JP2002372491A - Signal display method of organism light-measuring apparatus - Google Patents
Signal display method of organism light-measuring apparatusInfo
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- JP2002372491A JP2002372491A JP2002131352A JP2002131352A JP2002372491A JP 2002372491 A JP2002372491 A JP 2002372491A JP 2002131352 A JP2002131352 A JP 2002131352A JP 2002131352 A JP2002131352 A JP 2002131352A JP 2002372491 A JP2002372491 A JP 2002372491A
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- load
- measurement
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- living body
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- Investigating Or Analysing Materials By Optical Means (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、光を用いて生体内
の情報を計測する生体光計測方法及びその計測信号の表
示方法に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a biological light measurement method for measuring information in a living body using light and a method for displaying a measurement signal.
【０００２】[0002]
【従来の技術】生体組織内の酸素飽和度（動脈系と静脈
系の両者を含む平均的な酸素飽和度）及び血液量を計測
する方法として、ヨブシス等の方法（特開昭５７−１１
５２３２号公報）がある。この方法は、還元ヘモグロビ
ン（Ｈｂ）と酸化ヘモグロビン（ＨｂＯ2）の分光特性
を利用して生体組織内のＨｂ濃度とＨｂＯ2濃度と血液
量（以下、三者を併せて血液動態という）の相対変化量
を計測するものであり、酸素モニタと呼ばれている。こ
の酸素モニタは、計測開始時に計測される反射光強度あ
るいは透過光強度（以下、本明細書では両者を併せて通
過光強度という）を基準値とし、前記基準値と任意時刻
に計測される通過光強度との差から、相対的な血液動態
の変化量を演算して求める方法である。2. Description of the Related Art As a method for measuring oxygen saturation (average oxygen saturation including both arterial and venous systems) and blood volume in living tissue, a method such as Jobis et al.
No. 5232). This method utilizes the spectral characteristics of reduced hemoglobin (Hb) and oxyhemoglobin (HbO 2 ) to determine the relative concentrations of Hb, HbO 2, and blood in living tissue (hereinafter, the three are collectively referred to as hemodynamics). It measures the amount of change and is called an oxygen monitor. This oxygen monitor uses a reflected light intensity or a transmitted light intensity measured at the start of measurement (hereinafter, referred to as a “passed light intensity” in the present specification collectively) as a reference value. This is a method of calculating and calculating a relative change in blood dynamics from a difference from light intensity.
【０００３】[0003]
【発明が解決しようとする課題】生体の機能を解析する
ために、生体に対して負荷をかけた時の血液動態と無負
荷時の血液動態との差から、負荷に起因する血液動態の
変化を計測する場合がある。例えば、生体の脳では、生
体の各機能に対応して働く局所的な部位（以下、機能部
位という）が存在し、生体の任意の機能に対応して機能
部位の血液動態が変化する。この時、任意の機能部位の
血液動態の変化を計測することができれば、脳の機能部
位の位置あるいは働きを調べることができ、医学的に非
常に重要である。また、筋機能を調べる際に、無負荷時
の血液動態と負荷時の血液動態の差より、筋機能を計測
できる可能性もある。SUMMARY OF THE INVENTION In order to analyze the function of a living body, the difference between the blood dynamics when a load is applied to the living body and the blood dynamics when the load is not loaded is used to determine the change in the blood dynamics caused by the load. May be measured. For example, in the brain of a living body, there is a local part (hereinafter, referred to as a functional part) that works in accordance with each function of the living body, and the blood dynamics of the functional part changes in accordance with an arbitrary function of the living body. At this time, if it is possible to measure a change in blood dynamics at an arbitrary functional site, the position or function of the functional site of the brain can be examined, which is very important medically. Also, when examining muscle function, there is a possibility that the muscle function can be measured from the difference between the blood dynamics under no load and the blood dynamics under load.
【０００４】しかし、無負荷時の血液動態は常に一定で
はなく経時的な変化が存在する。具体例として、安静に
仰臥した被検者の側頭部に光を照射し、光照射位置より
３ｃｍ離れた点で通過光強度を計測した際の通過光強度
の時間変化を図１に示す。図１に示されているように、
計測系の揺らぎは０．３％程度にすぎないのに、生体通
過光強度は周期成分を含みながら全体としては不規則に
大きく変動している。この通過光強度の揺らぎは、生体
中の血液動態の変化に由来するものである。[0004] However, the hemodynamics under no load is not always constant, and there is a change over time. As a specific example, FIG. 1 shows a temporal change in transmitted light intensity when light is applied to the temporal region of a subject who is supine at rest and the transmitted light intensity is measured at a point 3 cm away from the light irradiation position. As shown in FIG.
Although the fluctuation of the measurement system is only about 0.3%, the intensity of the light passing through the living body fluctuates greatly irregularly as a whole while including a periodic component. The fluctuation of the transmitted light intensity is caused by a change in blood dynamics in a living body.
【０００５】この様に被検者が安静にしていても、通過
光強度信号に不規則な信号変化が表れるため、計測開始
時の通過光強度を基準値として処理をすると、負荷に起
因する血液動態の変化を計測信号から分離することは困
難である。さらに、このことが原因となり、表示装置に
表示される計測信号あるいは計測信号から演算される血
液動態の時間変化が、生体自身のもつ揺らぎから来る変
動であるのか負荷を加えたことによる変動であるのかを
観察者が判断することができない。従って、従来技術に
よると、被検者を安静にし、信号が安定するまで長時間
待たなければ計測ができなかった。本発明は、従来技術
のこれらの問題を解決するものである。As described above, even if the subject is at rest, an irregular signal change appears in the transmitted light intensity signal. Therefore, if the processing is performed using the transmitted light intensity at the start of the measurement as a reference value, the blood caused by the load is reduced. It is difficult to separate dynamic changes from the measurement signal. Further, due to this, the measurement signal displayed on the display device or the temporal change of the blood dynamics calculated from the measurement signal is a fluctuation caused by the fluctuation of the living body itself or a fluctuation caused by applying a load. The observer cannot judge whether it is. Therefore, according to the prior art, measurement cannot be performed without resting the subject and waiting for a long time until the signal is stabilized. The present invention solves these problems of the prior art.
【０００６】[0006]
【課題を解決するための手段】負荷に起因する血液動態
の変化を計測する場合、生体に負荷を印加しない時間
（無負荷時間）と生体に負荷を印加する時間（負荷時
間）を交互に与えて計測を行なう。ここで、生体光計測
装置で計測される信号（計測信号）をＳm(ｔ)、無負荷
時の血液動態の変化に起因する信号（無負荷信号）をＳ
tr(ｔ)、加負荷時の血液動態の変化に起因する信号（負
荷信号）をＳl(ｔ)とすると、計測信号Ｓm(ｔ)は次の
（１）式で表わされる。ここでｔは計測時間である。 Ｓm(ｔ)＝Ｓtr(ｔ)＋Ｓl(ｔ) （１）When measuring a change in blood dynamics due to a load, a time during which no load is applied to the living body (no load time) and a time during which a load is applied to the living body (load time) are alternately given. Perform measurement. Here, a signal (measurement signal) measured by the biological optical measurement device is S m (t), and a signal (unload signal) caused by a change in blood dynamics when no load is applied is S m (t).
