JPWO2010050170A1 - Biological light measurement device - Google Patents

Abstract

The biological optical measurement device of the present invention comprises a light irradiation probe / light receiving probe and a probe holding unit for holding these probes in order to irradiate light to the deep and bottom of the human brain stably with good reproducibility, It has the nose pad installed in a probe holding part, It is characterized by the above-mentioned. The light irradiation probe is installed so that light is irradiated approximately vertically between the eyebrows, and light is irradiated after the probe holder is fixed to the living body via the nose pad so that light does not enter the eyeball of the subject. It has a mechanism that starts irradiation of light from the probe toward the living body. It also has a mechanism for preventing the probe from hitting the eyeball.

Description

  The present invention relates to a biological light measurement device for noninvasively measuring cerebral blood dynamics.

  Local hemodynamic changes near the surface of the human brain can be measured non-invasively by optical topography. The optical topography method irradiates a subject with light having a wavelength belonging to the visible to infrared region, detects multiple signals of light that have passed through the subject with the same photodetector, and detects the amount of hemoglobin concentration change (or hemoglobin concentration). This is a method of measuring the change in the product of the optical path length) (see, for example, Patent Document 1). Compared to brain function measurement techniques such as MRI and PET, it has a feature of low restraint on subjects. In clinical settings, language functions and visual functions are measured. In recent years, the importance of measurement of the limbic and emotional systems of the brain has been recognized, and it has become important to measure the depth and bottom of the brain. Regarding the measurement of the deep part and the bottom part of the brain, a method is disclosed in which an optical fiber is inserted from the nostril and light is irradiated and detected in the deep part and the bottom part of the brain through the nasal cavity (for example, see Patent Document 2).

Japanese Unexamined Patent Publication No. 9-019408 Japanese Unexamined Patent Publication No. 7-59782

A. Maki et al., “Spatial and temporal analysis of human motor activity using noninvasive NIR topography,” Medical Physics Vol. 22, 1997-2005 (1995) E. T. Rolls, "The functions of the orbitofrontal cortex," Brain Cogn 55 (1), 11-29 (2004) E. Koechlin, G. Basso, P. Pietrini, S. Panzer and J. Grafman, "The role of the anterior prefrontal cortex in human cognition," Nature 399 (6732), 148-151 (1999)

  However, in the conventional optical topography method (for example, see Patent Document 1 and Non-Patent Document 1), it is known that the reaching depth of the light irradiated to the brain and returning to the scalp is about several centimeters from the scalp. ing. This is because light that has been irradiated from the scalp and reaches the deep part of the brain is scattered and absorbed, attenuated before returning to the scalp, and cannot be detected. Therefore, it is difficult to measure the hemodynamic changes in the deep and bottom of the brain using light, and functional magnetic resonance imaging (fMRI) must be relied upon to measure temporal changes in hemodynamics at the site. I could n’t.

Even when measuring the deep and bottom of the brain with fMRI, especially in the orbital frontal cortex and the marginal system, fMRI has cavities such as the nasal cavity and frontal sinus in the human head. In some cases, false measurements could not be detected due to the change, making it impossible to measure accurately. In other words, in fMRI, the signal is a T2 star (T2 ^* ) weighted signal, and the difference in permeability at the boundary of permeability (or magnetic susceptibility) such as nasal cavity, sinus cavity, ear cavity, tissue / air or tissue / fat May cause distortion of the local magnetic field, resulting in signal degradation and signal position error due to spin phase dispersion, that is, artifacts (false images).

  Even when an optical fiber was inserted into the nasal cavity, it was difficult to accurately irradiate the base of the brain and maintain that state, and it was not easy to measure the same part with good reproducibility. Inserting an optical fiber into the nasal cavity itself is not an easy task and requires skill, so it is difficult to maintain that state after insertion. In order to measure the bottom of the brain, it was necessary to devise a way to stably hold the optical fiber inserted into the nasal cavity. In measuring the function of emotion, it is important not to make the measurement device aware of it in a more natural state, and it is desirable that the device can be easily measured by anyone. Whether the optical fiber is inserted into the nasal cavity or the light is irradiated from outside the nasal cavity, between the eyebrows or from the forehead, the light irradiation position is closer to the eyeball than the conventional optical topography method. When performing such measurements, it is necessary to strengthen safety measures to prevent eye damage caused by light or a probe.

  The objective of this invention is providing the technique for solving the said subject.

  In order to achieve the above object, the living body optical measuring device of the present invention comprises a light irradiation / light receiving probe and a probe holding unit for holding these probes in order to irradiate light to the brain bottom stably with good reproducibility. And a nose pad installed on the probe holder. The light irradiation probe is installed so that light is irradiated approximately vertically between the eyebrows, and light is irradiated after the probe holder is fixed to the living body via the nose pad so that the light does not enter the eyeball of the subject. It has a mechanism that starts irradiation of light from the probe toward the living body. It also has a mechanism for preventing the probe from hitting the eyeball. The light receiving probe is placed between the eyebrows or on the forehead and receives light that has been transmitted and scattered through the bottom of the brain. In the case of irradiating light in the nasal cavity or in the nasal cavity instead of between the eyebrows and forehead, the light irradiation probe has an angle adjustment mechanism, and can irradiate light in an optimal irradiation direction that differs for each subject. The light receiving probe has a similar angle adjustment function.

  According to the present invention, it is possible to stably irradiate light to the deep part and the bottom part of the brain with good reproducibility. In particular, the ability to measure changes in blood dynamics in the limbic system, orbital frontal cortex, pituitary gland, thalamus, and hypothalamus at the bottom of the brain enables the acquisition of biological information that could not be obtained with conventional optical brain functional imaging technology become.

The apparatus block diagram of this invention. The apparatus block diagram which has a mechanical switch as a contact sensor. Control mechanism for limiting probe protrusion. Probe length adjustment mechanism. The block diagram at the time of holding band use. The flowchart from a probe set to laser irradiation. The flowchart of laser irradiation control. Probe placement. The position of the brain base. Example of measurement results. The flowchart of the isolation | separation method of the signal from the multiple brain site | parts (11 fields (orbital frontal field), 10 fields (frontal pole), 46 fields (frontal dorsolateral part), etc.)) by the measurement of multiple sites. The apparatus block diagram using radio | wireless. The apparatus block diagram using an eyeball protection board. The flowchart which shows the use procedure of an eyeball protection board. The apparatus block diagram when performing extranasal light irradiation and the light detection from a forehead. The apparatus block diagram when performing intranasal light irradiation and the light detection from a forehead. The apparatus block diagram when performing light irradiation and light detection in a nasal cavity. Probe angle setting screen. The flowchart at the time of a probe angle setting. The apparatus block diagram which has a visual stimulus presentation part. Signal fluctuation monitor screen. The block diagram at the time of measuring simultaneously a brain bottom part and another brain surface layer site | part. Measurement site selection screen. Simultaneous display of the base of the brain and other brain surface layers. An example in which a subject's internal changes are reflected in the brain function measurement display.

