WO1997018755A1 - Instrument servant a des mesures optiques sur des corps vivants - Google Patents

Instrument servant a des mesures optiques sur des corps vivants Download PDF

Info

Publication number
WO1997018755A1
WO1997018755A1 PCT/JP1996/003365 JP9603365W WO9718755A1 WO 1997018755 A1 WO1997018755 A1 WO 1997018755A1 JP 9603365 W JP9603365 W JP 9603365W WO 9718755 A1 WO9718755 A1 WO 9718755A1
Authority
WO
WIPO (PCT)
Prior art keywords
light
irradiation
positions
detection
measurement
Prior art date
Application number
PCT/JP1996/003365
Other languages
English (en)
Japanese (ja)
Inventor
Yuichi Yamashita
Atsushi Maki
Hideaki Koizumi
Original Assignee
Hitachi, Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from JP29954295A external-priority patent/JP3588880B2/ja
Priority claimed from JP31199395A external-priority patent/JP3682793B2/ja
Priority claimed from JP31419595A external-priority patent/JP3543453B2/ja
Application filed by Hitachi, Ltd. filed Critical Hitachi, Ltd.
Priority to DE19681107T priority Critical patent/DE19681107B4/de
Priority to CA002210703A priority patent/CA2210703C/fr
Priority to GB9713004A priority patent/GB2311854B/en
Priority to US08/875,081 priority patent/US6240309B1/en
Publication of WO1997018755A1 publication Critical patent/WO1997018755A1/fr
Priority to US10/689,760 priority patent/US7142906B2/en
Priority to US11/371,916 priority patent/US7774047B2/en
Priority to US11/371,918 priority patent/US20060184046A1/en
Priority to US11/371,919 priority patent/US20060184047A1/en

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6814—Head
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14552—Details of sensors specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14553—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/16—Devices for psychotechnics; Testing reaction times ; Devices for evaluating the psychological state
    • A61B5/18—Devices for psychotechnics; Testing reaction times ; Devices for evaluating the psychological state for vehicle drivers or machine operators
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B60—VEHICLES IN GENERAL
    • B60K—ARRANGEMENT OR MOUNTING OF PROPULSION UNITS OR OF TRANSMISSIONS IN VEHICLES; ARRANGEMENT OR MOUNTING OF PLURAL DIVERSE PRIME-MOVERS IN VEHICLES; AUXILIARY DRIVES FOR VEHICLES; INSTRUMENTATION OR DASHBOARDS FOR VEHICLES; ARRANGEMENTS IN CONNECTION WITH COOLING, AIR INTAKE, GAS EXHAUST OR FUEL SUPPLY OF PROPULSION UNITS IN VEHICLES
    • B60K28/00—Safety devices for propulsion-unit control, specially adapted for, or arranged in, vehicles, e.g. preventing fuel supply or ignition in the event of potentially dangerous conditions
    • B60K28/02—Safety devices for propulsion-unit control, specially adapted for, or arranged in, vehicles, e.g. preventing fuel supply or ignition in the event of potentially dangerous conditions responsive to conditions relating to the driver
    • B60K28/06—Safety devices for propulsion-unit control, specially adapted for, or arranged in, vehicles, e.g. preventing fuel supply or ignition in the event of potentially dangerous conditions responsive to conditions relating to the driver responsive to incapacity of driver
    • B60K28/066—Safety devices for propulsion-unit control, specially adapted for, or arranged in, vehicles, e.g. preventing fuel supply or ignition in the event of potentially dangerous conditions responsive to conditions relating to the driver responsive to incapacity of driver actuating a signalling device
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4738—Diffuse reflection, e.g. also for testing fluids, fibrous materials
    • G01N21/474—Details of optical heads therefor, e.g. using optical fibres
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0233—Special features of optical sensors or probes classified in A61B5/00
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0233—Special features of optical sensors or probes classified in A61B5/00
    • A61B2562/0242—Special features of optical sensors or probes classified in A61B5/00 for varying or adjusting the optical path length in the tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/04—Arrangements of multiple sensors of the same type
    • A61B2562/046—Arrangements of multiple sensors of the same type in a matrix array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7253—Details of waveform analysis characterised by using transforms
    • A61B5/7257—Details of waveform analysis characterised by using transforms using Fourier transforms
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4738—Diffuse reflection, e.g. also for testing fluids, fibrous materials
    • G01N21/474—Details of optical heads therefor, e.g. using optical fibres
    • G01N2021/4742—Details of optical heads therefor, e.g. using optical fibres comprising optical fibres

