JPS63149567A - Optical measuring method in physical property change - Google Patents
Optical measuring method in physical property changeInfo
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- JPS63149567A JPS63149567A JP29470686A JP29470686A JPS63149567A JP S63149567 A JPS63149567 A JP S63149567A JP 29470686 A JP29470686 A JP 29470686A JP 29470686 A JP29470686 A JP 29470686A JP S63149567 A JPS63149567 A JP S63149567A
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- light
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- changes
- physical property
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Links
- 230000000704 physical effect Effects 0.000 title claims abstract description 28
- 238000000034 method Methods 0.000 title claims abstract description 10
- 230000003287 optical effect Effects 0.000 title claims description 12
- 239000011159 matrix material Substances 0.000 claims abstract description 4
- 238000005259 measurement Methods 0.000 claims description 33
- 238000000691 measurement method Methods 0.000 claims description 11
- 230000001678 irradiating effect Effects 0.000 claims 1
- 210000004413 cardiac myocyte Anatomy 0.000 abstract description 23
- 230000001133 acceleration Effects 0.000 abstract description 15
- 210000004027 cell Anatomy 0.000 abstract description 10
- 239000000126 substance Substances 0.000 abstract description 2
- 230000010349 pulsation Effects 0.000 description 8
- 230000000694 effects Effects 0.000 description 4
- CIWBSHSKHKDKBQ-JLAZNSOCSA-N Ascorbic acid Chemical compound OC[C@H](O)[C@H]1OC(=O)C(O)=C1O CIWBSHSKHKDKBQ-JLAZNSOCSA-N 0.000 description 3
- 238000000354 decomposition reaction Methods 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 230000000007 visual effect Effects 0.000 description 3
- 238000000855 fermentation Methods 0.000 description 2
- 230000004151 fermentation Effects 0.000 description 2
- 210000003754 fetus Anatomy 0.000 description 2
- 230000004044 response Effects 0.000 description 2
- 206010021143 Hypoxia Diseases 0.000 description 1
- 231100000457 cardiotoxic Toxicity 0.000 description 1
- 230000001451 cardiotoxic effect Effects 0.000 description 1
- 238000007796 conventional method Methods 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 210000003722 extracellular fluid Anatomy 0.000 description 1
- 238000001093 holography Methods 0.000 description 1
- 230000007954 hypoxia Effects 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 230000002107 myocardial effect Effects 0.000 description 1
- 210000004165 myocardium Anatomy 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 230000035935 pregnancy Effects 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
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- Indicating Or Recording The Presence, Absence, Or Direction Of Movement (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は物性変化における光学的測定方法に係り、特に
細胞の薬物動態変化等を測定するのに好適な物性変化に
おける光学的測定方法に関する。DETAILED DESCRIPTION OF THE INVENTION [Industrial Application Field] The present invention relates to an optical measurement method for changes in physical properties, and particularly to an optical measurement method for changes in physical properties suitable for measuring changes in pharmacokinetics of cells.
一般に、物体の動きを光学的に測定する理論としては、
ドツプラー効果を利用する方法あるいはホログラフィ−
解析等が知られており、既に実用化されている。Generally, the theory of optically measuring the movement of objects is as follows:
Method using Doppler effect or holography
Analysis, etc. are known and have already been put into practical use.
ところが、これらの理論の対象となる物体は、運動力学
的様式に整然と当てはめることができる剛体に限られて
いる。すなわち、単位時間当りの動きを捉えた場合に、
物体自体が固有の運動をせず、物体のどの点を観察して
も全て等速度で運動する物体に限られている。このため
、例えば心筋細胞の特性である拍動に伴なう収縮性等、
前述の運動方程式に該当しない物性変化は、旧来の光学
的測定方法では測定できず、専ら顕微鏡による目視観察
に頼らざるを得なかった。However, the objects covered by these theories are limited to rigid bodies that can be systematically applied to kinematics. In other words, when capturing the movement per unit time,
The object itself has no inherent motion, and no matter which point on the object we observe, we are limited to objects that move at the same speed. For this reason, for example, the contractility associated with pulsation, which is a characteristic of cardiac muscle cells,
Changes in physical properties that do not fall under the above-mentioned equation of motion cannot be measured using conventional optical measurement methods, and have had to rely solely on visual observation using a microscope.