  Embodiments of the present invention will be described below with reference to the drawings.

  FIG. 1 shows an apparatus configuration diagram of the present invention. A probe holder 102 for holding the light irradiation probe 104 and the light receiving probes 103 a to 103 c is attached or fixed to the subject 10 via the nose pad 101 and the ear hook 105. With such a configuration, the reproducibility of the positions of the light irradiation probe 104 and the light receiving probe 103 with respect to the subject 10 is maintained. That is, even if the attachment / detachment is repeated, the positions of the light irradiation probe 104 and the light receiving probe 103 at the time of attachment are substantially the same on the subject 10. The light irradiation probe 104 and the light receiving probes 103a to 103c are optically connected to the light source 201 and the photodetectors 202a to 202c through optical fibers 301a to 301d. The light source 201 and the light detector 202 are electrically connected to the apparatus main body 20, and the apparatus main body 20 includes a control unit (not shown) therein. The control unit includes an analog-to-digital converter for analog-to-digital conversion of an analog signal photoelectrically converted by the photodetector, and a calculation unit for calculating / analyzing the biological information of the subject from the output of the analog-to-digital converter And a storage unit for recording the biological light measurement program and information necessary for the processing and temporarily storing the acquired data and the calculation result, controlling the irradiation timing of the light source 201, and the photodetector 202. Output amplification, analog-to-digital conversion, and calculation of acquired data. The measurement result obtained by the calculation is displayed on the display unit 30, and stimulation for the subject 10 is performed by the stimulus presentation unit 40. The display unit 30 and the stimulus presentation unit 40 are calculated or controlled by the control unit of the apparatus body 20. The display screen of the display unit 30 also has a part of the function of input means for the apparatus main body 20.

  It is desirable that the light irradiation probe 104 and the light receiving probe 103 are in contact with or close to contact with the subject 10 at the time of measurement, projecting from the probe holding unit 102, and placing the probe close to the eyeball When doing so, it is necessary to take measures not to poke the eyeball. For this reason, the light irradiation probe 104 and the light receiving probe 103 are provided with a safety mechanism that can only be protruded after the probe holder 102 is attached to the subject 10. Whether or not the probe holder 102 is set on the subject 10 is detected by the contact sensor in FIG. Here, the mechanical switch 401 (401a to 401c) is used, and is configured to be turned on when in contact. The mechanical switch 401 is provided at a plurality of locations on the probe holding unit 102, and is controlled so that the probe cannot be projected unless all the switches are completely turned on. As the mechanical switch 401, for example, a small micro switch or the like may be used. In addition to the mechanical switch 401, a pressure sensor or an optical sensor may be used as the contact state sensor. As a means for transmitting detection information of these contact sensors, electrical wiring may be passed over the probe holding unit 102, or wireless communication or the like may be used. The contact sensor information is transmitted to the control unit of the apparatus main body 20 or the light irradiation probe 104 / light receiving probe 103.

  An example of a control mechanism for limiting the probe protrusion is shown in FIG. If the mechanical switch 401 is OFF in a non-contact state and ON is in a contact state, in FIG. 3, A1 and B1 are in an OFF state, and A2 and B2 are in an ON state. When the mechanical switch 401 is OFF, the probe support member 112 is opened by the electromagnetic switch as in A1 and B1 and cannot support the probe 111. Therefore, the probe 111 is manually directed toward the subject 10. You can't stick out. When the mechanical switch 401 is ON, the probe support member 112 is closed by the electromagnetic switch as in A2 and B2, and can support the probe 111, and the probe 111 is manually directed toward the subject 10. Can stick out. At this time, for example, the protrusion length of the probe 111 can be adjusted by attaching a key-shaped unevenness to the outside of the probe 111 and the inside of the probe support member 112 as shown in FIG. At the time of manual protrusion, the structure is pushed in against the repulsive force of the compression spring 113. When the mechanical switch 401 is turned OFF, the probe support member 112 is electromagnetically removed, and the probe 111 is pulled back again by the force of the compression spring 113. As a result, even when the probe holder 102 is suddenly displaced due to the movement of the subject 10 during laser irradiation from the probe support member 112 and the mechanical switch 401 is turned off (non-contact state), It is possible to avoid a state in which 111 pokes the eyeball or the like of the subject 10. Further, when the mechanical switch 401 is turned OFF, laser irradiation is stopped even during measurement, and laser light can be prevented from entering the eyeball of the subject 10 unintentionally. Can keep. That is, the mechanical switch 401 is also used for stopping laser irradiation in an emergency. The opening / closing control of the probe support member 112 has been described on the assumption that it is performed by an electromagnetic switch using an electromagnet or the like. It is also possible to control so that 112 is opened and closed by the electromagnetic switch only when the mechanical switch 401 is in the ON state.

  Regarding the protrusion length adjustment mechanism of the probe 111, a structure using screws as shown in FIG. 4 is possible in addition to the configuration using the key-shaped irregularities of FIG. FIG. 4 shows an example of the probe length adjustment mechanism. In this case, it is assumed that the probe is placed between the eyebrows and the forehead. A similar configuration can be taken. The optical fiber 301 is fixed inside the bolt-shaped probe 121, and light can be irradiated and received from the tip of the bolt-shaped probe 121. A male screw is cut outside the bolt-shaped probe 121, and a female screw is cut inside the nut-shaped knob 122. The bolt-shaped probe 121 is inserted into the nut-shaped knob 122, and the probe holding portion 102. A through hole is formed at a place where the bolt-shaped probe 121 penetrates. The protruding length of the bolt-shaped probe 121 can be controlled by rotating the nut-shaped knob 122. At this time, the nut-shaped knob 122 is pressed by the nut pressing member 123 so that the position of the nut-shaped knob 122 does not change relative to the probe holding portion 102.

