JPH0239732B2 - - Google Patents
Info
- Publication number
- JPH0239732B2 JPH0239732B2 JP56210841A JP21084181A JPH0239732B2 JP H0239732 B2 JPH0239732 B2 JP H0239732B2 JP 56210841 A JP56210841 A JP 56210841A JP 21084181 A JP21084181 A JP 21084181A JP H0239732 B2 JPH0239732 B2 JP H0239732B2
- Authority
- JP
- Japan
- Prior art keywords
- circuit
- blood cells
- signal
- percentage
- level
- 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 - Lifetime
Links
- 210000000265 leukocyte Anatomy 0.000 claims description 44
- 239000002245 particle Substances 0.000 claims description 15
- 238000001514 detection method Methods 0.000 claims description 13
- 210000004369 blood Anatomy 0.000 claims description 9
- 239000008280 blood Substances 0.000 claims description 9
- 210000000601 blood cell Anatomy 0.000 claims description 9
- 230000001960 triggered effect Effects 0.000 claims description 9
- 239000007788 liquid Substances 0.000 claims description 5
- 230000003287 optical effect Effects 0.000 claims description 3
- 210000003743 erythrocyte Anatomy 0.000 description 14
- 238000005259 measurement Methods 0.000 description 11
- 239000003219 hemolytic agent Substances 0.000 description 9
- 210000004698 lymphocyte Anatomy 0.000 description 9
- 238000010586 diagram Methods 0.000 description 6
- 230000000527 lymphocytic effect Effects 0.000 description 5
- 210000003714 granulocyte Anatomy 0.000 description 4
- 238000004820 blood count Methods 0.000 description 3
- 210000001772 blood platelet Anatomy 0.000 description 3
- 210000004027 cell Anatomy 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 206010018910 Haemolysis Diseases 0.000 description 2
- 239000006285 cell suspension Substances 0.000 description 2
- 201000010099 disease Diseases 0.000 description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 2
- 230000008588 hemolysis Effects 0.000 description 2
- 208000033748 Device issues Diseases 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- 230000007012 clinical effect Effects 0.000 description 1
- 238000011109 contamination Methods 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 239000003085 diluting agent Substances 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000007274 generation of a signal involved in cell-cell signaling Effects 0.000 description 1
- 208000014951 hematologic disease Diseases 0.000 description 1
- 230000002934 lysing effect Effects 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 239000012528 membrane Substances 0.000 description 1
- 239000011780 sodium chloride Substances 0.000 description 1
- 239000004094 surface-active agent Substances 0.000 description 1
- 210000003462 vein Anatomy 0.000 description 1
Classifications
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06M—COUNTING MECHANISMS; COUNTING OF OBJECTS NOT OTHERWISE PROVIDED FOR
- G06M11/00—Counting of objects distributed at random, e.g. on a surface
- G06M11/02—Counting of objects distributed at random, e.g. on a surface using an electron beam scanning a surface line by line, e.g. of blood cells on a substrate
- G06M11/04—Counting of objects distributed at random, e.g. on a surface using an electron beam scanning a surface line by line, e.g. of blood cells on a substrate with provision for distinguishing between different sizes of objects
Landscapes
- Physics & Mathematics (AREA)
- General Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- Theoretical Computer Science (AREA)
- Investigating Or Analysing Biological Materials (AREA)
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、血液中の白血球の成分を分析する装
置に関するものであり、特に白血球のうちのリン
パ球および顆粒球の割合を求める分析装置に関す
るものである。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to an apparatus for analyzing components of white blood cells in blood, and more particularly to an analyzer for determining the proportion of lymphocytes and granulocytes among white blood cells. It is something.
白血球はリンパ球系白血球と顆粒球系白血球に
大別されるが、両者の割合は種々の血液疾患と大
いに関係があり、この割合を求めることにより、
病気の治療、診断に役立てることができる。
White blood cells are broadly classified into lymphoid leukocytes and granulocytic leukocytes, and the ratio of both is closely related to various blood diseases, and by determining this ratio,
It can be used to treat and diagnose diseases.
