JPH09149903A - Body interior imaging device by scattering light - Google Patents

Abstract

PROBLEM TO BE SOLVED: To efficiently image and measure information of an in-vivo wide space region by irradiating lights of different modulation frequencies at every plurality of parts and measuring modulation of a passing light obtained in a plurality of detection parts. SOLUTION: Each optical module 2 is composed of semiconductor lasers irradiating lights of a plurality of wavelengths in a wavelength region from visible rays to infrared rays and the semiconductor lasers are modulated by different frequencies by oscillating parts of oscillators 3 of different oscillating frequencies respectively. Three-wavelength lights are introduced into an irradiation optical fibers 8-1 to 8-16 according to each optical module and irradiated from an irradiation position of a subject 9. Its reflection lights are detected by detection optical fibers 10-1 to 10-25 arranged in detection positions and a modulated signal matched with an irradiation Position and wavelength is selectively detected bar a lock-in amplification module 12. Then, an analog output sill is converted into a digital signal by an A/D converter 14, calculated by a data processing part 16, and imaged and displayed on a display 17.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a technical field relating to an apparatus for imaging information inside a light scatterer, for example, inside a living body using light.

[0002]

2. Description of the Related Art An apparatus for measuring the inside of a living body easily and without harming the living body is desired in the fields of clinical medicine and brain science. For example, when the head is specifically considered as a measurement target, brain diseases such as cerebral infarction and intracerebral hemorrhage and higher brain functions such as thinking, language, and movement can be measured. Further, such an object to be measured is not limited to the head, and examples thereof include preventive diagnosis for heart diseases such as myocardial infarction in the chest and visceral diseases such as kidneys and liver in the abdomen. When measuring a disease or higher brain function in the brain by considering the head as a measurement target, it is necessary to clearly specify the diseased part or functional region. Therefore, it is very important to measure a wide area of the head as an image. As an example showing this importance, the positron emission tomography device (PET) and the functional nuclear magnetic resonance tomography device (fMRI) are currently widely used as image measuring devices in the brain. While these devices have the advantage of being able to measure a wide area inside a living body as an image, they are large and their handling is complicated. For example, the installation of these devices requires a dedicated room, which of course is not easy to move, and is highly restrictive to the subject. In addition, since a dedicated person for maintenance management is also required,
The operation of the device requires a huge cost.

On the other hand, optical measurement is very effective for the above-mentioned demand. The first reason is that normal and abnormal internal organs, as well as activation of the brain related to higher brain functions, are closely related to oxygen metabolism and blood circulation inside the body. This oxygen metabolism and blood circulation correspond to the concentrations of specific dyes (hemoglobin, cytochrome aa ₃ , myoglobin, etc.) in the living body, and this dye concentration is obtained from the amount of light absorption in the visible to infrared wavelength range. . The second and third reasons why optical measurement is effective are that light is easy to handle with an optical fiber, and that it does not harm the living body when used within the range of safety standards. As described above, the optical measurement has advantages that PET and fMRI do not have, such as real-time measurement and quantification of dye concentration in the living body, and the optical measurement device is suitable for miniaturization and simplification. An apparatus for measuring the inside of a living body by irradiating the living body with light having a wavelength from visible to infrared and detecting the light reflected from the living body by utilizing such an advantage of the optical measurement is disclosed in, for example, JP-A-57 / 57. -1152
32, JP-A-63-260532, JP-A-63-275323 or JP-A-5-3172.
No. 95 publication.

[0004]

However, the above-mentioned optical measurement technique using light can measure only a specific position of a living body or a limited narrow area, and does not consider image measurement in a wide spatial area of the living body. Here, regarding the light measurement method and the light irradiation / detection point arrangement, specific problems with the conventional method will be described below. First, the optical measurement method will be described. Image measurement in a wide space region requires light irradiation and detection at multiple points. An example of this multipoint measurement is shown in FIG.
I will briefly explain. In this example, light is irradiated from three positions (“irradiation position 1”, “irradiation position 2”, and “irradiation position 3”) on the surface of the subject, and reflected light is irradiated at three positions on the surface of the subject (“ The case where light is detected at "detection position 1", "detection position 2", and "detection position 3""is shown. In the case of image measurement, the measurement position must be specified. Regarding light propagation in a light scatterer, for example, in a living body, for example, NC Bruce describes “Experimental Study of Effects of Absorptive and Permeable Inclusions in Highly Scattering Media (Experimen
tal study of the effect of absorbing and transmitt
ing inclusions in highly scattering media) ", 19
October 1, 1994, Applied Optics, No. 33
Vol. 28, Nos. 6692-6698 (Applied optic
s, 33,28,6692 (1994)) and the results are shown in FIG. From FIG. 3, it is known that the vicinity of the midpoint of the light irradiation position and the detection position has a lot of information about a deep place from the surface. Therefore, when measuring a deep part of a living body, for example, a deeper part of the skin or bone from above the skin, the midpoint of the irradiation / detection position is the measurement position. For such measurement, it is necessary to pair the irradiation and detection positions and obtain information at the measurement position specified for each pair.

