JPS6334977B2 - - Google Patents
Info
- Publication number
- JPS6334977B2 JPS6334977B2 JP12184779A JP12184779A JPS6334977B2 JP S6334977 B2 JPS6334977 B2 JP S6334977B2 JP 12184779 A JP12184779 A JP 12184779A JP 12184779 A JP12184779 A JP 12184779A JP S6334977 B2 JPS6334977 B2 JP S6334977B2
- Authority
- JP
- Japan
- Prior art keywords
- light
- emulsion
- hemolysis
- signal
- emission
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
- 239000000839 emulsion Substances 0.000 claims description 42
- 206010018910 Haemolysis Diseases 0.000 claims description 34
- 230000008588 hemolysis Effects 0.000 claims description 34
- 238000001514 detection method Methods 0.000 claims description 21
- 210000002966 serum Anatomy 0.000 claims description 18
- 230000002949 hemolytic effect Effects 0.000 claims description 11
- 239000008280 blood Substances 0.000 claims description 8
- 210000004369 blood Anatomy 0.000 claims description 7
- 239000003086 colorant Substances 0.000 claims description 5
- 230000002238 attenuated effect Effects 0.000 description 5
- 108010054147 Hemoglobins Proteins 0.000 description 4
- 102000001554 Hemoglobins Human genes 0.000 description 4
- 208000007536 Thrombosis Diseases 0.000 description 4
- 238000004458 analytical method Methods 0.000 description 4
- 210000000601 blood cell Anatomy 0.000 description 4
- 238000004020 luminiscence type Methods 0.000 description 3
- 238000011179 visual inspection Methods 0.000 description 3
- 238000010521 absorption reaction Methods 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000004945 emulsification Methods 0.000 description 2
- 239000000049 pigment Substances 0.000 description 2
- INGWEZCOABYORO-UHFFFAOYSA-N 2-(furan-2-yl)-7-methyl-1h-1,8-naphthyridin-4-one Chemical compound N=1C2=NC(C)=CC=C2C(O)=CC=1C1=CC=CO1 INGWEZCOABYORO-UHFFFAOYSA-N 0.000 description 1
- 108010064719 Oxyhemoglobins Proteins 0.000 description 1
- 230000002378 acidificating effect Effects 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 238000009534 blood test Methods 0.000 description 1
- 230000006378 damage Effects 0.000 description 1
- 108010002255 deoxyhemoglobin Proteins 0.000 description 1
- 230000031700 light absorption Effects 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 230000003287 optical effect Effects 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
Classifications
-
- G—PHYSICS
- 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
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/314—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths
- G01N21/3151—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths using two sources of radiation of different wavelengths
Landscapes
- Physics & Mathematics (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Health & Medical Sciences (AREA)
- Analytical Chemistry (AREA)
- Life Sciences & Earth Sciences (AREA)
- Chemical & Material Sciences (AREA)
- Toxicology (AREA)
- Biochemistry (AREA)
- General Health & Medical Sciences (AREA)
- General Physics & Mathematics (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Investigating Or Analysing Biological Materials (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
Description
【発明の詳細な説明】
この発明は血液検体の溶血乳濁検出装置に関す
る。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a hemolytic emulsion detection device for blood samples.
臨床検査として血液検査をおこなうことが多く
あるがこの場合血液は遠心分離機にかけられ血清
または血漿にされる。この血清または血漿が分注
された後分析がおこなわれる。分析結果に対して
検体即ち血清または血漿の溶血及び乳濁が考慮さ
れるのだがこの溶血及び乳濁を検出するとき、従
来においては分注時に分析担当者が血清または血
漿の状態を目視により検査し、溶血及び乳濁を判
断している。この判断結果が分析結果と共に分析
依頼者に報告される。このように従来においては
目視により溶血及び乳濁が判定されているため、
判定者によつて判定にバラツキが生じまた判定に
はかなりの熟練を要する。 Blood tests are often performed as clinical tests, and in this case blood is centrifuged and turned into serum or plasma. After this serum or plasma is dispensed, analysis is performed. Hemolysis and emulsification of the sample, i.e., serum or plasma, are taken into consideration in the analysis results, but in order to detect this hemolysis and emulsion, conventionally, the analyst visually inspects the condition of the serum or plasma at the time of dispensing. Hemolysis and emulsification are determined. This judgment result is reported to the analysis requester together with the analysis result. Conventionally, hemolysis and emulsion are determined by visual inspection, so
Judgments vary depending on the judge, and judgment requires considerable skill.