  Although the adjustment of the protruding length of the bolt-shaped probe 121 by rotating the nut-shaped knob 122 is described here, the protruding length adjustment may be performed by fixing the nut-shaped knob and rotating the bolt-shaped probe 121. good. However, in that case, the entire optical fiber rotates, so it is necessary to consider the effect of twisting on the optical fiber. Further, the electromagnetic switch described in FIG. 3 is combined, and for example, the nut-like knob 122 is disassembled by cutting or the like, and the opening diameter is changed by the electromagnetic switch as in the probe support member 112 in FIG. Thus, the same safety mechanism as in FIG. 3 can be realized.

  In the present embodiment, the description has been made assuming that one light irradiation probe 104 and three light receiving probes 103 are provided. However, the present invention is not limited to this configuration, and a configuration in which the positions of the light irradiation probe 104 and the light receiving probe 103 are interchanged is described. The above object can be achieved even with a configuration in which the number of probes is changed. The probe holding portion 102 can take various shapes including a frame type as shown in FIG. FIG. 5 shows a configuration having the holding band 131. A holding band 131 is connected to or integrated with the probe holding unit 102 and fixed to the subject 10. In addition, various types such as a goggle type, a sun visor type, and a mask type are possible, and equivalent measurements can be performed.

FIG. 6 shows a flowchart from probe setting to laser irradiation.
(S601) The probe holder 102 is attached to the subject 10 (the mechanical switch 401 is turned on).
(S602) The light irradiation probe 104 and the light receiving probe 103 are pushed in, brought into contact with the subject 10 and fixed.
(S603) Laser irradiation is started.

Laser irradiation is performed after the probe holder 102 is attached to the subject 10 as in this flow. Only when the probe holder 102 is attached to the subject 10 and the contact state is confirmed by the mechanical switch 401, laser irradiation is possible. A part or all of the flow of FIG. 6 may be automatically performed. Next, FIG. 7 shows a flowchart of laser irradiation control after the start of laser irradiation.
(S701) Start of laser irradiation.
(S702) Judgment whether the probe mounting sensor is ON (mechanical switch 401 is ON).
(S703) Judgment whether the measurement is completed.
(S704) At the end of measurement (when a measurement end command is received) or when the probe mounting sensor is turned off (the probe is detached from the subject 10), the laser irradiation ends.

  Next, a schematic diagram of probe placement / measurement positions is shown in FIG. One light source 201 (including three wavelengths) is provided, and the light irradiation probe 104 is disposed between the eyebrows, and is connected by an optical fiber therebetween. As shown in FIG. 1, a total of three light receiving probes 103 are arranged several millimeters above the left and right eyebrows and below the center of the forehead, and are optically connected to the photodetector 202 by an optical fiber. A laser diode with three wavelengths of 678, 750, and 830 nm was used as the light source. Subject 10 was a healthy woman.

  The task needs to be a task that induces emotional changes as a stimulus to activate the orbital frontal cortex. It is known that the orbital frontal cortex is related to the emotional system and reward system (see Rolls, Brain Cogn., 2004, Non-Patent Document 2). FIG. 9 shows the location of the orbital frontal area located at the base of the brain. FIG. 9 shows an example of incident / detection positions of incident light 501 and detection light 502 for measuring the brain base 500 with light.

  The experiment described here is a configuration in which light is incident from between the eyebrows and the light is detected from the forehead. The authors' task is to display food on a display, see it, photographs, especially to see past photographs related to the subject 10, and mental arithmetic. Changes in hemodynamics were measured. The measurement principle of hemodynamic changes is a method of calculating the amount of change in the product of hemoglobin concentration and optical path length (here, this is defined as hemoglobin concentration length) using multiple wavelengths near 800 nm. Using. The analysis method of the hemodynamic change is described in detail in Patent Document 1, Non-Patent Document 1, and the like. Here, a past photograph related to the subject 10 such as a human face photograph was taken as a subject. The measurement result of channel 2 (ch2) in the probe arrangement of FIG. 8 is shown in FIG. A total of 40 seconds of 15 seconds (landscape photo), 10 seconds (face photo), and 15 seconds (landscape photo) was taken as one block, and this was repeated 10 blocks, and the averaging process was performed.

  In FIG. 10, the oxygenated hemoglobin concentration length change (oxy-Hb) increases during the task period in which the facial photograph is presented, and the deoxygenated hemoglobin concentration length change (deoxy-Hb) also slightly increases. Since the subject of photography is thought to affect the emotion of the subject 10, it is expected that the orbital frontal area located at the base of the brain is activated. Therefore, a part of the signal obtained in FIG. 10 is considered to be derived from the orbital front.

  In fact, the results obtained with ch1 and ch3 were different from the results obtained with ch2, and the effects of limited prefrontal activity were observed. For comparison of brain activity, when subject 10 performed mental arithmetic to activate 10 or 46 areas of Broadman in the prefrontal cortex, the signal synchronized with the task was weak in ch2, In ch3, a large task synchronization signal of oxygenated hemoglobin was obtained. This suggests that changes in the measurement site can separate the activity of the orbital frontal cortex (related to emotion) and the activity of the dorsolateral area of the frontal cortex (related to working memory use).

  Anatomically, the orbital forehead is located in 11 areas of Broadman in the prefrontal area, behind 10 areas of Broadman, so when light is applied to the orbital frontal area from the scalp or between the eyebrows There is a high possibility of simultaneously measuring 10 fields of Broadman or 46 fields of Broadman. Therefore, it is meaningful if a signal derived from the orbital frontal region and a signal derived from other prefrontal cortex can be separated by measuring and calculating a plurality of sites. As described in Non-Patent Document 3, etc., 10 fields of Broadman have a working memory integration function. Number memory, 2. Language tasks, 3. It is a part that works when a task called a branching task is performed, in which other tasks are performed while maintaining memory in a working memory, such as a series of tasks of calculation using previously stored numbers. Therefore, it is possible to extract the activities of 10 fields of Broadman by carrying out the control task well. Similarly, it is considered possible to extract the activities of 11 areas (near the orbitofrontal area) of Broadman related to emotion by performing appropriate control tasks and calculating the measurement results of a plurality of parts.