従来、血球計数器を用いて白血球計数を行うに
は、静脈などから採血した血液を0.85％食塩水な
どの血球浮遊用希釈液に希釈（例えば500倍）し、
界面活性剤などからなる溶血剤を滴下し赤血球の
みを溶血させてゴースト化した後、測定してい
た。すなわち、溶血剤を滴下して赤血球のみを溶
血させた血球浮遊希釈液中には、白血球、血小
板、赤血球のゴースト（膜部分）が存在し、この
血球浮遊希釈液を電気的または光学的検出原理に
基づく血球計数器により測定すると、赤血球のゴ
ーストや血小板による検出信号が白血球よりも小
さい信号を発するために所定の検出レベルを設定
し、そのレベル以上の信号を通過させることによ
り白血球数を測定していた。 Conventionally, in order to count white blood cells using a hemocytometer, blood collected from a vein or the like is diluted (for example, 500 times) with a diluent for blood cell suspension such as 0.85% saline.
Measurements were made after dropping a hemolytic agent such as a surfactant to lyse only the red blood cells and turning them into ghosts. In other words, ghosts (membrane parts) of white blood cells, platelets, and red blood cells are present in a diluted blood cell suspension in which only red blood cells are hemolyzed by dropping a hemolytic agent. When measured with a blood cell counter based on the standard, detection signals from red blood cell ghosts and platelets are smaller than white blood cells, so a predetermined detection level is set, and the number of white blood cells is measured by passing signals above that level. was.
一方、白血球細胞は溶血剤の影響により体積が
溶血剤滴下後縮小する。この縮小割合は白血球の
種類によつて異なり、また溶血剤滴下後の時間に
よつても経時変化する。前述のように白血球細胞
を大別すると、リンパ球系と顆粒球系に分かれ
る。リンパ球系の白血球細胞は顆粒球系の白血球
細胞に比べ、体積の縮小が早い時間、つまり溶血
剤滴下後直ちに始まり、ある一定時間後縮小は止
まり安定する。このときリンパ球系の白血球細胞
の検出信号パルス高さと、顆粒球系の白血球細胞
の検出信号パルス高さとでは明らかな差が生じ
る。この差を利用して白血球計数と同時にリンパ
球系細胞の割合、顆粒球系細胞の割合を得ること
ができる。 On the other hand, the volume of white blood cells decreases after the hemolytic agent is added due to the influence of the hemolytic agent. This reduction rate differs depending on the type of white blood cells and also changes over time depending on the time after the hemolytic agent is instilled. As mentioned above, white blood cells can be broadly classified into lymphocytes and granulocytes. Compared to granulocytic white blood cells, lymphoid white blood cells begin to shrink in volume more quickly, that is, immediately after the hemolytic agent is injected, and after a certain period of time, the reduction stops and becomes stable. At this time, a clear difference occurs between the detection signal pulse height of lymphoid white blood cells and the detection signal pulse height of granulocytic white blood cells. Utilizing this difference, it is possible to obtain the percentage of lymphoid cells and the percentage of granulocytic cells at the same time as counting white blood cells.
従来の測定法においては、上記リンパ球系の血
球細胞の割合および顆粒球系の割合は、いわゆる
粒度分布測定装置を用い、測定後に各々の粒子数
の割合を求めるなどの方法によつていた。 In conventional measurement methods, the percentage of lymphoid blood cells and the percentage of granulocytic cells are determined by using a so-called particle size distribution measuring device and determining the percentage of each particle number after measurement. .