従つて、この発明の目的は目視によらずに血液
検体の溶血および乳濁を検出する血液検体の液血
乳濁検出装置を提供することである。 SUMMARY OF THE INVENTION Accordingly, an object of the present invention is to provide a liquid-blood emulsion detection device for a blood sample that detects hemolysis and emulsion in a blood sample without visual inspection.
この発明によると、血清または血漿を収納する
透明容器を介して互いに対向配置される複数色発
光素子と受光素子とを有し前記発光素子の無発光
に対応する無発光信号及び複数色の発光に夫々対
応する複数の発光信号を出力する検出部と、この
検出部からの前記無発光信号と前記複数色の１つ
で溶血による影響を受けることがない波長光の発
光信号とを比較して乳濁判定信号を発生し、前記
影響を受けることのない波長光の発光信号と前記
複数色の１つで溶血による影響を受ける波長光の
発光信号とを比較して溶血判定信号を発生する比
較回路と、この比較回路からの前記乳濁判定信号
及び前記溶血判定信号から前記血液検体の溶血及
び乳濁を検出する手段とで構成される血液検体の
溶血乳濁検出装置が提供される。 According to the present invention, a multi-color light-emitting element and a light-receiving element are arranged facing each other through a transparent container containing serum or plasma, and a non-emission signal corresponding to non-emission of light from the light-emitting element and a multi-color emission signal are provided. A detection unit outputs a plurality of corresponding luminescence signals, and a detection unit compares the non-luminescence signal from the detection unit with a luminescence signal of a wavelength of light that is one of the plurality of colors and is not affected by hemolysis. a comparison circuit that generates a hemolysis determination signal and compares the light emission signal of the unaffected wavelength light with the light emission signal of the wavelength light affected by hemolysis in one of the plurality of colors to generate the hemolysis determination signal; and means for detecting hemolysis and emulsion in the blood sample from the emulsion determination signal and the hemolysis determination signal from the comparison circuit.
以下図面を参照してこの発明の実施例を説明す
る。 Embodiments of the present invention will be described below with reference to the drawings.
第１図には血清または血漿の検体１１が収納さ
れた検体容器１２が検体ラツク１３から上下動部
材１４によつて検体検出装置１５に送り込まれた
状態が示されている。この検体検出装置１５は第
２図に示すように界面検出器１６と溶血乳濁検出
器１７とで構成される。界面検出器１６は検体容
器１２を介在して互いに対向配置され発光素子、
例えば赤外光LEDを有する発光部１８と受光素
子、例えばフオトトランジスタを有する受光部１
９とで構成される。この界面検出器１６は血清ま
たは血漿２０と血餅または血球２１（含セパレー
タ２２）とを識別し界面を検出する。この界面検
出において血清または血漿に乳濁が含まれている
と光の透過が減衰し血餅または血球との光の透過
比が小さくなるので界面の検出が難しくなる。こ
のため乳濁の影響を受けにくい長波長の光を発す
る赤外LEDが用いられる。またこの赤外LEDは
小さいのでスペース的にも有利である。受光素子
としては明暗を判別できればよいので受光信号処
理回路を簡素化できるように増幅作用を有するフ
オトトランジスタが用いられる。 FIG. 1 shows a state in which a sample container 12 containing a serum or plasma sample 11 is fed from a sample rack 13 to a sample detection device 15 by a vertically movable member 14. This specimen detection device 15 is composed of an interface detector 16 and a hemolytic emulsion detector 17, as shown in FIG. The interface detectors 16 are arranged opposite to each other with the sample container 12 in between, and include light emitting elements,
For example, a light emitting section 18 having an infrared LED and a light receiving section 1 having a light receiving element, for example a phototransistor.