しかしながら目視観察による場合には、正確な物性変化
を把握することができず、物性変化の測定方法としては
極めて不完全であるという間融がある。However, when visual observation is used, it is not possible to accurately determine changes in physical properties, and it is extremely incomplete as a method for measuring changes in physical properties.
そこで一部では、第７図に示すように細胞Ｃ上の適当な
位置に、細胞Ｃを横切る基準線りを設定し、この基準！
Ｌ上の二点Ａ、Ｂ間の偏位を測定することにより、心筋
細胞の拍動に伴なう収縮性の変化を捉えようとする試み
がなされている。Therefore, as shown in Fig. 7, a reference line that crosses cell C is set at an appropriate position on cell C, and this reference line!
Attempts have been made to capture changes in contractility accompanying the pulsation of cardiac muscle cells by measuring the deviation between two points A and B on L.
ところで、第７図に示す測定方法は、測定結果を数値化
できるため、目視観察に比較してより正確な物性変化を
把握できるという利点を有している。By the way, the measurement method shown in FIG. 7 has the advantage that the measurement results can be quantified, so that changes in physical properties can be grasped more accurately than visual observation.
ところが、測定点がＡ、Ｂ二点のみであり、基準線りの
設定位置によってＡ、Ｂ二点間の偏位も当然異なるため
、必ずしも細胞Ｃ全体の変化を忠実に捉えているとは云
えないという問題がある。However, since the measurement points are only two points A and B, and the deviation between the two points A and B naturally differs depending on the setting position of the reference line, it cannot be said that changes in the entire cell C are necessarily accurately captured. The problem is that there is no.
本発明はかかる現況に鑑みなされたもので、心筋細胞の
拍動に伴なう収縮性の変化等の物性変化を正確に測定す
ることができる物性変化における光学的測定方法を提供
することを目的とする。The present invention was made in view of the current situation, and an object of the present invention is to provide an optical measurement method for changes in physical properties that can accurately measure changes in physical properties such as changes in contractility accompanying the pulsation of cardiac muscle cells. shall be.
本発明は、物体表面からの光の受光面への入射強度が、
単位受光面積と単位時間当りの流れとしてボインティン
グ・ベクトルＳの時間平均で与えられることに着目し、
物体の動きにより変化するＳの単位時間当りの平均値の
絶対値を速度成分としたものである。In the present invention, the intensity of light incident on the light receiving surface from the surface of the object is
Focusing on the fact that the unit light receiving area and the flow per unit time are given by the time average of the Bointing vector S,
The velocity component is the absolute value of the average value per unit time of S that changes due to the movement of the object.
すなわち、本発明は、多数の測定点をマトリクス状に配
列して構成される測定領域を被測定物体の表面に設定し
この測定領域に一定光量の光を照射する発光手段と、前
記測定領域からの反射光を受光しこれを前記各測定点別
に分解して認識する受光手段とを備え、前記受光手段に
より、受光手段への光の入射強度を各測定点別に測定す
るとともに、その単位時間当りの平均値の縁対値を求め
、これを各測定点における被測定物体の物性変化の速度
成分とするようにしたことを特徴とする。That is, the present invention provides a light-emitting means that sets a measurement area formed by arranging a large number of measurement points in a matrix on the surface of an object to be measured, and irradiates this measurement area with a constant amount of light; and a light-receiving means that receives the reflected light and recognizes the reflected light by separating it into each of the measurement points, and the light-receiving means measures the intensity of light incident on the light-receiving means for each measurement point, and measures the incident intensity of the light per unit time. The method is characterized in that the edge pair value of the average value of is determined, and this value is used as the velocity component of the physical property change of the object to be measured at each measurement point.
本発明に係る物性変化における光学的測定方法において
は、受光手段により、受光手段への光の入射強度を各測
定点別に測定するとともに、その単位時間当りの平均値
の絶対値を求め、これを各測定点における被測定物体の
物性変化の速度成分としている。したがって、この速度
成分を用いることにより、各測定点における速度。In the optical measurement method for changes in physical properties according to the present invention, the intensity of light incident on the light receiving means is measured at each measurement point, and the absolute value of the average value per unit time is determined. This is the velocity component of the physical property change of the object to be measured at each measurement point. Therefore, by using this velocity component, the velocity at each measurement point can be determined.
