JP2004184402A - Optical measuring device for living body - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To set a timing for which synchronous addition is effective, by repetitive impression of a task, in an optical measuring device for living body. <P>SOLUTION: The performing interval for task and rest, the number of repetitions of the task, mutual relation of each set on/off input for the light source for optical irradiator 2-6, are checked by a computer 1-11. If the mutual relation fits prescribed inhibition conditions, the computer urges resetting with an alarm, or automatically changes the on/off interval of the light source. <P>COPYRIGHT: (C)2004,JPO&NCIPI

Description

  The present invention relates to a biological light measurement device that measures the concentration of a metabolite in a living body or a change in the concentration using light.

  Using light represented by near-infrared light, which has high permeability to biological tissues, measures the concentration of metabolites in the living body represented by oxidized hemoglobin, reduced hemoglobin, and myoglobin or changes in the concentration, and images the concentration change A biological light measurement device that performs the measurement is described in Patent Document 1 (Japanese Patent Application Laid-Open No. 9-98972). FIG. 2 shows the configuration of the apparatus. The subject 2-1 wears a helmet 2-3 to which an optical fiber holder 2-2 used for measurement is fixed on a scalp or hair corresponding to an upper part of a measurement site. A light source (hereinafter, referred to as a light irradiator 2-7) typified by a semiconductor laser, a light emitting diode, and a lamp described later, or a detection typified by an avalanche photo diode and a photomultiplier tube is provided on the optical fiber holder. An optical fiber connector 2-5 connected to an optical fiber 2-4 connected to a detector (hereinafter, referred to as a photodetector 2-6) is inserted. The tip of the optical fiber connector 2-5 squeezes the hair of the subject and makes contact with the scalp. A part of the optical fiber (five optical fibers in FIG. 2) is connected to the light irradiator 2-7 as described above. The remaining optical fibers (four optical fibers in FIG. 2) are connected to the above-described photodetector 2-6. The optical fibers connected to the light irradiator 2-7 and the optical fibers connected to the light detector 2-6 are alternately arranged on the scalp at an interval of about 30 mm. The optical fiber connected to is detected from light emitted from an optical fiber located at a position about 30 mm away from the optical fiber and passed through the inside of the living tissue. The five light irradiators 2-7 may be any light irradiators capable of irradiating light sources of a plurality of wavelengths. This is because, as shown in FIG. 3, when the absorption spectra of the substances to be measured (oxyhemoglobin and reduced hemoglobin in FIG. 3) are different with respect to wavelength, by using a light source having a plurality of wavelengths, This is because the change in the concentration of the substance to be measured can be measured (see Non-Patent Document 1 (Atsushi Maki, Yuichi Yamashita, Yoshitoshi Ito, Eijyu Watanabe, Yoshia ki Mayanagi, and Hideaki Koizumi, “Spatial and temporal analysis of hum an motor activity ", Medical Physics, Vol. 22 (No. 12), pp. 1997-2005 (1995) (Medical Physics, Vol. 22 (12), 1997-2005, 1995))).

  Reference numeral 2-8 denotes a control device that can independently control the amount of light emitted from each light irradiator for each light source. The control content is electronic control represented by a personal computer and a workstation described in 2-9. It is controlled using a computer. In Patent Document 1 described above, when using the position information of each light irradiator and a plurality of wavelengths, the control device adjusts the intensity of each light source at different frequencies on the order of kilohertz in order to provide information on each wavelength. Modulated. Information on the modulation frequency for each of these light sources is transmitted to a signal processing device 2-10 described below via a transmission cable 2-11. The light intensity that has passed through the inside of the living body is detected by the light detector 2-6, and the light intensity is converted into an electric signal. The converted electric signal is transmitted to the signal processing device 2-10. The signal processing device 2-10 includes a lock-in amplifier and an analog / digital conversion device, and extracts components corresponding to each light source component from the light intensity detected by the photodetector 2-6. This extraction method will be described with reference to FIG. The extracted signal is transmitted to the computer 2-9, processes the measurement result, and displays it as a topography image.

  Next, a method of extracting components corresponding to each of the light source components described above will be described with reference to FIG. 4 and FIG. 4 are optical fibers connected to the light irradiator 2-7, respectively. 4-6, 4-7, 4-8, and 4-9 (1-4 shown by a large square) similarly indicate the positions where the light is connected to the photodetector 2-6, respectively. Figure 2 shows where the fiber is located. These locations are alternately arranged at a distance of about 30 mm, but are not limited to this value of 30 mm, and may vary from about 20 mm to about 40 mm depending on the structure of the head and optical constants (scattering coefficient and absorption coefficient). It is possible to set. Numerals 13 to 24 shown in small squares in FIG. 4 are sampling points (typically, one of these sampling points) that provide representative position information of blood volume changes detected using adjacent optical fiber pairs. (Reference numeral 4-10).

  In FIG. 4, the position of the sampling point is substantially the midpoint between the arrangement position of the optical fiber connected to the light irradiator and the connection position of the optical fiber connected to the photodetector. The reason will be described with reference to the structural model of the brain shown in FIG. Reference numerals 5-1, 5-2, 5-3, and 5-4 denote a scalp, a skull, a cerebrospinal fluid layer, and gray matter, respectively, which have a layered structure in FIG. An optical fiber holder 5-6 fixed by a helmet 5-5 is fixed on the scalp 5-1. The optical fiber 5-7 connected to the light irradiator 2-7 and the light detector 2-6 are fixed. The optical fibers 5-8 connected to 6 are connected at intervals of about 30 mm. As shown in FIG. 5, the distribution shape of the light emitted from the optical fiber connected to the light irradiator and reaching the optical fiber connected to the photodetector located at a position about 30 mm away is “banana shape 5- 9 ", the sensitivity to a change in blood volume in the cerebral cortex 5-10 is determined in the vicinity of the midpoint of the optical fiber connected to the light irradiator 2-7 and the light detector 2-6. This is because it is known that when the blood volume changes due to the activity, it is maximum.

  Here, with respect to the light source detected at the light detection position 4-6, an extraction method corresponding to each adjacent light source component will be described. There are three light sources, light irradiation positions 4-1, 4-2, and 4-3, which are present at an interval of about 30 mm from the light detection position 4-6. When each light source operates at the same intensity modulation frequency (including a continuous wave whose modulation frequency is 0), three light irradiation positions 4-1, 4-2, 4- The light source irradiated in 3 arrives, and it becomes difficult to discriminate from which light irradiation position the signal is. Therefore, in Patent Document 1 described above, the intensity modulation frequencies of the light sources at the light irradiation positions 4-1, 4-2, 4-3, 4-4, and 4-5 are all different values. By using this method, for example, even when light reaching the light detection position 4-6 is irradiated from three light irradiation positions, a lock-in amplifier and an analog / digital converter that perform a filter operation with reference to each modulation frequency are used. , The signal corresponding to each light source can be extracted.

  A measurement method capable of improving the spatial resolution in connection with such a biological light measurement device is disclosed in Japanese Patent Application Laid-Open No. 2002-586.