It consists of 9. This interface detector 16 distinguishes between serum or plasma 20 and blood clots or blood cells 21 (including separator 22) and detects the interface. In this interface detection, if serum or plasma contains emulsion, the transmission of light is attenuated and the transmission ratio of light to blood clots or blood cells becomes small, making it difficult to detect the interface. For this reason, infrared LEDs are used that emit long wavelength light that is less susceptible to emulsion. Also, since this infrared LED is small, it is advantageous in terms of space. Since the light receiving element only needs to be able to discriminate between brightness and darkness, a phototransistor having an amplification function is used so that the light receiving signal processing circuit can be simplified.
前記溶血乳濁検出器１６は界面検出器１７に近
接して設けられる発光部２３と受光部２４とから
成る。この溶血乳濁検出器１６は血球中のヘモグ
ロビン色素が血球の破壊等により血清中に溶けた
結果血清が赤色を帯びた状態即ち、溶血並びに血
清の濁りを即ち乳濁を検出する。溶血中のヘモグ
ロビン色素は第３図のヘモグロビンの吸収曲線に
示すように光学的に波長550nｍ近傍で特異吸収
を示すので溶血の検出には550nｍの光（緑色光）
を用いることが好ましい。但し第３図において曲
線Ａ，Ｂ，Ｃ，Ｄ，Ｅは酸素ヘモグロビン、還元
ヘモグロビン、Coヘモグロビン、酸性メトロヘ
モグロビン、CNメトロヘモグロビンを夫々示
す。これに対し乳濁を検出するには溶血による影
響を受けることがない波長の光が用いられ例えば
700nｍの波長の光（赤色光）が用いられる。こ
の実施例では上述のような２種類の波長の光を発
生する２色発光ダイオード（例えばシヤープ製２
色発光ダイオードＨ−127 3Y51）が発光部２３
の発光素子として用いられる。受光部２４として
は界面検出のように明か暗かの２値を識別するの
ではなく溶液または乳濁をアナログ量として検出
する必要があるので広範囲に亘つて直線性があり
しかも暗電流が小さい受光素子を用いる必要があ
る。このためこの実施例ではフオトダイオードが
用いられる。 The hemolytic emulsion detector 16 includes a light emitting section 23 and a light receiving section 24, which are provided close to the interface detector 17. The hemolyzed emulsion detector 16 detects the reddish state of serum caused by hemoglobin pigment in blood cells being dissolved into serum due to destruction of blood cells, that is, hemolysis, and the turbidity of serum, that is, emulsion. As shown in the hemoglobin absorption curve in Figure 3, the hemoglobin pigment during hemolysis exhibits optically specific absorption at a wavelength of around 550 nm, so 550 nm light (green light) is needed to detect hemolysis.
It is preferable to use However, in FIG. 3, curves A, B, C, D, and E represent oxyhemoglobin, deoxyhemoglobin, Cohemoglobin, acidic metropoglobin, and CN metroplobin, respectively. On the other hand, to detect emulsions, a wavelength of light that is not affected by hemolysis is used, e.g.
Light with a wavelength of 700 nm (red light) is used. In this embodiment, a two-color light emitting diode (e.g., Sharp's 2
Color light emitting diode H-127 3Y51) is the light emitting part 23
It is used as a light emitting device. The light-receiving section 24 needs to detect a solution or emulsion as an analog quantity, rather than distinguishing between light and dark as in the case of interface detection, so it can receive light with linearity over a wide range and with a small dark current. It is necessary to use an element. For this reason, a photodiode is used in this embodiment.
第４図には溶血乳濁検出器１７の電気回路系が
示されておりこの図に基いて溶血乳濁の検出動作
を説明する。 FIG. 4 shows the electric circuit system of the hemolyzed emulsion detector 17, and the operation of detecting hemolyzed emulsion will be explained based on this figure.