加速度、測定領域全体の速度、加速度、測定領域におけ
る被測定物体の物性変化の周期および方向等を容易に得
ることができ、物性変化を正確に測定することが可能と
なる。Acceleration, velocity of the entire measurement area, acceleration, period and direction of changes in physical properties of the object to be measured in the measurement area, etc. can be easily obtained, making it possible to accurately measure changes in physical properties.
以下本発明実施の一態様を図面を参照して説明する。 One embodiment of the present invention will be described below with reference to the drawings.
第１図は、単離心筋細胞の拍動に伴なう収縮性の変化を
測定するための装置の一例を示すもので、図中、符号１
は発光素子であり、この発光素子１からは、一定光量の
光が単離心筋細胞２に照射されるようになっている。そ
してこの光は、第１図に示すように単離心筋細胞２の境
界面で反射し、受光素子３の受光面で受光されるように
なっている。Figure 1 shows an example of an apparatus for measuring changes in contractility associated with the pulsation of isolated cardiomyocytes.
is a light emitting element, and from this light emitting element 1, a constant amount of light is irradiated onto the isolated cardiac muscle cells 2. Then, as shown in FIG. 1, this light is reflected at the interface of the isolated cardiac muscle cells 2 and is received by the light receiving surface of the light receiving element 3.
前記受光素子３は、第２図に示すようにその受光面が、
単位素子をＸ軸方向およびＹ軸方向にｎＸｎ個マトリク
ス状に配列して構成される例えばＣＣＤで形成されてお
り、この受光素子３は、前記単離心筋細胞２の全域から
の反射光を画像信号として受光できるように位置設定さ
れている。そしてこの画像信号は、第１図に示すように
画像分解回路４により各単位緊子別の信号に分解され、
フレームメモリ５に記憶されるようになっている。The light-receiving element 3 has a light-receiving surface as shown in FIG.
For example, it is formed of a CCD, which is constructed by arranging nXn unit elements in a matrix in the X-axis direction and the Y-axis direction. The position is set so that it can receive light as a signal. This image signal is then decomposed into signals for each unit by an image decomposition circuit 4 as shown in FIG.
It is designed to be stored in the frame memory 5.
次に、単離心筋細胞２の拍動に伴なう収縮性の変化の測
定方法について説明する。Next, a method for measuring changes in contractility associated with pulsation of isolated cardiomyocytes 2 will be described.
発光素子１から出力された光は、第１図に示すように単
離心筋細胞２に照射され、単離心筋細胞２の境界面で反
射した反射光は、受光素子３の単離心筋細胞２に対応す
る部分に位置する各単位素子で受光される。The light output from the light emitting element 1 is irradiated onto the isolated cardiomyocytes 2 as shown in FIG. The light is received by each unit element located at a portion corresponding to the .
ところで、単離心筋細に！ｔ２の境界面からの反射光の
受光素子３への入射強度は、単位素子面積と単位時間当
りの流れとして、ボインティング・ベクトルＳの時間平
均で与えられる。By the way, isolated cardiac muscle in detail! The intensity of the reflected light from the boundary surface at t2 entering the light receiving element 3 is given by the time average of the Bointing vector S, expressed as a unit area of the element and a flow per unit time.
したがって、単位素子（Ｘ、Ｙ）上における入射強度を
Ｉ（Ｘ、Ｙ）とすれば、入射強度工（Ｘ、Ｙ）は、
Ｉ （Ｘ、Ｙ）＝＜＋Ｓ＋＞＝ ！／Ｔ／Ｔ１８１ ａ
ｔただし Ｅ：１１１場の強さ
Ｈ：磁場の強さ
で表わすことができる。Therefore, if the incident intensity on the unit element (X, Y) is I(X, Y), the incident intensity factor (X, Y) is I (X, Y)=<+S+>=! /T/T181 a
t However, E: 111 Field strength H: Can be expressed as magnetic field strength.