Definitions

  • the present invention relates to an apparatus for measuring information inside a living body using light.
  • the development of a technology that can easily measure information inside a living body without harming the living body is expected in fields such as clinical medicine and brain science.
  • brain diseases such as cerebral infarction and intracerebral hemorrhage
  • measurement of higher brain functions such as thinking, language and movement.
  • the measurement target is not limited to the head, but also includes preventive diagnosis for heart diseases such as myocardial infarction in the chest and visceral diseases such as kidney and liver damage in the abdomen.
  • optical metrology is very promising.
  • the first reason The normal and abnormal organs in the living body, and the activation of the brain for higher brain functions are closely related to oxygen metabolism and blood circulation in the living body.
  • the oxygen metabolism and blood circulation, certain dyes in biological corresponds to the concentration of the dye concentration, absorption of light of a wavelength in the infrared region from the visible Because it can be obtained from
  • the second and third reasons that optical measurement technology is effective are that light is easy to handle with an optical fiber and that it does not cause any harm to living organisms when used within the safety standards. No.
  • optical measurement technology has advantages that PET and fMRI do not have in real-time measurement and quantification of dye concentration in living organisms, and is suitable for miniaturization of equipment and simplicity of handling. .
  • the living body is irradiated with light having a wavelength in the visible to infrared region, and the light (reflected light) that is absorbed and scattered in the living body and comes out of the living body again is detected.
  • Japanese Patent Application Laid-Open No. 57-11532, Japanese Patent Application Laid-Open No. 63-260532, Japanese Patent Application Laid-Open No. This is described in, for example, Japanese Patent Application Laid-Open No. 27532/23, Japanese Patent Application Laid-Open No. Hei 5-3-172595, and the like.
  • the above-described conventional biological measurement technique using light can measure only a specific position or a limited narrow area in a living body, and does not consider imaging measurement of a wide space area in the living body.
  • the optical measurement method For imaging measurement in a large space area, light irradiation and light detection at multiple points are required.
  • An example of this multi-point measurement will be briefly described with reference to FIG.
  • light is emitted from three places (irradiation position 1, irradiation position 2, and irradiation position 3) on the subject surface, and reflected light is reflected from three places (detection position 1, detection position 2, and detection position 3) on the subject surface. ) Shows the case of detection.
  • the measurement position In the case of imaging measurement, the measurement position must be specified.
  • the light detected at the detection position 2 includes not only the reflected light of the light irradiated from the irradiation position 2 but also the reflected light of the light irradiated from the irradiation position 1 and the irradiation position 3. Especially, so-called crosstalk occurs. Therefore, only the reflected light of the light irradiated at the irradiation position 2 cannot be separated and detected at the detection position 2, and accurate measurement at the measurement position 2 cannot be performed.
  • an object of the present invention is to provide a biological light measurement technique that enables highly efficient and accurate light measurement in a wide space area within a subject (living body).
  • Another object of the present invention is to enable optical measurement over a large spatial area in a subject.
  • An object of the present invention is to provide a small and easy-to-handle biological optical measurement device.
  • Still another object of the present invention is to provide a multi-channel simultaneous measurement method capable of simultaneously performing optical measurement at a plurality of measurement positions in a subject without crosstalk.
  • Still another object of the present invention is to provide a biological optical measurement device capable of measuring information in a deep part inside a subject with high sensitivity.
  • Still another object of the present invention is to use a biological measurement signal having a high spatial resolution obtained from the above-described biological optical measurement device as an input signal to control various external devices with high accuracy. It is to provide a high biological input device and a high biological control device.
  • light having a wavelength in the visible to infrared region is simultaneously irradiated into the subject from a plurality of irradiation sites on the surface of the subject (living body), passed through the subject, and re-transmitted.
  • a biological optical measurement device for simultaneously detecting light emitted outside the subject at a plurality of detection sites on the surface of the subject and imaging and measuring biological information inside the subject using the detection signals, Irradiation light from the irradiation part is intensity-modulated at a different modulation frequency for each irradiation part, and at the plurality of detection parts, light having a different modulation frequency is detected for each detection part. are doing.
  • the detection light of the specific modulation frequency detected at the specific detection part corresponds to only the irradiation light from the specific irradiation part irradiated with the light of the specific modulation frequency. Therefore, it is possible to obtain biological information at a specific measurement site in the subject that is determined corresponding to the specific irradiation site and the specific detection site without crosstalk. As a result, biological information on a plurality of measurement sites in the subject can be obtained simultaneously and without crosstalk, and multi-channel simultaneous measurement becomes possible. In addition, highly efficient and accurate optical measurement can be performed on a wide spatial area including a plurality of measurement sites in the subject.
  • the light selectively detected at each detection site is converted into another light.
  • the biological information at another measurement part in the subject determined in correspondence with the irradiation part irradiated with the light of the other modulation frequency and the detection part detecting the same can be obtained without crosstalk. be able to.
  • the number of irradiation sites and detection sites required for measurement of a predetermined number of measurement sites can be reduced. Therefore, the number of light sources for light irradiation and the number of detectors for light detection can be reduced, and a compact and easy-to-handle device configuration can be obtained.
  • the present invention it is possible to perform measurements on a plurality of measurement channels formed between a plurality of light irradiation points and a plurality of light detection points simultaneously and without crosstalk.
  • the plurality of pairs of light irradiation points and light detection points are arranged on a circumference surrounding a specific measurement site in the deep part of the subject, and the midpoint position (measurement position) of each pair is determined by this specific measurement site.
  • a biological optical measurement device capable of measuring biological information about a wide spatial region in a subject (living body) with high efficiency, high accuracy, and high spatial resolution can be realized.
  • a biological optical measurement device capable of measuring biological information about a wide spatial region in a subject (living body) with high efficiency, high accuracy, and high spatial resolution.
  • FIG. 1 is a diagram showing a schematic configuration of a biological light measurement device according to a first embodiment of the present invention
  • FIG. 2 is a diagram showing a positional relationship between a light irradiation position, a light detection position, and a measurement position in biological light measurement.
  • FIG. 3 is a diagram showing light propagation in a living body (light scattering body) in living body light measurement.
  • FIG. 4 is a light irradiation position for realizing more efficient living body light measurement according to the present invention. Diagram showing the positional relationship between the light detection position and the measurement position,
  • FIG. 5 is a diagram showing a specific configuration of each optical module in the embodiment shown in FIG. 1, and FIG. 6 is a light irradiation position, a light detection position, and a measurement position on the surface of the subject in the embodiment shown in FIG. Diagram showing the positional relationship between positions,
  • FIG. 7 shows a specific configuration of the lock-in amplifier module in the embodiment shown in FIG. .
  • FIG. 8 is a diagram showing the shape of the probe in the embodiment shown in FIG.
  • FIG. 9 is a diagram showing a specific configuration of the probe in the embodiment shown in FIG. 1
  • FIG. 10 is a diagram showing a configuration of a light source unit in the biological optical measurement device according to the second embodiment of the present invention.
  • FIG. 11 is a diagram showing the specific configuration of the optical modulator in the embodiment shown in FIG. 10, and FIGS. 12, 13, and 14 are diagrams showing the measurement sensitivity distribution and the production sensitivity in the in-vivo measurement according to the conventional technology. Diagram showing the relationship with body depth,
  • FIG. 15 is a diagram showing a schematic configuration of a biological optical measurement device S according to a third embodiment of the present invention.
  • FIG. 16 is another configuration example of the data collection unit in the embodiment shown in FIG. Figure showing
  • FIG. 17 is a diagram showing still another configuration example of the data collection unit in the embodiment shown in FIG.
  • FIG. 18 is a diagram showing still another configuration example of the data collection unit in the embodiment shown in FIG.
  • FIG. 19 is a diagram showing still another configuration example of the data collection unit in the embodiment shown in FIG.
  • FIG. 20 is a diagram showing still another configuration example of the data collection unit in the embodiment shown in FIG.
  • FIG. 21 is a diagram showing another example of the positional relationship between the irradiation optical fiber and the condensing optical fiber in the embodiment shown in FIG. 15,
  • FIG. 22 is a diagram showing still another example of the positional relationship between the irradiation optical fiber and the converging optical fiber in the embodiment shown in FIG.
  • FIG. 23 is a diagram showing still another example of the arrangement relationship between the irradiation optical fiber and the condensing optical fiber in the embodiment shown in FIG.
  • FIG. 24 is a diagram showing a schematic configuration of a living body optical measurement device suitable for measuring deep in-vivo information according to a fourth embodiment of the present invention.
  • FIGS. 25, 26 and 27 are diagrams showing the relationship between the measurement sensitivity distribution and the depth in the living body in the in-vivo measurement using the device S configuration shown in FIG.
  • FIG. 28 is a diagram showing a schematic configuration of a brain function activity measuring device used in a living human power device according to a fifth embodiment of the present invention.
  • FIG. 29 is a diagram showing an example of a change in the concentration of the mog mouth bin into the brain during right finger movement measured by the apparatus configuration shown in FIG.
  • FIG. 30 is a diagram showing an example of a change in the concentration of the mog mouth bin into the brain during the movement of the left finger measured by the device configuration shown in FIG.
  • Fig. 31 is a contour map showing an example of changes in total hemoglobin concentration in the brain during right finger movement measured by the device configuration shown in Fig. 28.
  • Fig. 32 is a contour map showing an example of the change in the total concentration of the hemagglutinating bin in the brain at the time of recalling the language measured by the device configuration shown in Fig. 28.
  • FIG. 33 is a diagram showing a schematic configuration of a biological control device according to a fifth embodiment of the present invention.
  • FIG. 34 is a first example of an arithmetic procedure in the arithmetic device in the embodiment shown in FIG. Flow chart showing
  • FIG. 35 is a flowchart showing a second operation procedure example in the operation device in the embodiment shown in FIG.
  • FIG. 36 is a diagram showing the data structure of learning data used in the second example of the operation procedure shown in FIG.
  • FIG. 37 is a diagram showing a schematic configuration of a biological control device according to a sixth embodiment of the present invention. , The best mode for carrying out the invention
  • optical measurements at a plurality of measurement positions in the subject are performed simultaneously and without crosstalk.
  • a multi-channel simultaneous measurement technique that can be performed is provided.
  • the present invention in order to solve the above-described crosstalk problem, light having a wavelength in the visible to infrared region is simultaneously irradiated into the subject from a plurality of irradiation positions on the surface of the subject (living body).
  • Biological light measurement that simultaneously detects light that passes through the sample and is emitted outside the subject again at multiple detection positions on the surface of the subject, and uses this detection signal to image and measure biological information inside the subject.
  • the modulation frequency of the light radiated into the subject from the plurality of irradiation positions is made different for each irradiation position, and at the plurality of detection positions, the light having the different modulation frequency is different for each detection site. It is configured to selectively separate and detect.
  • the detection light at the detection position 2 includes only the light component emitted from the irradiation position 2 and does not include the light component emitted from the other irradiation positions 3 at all. Therefore, the light with the modulation frequency f 2 selectively detected at the detection position 2 (light passing through the living body) Is a force that includes much in-vivo information at measurement position 2 between irradiation position 2 and detection position 2, and hardly includes in-vivo information at measurement positions 1 and 3. In other words, information about the other measurement positions 1 and 3 is not mixed in the information about the measurement position 2 to be measured at the detection position 2. This is exactly the same for the other detection positions 1 and 3. Thus, measurement without crosstalk can be performed at each measurement position.
  • multiple light beams with different wavelengths are used as the irradiation light to the living body and pass through the living body.
  • the measured light is spectrally measured by wavelength
  • the light of multiple wavelengths can be reflected and scattered by optical filters, diffraction gratings, prisms, and the like. Electrical spectrometry can be performed without using optical spectroscopy with loss.
  • the irradiation frequency from different irradiation positions is also detected at each detection position by changing the modulation frequency of the light selectively detected at each detection position. can do. For example, in FIG.
  • the modulation frequencies of the irradiation light from irradiation positions 1, 2, and 3 are f1, f2, and f3, respectively, the modulation frequency of the detection light at the detection position g2 is f2. If they are matched, only the irradiation light from the irradiation position 2 is selected and detected at the detection position 2. However, if the modulation frequency of the detection light at the detection position 2 is changed to f1 and f3, the irradiation position S Only the irradiation light from 1 and 3 can be selectively detected. The same applies to detection positions 2 and 3. This advantage is related to more efficient light irradiation and detection point arrangement.
  • a specific irradiation position and detection position are exclusively assigned to each measurement position for a plurality of measurement positions, i.e., when there are three measurement positions as shown in Fig. 2, the irradiation position and the detection position Three positions are required for each. So, for example, As shown in Fig.
  • the irradiation position 2 and the detection positions 1 and 2 are alternately arranged in a grid pattern, and the irradiation position 1 is shared by the measurement positions 1 and 4 and the irradiation position 2 is shared by the measurement positions 2 and 3 If the force, force, and detection position 1 can be shared with measurement position 2 and detection position 2 can be shared with measurement positions 3 and 4, the required irradiation position and detection position for a total of 4 measurement positions can be obtained. In two places each. That is, according to the modulation measurement method described above, the modulation frequencies of the irradiation light from the irradiation positions 1 and 2 in FIG. 4 are set to f 1 and f 2, and the modulation frequencies of the detection light at the detection positions 1 and 2 are set.
  • the detection position 1 , 2 can select and measure information about measurement positions 2 and 3, respectively.
  • the number of irradiation positions (and thus the number of light sources associated therewith) and the number of detection positions (and therefore the number of detectors associated therewith) can be greatly reduced, thereby improving system efficiency and reducing the size of the device configuration.
  • the handling can be simplified.
  • FIG. 1 shows a schematic configuration of a biological optical measurement device according to a first embodiment of the present invention.
  • the number of measurement channels (that is, the number of measurement positions [the number of S]) was set to 64, assuming that the inside of the cerebrum was imaged and measured by irradiating and detecting light from the skin of the human head, for example.
  • the device configuration will be described.
  • the light source unit 1 is composed of 16 optical modules 2 (1), 2 (2),... 2 (16). Each optical module is composed of three semiconductor lasers that individually emit light of multiple wavelengths within the visible to infrared wavelength range (for example, three wavelengths of 770 nm, 805 nm, and 830 nm). It is configured. All (48 total) semiconductor lasers included in the light source unit 1 receive modulation signals from the oscillation unit 3 composed of 48 oscillators having different oscillation frequencies, and receive different modulation frequencies. Emit laser light modulated by.
  • Fig. 5 shows the specific configuration inside each optical module.
  • semiconductor lasers 3 (1-a), 3 (1-b), 3 (1-c) and driving circuits 4 (Ia), 4 (1-b), 4 (1-c) is included.
  • the number (1) in parentheses indicates that the element belongs to the optical module of module number 1, and the alphabetic characters (a, b, c) indicate the wavelength, respectively.
  • Drive circuits 4 (1-a), 4 (l ⁇ b), and 4 (1-c) output different modulation frequencies f (Ia) and f (1-b) from the respective oscillators in the oscillator 3.
  • f (1-c) the modulation frequency corresponding to the output laser light from semiconductor lasers 3 (1-a), 3 (1-b), and 3 (1-c) is supplied.
  • the modulation in Output laser beams from the respective semiconductor lasers are individually introduced into the optical fiber 6 via the condenser lens 5.
  • the light introduced into each optical fiber 6 is introduced into one irradiation optical fiber 8-1 via an optical fiber coupler 7.
  • the reflected light from the subject 9 (the light that is absorbed and scattered by passing through the subject and emitted from the subject surface to the outside) is detected at a total of 25 locations on the subject surface. It is taken into the detection optical fibers 10 0-1, 10-2,.
  • FIG. 6 shows an example of the geometric arrangement of the irradiation positions (IP) 1 to 16 and the detection positions (DP) 1 to 25 on the surface of the subject 9.
  • the irradiation position (IP) and the detection position (DP) are alternately arranged in a square lattice.
  • the irradiation position (! P) and the detection position adjacent to each other Assuming that the midpoint of (DP) is the measurement position (MP), in this example, there are 64 combinations of the irradiation position (IP) and the detection position (DP) that are adjacent to each other.
  • the number, that is, the number of measurement channels is 64.
  • the detection light at each irradiation position has information in the cerebrum, It is reported in ⁇ f "PW McCormic;” Intracerebral penetration of infrared light ", J. Neurosurg., Vol.76, pp.315-318, (1992). Therefore, if a total of 64 measurement channels are set in the arrangement shown in FIG. 6, it is possible to measure intracerebral information in a wide area of about 15 cm ⁇ 15 cm as a whole.