Assuming that tr (t) and a signal (load signal) caused by a change in blood dynamics during loading are S l (t), the measurement signal S m (t) is expressed by the following equation (1). Here, t is a measurement time. S m (t) = S tr (t) + S l (t) (1)
【０００７】本発明においては、計測信号Ｓm(ｔ)よ
り、無負荷時間における信号を抽出して無負荷信号を表
わす関数Ｓtr(ｔ)（予測無負荷信号）を予測し、計測信
号Ｓm(ｔ)と予測無負荷信号Ｓtr(ｔ)の差から負荷信号
Ｓl(ｔ)を求める。さらに、求められた計測信号と予測
した無負荷信号を同時に表示することにより、計測信号
の変動が負荷による変動であるのか、無負荷時の生体由
来の揺らぎから来るものであるかの判断を容易にする。In the present invention, a signal during no-load time is extracted from the measurement signal S m (t), and a function S tr (t) (predicted no-load signal) representing the no-load signal is predicted. The load signal S l (t) is obtained from the difference between m (t) and the predicted no-load signal S tr (t). Furthermore, by displaying the measured signal and the predicted no-load signal at the same time, it is easy to determine whether the fluctuation of the measurement signal is due to the load or the fluctuation from the living body at the time of no load. To
【０００８】関数Ｓtr(ｔ)の決定は、不定係数を有する
任意関数をキーボード等から計算機に入力し、その関数
が無負荷時の信号に最適にフィットするように最小二乗
法等で不定係数を決定することにより行うことができ
る。また、負荷信号Ｓl(ｔ)は生体から負荷を除去して
も直ちにゼロにはならないため、負荷時間に続いて所定
の緩和時間を設定し、この緩和時間を含まない無負荷時
間の計測信号を用いて関数Ｓtr(ｔ)を決定するようにす
れば、より高精度に関数Ｓtr(ｔ)を決定することができ
る。The function S tr (t) is determined by inputting an arbitrary function having an indefinite coefficient from a keyboard or the like to a computer, and applying an indefinite coefficient by a least square method or the like so that the function fits optimally to a signal under no load. Can be determined. Further, since the load signal S l (t) does not immediately become zero even when the load is removed from the living body, a predetermined relaxation time is set following the load time, and the measurement signal of the no-load time not including the relaxation time is set. if to determine the function S tr (t) with, it is possible to determine the function S tr (t) more accurately.
【０００９】前記関数Ｓtr(ｔ)は、複数の負荷時間、例
えば全計測時間を１つの関数でカバーするように決定す
ることもできるし、各負荷時間のみをカバーするように
個々の負荷時間毎に決定することもできる。個々の負荷
時間の前後の計測信号Ｓm(ｔ)を用いて各負荷時間に対
して関数Ｓtr(ｔ)を求める方法によると高い予測精度が
得られる。The function S tr (t) can be determined so that a plurality of load times, for example, the entire measurement time is covered by one function, or individual load times are covered so as to cover only each load time. It can be determined every time. According to the method of obtaining the function S tr (t) for each load time using the measurement signal S m (t) before and after each load time, high prediction accuracy can be obtained.
【００１０】[0010]
【作用】従来技術によると、被検者を安静にし信号が安
定するまで待たなければ計測を行うことができなかった
が、本発明の計測方法によると信号の安定を待たずに計
測が可能となる。また、計測信号から揺らぎを除去する
ことができるので信号の精度を高めることができる。According to the prior art, measurement cannot be performed without resting the subject and waiting for the signal to stabilize. However, according to the measurement method of the present invention, measurement can be performed without waiting for signal stability. Become. In addition, since the fluctuation can be removed from the measurement signal, the accuracy of the signal can be improved.
【００１１】本発明の表示方法によると、負荷と計測信
号との相関が分かりやすくなり、計測信号の変動が負荷
を印加したことによる変動であるのか、生体由来の揺ら
ぎによる変動であるのかを容易に判断することができる
ようになる。According to the display method of the present invention, the correlation between the load and the measurement signal can be easily understood, and it is easy to determine whether the fluctuation of the measurement signal is the fluctuation due to the application of the load or the fluctuation due to the biological origin. Will be able to judge.
【００１２】[0012]
【実施例】図２に、光計測装置の装置構成例を概念的に
示す。本実施例で説明する信号例は、図２に概念を示す
光計測装置によるものである。光源３ａ，３ｂから発す
る異なる波長の光は、発振器２ａ，２ｂによって異なる
周波数で強度変調され、光ファイバーを用いて被検者頭
部８の１点に頭皮上から照射されている。さらに、頭皮
上で照射位置より３ｃｍはなれた位置に別の光ファイバ
ーの入射端を配置して通過光を集光し、検出器４で通過
光強度を検出し、ロックインアンプ５ａと５ｂで各光源
波長に対応する通過光強度に分離し、各波長毎の通過光
強度をアナログ−デジタル変換器６でアナログ−デジタ
ル変換した後に、計算機７で信号の記録及び演算が行わ
れ、信号や演算結果が表示装置１に表示される。計算機
７に接続されたキーボード等の入力装置２５は、後述す
るパラメータ等の入力に用いられる。図２では、光源３
ａ及び３ｂからの光を別々の光ファイバーで照射点に導
いているが、１本の光ファイバーで照射点に導くことも
できる。FIG. 2 conceptually shows a configuration example of an optical measuring device. The signal example described in the present embodiment is based on the optical measurement device whose concept is shown in FIG. Light of different wavelengths emitted from the light sources 3a and 3b is intensity-modulated at different frequencies by the oscillators 2a and 2b, and is radiated to one point of the subject's head 8 from above the scalp using an optical fiber. Further, an incident end of another optical fiber is arranged at a position 3 cm away from the irradiation position on the scalp to collect the passing light, the intensity of the passing light is detected by the detector 4, and each light source is detected by the lock-in amplifiers 5a and 5b. After being separated into transmitted light intensities corresponding to the wavelengths, and the transmitted light intensity for each wavelength is converted from analog to digital by the analog-to-digital converter 6, signal recording and calculation are performed by the computer 7, and the signals and calculation results are obtained. It is displayed on the display device 1. An input device 25 such as a keyboard connected to the computer 7 is used for inputting parameters and the like described later. In FIG. 2, the light source 3
Although the lights from a and 3b are guided to the irradiation point by separate optical fibers, they can be guided to the irradiation point by a single optical fiber.