界面検出器１６によりおこなわれる界面検出が
完了し検体の血餅面が同一高さに揃つたところで
CPU２５から溶血乳濁検出命令が出される。こ
の検出命令に従つて制御部２６はLED駆動部２
７及びデータセレクト回路２８に制御信号を与え
る。LED駆動部２７では発光素子２３ａ及び２
３ｂを発光させず外乱等のドリフト分がデータセ
レクト回路２８を介してアナログホールド回路２
９によつてサンプルホールドされる。次に、赤色
発光素子２３ａが発光され検体２０を介した発光
光が受光素子２４で受光される。受光信号は増幅
器３９により増幅データセレクト回路２８を介し
てアナログホールド回路３０にサンプルホールド
される。更に、縁色発光素子２３ｂが発光され検
体２０を介した緑色発光光は受光素子２４により
受光され受光信号に変換される。この受光信号は
アナログホールド回路３１にサンプルホールドさ
れる。アナログホールド回路２９及び３０にホー
ルドされた信号は差動増幅器３２に入力され両信
号の差の電圧が乳濁判定信号として比較器３４に
供給される。この比較器３４において差電圧は乳
濁判定基準電圧TH1と比較される。またアナロ
グホールド回路３０及び３１にホールドされた信
号は差動増幅器３３に入力され両信号の差の電圧
が取り出される。この差電圧は溶血判定信号とし
て比較器３５及び３６に供給される。比較器３６
において差電圧と弱度溶血判定基準電圧TH3と
が比較される。比較器３４及び３６の比較結果デ
ータは緑色発光素子２３ｂの発光中にラツチ回路
３７にラツチされラツチされたデータはCPU２
５において演算処理され出力装置３８、例えば表
示装置に表示されプリンタによりプリントされ
る。 When the interface detection performed by the interface detector 16 is completed and the blood clot surfaces of the specimen are aligned at the same height,
A hemolyzed emulsion detection command is issued from the CPU 25. According to this detection command, the control unit 26 controls the LED driving unit 2.
7 and the data select circuit 28. In the LED driving section 27, the light emitting elements 23a and 2
3b does not emit light and the drift due to disturbance etc. is sent to the analog hold circuit 2 via the data select circuit 28.
Sample and hold is performed by 9. Next, the red light emitting element 23a emits light, and the emitted light that passes through the specimen 20 is received by the light receiving element 24. The received light signal is sampled and held in the analog hold circuit 30 by the amplifier 39 via the amplified data select circuit 28. Further, the green light emitted by the edge color light emitting element 23b and passing through the specimen 20 is received by the light receiving element 24 and converted into a light reception signal. This light reception signal is sampled and held in an analog hold circuit 31. The signals held in the analog hold circuits 29 and 30 are input to a differential amplifier 32, and the voltage difference between the two signals is supplied to a comparator 34 as an emulsion determination signal. In this comparator 34, the differential voltage is compared with the emulsion determination reference voltage TH1 . Further, the signals held in the analog hold circuits 30 and 31 are input to a differential amplifier 33, and a voltage difference between the two signals is extracted. This differential voltage is supplied to comparators 35 and 36 as a hemolysis determination signal. Comparator 36
The differential voltage and the weak hemolysis determination reference voltage TH 3 are compared at . The comparison result data of the comparators 34 and 36 is latched by the latch circuit 37 while the green light emitting element 23b is emitting light, and the latched data is sent to the CPU 2.
5, the data is arithmetic processed, displayed on an output device 38, for example, a display device, and printed by a printer.
上記のような溶血乳濁検出装置によつて検体の
正常、溶血及び乳濁は次のような方法で検出され
る。まず、正常血清即ち、溶血及び乳濁を含まな
い血清の場合、赤及び緑色光はいずれも減衰され
ず従つて、赤及び緑色光に対する受光レベルは第
５図にＲ，Ｇで示すように等しく大きい。また、
この図において受光レベルＲと外乱分による受光
レベルＮとの差Ｒ−Ｎが乳濁判定基準レベル
THR-Nより大きいことが示されている。次に、
溶血判定をするために受光レベルＲとＧとの差Ｒ
−Ｇが求められこの差Ｒ−Ｇは図から明らかなよ
うに０であり溶血判定基準レベルTHR-Gより低く
なつている。次に、溶血を含んでいる場合につい
て述べると溶血により緑色光が減衰され緑色受光
レベルＧが低下する。しかし赤色光は減衰されず
高い受光レベルＲを示す。この結果、受光レベル
差Ｒ−Ｎは乳濁判定基準レベルTHR-Nより大き
くまた、受光レベル差Ｒ−Ｇも溶血判定基準レベ
ルTHR-Gより大きくなる。次に、乳濁を含んでい
る場合について述べると乳濁により赤及び緑色光
が共に減衰される。この結果、受光レベルＲ及び
Ｇは第５図に示すようになる。従つて、受光レベ
ル差Ｒ−Ｎ及びＲ−Ｇの両方が対応する基準レベ
ルTHR-N及びTHR-Gより低くなる。溶血と乳濁と
が共に含んでいる場合には正常とは全く反対の関
係になる。 Normality, hemolysis, and emulsion of a specimen are detected by the hemolytic emulsion detection device as described above in the following manner. First, in the case of normal serum, that is, serum that does not contain hemolysis or emulsion, neither red nor green light is attenuated, and therefore, the reception levels for red and green light are equal, as shown by R and G in Figure 5. big. Also,
In this figure, the difference RN between the received light level R and the received light level N due to the disturbance component is the emulsion judgment reference level.