特に、一般に用いられている赤血球を溶血させ
ゴースト化させる溶血剤は、溶血が完了するまで
の所要時間が数分以上もかかり、さらに顆粒球系
の白血球細胞と、リンパ球系の白血球細胞に分類
が可能な状態になるまでには、さらにかなりの時
間を必要とし、従つて温度などの物理的条件の影
響により、顆粒球系とリンパ球系の分類可能なレ
ベルが変動するなどの欠点があつた。 In particular, commonly used hemolytic agents that hemolyze red blood cells and turn them into ghosts take several minutes or more to complete hemolysis, and are further classified into granulocytic white blood cells and lymphocytic white blood cells. It takes a considerable amount of time to reach a state where granulocytic and lymphocytic systems can be classified, and the disadvantage is that the level at which granulocytic and lymphocytic systems can be classified fluctuates due to the effects of physical conditions such as temperature. Ta.
最近赤血球の溶血剤が改良されて、より強力で
瞬時に赤血球を溶血させることができるようにな
つた。 Recently, the hemolytic agent for red blood cells has been improved, making it more powerful and capable of instantly lysing red blood cells.
こういつた溶血剤の出現により、顆粒球系とリ
ンパ球系に分類可能に時間が短縮され、さらに特
殊な疾患の血液以外、ほとんどリンパ球系と顆粒
球系のレベルが一定であり、その区分が容易とな
つた。 With the advent of these hemolytic agents, the time required to classify the blood into granulocytic and lymphocytic systems has been shortened, and the level of lymphocytic and granulocytic systems is almost constant, except for blood for special diseases, and the classification is difficult. became easier.
しかし、一方では瞬時にして赤血球の溶血を行
うために白血球自体の大きさも小さくなり、ノイ
ズや赤血球のゴーストがリンパ球系の測定値に影
響を与える頻度も多くなつた。
However, on the other hand, because red blood cells are instantly hemolyzed, the size of the white blood cells themselves has become smaller, and the frequency with which noise and red blood cell ghosts affect lymphocyte measurements has increased.
本発明は上記状況に鑑みなされたものであり、
粒度分布測定装置のごとき、大がかりな装置を用
いずに、容易にリンパ球系細胞の割合や顆粒球系
細胞の割合が求められ、かつリンパ球系細胞信号
に混入するノイズがゴーストなどによる信号を確
実に検知し、簡単に短時間で正確な測定結果が得
られるような血液分析装置を提供する。 The present invention has been made in view of the above situation,
The percentage of lymphoid cells and the percentage of granulocytic cells can be easily determined without using large-scale equipment such as a particle size distribution measuring device, and the noise mixed in the lymphoid cell signal can be detected by signals such as ghosts. To provide a blood analyzer capable of reliably detecting and easily obtaining accurate measurement results in a short time.
本発明の血液分析装置は、液体に浮懸する血球
等の粒子を、液と粒子の光学的あるいは電気的な
差異に基づいて検出し粒子信号を発生する検出装
置１と、前記検出装置１に接続されそれぞれ異な
つた閾電圧を有する３つの比較回路２，３，４
と、前記３つの比較回路の２つ２，４に接続さ
れ、最も低いレベルＣを有する比較回路４から発
する信号の前縁でトリガされるパルスを加算し、
第２のレベルＡを有する比較回路２から発する信
号の後縁でトリガされるパルスを減算する加減算
可能な計数回路９と、前記計数回路９の計数値が
所定の値に達した時に警報を発する警報装置１２
と、さらに残りの最も高いレベルＢを有する比較
回路３からの信号を計数する第２の計数回路８
と、前記レベルＡを有する比較回路２の信号を計
数し、所定の最終の計数値に達した時に、前記第
２の計数回路８を停止させる回路７，１６と、前
記第２の計数回路８に接続され、前記最終の計数
値に対する割合（％）と、前記割合（％）の残り
の百分率（％）とを逐次演算する演算回路１３
と、前記演算回路１３の２つの演算結果を表示す
る表示装置１４，１５とを具え、測定終了と同時
にリンパ球系白血球の割合と、顆粒球系白血球の
割合とを表示することを特徴とする。
The blood analyzer of the present invention includes a detection device 1 that detects particles such as blood cells suspended in a liquid based on an optical or electrical difference between the liquid and the particles and generates a particle signal; Three comparison circuits 2, 3, 4 connected and each having a different threshold voltage
and a pulse triggered at the leading edge of the signal emanating from the comparator circuit 4 connected to two of said three comparator circuits 2, 4 and having the lowest level C;
A counting circuit 9 capable of addition and subtraction for subtracting pulses triggered by the trailing edge of the signal emitted from the comparator circuit 2 having a second level A, and issuing an alarm when the count value of the counting circuit 9 reaches a predetermined value. Alarm device 12
and a second counting circuit 8 that further counts the remaining signals from the comparator circuit 3 having the highest level B.