For example, in the measurement arrangement of FIG. 2, consider a case where light is emitted from these three irradiation positions at the same time and detected at three detection positions. In this case, in the measurement for the "measurement position 2" which is the midpoint between the "irradiation position 2" and the "detection position 2", the light detected at the "detection position 2" was irradiated at the "irradiation position 2". It is necessary to measure light accurately. However, in this case, the light detected at "detection position 2" is not limited to "irradiation position 2" but "irradiation position 1".
And the light emitted from the “irradiation position 3” is also included, that is, crosstalk occurs. Therefore, it is not possible to accurately obtain the detected light amount of the light emitted at the “irradiation position 2”. Here, if the measurement positions are sequentially switched using a switch or the like for each irradiation position, such crosstalk will not occur, but switching of many irradiation positions requires that much switching time. However, it becomes inefficient in time. An object of the present invention is to solve the above problems and to provide a small and simple apparatus using light, which is an apparatus for efficiently performing image measurement of information inside a living body in a wide space region in terms of time and system. Is to provide.

[0006]

In order to achieve the above object, the present invention irradiates a plurality of portions of a scatterer with light having a plurality of wavelengths in the visible to infrared region, and scatters light passing through the inside of the scatterer. In an apparatus for detecting and imaging from a plurality of parts of, for example, an oscillator, a semiconductor laser, an optical fiber,
Light with different modulation frequencies is generated and irradiated at each of multiple sites, and the transmitted light obtained at the multiple sites is detected by, for example, an optical fiber, a photodetector including a photodiode, a lock-in amplifier, an A / D converter, or the like. By performing modulation measurement, information on the inside of the scatterer corresponding to each irradiation position and detection position is imaged.

[0007]

BEST MODE FOR CARRYING OUT THE INVENTION In the present invention, in order to solve the above-mentioned problem of crosstalk, light having a different modulation frequency is irradiated for each irradiation position. For example, in "irradiation position 1", "irradiation position 2", and "irradiation position 3" shown in FIG.
Light of modulation frequencies f1, f2, and f3 is emitted.
In this case, when the light is detected at the "detection position 2", the detection light is converted into an electric signal by a photodetector, for example, a photomultiplier tube or a photodiode, and then the modulation frequency and phase are the frequencies irradiated at the irradiation position 2. When the detection is performed in synchronization with f2 (lock-in detection), only the detected light amount of the modulation frequency f2 emitted from the “irradiation position 2”, the modulation frequency f1 emitted from the “irradiation position 1” and the “irradiation position 3”, f3
It becomes possible to separate from and to measure selectively. Further, in the case of performing spectroscopic measurement using a plurality of wavelengths as irradiation light for quantitatively measuring the pigment concentrations of hemoglobin, cytochrome aa ₃ , and myoglobin, different modulation frequencies are assigned and irradiation is performed for each wavelength. By doing so, lock-in detection is performed for each of the modulation frequencies with respect to the light of different wavelengths that irradiate the same position, so that light of multiple wavelengths is reflected by the optical filter, diffraction grating, prism, etc. It becomes possible to perform spectroscopic measurement electrically without relying on the optical spectroscopic means accompanied by the loss of.