FIG. 11 is a flowchart of a method for separating signals from a plurality of brain regions (Broadman's 11 fields (orbital frontal field), 10 fields (frontal pole), 46 fields (frontal dorsolateral part), etc.)) Indicates. In this flow, when the overlap signal from two brain regions at each measurement point is separated, if the signal of one brain region has already been separately measured separately, each measurement point of the other signal is measured. The distribution in is separated. The signal separation method will be described in detail below.
(S1101) A plurality of brain regions to be separated are selected. These brain parts are set, for example, as A region: frontal pole and B region: orbital frontal area.
(S1102) A measurement point (light source / detector pair) is placed near the A area and the B area, and the measurement points are set to ch1, ch2,. The signals obtained from these measurement points are assumed to be dominated by signals from the A region and / or the B region. In other words, the signal change at each measurement point due to activation of other areas is ignored.
(S1103) A task for mainly activating the area A is performed and measurement is performed (task α). For example, a branching task for performing calculations during storage is performed. At this time, data obtained at the measurement point ch1 when task α is executed is expressed as D (ch1, α) or the like.
(S1104) A control task that does not activate area A is performed (task α '). For example, let's assume a dual task of continuously storing and calculating.
(S1105) The difference (D (ch1, α) −D (ch1, α ′)) and the like are calculated and set as the activity value of the area A at the measurement point ch1. Similarly, the activity value (A (ch1), A (ch2),...) Of area A at each measurement point is calculated.
(S1106) The activity value distribution of the A area at each measurement point is displayed with a numerical value or a color.
(S1107) The first task (task β1) that mainly activates the B region is caused to perform measurement. For example, the visual task is a photograph of a friend or family member of the subject 10.
(S1108) A second task (task β2) that mainly activates the B region is caused to perform measurement. For example, it is assumed that the subject 10 has a visual task with a photograph of a favorite food.
(S1109) The following simultaneous equations are calculated, and variables B (ch1), B (ch2), B (ch3), ka (β1), ka (β2), kb (β1), kb (β2) are obtained (measurement) When the point is 3 points). When the number of measurement points is 4 or more, obtain by the least square method.
Formula 1. D (ch1, β1) = ka (β1) × A (ch1) + kb (β1) × B (ch1)
Formula 2. D (ch2, β1) = ka (β1) × A (ch2) + kb (β1) × B (ch2)
Formula 3. D (ch3, β1) = ka (β1) × A (ch3) + kb (β1) × B (ch3)
Formula 4. D (ch1, β2) = ka (β2) × A (ch1) + kb (β2) × B (ch1)
Formula 5. D (ch2, β2) = ka (β2) x A (ch2) + kb (β2) x B (ch2)
Formula 6. D (ch3, β2) = ka (β2) x A (ch3) + kb (β2) x B (ch3)
Formula 7. kb (β1) = 1
Here, D is the measured value, and A is the activity value of the A area obtained in (S1105). Since the equation is 7 for variable 7, the variable can be obtained. For example, the difference between the average values of oxy-Hb during the stimulation period and during the non-stimulation period may be used as the calculation method of the measurement value.

  It seems that region A is also active by task β1 and task β2, and the contribution of the activity to the signal is unknown, but the contribution rate of the signal change to each measurement point is considered to be unchanged for each task. Therefore, by using the A area activity value obtained in (S1105) as the contribution rate from each area of the brain to a specific measurement point, the influence of the A area activity is eliminated, and the B area activity at each measurement point. The value can be determined. In order to determine the coefficients ka and kb and the activity value of the B region, two or more tasks for activating the B region are required, and three or more measurement points are required. Here, it is assumed that the B region active in task β1 and task β2 is the same region.

  In addition to the method described here, signals from two or more brain regions may be separately measured using principal component analysis or independent component analysis.

  Thus, if the orbital frontal area known to be related to the emotional system / reward system (see Rolls, Brain Cogn., 2004, Non-Patent Document 2) can be measured non-invasively, it can be used to monitor human emotional changes. It can be applied and contributes to the elucidation of emotional and reward functions in the human cerebral cortex, which is very meaningful.

  As an actual measurement example, in addition to the above, the activity of the orbital frontal region in the gustatory task is measured, and the change in the mood state of the driver is monitored by an attempt to measure the preference from the signal change and the measurement during driving of the passenger car. , It can be used for various feedbacks to the driver according to the state. There is a possibility that it can be used for the driver to call attention when the mood is unstable, to limit the speed in an irritated state, or to determine the mood state in combination with vehicle speed / acceleration information. is there.

  In addition, if the hypothalamus can be measured in the brain base, the hypothalamus is the center of human instinctive behavior including sleep. By measuring the hemodynamic changes around the hypothalamus during sleep, Can contribute to the elucidation of activities. In addition, because the hypothalamus regulates sympathetic and parasympathetic functions, these abnormalities may be detected early. Furthermore, the ability to measure the pituitary gland, which is an endocrine organ that secretes many hormones, is thought to be helpful in diagnosing diseases related to these hormone secretions.

  In addition, this apparatus may be configured to be installed in eyeglasses worn by the subject. When the glasses worn by the subject have a nose pad, the nose pad 101 of the present apparatus can be omitted. In this case, the present apparatus is configured to have a spectacle connecting portion for fixing to the spectacles instead of the nose pad 101. In addition, although the glasses worn by the subject have been described here, the glasses are not limited to glasses and may be goggles.

  In the living body light measurement apparatus of the first embodiment, the optical fiber 301 is eliminated, and the apparatus main body 20, the light source 201, and the photodetector 202 shown in FIG. is there. In FIG. 12, the light source 201 and the photodetector 202 in the wireless control device 151 are directly connected to the light irradiation probe 104 and the direct light receiving probe 103, respectively. The wireless control device 151 includes a wireless device, a circuit for driving the light source 201, an amplifier for amplifying the photocurrent from the photodetector 202 and converting it to a voltage, an analog-digital conversion circuit, and a battery. Yes. Data can be transmitted from the wireless control device 151 to the remote control device 150 wirelessly. The remote control device 150 may be a computer having a wireless device, and may include a display that displays obtained data and information of the subject 10. By using wireless, the restraint of movement on the subject 10 is reduced, and measurement in a more natural state is possible. In addition, the optical fiber 301 does not block the field of view of the subject 10, and it is possible to give a visual stimulus to the subject 10 without narrowing the field of view of the subject 10.