and circuits 7 and 16 that count the signals of the comparison circuit 2 having the level A and stop the second counting circuit 8 when a predetermined final count value is reached, and the second counting circuit 8 an arithmetic circuit 13 that is connected to and sequentially calculates the ratio (%) to the final count value and the remaining percentage (%) of the ratio (%);
and display devices 14 and 15 for displaying the two calculation results of the calculation circuit 13, and displaying the percentage of lymphoid leukocytes and the percentage of granulocytic leukocytes at the same time as the measurement is completed. .
本発明の血液分析装置においては、比較回路２
および計数回路７によつて白血球全体が弁別・計
数され、比較回路３および計数回路８によつて顆
粒球系白血球が弁別・計数され、演算回路１３に
よつて白血球細胞の各割合が演算されるので、粒
度分布測定装置のごとき大がかりな装置を用いず
に顆粒球系白血球の割合およびリンパ球系白血球
の割合を求めることができる。さらに、計数回路
９では、最も低いレベルＣを有する比較回路４か
ら発する信号の前縁でトリガされるパルス（白血
球、大きなノイズ信号、赤血球ゴーストによるパ
ルス）を加算し、第２のレベルＡを有する比較回
路２から発する信号の後縁でトリガされるパルス
（白血球によるパルス）を減算するので、白血球
によるパルスは結局加減算で０となり、大きなノ
イズ信号および赤血球ゴーストによるパルスのみ
を計数する。計数回路９の計数値が所定の値に達
したときには警報装置が警報を発するので、大き
なノイズ信号および赤血球ゴーストによるパルス
が多くリンパ球系白血球の計数に影響を与えてい
る危険性があることを知ることができる。
In the blood analyzer of the present invention, the comparison circuit 2
The counting circuit 7 discriminates and counts all white blood cells, the comparator circuit 3 and the counting circuit 8 discriminate and count granulocytic leukocytes, and the calculation circuit 13 calculates each percentage of white blood cells. Therefore, the proportion of granulocytic leukocytes and the proportion of lymphoid leukocytes can be determined without using a large-scale device such as a particle size distribution analyzer. Furthermore, in the counting circuit 9, the pulses triggered at the leading edge of the signal originating from the comparator circuit 4 having the lowest level C (pulses due to white blood cells, large noise signals, red blood cell ghosts) are added and the pulses having a second level A are added. Since the pulse triggered by the trailing edge of the signal emitted from the comparator circuit 2 (pulse due to white blood cells) is subtracted, the pulse due to white blood cells becomes 0 after addition and subtraction, and only pulses due to large noise signals and red blood cell ghosts are counted. When the count value of the counting circuit 9 reaches a predetermined value, the alarm device issues an alarm, indicating that there is a risk that large noise signals and pulses due to red blood cell ghosts may be affecting the count of lymphoid white blood cells. You can know.
以下図面の実施例に基づいて本発明実施例を説
明する。
Embodiments of the present invention will be described below based on the embodiments shown in the drawings.
