JPH08131445A - Optical measuring instrument - Google Patents

Abstract

PURPOSE: To obtain the instrument which measures scattered light or fluorescent light from a spot in a scattering body by making one of branched light incident on a sample, making the light scattered at the focus in the sample into a parallel light through an optical system, and putting the parallel light together with the other frequency-modulated light and detecting the plane wave component of the reflected light. CONSTITUTION: A light source 1 consists of lasers which have different wavelengths and the parallel light of respective wavelengths emitted by the light source 1 is demultiplexed into two; and one is sent to a modulation part 6 to impose frequency modulation, and the frequency-modulated light is sent to a multiplexing part 7. The other light is guided to the optical system, reflected by a half-mirror 2, and further photodetected by a lens 3 and focus 5 in the scattering body 4 as the sample. The light scattered at the focus 5 is made into the parallel light by a lens 3, transmitted through the halfmirror 2, and then multiplexed by a multiplexing part 7 with the modulated light. The light signal which is intensified by the multiplexing is detected by a detection part 8, whose signal is stored and processed by a computer 9 and displayed at a display part 10.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an apparatus for non-invasively measuring an absorbing substance or a fluorescent substance existing at a specific spot in a scatterer.

[0002]

2. Description of the Related Art An apparatus for non-invasively measuring the metabolic function of a living body using light is described in JP-A-57-115232. Furthermore, the optical CT device that visualizes the distribution of biological functions is
It is described in JP-A-60-72542 and JP-A-62-231625. A biological light measuring device for measuring a biological substance concentration by reducing a scattered light component by using a time gate method
It is described in No. 2-290534. An apparatus for measuring the two-dimensional distribution of fluorescence in a living body is described in JP-A-59-139237 and JP-A-4-83149. A confocal microscope for measuring fluorescence from a certain point in a minute tissue such as a cell is disclosed in a literature (TINS, vol.12, No.12, p486-
493,1989 (T. Wilson)). A heterodyne detection light receiving system is described in Japanese Patent Laid-Open No. 3-111737.

[0003]

In the conventional biological optical measuring device and optical CT device, the light including all the information on the path through which the light passes is measured and the scattered light component is suppressed by the time gate method. However, it is attempting to obtain information for each pixel by using the X-ray CT algorithm (back projection method). However, even in the conventional example, the light that has passed through the living body contains a scattered light component. Therefore, even if the conventional X-ray CT algorithm is applied as it is, it is impossible to obtain accurate information for each pixel.

Further, the conventional two-dimensional fluorescence distribution measuring device in the living body lacks information in the depth direction in order to continuously measure the fluorescence. The conventional confocal microscope can obtain information and a tomographic image in the depth direction of the fluorescence because it measures the fluorescence emitted from the focus, but it does not consider the scattering of light, so it can measure a minute sample. Limited to only. Moreover, even in the biological optical measurement device using the conventional heterodyne detection light receiving system,
No depth information is available.

An object of the present invention is to provide a method and apparatus for measuring scattered light or fluorescent light from a spot in a scatterer.

[0006]

To achieve the above object, the present invention splits light emitted from a light source, one of which is incident on a sample, and the light scattered at a specific focal point in the sample is optically reflected. Parallel light is generated by the system, the other light subjected to frequency modulation is combined with the parallel light, and the intensity signal of the light is measured to detect the plane wave component of the reflected light. In addition, assuming that the sample is a transparent medium, the shortest arrival time until the light emitted from the light source is scattered at the focal point in the sample and reaches the detector is τ
Then, if the detection light that has passed through the sample that is a scatterer has time τ
To τ + Δτ are set, and the light reaching the detector at the time within the time gate is used for data processing.

[0007]

Even when the scatterer is measured as described above, by using the plane wave component of the reflected light or the detection light in the time gate for data processing, the scattering is almost the same as when measuring the transparent medium. It is possible to detect the light scattered from or emitted from a specific spot in the body sample.

[0008]

DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 is a block diagram of a first embodiment of a living body optical measurement system of the present invention. The main configuration of the device will be described below. The apparatus includes a light source 1, a light detection unit 8, an optical system (consisting of a mirror 2, a lens 3 and the like) for focusing a focus 5 inside a subject (sample 4), a modulation unit 6, and a display unit 10 for displaying an image.
And a computer 9 that controls each unit and stores and calculates data.