【００１３】図３は、計測信号と予測無負荷信号の表示
例である。光源３ａに対応する計測信号１０ａと光源３
ｂに対応する計測信号１０ｂ、及び各計測信号から計算
された（計算方法は後述）予測無負荷信号１１ａと１１
ｂを、表示装置１に表示されたウィンドウ９内に表示す
る。表示されているグラフの横軸は計測時間を表わし、
縦軸は生体光計測装置により計測された通過光強度を表
わす計測信号の相対値である。FIG. 3 is a display example of a measurement signal and a predicted no-load signal. Measurement signal 10a corresponding to light source 3a and light source 3
b, and the predicted no-load signals 11a and 11 calculated from the measurement signals 10b and the respective measurement signals (the calculation method will be described later).
b is displayed in the window 9 displayed on the display device 1. The horizontal axis of the displayed graph represents the measurement time,
The vertical axis is a relative value of a measurement signal representing the intensity of transmitted light measured by the biological light measurement device.
【００１４】被検者に対して負荷を印加した場合には、
負荷印加開始時刻を表わす負荷開始マーク１２と負荷印
加終了時刻を表わす負荷終了マーク１３を直線で表示す
る。本実施例では、右手の運動を支配する大脳皮質領域
を頭皮上から頭蓋骨を通して計測しており、負荷として
右手あるいは左手の運動を与えている（負荷１及び負荷
３は右手運動、負荷２及び負荷４は左手運動）。図３に
は計測時間の全信号が表示されているが、任意の時間間
隔（例えば、負荷時間の前後を含む時間間隔）のみを表
示することも容易である。また、予測無負荷信号１１
ａ，１１ｂをそれまでの経時変動の延長線上で任意の時
間先まで表示することにより、計測中に計測信号１０
ａ，１０ｂと予測無負荷信号１１ａ，１１ｂを実時間で
同時に表示することも可能である。この様に計測信号１
０ａと１０ｂと予測無負荷信号１１ａと１１ｂを同時に
表示することで、生体中に血液動態の変化が生じた時
に、観察者が判断することが容易になる。なお、この先
追いして実時間で表示した予測無負荷信号は、予測無負
荷信号の計算が確定した段階で表示し直すようにすると
よい。When a load is applied to the subject,
A load start mark 12 indicating a load application start time and a load end mark 13 indicating a load application end time are displayed as straight lines. In the present embodiment, the cerebral cortex region which controls right hand movement is measured from above the scalp through the skull, and right or left hand movement is given as a load (load 1 and load 3 are right hand movement, load 2 and load 4 is left hand exercise). Although all signals of the measurement time are displayed in FIG. 3, it is easy to display only an arbitrary time interval (for example, a time interval including before and after the load time). Also, the predicted no-load signal 11
By displaying a and 11b up to an arbitrary time ahead on the extension of the time-dependent fluctuation, the measurement signal 10
a, 10b and the predicted no-load signals 11a, 11b can be simultaneously displayed in real time. Thus, measurement signal 1
By displaying 0a and 10b and the predicted no-load signals 11a and 11b at the same time, it becomes easier for the observer to determine when a change in blood dynamics occurs in the living body. It should be noted that the predicted no-load signal displayed in real time ahead of this may be displayed again when the calculation of the predicted no-load signal is determined.
【００１５】予測無負荷信号１１ａ，１１ｂは、計測信
号１０ａ，１０ｂから、負荷を与えた時間（負荷時間）
及び負荷を取り除いたあと信号が元に戻るまでの時間
（緩和時間）における信号を除き、残った期間の信号に
任意の関数を最小二乗法を用いてフィッティングするこ
とで求める。ここで、任意の関数と緩和時間は負荷の種
類や計測場所によって異なるため、計測の目的等に合わ
せて入力装置２５から入力する。本実施例では、任意関
数を５次の多項式、緩和時間を３０秒として処理してい
る。また、信号の表示は、観察者が見やすいように信号
毎に色あるいは線種を変えることも可能である。The predicted no-load signals 11a and 11b are calculated based on the measured signals 10a and 10b based on the load application time (load time).
The signal is obtained by fitting an arbitrary function to the signal in the remaining period using the least squares method, excluding the signal at the time (relaxation time) until the signal returns to the original state after removing the load. Here, since the arbitrary function and the relaxation time vary depending on the type of load and the measurement place, they are input from the input device 25 in accordance with the purpose of measurement and the like. In this embodiment, the arbitrary function is processed with a fifth-order polynomial and the relaxation time is set to 30 seconds. In addition, the display of the signal can be changed in color or line type for each signal so that the observer can easily see the signal.
【００１６】図４は、計測信号と予測無負荷信号の差分
信号の表示例であり、図３中の計測信号１０ａ及び１０
ｂと予測無負荷信号１１ａ及び１１ｂの差分を計算した
ものである差分信号１４ａ及び１４ｂの波形を、表示装
置１上に表示されたウィンドウ９内に表示している。表
示されているグラフの横軸は計測時間を表わし、縦軸は
相対的な差分信号強度を表わしている。さらに、被検者
に対して負荷を印加した場合には、負荷印加開始時刻を
表わす負荷開始マーク１２と負荷印加終了時刻を表わす
負荷終了マーク１３を直線で表示する。また、本グラフ
は０を中心としたグラフとなるので基線１５を表示す
る。FIG. 4 is a display example of a difference signal between the measurement signal and the predicted no-load signal, and shows the measurement signals 10a and 10a in FIG.
The waveforms of the difference signals 14a and 14b, which are obtained by calculating the difference between b and the predicted no-load signals 11a and 11b, are displayed in the window 9 displayed on the display device 1. The horizontal axis of the displayed graph represents the measurement time, and the vertical axis represents the relative difference signal strength. Further, when a load is applied to the subject, a load start mark 12 indicating a load application start time and a load end mark 13 indicating a load application end time are displayed in a straight line. Further, since this graph is a graph centered on 0, a base line 15 is displayed.
