JPS60188845A - Particle analyzing device - Google Patents
Particle analyzing deviceInfo
- Publication number
- JPS60188845A JPS60188845A JP59044708A JP4470884A JPS60188845A JP S60188845 A JPS60188845 A JP S60188845A JP 59044708 A JP59044708 A JP 59044708A JP 4470884 A JP4470884 A JP 4470884A JP S60188845 A JPS60188845 A JP S60188845A
- Authority
- JP
- Japan
- Prior art keywords
- blood
- valve
- electrolyte
- phosphorescence
- cells
- 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.)
- Granted
Links
- 239000002245 particle Substances 0.000 title claims description 11
- 210000004369 blood Anatomy 0.000 claims abstract description 47
- 239000008280 blood Substances 0.000 claims abstract description 47
- 230000003287 optical effect Effects 0.000 claims abstract description 17
- 238000007865 diluting Methods 0.000 claims abstract 2
- 230000001678 irradiating effect Effects 0.000 claims abstract 2
- 239000008151 electrolyte solution Substances 0.000 claims description 7
- 239000000126 substance Substances 0.000 claims description 5
- 238000005194 fractionation Methods 0.000 claims 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 claims 1
- 239000010931 gold Substances 0.000 claims 1
- 229910052737 gold Inorganic materials 0.000 claims 1
- 239000007788 liquid Substances 0.000 abstract description 17
- 239000003792 electrolyte Substances 0.000 abstract description 5
- 238000005070 sampling Methods 0.000 abstract description 4
- 239000003153 chemical reaction reagent Substances 0.000 abstract description 3
- 238000001514 detection method Methods 0.000 abstract description 3
- 230000017531 blood circulation Effects 0.000 abstract description 2
- 239000000463 material Substances 0.000 abstract description 2
- 230000004907 flux Effects 0.000 abstract 2
- 238000005375 photometry Methods 0.000 abstract 1
- 210000004027 cell Anatomy 0.000 description 35
- 238000010586 diagram Methods 0.000 description 6
- 239000000243 solution Substances 0.000 description 5
- 210000000601 blood cell Anatomy 0.000 description 4
- 238000002347 injection Methods 0.000 description 4
- 239000007924 injection Substances 0.000 description 4
- 238000002372 labelling Methods 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- 238000003756 stirring Methods 0.000 description 2
- 230000008673 vomiting Effects 0.000 description 2
- DSSYKIVIOFKYAU-XCBNKYQSSA-N (R)-camphor Chemical compound C1C[C@@]2(C)C(=O)C[C@@H]1C2(C)C DSSYKIVIOFKYAU-XCBNKYQSSA-N 0.000 description 1
- 241000723346 Cinnamomum camphora Species 0.000 description 1
- 241000257465 Echinoidea Species 0.000 description 1
- 241000036848 Porzana carolina Species 0.000 description 1
- 206010047700 Vomiting Diseases 0.000 description 1
- 239000000427 antigen Substances 0.000 description 1
- 102000036639 antigens Human genes 0.000 description 1
- 108091007433 antigens Proteins 0.000 description 1
- 229960000846 camphor Drugs 0.000 description 1
- 229930008380 camphor Natural products 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 239000003085 diluting agent Substances 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000012530 fluid Substances 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 210000004916 vomit Anatomy 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N35/00—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor
- G01N35/10—Devices for transferring samples or any liquids to, in, or from, the analysis apparatus, e.g. suction devices, injection devices
- G01N35/1095—Devices for transferring samples or any liquids to, in, or from, the analysis apparatus, e.g. suction devices, injection devices for supplying the samples to flow-through analysers
- G01N35/1097—Devices for transferring samples or any liquids to, in, or from, the analysis apparatus, e.g. suction devices, injection devices for supplying the samples to flow-through analysers characterised by the valves
-
- G01N15/1409—
Abstract
Description
【発明の詳細な説明】
〔発明の利用分野〕
本発明は溶液中に浮遊する粒子の種類、数、太き−gt
−分類する粒子分析装置に係シ、特に定められた流速で
連続した流れの溶液中の粒子を連続的に分析する粒子分
析装置に関する。[Detailed Description of the Invention] [Field of Application of the Invention] The present invention relates to the type, number, and thickness of particles suspended in a solution.