  First, the arrangement method of the irradiation optical fiber and the detection optical fiber shown in FIG. In this arrangement method, light irradiation positions 4-1 4-2, 4-3, 4-4, and 4-5 by optical fibers connected to the light irradiator 2-7 (1-5 shown by a circle). Are alternately separated by about 30 mm from the arrangement positions 4-6, 4-7, 4-8, and 4-9 of the optical fibers connected to the photodetector 2-6 (1-4 enclosed by a large square). Place. Here, numerals 13 to 24 shown in small squares in the figure are sampling points 4-10. If the arrangement interval between the optical fiber connected to the light irradiator 2-7 and the optical fiber connected to the photodetector 2-6 is 30 mm, the interval between adjacent sampling points, for example, the interval between sampling points 13 and 15 Is about 21 mm, which is √2 times 15 mm which is half of the optical fiber arrangement interval. The interval between the sampling points 13 and 18 is 30 mm, which is the same as the interval between the optical fibers.

  In order to improve the spatial resolution, it is essential to shorten the interval between the sampling points, and the above-mentioned Patent Document 2 uses the method described below. First, as shown in FIG. 6, another optical fiber array having the same arrangement as the optical fiber connected to the light irradiator 2-7 and the optical fiber connected to the photodetector 2-6 shown in FIG. Prepare. In FIG. 6, 6-1, 6-2, 6-3, 6-4, 6-5 (circled 6-10) indicate the positions of the optical fibers connected to the light irradiator 2-7. 6-6, 6-7, 6-8, and 6-9 (5-8 enclosed by a large square) indicate the positions of the optical fibers connected to the photodetector 2-6. . Numerals 1 to 12 shown in small squares in the figure indicate the positions of sampling points (one of these is denoted by reference numeral 6-10).

  Then, the optical fibers having the arrangement relationship shown in FIGS. 4 and 6 are arranged in the manner shown in FIG. In FIG. 7, 7-1, 7-2, 7-3, 7-4, and 7-5 denote the arrangement positions of the optical fibers connected to the light irradiator 2-7 shown in FIG. 7-7, 7-8, 7-9, and 7-10 indicate the positions of the optical fibers connected to the light irradiator 2-7 shown in FIG. 6, respectively, and 7-11, 7-12, and 7-11. 7-13 and 7-14 show the arrangement positions of the optical fibers connected to the photodetector 2-6 shown in FIG. 4, and 7-15, 7-16, 7-17 and 7-18 show in FIG. The arrangement positions of the optical fibers connected to the detected photodetectors 2-6 are shown respectively.

  In FIG. 7, the arrangement position of the optical fiber connected to the light irradiator 2-7 shown in FIG. 6 is changed to the arrangement position of the optical fiber connected to the photodetector 2-6 shown in FIG. Arrange them so that they are adjacent. That is, the arrangement position (for example, 7-9) of the optical fiber connected to the light irradiator 2-7 shown in FIG. 6 is changed to the arrangement position of the optical fiber connected to the light irradiator 2-7 shown in FIG. The optical fiber connected to the photodetector 2-6 is arranged (in the horizontal direction) between the position (for example, 7-2) and the arrangement position (for example, 7-13) of the optical fiber connected to the photodetector 2-6. As a result, in the upper stage and the lower stage, the arrangement positions 2, 9, and 1, 10 of the optical fibers connected to the light irradiator 2-7 are adjacent to each other, and the positions of the optical fibers connected to the photodetector 2-6 are adjacent thereto. The arrangement positions 3, 6 and 2, 7 are adjacent, and the arrangement positions 5, 6 and 4, 7 of the optical fiber connected to the light irradiator 2-7 are adjacent. In the middle stage, the arrangement positions 1 and 8 of the optical fibers connected to the photodetector 2-6 are adjacent, and the arrangement positions 3 and 8 of the optical fibers connected to the light irradiator 2-7 are adjacent thereto. Furthermore, the arrangement positions 4 and 5 of the optical fibers connected to the photodetector 2-6 are adjacent.

  FIG. 8 is a diagram showing the positions of 24 sampling points 1-24 (the reference numeral 8-1 is representatively given thereto) corresponding to the arrangement positions of the optical fibers shown in FIG. Here, the sampling point 1-12 is a sampling point obtained from the arrangement method of the optical fiber connected to the light irradiator 2-7 and the optical fiber connected to the light detector 2-6 shown in FIG. The sampling points 13-24 indicate sampling points obtained from the arrangement method of the optical fiber connected to the light irradiator 2-7 and the optical fiber connected to the photodetector 2-6 shown in FIG. . The area indicated by the light dots on the background in FIG. 8 is the measurement area.

  Comparing the distribution of the sampling points in FIGS. 8 and 4, in FIG. 4, the sampling points are arranged in a grid at an equal interval of 21 mm, whereas in FIG. It becomes what was arranged in the shape. As a result, the spatial resolution can be improved.

  However, in order to obtain the sampling points shown in FIG. 8 by the measurement method shown in FIG. 7, irradiation is performed from the arrangement positions 1 to 5 of each optical fiber connected to the light irradiator 2-7 shown in FIG. And the light emitted from the arrangement position 6-10 of each optical fiber connected to the light irradiator 2-7 shown in FIG. There is a need. The reason is explained in the above-mentioned Patent Document 2. For example, the optical fiber at the arrangement position 3 not only detects the light radiated from each optical fiber connected to the light irradiators 2-7 at the arrangement positions 2, 3 and 5 and propagates the light inside the living body, but also detects the light. The light emitted from the optical fiber connected to the light irradiator 2-7 at the position 9 and propagated inside the living body is also detected. The optical fiber connected to the light irradiator 2-7 at the disposition position 9 and the optical fiber connected to the photodetector 2-6 at the disposition position 3 correspond to the light set in FIGS. There is only half the distance of the fiber placement. The intensity of light that has propagated inside the living body at half the distance is about 1000 times the intensity due to propagation at the original distance. Therefore, light irradiated from the optical fiber connected to the light irradiator 2-7 at the arrangement position 9 and propagated inside the living body was detected by the photodetector 2-6 connected to the optical fiber at the arrangement position 3. If light is detected by the photodetector, the dynamic range of sensitivity may be exceeded.

  In Patent Document 2 described above, the light source of each optical fiber connected to the light irradiator 2-7 shown in FIG. 4 and the light source of each optical fiber connected to the light irradiator 2-7 shown in FIG. It has been proposed to address this problem by alternately flashing at T seconds. FIG. 9 is a time chart showing alternate blinking of the light source. Here, the light source of the probe group A means the light source of each optical fiber connected to the light irradiator 2-7 shown in FIG. 4, and when this is ON, the sampling points 13-24 shown in FIG. Only changes in blood volume are detected. On the other hand, the light source of the probe group B means the light source of each optical fiber connected to the light irradiator 2-7 shown in FIG. 6, and when this is ON, only the sampling points 1-12 shown in FIG. Detect changes in blood volume.