そしてこの入射強度１（Ｘ、Ｙ）は、単離心筋細胞２が
有する固有の組織が変化しない限り、単離心筋細胞２の
境界面の周期的な動きに対応して周期的に変化する。The incident intensity 1 (X, Y) changes periodically in response to the periodic movement of the interface of the isolated cardiomyocytes 2, unless the unique tissue of the isolated cardiomyocytes 2 changes.
第３図にその一例を示す。第３図は、３個の単位素子（
Ｘｍ−１，ＹｍＩＬ （Ｘｍ、Ｙｍ） ｅ （Ｘｍ十１
ｍＹｍ＋１）につき、縦軸に入射強度Ｉ、横軸に時間Ｔ
を取ってその変化を示したものである。An example is shown in FIG. Figure 3 shows three unit elements (
Xm-1, YmIL (Xm, Ym) e (Xm11
mYm+1), the vertical axis is the incident intensity I, and the horizontal axis is the time T.
The figure shows the change in the figure.
ところで、単位素子（Ｘ、Ｙ）上における入射強度Ｉ（
Ｘ、Ｙ）の単離心筋細胞２の動きによる時間変化を、Ｉ
（Ｘ、Ｙ）ｘｔＳＩ（Ｘ、Ｙｈ、、ｔｓ・・・・・・・
・・・・・・・・、Ｉ（Ｘ、Ｙ）ｎ−ｘｔ ｓ （ｔ：
脇秒）とすれば、速度Ｖ（Ｘ、Ｙ）および加速度α（
ｘ、ｙ）は次式で示される。By the way, the incident intensity I(
I
(X,Y)xtSI(X,Yh,,ts...
......,I(X,Y)n-xts (t:
(seconds), velocity V (X, Y) and acceleration α (
x, y) are shown by the following formula.
Ｖ（Ｘ ＃ Ｙ） ＝ ｌ Ｉ（Ｘ ＋ Ｙ）ｎｌ）”
Ａ１− Ｉ（Ｘ、Ｙ）ｎ −ｅ−ｔ ｌ／ｄｔ ”””
（２）ａｔｘ 、 ｙ） ＝ ＩＶ（Ｘ 、 Ｙ）（
、−２，、。ｔ −Ｖ（Ｘ＊ Ｑｎ−ｔ ）−、ｔ Ｌ
／ｄｔ鴬−−−−−（３）これを、単離心筋細胞２の全
域について計算すると、速度Ｖおよび加速度αは次式で
示されるＯ
第４図は、縦軸に速度Ｖ、横軸に時間Ｔをとって単離心
筋細胞２全域の速度Ｖの変化を示したものであり、また
第５図は、これに対応する加速度αの変化を縦軸に加速
度α、横軸に時間Ｔをとって示したものである。V(X #Y) = l I(X + Y)nl)”
A1- I(X,Y)n-e-t l/dt """
(2) atx, y) = IV(X, Y)(
,-2,,. t-V(X*Qn-t)-, tL
/dt Tsumugi (3) When this is calculated for the entire area of the isolated cardiomyocytes 2, the velocity V and acceleration α are expressed by the following formula. Fig. 5 shows the change in velocity V across the isolated cardiomyocytes 2 over time T, and Fig. 5 shows the corresponding change in acceleration α on the vertical axis and time T on the horizontal axis. This is what is shown.
第４図に示す速度Ｖの変化および第５図に示す加速度α
の変化は、単離心筋細胞２の拍動に伴なう収縮性の変化
に対応している。したがって、例えば第４図に示すよう
に１個の出力波形の時間ｔを測定することにより心拍時
間が求められる。なお、第５図に示す出力波形を用いて
も同様に求められる。Changes in velocity V shown in Figure 4 and acceleration α shown in Figure 5
The change corresponds to the change in contractility accompanying the pulsation of the isolated cardiomyocytes 2. Therefore, for example, as shown in FIG. 4, the heartbeat time can be determined by measuring the time t of one output waveform. Note that it can be similarly obtained using the output waveform shown in FIG.
