JPH04319345A - Photo-tomographic imaging system - Google Patents

Abstract

PURPOSE:To provide a tomographic with less false image by operating the intensity distribution of light detected with plural photodetection means, at the time, seeking the intensity of transmission light opposite to the irradiation angle of scanned beam light, and conducting image processing whose purpose is to obtain the tomographic image of a testee body from the intensity of this transmission light. CONSTITUTION:Beam light emitted from a light source 2 is radiated toward a testee body 4 by means of a light scanning device 3, and at this time, light received the effects of refraction and scattering and transmitted through the testee body 4 is detected by a detector group 5 consisting of plural detectors D1-Dn arranged in an array form. Signals outputted from respective detectors D1-Dn are inputted into a processing device 7 through an amplifier group 6 consisting of amplifiers Al-An, and processing analysis is performed, and light (optical axis transmission light) that transmitted along an optical transmitted along an optical axis on the occasion of light beam having taken a beam line, sought even if it is transmission light received the effects of refraction and scattering. Next, the irradiation angle of a photoscanning device 3 is sought by means of a controller 9, and a fault image is restructured from the optical axis transmission light and the irradiation angle by an image processing device 8, and the tomographic image is displayed on a display device 10.

Description

[Detailed description of the invention]

0001

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical tomographic imaging apparatus suitable for visualizing information inside a subject using light, such as fluoroscopy of the inside of a living body using light and tomography of the inside of a living body using light.

0002

[Prior Art] Light in the near-infrared region has characteristics such as high permeability to living tissues, absorbance for oxygen indicator substances such as hemoglobin and myoglobin, and changes in the absorption spectrum corresponding to the oxygen binding state. . There have been attempts to utilize such characteristics to image functional information inside a living body. For example, "biological measurement using light",
plus E, May 1987 to March 1988, research on non-invasive measurement of oxygen metabolism in internal tissues such as the heart, ``Basic study on visualization of internal blood vessels using near-infrared light'', electronic information Communication Society Technical Research Report, MB
As shown in E89-67, 1989, studies attempting to image blood vessels have been reported.

Furthermore, Japanese Patent Laid-Open No. 60-72542 describes a method for attempting to display tomographic images of a living body using the same principle as X-ray CT. In this method, highly transparent near-infrared light is irradiated onto a subject such as a living body, and the light transmitted through the subject is detected by detectors arranged in an array on the extension of the optical axis, and the distribution of the transmitted light is measured. This is a device that uses a computer to reconstruct tomographic images from all angles.

0004

[Problems to be Solved by the Invention] Incidentally, the refractive index of light in living tissue is approximately n=1.0 compared to that in air (n=1.0).
It shows a large value of around 4. When a beam of light is irradiated onto an object to be examined, such as biological tissue, refraction and reflection tend to occur on the object's surface due to the difference in refractive index with air, which bends the optical axis of the beam of light that passes through the object. was there. For this reason, the light may not be incident on the detector disposed on the extension of the irradiation optical axis, or the intensity of the light may be lower than that actually transmitted. Moreover, when a tomographic image is reconstructed based on the intensity of transmitted light affected by such refraction, a large false image occurs at the interface between the object and the air, resulting in significant image deterioration. Furthermore, biological tissue is known to be a strong scatterer of light. Therefore, even when a beam of light with a minute diameter is irradiated, the transmitted light will spatially spread widely due to scattering by the living tissue.

The present invention has been made in view of the above-mentioned circumstances, and even if the object to be examined has a large difference in refractive index from air, such as biological tissue, or is a strong scatterer, the transmitted beam light can be It is an object of the present invention to provide an optical tomographic imaging apparatus that can efficiently detect images and easily obtain good tomographic images with few artifacts.

[0006]

Means for Solving the Problems (1) An optical tomographic imaging apparatus according to claim 1 includes a light source that emits a beam of light;
a light scanning means for scanning the subject with the beam light emitted by the light source; and a light scanning means arranged in an array at a position where the light beam scanned by the light scanning means is incident, and light transmitted through the subject. a plurality of light detection means for detecting the light, and calculating the intensity distribution of the light detected by the plurality of light detection means, and determining the intensity of the transmitted light corresponding to the irradiation angle of the beam light scanned by the light scanning means. , and image processing means for performing image processing to obtain a tomographic image of the subject from the intensity of the transmitted light.

