JP2005103316A - Optical measuring apparatus for living body - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To shorten in measuring time by estimating fluctuation generated by an organism and further to make judgement of existence of measurement signal variation easier by simultaneously displaying estimation signals and measurement signals. <P>SOLUTION: This optical measuring apparatus for living body is equipped with a light emitting means for emitting light with an wavelength λ1 and λ2 to the head part of a subject, a light receiving means to detect light reflected by the inside of the subject, and a calculating means to calculate time variation of oxidized and reduced hemoglobin concentration relative variation by a load from the following equations (1), (2) to measure blood kinetics of the brain. LnäS<SB>tr</SB>(λ1, t)/Sm(λ1, t)} = ε<SB>oxy</SB>(λ1)×ΔC<SB>oxy</SB>(t)+ε<SB>deoxy</SB>(λ1)×ΔC<SB>deoxy</SB>(t) -(1). LnäS<SB>tr</SB>(λ2, t)/Sm(λ2, t)} = ε<SB>oxy</SB>(λ2)×ΔC<SB>oxy</SB>(t)+ε<SB>deoxy</SB>(λ2)×ΔC<SB>deoxy</SB>(t) -(2). <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

  The present invention relates to a biological light measurement method for measuring in-vivo information using light.

As a method for measuring oxygen saturation (average oxygen saturation including both arterial and venous systems) and blood volume in living tissue, there is a method such as Jobsis (Patent Document 1). This method uses the spectral characteristics of reduced hemoglobin (Hb) and oxyhemoglobin (HbO ₂ ) to compare the relative Hb concentration, HbO ₂ concentration and blood volume (hereinafter collectively referred to as hemodynamics) in living tissue. It measures the amount of change and is called an oxygen monitor. This oxygen monitor uses the reflected light intensity or transmitted light intensity measured at the start of measurement (hereinafter referred to as the passing light intensity together in this specification) as a reference value, and the reference value and the passage measured at an arbitrary time. This is a method of calculating the relative change in hemodynamics from the difference from the light intensity.

JP 57-115232 A

  In order to analyze the function of a living body, a change in hemodynamics caused by the load may be measured from a difference between a hemodynamic state when a load is applied to the living body and a non-loaded blood dynamic state. For example, in the brain of a living body, there exists a local site (hereinafter referred to as a functional site) that works corresponding to each function of the living body, and the hemodynamics of the functional site changes corresponding to an arbitrary function of the living body. At this time, if the change in hemodynamics of any functional part can be measured, the position or function of the functional part of the brain can be examined, which is very important medically. In addition, when examining muscle function, there is a possibility that muscle function can be measured from the difference between hemodynamics at no load and hemodynamics at load.

  However, the hemodynamics at no load is not always constant and changes over time. As a specific example, FIG. 1 shows a temporal change of the passing light intensity when light is irradiated on the temporal region of a subject who is lying on his back and the passing light intensity is measured at a point 3 cm away from the light irradiation position. As shown in FIG. 1, although the fluctuation of the measurement system is only about 0.3%, the intensity of light passing through the living body largely and irregularly fluctuates as a whole while including a periodic component. This fluctuation of the transmitted light intensity is derived from a change in blood dynamics in the living body.

  Even if the subject is resting in this way, irregular signal changes appear in the passing light intensity signal, so if the passing light intensity at the start of measurement is used as a reference value, the change in blood dynamics due to the load Is difficult to separate from the measurement signal. Furthermore, due to this, the measurement signal displayed on the display device or the time change of the hemodynamics calculated from the measurement signal is a variation resulting from fluctuations of the living body itself or a variation due to the addition of a load. The observer cannot judge whether Therefore, according to the prior art, measurement cannot be performed unless the subject is rested and the signal is stabilized for a long time.

  The present invention solves these problems of the prior art.

When measuring a change in hemodynamics caused by a load, the measurement is performed by alternately giving a time during which no load is applied to the living body (no load time) and a time during which the load is applied to the living body (load time). Here, S _m (t) is a signal (measurement signal) measured by the biological light measurement device, S _tr (t) is a signal resulting from a change in hemodynamics at no load, and S _tr (t) is applied. If the signal (load signal) resulting from the change in hemodynamics is S ₁ (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)

In the present invention, from the measurement signal S _m (t), a signal at no load time is extracted to predict a function S _tr (t) (predicted no load signal) representing the no load signal, and the measurement signal S _m (t ) And the predicted no-load signal S _tr (t), the load signal S _l (t) is obtained. In addition, by displaying the calculated measurement 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 when there is no load. To.

The function S _tr (t) is determined by inputting an arbitrary function having an indefinite coefficient to a computer from a keyboard or the like, and determining the indefinite coefficient by the least square method or the like so that the function optimally fits a signal at no load. Can be done. 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 does not include this relaxation time if to determine the function S _tr (t) with, it is possible to determine the function S _tr (t) more accurately.

