is used for plasma in a test tube,
PSD when sequentially passing through serum and air
FIG. 6 is a diagram showing changes with time of a received light signal and a position signal extracted from an output.

【図１５】透明容器内に収容された液体試料の一例を示
し、図１５(a) は血液から分離された沈殿物である血漿
と上澄み液である血清を、また図１５(b) は単一の液体
試料をそれぞれ示す。FIG. 15 shows an example of a liquid sample contained in a transparent container. FIG. 15 (a) shows plasma as a precipitate separated from blood and serum as a supernatant, and FIG. 15 (b) shows a single sample. Each one liquid sample is shown.

【符号の説明】[Explanation of symbols]

１ 試験管（透明容器） ２ 血漿（沈澱物） ３ 血清（上澄み液） ５ 投光光学系（投光手段） ６ 受光光学系（受光手段） ６ａ 第１の受光器 ６ｂ 第２の受光器 ７ 駆動部（投光位置移動手段） ８ 信号処理部（光量変化測定手段） ９ 制御部（制御手段） １０ 分量算出部（分量演算手段） １１ａ 投射光 １１ｂ 直線状の透過光 １１ｃ 全反射をした透過光 ２０ 液体試料 ２５ 位置検出素子（ＰＳＤ) ＬＤ 発光源 Ｌ0 対物レンズ Ｌ1 対物レンズ Ｌ2 対物レンズ ＰＳ1 第１の光センサ ＰＳ2 第２の光センサ ＳＬ1 スリット ＳＬ2 スリット Ｐ0 光投射位置 Ｐ1 直線状の透過光の透過位置 Ｐ2 全反射をした透過光の透過位置 Ｓ1 直線状の透過光の受光量を表す信号 Ｓ2 全反射をした透過光の受光量を表す信号 Ｓa ＰＳＤを用いた場合に得られる受光信号 Ｓp ＰＳＤを用いた場合に得られる位置信号DESCRIPTION OF SYMBOLS 1 Test tube (transparent container) 2 Plasma (precipitate) 3 Serum (supernatant) 5 Projecting optical system (projecting means) 6 Receiving optical system (receiving means) 6a First light receiver 6b Second light receiver 7 Drive unit (light emitting position moving means) 8 Signal processing unit (light quantity change measuring means) 9 Control section (control means) 10 Quantity calculating section (quantity calculating means) 11a Projected light 11b Linear transmitted light 11c Totally reflected transmission Light 20 Liquid sample 25 Position detection element (PSD) LD Light emission source L 0 Objective lens L 1 Objective lens L 2 Objective lens PS 1 First optical sensor PS 2 Second optical sensor SL 1 Slit SL 2 Slit P 0 Optical projection Position P 1 Linear transmission position of transmission light P 2 Transmission position of transmission light after total reflection S 1 Signal S representing linearly received light amount of transmitted light S 2 Signal S representing total reception amount of transmitted light a Light receiving signal S p PSD obtained when a PSD is used Position signal obtained by using

Claims (7)