Further, when this modulation method is used, not only the light from the "irradiation position 2" but also the "irradiation position 1" and the "irradiation position 3" are detected with respect to the light detected at the "detection position 2". It is also possible to measure the detected light amount of the emitted light. This advantage is related to efficient light irradiation / detection point arrangement, and details thereof will be given below. When a specific irradiation position and a detection position are exclusively assigned to a plurality of measurement positions for each measurement position, that is, when there are three measurement positions as shown in FIG. 2,
Three irradiation positions and three detection positions are required. Here, when the irradiation positions and the detection positions are alternately arranged in a grid pattern so as to be shared by a plurality of measurement positions as shown in FIG. 4, there are only two irradiation positions and two detection positions, and four irradiation positions are detected. The measurement position of can be set. here,
By the above-described modulation measurement, the light at the “irradiation position 1” and the “irradiation position 2” with different modulation frequencies are independently measured by the lock-in detection with respect to the light measured at the “detection position 1” in FIG. By doing so, it is possible to simultaneously measure “measurement position 1” and “measurement position 2”. Similarly, for the light measured at "detection position 2", "irradiation position 1" and "irradiation position 2" with different modulation frequencies are used.
By measuring the light of each by lock-in detection,
It is possible to simultaneously measure “measurement position 3” and “measurement position 4”. As described above, the number of irradiation positions (that is, the number of associated light sources) and the detection positions (that is, the number of associated detectors) can be significantly reduced, and the efficiency of the system is improved.

[0009]

Embodiments of the present invention will be described below in detail. (First Embodiment) FIG. 1 is a block diagram showing the essential parts of an imaging apparatus according to the first embodiment of the present invention. In the present embodiment, for example, an embodiment in which the inside of the cerebrum is imaged by irradiating and detecting light from above the skin of the head is shown when the number of measurement channels, that is, the number of measurement positions is 64. The light source unit 1 is composed of 16 optical modules 2.
Each optical module is composed of three semiconductor lasers that respectively emit light of a plurality of wavelengths in the visible to infrared wavelength region, for example, three wavelengths of 770 nm, 805 nm, and 830 nm. All of the 48 semiconductor lasers included in the light source unit 1 are modulated at different frequencies by the oscillation unit 3 composed of 48 oscillators having different oscillation frequencies.

Here, the internal structure of the optical module 2 will be described with reference to FIG. 5 by taking the optical module 2 (1) as an example. In the optical module 2 (1), semiconductor lasers 3 (1-a), 3 (1-b), 3 (1-
c), and drive circuits 4 (1-a), 4 (1-b), 4 for these lasers,
(1-c) is included. Here, regarding the characters in the parentheses, the numbers indicate the included optical module numbers, and a, b, and c indicate wavelengths of 770 nm, 805 nm, and 830 nm, respectively. These semiconductor laser drive circuits 4 (1-a), 4 (1-
b) By applying different frequencies f (1-a), f (1-b), and f (1-c) by the oscillator 3 to 4 (1-c),
The light emitted from the semiconductor lasers 3 (1-a), 3 (1-b) and 3 (1-c) is modulated. The light emitted from these semiconductor lasers is individually introduced into the optical fiber 6 by the condenser lens 5 for each semiconductor laser. The light of three wavelengths introduced into each optical fiber is introduced into one optical fiber, for example, the irradiation optical fiber 8-1 by the optical fiber coupler 7 for each optical module. For each optical module, three wavelengths of light are emitted from the optical fibers 8-1 to 8-
The light is introduced into the optical fiber 16 and the subject is irradiated with light from the other end of these irradiation optical fibers from 16 different positions on the surface of the subject 9. The light reflected from the subject is detected by the detection optical fibers 10-1 to 10-1 arranged at 25 locations on the surface of the subject.
It is detected at 0-25.

Here, FIG. 6 shows a geometrical arrangement of irradiation positions 1-16 and detection positions 1-25 on the surface of the subject. In this embodiment, the irradiation / detection positions are alternately arranged on a square lattice. At this time, assuming that the midpoint of the adjacent irradiation / detection positions is the measurement position, in this case, there are 64 combinations of the adjacent irradiation / detection positions, and therefore the number of measurement positions, that is, 64 measurement channels. If the distance between adjacent irradiation and detection positions is set to 3 cm, the light detected at each detection position may have cerebral information after passing through the skin and the skull, for example, Pee Double McCormick. (PWMcCormic) et al. "Infrared penetration of cerebral light
(Intracerebral penetration of infrared light) ",
1992, Journal of Neurosurgery, 7th
Volume 6, Items 315-318 (J. Neurosurg., 33,315 (199
2)). Therefore, if 64 measurement channels are set in this irradiation detection position arrangement, the cerebrum can be measured in a wide area of 15 cm × 15 cm as a whole. Each detection optical fiber 10-1 to 10
The reflected light captured by −25 is detected by 25 photodetectors, for example, photodiodes 11-1 to 11-25 independently for each detection position, that is, for each detection optical fiber.
After the optical signal is converted into an electric signal by these photodiodes, the lock-in amplifier module 12 including a plurality of lock-in amplifiers selectively detects the modulation signal corresponding to the irradiation position and the wavelength.