  • the reflected light captured by each detection optical fiber 10-1 to 10-25 is a total of 25 photodetectors (for example, photodiodes) 11-1-1, 11-2, ...
  • detection is performed independently for each detection position (that is, for each detection optical fiber).
  • the output electric signal from each photodetector is measured separately by a lock-in amplifier module 12 composed of a plurality of lock-in amplifiers for each modulation frequency corresponding to the irradiation position and the wavelength of the irradiation light.
  • the signal separation method will be described with reference to FIG. 7, taking the detection signal at the detection position (DP) 7 in FIG. 6, that is, the detection signal at the photodetector (photodiode) 11-17 as an example. .
  • the detection position (DP) 7 the light irradiated from the four irradiation positions (1P) 2, 5, and 6 adjacent to it, that is, the measurement positions (MP) 10, 11, 18, 18,
  • the light passing through 19 is targeted for detection.
  • the light detected by the photodetectors 11-17 mainly consists of the modulation frequencies ⁇ ⁇ (1 a), f (1-b) radiated from the irradiation positions (] P) 1, 2, 5, and 6.
  • f (1-c), f (2-a), f (2-b), f (2-c), f (5-a), f (5-b), f (5-c), f (6-a), f (6-b) and f (6-c) are included. Therefore, the output signals of the photodetectors 11 and 17 are used as reference signals for the corresponding modulation frequencies.
  • lock-in amplifier 1 3 In 3 1, since the reference signal frequency is set to f (1-a), the wavelength from the irradiation position (IP) 1 is 7770 nm from the optical signal detected by the photodetector 11. Only the signal components corresponding to the irradiating light (that is, the light whose modulation frequency is f (1-a)) are separated and selected and amplified. That is, the output signal from the lock-in amplifier 13-31 is applied to the light of wavelength 770 nm at the measurement position (MP) 10 existing between the irradiation position (IP) 1 and the detection position (DP) 7. It contains only biological reaction information such as absorption and scattering. Similarly, in other lock-in amplifiers, only light of a specific wavelength irradiated from a specific irradiation position is selectively detected.
  • MP measurement position
  • DP detection position
  • the optical signals detected at other detection positions are also modulated at the specific modulation frequencies determined corresponding to the light irradiation position and the irradiation light wavelength, respectively.
  • the mouth lock-in detection it becomes possible to separately measure the amount of light detected for all measurement positions and the irradiation light wavelength.
  • a total of 19 2 lock-in amplifiers 1 3— 1, 1 3—2, ⁇ ' ⁇ ⁇ 1 3— 19 2 are included.
  • the analog output signals from these 192-channel lock-in amplifiers are converted into digital signals by a 192-channel AZD converter 14, passed through a control unit 18, and recorded in a data recording unit 15. You.
  • these recorded signals are used in the data processing unit 16 by using the detected light amount of three waves at each measurement position, to obtain the oxygen concentration in the oxygenated hemoglobin, the oxygenated hemoglobin concentration, and the oxygenated hemoglobin concentration.
  • the total hemoglobin concentration as a total amount was calculated using the method described in the book, ⁇ Two-Wavelength Spectrophotometry and Its Applications, '' edited by Shodan Shibata et al., Published in 1979 by Kodansha. Ask.
  • the oxygenated hemoglobin concentration, the deoxygenated hemoglobin concentration, and the total hemoglobin concentration determined for each measurement position are displayed on the display unit 17, for example, in topography. Display as an image.
  • the data for displaying the topography image is obtained by, for example, interpolating (for example, linearly interpolating) the densities of the bins at each measurement position between the measurement positions.
  • the operation of each unit of the apparatus described above is controlled by the control unit 18.
  • a helmet or cap-shaped probe 21 as shown in FIG. 8 is used for light irradiation and light detection on the subject (human head).
  • a thermoplastic resin sheet having a thickness of about 3 mm is used as a base material, and a mold is formed in advance with the base material to match the external dimensions in the measurement region of the subject. This is fixedly mounted on the outer surface of the subject with, for example, a rubber cord 22 or the like.
  • Holes are provided in the probe base 23 at a plurality of positions corresponding to the irradiation position of the light on the subject 9 and the detection position of the reflected light from the subject 9, and the optical fiber holder 24 is fixedly mounted in each hole.
  • the optical fiber holder 24 includes a hollow cylindrical holder main body 24, a main body fixing screw 25 and an optical fiber fixing screw 26, and the holder main body 24 is inserted into each hole provided in the probe base 23. Then, the holder main body 23 is fastened and fixed to the probe base 23 with the main body fixing screws 25. Then, an irradiation optical fiber or a detection optical fiber is inserted into the center hole of the holder body 23, and the end of the optical fiber is lightly brought into contact with the surface of the subject 9; Fix it with it.
  • the present invention is not limited to this number of channels.
  • the present embodiment can be easily applied to a so-called optical CT device in which tomography of the inside of a living body is performed using light, and the obtained data is image-processed by a computer.
  • FIG. 10 shows a schematic configuration of a biological light measurement device according to a second embodiment of the present invention.
  • the basic configuration of the measurement system is the same as that of the first embodiment.
  • FIG. 10 shows the configuration of the light source unit 1 in the second embodiment.
  • a light source having a wavelength of 770 nm, for example, a semiconductor laser 31 is driven by a laser drive circuit 41 and emits continuous light without modulation. This light is introduced into the optical fiber 61, and is distributed through the optical fiber coupler 51 to 16 optical fibers 61-1-1 to 61-1-16.
  • Each of these 16 optical fibers includes an optical modulator 71-1 to 71-16 in its path.
  • the configuration of these optical modulators is shown in FIG. 11 using the optical modulator 71-1 as an example.
  • a liquid crystal filter 101 is built in the optical modulator 711, and the liquid crystal filter 101 is periodically turned on and off when a modulation voltage signal is applied from an oscillator in the oscillation unit 3. Is to repeat.
  • a modulation voltage signal having a modulation frequency of f (1 ⁇ a) is applied to the liquid crystal filter 101.
  • the light from the optical fiber 6 1-1 is applied to the liquid crystal filter 101 via the lens 5, and the light transmitted through the liquid crystal filter 1 1 is condensed by the lens 5 to form the optical fiber 8 1-1.
  • the optical modulators 7 1-1 to 7 1 _ 16 have different modulation frequencies, for example, f (1- a ), f (2-a), f (16-a)
  • the LCD filter is turned on and off.
  • a device using a rotary mechanical optical disc may be used in addition to the liquid crystal filter. In this way, the light beams modulated at the different modulation frequencies by the optical modulators 71-1-1 to 71-1-16 are introduced into the optical fibers 81-1 to 81-1-16 and transmitted.
  • light sources of other wavelengths in the light source unit 1 are driven by laser driving circuits 42 and 43, respectively.
  • Output lights from these light sources 32 and 33 are sent to fiber couplers 52 and 53 via optical fibers 6-2 and 6-3, respectively, and 16 optical fibers 62-1 to 16 are respectively provided. It is distributed to 6 2—16, 6 3—1 to 6 3—16.
  • the light distributed to the optical fibers 6 2—1 to 6 2—16, 6 3—1 to 6 3—16 is converted to optical modulators 7 2—1 to 7 2—16,
  • each of the optical modulators 72-1 to 72-16 has a different modulation frequency f (l-b), f (2-b),... F (16-b)
  • the signal is applied and the optical modulator 7 3— 1
  • the modulation signals having different modulation frequencies f (l-c), f (2-c) and f (16-c) are applied to.
  • the light that passed through the optical modulators 7 2—1 to 7 2—16 passed to the optical fibers 8 2—1 to 8 2—16 and the optical modulators 7 3—1 to 7 3—1 16 respectively.
  • the light is respectively introduced into optical fibers 83-1 to 83-16 and transmitted.
  • a total of 48 optical modulators 7 1-1 to 7 1-16, 7 2-1 to 7 2-16 and 7 3-1 to 7 3-16 are individually modulated, Total 4 8 optical fibers 8 1-1 to 8 1-16, 8 2-1 to 8 2-16 and 8 3-1 to 8 3-16 Independently transmitted and modulated respectively
  • a total of 48 types of light having different frequencies are grouped for each wavelength and introduced into one (total of 16) optical fibers in the following way: Optical fiber 8 1 — 1, 8 2-1 and
  • the light transmitted by 83-1 is collectively introduced into one irradiation optical fiber 8-1 via the optical fiber coupler 911.
  • the light transmitted through the optical fibers 8 1-16, 8 2-16 and 8 3-16 is converted into one irradiation optical fiber 8 by the optical fiber coupler 9 1 1 16. Introduced together in 16.
  • 16 types of irradiation optical fibers 8-1 to 8-16 are used to carry out three types of light (48 types in total) with different wavelengths and modulation frequencies.
  • the surface of the subject 9 is irradiated in the same manner as in the example. Note that the method of measuring the reflected light from the subject 9 is the same as in the first embodiment.
  • a biological optical measurement device capable of measuring information in a very small area in a deep city in a subject (living body) with high sensitivity and high resolution.
  • a living body is irradiated with light having a wavelength in the visible to infrared region, and reflected light from a deep region in the living body at a distance of about 10 to 50 mm from the irradiation position is detected, and biological information on the deep region is obtained.
  • a living body optical measuring device is disclosed in, for example, Japanese Patent Application Laid-Open Nos. 63-277038 and 5-30087.
  • Japanese Patent Application Laid-Open Nos. 63-277038 and 5-30087 it is difficult to obtain biological information on a minute region deep inside the living body with sufficient measurement accuracy.
  • the measurement results include information over a wide area in the living body.
  • the spatial characteristics of the detection sensitivity are such that the sensitivity in a shallow part of a living body near the light irradiation position and the light detection position is greater than the sensitivity in a deep part. For this reason, it is difficult to accurately measure a change in the concentration of a light absorbing substance in a deep region in a living body by a method that has been conventionally proposed.
  • the hemodynamic change in a relatively shallow region immediately below the scalp is largely reflected in the measured value for the above-described reason.
  • Figs. 12 to 14 show examples of the results of obtaining the relative sensitivity distribution with respect to the change in the concentration of the light absorbing substance in the living body using the above-mentioned conventional technology.
  • the present invention when irradiating light into the subject from a plurality of light irradiation positions on the subject surface, and condensing and detecting light transmitted through the subject at a plurality of light detection positions on the subject surface,
  • the plurality of light irradiation positions and the plurality of light irradiation positions are so set that the respective light paths of the light (transmitted light) irradiated from each of the plurality of light irradiation positions and transmitted through the subject overlap each other in a desired measurement region in the subject.
  • An arrangement relationship with the plurality of light detection positions is set, and light detection signals at the plurality of light detection positions are arithmetically processed, thereby increasing the detection sensitivity to the optical information in the desired measurement area. (The detection sensitivity for optical information in other areas is relatively reduced.)
  • the biological optical measurement device for deep information measurement inside a subject (living body) is basically for irradiating a plurality of irradiation lights having different wavelengths from a plurality of irradiation positions on the surface of the subject into the subject.
  • a light irradiating means having a plurality of irradiating portions; and a light irradiating means for condensing light (transmitted light) irradiated from each of the plurality of light irradiating positions and transmitted through the subject at a plurality of detecting positions on the surface of the subject.
  • a plurality of collections provided in an arrangement such that the optical paths of the respective lights (transmitted light) emitted from each of the plurality of irradiation units and transmitted through the subject overlap with each other in a predetermined measurement region in the subject.
  • a light condensing means having an optical part; and a plurality of light detectors for detecting light intensities of the respective transmitted lights condensed by the plurality of light condensing parts at each of the plurality of irradiation positions and each of the plurality of wavelengths.
  • the above-mentioned plurality of irradiation lights are subjected to intensity modulation at different modulation frequencies for each irradiation position and each wavelength, and a predetermined modulation frequency is obtained from the transmitted light condensed by each of the condensing sections.
  • a predetermined modulation frequency is obtained from the transmitted light condensed by each of the condensing sections.
  • the transmitted light condensed by each of the condensing sections is separated by a spectroscope for each wavelength, and only the light component intensity-modulated at a predetermined modulation frequency is separated and detected from the separated wavelength components ( By performing lock-in detection, the light intensity of the transmitted light component for each irradiation position and each wavelength may be obtained.
  • the optical information to be measured is a light absorption coefficient in the subject (living body).
  • a photoelectric conversion device that converts transmitted light having a predetermined intensity modulation frequency (or transmitted light having a predetermined wavelength having a predetermined intensity modulation frequency) into a transmitted light intensity signal having the predetermined intensity modulation frequency by photoelectric conversion.
  • the transmitted light intensity signal from the photoelectric conversion unit is transmitted to the AZD conversion unit.
  • Input and obtain a transmitted light intensity signal in the frequency space by Fourier transform, and a signal corresponding to the intensity modulation frequency given for each predetermined light irradiation position or for each predetermined wavelength is sent to the A / D converter.
  • a signal component having a frequency equal to the above-mentioned predetermined reference frequency may be calculated from the transmitted light intensity signal in the frequency space, and this may be used as an intensity signal of the transmitted light component having a predetermined intensity modulation frequency.
  • the plurality of irradiating units and the plurality of condensing units have at least one predetermined diameter centered on a point at which a perpendicular (a straight line perpendicular to the surface of the subject) passing substantially at the center of the predetermined measurement area intersects the surface of the subject.
  • the transmitted light intensity corresponding to the irradiation light for each wavelength from each light irradiation position is detected for each condensing position and each wavelength, and the transmitted light intensity for each wavelength from each light irradiation position is detected.
  • Select the transmitted light intensity for each wavelength from the light irradiation position that is in point symmetry with the condensing position, and select the transmitted light intensity detected on the same circle from the selected transmitted light intensity is performed.
  • the intensity of the transmitted light condensed by the light condensing part set on the circle with the smaller diameter is used as information from the shallow part of the subject, and the intensity is set on the circle with the larger diameter.
  • the transmitted light intensity condensed by the condensing portion is used as information from the deep part of the subject, and the transmitted light intensity is subjected to arithmetic processing. It can be arranged in a shape. In this case, the irradiating section and the condensing section are arranged on the grid points of the respective rows of the square lattice so that the row where the irradiating section is arranged and the row where the condensing section are arranged alternately. It is.
  • the plurality of irradiation units and the plurality of light collection units described above can be arranged in a regular hexagonal lattice.
  • the irradiating section and the condensing section are alternately arranged on each lattice point of the regular hexagonal lattice.
  • Light having a wavelength near 805 nm is used as light to irradiate the subject (living body). Based on the transmitted light intensity, changes in oxyhemoglobin concentration, changes in reduced hemoglobin concentration, and oxyhemoglobin concentration in the living body can be determined. The change in total hemoglobin concentration calculated as the sum of the change and the reduced hemoglobin concentration change is determined, and the total hemoglobin concentration change is calculated. Change over time can be displayed. Still, the total change in the concentration of moglobin may be obtained directly from the transmitted light intensity. In addition, as irradiation light to the inside of the subject (living body), irradiation light of a plurality of wavelengths (at least two wavelengths) in a wavelength range of 700 nm to 110 nm can be used.
  • the change in total hemoglobin concentration, the change in oxyhemoglobin concentration, or the change in reduced hemoglobin concentration, which is calculated as the sum of the change in oxyhemoglobin concentration and the change in reduced hemoglobin concentration, is represented by the color of the line, the type of line, or the line shape, respectively.
  • changes in oxyhemoglobin concentration may be displayed in red or orange
  • changes in reduced hemoglobin may be displayed in blue, indigo or green
  • changes in total hemoglobin concentration may be displayed in black or brown.
  • the images of total hemoglobin concentration change, oxyhemoglobin concentration change, or reduced hemoglobin concentration change calculated as the sum of the oxidized hemoglobin mouth concentration change and the reduced hemoglobin concentration change corresponded to the respective concentration changes. It may be displayed in color or brightness.When the density change is positive, the display is displayed in darker red or higher brightness as the absolute value of the density change value becomes larger, and when the density change is negative, As the absolute value of the value of the density change becomes smaller, the image may be displayed in dark blue or lower luminance.
  • the intensity of transmitted light having a predetermined wavelength detected on the circle is set to the surface of the subject through the center of the circle.
  • the change in the oxyhemoglobin concentration change and the reduction in the mog vine bottle concentration change in a predetermined range region of a predetermined depth in the subject on a perpendicular line perpendicular to the predetermined range or a predetermined range region of a predetermined rotating body having the perpendicular as a rotation axis.
  • the calculation can be performed assuming that the change in total hemoglobin concentration, the change in oxyhemoglobin concentration, or the change in reduced hemoglobin concentration calculated as the sum is reflected.
  • the diameter of the circle can be in the range of 25 mm to 35 mm, and the depth can be in the range of 12 mm to 25 mm. Also, by covering the contact surface of the irradiating section or the condensing section with the object surface with a flexible and highly transmissive member to the irradiation light, the irradiating section or the condensing section is The stimulus given to the subject can be softened.
  • the plurality of irradiation units and the plurality of light collection units are arranged on a circle having a predetermined diameter such that the optical paths of the irradiation light from the plurality of irradiation units in the subject overlap each other,