また、第３図に示すように各単位素子間の位相差および
その方向を測定することにより、単離心筋細胞２の動き
の方向が求められる。すなわち、第３図においては、単
位素子（Ｘｍ−１ｅＹｍ−１）から単位素子（Ｘｍ＋
１ ＊ Ｙｍ＋ １）に向かう方向に動いていることが
判る。Further, as shown in FIG. 3, by measuring the phase difference between each unit element and its direction, the direction of movement of the isolated cardiac muscle cells 2 can be determined. That is, in FIG. 3, from unit element (Xm-1eYm-1) to unit element (Xm+
It can be seen that it is moving in the direction of 1*Ym+1).
本発明者等は、ＩＣＲ系マウス胎仔（妊娠１４〜１６日
目）の培養心筋細胞を使用し、細胞外液中のＣａ の
濃度を０．４〜１０ｍＭの範囲で変化させて収縮性の変
化を測定し、第６図（ａ）〜（ｄ）に示す結果を得た。The present inventors used cultured cardiomyocytes of ICR mouse fetuses (days 14 to 16 of pregnancy) to change the contractility by varying the concentration of Ca in the extracellular fluid in the range of 0.4 to 10 mM. were measured, and the results shown in FIGS. 6(a) to (d) were obtained.
なお第６図（ａ）は速度（ｉｎＬ／ｍ５ｅｃ ）を、ま
た第６図（ｂ）はプラス方向の加速度（ｉｎｔ、／ｎ１
ｓｅｃ９〕を、また第６図（Ｃ）はマイナス方向の加速
度（ｉｎｔ、７ｍ５ｅｃ’〕を、さらに第６図（ｄ）は
心拍時間〔ＳｅＣ〕をそれぞれ示す。Note that Fig. 6(a) shows the velocity (inL/m5ec), and Fig. 6(b) shows the acceleration in the positive direction (int, /n1
sec9], FIG. 6(C) shows the acceleration in the negative direction (int, 7m5ec'), and FIG. 6(d) shows the heartbeat time [SeC].
本発明者等はまた、前記測定結果と第７図に示す従来の
測定方法による結果とを比較した。The inventors also compared the above measurement results with the results obtained by the conventional measurement method shown in FIG.
その結果、本発明に係る測定方法の方が、単離心筋細胞
の拍動に伴なう収縮性の変化をより忠実に捉えているこ
とが確認された。また本発明に係る測定方法は、細胞の
薬物動態変化に限らず、低酸素や心毒性物質等の外的刺
蛍に対する心筋細胞の応答過程を測定する上でも有用で
あることが確認された。As a result, it was confirmed that the measurement method according to the present invention more faithfully captures changes in contractility accompanying the pulsation of isolated cardiomyocytes. Furthermore, it has been confirmed that the measuring method according to the present invention is useful not only for measuring pharmacokinetic changes in cells, but also for measuring the response process of cardiac muscle cells to external stimuli such as hypoxia and cardiotoxic substances.
なお、前記実施の一郭様では、受光素子３としてＣＣＤ
を用いる場合について説明したが、ＢＢＤあるいはＣＩ
Ｄ等の他の固体撮像素子を用いるようにしてもよい。Note that in the above embodiment, the light receiving element 3 is a CCD.
We have explained the case where BBD or CI is used.
Other solid-state image sensors such as D may also be used.
また前記実施の一郭様では、受光素子３からの画像信号
を、画像分解回路４で単位素子の個数と同一のｎＸｎ個
の信号に分解する。すなわち単位素子の位置と単離心筋
細胞２上の測定点の位置とが一致している場合について
説明したが、受光素子３からの出力信号は連続した画像
信号であるので、単位素子の個数よりも多くの信号に分
解して測定点の数を増やすことも、また逆に測定点の数
を減らすこともできる。したがってこの点からすれば、
受光素子３は固体撮像素子に限らず、ビジコン等の光学
的撮像管を用いることもできる。Further, in one embodiment, the image signal from the light receiving element 3 is decomposed by the image decomposition circuit 4 into nXn signals, which are the same as the number of unit elements. In other words, we have explained the case where the position of the unit element and the position of the measurement point on the isolated cardiomyocytes 2 coincide, but since the output signal from the light receiving element 3 is a continuous image signal, the number of unit elements is smaller than the number of unit elements. It is also possible to increase the number of measurement points by decomposing the signal into many signals, or conversely to reduce the number of measurement points. Therefore, from this point of view,
The light receiving element 3 is not limited to a solid-state image sensor, and an optical image pickup tube such as a vidicon can also be used.