Details of each unit and operation will be described below. FIG.
Is a device for detecting reflected light having the same wavelength as the incident light. FIG.
The light source 1 is composed of a plurality of lasers having different wavelengths. The parallel light of each wavelength emitted from the light source 1 is split into two, one of which is sent to the modulator 6 for frequency modulation and further sent to the multiplexer 7. The other light is guided to the optical system, reflected by the half mirror 2, further received by the lens 3, and focused on the scatterer 4 as the sample.

The light scattered at the focal point 5 is collimated by the lens 3. The parallel light passes through the half mirror 2 and is combined with the light modulated by the combining unit 7. The optical signal strengthened by the multiplexing is detected by the detector 8. For the detector 8, for example, a photomultiplier tube or a photodiode may be used. The signal is stored and arithmetically processed by the computer 9 and displayed on the display unit 10. For example, a deflection mirror may be used instead of the half mirror 2. Instead of the lens 3, for example, another optical system such as a concave mirror may be used. Further, as the lens 3, an optical system having a linear focus may be used. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

FIG. 2 is a block diagram of an optical probe fixed to a sample. The parallel light emitted from the light source 1 is demultiplexed by the half mirror 11, one of which is sent to the modulator 6 to be frequency-modulated and further sent to the multiplexer 7. The other is reflected by the half mirror 2 and the lens 3 focuses the focus 5 in the sample. The light scattered at the focal point 5 is made into parallel light by the lens 3, passes through the half mirror 2, is guided to the combining unit 7, and is combined with one of the split lights. The signal strengthened by the multiplexing is detected by the detector 8 and sent to the computer 9 where it is stored and arithmetically processed. The fixing unit 12 fixes the device so that the sample surface is stable and does not leak light. Fixed part 1
For example, an adhesive seal may be used for 2. Lens barrel 13
Has a structure that supports the optical system and does not leak light. The inner surface of the lens barrel portion 13 may be covered with a light absorbing film. By operating the slide portion 14, the lens 3 moves up and down,
The focus can be scanned in the depth direction. The operation of the slide portion may be performed using a motor, for example. Alternatively, the slide unit may be manually operated.

FIG. 3 is an explanatory view of a probe portion similar to FIG. By moving the galvanometer 15, the focus can be scanned in the horizontal and vertical directions with respect to the sample surface. Instead of the galvanometer 15, another optical system may be used to scan the focus.

FIG. 4 shows an embodiment in which the present invention is applied to a head and brain function measuring device. One or a plurality of optical probes 16 are fixed to the head of the subject 17, and the activity of a specific spot on the brain is measured. In addition, this embodiment may be used for measuring other samples.

FIG. 5 shows an embodiment in which the present invention is applied to a diagnostic device. The subject 17 rides on the pedestal 20 and the optical probe 18 is applied to the measurement site. The probe 18 is moved in the vertical and horizontal directions according to the shape of the subject and the measurement site by a probe moving mechanism built in the support portion 19. Further, this embodiment may be used for measuring a sample other than a living body.

FIG. 6 is a block diagram of another embodiment of the present invention. The main configuration of the apparatus of this embodiment will be described below.
The apparatus is composed of a pulse light source 1, a light detection unit 8, an optical system for confocal focusing, a display unit 10 for displaying an image, and a computer 9 for controlling each unit and storing / calculating data.

The operation of each unit will be described in detail below. Figure 6
Is a device that detects reflected light having the same wavelength as incident light. The light source 1 in FIG. 6 is composed of a plurality of lasers having different wavelengths. The pulsed light of each wavelength is introduced into the first optical system including the half mirror 2 and the lens 3, and the half mirror 2
Is reflected by the lens 3 and is condensed by the lens 3 to form a focal point 5 in the scatterer 4. The light scattered at the focal point 5 is collimated by the lens 3. The parallel light passes through the half mirror 2 and is focused by a lens 21 on a pinhole 22 having a finite area. The light focused on the pinhole 22 passes through the pin pole 22 and is detected by the detector 8.

Here, a time-resolved light measuring instrument is used as the detector 8. For the detector 8, for example, a streak camera or an optical oscilloscope may be used. The data measured by the detector 8 is stored / calculated by the computer 9 and displayed on the display unit 10.