  • At each condensing part only the transmitted light of the irradiation light from the irradiating part located opposite to it is selectively detected, and the intensity of the transmitted light detected at each condensing part is multiplied to obtain the object surface. It is possible to improve the measurement sensitivity for a region (measurement region) located at a predetermined depth position inside the subject from the center position of the above circle.
  • two types of light having different wavelengths were used as irradiation light for the purpose of measuring changes in oxidized and reduced hemoglobin concentrations in a subject (living body).
  • Light detection positions are set at two locations, respectively. It is easy to further increase the number (wavelength number) of these irradiation lights, light irradiation positions, and light detection positions.
  • by increasing the number of irradiation light (number of wavelengths) it is possible to measure not only changes in the concentration of redox hemoglobin but also changes in the concentration of other light-absorbing substances in the living body such as cytochrome and myoglobin. Needless to say.
  • FIG. 15 shows a schematic configuration of the biological optical measurement device according to the present embodiment.
  • Output light from a plurality (four in this embodiment) of light sources 111, 1-1, 1-3, 114 are respectively illuminated optical fibers 2-i, 2--2, 2-3-3, 2 — Guided to 4.
  • the wavelength of the output light from the light sources 1-1, 1-3 is f1
  • the wavelength of the output light from the light sources 1-1, 1-4 is L2.
  • the wavelengths 1 and 2 are selected from the range of 400 nm to 2400 nm.
  • the output light from the light sources 111, 112, 113, and 114 is output from 100 Hz by the light source driving circuits 41, 4-2, 4-3, and 4-4, respectively.
  • Intensity modulation is performed at different modulation frequencies f 1, f 2, f 3, and f 4, respectively, during 1 OMHz.
  • the modulation frequency signals A, B, C, and D from the light source driving circuits 4-1, 4-1-2, 4-3, and 4-4 are used as reference frequency signals as phase detectors 27-1 and 27-. 2, 27-3, 27-4 are input.
  • the optical fibers 2-1 and 2-2 are connected to the optical directional coupler 3-1.
  • the optical fibers 2-3 and 2-4 are connected to the optical directional coupler 2-2.
  • Light from the light sources 1-1, 1-2 is mixed in the optical directional coupler 3-1 and introduced into the irradiation optical fiber 8-1, and light from the light sources 1-3, 1-4 is Are mixed in the optical directional coupler 3-2 and introduced into the irradiation optical fiber 8-2.
  • the irradiation optical fibers 8-1 and 8-2 and the condensing optical fibers 10-1 and 10-2 are fixed by the optical fiber holder 21 and applied to the surface of the subject (human head) 9. Touched.
  • the object 9 is irradiated with light from the irradiation optical fibers 8-1, 8-2, and the light transmitted through the object 9 through the condensing optical fibers 10-1 and 10-2 (transmitted light). Focus).
  • the irradiation optical fibers 8-1 and 8-2 and the condensing optical fibers 10-1 and 10-2 are arranged on the circumference of one circle set on the optical fiber holder 21.
  • the light-collecting optical fibers 10-1 and 10-2 are arranged at intervals and opposite to the irradiation optical fibers 8-1 and 8-2 with the center of the circle interposed therebetween. Have been.
  • the eyeba holder 21 is preferably formed of a black material or coated with a black material in order to enhance the light-shielding property, and preferably has a hollow structure as shown in the figure.
  • the irradiation optical fibers 8-1, 8-2 and the condensing optical fibers 10-1, 10-2 are also covered with a black material on the surface portions other than the contact surface with the subject 9. Is desirable.
  • the contact surfaces of the irradiation optical fibers 8-1, 8-2 and the condensing optical fibers 10-1, 10-2 with the subject 9 are brought into contact with the subject 9 so that the subject 9 It is desirable to apply a coating made of a material that is flexible and has good permeability to irradiation light, such as vinyl resin, for the purpose of reducing the stimulus that will endure.
  • the light transmitted through the subject (living body) condensed by the converging optical fibers 10 0-1 10-2 is guided to the photodetectors 1 1 1 1 1 and 1 1-2, respectively, and photoelectrically converted. Is detected. Photomultiplier tubes and avalanche photodiodes are used for the photodetectors 10-1 and 10-2.
  • the output signal from the photodetector 10-1 is divided into two and then input to the phase detectors 27-1 and 27-2, respectively, and the output signal from the photodetector 11-2 is also 2 After being divided into two, they are input to the phase detectors 27-3 and 27-4, respectively.
  • the signals input to the phase detectors 27-1, 27-2, 27-3, and 27-4 include the transmitted light intensity signals of all wavelengths of light radiated into the subject (living body).
  • the phase detectors 27-1, 27-2, 27-3, 27-4 have light source driving circuits 4-1, 4, 1-2, 4-3, 4-4 Since the reference frequency signals A, B, C, and D from 4 are respectively input, the phase detector 27-1 applies the wavelength 1 from the light source 111 and the irradiation light with the modulation frequency f 1 Only the corresponding transmitted light intensity component is detected by the phase detector 27-2. Only the transmitted light intensity component corresponding to the irradiation light having the wavelength ⁇ 2 and the modulation frequency ⁇ 2 from the light source 1-2 is detected by the phase detector 27.
  • the transmitted light intensity signal component of the wavelength 1 detected by the phase detectors 27-1 and 27-3 is The signal is input to the multiplier 28 1 and multiplied by both signal components, and the wavelengths detected by the phase detectors 27-2 and 27-4; the transmitted light intensity signal component of I 2 is calculated by the multiplier 28 The signal is input to —2 to multiply both signal components.
  • the output signals from multipliers 28-1 and 28-2 are input to log amplifiers 29-1 and 29-2, respectively. Further, the output signals from the log amplifiers 291-1 and 29-2 are input to AZD (analog-digital) converters 141-1 and 14-12, respectively, where they are converted into digital signals. After that, it is taken into the arithmetic unit 30.
  • the arithmetic unit 30 changes the oxyhemoglobin concentration, changes the reduced hemoglobin concentration, and expresses the blood volume to the oxidized to mog-to-bin concentration change and the reduced to the oxidized hemoglobin concentration based on the time-series signals of the transmitted two-wavelength transmitted light intensities.
  • the sum with the mouth bottle density change is calculated, and the calculation result is displayed on the display device 17 as a time series change graph. Further, when multipoint measurement (measurement for a plurality of measurement regions in the subject 9) is performed by the same device, the measurement result can be displayed on the display device 17 as an image.
  • the display device 17 When displaying the change of each hemoglobin concentration as a time-series change graph, if the display device 17 can display color, the display color is changed for each change graph of each hemoglobin concentration, and the display device 17 is displayed. When color display is not possible, the type or thickness of the display line can be changed for each change graph of hemoglobin concentration and displayed. For example, if the display device 17 can display color, the change in oxyhemoglobin concentration is red or orange, the change in reduced hemoglobin concentration is blue, indigo or green, and the change in total hemoglobin concentration is black, gray or brown. To display.
  • the result When displaying the result of the multipoint measurement as an image, the result may be displayed as a contour image, or the display color or the display brightness may be changed in accordance with the change in the density change value. Furthermore, the display may be displayed in deep red or dark gray as the absolute value of the positive density change value increases, and may be displayed in dark blue or pale white as the absolute value of the negative density change value increases.
  • FIGS. 16 to 20 show modified examples of the configuration of these data collection units.
  • FIG. 16 shows a first modified configuration example of the data collection unit.
  • the light source 11-1, 1-2, 1-3, 114 to the optical fibers 10-1 and 10-2 for condensing (the light irradiating section and condensing section) The configuration is the same as that in Fig. 15 and those parts are omitted for simplicity.
  • the encircled symbols A, B, C, and D in the figure represent reference frequency signals, as in the case of FIG. These points are the same for the following Figures 17 to 2 ⁇ .
  • the data collection unit consists of a photodetector 11-1, 1-11, and a phase detector 27-1,
  • phase detector 27-1, 27-2, 27-3, 27-4 The configuration up to the phase detector 27-1, 27-2, 27-3, 27-4 is the same as that in Fig. 15.
  • the force here is the phase detector 27-1, 27-2, Output signals (transmitted light intensity signals) from 27-3 and 27-4 were converted to digital signals by A / D converters 14-1, 14-14, 1-3 and 14-14, respectively. Later, arithmetic unit
  • the arithmetic unit 30 first multiplies the input transmitted light intensity signals of all the wavelengths between the transmitted light intensity signals of the same wavelength, and then calculates the natural logarithm of the result of the multiplication, or The natural logarithm operation is performed on all the transmitted light intensity signals thus obtained, and then the result of the natural logarithm operation is added between the same wavelengths.
  • the combination of the transmitted light intensity signals of the same wavelength described above is the combination of the output signals from the AZD converters 14-1 and 14-13 and the A / D converters 14-1 and 14-4 And two sets of output signals from.
  • FIG. 17 shows a second modified configuration example of the data collection unit.
  • the data collection unit of this configuration example includes a photodetector 111, a phase detector 27-11, 27-2, 27-3, 27-4, and a multiplier 28-1, 28. —2, AZD converters 14 1, 14 — 2, and an arithmetic unit 30. Up to the multipliers 28-1 and 28-2, the power is the same as that of the configuration shown in FIG. Output signals from 28-1 and 28-2 are converted into digital signals by the AZD converters 14-1 and 14-2, and then input to the arithmetic unit 30. The arithmetic unit 30 performs a natural logarithmic operation on the signals from the AZD converters 141-1 and 14-12, respectively.
  • FIG. 18 shows a third modification of the data collection unit.
  • the data acquisition section of this configuration example consists of a photodetector 1 1 1 1 1, 1 1 2, a phase detector 27-1, 27-2, 27-3, 27-4, and a log amp 29-1, 29- 2, 29-3, 29-4, adders 40-1, 40-2, AZD converters 14-1, 14-2, and an arithmetic unit 30.
  • Phase detectors 27-2, 27-3, 27-4 are the same as the configuration shown in FIG. 15. In this configuration example, the phase detectors 27-1, 27-2, Output signals from 27-3, 27-4 are input to log amps 29-1, 29-2, 29-3, and 29-4, respectively, and are subjected to natural logarithmic conversion.
  • the transmitted light intensity signals (the transmitted light intensity signals of wavelength ⁇ 1) from the log amplifiers 29-1 and 29-3 are input to the adder 40-1 and added together, and the log amplifiers 29-1 2, 29-4
  • the transmitted light intensity signal (the intensity signal of the transmitted light of wavelength 2) is input to the adder 40-2 and added together.
  • Output signals from the adders 40-1 and 40-2 are input to the AZD converters 141-1 and 144-2, respectively, converted into digital signals, and then input to the arithmetic unit 30.
  • FIG. 19 shows a fourth modification of the data collection unit.
  • the data acquisition unit of this configuration example consists of a photodetector 11 1 1 1 1 1 1 1 1 2, a phase detector 27 1 1, 27 2, 27-3, 27 4 2, 29-3, 29-4, an AZD converter 14-1, 14-2, 14-3, 14-14, and an arithmetic unit 30.
  • the configuration up to the phase detector 27-1, 27-2, 27-3, 27-4 is the same as that of Fig. 15, but in this example, the phase detector 27-1, 27-2, 27-
  • the output signals from 3, 27_4 are input to log amplifiers 29-11, 29-2, 29-3, and 29_4, respectively, and are first subjected to natural logarithmic conversion.
  • the output signals from amplifiers 29-1, 29-2, 29-3, and 29-4 were converted to digital signals by AZD converters 14-1, 1, 14-2, 14-3, and 14-4, respectively. Later, it is input to the arithmetic unit 30.
  • the input transmitted light intensity signal is added between transmitted light intensity signals of the same wavelength for all wavelengths.
  • the combination of the transmitted light intensity signals of the same wavelength described above is determined by the combination of the output signals from the AZD converters 14-1 and 14-3, the AZD converters 14-1 and the A / D converter 13-3 This is a total of two sets including the set of output signals from 4.
  • FIG. 20 shows a fifth modified configuration example of the data collection unit.
  • the data collection unit consists of a photodetector 1 1 1 1, 1 1 1 1 2 and an AZD converter 14 1
  • the configuration up to the photodetectors 1 1 1 1 and 1 1 1 1 2 is the same as that shown in Fig. 15. In this example, the power from the photo detectors 1 1 1 1 1 1 1 1 1 2
  • the output signals are input to the AZD converters 14-11 and 144-2, respectively, and are first subjected to AZD conversion.
  • the output signals from the AZD converters 141-1 and 14-12 are directly input to the arithmetic unit 30.
  • reference frequency signals (modulation frequency signals of each irradiation light) ⁇ , B, C, and D are respectively input and converted into digital signals, and then input to the arithmetic unit 30.
  • the arithmetic unit 30 Fourier-transforms the input signals from the AZD converters 14-1, 1, -2, 14-3, 14-1, 4, 1-5, 14-16, respectively. Then, the input signals from the AZD converters 14-13, 1-4, 14-5, and 14-16 are subjected to Fourier transform, respectively, and the highest-intensity frequencies obtained are fI, f2, f, respectively.
  • the signal strengths corresponding to the frequencies fl and f2 from the signal obtained by Fourier transforming the input signal from the A / D converter 14-1 are I (f1) and I (f 2), and the signal strengths corresponding to the frequencies f 3 and f 4 from the signals obtained by Fourier transforming the input signal from the AZD converters 14 and 1 are defined as I (f 3) and I (f 4) .
  • I (f 1) and I (f 3) are irradiation lights of the same wavelength. Since the signal is a transmitted light intensity signal corresponding to the wavelength of 1), a natural logarithm operation is performed after multiplying the two, and I (f 2) and I (f 4) also have the same wavelength. Irradiation light
  • the transmitted light intensity signal corresponds to (the light of wavelength 2 from the light sources 1-2 and 1-4 in FIG. 15)
  • natural logarithm calculation is performed after multiplying the two.
  • FIG. 21 shows a first arrangement example in which a large number of irradiation optical fibers and light collecting optical fibers are arranged.
  • this arrangement example three irradiating optical fibers and three concentrating optical fibers are arranged on each circumference of the double concentric circle, but the irradiating optical fiber and the concentrating optical fiber are arranged.
  • the measurement sensitivity for the deep part inside the subject (living body) can be increased. Furthermore, concentric circles in which the irradiation optical fiber and the condensing optical fiber are arranged are further multiplexed. It is needless to say that the measurement sensitivity at various depth positions in the subject (living body) can be enhanced by providing the information.
  • the irradiation optical fibers 8-1, 8-2, and 8-3 are arranged at regular intervals of 120 degrees on the circumference of the circle 50-1 outside the double concentric circle.
  • the converging optical fins 10-1, 10-2, and 10-3 are located at positions opposite to the irradiation optical fibers 8-1, 8-2, and 8-3 on the same circumference.
  • Each is arranged S.
  • the irradiating optical fibers 8-4, 8-5, and 8-6 are arranged at regular intervals of 120 degrees on the circumference of the circle 50-2 inside the double concentric circle.
  • the condensing optical fiber 10- is located at a position facing the irradiation optical fibers 8-4, 8-5, and 8-6 on the same circumference.
  • the transmitted light intensity detected on the circumference of the outer circle 50-1 is assigned as in-vivo deep part information.
  • To calculate the change in hemoglobin concentration in the deep part of the living body and assign the transmitted light intensity detected on the circumference of the inner circle 50-2 as shallow part information in the living body to perform the processing. This makes it possible to determine the change in hemoglobin concentration in the shallow part of the body.
  • the hemoglobin concentration change obtained by multiplying the hemoglobin concentration change calculated from the transmitted light intensity detected on the circumference of the inner circle 50-2 by a predetermined weighting factor estimated from the sensitivity distribution. Is subtracted from the hemoglobin concentration change calculated from the transmitted light intensity detected on the circumference of the outer circle 50-1 to further improve the relative sensitivity of the deep part of the body to the shallow part of the body. It is also possible.
  • FIG. 22 shows a second arrangement example in which a large number of irradiation optical fibers and light collecting optical fibers are arranged.
  • an optical fiber arrangement that is more efficient when measuring at various measurement positions in a subject (living body) based on the present invention will be described.
  • two pairs of one converging optical fiber for irradiation are arranged on the circumference of one circle as a basic fiber unit, and the basic fiber unit is set according to the desired measurement area size. Is provided in multiple units.
  • a square lattice An irradiation optical fiber and a condensing optical fiber are arranged on each of the lattice points, and the irradiation optical fiber and the condensing optical fiber are arranged alternately in the diagonal direction of the square lattice.
  • nine measurement positions are set, and nine circles 60-1 to 60-9 are set around each measurement position, and the irradiation optical fiber 8-1 to 8-8 and the condensing optical fiber 10-1 to 10-8 are arranged on the circumference of the circle and on the lattice points of the square lattice.
  • FIG. 23 shows a third arrangement configuration example in which a large number of irradiation optical fibers and condensing optical fibers are arranged.
  • three pairs of irradiating and condensing optical fiber pairs are arranged on the circumference of one circle as the basic fiber unit, and the basic fiber unit is divided into multiple units according to the desired measurement area. Attached.
  • the irradiating optical fiber and the converging optical fiber are alternately arranged on each grid point of the rectangular lattice, and the irradiating optical fiber and the converging optical fiber are alternately positioned in the diagonal direction of each lattice.
  • the irradiation optical fiber and the condensing optical fiber arranged on the intersection of the mutually adjacent circles have the number of intersecting circles (the lattice points inside the lattice) at the lattice points where they are arranged.
  • it works for the same number of measurement positions as 3), so measurement with fewer optical fibers is possible.
  • FIG. 24 shows a fourth embodiment of the present invention suitable for measuring in-vivo deep information. A biological light measurement device will be described.
  • light in an appropriate wavelength range is selected from white light, and the subject is irradiated with the light, and transmitted from the subject.
  • a method of detecting transmitted light of two different wavelengths required for measurement by spectroscopy of light with a spectroscope is adopted.
  • the light irradiation position and the light detection position on the subject are set at two cylinders each. However, it is easy to further increase the number (the number of wavelengths) of these irradiation lights, light irradiation positions, and light detection positions.
  • white light (light having a continuous wavelength spectrum) output from white light sources 80-1 and 80-2 passes through glass filters 84-1 and 84-2, respectively, for measurement. After being converted to light in the required wavelength range, they are introduced into the irradiation optical fibers 8-1 and 8-2 via the lenses 85-1 and 85-2, respectively, and transmitted to the subject (living body). 9 is irradiated.
  • the wavelength of the light irradiating the subject (living body) 9 is set within a range of 400 to 2400 nm. In particular, when measuring hemodynamics during vacation, the wavelength of the irradiated light is 7 ° ⁇ ! It is desirable to select the glass filters 84-1, 84-2 so as to be within the range of 1 to 100 nm.
  • output light from the light sources 80-1 and 80-2 are modulated by the light source driving circuits 4-1 and 4-2, respectively, so that the modulation frequencies f 1 and f 2 different from 100 Hz to 10 MHz are different from each other. Are intensity-modulated.