(2) In the optical tomographic imaging apparatus according to claim 2, the image processing means determines the irradiation angle of the beam light scanned by the scanning means and the receiving position of the transmitted light detected by the plurality of photodetectors. to correct the irradiation angle of the beam light scanned by the scanning means, and perform image processing to obtain a tomographic image from the intensity of transmitted light corresponding to the corrected irradiation angle of the beam light. .

[0008]

[Function] (1) In the structure according to claim 1, the plurality of light detection means detects the transmitted light transmitted through the subject by the beam light from the light source scanned by the light scanning means, and the image processing means detects the transmitted light transmitted through the object. The intensity distribution of the light detected by the plurality of light detection means is calculated, and the intensity of the transmitted light corresponding to the irradiation angle of the beam light scanned by the light scanning means is determined. Perform image processing to obtain the image.

(2) In the structure according to claim 2, the image processing means performs calculation processing on the irradiation angle of the beam light scanned by the light scanning means and the light receiving position of the transmitted light detected by the plurality of photodetectors. Then, the irradiation angle of the beam light scanned by the optical scanning means is corrected, and image processing is performed to obtain a tomographic image from the intensity of transmitted light corresponding to the corrected irradiation angle of the beam light.

0010

Embodiments Hereinafter, embodiments of the present invention will be described with reference to the drawings. 1 to 3 relate to an embodiment of the present invention, in which FIG. 1 is an overall configuration diagram of an optical tomographic imaging apparatus, FIG. 2 is a characteristic diagram showing an example of the distribution of light intensity detected by a group of detectors, FIG. 3 is an explanatory diagram for correcting the irradiation angle of the beam light. The optical tomographic imaging apparatus 1 shown in FIG. 1 includes a light source 2 that generates a beam of light indicated by a dotted line in the figure, an optical scanning device 3 that scans the beam of light in an irradiation range θ, and a beam of light that is covered by the scanning device 3. A detector group 5 includes a plurality of detectors D1 to Dn arranged in an array for detecting light irradiated onto the specimen 4 and transmitted between the specimens 4 under the influence of refraction and scattering; and the detector D1. -Amplifier group 6 consisting of amplifiers A1 to An that amplify the signals outputted by Dn, respectively;
The amplifier group 6 amplifies the signals corresponding to the transmitted light detected by the detectors D1 to Dn, and processes and analyzes the signals corresponding to the transmitted light detected by the detectors D1 to Dn to determine the optical axis when the light beam travels straight even if the transmitted light is affected by refraction or scattering. a processing device 7 that obtains the light that has passed through the top (hereinafter referred to as optical axis transmitted light); a control device 9 that controls the output of the light source 2 and the irradiation angle of the optical scanning device 3; an image processing device 8 that reconstructs a tomographic image from the irradiation angle;
and a display device 10 that displays the tomographic image.

The operation of the present invention will be explained with reference to FIGS. 1 to 3. First, the light source 2 emits a beam of light, and the optical scanning device 4 irradiates the subject 5 with the beam while scanning it. When the subject 4 has a larger refractive index than air and scatters light, such as biological tissue, the beam of light irradiated to the subject 4 is refracted, further spatially spread, and transmitted. The detector group 5 then detects the refracted and scattered light. The situation will be explained using FIG. 2.

FIG. 2 shows the light intensity distribution measured by the detector group 5 when a beam of light is irradiated at an irradiation angle θx. In the figure,
The horizontal axis represents the positions of the detectors D1 to Dn, and the vertical axis represents the normalized light intensity. When there is no refraction or scattering of light, the beam of light travels straight, so as shown by the dotted line 12 in the figure, it exhibits a distribution where only the detector Dx disposed in an extension of the irradiation angle θx has a maximum distribution. However, in living tissues where light is refracted or scattered, the maximum occurs at the detector Dx+a located off the extension of the illumination angle θx, as shown by the solid line 13 in the figure, and the distribution is spatially spread, resulting in detection of Light can also be detected by instruments. Therefore, the optical axis transmitted light is determined by the processing device 7 from the distribution as shown in practice 13 in FIG. Methods for obtaining this optical axis transmitted light include a method in which the light intensity distribution shown in FIG. Therefore, there is a method of approximating a quartic function or Gaussian distribution by least squares approximation, and finding the peak of this distribution to find the optical axis transmitted light. The image processing device 8 uses the transmitted light thus obtained and the irradiation angle outputted by the scanning device 3 as a pair of data. Similarly, change the irradiation angle and measure the distance between the optical axis transmitted lights. Furthermore, like X-ray CT, the light source 2, optical scanning device 3, and detector group 5 arranged around the subject 4 are rotated,
Transmitted light from all angles is determined, and a tomographic image is reconstructed by the image processing device 8.