Instead of the half mirror 2, for example, a deflection mirror may be used. Instead of the lenses 3 and 21, another optical system such as a concave mirror may be used. Further, as the lenses 3 and 21, an optical system having a linear focus may be used. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

Further, as shown in FIG. 7, the optical fiber 2
3 may be used to guide the light emitted from the light source 1 to the first optical system. Similarly, using the optical fiber 24, the pinhole 22
Light that has passed through may be guided to the detector 8.

FIG. 7 is still another embodiment and is a block diagram of an apparatus for measuring light having a wavelength different from the incident light.
The light emitted from the light source 1 is guided by the incident optical fiber 23 to the first optical system including the dichroic mirror 26 and the lenses 3 and 25. The light is collimated by the lens 25, reflected by the dichroic mirror 26, condensed by the lens 3, and reaches the focal point 5 in the scatterer 4.
The light excites the fluorescent substance in the focus to emit fluorescence.
The fluorescence becomes parallel light by the lens 3, passes through the dichroic mirror 26 and the cut filter 27, and is focused on the pinhole 7 by the lens 21. The focused light passes through the pinhole 22 and is guided to the detector 8 by the detection optical fiber 24.

Similar to the embodiment of FIG. 6, here also the detector 8
A time-resolved optical measuring instrument is used as
For example, a streak camera or an optical oscilloscope may be used. The measured data is stored and calculated by the computer 9 as in the case of FIG. 1, and is displayed on the display unit 10. Instead of the lenses 3, 21 and 25, another optical system such as a concave mirror may be used. As shown in FIG. 6, light may be guided without using the incident / detection optical fibers. Further, the cut filter 27 may be placed between the pinhole 22 and the detector 8. An optical system having a linear focus may be used as the lenses 3 and 21. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

FIG. 8 shows the time-resolved display of the light intensity measured by the detector 8 in a time-resolved manner. As shown in FIGS. 6 and 7, the length of each part of the optical system is L ₁ , L ₂ , L ₃ , the lengths of the incident and detection optical fibers are L _in , L _out , and the depth of the focal point from the sample surface is Letting d be the speed of light in air, c _{s be} the speed of light in the scatterer, and c _f be the speed of light in the optical fiber, the light emitted from the light source 1 is assumed if the sample is a transparent medium. The shortest arrival time τ from when the light reflects at the focal point 5 and passes through the pinhole 22 and reaches the detector 8 is the number when the optical fiber is not used (Fig. 6) and the number when the optical fiber is used (Fig. 7) It becomes 2.

[0023]

[Formula 1] τ = (L ₁ + 2L ₂ + L ₃ ) / c + 2d / c _s (Formula 1)

[0024]

Τ = (L ₁ + 2L ₂ + L ₃ ) / c + 2d / c _s + (L _in + L _out ) / c _f (Equation 2) A time gate from time τ to time τ + Δτ after a short time Δτ is set. Of the light that has passed through the scatterer sample, the light in the gate has a small number of scatterings, and is light that has traveled almost straight through the sample, as in the case where the sample is a transparent medium. The light measured at the time in the gate is calculated and used for imaging.

FIG. 9 is a block diagram of yet another embodiment of the present invention, which uses an optical shutter using a non-linear element. The optical shutter 29 has a property of passing the measurement light by the Kerr effect while the reference light is incident. The pulsed light emitted from the light source 1 is guided to the optical system, and is branched into the measurement light incident on the sample and the reference light incident on the optical shutter 29 through the delay unit 28. The reference light is delayed by the delay unit 28 in time and enters the optical shutter 29. As a result, the light reaching the detector 8 within the gate for a specific time passes through the optical shutter 29. The delay unit 28 adjusts the time width of the time gate. _Assuming that the distance from the light source 1 to the optical shutter 29 via the delay unit 28 is L _re , the delay time at this time is Equation 3 when an optical fiber is not used and Equation 4 when an optical fiber is used.