第１図は本発明実施例の構成を示すブロツクダ
イヤグラムであり、第２図は測定原理の説明図、
第３図は動作の説明図である。 FIG. 1 is a block diagram showing the configuration of an embodiment of the present invention, and FIG. 2 is an explanatory diagram of the measurement principle.
FIG. 3 is an explanatory diagram of the operation.
１は血球等の粒子と粒子を浮懸する液体の光学
的あるいは電気的な差異に基づいて粒子を検出す
る検出装置、２，３，４はそれぞれ異なつた閾電
圧を有する比較回路、６はそれぞれの比較回路へ
の閾電圧を送る閾電圧発生回路、７，８，９は計
数回路であり、９は特にアツプダウンカウンタと
称される加算計数と減算計数を行い得るものが用
いられている。１０は比較回路２の出力パルスの
後縁を検知し、カウンタ９の減算用のパルスを発
生させる回路であり、１１は比較回路４の出力パ
ルスの前縁を検知し、カウンタ９の加算用のパル
スを発生させる回路である。１２は警報装置であ
り、１３は演算回路、１４，１５は表示回路であ
り、１６は計数停止信号発生回路である。 1 is a detection device that detects particles based on an optical or electrical difference between particles such as blood cells and the liquid in which they are suspended; 2, 3, and 4 are comparison circuits each having a different threshold voltage; and 6 are respective ones. A threshold voltage generation circuit 7, 8, and 9 are counting circuits that send a threshold voltage to a comparison circuit, and 9 is a so-called up-down counter that can perform addition and subtraction counting. 10 is a circuit that detects the trailing edge of the output pulse of the comparator circuit 2 and generates a pulse for subtraction of the counter 9; 11 is a circuit that detects the leading edge of the output pulse of the comparator circuit 4 and generates a pulse for the addition of the counter 9; This is a circuit that generates pulses. 12 is an alarm device, 13 is an arithmetic circuit, 14 and 15 are display circuits, and 16 is a counting stop signal generating circuit.
第２図は白血球の粒度分布曲線の一例の説明図
であり、粒度の小さい方からノイズや赤血球のゴ
ーストあるいは血小板の分布、続いてリンパ球系
白血球の分布、さらに最も大きい顆粒球系白血球
の３つの領域に大別される。 Figure 2 is an explanatory diagram of an example of the particle size distribution curve of white blood cells, starting with the distribution of noise, ghosts of red blood cells, or platelets from the smallest particle size, followed by the distribution of lymphoid leukocytes, and then the distribution of the largest three granulocytic leukocytes. It is broadly divided into two areas.
従つて、それぞれの分布領域の境界に閾レベル
Ａ，Ｂを設定することにより、リンパ球系白血球
と、顆粒球系白血球の計数を行うことができる。 Therefore, by setting threshold levels A and B at the boundaries of the respective distribution regions, it is possible to count lymphoid leukocytes and granulocyte leukocytes.
さらに、レベルＣを設けることにより、溶血不
十分な場合における混入赤血球の監視や、あるい
はノイズの混入を検知し、警報を発することがで
きる。 Furthermore, by providing level C, it is possible to monitor contaminated red blood cells when hemolysis is insufficient, or to detect noise contamination and issue an alarm.
第３図は上記の警報動作を含む本発明実施例の
動作の説明図であり、検出装置１の出力として線
路１７に現れる信号１８、比較回路２，３，４の
各々の出力端１９，２０，２１に現れる各々の出
力信号２２，２３，２４と、パルス発生回路１１
の出力信号２５と、同じくパルス発生回路１０の
出力信号２６とが図示されている。 FIG. 3 is an explanatory diagram of the operation of the embodiment of the present invention including the above-mentioned alarm operation, in which the signal 18 appearing on the line 17 as the output of the detection device 1 and the output terminals 19, 20 of each of the comparator circuits 2, 3, 4 are shown. , 21 and the pulse generation circuit 11.
The output signal 25 of the pulse generating circuit 10 and the output signal 26 of the pulse generating circuit 10 are also shown.