Here, a concrete example of the modulation signal separation will be described with reference to FIG. 7 by taking the detection signal at the detection position 7 in FIG. 6, that is, the detection signal at the photodiode 11-7 as an example. In the "detection position 7", the adjacent "light irradiation position 1",
Light emitted from "light irradiation position 2", "light irradiation position 5", "light irradiation position 6", that is, "measurement position 10",
"Measurement position 11", "Measurement position 18", "Measurement position 1"
9 ”is the measurement target. Here, the photodiode 11
The light detected at -7 is mainly the modulation frequencies f (1-a), f (1) irradiated at "irradiation position 1", "irradiation position 2", "irradiation position 5", and "irradiation position 6". -b), f (1-c), f (2-a), f (2
-b), f (2-c), f (5-a), f (5-b), f (5-c), f (6-a),
It contains twelve modulation frequency signals f (6-b) and f (6-c). Therefore, the output signal of the photodiode 11-7 is set to 1
Twelve lock-in amplifiers 13- each of which is divided into two parts and uses these twelve modulation frequencies as reference signals.
31 to 13-42. As a result, for example, in the lock-in amplifier 13-31, the frequency of the reference signal is f (1-a)
Therefore, with respect to the light detected by the photodiode 11-7, only the light having the wavelength of 770 nm emitted at the “irradiation position 1”, that is, the light having the modulation frequency of f (1-a) is selectively selected. Can be detected. Similarly, in other lock-in amplifiers, it is possible to selectively detect light of a specific irradiation position and wavelength. In this way, even for light detected at other detection positions, that is, detection signals from other photodiodes, lock-in detection is individually performed for modulation frequencies corresponding to adjacent irradiation positions and wavelengths. As a result, it becomes possible to measure the amount of detected light at all measurement positions and wavelengths. In the case of three wavelengths and 64 measurement positions shown in this embodiment,
The lock-in module 12 includes a total of 192 lock-in amplifiers.

These lock-in amplifiers 13-1 to 13
-192 analog output signal is 192 channel A
The signals are converted into digital signals by the / D converter 14 and recorded in the data recording unit 15. Further, these recorded signals are used in the data processing unit 16 to detect the oxygenated hemoglobin concentration and the deoxygenated hemoglobin concentration, and the total hemoglobin concentration as the total hemoglobin concentration, by using the detection light amounts of the three wavelengths for each measurement position. For example, it is determined by the method described in "Two-wavelength spectrophotometric method and its application" written by Shozo Shibata, etc., published by Kodansha, 1979. The oxygenated hemoglobin, deoxygenated hemoglobin, and total hemoglobin concentration obtained at each measurement position are displayed on the display unit 17 as, for example, a topography image.
In this topography image, for example, each hemoglobin concentration at each measurement position is obtained by interpolating between measurement positions, for example, linear interpolation. The above measurement is controlled by the control unit 18.

Further, for the light irradiation and the light detection on the subject,
For example, a probe 21 having a helmet or cap shape as shown in FIG. 8 is used. This probe 21
For example, a thermoplastic plastic sheet having a thickness of about 3 mm is used as a base. A mold, that is, a mold is created in advance in the measurement region of the subject using this substrate, and the subject is attached with, for example, a rubber strap 22. The structure of this probe will be described with reference to FIG. Holes are formed in the probe board 23 at each of a plurality of positions for irradiating and detecting light on the subject. The optical fiber holder 24 is placed in this hole. The optical fiber holder 24 includes a hollow holder body 24, a nut screw 25, and an optical fiber fixing screw 26.
The holder main body 23 is fixedly attached to the probe base 23 by the nut screw 25. An irradiation optical fiber or a detection optical fiber is inserted into the inside of the holder body 23, and the optical fiber is lightly contacted with the surface of the subject and fixed by the optical fiber fixing screw 26. Although the number of measurement channels is 64 in the present embodiment, the number of channels is not limited in the implementation of the present invention. It should be noted that this embodiment can be easily applied to an optical CT apparatus in which tomography of the inside of a human body is performed using light and the obtained data is image-processed by a computer.