[0026]

## EQU3 ## τ '= τ-L _re / c (Equation 3)

[0027]

Τ ′ = τ−L _re / c _f (Equation 4) By delaying τ ′ and irradiating light for a minute time Δτ, the light in the time gate τ + Δτ can be passed.
In addition, as shown in FIG. 7, the light source 1 uses an optical fiber.
Light may be guided from the first optical system to the first optical system. Similarly, the light that has passed through the pinhole 22 is detected by the detector 8 using an optical fiber.
You may lead to. Further, the reference light may also be guided to the optical shutter 29 via the delay unit 28 using an optical fiber. At this time, L _re is the length of the optical fiber for reference light, and the speed of light c _f in the optical fiber is used instead of the speed of light c in the air.

In this case, the detector 8 may be a detector such as a photomultiplier tube which cannot perform time-resolved measurement. Further, instead of the lenses 3 and 21, other optical means such as a concave mirror may be used. Instead of the half mirror 2, other optical means such as a deflection mirror may be used. Instead of the half mirror 2, for example, a dichroic mirror may be used as shown in FIG. 7, and a cut filter may be placed in front of the pinhole 22 to measure the fluorescence emitted from the focus 5. Further, an optical system having a linear focus may be used as the lenses 3 and 21. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

The lens 3 shown in FIGS. 6, 7 and 9 may be slid up and down to scan the focal point 5 in the depth direction.

FIG. 10 is an explanatory view of an optical probe portion attached to the apparatus of FIGS. 6, 7, and 9 and fixed to the sample. The light guided by the incident optical fiber 23 is reflected by the lens 2
The light is collimated by 5 and reflected by the half mirror 2, and the lens 3 focuses a focal point 5 in the sample. The light scattered at the focal point 5 passes through the lens 3, the half mirror 2 and the lens 21 and is focused on the pinhole 22. The light passing through the pinhole 22 is guided to the detector 8 by the detection optical fiber 24. The fixing part 12 fixes the device stably to the sample surface so that light does not leak. In the fixed part 12,
For example, an adhesive seal may be used. The lens barrel portion 13 supports the optical system and has a structure in which light does not leak. The inner surface of the lens barrel portion 13 may be covered with a light absorbing film. Slide part 14
By operating, the lens 3 moves up and down, and the focal point is scanned in the depth direction. The operation of the slide portion may be performed using a motor, for example. Alternatively, the slide unit may be manually operated.

FIG. 11 is an explanatory diagram of a probe portion similar to that of FIG. By moving the galvanometer 15, the focus can be scanned in the horizontal and vertical directions with respect to the sample surface. Instead of the galvanometer 15, another optical system may be used to scan the focus.

FIG. 12 shows an example in which the embodiments of FIGS. 6, 7 and 9 are applied to a head and brain function measuring device. Fixing one or more optical probes 30 to the head 17 of the subject,
Measure activity at specific spots in the brain. Since the light is guided by the incident optical fiber 23 and the detection optical fiber 24, the optical probe 30 can be attached to any part of the subject's head. A plurality of probes may be bundled and used. Further, this embodiment may be used for measuring other samples.

FIG. 13 is an example in which the embodiments of FIGS. 6, 7, and 9 are applied to a diagnostic device. An optical probe 31 is arranged at a measurement site of the subject 17 on the pedestal 20. The probe 31 moves vertically and horizontally by a probe moving mechanism built in the support portion 19. Further, the present embodiment may be used for measuring a sample other than a living body.

FIG. 14 is a block diagram of still another embodiment of the biological optical measurement device of the present invention. The main configuration of the device will be described below. The apparatus is composed of a light source 1, a light detection unit 8, an optical system for confocal focusing, a display unit 10 for displaying an image, and a computer 9 for controlling each unit and storing / calculating data.

The operation of each unit will be described in detail below. FIG.
Reference numeral 4 is a device that detects reflected light having the same wavelength as the incident light.
The light source 1 in FIG. 14 is composed of a plurality of lasers having different wavelengths. The pulsed light of each wavelength is made incident inside from a site where the scatterer 4 is present. Part of the incident light passes through the scatterer, is scattered at the position of the focal point 5, and is condensed by the lens 3 to become parallel light. The parallel light passes through the half mirror 2 and is focused by a lens 21 on a pinhole 22 having a finite area.