【００１７】本実施例では、波形１４ａ，１４ｂを光源
波長毎に異なる座標軸上に表示しているが、同一座標軸
上に重ねて表示することも可能である。また、表示に
は、観察者が見やすいように色あるいは線種を変えて表
示することも可能である。図５は、負荷印加によるＨｂ
Ｏ2 とＨｂの濃度の相対変化量（以下、それぞれΔＣox
y，ΔＣdeoxyとする）を表わすグラフの表示例である。
図３中の計測信号１０ａ及び１０ｂと予測無負荷信号１
１ａ及び１１ｂから計算される（計算方法は後述）ΔＣ
oxy信号１６ａとΔＣdeoxy信号１６ｂの波形を、表示装
置１上に表示されたウィンドウ９内に表示している。表
示されているグラフの横軸は計測時間を表わし、縦軸は
ΔＣoxyとΔＣdeoxyの値を表わしている。さらに、負荷
開始マーク１２、負荷終了マーク１３、及び基線１５も
表示する。本実施例では、計測時間の全区間が表示され
ているが、任意の時間間隔（例えば、負荷時間の前後を
含む期間）のみを表示することも可能である。また、こ
こでは波形１６ａ，１６ｂを異なる座標軸に別々に表示
したが、同一座標軸上に重ねて表示しても構わない。さ
らに、各信号の色もしくは各信号の線種を変えて表示す
ることも可能で、例えばΔＣoxy信号１６ａを赤系統の
色で表示し、また、ΔＣdeoxy信号１６ｂを緑系統の色
で表示すれば、観察者も直感的に理解しやすい。本発明
の計測方法及び表示方法によると、負荷と計測信号との
相関が分かりやすく、計測信号から揺らぎが除去されて
いるので信号の精度が高い。In this embodiment, the waveforms 14a and 14b are displayed on different coordinate axes for each light source wavelength, but may be displayed on the same coordinate axis in a superimposed manner. In addition, it is also possible to change the color or line type so that the observer can easily see it. FIG.
The relative change in the concentration of O 2 and Hb (hereinafter ΔC ox , respectively)
y , ΔC deoxy ).
The measurement signals 10a and 10b and the predicted no-load signal 1 in FIG.
ΔC calculated from 1a and 11b (calculation method will be described later)
The waveforms of the oxy signal 16a and the ΔC deoxy signal 16b are displayed in the window 9 displayed on the display device 1. The horizontal axis of the displayed graph represents the measurement time, and the vertical axis represents the values of ΔC oxy and ΔC deoxy . Further, a load start mark 12, a load end mark 13, and a base line 15 are also displayed. In the present embodiment, all sections of the measurement time are displayed, but it is also possible to display only an arbitrary time interval (for example, a period including before and after the load time). Although the waveforms 16a and 16b are separately displayed on different coordinate axes here, they may be displayed on the same coordinate axis so as to overlap. Further, it is also possible to change the color of each signal or the line type of each signal to be displayed. For example, the ΔC oxy signal 16a is displayed in a red-based color, and the ΔC deoxy signal 16b is displayed in a green-based color. This makes it easy for the observer to understand intuitively. According to the measurement method and the display method of the present invention, the correlation between the load and the measurement signal is easily understood, and the fluctuation of the measurement signal is eliminated, so that the signal accuracy is high.
【００１８】図３に表示される二波長の計測信号１０
ａ，１０ｂと予測無負荷信号１１ａ，１１ｂから、Ｈｂ
Ｏ2 とＨｂの濃度の負荷印加による相対変化量を以下の
方法で求める。波長λにおける予測無負荷信号Ｓtr(λ,
ｔ)と光源強度Ｉ0(λ)の関係は、生体中での光減衰を散
乱と吸収に分離することで、以下の式（２）で示され
る。 −Ｌｎ｛Ｓtr(λ,ｔ)／Ｉ0(λ)｝ ＝εoxy(λ)・Ｃoxy(ｔ)・ｄ＋εdeoxy(λ)・Ｃdeoxy(ｔ)・ｄ ＋Ａ(λ)＋Ｓ(λ) （２）The two-wavelength measurement signal 10 shown in FIG.
a, 10b and the predicted no-load signals 11a, 11b, Hb
The relative change in the O 2 and Hb concentrations due to the application of the load is determined by the following method. The predicted no-load signal S tr (λ,
The relationship between t) and the light source intensity I 0 (λ) is expressed by the following equation (2) by separating light attenuation in a living body into scattering and absorption. −Ln {S tr (λ, t) / I 0 (λ)} = ε oxy (λ) · C oxy (t) · d + ε deoxy (λ) · C deoxy (t) · d + A (λ) + S (λ ) (2)
【００１９】ここで、εoxy(λ)は波長λにおける酸化
ヘモグロビンの吸光係数、εdeoxy(λ)は波長λにおけ
る還元ヘモグロビンの吸光係数、Ａ(λ)は波長λにおけ
るヘモグロビン以外による吸収による減衰、Ｓ(λ)は波
長λにおける散乱による減衰、Ｃoxy(ｔ)は計測時間ｔ
における酸化ヘモグロビン濃度、Ｃdeoxy(ｔ)は計測時
間ｔにおける還元ヘモグロビン濃度、ｄは生体内での注
目領域における実効的光路長を表す。Here, ε oxy (λ) is the extinction coefficient of oxyhemoglobin at wavelength λ, ε deoxy (λ) is the extinction coefficient of reduced hemoglobin at wavelength λ, and A (λ) is the attenuation due to absorption other than hemoglobin at wavelength λ. , S (λ) is the attenuation due to scattering at wavelength λ, and C oxy (t) is the measurement time t
, The oxygenated hemoglobin concentration, C deoxy (t) represents the reduced hemoglobin concentration at the measurement time t, and d represents the effective optical path length in the region of interest in the living body.
【００２０】また、計測信号Ｓm(λ,ｔ)と光源強度Ｉ
0(λ)の関係は（３）式で示される。 −Ｌｎ｛Ｓm(λ,ｔ)／Ｉ0(λ)｝ ＝εoxy(λ)・｛Ｃoxy(ｔ)＋Ｃ'oxy(ｔ)＋Ｎoxy(ｔ)｝・ｄ ＋εdeoxy(λ)・[Ｃdeoxy(ｔ)＋Ｃ'deoxy(ｔ)＋Ｎdeoxy(ｔ)]・ｄ ＋Ａ'(λ)＋Ｓ'(λ) （３）The measurement signal S m (λ, t) and the light source intensity I
The relationship of 0 (λ) is shown by equation (3). −Ln {S m (λ, t) / I 0 (λ)} = ε oxy (λ) · {C oxy (t) + C ′ oxy (t) + N oxy (t)} · d + ε deoxy (λ) · [C deoxy (t) + C ′ deoxy (t) + N deoxy (t)] · d + A ′ (λ) + S ′ (λ) (3)
【００２１】ここで、Ｃ'oxy(ｔ)は計測時間ｔにおける
負荷印加による酸化ヘモグロビン濃度の変化、Ｃ'deoxy
(ｔ)は計測時間ｔにおける負荷印加による還元ヘモグロ
ビン濃度の変化、Ｎoxy(ｔ)は雑音もしくは計測時間ｔ
における酸化ヘモグロビン濃度の高周波揺らぎ、Ｎ
deoxy(ｔ)は雑音もしくは計測時間ｔにおける還元ヘモ
グロビン濃度の高周波揺らぎを表す。Here, C ′ oxy (t) is a change in oxyhemoglobin concentration due to the application of a load at the measurement time t, and C ′ deoxy
(t) is the change in the reduced hemoglobin concentration due to the application of the load at the measurement time t, and N oxy (t) is the noise or the measurement time t.