  • the modulating frequency signals A and B from the light source driving circuits 4-1 and 4-2 are applied to the phase detectors 27-I and 27--2, 27--3 and 27--4 as reference frequency signals, respectively.
  • the irradiation optical fibers 8-1 and 8-2 are fixed to the optical fiber holder 21 together with the condensing optical fibers 10-1 and 10-2 and are in contact with the surface of the subject 9.
  • the subject 9 is irradiated with light from the irradiation optical fibers 8-1 and 8-2, and the converging optical fiber is irradiated.
  • the light transmitted through the subject 9 (transmitted light) at the optical fibers 10-1 and 10-2 is collected.
  • the irradiation optical fibers 8-1 and 8-2 and the condensing optical fibers 10-1 and 10-2 are arranged on the circumference of one circle set on the optical fiber holder 21.
  • the optical fibers 10-1 and 10-2 are located alternately at intervals and are opposite to the optical fibers 8-1 and 8-2 for irradiation with the center of the circle interposed therebetween. Are set to be located respectively.
  • the light transmitted through the subject (living body) condensed by the condensing optical fibers 10-1 and 10-2 is guided to the spectrometers 86-1 and 86-2, respectively, and separated (wavelength separated). You. In the spectrometers 86-1 and 86-2, only component light having the wavelengths ⁇ 1 and ⁇ 2 required for measurement are selected from the component light of various wavelengths that have been separated.
  • the transmitted light components at wavelengths ⁇ 1 and ⁇ 2 from the spectrometer 86-1 are transmitted by the photodetectors 11-1 and 11-12, respectively, and transmitted at wavelengths 1 and ⁇ 2 from the spectrometer 86-1 and 2.
  • the light components are detected (photoelectric conversion and amplification) by the photodetectors 11-3 and 11-4, respectively.
  • a photomultiplier tube or an avalanche photodiode is used as the photodetector 11-1 to 11-14.
  • Output signals (transmitted light intensity signals) from the photodetectors 11 1 to 11 to 11 are input to the phase detectors 27-1 to 27-4, respectively.
  • the signals input to each phase detector are mixed with transmitted light intensity signals having the same wavelength but different modulation frequencies, but the phase detectors 27-1 and 2-7-2, 2 Since the reference frequency signals A and B having the frequencies fl and f2 from the light source drive circuits 4-1 and 4-2 are input to 7-3 and 27-4, respectively, the phase detector 2 7 1 1 In the phase detector 271-2, only the transmitted light intensity component corresponding to the irradiating light of wavelength 1 from the irradiating optical fiber 8-1 is applied to the irradiating light of wavelength ⁇ 2 from the irradiating optical fiber 8-1. In the phase detector 27-3, only the corresponding transmitted light intensity component is transmitted.
  • the change in oxyhemoglobin concentration, the change in reduced hemoglobin concentration, and the change in oxidized hemoglobin concentration and the change in reduced hemoglobin concentration, which indicate blood volume, are obtained from the time-series signals of the transmitted light intensities of the two wavelengths taken in. (Total hemoglobin concentration change) is calculated, and the calculation result is displayed on the display device 17 as a time-series change graph.
  • Embodiment 3 (FIG. 15) and Embodiment 4 (FIG. 24) described above, an example is shown in which the optical fiber holder 1 is provided with two pairs of light-collecting optical fibers for irradiation.
  • the measurement sensitivity in the deep part inside the subject (living body) can be dramatically increased.
  • the measurement results obtained when four pairs of irradiating optical fibers were provided in the outgoing fiber holder 21 are shown in Figs. 25, 26, and 27. Show.
  • a circle with a diameter of 30 mm at the position of mm is set, and four irradiation optical fibers and four focusing optical fibers are alternately set on the circumference of the circle, and the center of each circle is set.
  • the results of measurement using four pairs of one light-collecting optical fiber pair consisting of an irradiation optical fiber and a condensing optical fiber that are point-symmetrical to each other as the center of point symmetry The relative sensitivity distribution at a depth of 2.5 mm (Fig.
  • the transmitted light in the subject of a plurality of wavelengths emitted from a plurality of light irradiation positions on a predetermined circle interposes the center of the circle with each of the plurality of light irradiation positions on the circle.
  • a configuration example was shown in which detection was performed at a plurality of light collection positions set at point-symmetric relational positions, and the intensity of transmitted light detected at these plurality of light collection positions was all multiplied for each same wavelength.
  • a device configuration in which all additions are performed for each of the same wavelengths has a reduced physical meaning, but it is possible to improve the relative sensitivity of a deep part in a subject (living body).
  • the measurement sensitivity of the target measurement area may be improved by using an apparatus configuration that performs four arithmetic operations on the transmitted light intensity in the subject (living body) detected at a plurality of light condensing positions.
  • region of predetermined depth in a test object (living body) can be measured with high precision.
  • An example of a measurement that requires sufficient measurement sensitivity deep inside the subject (living body) is, for example, measurement of changes in hemodynamics due to cerebral function activity.
  • Force according to the present invention ⁇ According to the present invention, Hemodynamic changes can be measured from above the scalp.
  • a living body light measuring device capable of measuring biological information with respect to a wide spatial region within a subject (living body) with high efficiency, high accuracy, and high spatial resolution can be realized. Therefore, by using the measurement signal from the biological optical measurement device directly as an input signal of various external devices, a highly practical biological input device and a biological device capable of controlling these various external devices quickly and with high accuracy.
  • a control device can be realized.
  • Various input devices such as a keyboard, a mouse, and a steering wheel are used to operate devices such as a computer and a game machine.
  • such input devices operated by humans with limbs reduce the sense of presence in game machines, for example, or make it difficult for persons with physical disabilities to operate.
  • a device for performing direct input from the brain using brain waves has been proposed, for example, in Japanese Patent Application Laid-Open No. 7-124331.
  • This device attempts to control a computer, especially a game machine, by inputting brain waves directly to the computer, such as when measuring an electrocardiogram.
  • Such a direct input device from the brain facilitates the control of external devices even for persons with impaired motor function, and is expected to contribute to the social participation of physically handicapped persons. .
  • the human brain is divided into regions with different cell structures, and each region has a different function.
  • the area involved in spontaneous movements is at the top
  • the area involved in sensation and vision is the occipital area
  • the area involved in language is the left half. It is located in the designated part.
  • a living body optical measurement device capable of measuring biological information in a wide spatial region within a subject (living body) with high efficiency, high accuracy, and high spatial resolution can be realized.
  • Directly input measurement signals from optical measurement devices to various external devices By using the signal as a signal, it is possible to provide a highly practical biological input device and a biological control device capable of controlling these various external devices quickly and with high accuracy.
  • the living body input device using the living body light measurement method according to the present invention comprises: a light irradiating means for irradiating light from outside the scalp of the human head into the brain; and irradiating the light into the brain by the light irradiating means.
  • Light collecting means for collecting the light passing through the brain by the light collecting means; light measuring means for measuring the intensity of the light passing through the brain collected by the light collecting means; and the light measuring means From the intensity of the light passing through the brain measured by the above, the oxyhemoglobin concentration change value, the reduced hemoglobin concentration change value, or the total hemoglobin concentration change value in a predetermined region in the brain is calculated and further calculated.
  • Calculating means for calculating a desired characteristic parameter value from the hemoglobin concentration change value obtained as described above, and determining and outputting the type of output signal based on the calculated characteristic parameter value; and Equipped with It becomes Te.
  • the biological input device may further include, as reference data for the characteristic parameter value, a change rate of the hemoglobin concentration at an arbitrary time interval, an intensity of the time change of the hemoglobin concentration at an arbitrary frequency, which is to be calculated by the arithmetic means, and the like. It may include storage means for setting and storing in advance. In this case, the calculating means determines the type of the output signal from the characteristic parameter value obtained by the above calculation and the reference data stored in the storage means and outputs it.
  • the biological control device using the optical biological measurement method according to the present invention includes the biological input device, and an output signal determined by the biological input device as an input signal, and a predetermined functional operation according to the type of the input signal. And an external device for performing the following.
  • the light condensed by the above-mentioned condensing means is a force classified into reflected light and transmitted light in a living body (brain). In the present invention, both of these are transmitted light (transmitted light). .
  • brain function activity localized in a living body (brain) is measured using light, and this measurement signal is used as an input signal to an external device such as a computer. That is, the irradiation optical fiber and the condensing optical fiber are connected to a desired measurement area in the brain (for example, (Right finger motor area, left finger motor area, language area, etc.) at the position on the head surface, irradiate light into the brain, collect and measure the light passing through the brain, and measure this signal.
  • a desired measurement area in the brain for example, (Right finger motor area, left finger motor area, language area, etc.
  • the arithmetic unit In the arithmetic unit, the cursor is moved to the left for signals from the right finger motor area, for example, the cursor is moved to the right for signals from the left finger motor area,
  • the type of output signal for performing a click operation or the like is determined, and the output signal is input to an external device such as a computer, a word processor, or a game machine.
  • the external device performs an operation according to the type of the input signal.
  • a change in the oxidized hemoglobin concentration, a change in the reduced hemoglobin concentration, or a change in the total hemoglobin concentration in the brain is calculated from the measured intensity of the light passing through the brain.
  • the type of the output signal is determined by comparing the calculated characteristic parameter value with the calculated characteristic parameter value and the characteristic parameter value (reference data) previously stored in the storage device. Input the output signal to the external device.
  • the operation content such as “cursor right”, “force cursor left”, “click”, etc.
  • the operator remembers the standard deviation value and average value for each feature parameter in each measurement area at that time as learning data in the storage device, and compares the actual measurement value with those learning data. Then, if they match within the allowable range, a signal instructing execution of the operation content corresponding to the learning data is output.
  • the Mahalanobis distance can be used to determine the type of output signal using the feature parameters, and a neural network can also be used.
  • the Mahalanobis distance is an index for determining whether an actual measurement value belongs to the distribution when the measurement value or the like is represented by a normal distribution having a variance.
  • the driver's dozing alarm device by arranging light irradiating means and condensing means at a number of points on the surface of the subject (living body), the driver's dozing alarm device, environmental control device, learning degree determination device, sick person, infant, animal, etc. It can also be applied to an intention display device, an information transmission device, or a lie detector.
  • FIG. 28 shows a schematic configuration of a brain function activity measuring device used in the biological input device according to the fifth embodiment of the present invention.
  • the localized brain function activity is measured using light, and the resulting signal is used as an input signal to a computer or an external device.
  • the purpose of this study was to measure changes in oxidized hemoglobin concentration and reduced hemoglobin concentration in the brain.
  • the changes in oxidized hemoglobin concentration and reduced hemoglobin concentration were independent.
  • the oxyhemoglobin concentration and the reduced hemoglobin concentration are measured separately. If the number of wavelengths of the irradiation light is further increased, the measurement accuracy will be further improved, and the concentration of substances other than oxidized and reduced hemoglobin can be measured.
  • the light irradiation position and the light detection position are each set to one position will be described. However, it is easy to expand the measurement area by increasing the number of each.
  • light beams with specific wavelengths 1 and 2 are output from light sources 1-1 and 1-2, respectively, and introduced into optical fibers 2-1 and 2-2, respectively.
  • the wavelengths 1 and ⁇ 2 of the output light from the light sources 1-1 and 1-2 are respectively selected from the wavelength range of 400 nm to 240 nm.
  • the measurement accuracy is selected from within the wavelength range of 700 nm to 110 nm so that the wavelength difference between them is within 50 nm. Desirable to raise.
  • this wavelength In the region, light transmission in the living body is high. At longer wavelengths, light absorption by moisture increases, and at shorter wavelengths, hemoglobin itself also increases light absorption, which is not convenient.
  • the output lights from the light sources 111 and 112 are intensity-modulated by the drive circuits 411 and 4-2 at different modulation frequencies f1 and f2, respectively.
  • the modulation frequency signals A and B from the drive circuits 4-1 and 4-2 are input to the phase detectors 27-1 and 27-2, respectively, as reference frequency signals. This is to separate and extract each signal component from the detection signal in which the signal component corresponding to the oxidized hemoglobin concentration value and the signal component corresponding to the reduced hemoglobin concentration value are mixed.
  • the optical fibers 2-1 and 2-2 are connected to the optical directional coupler 3-1.
  • the light of wavelengths 1 and 2 from the light sources 111 and ⁇ -2 are mixed here for irradiation. Is introduced into the optical fiber 8-1, and transmitted to the surface of the subject (living body) 9.
  • the irradiation optical fiber 8-1 Light is emitted from the irradiation optical fiber 8-1 into the subject (living body) 9, and the light passing through the living body is collected and detected by the collecting optical fiber 10-1.
  • changes in the oxidized and reduced hemoglobin concentrations in blood can be measured as changes in the respective colors (changes in the light absorption wavelength).
  • Oxygen saturation is high in arteries (the proportion of oxyhemoglobin occupied in total hemoglobin), but oxygen saturation is lower in veins than in arteries.
  • the distance between the irradiation optical fiber 8-1 and the light condensing optical fin 10-1 is in the range of 10 to 50 mm depending on the desired depth of the measurement area in the living body and the like. Is set to 30 mm in this embodiment.
  • the light passing through the living body condensed by the condensing optical fiber 10-1 is sent to the photodetector 11-1 where it is photoelectrically converted and amplified. Photomultipliers and avalanche photodiodes are used for the photodetectors.
  • the output signal from the photodetector 11 is divided into two and then input to the phase detectors 27-1, 27-2.
  • the signals input to the phase detectors 27-1 and 27-2 include the two wavelengths irradiated into the living body 9 from the irradiation optical fiber 8-1; corresponding to the light of I 1 and E 2, respectively.
  • Living body The phase detector 27-2 27-2 receives the reference frequency signal from the drive circuits 41-1 and 42-2, respectively.
  • the intensity signal of the light passing through the living body corresponding to the irradiation light having the wavelength ⁇ 1 (modulation frequency f1) from the light source 1_i is obtained.
  • the phase detector 27-2 the light source 1 2, the intensity signal of the light passing through the living body corresponding to the irradiation light having the wavelength ⁇ 2 (modulation frequency f 2) is separated and selected and output.
  • the in-vivo transmitted light intensity signals separated and selected by the phase detectors 27-1 and 27-2 are then input to the ⁇ / D converters 14 1 and 14-2, respectively. After being converted into a digital signal, it is taken into the arithmetic unit [130].
  • the arithmetic unit 3 ⁇ calculates the oxyhemoglobin concentration, the reduced hemoglobin concentration, and the sum of the oxidized hemoglobin concentration and the reduced hemoglobin concentration representing the blood volume from the time-series signals of the transmitted light intensities at the two wavelengths.
  • the calculation result is displayed on the display device 17 as a time-series change graph.
  • the total amount (volume) of hemoglobin in the blood is constant, so simply adding the amount of oxidized hemoglobin and the amount of reduced hemoglobin gives the total blood *.
  • a method of calculating changes in oxyhemoglobin, reduced hemoglobin, and total hemoglobin concentration accompanying brain activity is described in, for example, a patent application by the present applicant (Japanese Patent Application No. Hei 7-309). 72 application) in the specification and drawings (arithmetic processing method). Although only the amount of change in hemoglobin concentration is calculated here, the absolute amount of hemoglobin concentration can be measured by performing calculation excluding the influence of light scattering in a living body.
  • FIG. 29 is a graph illustrating an example of a change in hemoglobin concentration during right finger movement measured using the brain function activity measurement device of this example.
  • the region in the brain the right finger motor area
  • the changes in the oxyhemoglobin concentration (a), the reduced hemoglobin concentration (b), and The time series change of the total hemoglobin concentration change (c) is shown. Note that the time indicated by diagonal lines in the figure
  • the area (T:) is the period during which the right finger exercises.
  • FIG. 30 is a graph showing an example of a change in hemoglobin concentration during left finger movement measured using the brain function activity measurement device of the present example.
  • the region in the brain related to the movement of the left finger (the left finger speed field) is used as the measurement region, and the change in oxyhemoglobin concentration (d), the change in reduced hemoglobin concentration (e), And changes in total hemoglobin concentration).
  • the hatched time region (T 2 ) in the figure is the exercise period of the left finger.
  • FIG. 31 is a contour graph showing an example of a change in total hemoglobin concentration during right finger movement measured by the brain function activity measuring device of the present embodiment.
  • measurement is performed at multiple points in the brain so as to encompass the right finger motor area, and the amount of change in the total hemoglobin concentration during right finger movement is shown as a contour graph.
  • the vertical direction corresponds to the vertical direction of the brain
  • the left side corresponds to the front side of the brain
  • the right side corresponds to the back side of the brain. From this figure, it can be seen that the brain function activity measuring device of the present embodiment can measure brain function activity at a local site in the brain showing such a remarkable change.