JP-A-9-98972

JP-A-2002-586 Atsushi Maki, Yuichi Yamashita, Yoshitoshi Ito, Eijyu Watanabe, Yoshia ki Mayanagi, and Hideaki Koizumi, “Spatial and temporal analysis of hum an motor activity”, Medical Physics, Vol. 22 (No. 12), pp. 1997-2005 ( 1995) (Medical Physics, Vol. 22, No. 12, 1997-2005, 1995)

  When examining the brain activity of a subject, a doctor or a laboratory technician may stimulate the subject to activate the brain of the subject. For example, in the above-mentioned Patent Document 1 (Japanese Patent Application Laid-Open No. 9-98972), as shown in FIG. 10, first, the subject is kept in a resting state for a certain period of time (for example, X seconds (hereinafter referred to as a rest period)). Let Then, an instruction to start the movement of the finger and an instruction to end the movement of the finger after a given period of time (for example, Y seconds (hereinafter, referred to as a task period)) have elapsed since the instruction was given, Is rested again. In addition, in order to reduce the noise of the signal to be measured, these resting states and the state of activating the brain are alternately repeated, and the measurement result is added only to the data during the rest period and only to the data during the task period, That is, a method of performing synchronous addition is disclosed. However, in the measurement method described in the above-mentioned Patent Document 1 (Japanese Patent Application Laid-Open No. 9-98972), a plurality of light irradiators and light for irradiating the object with light emitted from the light irradiators are used. It is assumed that the irradiating means and the arrangement position of the optical fiber of the optical system composed of a plurality of photodetectors for detecting light radiated to the subject and propagated inside the subject are designed as shown in FIG. 4 or FIG. Therefore, it was not necessary to blink the light source, and the blood volume change at all sampling points could be simultaneously and continuously measured. Therefore, the rest period and the task period can be set arbitrarily. The task referred to here is not limited to the behavior of the subject such as exercising a finger.For example, even if the subject itself is passive, such as making the subject hear sound, What is necessary is just to bring out the activity.

  On the other hand, as disclosed in Patent Document 2 (Japanese Patent Laid-Open No. 2002-586), in order to increase the density of sampling points, a plurality of light irradiators such as probe groups A and B are used. A light irradiation means for irradiating the object with light irradiated from the light irradiator; and an optical system including a plurality of photodetectors for detecting light irradiated to the object and propagated inside the object. In the case where the arrangement positions of the optical fibers are grouped and the light source is turned on and off at a period T corresponding to the group and the measurement is performed, it is impossible to detect the blood volume change at all the sampling points at the same time. Therefore, it is useful to detect a change in blood volume at all sampling points at an arbitrary time equivalently using the synchronous addition method described in Reference 1 (Japanese Patent Application Laid-Open No. 9-98972). It is. However, the above-mentioned patent documents and non-patent documents disclosed so far do not disclose a method of setting the blink period T, the rest period X, and the task period Y of the light source.

  Now, for example, as shown in FIG. 11, consider a case where a setting is made between X, Y, and T using a natural number n so as to satisfy the relationship of equation (1).

X + Y = nxT ---- (1)
FIG. 11 is an example in which X = 2T and Y = 3T are set. In the case of FIG. 11, the light source of the probe group A is always turned off and the light source of the probe group B is turned on during the period of T / 2 at the start of the task period. This means that during the period of T / 2 at the start of the task period, only the change in blood volume at each sampling point in the probe group B can be measured, and the change in blood volume at each sampling point in the probe group A can be measured. Means that measurement is not possible. In the subsequent period of T / 2, only the change in blood volume at each sampling point in the probe group A can be measured, and the change in blood volume at each sampling point in the probe group B cannot be measured. This is the same for the subsequent measurement. As a result, even if the synchronous addition for adding the data of the task period and the rest period several times is performed, only the blood volume change for each T / 2 period of the task period and the rest period is repeatedly detected. Become. That is, since the entire range of the task period and the rest period cannot be measured uniformly, not only does the effect of the synchronous addition diminish, but also data loss corresponding to the period during which measurement cannot be performed occurs.

  Accordingly, it is an object of the present invention to provide a setting method for effectively performing synchronous addition and an optical measuring device capable of easily performing the setting method.

  The living body light measurement device according to the present invention has a timing setting unit that allows a user represented by a doctor or a laboratory technician to set all or any of the blinking cycle of the light source, the rest period, the task period, and the number of times the task is repeated. When the input result meets a predetermined prohibition condition, the setting is prohibited. Typically, the prohibition condition is that the sum of the rest period and the task period is an integral multiple of the blinking cycle of the light source (formula (1)). For example, when the setting input satisfies the above-mentioned prohibition condition, a warning is issued, and all or any of the blinking cycle, the rest period, the task period, and the number of times the task is repeated are reset.

  Alternatively, there is provided a means for automatically changing the blinking cycle of the light source when the setting input satisfies the prohibition condition.

  A setting method for preventing data loss and effectively performing synchronous addition, and an optical measurement device capable of easily performing the setting method can be provided.

  Hereinafter, embodiments according to the present invention will be described.

(Example 1)
FIG. 1 shows a device configuration of a biological light measurement device according to the present invention. The subject 1-1 wears a helmet 1-3 to which an optical fiber holder 1-2 used for measurement is fixed, on a scalp or hair corresponding to an upper part of a measurement site. The optical fiber holder 1-2 includes a light source (hereinafter, referred to as a light irradiator 1-7) represented by a semiconductor laser, a light emitting diode, and a lamp described later, or an avalanche photo diode and a photomultiplier tube. An optical fiber connector 1-5 connected to an optical fiber 1-4 connected to a detector (hereinafter, referred to as a photodetector 1-6) is inserted. The tip of the optical fiber connector 1-5 squeezes the hair of the subject and makes contact with the scalp. A part of the optical fiber 1-4 (10 optical fibers in FIG. 1) is connected to the light irradiator 1-7 as described above. The remaining optical fibers (eight optical fibers in FIG. 1) are connected to the above-described photodetector 1-6. In FIG. 1, the optical fiber connector and the optical fiber holder shown in black color are herein referred to as a probe group A, and similarly, the optical fiber connector and the optical fiber holder shown in gray are referred to as a probe group B here. .

  In each of the probe group A and the probe group B, the optical fiber connected to the light irradiator 1-7 and the optical fiber connected to the light detector 1-6 are alternately arranged at intervals of about 30 mm. . This arrangement interval is not limited to the interval of about 30 mm, and can be set to an arbitrary value according to the biological structure and the optical constant. Also, in FIG. 1, as described with reference to FIG. 7, the probe group A is located at a substantially middle point between the arrangement position of the optical fiber connected to the light irradiator and the arrangement position of the optical fiber connected to the photodetector. Either the light irradiator of B or the optical fiber connected to the photodetector is arranged.