FIG. 13 shows a configuration in which the eyeball is protected by the eyeball protection plate 191 in the living body light measurement apparatus of the first embodiment until just before the start of measurement. The eye protection plate 191 is a slide type filter. This is to prevent the light from the light irradiation probe and the light irradiation probe / light receiving probe from hitting the eyeball. The eye protection plate 191 is slidable and can be removed. After the probe set is completed, the eye protection plate 191 can be removed, and measurement can be started after adjusting the probe length. A flowchart showing the procedure for using the eye protection plate 191 is shown in FIG.
(S1401) The probe holder 102 is attached to the subject 10 (the mechanical switch 401 is turned on).
(S1402) The eye protection plate 191 is slid and removed.
(S1403) The light irradiation probe 104 and the light receiving probe 103 are pushed in and brought into contact with the subject 10 and fixed.
(S1404) Laser irradiation is started.
Note that a part or all of this flow may be automatically performed. For example, the sliding-type opening / closing operation of the eyeball protection plate 191 can be realized using an electromagnetic switch or the like that responds to ON / OFF of the mechanical switch 401. Further, regarding the probe pushing in (S1403), it is possible to adopt a configuration in which the probe protrudes only by the spring force by shrinking the spring or the like with a weak force in advance. Laser irradiation can also be realized using electromagnetic switches.

  In the first embodiment, the configuration in which light is irradiated between the eyebrows of the subject 10 has been described, but FIG. 15 illustrates that the light is irradiated into the nasal cavity through the nostril to measure the brain bottom, and the nasal cavity directly below the brain bottom. In this configuration, light is directly applied to the inner mucous membrane. The light can be detected from between the eyebrows, the forehead, or under the nostrils of the subject 10. FIG. 15 shows an example in which light is emitted from the nasal cavity toward the nostril and light detection is performed from the forehead. The optical fiber 301 and the light irradiation probe 104 may be inserted into the nasal cavity as shown in FIG. Further, the light receiving probe 103 or the light receiving optical fiber 301 is also inserted from the same nostril or the other nostril on the left and right sides, so that light can be irradiated and detected only by being inserted into the nose as shown in FIG. You can also. 15 to 17, it is possible to irradiate the orbital frontal cortex (11 fields of Broadman) with high accuracy by directly irradiating the intranasal mucosa directly below the brain bottom. The advantage of this method is that it is less susceptible to the activity of other brain regions (e.g., frontal poles (10 broadman fields) and dorsolateral prefrontal areas (46 broadman fields)). And it is known in anatomy that the skull just below the brain base is very thin, and measurement is possible even if the distance between the light irradiation probe and the light receiving probe is short. A probe angle adjustment mechanism 161 is provided to control the direction of the light irradiation probe or the light receiving probe. For example, the probe angle can be manually adjusted by providing a rotation mechanism and fixing with a screw or the like. Thereby, it becomes possible to set the optimal light irradiation angle or light receiving angle for each subject. Since the light irradiation probe and the light receiving probe are held by the probe holding unit 102 and the probe holding unit 102 is fixed to the subject 10 via the nose pad 101, it is possible to perform stable measurement and measure again. The reproducibility is maintained even when doing so. In particular, in the case of light irradiation from outside the nasal cavity, a lens for narrowing the beam divergence angle may be provided at the tip of the probe in order to suppress the spread of the light from the optical fiber 301 to be less than the diameter of the nostril.

When irradiating light into the nasal cavity through the nostril, the incident angle of light becomes important. In the case of receiving light between the eyebrows or the forehead, if the incident direction is closer to the front side (facial surface side), the light passes through the surface of the face and is not absorbed by the tissue so much. growing. In this case, light is transmitted only through the surface layer of the brain, and the hemoglobin signal intensity is considered to be small. That is, it does not mean that the light detection intensity is high. When the incident direction is closer to the back of the head, the light is incident on the deep brain, and the amount of light detected between the eyebrows or the forehead is small. At this time, the amplitude of blood volume fluctuation due to brain activity is expected to increase, but the detected light quantity decreases, so the signal-to-noise ratio (S / N ratio) decreases. Therefore, when light enters the nasal cavity through the nostril, there is an optimum angle for measuring the brain base in terms of the S / N ratio. The angle varies depending on the site where hemodynamic changes are to be measured. For example, it is expected that there will be a difference between 11 fields in Broadman and 46 fields in Broadman.
Therefore, it is necessary to determine the optimum angle by the apparatus body 20 and set the probe angle to the angle by the probe angle adjustment mechanism 161. Therefore, for example, the probe angle is set as follows. A description will be given using a probe angle setting screen example of the display unit 30 as shown in FIG. First, an optimization (maximization) parameter is selected with a radio button 1801. Here, “detected light quantity” or “hemoglobin (Hb) signal intensity” can be selected. In FIG. 18, “detected light amount (Light amplitude)” is selected. Next, use data is selected with a radio button 1802. Here, “Measure from now” or “Read from database” can be selected. In FIG. 18, “measurement from now” is selected. When “measure from now” is selected, the probe angles are set manually or automatically in order, and a “measure” button 1805 is pressed. After the measurement, the measured value 1803 for each channel is displayed on the screen. When remeasurement is performed, a “remeasurement” button 1804 is pressed. For each measurement, an optimization function is calculated in consideration of the optimization parameter, and an optimum angle determination result is displayed on the optimum angle determination result display unit 1806. When the measurement of the candidate probe angle is completed and the result is stored, a “save” button 1807 is pressed, and when the angle setting is ended as it is, an “OK” button 1808 is pressed. When “Read from database” is selected with the radio button 1802, the measured values of each channel can be obtained by reading the past measurement result of the subject to be measured or by reading the average value in the same age group. The evaluation function is calculated based on the optimization parameter displayed and selected with the radio button 1801, and the result of the optimum angle is displayed on the result display unit 1806. By using a database, it is possible to save the trouble of measurement. As the evaluation function here, for example, an average value of all measurement channels may be used. Also, a weighted sum corresponding to a brain region to be measured with priority in each measurement channel may be used.

FIG. 19 shows a flowchart when setting the probe angle.
(S1901) An optimization parameter is selected (for example, “detection intensity”, “orbital frontal field Hb signal intensity”, etc.).
(S1902) Use data is selected (for example, “measure from now”, “read from database”, etc.).
(S1903) When “Read from database” is selected, the database is read,
(S1904) When “measurement from now” is selected, an initial value of the angle of the probe for irradiation / light reception is set.
(S1905) Measurement is performed (for example, the task for the orbital frontal area and the task for the frontal pole are performed together and detected at a plurality of sites).
(S1906) A signal (for example, orbital frontal area activity) is extracted.
(S1907) Judgment whether all kinds of angles were measured.
(S1908) When not measuring all kinds of angles, the probe is set to the next angle.
(S1909) When the database is read or when all kinds of angles are measured, the angle that takes the maximum value is selected.
(S1910) A result is displayed on a display part.
(S1911) Judgment whether to save the result in the database.
(S1912) When saving the result in the database, executing the saving.
In this flowchart, a part or the whole may be automatically performed by the control unit of the apparatus main body 20. As the probe angle adjusting mechanism 161, a mechanism for automatically adjusting the angle using a small motor or the like is provided, and it is possible to automatically set each angle and repeat the measurement. Also, in this measurement, by measuring all angles, the measurement data at each angle can be analyzed, and a wider range of brain activity distribution can be known.