- It relates to a particle analyzer for classifying particles, and more particularly to a particle analyzer for continuously analyzing particles in a solution flowing continuously at a predetermined flow rate.
本明細曹においては溶液中に浮遊する粒子分析装置に係
るが説明含分り易くするπめノズ下血敢中の細胞分析を
例に説明する。This specification relates to a particle analyzer suspended in a solution, but to make the explanation easier to understand, an example will be given of cell analysis of blood cells in the bloodstream.
従来細眠分析装置は被検体(血液)に光が当ると蛍光を
発するような蛍光物質を含ませ抗体を血液に摘下して抗
原抗体反応を起こさせて、血液中の抗原を検出している
。この検出にあたり、従来よシ血液を細い流れとし、そ
の流れに光を当てると、血液中の細胞が光を横切る除光
に当たシ、蛍光標識ちれた細胞から蛍光71+−発する
ので、その蛍光を検出器で検出することで血液中に浮遊
する細胞の分析を行なっている。しかしながらこのよう
な従来の装置にあっては蛍光を検出し細胞分析している
ため、一般に細胞そのものが自分で蛍光を発する場合が
多く、この自分の発する蛍光が抗体反応での蛍光を検出
する場合の妨害(ノイズ)となシ感度を落とし分析精度
が悪いという欠点を有している。Conventional sleep analyzers detect antigens in the blood by containing a fluorescent substance that emits fluorescence when the subject (blood) is exposed to light and extracting antibodies from the blood to cause an antigen-antibody reaction. There is. For this detection, conventionally, when blood is made into a thin flow and the flow is shined with light, the cells in the blood are exposed to the light that crosses the light, and the fluorescently labeled cells emit fluorescence 71+-. Cells floating in blood are analyzed by detecting fluorescence with a detector. However, in conventional devices like this, cells are analyzed by detecting fluorescence, so in many cases the cells themselves emit fluorescence, and when this self-emitted fluorescence is detected as fluorescence from an antibody reaction. This method has the disadvantage of lowering sensitivity and poor analysis accuracy due to interference (noise).
本発明の目的は特定の細胞を精度良く検出することので
きる粒子分析装置を提供することにある。An object of the present invention is to provide a particle analyzer that can accurately detect specific cells.
本発明は、抗体に蛍光物質を用いる代シにリン光発光物
質を含ませて、抗原抗体反応を起こさせて細胞の分析を
行なうようにすることにより、特屋の細胞全精度良く検
出しようというものである。The present invention aims to detect all the cells of Tokuya with high accuracy by incorporating a phosphorescent substance into an antibody that uses a fluorescent substance and causing an antigen-antibody reaction to analyze the cells. It is something.
以下、本発明の実施例について説明する。 Examples of the present invention will be described below.
第1図には、本発明に係る粒子分析装置の適用される流
路系統図が示されている。FIG. 1 shows a flow path system diagram to which a particle analyzer according to the present invention is applied.
図において、切換弁1の一方の入力端にはt解質液10
がシリンジポンプ5によって吸入されるように構成され
ている。また、この切換弁1の他方の入力端には、サン
プリングノズル11がM合てれておシ、このサンプリン
グノズル11の先端から血t13が給入できるように構
成嘔れている。In the figure, one input end of the switching valve 1 has a solute liquid 10
is configured to be inhaled by the syringe pump 5. Further, a sampling nozzle 11 is fitted to the other input end of the switching valve 1, and is configured such that blood t13 can be supplied from the tip of the sampling nozzle 11.
この切換弁1は、流路15を切換える定量弁16の構成
がとられている。この切換弁1の一方の出力端には軟式
チューブ4が接続されている。この軟式チューブ4には
、検知器14とシゴキボンプ3が設けられている。This switching valve 1 has a configuration of a metering valve 16 that switches a flow path 15. A flexible tube 4 is connected to one output end of the switching valve 1. This soft tube 4 is provided with a detector 14 and a squeeze pump 3.