  Light emitted from the optical fiber connected to the light irradiator 1-7 propagates inside the subject, and is detected using the optical fiber connected to the light detector 1-6. The light irradiators 1-7 modulate the intensity at different frequencies for each light source. The information on the modulation frequency is transmitted through a transmission cable 1-11 to a signal processing device 1-10 including a lock-in amplifier and an analog / digital converter. The signal processing device 1-10 processes the result of converting the intensity of light that has passed through the inside of the living body from the optical signal to the electric signal by the photodetector 1-6. Reference numeral 1-9 denotes an electronic computer typified by a personal computer or a workstation, which is a task period, a rest period, the number of task repetitions, an intensity modulation frequency of a light irradiator, and a blinking timing in brain function measurement. It has the function of setting conditions, calculating the change in blood volume from the intensity of light passing through the inside of the living body, and imaging the result. Among them, a display screen 1-13 is used for setting all or any information related to the above-described measurement conditions. Reference numeral 1-12 denotes a speaker used to present a trouble or the like to the user at the time of measurement, and is specifically characterized by emitting sound. 1-15 is an input device such as a keyboard, for example, for inputting measurement conditions represented by the task period, the rest period, the number of task repetitions, the intensity modulation frequency of the light irradiator, and the blink timing in the brain function measurement described above. Used for Reference numeral 1-8 denotes a control device that can control the amount of light emitted from each light irradiator 1-7 independently for each light source, and the control content is controlled using an electronic computer 1-9. Information on the modulation frequency for each of these light sources is transmitted to the signal processing device 1-10 via the transmission cable 1-11. The processing result of the signal processing device 1-10 is sent to the computer 1-9, where the measurement result is processed and displayed on the display screen 1-13 as a topography image. Note that, as described above, the task referred to here is not limited to the behavior of the subject such as making the subject move his / her finger. The specimen itself may be passive, as long as it exhibits brain activity. When the subject exercises his / her finger, an exercise instruction may be displayed on the above-described display screen 1-13. Further, when the subject can hear the sound, the above-described speaker 1-12 can be used for this purpose.

FIG. 12 shows inputs for setting measurement conditions represented by the above-described task period (Y), rest period (X), number of task repetitions (R), and flash timing of the light irradiator (light source switching cycle T ₁ ). It is a figure showing an example of a screen. Here, R must be a natural number. The setting of the measurement condition includes, for example, setting of an intensity modulation frequency corresponding to each light irradiator 1-7. It is convenient that these settings have standard setting values in advance and can be changed according to the user's idea.

  FIG. 13 is a diagram showing an example of the ON and OFF states of the light sources of the probe group A and the probe group B during the task period and the rest period under the appropriate settings in FIG. In the figure, a period indicated by hatching in the upper left in the upper part of the task period indicates a period in which measurement data is obtained by turning on the light source of the probe group A, and a period indicated by hatching in the lower right in the lower part indicates the period of the probe group B. The period during which measurement data is obtained by turning on the light source is shown.

Here, the light source switching cycle T ₁ , the task period Y, and the rest period X are set so as not to satisfy the above-described expression (1). That is, they are set as shown in the equation (2).

X + Y ≠ nT ₁ ---- (2)
However, the task repetition count R is selected so that R (X + Y) does not exceed a certain value considering the burden on the subject. That is, the subject is required to maintain the posture requested by the user or to repeatedly perform the operation corresponding to the task during the time of R (X + Y).

As can be seen by comparing FIGS. 13 and 11, the light source switching period T shown in FIG. 11 is changed to the light source switching period T ₁ shown in FIG. 13. Light source switching period T _1, as compared to the light source switching period T shown in FIG. 11, which is approximately 10% longer. Therefore, when the measurement is performed under the light source ON / OFF cycle shown in FIG. 13, the light source ON timing is slightly shifted in each task period and rest period. As a result, the effect of synchronous addition by repeating the task period and the rest period can be obtained. That is, in the probe group A and the probe group B, the ON and OFF states of the light source are measured at the same timing in each of the task period and the rest period under the light source switching period T shown in FIG. On the other hand, in FIG. 13, a period during which measurement data is obtained by turning on the light source of the probe group A, which is indicated by an upper left hatching in the upper part during the task period, and a lower right hatching in the lower part. As can be seen by comparing the state of each cycle of the period in which the measurement data is obtained by turning on the light source of the probe group B, it can be seen that the measurement data is obtained in different periods for each task period. As a result, if data for several task periods is obtained and synchronously added, measurement without data loss can be performed. It goes without saying that the same applies to the rest period.

  An example of setting the number of task repetitions R so as to reduce the burden on the subject as much as possible by using the input screen of FIG. 12 to execute the measurement as shown in FIG. 13 will be described below.

First, a user who is a doctor or a laboratory technician inputs values of the task period X and the rest period Y. The light source switching period T _1, may be as set by the user, the computer 1-9, in advance, may be what gives a proper value. For these X and Y and T _1, as described above (1) is not satisfied. Therefore, when a numerical value satisfying the expression (1) is input, the input screen shown in FIG. 12 is flickered, or the input character is displayed in red to inform the user that the input number is invalid. Preferably, a warning sound is emitted from the speaker 1-12 shown in FIG. The user who has noticed that the input number is inappropriate may perform the input again.

The task repetition count R is set by the user in consideration of the condition of the subject, that is, age, physical strength, familiarity with this test, and the like. The input value of the task number of repetitions R, task period X, the relation between rest periods Y and light source switching period T _1, when the result of the synchronous addition is not a sufficient electronic computer 1-9 determines the In order for the computer 1-9 to recommend an appropriate value near the input task repetition count R, the input portion of the task repetition count on the input screen shown in FIG. 12 is flickered or displayed in red. Further, an audio warning from the speaker 1-12 is also used. For this purpose, the electronic computer 1-9, task period X, comprises a table or the like of the recommended data for task repeat count from the relationship of rest periods Y and light source switching period T _1, o program for comparison of the input value Shall be provided. Of course, if the number of task repetitions exceeds a certain level, the effect of the synchronous addition will be sufficient. Therefore, by setting the formula (1) to be unsatisfied, data bias can be prevented and measurement with reduced noise can be performed. It becomes.

  The setting values described with reference to FIG. 12 are transmitted from the computer 1-9 to the light irradiator 1-7, and are used for controlling the modulation and blinking of each light source in the light irradiator 1-7.

  Next, the validity of the method of setting each value described above will be described with reference to FIGS.

  First, FIG. 14 is a diagram illustrating an example of measured values of the change in transmitted light intensity obtained when a light source is continuously turned on at a certain sampling point and a rest period and a task period are changed for a subject in a cycle of 12 seconds. It is. The horizontal axis represents time, and the vertical axis represents transmitted light intensity. Here, X = Y = 12 seconds. Since the light source is continuously turned on, the measurement data is naturally continuous. However, actually, in the signal processing device 1-10, the output of the photodetector 1-6 is sampled at a predetermined cycle and subjected to analog-digital conversion to obtain detection data. Since the data is sent to -9, it is not the continuous data shown in the figure, but may be considered as continuous data in a practical sense.

  As can be seen from this data, since the data is one sampling point, the measured values show similar patterns in each of the rest period and the task period. However, strictly speaking, they are not the same pattern. This pattern shift is caused by a mixture of an element due to a change in the measured value according to the state of the subject and an element due to the measurement noise. Therefore, by synchronously adding each of the data of the rest period and the data of the task period, it is possible to reduce an element due to measurement noise.