Frequency fluctuation of oxygenated hemoglobin concentration at
deoxy (t) represents noise or high-frequency fluctuation of the reduced hemoglobin concentration at the measurement time t.
【００２２】Ａ(λ)及びＳ(λ)が負荷印加及び非印加の
状態で変化しないとすれば、すなわち、負荷により生じ
る計測信号変化は酸化及び還元ヘモグロビン濃度の変化
のみによるとすれば、（２）及び（３）式の差分は以下
の（４）式で表される。 Ｌｎ｛Ｓtr(λ,ｔ)／Ｓm(λ,ｔ)｝ ＝εoxy(λ)｛Ｃ'oxy(ｔ) ＋Ｎoxy(ｔ)｝ｄ ＋εdeoxy(λ)｛Ｃ'deoxy(ｔ)＋Ｎdeoxy(ｔ)｝ｄ （４）Assuming that A (λ) and S (λ) do not change with and without the load applied, that is, if the change in the measurement signal caused by the load is only due to the change in the oxidized and reduced hemoglobin concentrations, The difference between the expressions (2) and (3) is expressed by the following expression (4). Ln {S tr (λ, t ) / S m (λ, t)} = ε oxy (λ) {C 'oxy (t) + N oxy (t)} d + ε deoxy (λ) {C' deoxy (t) + N deoxy (t)｝ d (4)
【００２３】ここで、負荷による酸化ヘモグロビン濃度
及び還元ヘモグロビン濃度の相対変化ΔＣoxy及びΔＣ
deoxyを以下の式で定義する。 ΔＣoxy(ｔ)＝｛Ｃ'oxy(ｔ)＋Ｎoxy(ｔ)｝ｄ ΔＣdeoxy(ｔ) ＝｛Ｃ'deoxy(ｔ)＋Ｎdeoxy(ｔ)｝ｄ （５）Here, relative changes ΔC oxy and ΔC of the oxyhemoglobin concentration and the reduced hemoglobin concentration due to the load.
Deoxy is defined by the following formula. ΔC oxy (t) = ｛C ′ oxy (t) + N oxy (t)｝ d ΔC deoxy (t) = ｛C ′ deoxy (t) + N deoxy (t)｝ d (5)
【００２４】ここで、普通ｄを特定することは困難であ
るため、これらの濃度変化量の次元は濃度と距離ｄの積
となっている。しかし、（５）式でｄはΔＣoxyとΔＣ
deoxyに同様に作用するため、（５）式を各ヘモグロビ
ン濃度の相対変化量とする。計測に二波長λ1、λ2を用
いると、各波長毎の予測無負荷信号Ｓtr(λ1,ｔ)，Ｓtr
(λ2,ｔ)及び計測信号Ｓm(λ1,ｔ)，Ｓm(λ2,ｔ)によ
り、（４）式からΔＣoxy(ｔ)及びΔＣdeoxy(ｔ)に対す
る二元連立方程式が得られ、それを解くことによりΔＣ
oxy(ｔ)及びΔＣdeoxy(ｔ)が求まる。さらに、負荷時間
及び緩和時間以外においてはＣ'oxy(ｔ)＝０，Ｃ'deoxy
(ｔ)＝０とおけるので、負荷時間及び緩和時間以外の時
間におけるΔＣoxy(ｔ)及びΔＣdeoxy(ｔ)は、雑音もし
くは酸化ヘモグロビン濃度及び還元ヘモグロビン濃度の
高周波揺らぎを表わしていることになる。Here, since it is usually difficult to specify d, the dimension of the density change amount is the product of the density and the distance d. However, in equation (5), d is ΔC oxy and ΔC
Equation (5) is used as a relative change amount of each hemoglobin concentration because it acts on deoxy similarly. If two wavelengths λ 1 and λ 2 are used for measurement, the predicted no-load signals S tr (λ 1 , t) and S tr for each wavelength
Based on (λ 2 , t) and the measurement signals S m (λ 1 , t) and S m (λ 2 , t), a binary simultaneous equation for ΔC oxy (t) and ΔC deoxy (t) is obtained from the equation (4). And solving it gives ΔC
oxy (t) and ΔC deoxy (t) are obtained. Furthermore, C ′ oxy (t) = 0 and C ′ deoxy except for the load time and the relaxation time.
Since (t) = 0, ΔC oxy (t) and ΔC deoxy (t) at times other than the loading time and the relaxation time represent noise or high-frequency fluctuations of the oxyhemoglobin concentration and the reduced hemoglobin concentration. .
【００２５】図６は、予測無負荷信号の精度を上げるた
めに、負荷印加毎に無負荷信号の予測をする場合の時間
定義を表わしている。図６のグラフは横軸を計測時間と
し、縦軸を通過光強度として、計測信号１０と求めた予
測無負荷信号１１を表わしている。ここで、Ｔ1を負荷
前予測時間、Ｔ2を負荷後予測時間、Ｔtを負荷時間すな
わち負荷を印加している時間、Ｔrを緩和時間すなわち
負荷印加の影響が残っている時間とする。これらの時間
は、計測位置や計測対象によって変わるため、パラメー
タとして入力する。本図の予測無負荷信号１１は、Ｔ1
＝３０秒，Ｔ2＝３０秒，Ｔr＝３０秒として、負荷前予
測時間Ｔ1と負荷後予測時間Ｔ2の計測信号から最小二乗
法で求められた。また、予測無負荷信号１１を表わす任
意関数として５次式を入力した。FIG. 6 shows a time definition when a no-load signal is predicted every time a load is applied in order to improve the accuracy of the predicted no-load signal. In the graph of FIG. 6, the horizontal axis represents the measurement time, and the vertical axis represents the passing light intensity, and represents the measurement signal 10 and the calculated predicted no-load signal 11. Here, T 1 is a predicted time before load, T 2 is a predicted time after load, T t is a load time, that is, a time during which a load is applied, and T r is a relaxation time, that is, a time during which the effect of the load application remains. . Since these times vary depending on the measurement position and the measurement target, they are input as parameters. Predicted no-load signal 11 of the figure, T 1
= 30 seconds, T 2 = 30 seconds, and T r = 30 seconds, and were obtained by the least squares method from the measurement signals of the pre-load prediction time T 1 and the post-load prediction time T 2 . In addition, a quintic equation was input as an arbitrary function representing the predicted no-load signal 11.