また、切換弁1の他方の出力端には流路18が接続嘔れ
ておシ、このぴL路18の先端は液体収容器19に接続
されている。この液体収容器19の液体は、弁30を介
してコンプレッサ21がら供給嘔れるエアによって攪拌
されるように構成芒れている。また、この液体収容器1
9の出力端には弁31を介して切換弁2の一方の入力端
が接続されている。この切換弁2の他方の入力端には、
流路24を介して弁34が接続されている。この弁34
の出力端にはシリンシボ/プロによって′亀解質液10
が吸入できるように構成嘔れている。また、弁34の入
力端にはi4!、m質液28が吸入できる流路が接続さ
れている。Further, a flow path 18 is connected to the other output end of the switching valve 1, and the tip of this L path 18 is connected to a liquid container 19. The liquid in the liquid container 19 is configured to be agitated by air supplied from the compressor 21 via the valve 30. In addition, this liquid container 1
One input end of the switching valve 2 is connected to the output end of the switching valve 9 via the valve 31. At the other input end of this switching valve 2,
A valve 34 is connected via the flow path 24 . This valve 34
At the output end of ``Turtle electrolyte liquid 10'' is applied by Shirinshibo/Pro.
It is composed of vomiting that can be inhaled. In addition, the input end of the valve 34 has i4! , a flow path through which the substance fluid 28 can be inhaled is connected.
また、切換弁2は、建短弁23によって流路22が切換
るように構成されており、この切換弁2の一方の出力端
とはシリンジポンプ8が接続されている。また、この切
換弁2の他方の出力端には光学セル26が流路25を介
して接続されている。この光学セル26の他の入力端と
は流路29を介して弁35が接続ちれている。この弁3
5はうに構成されている。また、弁35の他方の端子に
は、槽27に収容されている電M質液28が吸入できる
ように流路が接続ちれている。また、光学セル26の出
力端には弁32の設けられている流路を介してシリンジ
ポンプ8が接続されている。Further, the switching valve 2 is configured such that the flow path 22 is switched by a short/open valve 23, and a syringe pump 8 is connected to one output end of the switching valve 2. Further, an optical cell 26 is connected to the other output end of the switching valve 2 via a flow path 25. A valve 35 is connected to the other input end of the optical cell 26 via a flow path 29. This valve 3
5 is composed of sea urchins. Further, a flow path is connected to the other terminal of the valve 35 so that the electromagnetic liquid 28 contained in the tank 27 can be sucked. Furthermore, a syringe pump 8 is connected to the output end of the optical cell 26 via a flow path in which a valve 32 is provided.
この光学セル26は光源20によって発せられた光によ
って蛍光を登じた光が検出器12によって検出するだめ
のものである。This optical cell 26 is used for detecting the light emitted by the light source 20 with fluorescence added thereto by the detector 12.
このように構成されるものであるから、切換弁1は第2
凶、@3図に示す如く流路の一部を回転あるいは上下動
することにより切断し、液体の一部を分取し別の流路に
切換える機能を有する。この機能は切換弁2も同様に有
している。また、シゴギボンプ3は軟式チューブ4tロ
ーラによってしごき、チューブ4内の液をローラの回転
方向と同じ方向に移送する。また、シリンジポンプ5゜
6.7.8は稀釈液lOを吸い上げ、指令によって流路
へ一定値の液を送付する穏f4@全備えている。Since it is constructed in this way, the switching valve 1 is
Unfortunately, as shown in Figure 3, it has the function of cutting a part of the flow path by rotating or moving it up and down, separating a part of the liquid, and switching it to another flow path. The switching valve 2 also has this function. Further, the squeeze pump 3 is squeezed by a roller 4t of a soft tube, and the liquid in the tube 4 is transferred in the same direction as the rotational direction of the roller. In addition, the syringe pump 5°6.7.8 is fully equipped with a syringe pump 5°6.7.8 that sucks up the diluent lO and sends a constant amount of liquid to the flow path according to a command.