  In the configuration in which light is irradiated into the nasal cavity through the nostril as in this example, and light is directly applied to the intranasal mucosa just below the brain bottom, the light is directly irradiated to the hypothalamus and pituitary gland of the brain, Biological information can be monitored. The hypothalamus regulates sympathetic nerve function, parasympathetic nerve function, and endocrine function, and is also known to be the center of instinct behavior such as eating and drinking behavior, sleep, and emotional behavior such as anger and anxiety. If biometric information from the hypothalamus can be stably obtained by the present invention, it becomes possible to diagnose diseases related to these functions, measure changes due to aging, and the like. The pituitary gland also regulates endocrine function, and it is known that hypopituitar function causes growth hormone deficiency and thyroid stimulating hormone deficiency, and pituitary tumors press the optic nerve in the brain to reduce vision・ It is known that visual field disturbances and pressure on the hypothalamus can cause mental and consciousness disorders. If it is possible to measure hemodynamic fluctuations in the pituitary gland and monitor it over time according to the present invention, it becomes possible to make early diagnosis of various diseases associated with pituitary function decline. This technique can also be used to monitor hemodynamic changes in the hypothalamus and pituitary gland during surgery. When measuring the hypothalamus or pituitary gland, it may be necessary to insert a probe all the way to the nasal cavity or through the sphenoid sinus. In such a case, an operation by a specialist is necessary, but the advantage of being able to measure deep brain areas that cannot be measured from the head surface during surgery is very great. Since fMRI may not be accurate due to the magnetic susceptibility non-uniformity due to the presence of the nasal cavity, it is an important technique in clinical settings.

  In this embodiment, an optical system such as one or a plurality of concentrators is provided in the nasal cavity or outside the nasal cavity to receive light from a specific location on the intranasal mucosa and receive light from the specific location. It is good also as a structure which enables. In addition, if the light emitted from the fiber is collected with a lens or the like smaller than the diameter of the nostril, and the light is irradiated almost evenly in the nasal cavity, the angle dependence can be reduced without adjusting the angle. It is thought that few measurements are possible. Furthermore, in order to finely adjust the position and angle of light irradiation / detection in the nasal cavity, an observation endoscope or an image fiber may be simultaneously inserted into the nasal cavity to monitor the nasal cavity. The biological light measurement device according to the present invention includes a probe or an image fiber having an endoscope function, so that high accuracy of the light irradiation / detection position can be realized. Since the probe or image fiber having an endoscope function is fixed to the probe holding unit 102 and is stably fixed to the subject 10 by the effect of the nose pad 101, the burden on the doctor who is an operator can be reduced. The position and angle of the light irradiation / light receiving probe can be finely adjusted directly by the robot arm for endoscopic surgery.

  In Examples 1 to 4, it is necessary to present a stimulus to the subject 10 in order to measure the brain activity of the subject 10, but in the measurement device of the present invention, a visual stimulus presented fixed to the probe holding unit 102 is presented. The configuration having the display 171 or the earphone 181 for presenting the auditory stimulus is shown in FIG. FIG. 20 illustrates a case where the probe holding unit 102 has a spectacle frame shape having a nose pad and an ear hook. A visual stimulus presentation display 171 is provided in front of the eyeball, and the visual activity is presented to the subject 10 and simultaneously the brain activity of the subject 10 is measured. Alternatively, the auditory stimulus presentation earphone 181 presents the auditory stimulus to the subject 10 and simultaneously measures the brain activity of the subject 10. Other stimulus presenting means may be provided. When brain activity is measured, it is often necessary to present stimuli. By connecting to a device, efficient measurement is possible. For example, when the visual stimulus presentation display covers the front of the eyeball, it is possible to eliminate most of the effects of other visual stimuli. That is, the viewing angle of the stimulus presenting unit for the subject 10 can be increased. In the case of a normal display, since the viewing angle with respect to the subject 10 is narrow, it is necessary to improve the surrounding environment so that objects other than stimuli do not enter the visual field. In addition, the subject 10 is normally restricted in movement during the presentation of the visual stimulus in the measurement. By using the visual stimulus presentation display 171 of the present invention, this visual stimulus presentation device is fixed relatively stably with respect to the subject 10, so that the subject 10 may move and the visual control. There is no need for special maintenance of the surrounding environment. Therefore, when the probe holding unit 102 of the apparatus of the present invention has the visual stimulus presentation display 171, it is possible to make the brain function measurement more efficient and perform measurement with higher reproducibility. In order to eliminate a visual obstacle to the subject 10, an optical fiber 301 connected to the light emitting probe 104 and the light receiving probe 103 is placed along the probe holding unit 102 from the rear side of the head of the subject 10 to the light source 201 or light. It can be connected to the detector 202 or the apparatus main body 20. Alternatively, a visual obstacle to the subject 10 can be removed by using a wireless system as described in the second embodiment.

  The present embodiment relates to how to display the measurement results in the first to fifth embodiments. Some changes in the signal at the base of the brain, especially the orbital frontal cortex, are thought to reflect emotional changes. Therefore, by displaying the activity value of the orbital frontal area, for example, the moving average value of the oxygenated hemoglobin concentration length change amount, it is possible to monitor the fluctuation of the emotion in real time. Furthermore, by predicting the type of emotion from the task to be caused by the subject 10, it becomes possible to know what kind of emotion the subject 10 has when the blood dynamic fluctuation in the orbital frontal area is large. For example, the emotional index in response to the task of showing food or smelling food represents the magnitude of emotional changes related to appetite or taste. In addition, the emotional index for the task of showing a photograph of a person's face is considered to reflect the strength of the impression of the person, the presence or absence of favor or malice, and the like. Furthermore, the emotional index when stress such as computational load is applied is considered to be emotional change due to stress caused by computational load. Here, an example of a monitor screen of each signal variation on the display unit 30 when a total of three measurement points (ch1, ch2, ch3) and a signal from the frontal pole and a signal from the frontal orbital field are separated is shown. 21. In FIG. 21, the causes of emotional changes (here, Sweetness) (2101), the names of regions A (2102) and B (2103), which are brain regions for signal separation, are respectively the frontopolar areas. ), Orbital frontal area. The graph on the right side of FIG. 21 shows raw data (2108), and the raw data waveform (2109) at each measurement point is displayed together with the stimulus presentation period (2110). The left side of FIG. 21 shows data (2104) obtained by separating signals derived from each brain region. In the upper human picture, the A region activity value at each measurement point at a certain time is displayed in shades of color, and the value at each measurement point is displayed in a color obtained by linear interpolation (2105). Similarly, in the lower human picture, the B region activity value at each measurement point at a certain time is displayed in shades of color, and the value at each measurement point is displayed in a color obtained by linear interpolation ( 2106). The correspondence between each color and the activity value is shown in the color bar (2107). In this case, since it is the activity value of the region B (here, the orbitofrontal cortex) that mainly represents the change in emotion, the change in the region B can be seen when it is desired to see the emotional change. Even at the same position on the head surface, a signal is obtained as a haemodynamic change of the signal changes of multiple brain regions. Therefore, it is necessary to display the activity values separately for each region in this way. , It is very important in examining the effects on specific brain regions. For example, the stimulus itself can be evaluated by giving the subject 10 a stimulus that cannot be predicted what kind of brain activity appears and separating the response signal into signals derived from each brain region. Similarly, the signal derived from each brain region when the subject 10 uses the product 10 is a signal that reflects the feeling of the subject 10 regarding the use of the product, and thus can be used for evaluating the product.