【００２６】図７は、各負荷時間毎のΔＣoxy負荷時間
積分値１７ａ，ΔＣdeoxy負荷時間積分値１７ｂの表示
例である。図５中のΔＣoxy信号１４ａとΔＣdeoxy信号
１４ｂを負荷時間毎に時間積分してΔＣoxy負荷時間積
分値１７ａとΔＣdeoxy負荷時間積分値１７ｂを求め、
表示装置１上に表示されたウィンドウ９内に、負荷番号
毎に立体棒グラフで表示している。ここで、横軸は負荷
番号を表わし、縦軸はΔＣ oxy負荷時間積分値及びΔＣ
deoxy負荷時間積分値を表わしている。ここで、ΔＣ oxy
負荷時間平均値及びΔＣdeoxy負荷時間平均値を表示す
ることも可能である。また、表示には、観察者が見やす
いように色を変えて表示することも可能である。FIG. 7 shows ΔC for each load time.oxyLoad time
Integral value 17a, ΔCdeoxyDisplay of load time integral 17b
It is an example. ΔC in FIG.oxySignal 14a and ΔCdeoxysignal
14b is integrated over time for each load time to obtain ΔCoxyLoad time product
Minute value 17a and ΔCdeoxyThe load time integral value 17b is obtained,
In the window 9 displayed on the display device 1, the load number is displayed.
Each is displayed as a three-dimensional bar graph. Where the horizontal axis is the load
And the vertical axis is ΔC oxyLoad time integral and ΔC
deoxyIt represents the load time integration value. Where ΔC oxy
Average load time and ΔCdeoxyDisplays the average load time
It is also possible. In addition, the display is easy for the observer to see.
It is also possible to display in different colors.
【００２７】図８は、生体光計測装置を用いて複数の計
測位置で計測した場合の表示例を示す。ここでは、計測
部位を頭部とし、頭部上に４点計測位置を設定した場合
の例を説明する。本表示例では、被検者の計測部位像１
８と、設定した計測位置を表わす計測位置マーク１９ａ
〜１９ｄと、各計測位置に対応しグラフ２１ａ〜２１ｄ
と、計測位置とグラフの対応関係を示す指示線２０ａ〜
２０ｄとを、表示装置１上に表示したウィンドウ９上に
表示する。ここで、計測部位像１８としては、頭部モデ
ル図あるいはＭＲＩ装置で代表されるような画像診断装
置で撮影された被検者本人の計測部位断層画像あるいは
計測部位３次元画像を用いることができる。FIG. 8 shows a display example in the case where measurement is performed at a plurality of measurement positions using the biological light measurement device. Here, an example in which the measurement site is the head and four measurement positions are set on the head will be described. In this display example, the measurement site image 1 of the subject
8 and a measurement position mark 19a representing the set measurement position
To 21d and graphs 21a to 21d corresponding to the respective measurement positions.
And indication lines 20a to 20c indicating the correspondence between measurement positions and graphs
20d is displayed on the window 9 displayed on the display device 1. Here, as the measurement part image 18, a measurement part tomographic image or a measurement part three-dimensional image of the subject himself or herself captured by an image diagnostic apparatus typified by a head model diagram or an MRI apparatus can be used. .
【００２８】[0028]
【発明の効果】計測信号から予測信号を計算すること
で、生体の揺らぎが安定することを待たずに計測が可能
となる。また、計測信号と計算した予測信号を同時に表
示することによって、観察者が計測信号の変化の有無を
容易に判断することができる。By calculating the prediction signal from the measurement signal, the measurement can be performed without waiting for the fluctuation of the living body to stabilize. Also, by simultaneously displaying the measurement signal and the calculated prediction signal, the observer can easily determine whether or not the measurement signal has changed.
【図面の簡単な説明】[Brief description of the drawings]
【図１】生体にある自然にある揺らぎを表わす図。FIG. 1 is a diagram showing a natural fluctuation in a living body.
【図２】生体光計測装置の概念図。FIG. 2 is a conceptual diagram of a biological light measurement device.
【図３】本発明による表示例を示す図。FIG. 3 is a diagram showing a display example according to the present invention.
【図４】本発明による表示例を示す図。FIG. 4 is a diagram showing a display example according to the present invention.
【図５】本発明による表示例を示す図。FIG. 5 is a diagram showing a display example according to the present invention.
【図６】本発明による時間軸定義の説明図。FIG. 6 is an explanatory diagram of a time axis definition according to the present invention.
【図７】本発明による表示例を示す図。FIG. 7 is a diagram showing a display example according to the present invention.
【図８】本発明による表示例を示す図。FIG. 8 is a diagram showing a display example according to the present invention.
１：表示装置、２：発振器、３ａ，３ｂ：光源、４：検
出器、５：ロックインアンプ、６：アナログ−デジタル
変換器、７：計算機、８：被検者、９：ウィンドウ、１
０：計測信号、１１：予測無負荷信号、１２：負荷開始
マーク、１３：負荷終了マーク、１４：差分信号、１
５：基線、１６ａ：ΔＣoxy信号、１６ｂ：ΔＣdeoxy信
号、１７ａ：ΔＣoxy負荷時間積分値、１７ｂ：ΔＣ
deoxy負荷時間積分値、１８：計測部位像、１９：計測
位置マーク、２０：指示線、２１：グラフ、２５：入力
装置1: display device, 2: oscillator, 3a, 3b: light source, 4: detector, 5: lock-in amplifier, 6: analog-digital converter, 7: computer, 8: subject, 9: window, 1
0: measurement signal, 11: predicted no-load signal, 12: load start mark, 13: load end mark, 14: difference signal, 1
5: Base line, 16a: ΔC oxy signal, 16b: ΔC deoxy signal, 17a: ΔC oxy load time integration value, 17b: ΔC
Deoxy load time integration value, 18: measurement site image, 19: measurement position mark, 20: instruction line, 21: graph, 25: input device
─────────────────────────────────────────────────────
────────────────────────────────────────────────── ───
【手続補正書】[Procedure amendment]
【提出日】平成１４年５月２８日（２００２．５．２
８）[Submission Date] May 28, 2002 (2002.5.2)
8)
【手続補正１】[Procedure amendment 1]
【補正対象書類名】明細書[Document name to be amended] Statement
【補正対象項目名】発明の名称[Correction target item name] Name of invention
【補正方法】変更[Correction method] Change
【補正内容】[Correction contents]
【発明の名称】 生体光計測装置の信号表示方法Patent application title: Signal display method for biological optical measurement device
【手続補正２】[Procedure amendment 2]
【補正対象書類名】明細書[Document name to be amended] Statement
【補正対象項目名】特許請求の範囲[Correction target item name] Claims
【補正方法】変更[Correction method] Change
【補正内容】[Correction contents]
【特許請求の範囲】[Claims]
【手続補正３】[Procedure amendment 3]
【補正対象書類名】明細書[Document name to be amended] Statement
【補正対象項目名】０００１[Correction target item name] 0001
【補正方法】変更[Correction method] Change
【補正内容】[Correction contents]
【０００１】[0001]
【発明の属する技術分野】本発明は、光を用いて生体内
の情報を計測する生体光計測装置の計測信号の表示方法
に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method for displaying a measurement signal of a living body light measuring device for measuring information in a living body using light.
