JPS6113179B2 - - Google Patents
Info
- Publication number
- JPS6113179B2 JPS6113179B2 JP7909075A JP7909075A JPS6113179B2 JP S6113179 B2 JPS6113179 B2 JP S6113179B2 JP 7909075 A JP7909075 A JP 7909075A JP 7909075 A JP7909075 A JP 7909075A JP S6113179 B2 JPS6113179 B2 JP S6113179B2
- Authority
- JP
- Japan
- Prior art keywords
- diluent
- conductivity
- signal
- circuit
- blood cell
- 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
- 210000000601 blood cell Anatomy 0.000 claims description 19
- 239000003085 diluting agent Substances 0.000 claims description 14
- 238000005534 hematocrit Methods 0.000 claims description 9
- 238000006243 chemical reaction Methods 0.000 claims description 5
- 238000009499 grossing Methods 0.000 claims description 5
- 238000012544 monitoring process Methods 0.000 claims description 4
- 239000002245 particle Substances 0.000 claims description 4
- 210000004369 blood Anatomy 0.000 claims description 3
- 239000008280 blood Substances 0.000 claims description 3
- 238000005259 measurement Methods 0.000 claims 1
- 238000001514 detection method Methods 0.000 description 5
- 239000007788 liquid Substances 0.000 description 5
- 230000005284 excitation Effects 0.000 description 4
- 230000001186 cumulative effect Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 239000000284 extract Substances 0.000 description 2
- 230000007423 decrease Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000000034 method Methods 0.000 description 1
Landscapes
- Investigating Or Analysing Biological Materials (AREA)
- Investigating Or Analyzing Materials By The Use Of Electric Means (AREA)
Description
【発明の詳細な説明】
この発明は血液希釈液を血球粒子が同時に二個
通過できない程度に狭あいに形成された微細孔に
通過させ、血球の通過時において血球と希釈液と
の電導度の相違に基づく抵抗変化を電気的にとり
出して計測する装置に関するものであり、希釈血
液の電導度変化によるヘマトクリツト値の変動を
自動的に補償する装置を提供するものである。DETAILED DESCRIPTION OF THE INVENTION This invention allows a blood diluent to pass through micropores formed so narrow that two blood cell particles cannot pass through at the same time, and reduces the electrical conductivity between the blood cells and the diluent when the blood cells pass through. The present invention relates to a device that electrically extracts and measures resistance changes based on differences, and provides a device that automatically compensates for fluctuations in hematocrit values due to changes in the conductivity of diluted blood.
一般の導電式血球計数器においては、血球が微
細孔を通過する時の抵抗の変化は、希釈液の電導
度の逆数である比抵抗と血球容積に比例し、微細
孔の面積の二乗に反比例する。よつて、希釈液の
電導度が変化すると比抵抗値も変化し、それによ
り血球信号の大きさも変化する。その結果とし
て、血球信号波高値の累積値であるヘマトクリツ
ト値が変動するという欠点があつた。 In a general conductive blood cell counter, the change in resistance when blood cells pass through the micropores is proportional to the specific resistance, which is the reciprocal of the conductivity of the diluent, and the blood cell volume, and inversely proportional to the square of the area of the micropores. do. Therefore, when the conductivity of the diluent changes, the specific resistance value also changes, and thereby the magnitude of the blood cell signal also changes. As a result, there was a drawback that the hematocrit value, which is the cumulative value of blood cell signal peak values, fluctuated.
本発明はこれを解決したもので、以下図面に基
づいて本発明を説明する。 The present invention solves this problem, and the present invention will be explained below based on the drawings.
図面は本発明装置の構成を示す説明図であり、
血球の検出部を図面の左側に具体的な断面図で表
わしている。 The drawing is an explanatory diagram showing the configuration of the device of the present invention,
The blood cell detection section is shown in a detailed cross-sectional view on the left side of the drawing.
本装置は、サンプル容器１７に収納された試料
１８の液面下に微細孔１９が位置するように、試
料１８中に浸漬された検出器２０の内部の希釈液
２１に浸漬された電極１２と、検出器２０の外側
の試料１８中に浸漬された外部電極２２と、微細
孔１９を通じて検出器２０の内部に吸引される試
料１８を確認するための液面検出手段１４と、前
記電極１２に接続した発振器１と前置増幅器２と
ろ波器３と整流器４と平滑回路５とで、前記希釈
液２１中の電導度を監視する手段と、前記平滑回
路５に接続した電圧時定数変換回路９と遅延回路
１０とスタート回路１１とで構成されゲート回路
８にスタート・ストツプ信号を送る回路と、前記
電極１２に接続され粒子信号を検出するための励
起電源１６と前置増幅器２とろ波器３ａと主増幅
器６とＡ−Ｄ変換器７と計数回路１３と表示回路
等で構成されている。 This device includes an electrode 12 immersed in a diluent 21 inside a detector 20 immersed in a sample 18 so that a microhole 19 is located below the liquid level of the sample 18 housed in a sample container 17. , an external electrode 22 immersed in the sample 18 outside the detector 20, a liquid level detection means 14 for checking the sample 18 sucked into the detector 20 through the microhole 19, and an external electrode 22 immersed in the sample 18 outside the detector 20; Means for monitoring the electrical conductivity in the diluent 21 by the connected oscillator 1, preamplifier 2, filter 3, rectifier 4, and smoothing circuit 5; and a voltage time constant conversion circuit 9 connected to the smoothing circuit 5. A circuit comprising a delay circuit 10 and a start circuit 11 and sending start/stop signals to the gate circuit 8; an excitation power source 16 connected to the electrode 12 for detecting particle signals; a preamplifier 2; and a filter 3a. It is composed of a main amplifier 6, an A-D converter 7, a counting circuit 13, a display circuit, etc.