In this embodiment, even if the object 4 is a biological tissue that has a large refractive index with respect to air and is a strong scatterer, the beam light that has passed therethrough will be affected by the light on the original optical axis. Can be detected as transmitted light. Therefore, a good tomographic image with less artifacts can be obtained.

Further, with reference to FIG. 3, an operation for further appropriately correcting the irradiation angle will be explained. As shown in FIG. 3, in the above-mentioned device, a value θx is used, which is set in the optical scanning device 3 as the irradiation angle corresponding to the optical axis transmitted light 14, but in reality, the optical axis is set at the irradiation angle due to the influence of refraction. It does not match θx. Therefore, the detector Dx+a that detected the transmitted light
By setting a new irradiation angle to an angle θ=(θx+θx+a)/2 which is the average of the irradiation angle θx+a corresponding to θx+a and the above-mentioned θx, it is possible to approximate the actual optical axis. If such correction is performed, for example, by the image processing device 8, the maximum error can be simply halved, and the image quality of the central part of the subject 4 can be particularly improved. Further, as a correction method, in addition to uniformly correcting at all angles such as the method of calculating the average, calculations may be performed in which each angle is weighted.

[0015] When observing the inside of a living body using light, the resolution and contrast rapidly decrease due to the strong light scattering of the living tissue. Therefore, in order to image the inside of a living body with high resolution using light, it is necessary to eliminate light scattering. As a method for removing this light scattering (a method for suppressing scattered components), there is a method previously filed by the present applicant, and a method described in Japanese Patent Application No. 2-81552.

[0016] This has a configuration as shown in FIG.
This is to suppress scattered light components and provide images with high resolution. This scattered component suppression device 15 includes a light source 16 that irradiates a beam of light, and a photodetector (1) 18 and a photodetector (2) 19 that sandwich a sample 17 and face the light source 16. A collimator (1) 20 is connected to the light receiving side of the photodetector (1) 18, and the collimator (1) 20 is set so that the optical axis is correctly aligned with the optical axis of the light beam from the light source 16. The collimator (1) 20 causes the photodetector (1) 18 to detect the sum of the straight light component that has passed through the sample 17 and the scattered light component of the beam light. On the other hand, a collimator (2) 21 arranged at a constant angle θ1 with respect to the beam light is connected to the detector (2) 19.
is the sample 17 out of the beam light that has passed through the sample 17.
Only the scattered light components scattered by are detected. Further, the photodetector (1) 18 and the photodetector (2) 19 are connected to non-inverting and inverting input terminals of a differential amplifier (1) 22, respectively. ) 22 from the output of photodetector (1) 18 to photodetector (2) 19
By weighting the output by angle θ1 and subtracting it, the scattered light component can be canceled and the straight light component can be extracted.

FIG. 5 shows an example of a scattered component suppression device different from the device shown in FIG. In this embodiment, in the configuration shown in the scattered component suppressing device 15 of FIG. 4, a plurality of means (scattered light detection means) for detecting only the scattered light component consisting of a collimator and a light detector are provided. According to the embodiment of FIG. 5, the spatial resolution can be further improved.

In addition to the configuration shown in FIG. 4, the scattered component suppressing device 15A shown in FIG. Collimator (3) 21a and photodetector (3) 19a, the light output detected by the photodetector (3) 19a, and the light output detected by the photodetector (1) 18 via the collimator (1) 20. a differential amplifier (2) 22a for calculating the difference in optical output;
) 22 and an adder 23 that adds the outputs of the differential amplifier (2) 22a.

With this configuration, the beam light emitted by the light source 16 is irradiated onto the sample 17, and the light transmitted through the sample 17 is transmitted to the photodetector (1) 20 to (3) 21a, respectively. 1) 18 to (3) 19a, respectively. The effects of collimator (1) 20 and collimator (2) 21 are the same as described above. and,
The collimator (3) 21a and the photodetector (3) 19a detect only the scattered light component, and after weighting the optical output by an angle θ2, the differential amplifier (2) 22a detects the scattered light component. Through 20, the photodetector (1)
A differential amplifier (2) 22 performs a difference from the optical output detected at 21 . This allows the scattered light components to be canceled and the straight components to be extracted. Furthermore, if the angularly rectilinear light components detected by the differential amplifier (1) 22 and the differential amplifier (2) 22a are added together by the adder 23, the scattered light components cancel each other out, resulting in a good S/N ratio. Straight light can be detected. Therefore, the scattered light suppressing device 15A can further improve the spatial resolution than the device 15 of FIG. 4. Note that a plurality of the scattered light component detection means may be provided.