TH RN is shown to be greater than TH RN. next,
To determine hemolysis, the difference R between the received light level R and G
-G is determined, and as is clear from the figure, this difference RG is 0, which is lower than the hemolysis determination reference level THRG . Next, regarding the case where hemolysis is included, the green light is attenuated due to hemolysis and the green light reception level G is lowered. However, red light is not attenuated and exhibits a high light reception level R. As a result, the received light level difference RN is greater than the emulsion determination reference level THRN , and the received light level difference RG is also greater than the hemolysis determination reference level THRG . Next, regarding the case where emulsion is included, both red and green light are attenuated by the emulsion. As a result, the received light levels R and G become as shown in FIG. Therefore, both the received light level differences RN and RG are lower than the corresponding reference levels TH RN and TH RG . When both hemolysis and emulsion are present, the relationship is completely opposite to normal.
以上のことを総合すると正常、溶血及び乳濁並
びに溶血乳濁とは次のように示すことができる。 Taking all the above into consideration, normal, hemolysis and emulsion, and hemolytic emulsion can be expressed as follows.
正常 Ｒ−Ｇ＜THR-G
Ｒ−Ｎ＞THR-N
溶血 Ｒ−Ｇ＞THR-G
Ｒ−Ｎ＞THR-N
乳濁 Ｒ−Ｇ＜THR-G
Ｒ−Ｎ＜THR-N
溶血乳濁 Ｒ−Ｇ＞THR-G
Ｒ−Ｎ＜THR-N
上記の関係から正常、溶血、乳濁及び溶血乳濁
の判定がなされる。Normal R-G<TH RG R-N>TH RN hemolysis R-G>TH RG R-N>TH RN emulsion R-G<TH RG R-N<TH RN hemolytic emulsion R-G>TH RG R -N<TH RN Normal, hemolysis, emulsion, and hemolytic emulsion are determined from the above relationship.
以上この発明の溶血乳濁検出装置によると目視
にたよらないので判定者に経験を必要としなく判
定者の個人差により判定結果にバラツキが生じる
ことがなく一旦決めた基準に対し適切な判定結果
が得られる。また自動血清分注装置の一機構とし
て界面検出が完了した直後に検出装置が作動され
るので血清分注が終つた時点で血清の状態情報が
得られる。更に光源として２色発光ダイオードを
採用しているので光学フイルタを必要とせず狭い
スペースに検出器を設置することができる。 As described above, the hemolytic emulsion detection device of the present invention does not rely on visual inspection, does not require experience on the part of the judge, does not cause variations in judgment results due to individual differences in the judge, and can provide appropriate judgment results based on once-determined standards. can get. Furthermore, as a mechanism of the automatic serum dispensing device, the detection device is activated immediately after interface detection is completed, so that serum status information can be obtained at the time when serum dispensing is completed. Furthermore, since a two-color light emitting diode is used as the light source, the detector can be installed in a narrow space without requiring an optical filter.