───────────────────────────────────────────────────── フロントページの続き (72)発明者 伊藤 嘉敏 東京都国分寺市東恋ヶ窪一丁目280番地 株式会社日立製作所中央研究所内 Ｆターム(参考） 2G059 AA01 AA05 BB12 CC16 EE01 EE11 FF04 GG03 GG06 JJ17 KK01 MM01 MM03 MM09 MM10 PP04 4C038 KK01 KL05 KL07 KM00 KM01 KX01 KX02 ──────────────────────────────────────────────────続 き Continuing on the front page (72) Inventor Yoshitoshi Ito 1-280 Higashi-Koigabo, Kokubunji-shi, Tokyo F-term in Central Research Laboratory, Hitachi, Ltd. (Reference) 2G059 AA01 AA05 BB12 CC16 EE01 EE11 FF04 GG03 GG06 JJ17 KK01 MM01 MM03 MM09 MM10 PP04 4C038 KK01 KL05 KL07 KM00 KM01 KX01 KX02
Claims (17)
印加しない無負荷時間を交互に設けながら生体に光を照
射して生体通過光強度を計測する生体光計測方法におい
て、前記負荷時間に続く緩和時間を設定し、緩和時間を
含まない無負荷時間における計測信号から計測信号に含
まれる生体由来の揺らぎに相当する信号を予測すること
を特徴とする生体光計測方法。1. A biological light measurement method for measuring light intensity passing through a living body by irradiating the living body with light while alternately providing a load time for applying a load to the living body and a no-load time for not applying a load, A biological light measurement method, comprising: setting a subsequent relaxation time, and predicting a signal corresponding to a biological fluctuation included in the measurement signal from a measurement signal during a no-load time that does not include the relaxation time.
定し、各緩和時間の直後に負荷後予測時間を設定し、各
負荷時間毎に負荷前予測時間における計測信号と負荷後
予測時間における計測信号から計測信号に含まれる生体
由来の揺らぎに相当する信号を予測することを特徴とす
る請求項１記載の生体光計測方法。2. A pre-load prediction time is set immediately before each load time, a post-load prediction time is set immediately after each relaxation time, and a measurement signal and a post-load prediction time in the pre-load prediction time are set for each load time. 2. The living body light measurement method according to claim 1, wherein a signal corresponding to the fluctuation derived from the living body included in the measurement signal is predicted from the measurement signal in the step (c).
意関数を設定し、該任意関数が緩和時間を含まない無負
荷時間における計測信号に最適に適合するように最小二
乗法によって前記不定係数を決定し、こうして決定され
た最適適合関数を生体由来の揺らぎに相当する信号とす
ることを特徴とする請求項１又は２記載の生体光計測方
法。3. An arbitrary function having one or a plurality of indefinite coefficients is set, and the indefinite coefficient is determined by a least square method so that the arbitrary function optimally fits a measurement signal in a no-load time that does not include a relaxation time. The biological light measurement method according to claim 1, wherein the method is determined, and the determined optimal fitting function is a signal corresponding to fluctuation derived from a living body.
相当する信号の差分を演算することを特徴とする請求項
１又は２記載の生体光計測方法。4. The living body light measurement method according to claim 1, wherein a difference between the measurement signal and a signal corresponding to the predicted fluctuation derived from the living body is calculated.
号と計測信号の比、光源波長に対する酸化ヘモグロビン
の吸光係数、及び光源波長に対する還元ヘモグロビンの
吸光係数を用い、生体中の酸化ヘモグロビン濃度と還元
ヘモグロビン濃度の和の相対変化量あるいは酸化ヘモグ
ロビン濃度の相対変化量と還元ヘモグロビン濃度の相対
変化量、前記各相対変化量の時間変化、前記各相対変化
量を所定の時間にわたって積算した積算相対変化量、又
は所定の時間間隔における平均相対変化量を演算するこ
とを特徴とする請求項１、２又は３記載の生体光計測方
法。5. The concentration of oxyhemoglobin in a living body and the reduction of oxyhemoglobin in a living body using a predicted ratio of a signal corresponding to fluctuation derived from a living body to a measurement signal, an absorption coefficient of oxyhemoglobin with respect to a light source wavelength, and an absorption coefficient of reduced hemoglobin with respect to a light source wavelength. The relative change amount of the sum of the hemoglobin concentrations or the relative change amount of the oxyhemoglobin concentration and the relative change amount of the reduced hemoglobin concentration, the time change of each of the relative change amounts, and the integrated relative change amount obtained by integrating the relative change amounts over a predetermined time 4. The biological light measurement method according to claim 1, wherein an average relative change amount in a predetermined time interval is calculated.
測し、計測信号あるいは計測信号を演算した信号を表示
装置に表示する生体光計測装置の信号表示方法におい
て、計測信号に含まれる生体由来の揺らぎに相当する信
号を予測し、前記予測した信号を計測信号と共に表示す
ることを特徴とする生体光計測装置の信号表示方法。6. A signal display method of a living body light measuring device for irradiating a living body with light, measuring the intensity of light passing through the living body, and displaying a measurement signal or a signal obtained by calculating the measurement signal on a display device. A signal display method for a biological optical measurement device, comprising predicting a signal corresponding to a fluctuation originating in a living body and displaying the predicted signal together with a measurement signal.
印加しない無負荷時間を交互に設けながら生体に光を照
射して生体通過光強度を計測し、計測信号あるいは計測
信号を演算した信号を表示装置に表示する生体光計測装
置の信号表示方法において、前記無負荷時間における計
測信号から計測信号に含まれる生体由来の揺らぎに相当
する信号を予測し、前記予測した信号を予測無負荷信号
として計測信号と共に表示することを特徴とする生体光
計測装置の信号表示方法。7. A signal obtained by irradiating a living body with light while alternately providing a load time for applying a load to a living body and a no-load time for not applying a load, measuring the intensity of light passing through the living body, and calculating a measurement signal or a measurement signal. In the signal display method of the biological optical measurement device that displays on the display device, the signal corresponding to the fluctuation derived from the living body included in the measurement signal from the measurement signal in the no-load time is predicted, and the predicted signal is a predicted no-load signal. And displaying the signal together with the measurement signal.