(Second Embodiment) A second embodiment according to the present invention will be described with reference to FIG. In this embodiment, the basic structure of the measurement system is similar to that of the first embodiment, and the structure of the light source unit 1 is different. FIG. 10 shows the light source unit 1 of the second embodiment. A light source having a wavelength of 770 nm, for example, a semiconductor laser 31 is driven by a laser driving circuit 41 and emits continuous light to which no modulation is applied. This light is introduced into the optical fiber 6 and distributed by the optical fiber coupler 51 to the 16 optical fibers 61-1 to 61-16. These optical fibers have optical modulators 71-1 to 71-in their paths.
16 is included. The structures of these optical modulators are shown in FIG. 11 using the optical modulator 71-1 as an example. A liquid crystal filter 101, for example, is built in the optical modulator, and the liquid crystal filter is periodically turned on and off by a modulation voltage signal from an oscillator in the oscillator 3. For example, the optical modulator 71-1 applies the modulation frequency f (1-a) to the liquid crystal filter 101. The light from the optical fiber 61-1 is irradiated onto the liquid crystal filter 101 via the lens 5, and the light transmitted through this liquid crystal filter is condensed by the lens 5 and is introduced again into the optical fiber 81-1. Here, the optical modulators 71-1 to 71-16 have different modulation frequencies,
For example, the liquid crystal filter is turned on / off at f (1-a), f (2-a) to f (16-a). As the light modulator, a rotary mechanical optical chopper may be used instead of the liquid crystal filter.

Similarly, a light source of another wavelength inside the light source section, for example, a semiconductor laser 3 having wavelengths of 805 and 830 nm is used.
The laser drive circuits 42, 4 are also provided for the reference numerals 2, 33, respectively.
And 16 optical fibers in each of the optical fiber couplers 52 and 53 for each wavelength.
1 to 62-16 and 63-1 to 63-16. Here, the optical modulators 72-1 to 7-7 are provided with different modulation frequencies for the lights transmitted through these optical fibers.
2-16 and 73-1 to 73-16. Here, in the optical modulators 72-1 to 72-16, the modulation frequencies f (1-b) to f (16-b) are respectively changed to the optical modulators 73-1 to 7-16.
73-16, modulation frequencies f (1-c) to f (16
-c) is applied. Here, the optical modulators 72-1 to 72-1
The light transmitted through the optical fiber 6 is the optical fibers 82-1 to 82
The light transmitted through the optical modulators 83-1 to 83-16 is re-introduced into the optical fibers 83-1 to 83-16. Here, forty-eight optical fibers each containing light that has passed through a total of forty-eight optical modulators are introduced into one optical fiber for every three wavelengths in the following manner. For example, the optical fibers 81-1, 82-1 and 83-1 are connected to one irradiation optical fiber 8 by the optical fiber coupler 91-1.
-1 is introduced. Similarly, the optical fiber 81-1
The optical fibers up to 6, 82-16, 83-16 are introduced into one irradiation optical fiber 8-16 by the optical fiber coupler 91-16. The irradiation optical fibers 8-1 to 8-16 containing lights each having three wavelengths and different modulation frequencies from each other irradiate the subject in the same manner as in the first embodiment. In addition, the measurement using these lights is also the first
This is the same as the embodiment.

[0017]

As described above, according to the present invention, information in the living body can be efficiently processed in a wide space region in terms of time and system, and can be miniaturized.
The image can be easily measured.

[Brief description of the drawings]

FIG. 1 is a block diagram showing a configuration of an imaging device according to a first exemplary embodiment of the present invention.

FIG. 2 is a diagram illustrating an arrangement of an irradiation position, a detection position, and a measurement position in optical measurement.

FIG. 3 is a diagram showing light propagation in a scatterer in optical measurement.

FIG. 4 is a diagram showing an efficient light irradiation / detection position arrangement in the present invention.

FIG. 5 is a block diagram showing a configuration of an optical module according to the first embodiment of the present invention.