The light focused on the pinhole 22 passes through the pin pole 22 and is detected by the detector 8. In this case, a time-resolved light measuring device is used as the detector 8. For the detector 8, for example, a streak camera or an optical oscilloscope may be used. The data measured by the detector 8 is stored / calculated by the computer 9 and displayed on the display unit 10. Instead of the lenses 3 and 6, another optical system such as a concave mirror may be used. Further, light may be guided from the light source 1 to the scatterer 4 using an optical fiber. Similarly, the light passing through the pinhole 22 may be guided to the detector 8 by using an optical fiber. Further, an optical system having a linear focus may be used as the lenses 3 and 21. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

FIG. 15 is a block diagram of an apparatus for measuring light having a wavelength different from the incident light, which is another embodiment of the biological light measuring apparatus according to the present invention. The light emitted from the light source 1 is made incident inside from the site where the scatterer 4 exists by the incident optical fiber 23, and a part of the incident light reaches the focal point 5 to excite the fluorescent substance in the focal point. The fluorescence emitted thereby becomes parallel light by the lens 3, is condensed by the lens 21, passes through the cut filter 27, and is focused on the pinhole 22. The focused light passes through the pinhole 22 and is guided to the detector 8 by the detection optical fiber 24. Similar to FIG.
Also in this case, a time-resolved light measuring device may be used as the detector 8, and for example, a streak camera or an optical oscilloscope may be used. The measured data is stored and stored as in the case of FIG.
Calculated and displayed. Instead of the lenses 3 and 21, another optical system such as a concave mirror may be used. As shown in FIG. 14, light may be guided without using the detection optical fiber. The cut filter 27 may be placed between the pinhole 22 and the detector 8. Further, an optical system having a linear focus may be used as the lenses 3 and 21. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

In FIGS. 14 and 15, the lengths of the respective parts of the optical system are L ₄ , L ₅ , L ₆ , the lengths of the incident and detecting optical fibers are L _in , L _out , and the depth of the focal point viewed from the sample surface. Let d be the light velocity in the air, c be the light velocity in the scatterer, c _{s be} the light velocity in the optical fiber, and c _f be the light velocity in the optical fiber. Scattered by detector 8
The time τ to reach is when the optical fiber is not used (Fig. 14), when the optical fiber is used (Fig. 15)
It becomes the number 6.

[0039]

(5) τ = (L ₄ + L ₆ ) / c + (L ₅ + 2d) / c _s (Equation 5)

[0040]

## EQU6 ## τ = L ₆ / c + (L ₅ + 2d) / c _s + (L _in + L _out ) / c _f (Equation 6) From the time τ in the signals time-resolved and measured in FIGS. 14 and 15. By using the signal in the time gate up to τ + Δτ, the number of scatterings in the sample is small, and it is possible to collect the light that has traveled almost straight. The light measured at the time in the gate is used for calculation.

FIG. 16 is a block diagram of an embodiment of the present invention using an optical shutter using a non-linear element. The optical shutter 29 has a property of passing the measurement light by the Kerr effect while the reference light is incident. The pulsed light emitted from the light source 1 is guided to the optical system and is incident on the sample.
It is split into reference light that enters the optical shutter 29 via the delay unit 28. The reference light is delayed by the delay unit 28 and enters the optical shutter 29. As a result, the light that reaches the detector 8 within the gate at a specific time is transmitted by the optical shutter 29.
Pass through. The time width of the time gate is also adjusted by the delay unit 28. When the distance from the light source 1 to the optical shutter 29 via the delay unit 28 is L _re , this delay time τ ′ is 7 when the optical fiber is not used and 8 when the optical fiber is used.

[0042]

Τ ′ = τ−L _re / c (Equation 7)

[0043]

Τ ′ = τ−L _re / c _f (Equation 8) By delaying τ ′ and continuing to irradiate light for a minute time Δτ, it is possible to pass the light of the time gate τ ′ + Δτ. Becomes Further, as shown in FIG. 15, an optical fiber may be used to guide the light emitted from the light source 1 to the optical system. Similarly, light that has passed through the pinhole 22 may be guided to the detector 8 using an optical fiber. Similarly, the reference light may be guided to the optical shutter 29 via the delay unit 28 using an optical fiber. At this time, L _re is the length of the reference light optical fiber. The light speed c _f in the optical fiber is used instead of the light speed c in the air. In this case, the detector 8 may be a detector that cannot perform time-resolved measurement, such as a photomultiplier tube.