  FIG. 15A is a diagram showing the measurement results shown in FIG. 14, and FIG. 15B is a diagram showing the measurement results obtained by measuring the prohibition condition described in FIG. It is. In FIGS. 15A and 15B, the time axis is shown twice as wide as that in FIG. 14 for easy understanding. In FIG. 15B as well, X = Y = 12 seconds, but it is assumed that the measurement point of interest is illuminated by the light source of the probe group A, and five times the ON / OFF cycle T of the light source is the rest period + The ON / OFF state of the light source when it is set in the task period (X + Y) and the measurement results corresponding thereto are shown. The setting of X + Y = 5T matches the prohibition condition shown in Expression (1). As a result, as shown in FIG. 15B, only the measurement results at the same timing are obtained in each of the rest period and the task period. This means that when the synchronous addition is performed in each of the rest period and the task period, there is a merit of the synchronous addition in the period in which the data is obtained, but the data corresponding to the period in which the light source is OFF is not obtained. Data loss corresponding to the OFF period occurs.

FIG. 16 (A) is a diagram showing the measurement result shown in FIG. 14 which is the same as FIG. 15 (A), and FIG. 16 (B) is a diagram showing the result of the prohibition condition described in FIG. It is a figure showing the measurement result of having measured. FIGS. 16A and 16B have the same time axis as FIGS. 15A and 15B. 16 But (B), a X = Y = 12 seconds, it is assumed that the measurement point of interest is illuminated by a light source probe group A, ON of a light source, 4.5 times the OFF period _{T 1} Is set to the rest period + the task period (X + Y), the ON / OFF state of the light source, and the measurement results corresponding thereto. That is, FIG. 15 (A), (B) and FIG. 16 (A), the in (B), because it is _{X + Y = 5T = 4.5T 1} , T 1 = 1.11T , and the FIG. 16 (A), the ( In FIG. 15B, the measurement is performed by the ON / OFF cycle of the light source which is about 10% longer than in FIGS. 15A and 15B.

As can be seen from FIG. 16B, according to the first embodiment, the ON and OFF timings are slightly shifted in the rest period and the task period, respectively, so that the data shown in FIG. Is eliminated. In Example 1, the light source of the ON, 4.5 times the rest period + task period of OFF period _{T 1} (i.e., X + Y = 4.5T ₁₎ and then from the, as seen with reference to FIG. 16 (B) The ON and OFF of the light source during the first rest period and the ON and OFF of the light source during the second rest period are exactly reversed. This is the same for the task period. Therefore, the data obtained by turning on the light source in the first rest period and the data obtained by turning on the light source in the second rest period are data corresponding to the OFF period of the other party.

  FIG. 17 is a diagram for more specifically explaining the elimination of data loss. In FIG. 17, the horizontal axis shows the time based on the ON / OFF cycle of the light source, and the vertical axis shows the measurement result of the transmitted light intensity during the rest period shown in FIG. The measurement result of the transmitted light intensity during the first rest period shown in FIG. 16 is indicated by a solid line, the measurement result of the transmitted light intensity during the second rest period is indicated by a thick broken line, and the measurement result of the transmitted light intensity during the third rest period is shown. Are indicated by thick dashed lines, respectively. As can be easily understood from the figure, data during a period in which there is no data in the first rest period (solid line) is obtained as shown in data in the second rest period (dashed line). Further, data (chain line) of the third rest period is obtained as data of the period corresponding to the data (solid line) of the first rest period. Therefore, if the rest period and the task period are repeated six times, that is, if the number of task repetitions R is 6, three measurement results can be obtained in each ON or OFF period. Therefore, if these are added and divided by 3, not only the advantage of synchronous addition can be obtained, but also data loss can be prevented. The description of the task period is omitted, but the same applies.

In Figure 17, ON of a light source, set 4.5 times the OFF period T ₁ and rest period + task period, and data obtained by ON of first rest period sources, the second rest period the light source the data obtained by the turned oN, respectively, oN of the light source so that the time data corresponding to the duration of the opponent to OFF, chose OFF period T _1. ON of the light source, setting 5.5 times the rest period + task period of OFF period _{T 1 (X + Y = 5.5T} 1), is the same. However, it is only necessary to set not only the data of the time corresponding to the OFF period of the other party as described above, but also to determine an arbitrary time lag. In any case, the synchronous addition process may be performed after the repetition of the appropriate rest period and task period according to the deviation.

(Example 2)
Next, a measurement method different from that of the first embodiment will be described.

FIG. 18 is a diagram illustrating a measurement sequence according to the second embodiment. In this measuring method, the light source probe group A, first to ON, after was resting subjects (t ₀₂ from t ₀₁ in rest ... _Figure), applying a load to a subject (task ... t ₀₂ in FIG. To t ₀₃ ), and then rest the subject again (rest ... t ₀₃ to t _{04 in} FIG. 18). The Rest - task - (from _{t 01} in FIG. 18 _{t 04)} while performing the rest of the sequence of the probe group B light source is turned OFF. Next, from time _t04 to _t07 , the light source of the probe group B is turned on, while the light source of the probe group A is turned off. Then, the rest, the task, and the rest are performed in a period from time t ₀₄ to t ₀₅ , a period from t ₀₅ to t ₀₆ , and a period from t ₀₆ to t ₀₇ , respectively. Then, again, ON the light source probe group A, and OFF the light source probe group B _(t 10 from _{t 07} in FIG. 18). Further, thereafter, the ON light source probe group B, and OFF the light source probe group A _(t 13 from _{t 10} in FIG. 18).

  In the second embodiment, if the rest period and the task period are set to be equal to each other as compared with the measurement sequence shown in the first embodiment, a double rest period is required. In the measurement sequence shown in FIG. 18, after the light source of the probe group A is turned on and the rest-task-rest is performed, the light source of the probe group B is turned on and the rest-task-rest is performed again. This eliminates the necessity of blinking the light source in a short time cycle as compared with performing the task-rest-task-rest continuously as in the measurement method shown in FIG. 13, thereby increasing the stability of the system. .

Also in the measurement sequence shown in FIG. 18, the task period (X), the rest period (Y), and the number of task repetitions (R) are set on the setting screen shown in FIG. Here, it is assumed that the time corresponding to the light source switching period shown in FIG. 12 described above (the time corresponding to t ₀₄ from t ₀₁ in FIG. 18) is given by the electronic computer 1-9, if necessary, The setting may be made by the user in the same manner as the setting screen of FIG. Note that the prohibition condition required to prevent data loss in the first embodiment is automatically resolved in the second embodiment. That is, when the light source is turned on and data is sampled, the data is continuously measured in any of the rest period and the task period, so that data loss does not occur. These values are inputted to the computer 1-9 shown in FIG. 1, and based on the inputted values, the control device 1-8 sends ON / OFF control signals for the respective light irradiators 1-7. .

  FIG. 20 is a diagram showing a transmitted light intensity signal detected at a certain sampling point of the probe group A when the task period = rest period = 12 seconds and the number of repetitions = 2 on the setting screen shown in FIG. It is. The horizontal axis indicates the passage of time.