FIG. 6 shows another example of the scattered component suppression device. In the apparatus of FIG. 6, the scattered component suppression device 15A of FIG.
In the configuration shown in 2, a means for varying the optical axis is provided in front of the incident part of the scattered light detecting means. Other configurations and operations similar to those of the device 15A in FIG. 5 are designated by the same reference numerals, and description thereof will be omitted. Scattered light suppression device 15B shown in FIG. 6 includes a collimator (2
) 21 and the collimator (3) 21a, an incident angle changing device (1) 24 and an incident angle changing device (2) 24a that change the incident angle with respect to the optical axis of the beam light are arranged in front of the light incident surface of the collimator (3) 21a. There is. The incident angle changing device (1) 24, (2)
24a is a prism or an AO element (acousto-optic element)
Consists of etc.

With this configuration, in order to detect only the scattered light component of the light transmitted through the sample, the incident angle changing device 2
4, 24a and photodetectors 19, 19a, the incident angle changing device (1) 24, (2) 2 changes the incident angle of the beam light with respect to the optical axis.
4a. For example, an angle of incidence focused on the surface of the sample 17, such as the optical axis 25, is changed to an angle of incidence focused on the inside of the sample 17, such as the optical axis 25a.

In this embodiment, since the scattered components can be detected with high precision, measurement with a better S/N ratio is possible, and the spatial resolution can be improved.

Note that the position of the focal point may be determined by scanning within the sample 17. That is, when an AO element is used as the incident angle changing device (1) 24, (2) 24a, the incident angle can be changed over time by changing the signal applied to the AO element, and the focal point can be changed over time. The sample 17 can be scanned.

[0024] As in the above-mentioned example, when imaging the inside of a living body using light, a method is usually used in which light is irradiated from outside the living body and the light is detected outside the living body. For it,
A possible method is to insert a light irradiation means or a light detection means into an organ in a body cavity of a living body, place a light detection means or an irradiation means outside the body, and image the living tissue between the body cavity and the body. . For example, as a conventional example, Japanese Patent Application Laid-open No. 63-135120 and Japanese Patent Application Laid-open No. 63-1 filed earlier by the present applicant
There are methods described in Japanese Patent Application No. 61936 and Japanese Patent Application No. 61-313274. FIG. 7 shows an optical tomographic imaging device that irradiates and detects light between the inside of the body cavity and the outside of the body, and images the living tissue located therebetween.

As shown in FIG. 7, a tomographic imaging device 7
0 is designed to image living tissue by inserting a light irradiation means into a body cavity and arranging a light detection means outside the body. This optical tomographic imaging apparatus 70 includes a light source 26 that generates pulsed light with a half-width of several picoseconds, a probe 27 that guides and irradiates the pulsed light generated by the light source to organs in the body cavity of a living body 38, and an optical fiber bundle 28 disposed in contact with or close to the surface of the living body 38 in order to detect the pulsed light transmitted through the body, and a streak camera 29 that measures the pulsed light detected by the optical fiber bundle 28 in a time-resolved manner. , a processing device 30 that reconstructs a tomographic image of a living body 38 from pulses measured by the streak camera 29;
, a control device 31 that synchronizes and controls the probe 27 and the processing device 30, and a display device 32 that receives an output signal from the processing device 30 and displays a tomographic image.