Further, instead of the lenses 3 and 21, other optical means such as a concave mirror may be used. Instead of the half mirror 2, other optical means such as a deflection mirror may be used. Instead of the half mirror 2, for example, FIG.
As described above, a dichroic mirror may be used, and a cut filter may be placed in front of the pinhole 22 to measure the fluorescence emitted from the focal point 5. Further, an optical system having a linear focus may be used as the lenses 3 and 21. When using an optical system having a linear focus, a linear slit having a finite area may be used instead of the pinhole 22.

FIG. 17 is an explanatory view of an optical probe portion attached to the apparatus of FIGS. 14, 15, and 16 and fixed to the sample. The light scattered at the focal point 5 of the sample is reflected by the lens 3,
And 21 to focus on pinhole 22. The light passing through the pinhole 22 is guided to the detector 8 by the detection optical fiber 24. The fixing unit 12 fixes the device so that the sample surface is stable and does not leak light. An adhesive seal may be used for the fixing portion 12, for example. The lens barrel portion 13 supports the optical system and has a structure in which light does not leak. The inner surface of the lens barrel portion 13 may be covered with a light absorbing film. By operating the slide unit 14, the lens 3 moves up and down, and the focus is scanned in the depth direction. The operation of the slide part
For example, a motor may be used. Alternatively, the slide unit may be manually operated.

FIG. 18 is a configuration diagram of a probe portion similar to FIG. By moving the galvanometer 15, the focus can be scanned in the direction horizontal or vertical to the sample surface. Instead of the galvanometer 15, another optical system may be used to scan the focus.

FIG. 19 is an example in which the embodiment of FIGS. 14, 15 and 16 is applied to a head and brain function measuring device. An optical fiber 32 arranged on the surface of the subject makes light incident from an arbitrary part of the subject, and fixes one or a plurality of optical probes 33 to the head 17 of the subject to measure the activity of a specific brain spot. To do. Since the light is guided by the detection optical fiber 24 and the optical fiber 32, the optical probe 33 can be attached to any part of the subject's head.
A plurality of probes may be bundled and used. Optical fiber 3
2 may be inserted into the subject and used. Further, this embodiment may be used for measuring other samples.

FIG. 20 shows an example in which the embodiments of FIGS. 14, 15 and 16 are applied to a diagnostic device. The optical probe 34 is applied to the measurement site of the subject 17 on the pedestal 20.
The probe 34 moves vertically and horizontally by a probe moving mechanism built in the support portion 19. Light incident from an arbitrary portion of the subject through the optical fiber 32 arranged on the subject surface is measured by the optical probe 34 and sent to the detector 8. The data detected by the detector 8 is
It is calculated by the computer 9 and displayed on the display unit 10.
The optical fiber 32 may be inserted into the non-specimen for use. Furthermore, the present embodiment may be used for measuring a sample other than a living body.

As described above, in FIG. 1 to FIG. 7 and FIG. 9 to FIG. 20, the light source 1 is a one-wavelength or multi-wavelength light source.

[0050]

By using the optical measuring device of the present invention, it is possible to measure scattered light or fluorescence at a specific spot in a scatterer sample. Can be performed without being affected by. Further scanning of the spot provides high resolution 2D and 3D images that are not affected by scattering. Further, by using the scatterer for the sample, even when a high-power laser is used, high energy is not concentrated at the focal position, and the sample can be safely measured without being destroyed.

[Brief description of drawings]

FIG. 1 is a block diagram of an optical measuring device for scattered light measurement according to an embodiment of the present invention.

FIG. 2 is an explanatory view of an optical probe fixed to a sample of an example according to the present invention.

FIG. 3 is an explanatory diagram of a horizontal scanning optical probe fixed to a sample of an example according to the present invention.

FIG. 4 is a block diagram of an optical measuring device for measuring head and brain functions according to an embodiment of the present invention.

FIG. 5 is a block diagram of a diagnostic optical measurement device according to an embodiment of the present invention.

FIG. 6 is a block diagram of a laser confocal light measuring device for measuring scattered light according to an embodiment of the present invention.

FIG. 7 is a block diagram of a laser confocal optical measurement device for fluorescence measurement according to an embodiment of the present invention.

FIG. 8 is a characteristic diagram of a time spectrum of light intensity detected by the device of the present invention.