The function S _tr (t) can be determined so as to cover a plurality of load times, for example, the entire measurement time, by one function, or determined for each load time so as to cover only each load time. You can also According to the method of obtaining the function S _tr (t) for each load time using the measurement signals S _m (t) before and after each load time, high prediction accuracy can be obtained.

  According to the prior art, measurement cannot be performed unless the subject is rested and waits until the signal is stabilized. However, according to the measurement method of the present invention, measurement can be performed without waiting for signal stabilization. In addition, since the fluctuation can be removed from the measurement signal, the accuracy of the signal can be increased.

  According to the display method of the present invention, the correlation between the load and the measurement signal becomes easy to understand, and it is easily determined whether the fluctuation of the measurement signal is a fluctuation caused by the application of the load or a fluctuation caused by a living body-derived fluctuation. Will be able to.

  FIG. 2 conceptually shows a device configuration example of the optical measurement device. The signal example described in this embodiment is based on the optical measuring device whose concept is shown in FIG. Lights of different wavelengths emitted from the light sources 3a and 3b are intensity-modulated at different frequencies by the oscillators 2a and 2b, and are irradiated onto 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 on the scalp at a position 3 cm away from the irradiation position, the passing light is condensed, the passing light intensity is detected by the detector 4, and each light source is detected by the lock-in amplifiers 5a and 5b. After separating the transmitted light intensity corresponding to the wavelength and converting the transmitted light intensity for each wavelength by the analog-to-digital converter 6, the signal is recorded and calculated by the computer 7. 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 which will be described later. In FIG. 2, the light from the light sources 3a and 3b is guided to the irradiation point by separate optical fibers, but can also be guided to the irradiation point by a single optical fiber.

  FIG. 3 is a display example of the measurement signal and the predicted no-load signal. A window 9 in which a measurement signal 10a corresponding to the light source 3a, a measurement signal 10b corresponding to the light source 3b, and predicted no-load signals 11a and 11b calculated from each measurement signal (calculation method will be described later) are displayed on the display device 1. Display within. The horizontal axis of the displayed graph represents the measurement time, and the vertical axis represents the relative value of the measurement signal representing the intensity of the passing light measured by the biological light measurement device.

  When a load is applied to the subject, a load start mark 12 representing the load application start time and a load end mark 13 representing the load application end time are displayed in a straight line.

  In this embodiment, the cerebral cortex region that controls the right hand movement is measured from the top of the scalp through the skull, and the right hand 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 movement). Although all signals of the measurement time are displayed in FIG. 3, it is easy to display only arbitrary time intervals (for example, time intervals including before and after the load time). In addition, by displaying the predicted no-load signals 11a and 11b up to an arbitrary time ahead on the extension line of the temporal variation so far, the measurement signals 10a and 10b and the predicted no-load signals 11a and 11b can be simultaneously displayed in real time during measurement. It is also possible to display. Thus, by displaying the measurement signals 10a and 10b and the predicted no-load signals 11a and 11b at the same time, it becomes easy for the observer to judge when a change in hemodynamics occurs in the living body. It should be noted that the predicted no-load signal displayed in real time ahead of time is preferably displayed again when the calculation of the predicted no-load signal is confirmed.

  Predicted no-load signals 11a and 11b remained from measurement signals 10a and 10b, except for signals at the time when the load was applied (load time) and the time until the signal returned to the original state after the load was removed (relaxation time). An arbitrary function is fitted to the signal of the period using the least square method. Here, since the arbitrary function and the relaxation time differ depending on the type of load and the measurement location, they are input from the input device 25 in accordance with the purpose of measurement. In this embodiment, the arbitrary function is processed as a fifth-order polynomial and the relaxation time is 30 seconds. In addition, the display of the signal can change the color or line type for each signal so that the viewer can easily see it.

  FIG. 4 is a display example of the difference signal between the measurement signal and the predicted no-load signal. The difference signals 14a and 14b are obtained by calculating the difference between the measurement signals 10a and 10b and the predicted no-load signals 11a and 11b in FIG. Is displayed in a 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 intensity. Further, when a load is applied to the subject, a load start mark 12 representing the load application start time and a load end mark 13 representing the load application end time are displayed in a straight line. Since this graph is a graph centered on 0, the base line 15 is displayed.