  • FIG. 32 is a contour graph showing an example of a change in the total hemoglobin concentration at the time of recalling a language measured by the brain function activity measuring device of the present embodiment.
  • measurements are made at multiple points in the brain so as to encompass the brain area (language area) involved in language activity, and the amount of change in oxidized hemoglobin concentration when words are recalled is shown in a contour graph.
  • the language field is It is located in the brain near the temple on the left side of the head.
  • the brain function activity measuring apparatus of this embodiment measures the brain function activity at a local site in the brain showing a remarkable change. According to the brain function activity measuring device of the present embodiment, it is possible to measure such a language recall activity in the brain.
  • a highly accurate and practical direct input method from the brain is realized by using a highly accurate measurement signal measured by the brain function activity measuring device as an input signal to an external device. Can be.
  • FIG. 33 is a schematic configuration diagram of a biological control device according to a fifth embodiment of the present invention.
  • the biological control device according to the present embodiment includes a biological input device 100 and an external device 200.
  • the brain function activity measuring device 110 having the configuration shown in FIG. 28 is used to receive light through the irradiation optical fibers 8-1, 8-2, and 8-3.
  • the specimen (human head) 9 is irradiated with light, and the transmitted light from the subject 9 is condensed by the condensing optical fibers 10-1, 10-2 and 10-3 to reduce the transmitted light intensity. measure.
  • the irradiation and collection optical fibers are composed of a pair of irradiation optical fiber 8-1 and collection optical fiber 10-1 in the first measurement area, and a pair of irradiation optical fiber 8-2 and collection optical fiber 8-1.
  • the pair of optical fibers 10 and 12 correspond to the second measurement region, and the pair of the irradiation optical fiber 8-3 and the collection optical fiber 10 and 13 correspond to the third measurement region, respectively. It is fixed to the helmet 21 for fixing the optical fiber.
  • Passing light intensity for each measurement area measured by the brain function activity measurement device 110 Is input to the arithmetic unit 120.
  • the arithmetic unit 120 receives the input transmitted light intensity for each measurement area, the light absorption coefficient of the oxidation and reduction hemo-mouth bottles stored in the storage device 130 in advance, and other arithmetic data. Then, an arithmetic operation according to an arithmetic method described later is performed, and a desired signal is specified and input to the external device 200.
  • the storage device 130 stores in advance the results of the learning (light absorption coefficient and various calculation data) in order to determine the meaning of each signal. Is stored.
  • the external concealment 200 operates according to the type of the signal manually input from the arithmetic unit 120.
  • Examples of the external device 200 include a computer, a word processor, a game machine, and a communication device.
  • FIG. 34 is a flowchart illustrating an example of a first calculation procedure in the calculation device 120.
  • a pair of the irradiation optical fiber 8-1 and the condensing optical fiber 10-1 is placed in the left finger motor area (measurement area 1), and the irradiation optical fiber 8-2 and the condensing optical fiber 10 0 —
  • the pair of 2 and 3 correspond to the right finger motor area (measurement area 2), and the pair of irradiation optical fiber 8-3 and condensing optical fiber 10-3 correspond to the language area (measurement area 3).
  • the in-vivo light intensity in each measurement area is measured, and the measurement result is input to the arithmetic unit 120.
  • the characteristic parameters include, for example, the integrated value of each or any hemoglobin concentration at an arbitrary time interval, The rate of change of the hemoglobin concentration and the intensity of the arbitrary frequency of the time change of each or any hemoglobin concentration are used, and these can be variously determined.
  • the feature parameter value calculated in step 1-2 is compared with the learning value stored in the storage device 130 to determine whether or not the feature parameter value is within a predetermined threshold range. Is determined, and if it is within the range (yes), the output is Nobuy ⁇ 1 ( , and if it is outside the range ( ⁇ 0), the process proceeds to ste ⁇ 14.
  • the characteristic parameters include, for example, an integrated value of each or any hemoglobin concentration at an arbitrary time interval, a change rate of each or any hemoglobin concentration at an arbitrary time, and a time of each or any hemoglobin concentration.
  • the intensity at any frequency of change is used and these can be determined variously.
  • a characteristic parameter value is calculated from each or any hemoglobin concentration value calculated in step 1-7 to obtain a value.
  • the feature parameters for example, arbitrary time intervals Of each or any hemoglobin concentration, the rate of change of each or any hemoglobin concentration at any time, and the intensity of the time change of each or any hemoglobin concentration at any frequency. Used, and these can be determined in various ways.
  • Step 1 Feature parameter value calculated by 1-8 Determine whether it is within a predetermined threshold range, and if it is within the range (yes), output signal 3 c If out of range (no), return to step 1-1.
  • the external device 200 is a computer
  • the external device 200 is always kept in an input waiting state.
  • move the cursor to the left for signal 1 input move the cursor right for signal 2 input, and click for signal 3 input. It is also possible to make the response function of the device 200 correspond.
  • step 1-3 step 1-6 and step 1-19
  • a “0” signal is output when the signal is within the threshold range
  • a “1” signal is output when the signal is outside the threshold value
  • eight combinations (0 00 to 11 1) can be made as signals output from the arithmetic unit 120.
  • the arithmetic unit 120 may output signals 1 to 8, and the response function of the external device 200 corresponding to each output signal may be determined in advance.
  • the measurement areas are determined in advance as the right finger motor area, the left finger motor area, and the language area, and the measurement signal from each measurement area and the response function of the external device are one-to-one. I described the case where it was made to correspond to.
  • FIG. 35 is a flowchart showing a second example of the calculation procedure in the arithmetic unit 120.
  • This second example of the calculation procedure is a measurement of the oxidation, reduction, or change in the concentration of total hemoglobin in each measurement region. This is the case where the value and the signal input to the external device 200 do not have a one-to-one correspondence.
  • the predetermined measurement area specifically Signals from specific brain regions involved in functional movements
  • this signal is associated one-to-one with the specific functional movements described above. If you have a willingness to move it, you must remind yourself to move your left hand accordingly, and the actual function of the external device and the intention of the operator may be far apart.
  • the second operation procedure example described below takes into consideration the above-mentioned problems in the first operation procedure example.
  • the measurement area is set at a plurality of arbitrary locations (i locations), an irradiation optical fiber and a condensing optical fiber are arranged in each measurement area, and the in-vivo light intensity in each measurement area is measured.
  • the result is input to the arithmetic unit 120.
  • the purpose is to target a predetermined specific measurement area (a specific brain area involved in a specific functional operation) and selectively measure signals from only these specific measurement areas.
  • the measurement optical fiber pair is placed at arbitrary positions K on the surface of the subject (human head) without specifying the measurement area, and the operator connects to an external device (for example, a computer).
  • the learning is performed by repeatedly measuring the change in the concentration of hemoglobin at these multiple positions accompanying the brain function activity when recalling the input operation, and the learning result is stored in the storage device 130 in advance. is there. Then, hemoglobin concentration and characteristic parameters are calculated and obtained from the actually measured signals, and it is searched whether or not there is a similar characteristic parameter in the data stored in the storage device 130. The signal to be input to the device is determined.
  • the value P i, j (matrix value) of each feature parameter j for each measurement area i is calculated and obtained.
  • the characteristic parameter j is, for example, an integrated value of each or any hemoglobin concentration at any time interval, a change rate of each or any hemoglobin concentration at any time, or a time change of each or any hemoglobin concentration.
  • the intensity at an arbitrary frequency is used, which can be determined variously.
  • the storage device 130 stores learning data about general or individual operators in advance.
  • the learning data structure is a standard deviation value and an average value for each feature parameter j for each measurement area i having the same structure for each output signal k. That is, it is assumed that the probability variance of the feature parameters is a Gaussian distribution.
  • the Gaussian function can be described by the standard deviation and the mean.
  • the cursor is set to move to the right when the signal k from the arithmetic device 12 ° is input to the computer in advance.
  • the operator wears the brain function activity measuring device 110 and repeatedly remembers “moving the force sol right” a plurality of times in advance.
  • a standard deviation value and an average value are calculated for each feature parameter j for each measurement area i to be measured.
  • the obtained standard deviation value and average value for each feature parameter j for each measurement area i are stored in the storage device 130 as learning data of the signal k.
  • the stored learning data Di, j, k are read into the arithmetic unit 120.
  • Figure 36 shows the data structure of the learning data Di, j, k.
  • S represents the standard deviation value
  • A represents the average value
  • the dotted line ( ⁇ ) means omission.
  • the measurement area i is set to n places, and the number of types of the characteristic parameter j is set to m.
  • the Mahalanobis is used for each signal k using all stored learning data D i, j, k and the value P i, j of each characteristic parameter j for each measurement area i calculated by ste ⁇ 2-2.
  • the distance MD k is calculated and found. This Mahalanobis distance is represented by a well-known simple equation.
  • the signal k obtained as described above is output and sent to an external device (computer) 200.
  • the above-mentioned second example of the operation procedure is an application of the Mahalanobis estimation method, but there is also a method of applying a neural network as a third operation method in order to perform a similar estimation.
  • the neural network learns in advance by each operator or a plurality of operations by a general operator so as to output an arbitrary signal k according to the value of each feature parameter j for each measurement area i.
  • the same function as that obtained by the Mahalanobis estimation shown in Fig. 35 can be obtained, and a signal corresponding to the user's recall can be output.
  • a neural network is connected to the subsequent stage of the arithmetic unit 120, characteristic parameters are input to input terminals of the network, and output terminals of the network are connected to the external device 200.
  • the arithmetic device determines the type of output signal by directly using the signal measured by the detector for measuring brain function activity. It is of course possible to do so.
  • FIG. 37 shows a schematic configuration of a biological control device according to a sixth embodiment of the present invention.
  • This embodiment is an example in which a signal from the brain function activity measuring device according to the present invention is used to give a drowsiness warning to a car driver.
  • 9 is the driver (subject), 102 is the steering wheel, 103 is the seat, 104 is the car, 105 is the driving circuit, 106 is the speaker, and 107 is the light.
  • Fiber fixing device or helmet for fixing optical fiber 108 is optical fino for light irradiation, ', 109 is optical fiber for condensing light
  • 111 is input device
  • 112 is biological light measurement Unit (brain function measurement device)
  • 113 is an input signal judgment unit
  • 114 is a signal line
  • 115 is a microcomputer
  • 116 is a storage device.
  • a drowsiness warning is issued to the driver 9 using the living body measurement signal from the living body light measuring unit 112.
  • the input device 1 1 1 biological light measuring unit 1 1 2, input signal judging unit 1 1 3, light irradiating optical fiber 108, light condensing optical fiber 109, and light (Including a fiber fixing device or an optical fiber fixing helmet 107)
  • Force A living body input device according to the present invention is constituted, and a microcomputer 115 is used as an external device.
  • FIG. 37 shows a state in which the driver 9 is driving the automobile 104 by operating the steering wheel 102 while sitting in the seat 103.
  • Driver 9 wears an optical fiber fixing device (Hellmet) 107.
  • One or more pairs of light irradiation optical fibers 108 and light condensing optical fibers 109 are fixed to this optical fiber fixing device (helmet) 107.
  • Light is constantly radiated to the head of the driver 9 from the optical fiber for light irradiation 108, and the light is fixed to a condensing position at an arbitrary distance (for example, about 30 mm) from the light irradiation position.
  • the light passing through the living body is collected by the light collecting optical fiber 109.
  • the light source of the light emitted from the optical fiber for light irradiation 108 is installed in the biological light measurement unit 112.
  • a photodetector for detecting the light condensed by the light condensing optical fiber 109 is provided in the biological light measurement unit 112 similarly.
  • modulation at different modulation frequencies is given to each irradiation light intensity for each different light irradiation position and each different irradiation light wavelength, and the light detectors use If the detected in-vivo transmitted light intensity signal is phase-detected and the transmitted light intensity components for each modulation frequency are separated and measured, the effect of stray light from other than the desired measurement position can be removed, It is possible to separate and measure the in-vivo light intensity components for each wavelength at each measurement position.
  • the measurement position defined by a pair of optical fins for irradiating light, '108, and optical fins for condensing light 109, can be set to any arbitrary number of positions for each driver 9. If characteristic regions such as the frontal region with high permeability and the region where hemodynamics are significantly changed by drowsiness are known in advance, the measurement position is selectively set to these characteristic regions. Is good.
  • a drowsiness signal is extracted in the input signal determination unit 113 based on the measurement signal indicating the blood circulation of the head measured by the living body light measurement unit 112.
  • the input signal determination unit 112 includes a storage device that stores constant data necessary for hemodynamic calculation such as optical parameters such as hemoglobin and learning data on the driver 9, and calculates hemodynamics. And an arithmetic unit for determining the input signal. Further, as shown in the third example of the operation procedure, it is also possible to use a neural network to determine the input signal.
  • this sleepiness detection output signal is input to the microcomputer 115 via the signal line 114, and the microcomputer 1 From 15, a signal is sent to the drowsy alarm system consisting of the drive circuit 105 and the speaker 106 to issue an alarm.
  • the drowsiness alarm system sends an alarm sound signal from the drive circuit 105 to the speaker 106 to generate an alarm sound.
  • a light stimulating means or a seat stimulating means Various means, such as one that vibrates 103, can be considered.
  • the voice signal data stored in the storage device 116 is selected according to the alarm level, and for example, “Danger! , Danger! , ⁇ ⁇ ⁇ ] Can be output as an audio alert indicating the content of the alert.
  • the input device 111 in the optical fiber fixing device 107 and send a signal to the dozing alarm system by electromagnetic waves without using the signal line 114.
  • the microcomputer 115 determines that the alarm level has risen, the microcomputer 115, for example, applies a brake or stops the engine as indicated by a downward arrow. Can be directly output.
  • the alarm generation method using such a biological measurement signal can be applied not only to the driving of a car shown in Fig. 37 but also to the driving of all means of transportation such as an airplane and a train.
  • the system can be applied as a device that automatically determines the drowsiness, fatigue, annoyance, redout, blackout, and other sensational conditions that may interfere with driving while the vehicle is operating.
  • redout and blackout are symptoms in which blood flow in the brain concentrates locally due to large acceleration during operation of an airplane or the like, causing visual abnormalities and loss of consciousness.
  • the biological input device according to the present invention as an input device to a microcomputer, it can be applied, for example, as an environment control device.
  • it is used as a device that can judge the subjective sensation state of the environment such as cold, hot, relaxed, etc., and control the environmental conditions such as environmental temperature, environmental music, brightness, and image state. be able to.
  • epilepsy It can also be applied as a diagnostic and alarm device in medical treatment. That is, epilepsy It can be applied to diagnostic devices for determining epileptic focus in patients, brain function testing devices for brain disease patients, and alarm devices for epileptic seizures.
  • the present invention can be applied as a device for displaying sensations and thoughts of those who cannot communicate their intentions to the outside such as patients, infants, animals, etc. with muscular diseases or vegetative states, or who originally cannot communicate. More specifically, an infant captures what he or she thinks, converts it into a digital electric signal, inputs it to a microcomputer, and registers meaningful words in memory beforehand. Select it and output it by voice. In addition, the information in the brain of the infant is captured by a biological input device, and changes in brain activity are detected every moment, and the changes are input to the speech synthesis circuit as phonemes, and the intention of the infant is conveyed as speech. Furthermore, by attaching the living body input device according to the present invention to animals, pets, and the like, it is possible to know what these animals want.
  • the present invention can be applied to a device that determines emotions such as emotions and emotions and transmits emotion information by videophone or the like.
  • An expression can be added to the computer graphics image of the sender's face displayed on the receiver side from the sender's emotion information transmitted by this device.
  • the present invention can be applied to a device that determines the concentration and displays the same. Furthermore, it can also be applied to a lie detector.
  • localized brain function information is measured by a brain function measurement device, and this measurement signal is used as an input signal to an external device.
  • a brain function measurement device In addition to being able to control external devices without using a steering wheel, a vehicle alarm device, an environmental control device, a learning level determination device, a medical diagnostic and alarm device, a willingness display device, an information transmission device, It can also be applied to force judgment devices and lie detectors. Therefore, communication between persons who do not have the information transmission means, which has not been possible in the past, becomes possible.
  • the biological optical measurement device can be directly used as a device for measuring in-vivo information for medical use or the like, and indirectly, based on the measured in-vivo information. It can be used as a control device to activate an alarm device, a braking device, etc. of an automobile.