また前記実施の一郭様では、心筋細胞の拍動に伴なう収
縮性の変化を測定する場合を例に採つて説明したが、心
筋細胞以外の細胞の測定にも同様に適用できる。また細
胞に限らず、スタンディングウェーブ現象によるタイヤ
の変形過程の測定、界面活性における境界面の動的変化
の測定、あるいは発酵により発生する気泡の社で変化す
る液面状態を観察して発酵状態を測定する場合等にも適
用できる。Further, in the embodiment described above, the case where changes in contractility accompanying the pulsation of cardiomyocytes are measured is taken as an example and explained, but the present invention can be similarly applied to measurement of cells other than myocardial cells. In addition to cells, we can also measure the deformation process of tires due to the standing wave phenomenon, measure dynamic changes in the interface due to surface activity, or observe the changing liquid level in the bubbles generated during fermentation to determine the fermentation state. It can also be applied to measurements, etc.
以上説明したように本発明は、受光手段により、受光手
段への光の入射強度を各測定点別に測定するとともに、
その単位時間当りの平均値の絶対値を求め、これを各測
定点における被測定物体の物性変化の速度成分としてい
るので、この速度成分を用いることにより、各測定点に
おける速度、加速度、測定領域全体の速度、加速度、測
定領域における被測定物体の物性変化の周期および方向
等を数値として得ることができ、物性変化を正確に測定
し把握することができる。As explained above, the present invention measures the intensity of light incident on the light receiving means at each measurement point using the light receiving means, and
The absolute value of the average value per unit time is determined and this is used as the velocity component of the physical property change of the object to be measured at each measurement point. By using this velocity component, the velocity, acceleration, and measurement area at each measurement point can be calculated. The overall velocity, acceleration, period and direction of change in physical properties of the object to be measured in the measurement area can be obtained as numerical values, and changes in physical properties can be accurately measured and understood.
第１図は本発明に係る物性変化における光学的測定方法
で用いられる装置の一例を示す構成図、第２図は第１図
の受光素子の受光面の構成を示す説明図、第３図は３個
の単位素子における入射強度の変化の一例を示すグラフ
、第４図は単離心筋細胞全域の速度変化の一例を示すグ
ラフ、第５図は同様の加速度変化の一例を示すグラフ、
第６図（ａ）はＩＣＲ系マウス胎仔の培養心筋細胞を用
いた実験における速度変化の結果を示すグラフ、第６図
（ｂ）は同様のプラス方向の加速度変化の結果を示すグ
ラフ、第６図（Ｃ）は同様のマイナス方向の加速度変化
の結果を示すグラフ、第６図（ｄ）は同様の心拍時間の
変化の結果を示すグラフ、第７図は心筋細胞の拍動に伴
なう収縮性の変化を測定する従来の方法を示す説明図で
ある。
１・・・発光素子、 ２・・・単離心筋細胞、 ３・・
・受光素子、 ４・・・画像分解回路、 ５・・・７レ
ームメモリ。
第１図
第２図FIG. 1 is a configuration diagram showing an example of a device used in the optical measurement method for changes in physical properties according to the present invention, FIG. 2 is an explanatory diagram showing the configuration of the light-receiving surface of the light-receiving element in FIG. A graph showing an example of a change in incident intensity in three unit elements, FIG. 4 is a graph showing an example of a velocity change in the entire area of an isolated cardiac muscle cell, and FIG. 5 is a graph showing an example of a similar acceleration change.
FIG. 6(a) is a graph showing the results of velocity changes in an experiment using cultured cardiomyocytes of ICR mouse fetuses, FIG. 6(b) is a graph showing the results of similar acceleration changes in the positive direction, Figure (C) is a graph showing the result of a similar change in acceleration in the negative direction, Figure 6 (d) is a graph showing the result of a similar change in heartbeat time, and Figure 7 is a graph showing the result of a similar change in heartbeat time. FIG. 2 is an explanatory diagram showing a conventional method of measuring changes in contractility. 1... Light emitting element, 2... Isolated cardiomyocytes, 3...