  In this embodiment, when the biological optical measurement device of the present invention is used simultaneously with an optical topography device (for example, Patent Document 1) for measuring the surface layer of the brain, or the biological optical measurement device of the present invention is connected to the brain. This is a case where a light source, a light detector, a light irradiation probe, a light receiving probe and the like having a function of a head-mounted optical topography for measuring the brain surface layer part are further provided in addition to the probe for measuring the bottom part.

  FIG. 22 shows a block diagram when the brain bottom and other brain surface layer sites are simultaneously measured. The “brain surface layer” described here refers to the frontal lobe, temporal lobe, parietal lobe, occipital lobe and the like other than the brain bottom. FIG. 23 shows a selection diagram of measurement parts when measuring the brain surface layer part or the brain bottom part. As shown in Example 1, when extracting the activity of the brain base, it is necessary to separate the activity from the vicinity of the frontal pole (10 areas of Broadman). Will be measured. In FIG. 23, it is possible to select one or both of the brain surface layer part and the brain bottom part on the display screen of the display unit 30 via the input means.

  When both parts are selected, the display unit 30 in FIG. 22 displays the time series measurement data of the brain base (orbital frontal area, etc.) and the time series measurement data of other brain surface layer parts at the same time. The display is controlled by the control unit.

  FIG. 24 shows an example of simultaneous display of the brain bottom and other brain surface layer regions. In FIG. 24, brain surface layer data (2401) in the left and right temporal regions, frontal pole extraction data (2402), and orbital frontal cortex extraction data (2403) are simultaneously displayed. According to the color bar (2404), the change in the concentration length of oxygenated hemoglobin in each measurement channel is represented by black and white shading.

  As a display method, a display control method may be adopted in which acquired time-series data is arranged in the order of measurement channels, or spline interpolation is performed between measurement point data by the control unit based on position information of the measurement points. It is possible to display a two-dimensional map by performing the above-described processing, and it is also possible to display a three-dimensional solid. These data may be projected and displayed on measurement data including image data by MRI, X-ray CT or the like, or average data of a plurality of human MRI and X-ray CT data.

  When measuring both the brain surface layer and the brain bottom, it is possible to evaluate the data of the brain surface using the data of the brain bottom. In normal optical brain function measurement, it is desirable to carry out measurement in a state where there is no influence of the subject's internal changes (in this case, emotion, concentration, motivation, etc.) or those changes are as small as possible. The reason is that the magnitude of the hemodynamic fluctuation for the same stimulus may change due to the subject's internal changes such as increased concentration. Internal changes in the subject's emotion, concentration, motivation, and the like are monitored by measuring the brain base (orbital frontal cortex) that can be measured by the biological optical measurement device of the present invention.

  FIG. 25 shows an example in which the internal changes of the subject are reflected in the display of the brain function measurement. This is an example of simultaneous measurement of the visual cortex and the orbital frontal cortex. The horizontal axis of the graph is time [sec], and the vertical axis is the oxygenated hemoglobin concentration length change [mM · mm]. Representative measurement point data (2501) of the visual cortex and representative measurement point data (2502) of the orbital frontal area are displayed. Also, the calculation result (2503) calculated by the control unit using these data can be displayed on the same screen. Here, the first derivative of the data obtained by measuring the orbital frontal cortex is obtained, and that value is used as an evaluation value of the subject's internal change. When the first derivative of the orbital frontal cortex is positive (or, for example, 0.1 or more) Is used to display the measurement data of the visual cortex using a thick black line and a thick white line when the first derivative is negative (or less than -0.1, for example).

  Therefore, the waveform matches the measurement data of the visual cortex displayed on the top graph. This display makes it possible to grasp changes (internal changes) in the emotion, concentration, motivation, etc. of the subject at each time when the visual cortex is measured. For example, in this example, visual cortex data in a state without a thick line (when the first derivative is 0 or close to 0, that is, when the internal change is small), the visual cortex data is not affected by the internal change. It is data. By controlling to bring about a visual change (color coding, etc.) in this way, it becomes easier to grasp changes (internal changes) in the subject's emotion, concentration, motivation, and the like.

  By using this method, if necessary, the control unit determines that the data includes a large amount of the influence of the internal change when the primary differential value is equal to or greater than a predetermined threshold, and determines the influence of the internal change. It can be said that a lot of data is removed. Even if this calculation method is not used, the effect of the internal changes of the subject on the blood dynamics in the brain surface layer can be evaluated by displaying the calculation results such as simply subtracting orbital frontal cortex data. You may be able to do it. Here, an example of the visual cortex is shown, but other brain surface layers may be used.

  Conventionally, the subjective mood state during measurement was grasped by conducting a questionnaire to the subjects before or after brain function measurement, but the fluctuation of the mood state at each time could not be grasped. By using the present invention, it is possible to monitor emotional changes during brain function measurement in the surface layer of the brain in real time, and it is possible to measure brain function more accurately after grasping the change in the mood state of the subject. It becomes.