Abstract

L'invention porte sur un instrument servant à des mesures optiques efficaces sur des corps vivants en différentes régions de l'espace corporel et fournissant des informations internes tout en éliminant la diaphonie. Une source lumineuse (1) comporte une série de modules lumineux (2(1) à 2(16)) émettant des faisceaux modulés en intensité de différentes fréquences par l'intermédiaire de fibres optiques (8-1 à 8-16) pouvant être introduite dans l'organisme (9) par différents orifices jusqu'en divers points. Les faisceaux traversant le corps sont captés à la surface des organes (9) puis guidés vers des photodétecteurs (1-1 à 11-25) par l'intermédiaire de fibres optiques (10-1 à 10-25). Les signaux des photodétecteurs (1-1 à 11-25) sont ensuite dirigés sur un amplificateur synchrone (12) où l'intensité des faisceaux en retour détectés par les différents détecteurs et présentant la même modulation de fréquence que leurs faisceaux entrants respectifs sont mesurés sélectivement. Les intensités des faisceaux lumineux recueillis en différents points sont traitées par un processeur (16) et des informations internes relatives à plusieurs parties du corps peuvent être ainsi obtenues sans diaphonie.
PCT/JP1996/003365 1995-10-06 1996-11-15 Instrument servant a des mesures optiques sur des corps vivants WO1997018755A1 (fr)

Priority Applications (8)

Application Number Priority Date Filing Date Title
DE19681107T DE19681107B4 (de) 1995-11-17 1996-11-15 Instrument für optische Messung in einem lebenden Körper
CA002210703A CA2210703C (fr) 1995-11-17 1996-11-15 Instrument servant a des mesures optiques sur des corps vivants
GB9713004A GB2311854B (en) 1995-11-17 1996-11-15 Optical measurement instrument for living body
US08/875,081 US6240309B1 (en) 1995-10-06 1996-11-15 Optical measurement instrument for living body
US10/689,760 US7142906B2 (en) 1995-10-06 2003-10-22 Optical measurement instrument for living body
US11/371,919 US20060184047A1 (en) 1995-11-17 2006-03-10 Optical measurement instrument for living body
US11/371,918 US20060184046A1 (en) 1995-10-06 2006-03-10 Optical measurement instrument for living body
US11/371,916 US7774047B2 (en) 1995-10-06 2006-03-10 Optical measurement instrument for living body

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
JP29954295A JP3588880B2 (ja) 1995-11-17 1995-11-17 生体光計測装置
JP7/299542 1995-11-17
JP7/311993 1995-11-30
JP31199395A JP3682793B2 (ja) 1995-11-30 1995-11-30 光による散乱体内部画像化装置
JP31419595A JP3543453B2 (ja) 1995-12-01 1995-12-01 光生体計測法を用いた生体入力装置
JP7/314195 1995-12-01

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US08/539,871 Continuation-In-Part US5803909A (en) 1994-10-06 1995-10-06 Optical system for measuring metabolism in a body and imaging method

Related Child Applications (3)

Application Number Title Priority Date Filing Date
US08875081 A-371-Of-International 1996-11-15
US08/875,081 A-371-Of-International US6240309B1 (en) 1995-10-06 1996-11-15 Optical measurement instrument for living body
US09/849,409 Continuation US6640133B2 (en) 1995-10-06 2001-05-07 Optical measurement instrument for living body

Publications (1)