  FIGS. 21A and 21B are diagrams illustrating the result of performing synchronous addition on the measurement result of FIG. FIG. 21A shows the first measurement result and the second measurement result to be subjected to synchronous addition in a superimposed manner. Here, the time axis is shown wider than that of FIG. The solid line indicates the first measurement result, and the broken line indicates the second measurement result. FIG. 21B shows the result of synchronous addition in which the measurement results shown in FIG. 21A are added and divided by two. As can be seen from FIGS. 21A and 21B, it is possible to acquire time-series data without loss even using the measurement sequence of the second embodiment shown in FIG. Looking at the waveform of the result of the synchronous addition in FIG. 21B, the waveform at the time of each measurement in FIG. 20 is smooth, and the advantages of the synchronous addition can be understood from this.

  FIG. 18 is an example in which the time period between the task period and the rest period in the data sampling period is set such that the rest period is 2 with respect to 1 of the task period. Needless to say, the distribution may be set to 1. By doing so, the task period and the rest period can be made equal throughout the measurement on the A-side and the B-side, so that there is an advantage that the subject can easily cope with the repetition of the task.

  Next, a data sampling method according to the second embodiment will be described in detail. First, referring to FIG. 14, the measurement data is obtained by sampling the output of the photodetector 1-6 at a predetermined cycle and performing analog-digital conversion to obtain detection data. In a sense, it has been described that the data can be considered as continuous data. However, here, the description will be made focusing on the sampling timing.

FIG. 22 is a diagram illustrating an example of a data sampling method according to the second embodiment. This is based on the measurement sequence shown in FIG. The solid lines 22A and 22B in FIG. 22 indicate the respective task periods and rest periods on the A and B planes in the measurement sequence shown in FIG. 18 and the light source blinking status on each plane. Here, the horizontal axis indicates the time indicating the progress of the measurement. The rest period and the task period on the side A correspond to the rest period and the task period on the side B, respectively. The dashed-dotted line shown in FIG. 22 indicates the data sampling timing, T _A1 is the data sampling timing period in the rest period on the A-side and the task period, and T _B1 is the rest period and the task period on the B-side. Respectively indicate the data sampling timing periods. In FIG. 22, four dashed lines exist in each of the rest period and the task period, and the dashed lines exist at equal intervals, and the sampling timings on the A and B planes correspond. This indicates that the data of the rest period and the task period are acquired at equal intervals, and four times of data are acquired at the timing corresponding to each period.

FIG. 23 shows a result obtained by synchronously adding the measurement results on the surfaces A and B for each data of each surface based on the sampling timing of the data in the measurement sequence shown in FIG. Here, in order to make the figure easier to understand, the time axis is shown twice as large as that in FIG. _{Here, t 1, t 3, ---} , t 23 is the sampling timing of the sampling period T _A of the A side, the sampling timing of the A and B-sides are compatible, the sampling timing, corresponding to the sampling timing of the sampling period T _B of the intact B plane. Here, for convenience of explanation, subscripts of odd numbers 1 to 23 are given to the reference numbers assigned to the respective sampling points. As a result of the synchronous addition, a result equivalent to that described with reference to FIGS. 21A and 21B is obtained for each of the A-side and the B-side.

  In the second embodiment, since the sampling timings on the planes A and B correspond to each other, the time resolution is not improved even in a topographic image obtained by integrating the timings. However, as described with reference to FIG. Therefore, the spatial resolution is improved. Note that, in the measurement sequence shown in FIG. 18, as described above, since data acquisition does not involve data loss, the data sampling timing shown in FIG. There is no problem of loss.

(Example 3)
FIG. 24 is a diagram showing an example in which the data sampling timing is changed from FIG. As can be easily understood by comparing FIG. 24 with FIG. 22, the measurement sequences of the two are the same, but the sampling period _{TA2 of the} surface A is slightly delayed with respect to the sampling period _TA1 . The sampling period _TB2 is slightly advanced with respect to the sampling period _TB1 . Here, an example is shown in which the time from the sampling period T _A2 to the sampling period T _B2 is changed to be half the sampling period. The control for shifting the timing can be easily realized by performing the control by the computer 1-9.

FIG. 25 shows a result obtained by synchronously adding the measurement results on the surface A and the surface B for each data of each surface based on the data sampling timing in the measurement sequence shown in FIG. Here, in order to make the figure easier to understand, the time axis is shown twice as large as that in FIG. In FIG. 25, the sampling period T _{A2 for the} surface A is indicated by a dashed line, and each sampling timing is indicated by t ₁ , t ₃ ,..., T _{23 as} in FIG. In contrast, the sampling period _{T B2} by B plane indicated by a chain double-dashed line, each sampling _timing, t 0, _{t 2, ---,} indicated by _{t 22.} Here, for convenience of explanation, reference numerals given at the respective sampling points are given subscripts of even numbers from 0 to 22. 22A and 22B are sequences of the task period and the rest period on the A and B sides. As described with reference to FIG. 24, the sampling period T _A2 delays the sampling timing shown in FIG. 22, and the sampling period TB ₂ is advanced in the reverse direction, and the difference between the two becomes half the sampling period. because the way, the timing _t 1, _{t 3} of the sampling of the sampling period _{T A2, ---,} timing _t 0, _{t 2} of the sampling of the intermediate position to the sampling period _{T B2} of _{t 23, ---, t 22} is It becomes the inserted shape.

  As a result, this is equivalent to sampling data at half the time interval of the sampling cycle shown in FIG. 22, and it is possible to improve the time resolution in measurement, and to observe the ever-changing concentration change of the metabolite in the living body. It became possible to grasp in detail.

(Example 4)
Third Embodiment A measuring method for substantially halving the sampling period has been described in the third embodiment. Fourth Embodiment In a fourth embodiment, an equivalent method for halving the sampling period that can be applied to any of the first to third embodiments will be described. In the fourth embodiment, in any of the embodiments, it is proposed that data is interpolated by paying attention to the fact that the data between each adjacent time point at each sampling time point is data at a short sampling interval. Here, a description will be given assuming that the fourth embodiment is applied to the measurement method of the third embodiment.

  FIG. 26A is an enlarged view showing a sampling timing when data is sampled by the measurement sequence shown in FIG. 22, and FIG. 26B is a diagram showing a result of sampling data by the measurement sequence 22 shown in FIG. 4 is a table showing an example of data at each sampling point. Here also, for convenience of explanation, subscripts of odd numbers from 1 to 23 are added to the reference numbers assigned to the respective sampling points.

Measurement sequence shown in FIG. 22, as described earlier, since sampling at regular intervals, the sampling timing of the sampling period T _A of the A plane t _1, t _3, ---, the sampling timing in the t ₂₃ but corresponds to the sampling timing of the sampling period T _B of the intact B plane. Therefore, at each timing, the transmitted light intensity data va1, va3,..., Va23 on the A surface and the transmitted light intensity data vb1, vb3,. In the second embodiment, it has been described that this is synchronously added for each of the A side and the B side to obtain data corresponding to FIG.