  In this example, it is assumed that hemodynamic fluctuations in the surface layer of the brain are affected by the internal changes of the subject, but in reality, internal changes such as emotions and motivations and fluctuations in cerebral hemodynamics are assumed. Are considered to be in an interactive relationship. For example, it may be possible to induce internal changes in the subject, such as increased or decreased motivation, depending on the type of task to be given to the subject and the magnitude of the load. Tasks performed by the subject (stimulations presented to the subject) by performing correlation analysis using the first derivative of the brain bottom data or brain surface data and brain surface layer data, analysis of the phase difference of each signal, etc. in the control unit ) And emotional changes can be visually displayed and evaluated.

  According to the present invention, in a brain blood volume measurement device using light, it becomes possible to stably irradiate light to the deep brain / bottom with good reproducibility, and the deep brain / bottom brain reflecting human emotional changes and the like. Changes in blood volume can be measured.

10: Subject 20: Device main body 30: Display unit 40: Stimulus presentation unit 101: Nose pad 102: Probe holding units 103a to 103c: Light receiving probe 104: Light irradiation probe 105: Ear hook 111: Probe 112: Probe support member 113: Compression spring 121: Bolt-shaped probe 122: Nut-shaped knob 123: Nut holding member 131: Holding band 150: Remote control device 151: Wireless control device 161: Probe angle adjustment mechanism 171: Visual stimulus presentation display 181: Auditory stimulus presentation Earphone 191: Eyeball protection plate 201: Light sources 202 a to 202 c: Photo detectors 301 a to 301 d: Optical fibers 401 a to 401 c: Mechanical switches (contact sensors)
500: Brain floor 501: Incident light 502: Detection light 1801: Radio button 1802: Radio button 1803: Measurement value 1804 in each channel: “Re-measurement” button 1805: “Measurement” button 1806: Optimal angle determination result display unit 1807 : “Save” button 1808: “OK” button 2101: Cause input of emotion change (eg, sweetness)
2102: Name of region A (eg, frontal pole)
2103: Name of region B (eg, orbital frontal area)
2104: Area separation data 2105: Activity value at each measurement point in area A 2106: Activity value at each measurement point in area B 2107: Color bar 2108 indicating activity value: Measurement raw data 2109: Raw data waveform 2110 at measurement point: Stimulus period 2401: Brain surface layer data 2402 in left and right temporal regions 2402: Frontal pole extraction data 2403: Orbital frontal area extraction data 2404: Color bar 2501: Visual cortex representative measurement point data 2502: Orbital frontal cortex Data 2503: calculation result.

Claims (22)

One or more light sources;
One or more light irradiation probes for irradiating the subject with light from the one or more light sources;
One or more light-receiving probes for receiving light emitted from the one or more light-irradiating probes and propagated or reflected from the subject;
One or more photodetectors for photoelectrically converting light received by the one or more light receiving probes;
A probe holding unit for holding the one or more light irradiation probes and the one or more light receiving probes;
A living body optical measurement device comprising holding means for supporting the probe holding unit in the nose of the subject. An analog-to-digital converter for analog-to-digital conversion of the analog signal photoelectrically converted by the one or more photodetectors;
A calculation unit for calculating and analyzing the biological information of the subject from the output of the analog-digital converter;
A storage unit for temporarily storing a calculation result by the calculation unit;
The living body light measurement apparatus according to claim 1, further comprising a display unit that displays a calculation result of the calculation unit. The one or more light-emitting probes, or the one or more light-receiving probes,
Installed in the subject's nasal cavity to irradiate or detect light in the subject's nasal cavity;
Or placed outside the nasal cavity of the subject to irradiate light into the nasal cavity through the nostrils or to detect light from within the nasal cavity, even if not in the nasal cavity,
The probe holding unit includes a probe angle adjusting unit for adjusting a light irradiation direction or a light detection direction of the one or a plurality of light irradiation probes or the one or a plurality of light receiving probes. The biological light measurement device according to claim 1.   The biological light measurement apparatus according to claim 2, wherein at least one wireless communication unit is used as a data communication unit between the analog-digital converter and the display unit.   The biological light measurement apparatus according to claim 2, wherein the one or more light sources are LEDs or semiconductor lasers.   The biological light measurement apparatus according to claim 1, wherein the one or more light irradiation probes are installed below the one or more light receiving probes.   An optical waveguide is provided between the one or more light sources and the one or more light irradiation probes, or between the one or more photodetectors and the one or more light receiving probes. The living body light measuring device according to claim 1, wherein the living body light measuring device is provided.   The living body optical measurement device according to claim 1, wherein the optical waveguide is an optical fiber.   The living body light measurement apparatus according to claim 1, wherein the probe holding portion is a spectacle frame type, a band type, a sun visor type, a hat type, or an adhesive seal type.   The living body optical measurement device according to claim 1, wherein the probe holding portion has an ear hook.   The probe holding unit is a probe in which the one or more light irradiation probes or the one or more light receiving probes are in contact with or close to contact with the subject's skin approximately perpendicularly. The living body light measuring device according to claim 1, further comprising an insertion port.   The living body optical measurement according to claim 1, further comprising a distance adjusting mechanism for adjusting a distance between the one or more light irradiation probes or the one or more light receiving probes and the subject. apparatus.   The living body light measurement apparatus according to claim 1, further comprising an installation state sensor for determining an installation state of the probe holding unit on the subject.   The biological light measurement apparatus according to claim 1, wherein the installation state sensor is a pressure sensor, an optical sensor, or a mechanical switch.   The living body light measurement apparatus according to claim 11, further comprising a mechanism for electromagnetically changing an opening diameter of the probe insertion opening.   The living body light measuring apparatus according to claim 1, further comprising a stimulus presenting unit for presenting a stimulus to the subject.   17. The biological light measurement apparatus according to claim 16, wherein the stimulus presenting means is a sound generator such as a display for presenting an image to the subject or an earphone for presenting sound. The computing unit separates and identifies biological information generated from one or more brain regions of the subject,
The biological light measurement device according to claim 2, wherein the display unit separately displays a signal from each brain region.   19. The biological optical measurement according to claim 18, wherein there are three or more measurement positions which are substantially midpoints between the one or more light irradiation probes and the one or more light receiving probes. apparatus. The one or more light emitting probes, or the one or more light receiving probes;
Between the subject,
The living body light measuring device according to claim 1, comprising one or a plurality of concentrators.   19. The biological optical measurement device according to claim 18, wherein the probe holding unit has a removable protective plate for protecting the eyeball of the subject.   The living body optical measuring device according to claim 3, further comprising a probe fixed to the probe holding unit and having an endoscope function that can be inserted into a nasal cavity, sinus cavity or oral cavity of the subject.

Images