In the present embodiment, the waveforms 14a and 14b are displayed on different coordinate axes for each light source wavelength, but can be displayed on the same coordinate axis. In addition, the display can be displayed by changing the color or line type so that the viewer can easily see. FIG. 5 is a display example of a graph showing the relative changes in the concentrations of HbO ₂ and Hb (hereinafter referred to as ΔC _oxy and ΔC _deoxy , respectively) due to load application. A window 9 displayed on the display device 1 shows the waveforms of the ΔC _oxy signal 16a and the ΔC _deoxy signal 16b calculated from the measurement signals 10a and 10b and the predicted no-load signals 11a and 11b in FIG. It is displayed in. 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 arbitrary time intervals (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.

Furthermore, it is also possible to display the signals by changing the color of each signal or the line type of each signal. For example, the ΔC _oxy signal 16a is displayed in a red color, and the ΔC _deoxy signal 16b is displayed in a green color. For example, it is easy for an observer to understand intuitively. According to the measurement method and display method of the present invention, the correlation between the load and the measurement signal is easy to understand, and fluctuations are removed from the measurement signal, so that the accuracy of the signal is high.

From the two-wavelength measurement signals 10a and 10b and the predicted no-load signals 11a and 11b displayed in FIG. 3, the relative change amount due to the load application of the HbO ₂ and Hb concentrations is obtained by the following method. The relationship between the predicted no-load signal S _tr (λ, t) and the light source intensity I ₀ (λ) at the wavelength λ is expressed by the following equation (2) by separating light attenuation in the living body into scattering and absorption. It is.

−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)

Where ε _oxy (λ) is the extinction coefficient of oxygenated hemoglobin at wavelength λ, ε _deoxy (λ) is the extinction coefficient of reduced hemoglobin at wavelength λ, A (λ) is attenuation due to absorption by other than hemoglobin at wavelength λ, S ( λ) is the attenuation due to scattering at wavelength λ, C _oxy (t) is the oxygenated hemoglobin concentration at measurement time t, C _deoxy (t) is the reduced hemoglobin concentration at measurement time t, and d is the effective optical path in the region of interest in the living body. Represents length.

Further, the relationship between the measurement signal S _m (λ, t) and the light source intensity I ₀ (λ) is expressed 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)

Here, C ′ _oxy (t) is a change in oxidized hemoglobin concentration due to load application at measurement time t, C ′ _deoxy (t) is a change in reduced hemoglobin concentration due to load application at measurement time t, and N _oxy (t) is noise. Alternatively, high-frequency fluctuations in the oxygenated hemoglobin concentration at the measurement time t and N _deoxy (t) represent noise or high-frequency fluctuations in the reduced hemoglobin concentration at the measurement time t.

  If A (λ) and S (λ) do not change when the load is applied and not applied, that is, if the change in the measurement signal caused by the load is only due to changes in the oxidized and reduced hemoglobin concentrations, (2) and The difference of (3) Formula is represented by the following (4) Formula.

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)

Here, relative changes ΔC _oxy and ΔC _deoxy of the oxygenated hemoglobin concentration and the reduced hemoglobin concentration due to the load are defined by the following equations.

ΔC _oxy (t) = {C ′ _oxy (t) + N _oxy (t)} d ΔC _deoxy (t)
= { _C'deoxy (t) + _Ndeoxy (t)} d (5)

Here, since it is usually difficult to specify d, the dimension of these density change amounts is a product of density and distance d. However, since d acts in the same way on ΔC _oxy and ΔC _deoxy in equation (5), equation (5) is used as the relative change amount of each hemoglobin concentration. When the two wavelengths λ ₁ and λ ₂ are used for measurement, the predicted no-load signal S _tr (λ ₁ , t), S _tr (λ ₂ , t) and the measurement signal S _m (λ ₁ , t) for each wavelength, From S _m (λ ₂ , t), a binary simultaneous equation for ΔC _oxy (t) and ΔC _deoxy (t) is obtained from the equation (4), and by solving it, ΔC _oxy (t) and ΔC _deoxy (t ) Is obtained. Further, since C ′ _oxy (t) = 0 and C ′ _deoxy (t) = 0 except for the load time and the relaxation time, ΔC _oxy (t) and ΔC _deoxy (t) at a time other than the load time and the relaxation time. ) Represents high-frequency fluctuations in noise or oxyhemoglobin concentration and reduced hemoglobin concentration.

FIG. 6 shows a time definition in the case where the no-load signal is predicted every time the load is applied in order to increase the accuracy of the predicted no-load signal. The graph in FIG. 6 represents the measurement signal 10 and the calculated predicted no-load signal 11 with the horizontal axis as the measurement time and the vertical axis as the passing light intensity. Here, T ₁ is the pre-load prediction time, T ₂ is the post-load prediction time, T _t is the load time, that is, the time during which the load is applied, and T _r is the relaxation time, ie, the time during which the influence of the load application remains. . Since these times vary depending on the measurement position and measurement object, they are input as parameters. The predicted no-load signal 11 in this figure is T ₁ = 30 seconds, T ₂ = 30 seconds, T _r = 30 seconds, and the least square method is used from the measurement signals of the pre-load prediction time T ₁ and the post-load prediction time T _2. I was asked. Further, a quintic equation was input as an arbitrary function representing the predicted no-load signal 11.