印加しない無負荷時間を交互に設けながら生体に光を照
射して生体通過光強度を計測し、計測信号あるいは計測
信号を演算した信号を表示装置に表示する生体光計測装
置の信号表示方法において、前記負荷時間に続く緩和時
間を設定し、緩和時間を含まない前記無負荷時間におけ
る計測信号から計測信号に含まれる生体由来の揺らぎに
相当する信号を予測し、前記予測した信号を予測無負荷
信号として計測信号と共に表示することを特徴とする生
体光計測装置の信号表示方法。8. A signal obtained by irradiating a living body with light while alternately providing a load time for applying a load to a living body and a no-load time for not applying a load, measuring the intensity of light passing through the living body, and calculating a measurement signal or a measurement signal. In the signal display method of the biological light measurement device that displays on the display device, the relaxation time following the load time is set, from the measurement signal in the no-load time that does not include the relaxation time to the fluctuation from the living body included in the measurement signal included in the measurement signal A signal display method for a biological optical measurement device, wherein a corresponding signal is predicted, and the predicted signal is displayed together with a measurement signal as a predicted no-load signal.
定し、各緩和時間の直後に負荷後予測時間を設定し、各
負荷時間毎に負荷前予測時間における計測信号と負荷後
予測時間における計測信号から前記予測無負荷信号を求
めることを特徴とする請求項８記載の生体光計測装置の
信号表示方法。9. A pre-load prediction time is set immediately before each load time, a post-load prediction time is set immediately after each relaxation time, and a measurement signal and a post-load prediction time in the pre-load prediction time are set for each load time. 9. The signal display method for a biological optical measurement device according to claim 8, wherein the predicted no-load signal is obtained from the measurement signal in step (a).
任意関数を設定し、該任意関数が緩和時間を含まない無
負荷時間における計測信号に最適に適合するように最小
二乗法によって前記不定係数を決定し、こうして決定さ
れた最適適合関数を前記生体由来の揺らぎに相当する信
号とすることを特徴とする請求項７、８又は９記載の生
体光計測装置の信号表示方法。10. An arbitrary function having one or a plurality of indefinite coefficients is set, and said indefinite coefficient is determined by a least square method so that the arbitrary function optimally fits a measurement signal in a no-load time that does not include a relaxation time. 10. The signal display method for a biological optical measurement device according to claim 7, wherein the signal is determined, and the determined optimal fitting function is a signal corresponding to the fluctuation derived from the living body.
し、演算結果を表示することを特徴とする請求項７〜１
０のいずれか１項記載の生体光計測装置の信号表示方
法。11. The method according to claim 7, wherein a difference between the measured signal and the predicted no-load signal is calculated, and the calculation result is displayed.
0. The signal display method for a biological optical measurement device according to any one of 0 to 0.
波長に対する酸化ヘモグロビンの吸光係数、及び光源波
長に対する還元ヘモグロビンの吸光係数を用い、生体中
の酸化ヘモグロビン濃度と還元ヘモグロビン濃度の和の
相対変化量あるいは酸化ヘモグロビン濃度の相対変化量
と還元ヘモグロビン濃度の相対変化量を演算し、前記各
相対変化量の時間変化、前記各相対変化量を所定の時間
にわたって積算した積算相対変化量、又は所定の時間間
隔における平均相対変化量を表示することを特徴とする
請求項７〜１１のいずれか１項記載の生体光計測装置の
信号表示方法。12. The relative ratio of the sum of the oxyhemoglobin concentration and the reduced hemoglobin concentration in a living body using the ratio of the predicted no-load signal to the measurement signal, the extinction coefficient of oxyhemoglobin with respect to the light source wavelength, and the extinction coefficient of reduced hemoglobin with respect to the light source wavelength. The relative change amount of the change amount or the oxyhemoglobin concentration and the relative change amount of the reduced hemoglobin concentration are calculated, and the time change of each relative change amount, the integrated relative change amount obtained by integrating the relative change amounts over a predetermined time, or a predetermined amount The signal display method of the biological optical measurement device according to any one of claims 7 to 11, wherein an average relative change amount in the time interval is displayed.
る色あるいは異なる線種を用いて表示することを特徴と
する請求項６〜１２のいずれか１項記載の生体光計測装
置の信号表示方法。13. The method according to claim 6, wherein the display is performed using different colors or different line types for different signals or calculation results.
図形を共に表示することを特徴とする請求項７〜１３の
いずれか１項記載の生体光計測装置の信号表示方法。14. The signal display method for a biological optical measurement device according to claim 7, wherein a figure indicating a start time and an end time of the load time is displayed together.
し、予測無負荷信号は表示されている計測信号より先の
時間まで表示することを特徴とする請求項７〜１４のい
ずれか１項記載の生体光計測装置の信号表示方法。15. The method according to claim 7, wherein the measurement signal is displayed in real time together with the measurement, and the predicted no-load signal is displayed until a time earlier than the displayed measurement signal. Signal display method of the biological light measurement device of the present invention.
を、生体の計測部位を示す図と、計測位置を示す図形
と、計測位置と前記信号との対応を指示する図形ととも
に表示することを特徴とする請求項６〜１５のいずれか
１項記載の生体光計測装置の信号表示方法。16. A method for displaying a plurality of signals for a plurality of measurement positions together with a diagram showing a measurement site of a living body, a figure showing the measurement positions, and a figure designating a correspondence between the measurement positions and the signals. The signal display method of the biological light measurement device according to claim 6.
によって撮影された画像を用いることを特徴とする請求
項１６記載の生体光計測装置の信号表示方法。17. The signal display method for a biological optical measurement device according to claim 16, wherein an image photographed by an image diagnostic device is used as a diagram showing a measurement site.
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2008194453A (en) * | 2007-01-17 | 2008-08-28 | Hitachi Ltd | Optical measuring device for living body |
| JP2009066269A (en) * | 2007-09-14 | 2009-04-02 | Yoshifumi Takada | Apparatus for measuring blood oxygen saturation, method for predicting risk of cardiovascular event, diagnostic apparatus, method for predicting high crp value with high sensitivity |
| JP2011125469A (en) * | 2009-12-17 | 2011-06-30 | Hitachi Ltd | Biological light measuring apparatus and living body measuring method |
-
2002
- 2002-05-07 JP JP2002131352A patent/JP2002372491A/en active Pending
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2008194453A (en) * | 2007-01-17 | 2008-08-28 | Hitachi Ltd | Optical measuring device for living body |
| JP2009066269A (en) * | 2007-09-14 | 2009-04-02 | Yoshifumi Takada | Apparatus for measuring blood oxygen saturation, method for predicting risk of cardiovascular event, diagnostic apparatus, method for predicting high crp value with high sensitivity |
| JP2011125469A (en) * | 2009-12-17 | 2011-06-30 | Hitachi Ltd | Biological light measuring apparatus and living body measuring method |
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