マタ、光学セル26は−ffにシースフローセルと称さ
れ、第4図に示す如く液注入口37がら流路29を介し
て、逼M質液28を送シ、同時に試料注入口36から血
液全送り込む。この際、血液は液注入口37から供給さ
れる電解負液の流れのサヤ(シース)に包まれた細く絞
った流れを形成する。この血液の流れの太さはMLs負
液の流速と血液の流速との比て定まシ、必費に応じ自由
に選択できる。いま、患者から血液を採血し検査依%
y、−受けると、血液中の細胞にリン光標識を付ける試
薬を加え、良く振って撹拌した後V/プリングノズル1
1にセット嘔れる。この血液がセットされると、図示さ
れていないdIIj定用開舶用開始スイッチ。すると、
まず、シゴキボンプ3が回転しチューブ4がしごかれサ
ンプリングノズル11がら血液13が吸引され、血液検
知器14″!、で吸われる。The optical cell 26 is referred to as a sheath flow cell, and as shown in FIG. Send it in. At this time, the blood forms a narrow stream wrapped in a sheath of the electrolytic negative solution supplied from the liquid inlet 37. The thickness of this blood flow is determined by the ratio of the flow rate of the MLs negative liquid to the flow rate of the blood, and can be freely selected depending on the necessity. Currently, blood is collected from the patient and tested.
y, - When receiving, add a reagent to phosphorescently label cells in the blood, shake well to stir, and then apply the V/pulling nozzle 1.
Setting it to 1 makes me vomit. When this blood is set, the dIIJ regular vessel opening start switch (not shown) is activated. Then,
First, the squeeze pump 3 rotates, the tube 4 is squeezed, and the blood 13 is sucked through the sampling nozzle 11, and is sucked by the blood detector 14''!.
この血液を検知すると、検知器14が働らきシゴキボン
ブ3を停止する。一方、切換弁1の流路15には前記動
作によシ、血液13が定量弁16の切換により一定量分
散される。この定量弁16によって一定量分取された血
液13は、シリンジポンプ5の動作によって流路18を
経て、液体収容器19にポンプ5を流路17に定量゛さ
れた電解質液10と共に吐出される。吐出された血液1
3と電解質液10は弁30が開きコンプレッサ21の圧
縮空気で攪拌される。次に、弁31を開くと電解質液で
稀釈された血液が切換弁2へ送り込まれる。この切換弁
2の流路22に血液が満たされた所で、定量弁23が動
作し流路22で一定量分取された稀釈血液は流路24,
25に接続される。When this blood is detected, the detector 14 is activated and the squeeze bomb 3 is stopped. On the other hand, a certain amount of blood 13 is dispersed in the flow path 15 of the switching valve 1 by switching the metering valve 16 due to the above operation. A fixed amount of blood 13 is taken out by the metering valve 16, and is discharged into the liquid container 19 through the channel 18 by the operation of the syringe pump 5, together with the electrolyte solution 10 metered into the channel 17. . Spiked blood 1
3 and the electrolyte solution 10 are stirred by compressed air from the compressor 21 when the valve 30 is opened. Next, when the valve 31 is opened, the blood diluted with the electrolyte solution is sent to the switching valve 2. When the flow path 22 of this switching valve 2 is filled with blood, the metering valve 23 is operated and the diluted blood collected in a certain amount in the flow path 22 is transferred to the flow path 24.
25.
そこで弁33を開き、コンプレッサ21の圧縮空気で槽
27内のFkL解質gzsを加圧し、その液圧で流路2
4、流路29を加圧する。流路24、流路29の内圧が
一定時間経過した後、弁34゜35な切換え、同時に弁
32を開き、シリンジポンプ6.7を駆動させる。シリ
ンジポンプ7は電解質液28をゆつくシ第4図図示液注
入口37より光学セル26に押し込む。一方、同時にシ
リン稀釈血液は第4図図示試料注入口36から押し込ま
れ、第4図図示液注入口37よシ押し込まれた故のサヤ
で細くしぼられた光学セル26内をノーをなして安定に
流れる。一方光源2oの光は、たえず光学セル26に直
角な方向、かつ上記サヤに細くしぼられた稀釈血液の流
れの中心に照射されている。このように、光源20から
発せられた光束40が第5図に示す如く稀釈血液41の
流れに当たっても血球が存在しないときは、リン光を発
生しない。これに対し稀釈血液41中に浮遊する細胞(
血球)42が光束4oを通過する際、光を受けリン光音
発生する。このリン光は検出器12で測光され抗原抗体
反応から細胞の種類を分析する。Then, the valve 33 is opened, the FkL solute gzs in the tank 27 is pressurized with the compressed air of the compressor 21, and the flow path 2 is
4. Pressurize the channel 29. After the internal pressures in the channels 24 and 29 have increased for a certain period of time, the valves 34 and 35 are switched, and at the same time, the valve 32 is opened and the syringe pump 6.7 is driven. The syringe pump 7 slowly pushes the electrolyte solution 28 into the optical cell 26 through the solution injection port 37 shown in FIG. On the other hand, at the same time, the diluted blood was pushed in from the sample injection port 36 shown in FIG. flows to On the other hand, the light from the light source 2o is constantly irradiated in a direction perpendicular to the optical cell 26 and at the center of the flow of diluted blood narrowly squeezed into the sheath. In this way, even if the light beam 40 emitted from the light source 20 hits the flow of diluted blood 41 as shown in FIG. 5, no phosphorescence is generated when no blood cells are present. In contrast, cells floating in diluted blood 41 (
When the blood cells (blood cells) 42 pass through the light beam 4o, they receive light and generate a phosphorescent sound. This phosphorescence is measured by a detector 12 and the type of cell is analyzed from the antigen-antibody reaction.