比較回路２の閾電圧はＡであり、比較回路３の
閾電圧はＢ、比較回路４の閾電圧はＣである。 The threshold voltage of the comparison circuit 2 is A, the threshold voltage of the comparison circuit 3 is B, and the threshold voltage of the comparison circuit 4 is C.
今、第３図の信号１８において比較的大きな顆
粒球系の信号２７が検出装置１から出力される
と、比較回路２，３，４はそれぞれON状態とな
り、出力電圧２８，２９，３０を発生させ、さら
にパルス発生回路１１は、信号３０の前縁でトリ
ガされ、信号３１を発生し、同じくパルス発生回
路１０は、信号２８の後縁でトリガされ、信号３
２を発生する。 Now, when a relatively large granulocyte-based signal 27 is output from the detection device 1 in the signal 18 of FIG. Further, the pulse generating circuit 11 is triggered on the leading edge of the signal 30 and generates the signal 31, and the pulse generating circuit 10 is also triggered on the trailing edge of the signal 28 and generates the signal 31.
Generates 2.
信号２９は線路２０を通じ計数回路８に送ら
れ、信号２８は線路１９を通じ計数回路７および
パルス発生回路１０に送られる。同様に信号３０
は線路２１を通じパルス発生回路１１に送られ
る。 Signal 29 is sent to counting circuit 8 through line 20, and signal 28 is sent to counting circuit 7 and pulse generating circuit 10 through line 19. Similarly, signal 30
is sent to the pulse generating circuit 11 through the line 21.
比較的大きなノイズ信号３３はレベルＣを越え
るために比較回路４を通過し、信号３５を発生し
その前縁でトリガされ、パルス発生回路１１の出
力に信号３６を発生する。 The relatively large noise signal 33 passes through the comparator circuit 4 in order to exceed level C and generates a signal 35 which is triggered on its leading edge and generates a signal 36 at the output of the pulse generating circuit 11.
リンパ球系白血球による信号３７は、比較回路
２，４をONさせ、信号３８，３９を線路１９，
２１にそれぞれ発生させるために、前者の信号３
８は計数回路７とパルス発生回路１０に、後者の
信号３９はパルス発生回路１１に送られる。パル
ス発生回路１０からは信号４１が、パルス発生回
路１１からは信号４０が出力される。 The signal 37 from the lymphoid leukocytes turns on the comparison circuits 2 and 4, and the signals 38 and 39 are sent to the lines 19 and 4.
21 respectively, the former signal 3
8 is sent to the counting circuit 7 and the pulse generating circuit 10, and the latter signal 39 is sent to the pulse generating circuit 11. The pulse generating circuit 10 outputs a signal 41, and the pulse generating circuit 11 outputs a signal 40.
レベルＣよりも小さいノイズ信号４２は、どの
比較回路もトリガすることができないために出力
は生じない。 A noise signal 42 smaller than level C cannot trigger any comparator circuit and therefore produces no output.
レベルＢを越えた信号２９は、計数回路８で、
顆粒球系白血球として計数される。レベルＡを越
えた信号２８と３８は、リンパ球系および顆粒球
系白血球の総数として、計数回路７に計数される
と同時に、パルス発生回路１０を介し、計数回路
９に減算用のパルス３２と４１を送り、レベルＣ
を越えパルス発生回路１１を介して送られて来た
信号３１，３６，４０による計数回路９に加算さ
れた計数値から逐次減算が行われる。すなわち、
レベルＡを越えた信号２７と３７に対しては、差
し引きゼロであるが、レベルＣを越え、Ａを越え
ない信号３３によるパルス３６が計数回路９に残
留し、これが所定の値を越えると警報装置１２を
作動させ警報を発する。 The signal 29 exceeding level B is sent to the counting circuit 8.