FIG. 9 is a block diagram of a laser confocal optical measurement device that performs time-resolved measurement using the optical shutter of the embodiment according to the present invention.

FIG. 10 is an explanatory diagram of an optical probe fixed to a sample of an example according to the present invention.

FIG. 11 is an explanatory diagram of a horizontal scanning optical probe fixed to a sample of an example according to the present invention.

FIG. 12 is a block diagram of a laser confocal optical measurement device for measuring head and brain function according to an embodiment of the present invention.

FIG. 13 is a block diagram of a diagnostic laser confocal optical measurement device according to an embodiment of the present invention.

FIG. 14 is a block diagram of an optical measuring device for scattered light measurement according to an embodiment of the present invention.

FIG. 15 is a block diagram of an optical measurement device for fluorescence measurement according to an example of the present invention.

FIG. 16 is a block diagram of an optical measurement device that performs time-resolved measurement using the optical shutter of the embodiment according to the present invention.

FIG. 17 is an explanatory diagram of an optical probe fixed to a sample of an example according to the present invention.

FIG. 18 is an explanatory diagram of a horizontal scanning optical probe fixed to a sample of an example according to the present invention.

FIG. 19 is a block diagram of an optical measurement device for measuring head and brain functions according to an embodiment of the present invention.

FIG. 20 is a block diagram of a diagnostic optical measurement device according to an embodiment of the present invention.

[Explanation of symbols]

1 ... Light source part, 2 ... Half mirror, 3 ... Lens, 4 ... Sample, 5 ... Focus, 8 ... Photodetector, 9 ... Computer, 10
... display part, 21 ... lens, 22 ... pinhole.

Front page continuation (72) Inventor Atsushi Maki 1-280, Higashi Koigokubo, Kokubunji, Tokyo, Hitachi Central Research Laboratory (72) Inventor Hideaki Koizumi 1-280, Higashi Koikeku, Kokubunji, Tokyo Hitachi Central Research Laboratory (72) Inventor Yoshitoshi Ito 1-280, Higashi Koigokubo, Kokubunji, Tokyo Inside the Central Research Laboratory, Hitachi, Ltd.

Claims (26)