- Light receiving element, 4... Image decomposition circuit, 5... 7 frame memory. Figure 1 Figure 2
Claims (1)
測定領域を被測定物体の表面に設定しこの測定領域に一
定光量の光を照射する発光手段と、前記測定領域からの
反射光を受光しこれを前記各測定点別に分解して認識す
る受光手段とを備え、前記受光手段により、受光手段へ
の光の入射強度を各測定点別に測定するとともに、その
単位時間当りの平均値の絶対値を求め、これを各測定点
における被測定物体の物性変化の速度成分としたことを
特徴とする物性変化における光学的測定方法。 ２）各測定点における速度成分は、その総和により測定
領域における被測定物体の物性変化の速度成分とされる
ことを特徴とする特許請求の範囲第１項記載の物性変化
における光学的測定方法。 ３）受光手段は、固体撮像素子または光学的撮像管で形
成される受光装置と、この受光装置からの画像信号を各
測定点別の信号に分離して記憶する記憶装置とを備えて
いることを特徴とする特許請求の範囲第１項または第２
項記載の物性変化における光学的測定方法。[Scope of Claims] 1) A light emitting means for setting a measurement area formed by arranging a large number of measurement points in a matrix on the surface of an object to be measured and irradiating this measurement area with a constant amount of light; a light receiving means that receives reflected light from the area, decomposes it into each of the measurement points, and recognizes the same; the light receiving means measures the intensity of light incident on the light receiving means for each measurement point; 1. An optical measurement method for changes in physical properties, characterized in that the absolute value of the average value per time is determined, and this is taken as the velocity component of the change in physical properties of an object to be measured at each measurement point. 2) The optical measuring method for changes in physical properties according to claim 1, characterized in that the sum of the velocity components at each measurement point is used as the velocity component of changes in physical properties of the object to be measured in the measurement area. 3) The light-receiving means includes a light-receiving device formed by a solid-state image sensor or an optical image pickup tube, and a storage device that separates and stores the image signal from the light-receiving device into signals for each measurement point. Claim 1 or 2 characterized by
Optical measurement method for changes in physical properties described in Section 1.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP29470686A JPS63149567A (en) | 1986-12-12 | 1986-12-12 | Optical measuring method in physical property change |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP29470686A JPS63149567A (en) | 1986-12-12 | 1986-12-12 | Optical measuring method in physical property change |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPS63149567A true JPS63149567A (en) | 1988-06-22 |
Family
ID=17811246
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP29470686A Pending JPS63149567A (en) | 1986-12-12 | 1986-12-12 | Optical measuring method in physical property change |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS63149567A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR100681855B1 (en) | 2004-08-31 | 2007-02-15 | (주) 엠큐브테크놀로지 | A measuring method for obtaining an ultrasonic image, having improved resolution |
| JP2014076000A (en) * | 2012-10-10 | 2014-05-01 | Nikon Corp | Cell motion observation method, image processing program and image processing apparatus |
| JP2019140989A (en) * | 2018-02-21 | 2019-08-29 | ブレインビジョン株式会社 | Cell observation device and method |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS54123073A (en) * | 1978-03-17 | 1979-09-25 | Hitachi Ltd | Sensitivity adjusting method and device for laser flow meter |
-
1986
- 1986-12-12 JP JP29470686A patent/JPS63149567A/en active Pending
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS54123073A (en) * | 1978-03-17 | 1979-09-25 | Hitachi Ltd | Sensitivity adjusting method and device for laser flow meter |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR100681855B1 (en) | 2004-08-31 | 2007-02-15 | (주) 엠큐브테크놀로지 | A measuring method for obtaining an ultrasonic image, having improved resolution |
| JP2014076000A (en) * | 2012-10-10 | 2014-05-01 | Nikon Corp | Cell motion observation method, image processing program and image processing apparatus |
| JP2019140989A (en) * | 2018-02-21 | 2019-08-29 | ブレインビジョン株式会社 | Cell observation device and method |
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