The structure and operation of the light source 26 and probe 27 are similar to those described in Japanese Patent Application No. 2-259914 filed by the present applicant. The light source 26 includes a pulsed laser 33 that is a combination of a dye laser and an Nd:YAG laser that generates pulsed light, a beam sampler 34 made of, for example, a half mirror that extracts a part of the pulsed light emitted by the pulsed laser 33, and A detector 35 detects the light extracted by the sampler 34 and generates a synchronization signal for the streak camera 29, and a lens 36 guides pulsed light to an optical fiber 37 disposed within the probe 27.
It is equipped with The probe 27 includes an elongated and flexible insertion section 3 inserted into the body cavity of a living body 38.
9 and a large-diameter operating section 40 provided on the base side of the insertion section 39, and a cylindrical translucent cover 41 with a closed end is attached to the distal end side of the insertion section 39. has been done. Further, a flexible shaft 42 is installed substantially on the axis of the insertion portion 39, through which an optical fiber 37 is inserted through which the pulsed light emitted by the light source 26 is introduced between the lenses 36. Both ends are rotatably supported by bearings 43a and 43b. Further, the flexible shaft 42 has a prism 44 connected to the end on the side of the translucent cover 41 and having an inclination angle of, for example, 45 degrees with respect to the axis. moreover,
The flexible shaft 42 has a gear 45 externally fitted and fixed to the end on the side of the operating section 40, and this gear 45 is connected to a gear 46.
are interlocking. Further, this gear 46 is fixed to the output shaft of a motor 47, and this motor 47 has an encoder 48.
are installed in succession. The motor 47 includes the control circuit 3
1 is electrically connected, and this control circuit 31 receives a signal from the encoder 48 and controls the rotation of the motor 47. With this configuration, the pulse laser 33 emits pulsed light having a half-width of several picoseconds. At this time, near-infrared light (wavelength: 700 nm to 1200 nm), which has high tissue penetration, is used as the pulsed light. The pulsed light emitted by the pulsed laser 33 is guided by a lens 36 to an optical fiber 37 disposed within the probe 27 . With the insertion section 39 of the probe 27 inserted into the internal organ of the body cavity 38, the optical pulse light that has passed through the optical fiber 37 is rotated and scanned in the side radiation direction via the rotating prism 44, and the optical pulse light is scanned in the lateral direction through the rotating prism 44. The inner wall 38a is irradiated. The irradiated pulsed light passes through the living tissue while being absorbed by, for example, hemoglobin.

The transmitted pulsed light is detected by an optical fiber bundle 28 placed outside the living body 38 and surrounding the living body 38, facing the tip of the probe 27. Then, pulsed light from each point detected by the optical fiber bundle 28 is measured by a streak camera 29 in a time-resolved manner. Then, the processing device 30 processes and analyzes the time-resolved waveforms of the respective pulsed lights that have passed through each fiber constituting the optical fiber bundle 28, and can obtain a tomographic image with little influence of light scattering and high spatial resolution. . At this time, the irradiation angle of the light irradiated from the tip of the probe 27 and the time-resolved waveform are controlled by the control device 31 and are synchronized.

FIG. 8 shows another example in which, contrary to the apparatus 70 shown in FIG. 7, the light irradiation means is placed outside the body and the light detection means is inserted into the body cavity to image the living tissue. Others, Figure 7
The structure and operation are the same as those of the device shown in FIG. As shown in FIG. 8, this optical tomographic imaging apparatus includes a light source 33 that generates pulsed light, a light scanning means 50 that sequentially scans and guides the pulsed light onto an optical fiber bundle 49, and a light source 33 that generates pulsed light. a probe 27 that scatters and absorbs light transmitted from the inner wall 38a of an internal organ in the body cavity; a time-resolved measurement device 51 that measures the light detected by the probe 27 in a time-resolved manner; motor 47, encoder 48,
It includes a control device 64 that controls the optical scanning means 50 and the moving stage 63, and a signal processing device 65 that reconstructs a tomographic image of the living body 38 from the signals from the time-resolved measurement device 51.

The time-resolved measuring device 51 includes a lens 5 that focuses the pulsed light transmitted through the living body 38 and the reference pulsed light.
2, a nonlinear optical element 53 that generates the second harmonic of each focused pulsed light, an optical filter 54 that transmits only the second high frequency, and a photoelectron intensifier that detects the light that has passed through the filter 54. It consists of a multiplier tube (PMT) 55 and an amplifier 56. Light guide (1) 57 and ride guide (2)
) 58 are arranged to face the same end surface of the lens 52. The light guide (1) 57 is disposed at the input end thereof so as to guide the light emitted from the optical fiber 37 built into the probe 27 via a lens 59. Moreover, at the entrance end of the light guide (2) 58,
The pulsed light (reference light) partially taken out by the half mirror 60 is arranged so as to be guided through a delay circuit 61 consisting of a prism etc. attached to a moving stage 63 and mirrors 62a and 62b. . In such a configuration, the delay circuit 61 can vary the optical path length of the pulsed light by being moved by the moving stage 63, and can measure the light intensity of the pulsed light at each time, that is, the time-resolved waveform. ing.