このリン光舎元度計で測定することによる細胞の種類の
分析について第4図、第5図を用いて説明する。Analysis of cell types by measuring with this Rinkosha Gendometer will be explained using FIGS. 4 and 5.
光源20の光束40は光学セル26を通過した所でブロ
ッカ3Bで光が他へ散乱しないようブロックする。また
検出器12は光源2oの光軸とおれ九所に、光源20の
光を感することなく、かつリン光の感度良く検出するよ
うな位置に配置しておく。いま試料注入口36から血液
中の細胞に標識化のだめの試薬を加えられた血液41を
、液注入口37の電解液で細くしばり込み光学セル26
に流し込む。流れの途中で第5図図示細胞42が光束4
0に当たると細胞から蛍光およびリン光金発する。しか
し蛍光、リン光発生点46と検出器12の測定点45に
時間差金持たせておくと蛍光44は消滅しリン光43の
みを検出できる。以上によシ血液中の標識化された圧細
胞を精度良く検出、分析することができる。鵠6図は本
実施例に係る粒子分析装置における制御ブロック図が示
されている。After the light beam 40 from the light source 20 passes through the optical cell 26, the blocker 3B blocks the light from being scattered elsewhere. Further, the detectors 12 are arranged at nine points along the optical axis of the light source 2o, so that they do not sense the light from the light source 20 and can detect phosphorescence with high sensitivity. The blood 41 to which a labeling reagent has now been added to the cells in the blood from the sample injection port 36 is tightly tied with the electrolytic solution from the liquid injection port 37 and transferred to the optical cell 26.
Pour into. In the middle of the flow, the cell 42 shown in FIG.
When it hits 0, the cells emit fluorescence and phosphorescence. However, if a time difference is provided between the fluorescence or phosphorescence generation point 46 and the measurement point 45 of the detector 12, the fluorescence 44 disappears and only the phosphorescence 43 can be detected. As described above, labeled pressure cells in blood can be detected and analyzed with high accuracy. Figure 6 shows a control block diagram of the particle analyzer according to this embodiment.
検査技師が試料吸上ノズルに標識材てれた血液13をセ
ットしスタートスイッチ56を押すと、コンピュータ5
0は樟栴制御部51へ指命を出し血液13を吸上げ、切
換弁1、シゴキボンプ3、シリンジポンプ6を制御する
ことで血液13のサンプリング、稀釈、攪拌を行ない、
光学セル26に試料を導入し、血液中の細胞を分析する
と共に結果をプリンタ53に打出し、C几T54上にデ
ータを表示する。さらにコンピュータ50it、各部を
モニタし故障箇所をCRT54に表示し使用者にブザー
にてrラームを出す等の動作を実行する。When the laboratory technician sets the blood 13 containing the labeling material in the sample suction nozzle and presses the start switch 56, the computer 5
0 issues an instruction to the camphor control unit 51 to suck up the blood 13, and controls the switching valve 1, squeeze pump 3, and syringe pump 6 to sample, dilute, and stir the blood 13.