Publication Number Publication Date
WO1997018755A1 true WO1997018755A1 (fr) 1997-05-29

Family

ID=27338317

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP1996/003365 WO1997018755A1 (fr) 1995-10-06 1996-11-15 Instrument servant a des mesures optiques sur des corps vivants

Country Status (4)

Country Link
CA (1) CA2210703C (fr)
DE (1) DE19681107B4 (fr)
GB (1) GB2311854B (fr)
WO (1) WO1997018755A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2003509687A (ja) * 1999-09-14 2003-03-11 ザ・リサーチ・ファンデーション・オブ・ステート・ユニバーシティ・オブ・ニューヨーク 散乱媒体の動的性質のトモグラフィ画像化システム及び方法
US7072700B2 (en) * 1999-12-27 2006-07-04 Hitachi, Ltd. Biological photometric device
USRE44735E1 (en) 1998-10-13 2014-01-28 Covidien Lp Multi-channel non-invasive tissue oximeter

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE69929380T2 (de) * 1998-12-07 2006-08-31 Hitachi, Ltd. Vorrichtung zur Steuerung von Anlagen mit Hilfe von Körpersignalen
DE19922772A1 (de) * 1999-05-18 2001-02-08 Phiscience Gmbh Entwicklung Vo Vorrichtung zur Bestimmung verschiedener Druchblutungszustände und der Sauerstoffsättigung in blutführendem Gewebe
US6526297B1 (en) 1999-10-04 2003-02-25 Instrumentarium Corp. Method and apparatus for quantifying the hypnotic component of the depth of anesthesia by monitoring changes in optical scattering properties of brain tissue
IL138683A0 (en) 2000-09-25 2001-10-31 Vital Medical Ltd Apparatus and method for monitoring tissue vitality parameters
EP1327418B1 (fr) * 2000-10-16 2010-05-19 Hitachi Medical Corporation Instrument de mesure optique d'organismes
JP4090699B2 (ja) * 2001-04-02 2008-05-28 株式会社日立製作所 生体光計測装置
IL148795A0 (en) 2002-03-20 2002-09-12 Vital Medical Ltd Apparatus and method for monitoring tissue vitality parameters for the diagnosis of body metabolic emergency state
JP3635332B2 (ja) 2003-03-20 2005-04-06 独立行政法人情報通信研究機構 頭部装着具
DE102004032094A1 (de) * 2004-07-01 2006-01-26 Micro-Epsilon Messtechnik Gmbh & Co Kg Verfahren und eine Vorrichtung zur Messung der Blutsauerstoffsättigung
GB0426993D0 (en) 2004-12-09 2005-01-12 Council Cent Lab Res Councils Apparatus for depth-selective raman spectroscopy
JP5018105B2 (ja) * 2007-01-25 2012-09-05 株式会社日立製作所 生体光計測装置

Citations (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS57115232A (en) * 1980-07-09 1982-07-17 Deyuuku Univ Inc Apparatus for measuring metabolic action in internal organ
JPS61502660A (ja) * 1984-07-11 1986-11-20 ザ・ジョンズ・ホプキンス・ユニバ−シティ Ｃｗ励起源を用いる光放射の期間中に生成された瞬間的一量状態酸素濃度を監視するための電子光学デバイス
JPS62231625A (ja) * 1986-03-31 1987-10-12 住友電気工業株式会社 光ｃｔスキヤナ装置
JPS635234A (ja) * 1986-06-25 1988-01-11 Shimadzu Corp １〜２次元測光装置
JPS63305845A (ja) * 1987-06-05 1988-12-13 Nissan Motor Co Ltd 身体異常検出装置
JPH01262839A (ja) * 1987-12-02 1989-10-19 Boc Group Inc:The 周波数分割マルチプレクス式の血液成分監視装置
JPH03241414A (ja) * 1990-02-20 1991-10-28 Nippon Telegr & Teleph Corp <Ntt> 頭皮準備電位パターンによる操作装置
JPH03505922A (ja) * 1988-06-08 1991-12-19 バーバー，ランダル　エル． ランダムな媒体を画像化するためのシステム
JPH04166144A (ja) * 1990-10-31 1992-06-12 Matsushita Electric Ind Co Ltd 生体組織測定装置
JPH05103786A (ja) * 1991-10-16 1993-04-27 Olympus Optical Co Ltd 代謝情報測定装置
JPH05115485A (ja) * 1991-10-25 1993-05-14 Hitachi Ltd 生体光計測装置
JPH05261110A (ja) * 1992-03-19 1993-10-12 Hitachi Ltd 生体光計測装置
WO1994005209A1 (fr) * 1992-08-31 1994-03-17 Hitachi, Ltd. Appareil de tomographie optique informatisee
WO1994010901A1 (fr) * 1992-11-09 1994-05-26 Boehringer Mannheim Gmbh Procede et dispositif d'analyse de glucose dans une matrice biologique
JPH06181930A (ja) * 1992-12-21 1994-07-05 Hitachi Ltd 生体光計測装置
JPH06245938A (ja) * 1993-02-23 1994-09-06 Hitachi Ltd 光計測装置
DE4318823A1 (de) * 1993-06-07 1994-12-08 Zeiss Carl Fa Vorrichtung zur scannenden optischen Gewebe-Untersuchung
JPH07103884A (ja) * 1993-10-04 1995-04-21 Technol Res Assoc Of Medical & Welfare Apparatus 光ｃｔ
JPH07117595A (ja) * 1993-10-21 1995-05-09 Fujikura Ltd 居眠り運転防止装置
JPH07120384A (ja) * 1993-10-25 1995-05-12 Hitachi Ltd 光計測方法および装置
JPH07204168A (ja) * 1994-01-12 1995-08-08 Nou Kinou Kenkyusho:Kk 生体情報自動識別装置
JPH0919408A (ja) * 1995-07-05 1997-01-21 Hitachi Ltd 生体光計測装置及びその装置における画像作成方法

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5353799A (en) * 1991-01-22 1994-10-11 Non Invasive Technology, Inc. Examination of subjects using photon migration with high directionality techniques
GB2228314B (en) * 1989-02-16 1992-11-18 Hamamatsu Photonics Kk Examination apparatus
US5213105A (en) * 1990-12-04 1993-05-25 Research Corporation Technologies, Inc. Frequency domain optical imaging using diffusion of intensity modulated radiation
DE4340072C2 (de) * 1993-11-24 1996-05-15 Siemens Ag Vorrichtung zur Untersuchung von Gewebe mit Licht

Patent Citations (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS57115232A (en) * 1980-07-09 1982-07-17 Deyuuku Univ Inc Apparatus for measuring metabolic action in internal organ
JPS61502660A (ja) * 1984-07-11 1986-11-20 ザ・ジョンズ・ホプキンス・ユニバ−シティ Ｃｗ励起源を用いる光放射の期間中に生成された瞬間的一量状態酸素濃度を監視するための電子光学デバイス
JPS62231625A (ja) * 1986-03-31 1987-10-12 住友電気工業株式会社 光ｃｔスキヤナ装置
JPS635234A (ja) * 1986-06-25 1988-01-11 Shimadzu Corp １〜２次元測光装置
JPS63305845A (ja) * 1987-06-05 1988-12-13 Nissan Motor Co Ltd 身体異常検出装置
JPH01262839A (ja) * 1987-12-02 1989-10-19 Boc Group Inc:The 周波数分割マルチプレクス式の血液成分監視装置
JPH03505922A (ja) * 1988-06-08 1991-12-19 バーバー，ランダル　エル． ランダムな媒体を画像化するためのシステム
JPH03241414A (ja) * 1990-02-20 1991-10-28 Nippon Telegr & Teleph Corp <Ntt> 頭皮準備電位パターンによる操作装置
JPH04166144A (ja) * 1990-10-31 1992-06-12 Matsushita Electric Ind Co Ltd 生体組織測定装置
JPH05103786A (ja) * 1991-10-16 1993-04-27 Olympus Optical Co Ltd 代謝情報測定装置
JPH05115485A (ja) * 1991-10-25 1993-05-14 Hitachi Ltd 生体光計測装置
JPH05261110A (ja) * 1992-03-19 1993-10-12 Hitachi Ltd 生体光計測装置
WO1994005209A1 (fr) * 1992-08-31 1994-03-17 Hitachi, Ltd. Appareil de tomographie optique informatisee
WO1994010901A1 (fr) * 1992-11-09 1994-05-26 Boehringer Mannheim Gmbh Procede et dispositif d'analyse de glucose dans une matrice biologique
JPH06181930A (ja) * 1992-12-21 1994-07-05 Hitachi Ltd 生体光計測装置
JPH06245938A (ja) * 1993-02-23 1994-09-06 Hitachi Ltd 光計測装置
DE4318823A1 (de) * 1993-06-07 1994-12-08 Zeiss Carl Fa Vorrichtung zur scannenden optischen Gewebe-Untersuchung
JPH07103884A (ja) * 1993-10-04 1995-04-21 Technol Res Assoc Of Medical & Welfare Apparatus 光ｃｔ
JPH07117595A (ja) * 1993-10-21 1995-05-09 Fujikura Ltd 居眠り運転防止装置
JPH07120384A (ja) * 1993-10-25 1995-05-12 Hitachi Ltd 光計測方法および装置
JPH07204168A (ja) * 1994-01-12 1995-08-08 Nou Kinou Kenkyusho:Kk 生体情報自動識別装置
JPH0919408A (ja) * 1995-07-05 1997-01-21 Hitachi Ltd 生体光計測装置及びその装置における画像作成方法

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
JAPANESE UTILITY MODEL, Registration No. 3016160, Z1 (YUGEN KAISHA TOSTEC), 19 July 1995. *

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
USRE44735E1 (en) 1998-10-13 2014-01-28 Covidien Lp Multi-channel non-invasive tissue oximeter
JP2003509687A (ja) * 1999-09-14 2003-03-11 ザ・リサーチ・ファンデーション・オブ・ステート・ユニバーシティ・オブ・ニューヨーク 散乱媒体の動的性質のトモグラフィ画像化システム及び方法
JP2003527883A (ja) * 1999-09-14 2003-09-24 ザ・リサーチ・ファンデーション・オブ・ステート・ユニバーシティ・オブ・ニューヨーク 散乱媒体の動力学を画像化する方法及びシステム
US7072700B2 (en) * 1999-12-27 2006-07-04 Hitachi, Ltd. Biological photometric device

Also Published As

Publication number Publication date
GB2311854A (en) 1997-10-08
GB2311854B (en) 2000-03-22
CA2210703A1 (fr) 1997-05-29
GB2311854A9 (en)
GB9713004D0 (en) 1997-08-27
CA2210703C (fr) 2001-10-09
DE19681107T1 (de) 1997-12-11
DE19681107B4 (de) 2006-01-26

Similar Documents

Publication Publication Date Title
US7774047B2 (en) Optical measurement instrument for living body
JP3543453B2 (ja) 光生体計測法を用いた生体入力装置
US20060184047A1 (en) Optical measurement instrument for living body
Chance et al. A novel method for fast imaging of brain function, non-invasively, with light
Quaresima et al. A mini-review on functional near-infrared spectroscopy (fNIRS): where do we stand, and where should we go?
Sitaram et al. Hemodynamic brain–computer interfaces for communication and rehabilitation
JP3682793B2 (ja) 光による散乱体内部画像化装置
Franceschini et al. On-line optical imaging of the human brain with 160-ms temporal resolution
Koizumi et al. Higher-order brain function analysis by trans-cranial dynamic near-infrared spectroscopy imaging
Sato et al. Temporal cortex activation during speech recognition: an optical topography study
Li et al. Tutorial on use of intraclass correlation coefficients for assessing intertest reliability and its application in functional near-infrared spectroscopy–based brain imaging
WO1997018755A1 (fr) Instrument servant a des mesures optiques sur des corps vivants
Hoshi Towards the next generation of near-infrared spectroscopy
JP3532800B2 (ja) 聴診器
Nosrati et al. Event-related changes of the prefrontal cortex oxygen delivery and metabolism during driving measured by hyperspectral fNIRS
Hakimi et al. Proposing a convolutional neural network for stress assessment by means of derived heart rate from functional near infrared spectroscopy
JPH09135825A (ja) 生体光計測装置
Mirbagheri et al. Simulation and in vivo investigation of light-emitting diode, near infrared Gaussian beam profiles
JP2002143169A (ja) 光計測装置、および光ファイバー保持装置
Saikia et al. 3D-printed human-centered design of fNIRS optode for the portable neuroimaging
Sitnikova et al. Functional near-infrared spectroscopy applications in developmental cognitive neuroscience
JP3801172B2 (ja) 生体光計測装置
JPH11169361A (ja) 生体光計測装置
Lu et al. Explore the brain activity during translation and interpreting using functional near-infrared spectroscopy
KR101801473B1 (ko) 다발형 광소자를 이용하는 휴대용 뇌 영상장치

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): CA DE GB US

WWE Wipo information: entry into national phase

Ref document number: 9713004.1

Country of ref document: GB

ENP Entry into the national phase

Ref document number: 2210703

Country of ref document: CA

Ref document number: 2210703

Country of ref document: CA

Kind code of ref document: A

WWE Wipo information: entry into national phase

Ref document number: 08875081

Country of ref document: US

RET De translation (de og part 6b)

Ref document number: 19681107

Country of ref document: DE

Date of ref document: 19971211

WWE Wipo information: entry into national phase

Ref document number: 19681107

Country of ref document: DE