FIG. 6 is a diagram showing an irradiation detection position arrangement in the first embodiment of the present invention.

FIG. 7 is a block diagram showing a configuration of a lock-in amplifier module according to the first embodiment of the present invention.

FIG. 8 is a diagram showing a shape of a probe according to the first embodiment of the present invention.

FIG. 9 is a diagram showing a structure of a probe in the first embodiment of the present invention.

FIG. 10 is a block diagram showing a configuration of a light source section in a second embodiment of the present invention.

FIG. 11 is a diagram showing a structure of an optical modulator according to a second embodiment of the present invention.

[Explanation of symbols]

1: Light source part, 2: Optical module, 3: Oscillation part, 3 (1-a)
3 (1-c): semiconductor laser, 4 (1-a) to 4 (1-c): laser drive circuit, 5: condenser lens, 6: optical fiber, 7: optical fiber coupler, 8-1 ~ 8-16: Optical fiber for irradiation,
9: subject, 10-1 to 10-25: optical fiber for detection, 11-1 to 11-25: photodiode, 12:
Lock-in amplifier module, 13-1 to 13-19
2: Lock-in amplifier, 14: A / D converter, 15: Storage unit, 16: Processing unit, 17: Display unit, 18: Control unit, 2
1: probe, 22: elastic band, 23: probe base,
24: optical fiber holder body, 25: nut, 26: optical fiber fixing screw, 31, 32, 33: semiconductor laser,
41, 42, 43: Semiconductor laser drive circuit, 51, 5
2, 53: optical fiber couplers, 61-1 to 61-16,
62-1 to 62-16, 63-1 to 63-16, 81-
1-81-16, 82-1-82-16, 83-1-8
3-16: Optical fiber, 71-1 to 71-16, 72-
1 to 72-16, 73-1 to 73-16: Optical modulator, 9
1-1 to 91-16: Optical fiber coupler, 101: Liquid crystal filter.

Claims (11)

[Claims] 1. A device for irradiating light having a plurality of wavelengths in the visible to infrared region to a plurality of portions of a scatterer and detecting the light passing through the inside of the scatterer from the plurality of portions of the scatterer to form an image, with different modulations. Information about the inside of the scatterer corresponding to each irradiation position and detection position is provided, which is provided with a means for generating light of a frequency and irradiating it for each of a plurality of sites, and a means for performing modulation measurement on the passing light obtained at a plurality of detection sites. A scatterer internal imaging device by light, characterized in that it is configured to image. 2. The imager according to claim 1, wherein the scatterer internal image is formed by applying different modulation frequencies to light of a plurality of wavelengths with which the scatterer is irradiated. Device. 3. The imaging device according to claim 1, wherein the modulation frequency corresponding to the wavelength and the light irradiation position is separated from the signals detected by the plurality of photodetectors. A light scatterer internal imaging device. 4. The imaging device according to claim 1, wherein the scatterer is irradiated with light by an optical fiber, and the light passing through the inside of the scatterer is captured and detected by the optical fiber. Characterized by a light scatterer internal imaging device. 5. The imaging device according to claim 1, wherein a plurality of semiconductor lasers are used as a light source, and these semiconductor lasers are driven by a modulation current or a modulation voltage. Scatterer internal imaging device. 6. The imaging device according to claim 1, wherein the light from the light source is distributed to a plurality of optical fibers, and the light is directly modulated in a light path to a plurality of irradiation sites of the scatterer. A scatterer internal imaging device by light, characterized by being configured. 7. The imager according to claim 6, wherein the liquid scatterer internal imager is configured to directly modulate light with a liquid crystal filter or an optical chopper. 8. The imaging device according to any one of claims 1 to 7, wherein light is irradiated and detected at a position where a grating is formed on the surface of the scatterer, to image the inside of the scatterer by light. apparatus. 9. The imaging device according to claim 8, wherein light is irradiated and detected at lattice points of a square lattice on the surface of the scatterer, and irradiation and detection positions are alternately arranged. A light scatterer internal imaging device. 10. The imaging apparatus according to claim 1, further comprising a probe in which a plurality of light irradiation positions on the scatterer and a plurality of light detection positions from the scatterer are arranged.
Light scatterer internal imaging device. 11. The imager according to claim 10, wherein a thermoplastic resin is used as a base of the probe, and an imager for scatterer inside light is used.