まず、希釈液の電導度の変化を取り出すための
発振器１と、血球信号を取り出すための励起電源
１６により、電極１２と電極２２の間に発生した
信号を前置増幅器２で増幅し、前置増幅器２の出
力から発振器１の周波数成分のみをろ波器３にて
取り出し、整流器４と平滑回路５とでその振幅の
実効直流電圧に変換する。 First, a preamplifier 2 amplifies a signal generated between the electrodes 12 and 22 using an oscillator 1 for extracting changes in the conductivity of the diluent and an excitation power source 16 for extracting blood cell signals. A filter 3 extracts only the frequency component of the oscillator 1 from the output of the amplifier 2, and a rectifier 4 and a smoothing circuit 5 convert it into an effective DC voltage of the amplitude.
一方、ろ波器３ａによつて粒子信号のみを取り
出し、主増幅器６を通してＡ−Ｄ変換器７でその
波高値をＡ−Ｄ変換し、ヘマトクリツト値を計数
し、表示する。その途中にゲート回路８を設け、
計数スタート・ストツプ信号にて計数時間を設定
できるようにする。 On the other hand, only the particle signal is taken out by the filter 3a, passed through the main amplifier 6, and its peak value is subjected to AD conversion by the AD converter 7, and the hematocrit value is counted and displayed. A gate circuit 8 is provided in the middle,
Allows the counting time to be set using the counting start/stop signal.
そこで、平滑回路５の出力電圧で電圧時定数変
換回路９を動作させ、その時定数変化に比例して
遅延回路１０の遅延時間が変化するようにし、ス
タート回路１１の出力信号でゲートを開き、又遅
延回路１０の出力信号でゲートが閉じるようにす
る。以上の回路構成によつて、希釈液の電導度変
化に対してヘマトクリツト値を無関係にすること
ができる。 Therefore, the voltage time constant conversion circuit 9 is operated by the output voltage of the smoothing circuit 5, the delay time of the delay circuit 10 is changed in proportion to the change in the time constant, and the gate is opened by the output signal of the start circuit 11. The gate is closed by the output signal of the delay circuit 10. With the above circuit configuration, it is possible to make the hematocrit value irrelevant to changes in the conductivity of the diluent.
血球が微細孔１９を通過する時の電極１２と電
極２２の間の抵抗変化は、希釈液の電導度の逆数
である比抵抗に比例するため、電導度が大きくな
ると、比抵抗が小さくなり変化抵抗値は小さくな
る。その結果、励起電源１６によつて電極１２と
電極２２の間に発生する変化電圧（血球信号）も
小さくなる。一方、ヘマトクリツト値は血球信号
の波高値の累積値、すなわち血球信号をＡ−Ｄ変
換しパルス数を計数回路１３で計数した値である
から、結果としてヘマトクリツト値は小さくなる
ので、遅延時間を電導度に比例して長くすればよ
い。 The change in resistance between the electrodes 12 and 22 when blood cells pass through the micropores 19 is proportional to the specific resistance, which is the reciprocal of the electrical conductivity of the diluent, so as the electrical conductivity increases, the specific resistance decreases and changes. The resistance value becomes smaller. As a result, the changing voltage (blood cell signal) generated between the electrodes 12 and 22 by the excitation power source 16 also becomes smaller. On the other hand, the hematocrit value is the cumulative value of the peak values of the blood cell signal, that is, the value obtained by A-D converting the blood cell signal and counting the number of pulses in the counting circuit 13. As a result, the hematocrit value becomes small, so the delay time is It can be made longer in proportion to the degree.
上記ゲート回路８はろ波器３，３ａから計数回
路１３までの間であればどこに設けても同じこと
である。 The gate circuit 8 can be provided anywhere between the filters 3 and 3a and the counting circuit 13.
又、計数回路１３をゲート回路８を用いずに直
接スタート・ストツプ信号でコントロールしても
よい。 Further, the counting circuit 13 may be directly controlled by a start/stop signal without using the gate circuit 8.