However, the third embodiment is a measurement method in which the sampling timing is changed to substantially reduce the sampling period to half. FIG. 27A is an enlarged view showing a sampling timing when data is sampled by the measurement sequence shown in FIG. 24, and FIG. 27B is a diagram showing each result of data sampling by the measurement sequence shown in FIG. It is a table | surface which shows the example of data at the time of sampling. Here, as for the sampling time points of the sampling period _TA2 , similarly to FIG. 23, reference numerals given to the respective sampling time points are given subscript numbers by odd numbers 1-23. On the other hand, the sampling time of the sampling period T _B2, denoted by subscript numbers by an even number of 0-22 in reference numbers assigned to each sampling time point.

As previously mentioned, do not correspond to the data of the sampling time of the sampling period T the sampling time points of the data and the sampling period T _B2 of _A2, the data obtained in each sampling time, as shown in FIG. 27 (B) Although the data at the sampling point in the sampling period _TA2 (data on plane A) is the same as in FIG. 26, there is no data on plane B at this sampling point. On the other hand, data of the sampling time of the sampling period _{T B2} (data B _{surface), t 0, t 2, ---} , vb0 to sampling timing _{t 22,} vb2, ---, _vb22 is obtained. However, there is no A-side data at the time of this sampling.

FIG. 28 is a table showing a state including data interpolated according to the fourth embodiment based on the data of FIG. That is, the sum of the data at the adjacent sampling points is calculated for each of the planes A and B, and a half of the sum is estimated as the data at the unmeasured point between the sampling points. As a result, as it can be seen from Figure 28, at all sampling times (t ₀ and t ₂₃ are excluded), so that the A side, the data of the B surface can be obtained. That is, not only the sampling cycle is substantially reduced to half, but all data on the A and B planes can be obtained at this cycle. Such an estimation operation by interpolation can be easily performed by the computer 1-9.

  In the other embodiments, the sum of the data at adjacent sampling points is calculated, and a half of the sum is estimated as the data at the unmeasured point between the sampling points to substantially reduce the sum. It is clear that not only the sampling period is reduced by half, but also all data can be obtained in this period.

(Other)
In any of the embodiments described above, no specific example of the data sampling interval has been described. In actual brain function measurement, it is appropriate to set the data sampling interval to about 1 second or less. This is because it is generally known that the speed of change in blood volume due to brain activity is several seconds, so if the interval is sufficiently shorter than this time within 1 second, the change in blood volume due to brain activity will occur. This is because it becomes possible to acquire sequence data (in other words, to observe a change). Also, when the sampling interval is within 1 second, no special load is imposed on the operation of the control device 1-8, the electronic computer 1-9, or the signal processing device 1-10.

It is a figure showing the device composition of the living body light measuring device based on the present invention. FIG. 9 is a diagram illustrating a configuration of a conventional biological light measurement device. It is a figure which shows the absorption spectrum of oxyhemoglobin which is a metabolite in a living body, and deoxygenated hemoglobin measured by a living body light measuring device. It is a figure which shows the arrangement | positioning position of the optical fiber connected to the light irradiation device and the optical fiber connected to the photodetector, and the distribution (1) of the sampling point obtained from these arrangement | positioning. It is a figure which shows the structural model of a brain and the propagation path of the light in the brain. It is a figure which shows the arrangement | positioning position of the optical fiber connected to the light irradiation device, and the optical fiber connected to the photodetector, and the distribution (2) of the sampling point obtained from these arrangement | positioning. It is a figure which shows the arrangement | positioning position of the optical fiber connected to the light irradiation device, and the optical fiber connected to the photodetector for the purpose of arrange | positioning a sampling point at high density. FIG. 8 is a diagram illustrating a spatial distribution of sampling points obtained from an arrangement position of an optical fiber connected to a light irradiator and an arrangement position of an optical fiber connected to a photodetector illustrated in FIG. 7. FIG. 10 is a diagram illustrating a sequence related to blinking of the light sources belonging to the probe group A and the probe group B, which is performed when the method of arranging the optical fibers illustrated in FIGS. 7, 8, and 9 is adopted. FIG. 10 is a diagram showing a sequence illustrating a task and a rest execution method in the conventional biological light measurement device. FIG. 7 is a diagram illustrating a case where a light source blink cycle T for data measurement and a sum of a task period and a rest P period satisfy a relationship of a multiple of a natural number n. FIG. 9 is a diagram illustrating an example of a screen that can be used by a user to set a light source switching cycle, a task period, a rest period, and the number of task repetitions. FIG. 13 is a diagram illustrating an example of the ON and OFF states of the light sources of the probe group A and the probe group B during the task period and the rest period under the appropriate settings in FIG. 12. It is a figure which shows the example of the measured value of the change of the transmitted light intensity obtained when the light source is continuously turned on at a certain sampling point and the rest period and the task period are set to the subject every 12 seconds. (A) is a diagram showing the measurement results shown in FIG. 14, and (B) is a diagram showing the measurement results obtained by measuring the prohibition conditions described in FIG. 11 in a manner satisfying the expression (1). (A) is a diagram showing the measurement result shown in FIG. 14 that is the same as FIG. 15 (A), and (B) is a measurement result obtained by measuring the prohibition condition described in FIG. FIG. FIG. 4 is a diagram for more specifically explaining the resolution of data loss. FIG. 9 is a diagram illustrating a measurement sequence according to the second embodiment. It is a figure showing an example of a screen which a user can use for setting a task period, a rest period, and the number of task repetitions. FIG. 20 is a diagram illustrating a transmitted light intensity signal detected at a certain sampling point of the probe group A when the task period = rest period = 12 seconds and the number of repetitions = 2 on the setting screen illustrated in FIG. 19. (A), (B) is a figure explaining the result of having performed synchronous addition with respect to the measurement result of FIG. 9 is a diagram illustrating an example of a data sampling method according to a second embodiment. FIG. 23 is a diagram illustrating a result obtained by synchronously adding the measurement results on the surface A and the surface B for each data of each surface based on the sampling timing of the data in the measurement sequence illustrated in FIG. 22. FIG. 23 is a diagram showing an example in which the data sampling timing is changed from FIG. 22. FIG. 25 is a diagram illustrating the timing of data sampling shown in FIG. 24. (A) is an enlarged view showing the sampling timing when data is sampled by the measurement sequence shown in FIG. 22, and (B) is data at each sampling time point as a result of sampling data by the measurement sequence shown in FIG. It is a table showing an example. (A) is a diagram showing an enlarged sampling timing when data is sampled according to the measurement sequence shown in FIG. 25, and (B) is a data at each sampling time point as a result of sampling data according to the measurement sequence shown in FIG. It is a table showing an example. 28 is a table showing a state including data interpolated according to the fourth embodiment based on the data in FIG.