(57)【特許請求の範囲】(57) [Claims] 【請求項１】 液体試料が収容された透明容器内側面
に、光を斜め上方を向く所定の仰角を付けて、スポット
状に収束するように投射する投光手段と、 この投光手段の上記透明容器に対する光投射位置を、透
明容器深さ方向へ所定速度をもって相対的に移動させる
投光位置移動手段と、 上記透明容器を挟んで上記投光手段に対向して設けら
れ、この投光手段から上記透明容器内を直線状に透過し
た光と全反射して透過した光とを受光して光電変換する
受光手段と、 この受光手段の出力の経時的変化を測定する光量変化測
定手段と、 この光量変化測定手段および上記投光位置移動手段を同
期して制御する制御手段と、 上記光量変化測定手段の測定結果に基づいて、上記透明
容器内の液体試料の分量を演算する分量演算手段とを備
えてなり、 上記受光手段の受光素子は、上記投光手段と一定の位置
関係を保って、上記直線状の透過光および全反射した透
過光の双方を受光し得る位置に配置した位置検出素子で
あり、 上記光量変化測定手段は、上記位置検出素子の出力から
全透過光量の変化と受光重心位置の変化を算出・測定す
るものであり、 上記分量演算手段は、この光量変化測定手段の測定結果
に基づいて上記透明容器内の液体試料の分量を演算する
ものである ことを特徴とする透明容器内試料の分量測定
装置。1. A light projecting means for projecting light so as to converge in a spot shape on the inner side surface of a transparent container containing a liquid sample with a predetermined elevation angle directed obliquely upward, and the above-mentioned light projecting means. The light projecting position moving means for relatively moving the light projecting position with respect to the transparent container in the depth direction of the transparent container at a predetermined speed, and the light projecting means provided so as to face the light projecting means with the transparent container interposed therebetween. From the light receiving means for receiving and photoelectrically converting the light linearly transmitted through the transparent container and the light totally reflected and transmitted, and a light amount change measuring means for measuring the change with time of the output of the light receiving means, Control means for synchronously controlling the light quantity change measuring means and the light projection position moving means, and quantity calculating means for calculating the quantity of the liquid sample in the transparent container based on the measurement result of the light quantity change measuring means. Equipped
In addition, the light receiving element of the light receiving means has a fixed position with the light emitting means.
In keeping with the relationship, the linear transmitted light and the totally reflected light are transmitted.
With a position detection element placed at a position that can receive both of the excess light
Yes, the light amount change measuring means is based on the output of the position detecting element.
Calculates and measures changes in the total transmitted light amount and changes in the center of gravity of received light.
A shall, said amount calculating means, the measurement result of the light intensity change measuring means
Calculate the amount of liquid sample in the transparent container based on
A device for measuring the amount of a sample in a transparent container, which is characterized in that 【請求項２】 上記投光手段の上記透明容器に対する光
の入射角が、試料液面の水平部で全反射を起こす大きさ
に設定されている請求項１に記載の透明容器内試料の分
量測定装置。2. The quantity of the sample in the transparent container according to claim 1 , wherein an incident angle of light of the light projecting means with respect to the transparent container is set to a size that causes total reflection at a horizontal portion of a sample liquid surface. measuring device. 【請求項３】 上記受光手段は、上記透明容器内を直線
状に透過した光を受光する第１の受光器と、試料液面で
全反射して透過した光を受光する第２の受光器とを備え
てなる請求項１または請求項２に記載の透明容器内試料
の分量測定装置。3. The light-receiving means includes a first light-receiver for receiving light linearly transmitted through the transparent container and a second light-receiver for receiving light totally reflected on a sample liquid surface. The quantity measuring device for a sample in a transparent container according to claim 1 or 2 , further comprising: 【請求項４】 上記第１の受光器が、上記投光手段の光
軸の延長線上に配置されるとともに、上記第２の受光器
が、上記投光手段側にある表面張力による液面周縁の湾
曲面に近接した液面水平部で全反射した光の到達位置に
配置されている請求項３に記載の透明容器内試料の分量
測定装置。4. The first light receiver is arranged on an extension line of an optical axis of the light projecting means, and the second light receiver is provided on the light projecting means side by a liquid surface peripheral edge due to surface tension. The apparatus for measuring a quantity of a sample in a transparent container according to claim 3 , wherein the apparatus is arranged at a position where light totally reflected by a horizontal portion of the liquid surface near the curved surface of (1) reaches. 【請求項５】 上記第１および第２の受光器の受光素子
が光センサであり、各光センサの受光面積は、上記透明
容器内側面の投射位置から透明容器内を進んで、反対側
内側面の透過位置に達した透過光の光スポット面積より
多少大きな面積に対して感応するように設定されている
請求項３または請求項４に記載の透明容器内試料の分量
測定装置。5. The light receiving element of each of the first and second light receivers is an optical sensor, and the light receiving area of each of the optical sensors advances from the projection position of the inner surface of the transparent container to the inside of the transparent container, and then to the inside of the opposite side. The device for measuring the amount of a sample in a transparent container according to claim 3 or 4 , wherein the device is set so as to be sensitive to an area slightly larger than a light spot area of the transmitted light reaching the transmission position on the side surface. 【請求項６】 上記光量変化測定手段は、上記受光手段
の第１の受光器の出力から第２の受光器の出力を減算し
たデータの経時的変化を測定するものである請求項３〜
５のいずれか一つに記載の透明容器内試料の分量測定装
置。Wherein said light quantity change measuring means, first claim 3 from the output of the light receiver in which the output of the second photodetector to measure the time course of the data obtained by subtracting the light receiving means -
5. A device for measuring a quantity of a sample in a transparent container according to any one of 5 above. 【請求項７】 上記液体試料は、遠心分離器等により沈
澱物から分離された上澄み液であり、 上記分量演算手段は、上記光量変化測定手段で測定した
全透過光量の変化から、上記沈澱物および上澄み液の境
界を検出し、受光重心位置の変化からこの上澄み液の液
面を検知して、透明容器内の液体試料の分量を演算する
ものである請求項１に記載の透明容器内試料の分量測定
装置。7. The liquid sample is a supernatant liquid separated from the precipitate by a centrifuge or the like, and the quantity calculating means calculates the amount of transmitted light measured by the light quantity change measuring means from the precipitate. The sample in the transparent container according to claim 1 , wherein the boundary between the supernatant liquid is detected, the liquid level of the supernatant liquid is detected from the change in the center of gravity of the received light, and the quantity of the liquid sample in the transparent container is calculated. Measuring device.
JP24057493A 1993-08-31 1993-08-31 Device for measuring the amount of sample in a transparent container Expired - Fee Related JP3370746B2 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP24057493A JP3370746B2 (en) 1993-08-31 1993-08-31 Device for measuring the amount of sample in a transparent container

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
JP24057493A JP3370746B2 (en) 1993-08-31 1993-08-31 Device for measuring the amount of sample in a transparent container

Publications (2)

Publication Number Publication Date
JPH0798239A JPH0798239A (en) 1995-04-11
JP3370746B2 true JP3370746B2 (en) 2003-01-27

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JP2005345370A (en) * 2004-06-04 2005-12-15 Aloka Co Ltd Interface detecting device and method, and volume measuring device and method
US7323705B2 (en) * 2004-06-29 2008-01-29 Applera Corporation Liquid level measurement
JP2008070387A (en) * 2007-12-03 2008-03-27 Hitachi Ltd Liquid level detection method by means of sound and its device
JP5330317B2 (en) * 2010-06-02 2013-10-30 株式会社日立ハイテクノロジーズ Biological sample analysis method and analyzer
JP5414707B2 (en) * 2011-01-31 2014-02-12 株式会社日立ハイテクノロジーズ Analysis equipment
JP5470295B2 (en) * 2011-02-03 2014-04-16 株式会社日立ハイテクノロジーズ Biological sample analyzer and method
JP6143584B2 (en) * 2013-07-04 2017-06-07 株式会社日立ハイテクノロジーズ Detector and biological sample analyzer
WO2020159992A1 (en) * 2019-01-29 2020-08-06 Instrumentation Laboratory Company Hematocrit level detection using ir laser refraction

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