FIG. 7 is a display example of the ΔC _oxy load time integrated value 17a and the ΔC _deoxy load time integrated value 17b for each load time. The ΔC _oxy signal 14a and the ΔC _deoxy signal 14b in FIG. 5 are time integrated for each load time to obtain a ΔC _oxy load time integrated value 17a and a ΔC _deoxy load time integrated value 17b, and a window 9 displayed on the display device 1 is obtained. Inside, a solid bar graph is displayed for each load number. Here, the horizontal axis represents the load number, and the vertical axis represents the ΔC _oxy load time integrated value and the ΔC _deoxy load time integrated value. Here, it is also possible to display the ΔC _oxy load time average value and the ΔC _deoxy load time average value. Also, the display can be displayed in a different color so that the viewer can easily see it.

  FIG. 8 shows a display example when measurement is performed at a plurality of measurement positions using the biological light measurement device. Here, an example will be described in which the measurement site is the head and four measurement positions are set on the head. In this display example, the measurement site image 18 of the subject, the measurement position marks 19a to 19d representing the set measurement positions, the graphs 21a to 21d corresponding to the measurement positions, and the correspondence between the measurement positions and the graphs are shown. The instruction lines 20 a to 20 d are displayed on the window 9 displayed on the display device 1. Here, as the measurement site image 18, a measurement site tomographic image or a measurement site three-dimensional image of the subject himself / herself photographed by an image diagnosis apparatus represented by a head model diagram or an MRI apparatus can be used. .

  By calculating the prediction signal from the measurement signal, measurement can be performed without waiting for the biological fluctuation to stabilize. Further, by simultaneously displaying the measurement signal and the calculated prediction signal, the observer can easily determine whether or not the measurement signal has changed.

The figure showing the fluctuation which exists in the living body naturally. The conceptual diagram of a biological light measuring device. The figure which shows the example of a display by this invention. The figure which shows the example of a display by this invention. The figure which shows the example of a display by this invention. Explanatory drawing of the time-axis definition by this invention. The figure which shows the example of a display by this invention. The figure which shows the example of a display by this invention.

Explanation of symbols

1: Display device, 2: Oscillator, 3a, 3b: Light source, 4: Detector, 5: Lock-in amplifier, 6: Analog-digital converter, 7: Calculator, 8: Subject, 9: Window, 10: Measurement signal, 11: Predicted no-load signal, 12: Load start mark, 13: Load end mark, 14: Differential signal, 15: Base line, 16a: ΔC _oxy signal, 16b: ΔC _deoxy signal, 17a: ΔC _oxy load time integration 17b: ΔC _deoxy load time integral value, 18: measurement site image, 19: measurement position mark, 20: indicator line, 21: graph, 25: input device

Claims (3)

Light irradiating means for irradiating light of wavelength λ1 and wavelength λ2 to the subject's head;
A light receiving means for detecting light irradiated from the light irradiation means and reflected inside the subject,
A biological optical measuring device for measuring brain hemodynamic changes characterized by having a calculation means for calculating temporal changes in the amount of relative change in oxidized and reduced hemoglobin concentration due to load from the following formulas (1) and (2) .
Ln {S _tr (λ1, t) / Sm (λ1, t)} = ε _oxy (λ1) · ΔC _oxy (t) + ε _deoxy (λ1) · ΔC _deoxy (t) · (1)
Ln {S _tr (λ2, t) / Sm (λ2, t)} = ε _oxy (λ2) · ΔC _oxy (t) + ε _deoxy (λ2) · ΔC _deoxy (t) · (2)
S _tr (λ, t): Time variation of predicted no-load signal at wavelength λ
Sm (λ, t): time change epsilon _{the oxy} of the measurement signals at the wavelength lambda _(lambda): absorption coefficient epsilon _{the deoxy} oxyhemoglobin at wavelength lambda _(lambda): absorption coefficient [Delta] C _{the oxy} of reduced hemoglobin at the wavelength λ _(t): Load Change of oxyhemoglobin concentration relative change with time ΔC _deoxy (t): Change with time of change of reduced hemoglobin concentration relative change   The biological light measurement apparatus according to claim 1, further comprising an image display unit configured to display a temporal change in the relative change amount of the oxidized and reduced hemoglobin concentration due to the load. A modulator for intensity-modulating the light of the wavelengths λ1 and λ2 at different modulation frequencies,
The living body light measurement apparatus according to claim 1, further comprising: a lock-in amplifier that separates light modulated by the modulator.

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