Explanation of reference numerals

1-1 subject, 1-2 optical fiber holder, 1-3 helmet, 1-4 optical fiber, 1-5 fiber connector, 1-6 photodetector, 1-7 light irradiator 1-8: Control device, 1-9: Computer, 1-10: Signal processing device, 1-11: Transmission cable, 1-12: Speaker, 1-13: Display screen, 1-15: Input device, 2-1 subject, 2-2 optical fiber holder, 2-3 helmet, 2-4 optical fiber, 2-5 optical fiber connector, 2-6 photodetector, 2-7 light irradiation 2-8: Control device, 2-9: Computer, 2-10: Signal processing device, 2-11: Transmission cable, 4-1 to 4-5: Arrangement of optical fibers connected to the light irradiator Position, 4-6 to 4-9: Arrangement position of optical fiber connected to photodetector, 4-10: Sampling point, 5 1 scalp, 5-2 skull, 5-3 cerebrospinal fluid layer, 5-4 gray matter, 5-5 helmet, 5-6 optical fiber holder, 5-7 connected to light irradiator Optical fiber, 5-8: Optical fiber connected to photodetector, 5-9: Propagation path of light emitted from light irradiator and reaching photodetector, 5-10: Change in blood volume due to brain activity Area, 6-1 to 6-5: Position of optical fiber connected to light irradiator, 6-6 to 6-9: Position of optical fiber connected to photodetector, 6-10: Sampling point , 7-1 to 7-5... Positions of optical fibers connected to the light irradiator shown in FIG. 4, 7-6 to 7-10... Of optical fibers connected to the light irradiator shown in FIG. Arrangement positions, 7-11 to 7-14 ... Arrangement positions of optical fibers connected to the photodetectors shown in FIG. 4, 7-15 to 7-18 ... 6, the arrangement positions of the optical fibers connected to the photodetectors shown in FIG. 6, 8-1... Sampling points, 22, 22A and 22B... Each task period on the A and B surfaces in the measurement sequence shown in FIG. The rest period and the blinking state of the light source on each surface, T _A1 , T _A2 ... The data sampling timing period during the rest period and the task period on the A surface, and the T _B1 , T _B2 . Data sampling timing period in the period.

Claims (8)

A plurality of light irradiators, light irradiating means for irradiating the object with light irradiated from the light irradiator, a plurality of light detectors for detecting light irradiating the object and propagating inside the object, Control means for controlling on / off timing of light irradiation of the plurality of light irradiation devices and modulation of light to be irradiated, processing means for processing detection signals of the plurality of light detectors, the light irradiation means and light detector Are arranged in a predetermined relationship and are combined with the helmet for mounting on the subject and the control means and the processing means to provide necessary signals to the control means, and to process the signals of the processing means in an appropriate form. An electronic computer having input means for inputting settings for various controls and a display screen for displaying a signal, and measuring the concentration or change in concentration of metabolites in a living body from measurement data obtained by the photodetector. In the optical measuring device,
The task period to apply a load to the subject and the rest period to remove the load are applied periodically multiple times, and when measuring the sampling timing data of a predetermined sampling cycle in the task period and the rest period, the task A biological light measurement device, wherein the sum of the period and the rest period is set to a relationship that is not an integral multiple of the ON / OFF cycle of light irradiation of the plurality of light irradiation devices.   The plurality of light irradiators, light irradiation means for irradiating the object with light emitted from the light irradiator, and a plurality of light detectors for detecting light irradiated to the object and propagated inside the object A first set and the plurality of light irradiators, light irradiating means for irradiating the object with light radiated from the light irradiator, and a plurality of light irradiators irradiating the object and detecting light transmitted through the inside of the object A second set of photodetectors, wherein the on / off of light irradiation of the first set of light irradiators and the on / off of light irradiation of the second set of light irradiators have opposite phases. The biological light measurement device according to claim 1, wherein:   A light irradiator or light detector of the second pair of light irradiators and light detectors is located at approximately the midpoint of the first pair of light irradiators and light detectors. The biological light measurement device according to claim 2, wherein the device is disposed.   When the user of the living body light measurement device gives an input signal for setting the task period and the rest period to the computer, the time of the sum of the task period and the rest period is the plurality of light irradiators. The biological light measurement device according to any one of claims 1 to 3, wherein the computer displays a warning that the setting is inappropriate when the ON / OFF cycle of the light irradiation is an integral multiple of the ON / OFF period. A plurality of light irradiators, light irradiating means for irradiating the object with light emitted from the light irradiators, and a plurality of light detectors for detecting light irradiated to the object and propagated inside the object A first optical system, a plurality of light irradiators, light irradiating means for irradiating the object with light radiated from the light irradiator, and a plurality of light irradiating the object and detecting light transmitted to the inside of the object A second optical system including a photodetector, a control unit that controls on / off timing of light irradiation of a plurality of light irradiation units of the first and second optical systems and modulation of light to be irradiated, A processing means for processing detection signals of a plurality of light detectors, a helmet for arranging the light irradiating means and the light detectors in a predetermined relationship and attaching to a subject, and being combined with the control means and the processing means; Providing necessary signals to the control means; Along with processing the signal in an appropriate form, it comprises an electronic computer equipped with input means for setting various controls and a display screen for displaying the signal, from the measurement data obtained by the photodetector, In a biological optical measurement device that measures concentration or concentration change,
When turning on the light irradiation of the plurality of light irradiators of the first optical system, the light irradiation of the plurality of light irradiators of the second optical system is turned off, and the plurality of lights of the second optical system are turned off. When the light irradiation of the irradiator is turned on, the light irradiation of the plurality of light irradiators of the first optical system is turned off, and a load is applied to the subject while the light irradiation of each optical system is turned on. A biological light measuring apparatus, wherein a task period for applying a load and a rest period for removing a load are periodically acted a plurality of times, and data is measured at a sampling timing of a predetermined period in the task period and the rest period. .   When turning on the light irradiation of the plurality of light irradiators of the first optical system, the light irradiation of the plurality of light irradiators of the second optical system is turned off, and the plurality of lights of the second optical system are turned off. When the light irradiation of the irradiator is turned on, the light irradiation of the plurality of light irradiators of the first optical system is turned off, and the task period and the rest period during which the light irradiation of each optical system is turned on are set. 6. The living body light measurement device according to claim 5, wherein the data measurement at a predetermined cycle during the period is performed at a sampling timing of a continuous sampling cycle.   When turning on the light irradiation of the plurality of light irradiators of the first optical system, the light irradiation of the plurality of light irradiators of the second optical system is turned off, and the plurality of lights of the second optical system are turned off. When the light irradiation of the irradiator is turned on, the light irradiation of the plurality of light irradiators of the first optical system is turned off, and the task period and the rest period during which the light irradiation of each optical system is turned on are set. In the data measurement at a predetermined cycle in the period, the sampling timing of the sampling cycle of the first optical system is different from the sampling timing of the sampling cycle of the second optical system by about a half cycle of the sampling cycle. The biological light measurement device according to claim 5, wherein   8. The method according to claim 1, wherein, in addition to the measurement data based on the sampling timings in the task period and the rest period, an estimated value that is の of a sum of two measurement data based on adjacent sampling timings is used as the measurement data. The biological light measurement device according to claim 1.

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