A sample is introduced into the optical cell 26, cells in the blood are analyzed, and the results are printed on the printer 53 and the data are displayed on the C-T54. Furthermore, the computer 50it monitors each part, displays the failure location on the CRT 54, and performs operations such as issuing an alarm to the user with a buzzer.
したがって、本実施例によれば、血液中の細胞にリン光
標識を用い、細胞への光照射軸とリン光検出器の位fR
kずらしておくことにより安定な細胞検出を行なうどと
ができる。Therefore, according to this embodiment, a phosphorescent label is used for cells in blood, and the position fR of the light irradiation axis to the cells and the phosphorescent detector is
By shifting by k, stable cell detection can be performed.
以上説明したように、本発明によれば、特定の細胞をn
匿良く検出することができる。As explained above, according to the present invention, specific cells can be
It can be detected anonymously.
第1図は本発明の適用される流路系統図、第2図、第3
図は第1図図示切換弁による血液定七−分取の切換を示
す図、第4図は第1図図示光学セルの詳細図、第5図は
血液中の細胞が光を受け蛍光・す/元金発生する残光特
性を示す図、第6図は第1図図示装置の制御ブロック図
である。
10.28・・・電解質液、12・・・検出器、13・
・・血液、16.23・・・定量弁、2o・・・光源、
26・・・光学セル。
代理人 弁理士 鵜沼辰之
も2図 宙3図
1)
準t4−図
′36
率5図Figure 1 is a flow path system diagram to which the present invention is applied, Figures 2 and 3.
The figures are a diagram showing the switching between blood constant and preparative separation using the switching valve shown in Figure 1, Figure 4 is a detailed view of the optical cell shown in Figure 1, and Figure 5 is a diagram showing the fluorescence and FIG. 6 is a control block diagram of the apparatus shown in FIG. 1. 10.28... Electrolyte solution, 12... Detector, 13.
... Blood, 16.23 ... Metering valve, 2o ... Light source,
26...Optical cell. Agent Patent Attorney Tatsuyuki Unuma also Figure 2 Sora 3 Figure 1) Quasi-t4-Figure '36 Rate 5 Figure
Claims (1)
の手段と、前記第1の手段によって分取された血液を電
解質液で定Ii1稀釈する第2の手段と、前記第2の手
段において稀釈された血液を光学セルに供給する第3の
手段と、前記第3の手段において供給する光学セルの側
部よシミ解質液をある一足圧で供給する第4の手段と、
前記光学セルに光源よシ一定の幅の光束を照射させる第
5の手段と、前記第5の手段による光束を照射後の稀釈
血液のリン光を検出する第6の手段とからなることを特
徴とする粒子分析装置。1. Quantitative fractionation of blood gold containing phosphorescent substance Kanakura
a second means for diluting the blood separated by the first means with an electrolyte solution; and a third means for supplying the blood diluted in the second means to the optical cell. , a fourth means for supplying the stain solute at a certain pressure from the side of the optical cell supplied in the third means;
A fifth means for irradiating the optical cell with a light beam of a constant width from a light source, and a sixth means for detecting phosphorescence of diluted blood after being irradiated with the light beam by the fifth means. Particle analyzer.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP59044708A JPS60188845A (en) | 1984-03-08 | 1984-03-08 | Particle analyzing device |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP59044708A JPS60188845A (en) | 1984-03-08 | 1984-03-08 | Particle analyzing device |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS60188845A true JPS60188845A (en) | 1985-09-26 |
JPH0321069B2 JPH0321069B2 (en) | 1991-03-20 |
Family
ID=12698914
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP59044708A Granted JPS60188845A (en) | 1984-03-08 | 1984-03-08 | Particle analyzing device |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS60188845A (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5480775A (en) * | 1990-01-26 | 1996-01-02 | Canon Kabushiki Kaisha | Method for measuring a specimen by the use of fluorescent light |
-
1984
- 1984-03-08 JP JP59044708A patent/JPS60188845A/en active Granted
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5480775A (en) * | 1990-01-26 | 1996-01-02 | Canon Kabushiki Kaisha | Method for measuring a specimen by the use of fluorescent light |
Also Published As
Publication number | Publication date |
---|---|
JPH0321069B2 (en) | 1991-03-20 |
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