Counted as granulocytic leukocytes. The signals 28 and 38 exceeding level A are counted by the counting circuit 7 as the total number of lymphocytes and granulocytic leukocytes, and at the same time, they are sent to the counting circuit 9 via the pulse generating circuit 10 as a pulse 32 for subtraction. Send 41 and level C
Subtraction is performed successively from the count value added to the counting circuit 9 based on the signals 31, 36, and 40 sent via the pulse generating circuit 11. That is,
For signals 27 and 37 that exceed level A, the subtraction is zero, but a pulse 36 caused by signal 33 that exceeds level C but does not exceed level A remains in the counting circuit 9, and if this exceeds a predetermined value, an alarm is issued. The device 12 is activated to issue an alarm.
一方、計数回路７に送られた信号２８，３８は
白血球の総数として計数され、例えば計数値が
512に達すると、計数停止信号発生回路１６をト
リガし、計数回路８と計数回路９に停止信号を送
る。 On the other hand, the signals 28 and 38 sent to the counting circuit 7 are counted as the total number of white blood cells, and for example, the counted value is
When it reaches 512, it triggers the counting stop signal generation circuit 16 and sends a stop signal to the counting circuit 8 and the counting circuit 9.
演算回路１３は、計数回路７の最終計数値が
512である場合には、パルスが１個加算されるご
とに、
Y1＝Ｘ（１／512）×100
と、
Y2＝100−Ｘ（１／512）×100
の演算を行い、Y1を表示装置１４で、Y2を表示
装置１５で表示する。すなわち、Ｘは顆粒球系白
血球のパルス数であり、最終計数値512に対して
何％あるかを示すものであり、一方100から顆粒
球系白血球の割合を引いたものが残りのリンパ球
系白血球数の％表示値である。 The arithmetic circuit 13 calculates the final count value of the counting circuit 7.
512, each time one pulse is added, calculate Y 1 = X (1/512) x 100 and Y 2 = 100 - X (1/512) x 100 , and is displayed on the display device 14 and Y 2 is displayed on the display device 15. In other words, X is the pulse number of granulocytic leukocytes, which indicates what percentage of the final count of 512 there is, and on the other hand, subtracting the percentage of granulocytic leukocytes from 100 is the number of pulses of the remaining lymphocytes. This is the percentage value of white blood cell count.
以上の測定は通常の血球計数と同時にスタート
し、血球計数が終了する以前に測定結果が得ら
れ、また一方では、ノイズの混入、あるいは長時
間放置したためにリンパ球系の白血球がノイズの
検知領域に混入した場合などにおいて、確実に警
報を発するので、例えば検出装置１を一般の血球
計数装置と共用し、本発明装置を血球計数装置に
内蔵したり、オブシヨンとして用いた場合におい
ても、正常な計数測定が行われているかの判断と
して用いることも可能である。 The above measurements start at the same time as normal blood cell counting, and the measurement results are obtained before the blood cell counting is completed.On the other hand, it is possible that noise is mixed in, or that lymphocyte white blood cells are left in the noise detection area due to being left for a long time. For example, if the detection device 1 is used in common with a general blood cell counter, and the device of the present invention is built into the blood cell counter or used as an accessory, it will be possible to detect normal It can also be used to determine whether counting measurements are being performed.
以上のように、本発明の血液分析装置によれ
ば、従来のごとく、粒度分布曲線を求め、さらに
演算によつて各々のパーセンテージを算出するの
ではなく、測定終了と同時に結果が得られるた
め、臨床上すこぶる効果が大きい。
As described above, according to the blood analyzer of the present invention, instead of obtaining a particle size distribution curve and calculating each percentage by calculation as in the past, results can be obtained at the same time as the measurement is completed. It has great clinical effects.