第１図はこの発明の一実施例に従つた溶血乳濁
検出器を含む検体検出装置及び検体ラツクの側断
面図、第２図は検体検出装置の断面図、第３図は
ヘモグロビンの光吸収率を示す曲線図、第４図は
溶血乳濁検出器の回路図、そして第５図は受光レ
ベルを説明する図である。
１１……検体、１２……検体容器、１６……界
面検出器、１７……溶血乳濁検出器、２０……血
清、２１……血餅、２３ａ……赤色発光素子、２
３ｂ……緑色発光素子、２４……受光素子、２
９，３０，３１……ホールド回路、３２，３３…
…差動増幅器、３４，３５，３６……比較器。
FIG. 1 is a side cross-sectional view of a sample detection device and sample rack including a hemolytic emulsion detector according to an embodiment of the present invention, FIG. 2 is a cross-sectional view of the sample detection device, and FIG. 3 is a light absorption of hemoglobin. FIG. 4 is a circuit diagram of the hemolytic emulsion detector, and FIG. 5 is a diagram explaining the light reception level. 11... Specimen, 12... Sample container, 16... Interface detector, 17... Hemolysis emulsion detector, 20... Serum, 21... Blood clot, 23a... Red light emitting element, 2
3b... Green light emitting element, 24... Light receiving element, 2
9, 30, 31...Hold circuit, 32, 33...
...Differential amplifier, 34, 35, 36... Comparator.
Claims (1)
互いに対向配置される複数色発光素子と受光素子
とを有し前記発光素子の無発光に対応する無発光
信号及び複数色の発光に夫々対応する複数の発光
信号を出力する検出部と、この検出部からの前記
無発光信号と前記複数色の１つで溶血による影響
を受けることがない波長光の発光信号とを比較し
て乳濁判定信号を発生し、前記影響を受けること
のない波長孔の発光信号と前記複数色の１つで溶
血による影響を受ける波長光の発光信号とを比較
して溶血判定信号を発生する比較回路と、この比
較回路からの前記乳濁判定信号及び前記溶血判定
信号から前記血液検体の溶血及び乳濁を検出する
手段とで構成される血液検体の溶血乳濁検出装
置。1 A multi-color light-emitting element and a light-receiving element are arranged opposite to each other through a transparent container containing serum or plasma, and a non-emission signal corresponds to the non-emission of light from the light-emitting element, and a plurality of light-emission signals correspond to the plurality of colors of light emission, respectively. a detection unit that outputs a luminescent signal, and compares the non-luminescent signal from the detection unit with a luminescent signal of a wavelength of light that is one of the plurality of colors and is not affected by hemolysis to generate an emulsion determination signal. a comparison circuit that generates a hemolysis determination signal by comparing the light emission signal of the wavelength hole that is generated and is not affected by the light emission signal of the wavelength light that is affected by hemolysis in one of the plurality of colors; A blood sample hemolytic emulsion detection device comprising means for detecting hemolysis and emulsion in the blood sample from the emulsion determining signal from a circuit and the hemolysis determining signal.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP12184779A JPS5646450A (en) | 1979-09-21 | 1979-09-21 | Detector for hematic emulsion in blood specimen |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP12184779A JPS5646450A (en) | 1979-09-21 | 1979-09-21 | Detector for hematic emulsion in blood specimen |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5646450A JPS5646450A (en) | 1981-04-27 |
| JPS6334977B2 true JPS6334977B2 (en) | 1988-07-13 |
Family
ID=14821399
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP12184779A Granted JPS5646450A (en) | 1979-09-21 | 1979-09-21 | Detector for hematic emulsion in blood specimen |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5646450A (en) |
Families Citing this family (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6367865U (en) * | 1986-10-20 | 1988-05-07 | ||
| JPH0540447Y2 (en) * | 1987-09-14 | 1993-10-14 | ||
| US20030203504A1 (en) | 2002-04-26 | 2003-10-30 | John Hefti | Diffusion-based system and method for detecting and monitoring activity of biologic and chemical species |
| WO2004097370A2 (en) * | 2003-04-25 | 2004-11-11 | Prometheus Biosciences, Inc. | Systems and methods for monitoring chemical and biolgical activities using differential measurements |
| CN101151521A (en) * | 2005-03-29 | 2008-03-26 | 希森美康株式会社 | Method of analyte analysis and analyte analyzer |
| 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 |
-
1979
- 1979-09-21 JP JP12184779A patent/JPS5646450A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5646450A (en) | 1981-04-27 |
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