[Claims] 1. A measuring device having a light source, an optical system, an optical modulator, a light branching means, and a detector, wherein the light emitted from the light source is split into two by the branching means, and one of the branched lights is provided. Is guided into the sample by the optical system and focused, and the light that is scattered at the focus and is guided again to the optical system is combined with the other branched light modulated by the optical modulator, An optical measuring device characterized by detecting a parallel component in reflected light from a sample by detecting the light generated by. 2. The optical measuring device according to claim 1, wherein the depth or position of the focal point in the sample is adjusted by moving the optical system. 3. The optical measuring device according to claim 1, wherein a two-dimensional or three-dimensional image is obtained by scanning the focal point. 4. An optical measuring device according to claim 1, 2 or 3, wherein an optical system for forming a linear focus is used. 5. The optical measuring device according to claim 1, 2, 3 or 4, wherein a plurality of light sources having different wavelengths are used. 6. The method according to claim 1, 2, 3, 4 or 5.
An optical measuring device that fetches the detected data into a computer and calculates a plurality of data by the plurality of light sources or performs image processing. 7. An apparatus having a light source that emits pulsed light, a first optical system that focuses on an arbitrary position in a sample, and a second optical system that focuses on a pinhole having a finite area. ,
The pulsed light emitted from the light source is guided to the first optical system, and the sample is focused by the first optical system, and the light scattered from the focus and the fluorescence emitted from the focus are again detected by the first optical system. The parallel light is guided to one optical system, and the parallel light is focused on the pinhole having a finite area by the second optical system, and the light passing through the pinhole is guided to the detector for time-resolved measurement. An optical measuring device characterized by: 8. An apparatus having a light source that emits pulsed light, a first optical system that focuses on an arbitrary position in a sample, and a second optical system that focuses on a pinhole having a finite area. ,
The light emitted from the light source is incident on the sample, the light scattered from the focus in the sample and the fluorescence emitted from the focus are converted into parallel light by the first optical system, and the finite area by the second optical system. An optical measuring device characterized in that a light is passed through the pinhole and guided to a detector for time-resolved measurement. 9. The optical measuring device according to claim 7, wherein a data signal detected in a time gate having a specific time width is used for calculation. 10. The light emitted from a light source is incident on the sample, and is detected via a focal point in the sample and an optical system when the sample is assumed to be a transparent medium. When the shortest time to reach the vessel is τ, the data detected in the time gate from time τ to time τ + Δτ among the light measured by time resolution with the light emission time of the light source as the time origin is used for the arithmetic processing. Optical measuring device. 11. The optical measuring device according to claim 9, wherein the start time τ of the time gate is changed in association with the depth of the focus in the sample or the distance from the light incident point to the focus. 12. The optical measuring device according to claim 7, 8, 9, 10 or 11, wherein the depth or position of the focal point in the sample is adjusted by moving the first optical system. 13. A method according to claim 7, 8, 9, 10, 11 or 1.
2. An optical measuring device according to 2, wherein a two-dimensional or three-dimensional image is obtained by scanning the focal point. 14. An optical measuring device according to claim 7, 8, 9, 10, 11, 12 or 13, wherein an optical system for forming a linear focus is used. 15. Claims 7, 8, 9, 10, 11, 12,
13 or 14 is an optical measuring device using a plurality of light sources having different wavelengths. 16. A method according to claim 7, 8, 9, 10, 11, 12,
13. An optical measuring device according to 13, 14 or 15, which incorporates the detected data into a computer and calculates a plurality of data by the plurality of light sources or performs image processing. 17. A light source that emits pulsed light, a detector, a first optical system that focuses on an arbitrary position in a sample, and a second optical system that focuses on a pinhole having a finite area. , A device having an optical shutter consisting of a non-linear element, which guides the pulsed light emitted from the light source to the first optical system, focuses the sample in the sample by the first optical system, and scatters the light at the focal point. And the fluorescence emitted from the focal point is again guided to the first optical system to be parallel light, and the parallel light is focused on a pinhole having a finite area by the second optical system and passes through the pinhole. An optical measuring device, wherein the detected light is guided to an optical shutter, and the light passing through the optical shutter is detected by a detector. 18. A light source that emits pulsed light, a detector, a first optical system that focuses on an arbitrary position in a sample, and a second optical system that focuses on a pinhole having a finite area. , An optical measuring device having an optical shutter composed of a non-linear element,
The light emitted from the light source is incident on the sample, the light scattered from the focus in the sample and the fluorescence emitted from the focus are converted into parallel light by using the first optical system, and the second light is emitted. Use an optical system to focus on a pinhole with a finite area,
Guide to the second optical system to focus on the pinhole, guide light passing through the pinhole to the optical shutter, pass light reaching the optical shutter within a specific time, and detect An optical measuring device characterized by being detected by a measuring instrument. 19. The optical measuring device according to claim 17, wherein an optical shutter is opened within a specific time gate, light passing through the optical shutter is detected, and the detection signal is used for arithmetic processing. 20. The apparatus according to claim 17, 18 or 19, wherein, when the sample is assumed to be a transparent medium, light emitted from a light source is incident on the sample and further passes through a focal point in the sample and an optical system. When the shortest time to reach the detector is τ, the optical shutter is opened from time τ to time τ + Δτ, where the light emission time of the light source is the time origin, and the light passing through the optical shutter is detected during that time. , Optical measurement device used for arithmetic processing. 21. The optical measurement according to claim 17, 18, 19 or 20, wherein the opening time τ of the optical shutter is changed in association with the depth of the focal point in the sample or the distance from the incident point of light to the focal point. apparatus. 22. A method according to claim 17, 18, 19, 20 or 2.
1 is an optical measurement device for adjusting the depth or position of a focal point in a sample by moving the first optical system. 23. The optical measuring device according to claim 17, 18, 19, 20, 21 or 22, which obtains a two-dimensional or three-dimensional image of a sample by scanning a focal point formed in the sample. 24. A method according to claim 17, 18, 19, 20, 21,
22 or 23, an optical measuring device using an optical system for forming a linear focus. 25. A method according to claim 17, 18, 19, 20, 21,
22, 23, or 24, an optical measuring device using a plurality of light sources having different wavelengths. 26. A method according to claim 17, 18, 19, 20, 21,
An optical measuring device which captures the detected data in 22, 23, 24, or 25 in a computer and calculates a plurality of data by the plurality of light sources or performs image processing.