さらに、液面検出装置１４がなくても、スター
ト回路１１の出力信号を別の方法、例えばマニユ
アルの信号等によつて与えることも可能である。
こうすることによつて、液面検出装置も不要とな
る。 Furthermore, even without the liquid level detection device 14, it is possible to provide the output signal of the start circuit 11 by another method, such as a manual signal.
This also eliminates the need for a liquid level detection device.
なお、図中１５は表示手段、１２は電極、１６
は励起電源、１７はサンプル容器、１８は試料、
１９は微細孔を示す。 In addition, in the figure, 15 is a display means, 12 is an electrode, and 16
is an excitation power source, 17 is a sample container, 18 is a sample,
19 indicates a micropore.
以上の如く、本発明によれば希釈液の電導度変
化に対して自動的にヘマトクリツト値を無関係に
することが可能であり、また、マニユアル信号で
スタート信号を与えれば、従来粒子計数装置には
不可欠であつた微細孔１９を通じて検出器内に吸
引される試料１８を定量するための複数の液面検
出装置が不要となる等、コスト的にも優れた効果
を奏するものである。 As described above, according to the present invention, it is possible to automatically make the hematocrit value irrelevant to changes in the conductivity of the diluent, and if a start signal is given using a manual signal, it is possible to This eliminates the need for a plurality of liquid level detection devices for quantifying the sample 18 sucked into the detector through the fine holes 19, which were essential, and provides excellent cost-effective effects.
図面は本発明のブロツクダイヤグラムである。
１……発振器、２……前置増幅器、３……ろ波
器、８……ゲート回路、９……電圧時定数変換回
路、１０……遅延回路。
The drawing is a block diagram of the invention. 1... Oscillator, 2... Preamplifier, 3... Filter, 8... Gate circuit, 9... Voltage time constant conversion circuit, 10... Delay circuit.
Claims (1)
ない程度に狭あいに形成された微細孔１９に通過
させ、血球の通過時において血球と希釈液との電
導度の相違に基づく抵抗変化を電気的にとり出し
計測する装置において、発振器１及び励起電源１
６により希釈液２１中に浸漬された電極１２に発
生した信号を前置増幅器２で増幅後、ろ波器３を
通して発振器１の周波数成分を取り出し、整流器
４と平滑回路５で整流、平滑して希釈液の電導度
を直流電圧に変換する電導度監視手段と、前記前
置増幅器２の出力信号から血球信号をろ波器３ａ
で取り出し、主増幅器６で増幅した後、Ａ−Ｄ変
換器７で前記血球信号の波高値をパルス数に変換
する手段と、前記電導度監視手段からの出力電圧
で電圧時定数変換回路９を動作させ、その時定数
変化に比例して遅延回路１０で遅延させたストツ
プ信号をゲート回路８に送りスタート回路１１か
らのスタート信号で開かれたゲートを閉じること
によつて、計数回路１３、表示手段１５で計数表
示されるヘマトクリツト値を前記電導度監視手段
の出力に基づいて調整できる手段とからなるヘマ
トクリツト測定装置。1 A blood diluent is passed through a micropore 19 formed so narrow that two blood cell particles cannot pass through at the same time, and resistance changes due to differences in conductivity between the blood cells and the diluent are electrically measured when the blood cells pass through. In a device that takes measurements at
6, the signal generated at the electrode 12 immersed in the diluent 21 is amplified by the preamplifier 2, and then passed through the filter 3 to extract the frequency component of the oscillator 1. The signal is then rectified and smoothed by the rectifier 4 and the smoothing circuit 5. conductivity monitoring means for converting the conductivity of the diluent into a DC voltage; and a filter 3a for detecting blood cell signals from the output signal of the preamplifier 2.
After being amplified by the main amplifier 6, the A-D converter 7 converts the peak value of the blood cell signal into a pulse number, and the output voltage from the conductivity monitoring means converts the voltage time constant conversion circuit 9. The counting circuit 13 and the display means 15. A hematocrit measuring device comprising means for adjusting the hematocrit value counted and displayed in step 15 based on the output of the conductivity monitoring means.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7909075A JPS522770A (en) | 1975-06-24 | 1975-06-24 | Hematocrit measuring device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7909075A JPS522770A (en) | 1975-06-24 | 1975-06-24 | Hematocrit measuring device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS522770A JPS522770A (en) | 1977-01-10 |
| JPS6113179B2 true JPS6113179B2 (en) | 1986-04-11 |
Family
ID=13680172
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP7909075A Granted JPS522770A (en) | 1975-06-24 | 1975-06-24 | Hematocrit measuring device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS522770A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS55159156A (en) * | 1979-05-31 | 1980-12-11 | Toa Medical Electronics Co Ltd | Hematocrit value measuring apparatus |
| US5385846A (en) * | 1993-06-03 | 1995-01-31 | Boehringer Mannheim Corporation | Biosensor and method for hematocrit determination |
-
1975
- 1975-06-24 JP JP7909075A patent/JPS522770A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS522770A (en) | 1977-01-10 |
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