第１図は本発明実施例のブロツク図であり、第
２図、第３図は測定原理および動作の説明図であ
る。
１……検出回路、２，３，４……比較回路、
７，８，９……計数回路、１０，１１……パルス
発生回路、１３……演算回路、１４，１５……表
示回路。
FIG. 1 is a block diagram of an embodiment of the present invention, and FIGS. 2 and 3 are illustrations of the measurement principle and operation. 1...detection circuit, 2, 3, 4...comparison circuit,
7, 8, 9... Counting circuit, 10, 11... Pulse generation circuit, 13... Arithmetic circuit, 14, 15... Display circuit.
Claims (1)
光学的あるいは電気的な差異に基づいて検出し粒
子信号を発生する検出装置１と、前記検出装置１
に接続されそれぞれ異なつた閾電圧を有する３つ
の比較回路２，３，４と、前記３つの比較回路の
２つ２，４に接続され、最も低いレベルＣを有す
る比較回路４から発する信号の前縁でトリガされ
るパルスを加算し、第２のレベルＡを有する比較
回路２から発する信号の後縁でトリガされるパル
スを減算する加減算可能な計数回路９と、前記計
数回路９の計数値が所定の値に達した時に警報を
発する警報装置１２と、さらに残りの最も高いレ
ベルＢを有する比較回路３からの信号を計数する
第２の計数回路８と、前記レベルＡを有する比較
回路２の信号を計数し、所定の最終の計数値に達
した時に、前記第２の計数回路８を停止させる回
路７，１６と、前記第２の計数回路８に接続さ
れ、前記最終の計数値に対する割合（％）と、前
記割合（％）の残りの百分率（％）とを逐次演算
する演算回路１３と、前記演算回路１３の２つの
演算結果を表示する表示装置１４，１５とを具
え、測定終了と同時にリンパ球系白血球の割合
と、顆粒球系白血球の割合とを表示することを特
徴とする血液分析装置。1 A detection device 1 that detects particles such as blood cells suspended in a liquid based on an optical or electrical difference between the liquid and the particles and generates a particle signal, and the detection device 1
Three comparison circuits 2, 3, and 4 are connected to each other and have different threshold voltages. a counting circuit 9 capable of addition and subtraction for adding edge-triggered pulses and subtracting trailing edge-triggered pulses of the signal emanating from the comparator circuit 2 having a second level A; An alarm device 12 that issues an alarm when a predetermined value is reached, a second counting circuit 8 that counts the remaining signals from the comparator circuit 3 having the highest level B, and a comparator circuit 2 having the level A. circuits 7 and 16 that count signals and stop the second counting circuit 8 when a predetermined final count value is reached; (%) and the remaining percentage (%) of the ratio (%), and display devices 14 and 15 that display the two calculation results of the calculation circuit 13. A blood analyzer characterized in that it simultaneously displays the percentage of lymphoid leukocytes and the percentage of granulocytic leukocytes.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56210841A JPS58113735A (en) | 1981-12-26 | 1981-12-26 | Analyzing device for blood |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56210841A JPS58113735A (en) | 1981-12-26 | 1981-12-26 | Analyzing device for blood |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS58113735A JPS58113735A (en) | 1983-07-06 |
| JPH0239732B2 true JPH0239732B2 (en) | 1990-09-06 |
Family
ID=16595990
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP56210841A Granted JPS58113735A (en) | 1981-12-26 | 1981-12-26 | Analyzing device for blood |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS58113735A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS62134542A (en) * | 1985-12-07 | 1987-06-17 | Hitachi Electronics Eng Co Ltd | Data processing system of fine particle detector |
| JPH0251044A (en) * | 1988-08-12 | 1990-02-21 | Omron Tateisi Electron Co | Cell analyzer |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS56106135A (en) * | 1980-01-28 | 1981-08-24 | Toa Medical Electronics Co Ltd | Particle analyzer |
-
1981
- 1981-12-26 JP JP56210841A patent/JPS58113735A/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS56106135A (en) * | 1980-01-28 | 1981-08-24 | Toa Medical Electronics Co Ltd | Particle analyzer |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS58113735A (en) | 1983-07-06 |
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