With this configuration, the pulsed light generated by the pulsed laser 33 is divided into two parts by the half mirror 60, and one of the pulsed lights is guided to the light guide (2) 58 via the delay circuit 61 etc. . On the other hand, the pulsed light is guided by the optical scanning means 50 to each fiber of the fiber bundle 49 so as to rotate sequentially, and is incident on the living body 38 while changing the irradiation position. Then, the incident pulsed light passes through the inside of the living body 38, and is transmitted through the inner wall 38a while being scattered and absorbed. The pulsed light transmitted through the inner wall 38a enters the rotating prism 44 placed at the tip of the probe 27, and passes through the optical fiber 37, lens 59, and light guide (1) 57 placed approximately at the center of the probe 27. Then, it is guided to the time-resolved measuring device 51. At this time, the prism 44 is rotating, and its direction is controlled in synchronization with the optical scanning means 50 by the control device 64 so that it faces the position of the pulsed light irradiated from the outside of the living body 38. The nonlinear optical element 53 generates a second high frequency wave by inputting the transmitted light of the subject 3 and the reference light. This second high frequency wave passes through a filter 54 that only passes this second high frequency wave, and is detected by the PMT 55. The delay circuit 61 changes the optical path length of the reference light by moving the moving stage 63. The intensity of the second high frequency wave generated by the linear optical element 53 is proportional to the integral value of the product of the transmitted light and the reference light, when each of the transmitted light and the reference light is a function of time. Therefore, by driving the delay mirror circuit 61 and changing the optical path length of the reference light, the PMT 55 allows the object 38 to be
It is possible to detect the intensity of any time component of the transmitted light. In this way, the time-resolved waveform of the light transmitted through the subject 38 can be detected.

In this way, the transmitted light of the object 38 is measured in a time-resolved manner by the time-resolved measuring device 51, and the time-resolved waveform, the position where the light is irradiated, that is, the control signal of the optical scanning means 50, and the detected direction are In other words, the signal processing device 65 processes and analyzes the signal based on the control signal of the probe 27, and the inside of the living body 38 can be imaged.

[0032]

[Effects of the Invention] As described above, according to the present invention, even if the object to be examined has a large difference in refractive index from air or is a strong scatterer, a good tomographic image with few false images can be obtained. There is an effect that it can be done.

[Brief explanation of drawings]

FIG. 1 is an overall configuration diagram of an optical tomographic imaging apparatus.

FIG. 2 is a characteristic diagram showing an example of the distribution of light intensity detected by a group of detectors.

FIG. 3 is an explanatory diagram for correcting the irradiation angle of beam light.

FIG. 4 is a configuration diagram for explaining a scattering component suppression method.

FIG. 5 is a configuration diagram related to an improvement of the scattered component suppression method shown in FIG. 4;

FIG. 6 is a configuration diagram related to an improvement of the scattered component suppression method shown in FIG. 4;

FIG. 7 is a configuration diagram showing an application example of an optical tomographic imaging apparatus.

FIG. 8 is a configuration diagram showing an application example of an optical tomographic imaging apparatus.

[Explanation of symbols] 1... Optical tomographic imaging device 2...Light source 3... Optical scanning device 4...Subject 5...Detector group 7...Processing device 8...Image processing device 9...Control device 10...Monitor

Claims (2)

[Claims] 1. A light source that emits a beam of light, a light scanning device that scans a subject with the beam of light emitted by the light source, and a light beam that is arranged in an array at a position where the beam of light scanned by the light scanning device is incident. A plurality of light detection means are arranged to detect the light transmitted through the object, and the intensity distribution of the light detected by the plurality of light detection means is calculated, and the light beam scanned by the light scanning means is calculated. Optical tomographic imaging characterized by comprising: image processing means for determining the intensity of transmitted light corresponding to the irradiation angle and performing image processing to obtain a tomographic image of the subject from the intensity of the transmitted light. Device. 2. The image processing means performs calculation processing on the irradiation angle of the beam light scanned by the scanning means and the light receiving position of the transmitted light detected by the plurality of photodetectors, so that the scanning means performs scanning. 2. The method according to claim 1, wherein the irradiation angle of the beam light is corrected, and image processing is performed to obtain a tomographic image from the intensity of the transmitted light corresponding to the corrected irradiation angle of the beam light. Optical tomography imaging device.