JP2008151697A - Optical tomographic imaging device - Google Patents

Optical tomographic imaging device Download PDF

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JP2008151697A
JP2008151697A JP2006341167A JP2006341167A JP2008151697A JP 2008151697 A JP2008151697 A JP 2008151697A JP 2006341167 A JP2006341167 A JP 2006341167A JP 2006341167 A JP2006341167 A JP 2006341167A JP 2008151697 A JP2008151697 A JP 2008151697A
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light
interference signal
means
measurement
tomographic
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JP5052116B2 (en
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Sadataka Akahori
Wataru Ito
Kensuke Terakawa
渡 伊藤
賢祐 寺川
貞登 赤堀
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Fujifilm Corp
富士フイルム株式会社
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Abstract

<P>PROBLEM TO BE SOLVED: To compensate deterioration of an interference signal obtained by OCT measurement and improve a quality of tomographic information obtained by frequency analysis. <P>SOLUTION: Light in a predetermined wavelength band emitted from a light source is divided into measurement light and reference light; reflected light produced by reflecting the divided measurement light from an object to be measured and the reference light are combined; and the intensity of the interference light of the combined reflected light and the reference light is detected by an interference signal detector 2. The intensity of the interference light combining the reflected light that the measurement light is reflected from a predetermined depth position of a substance and the reference light is previously measured, by using the substance having characteristics similar to the object instead of the object; and the attenuation factor and the refractive index obtained by the previous measurement are stored in a compensation data storing unit 51, as compensating data C. Attenuation compensation and dispersion compensation of the strength of the interference signal I is performed by using the compensation data C, by a compensating unit 52; and the tomographic information r(z) of the object is acquired by frequency analyzing the compensated interference signal Ic by a tomographic information acquiring unit 53. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an optical tomographic imaging apparatus that acquires an optical tomographic image by OCT (Optical Coherence Tomography) measurement.

  Conventionally, when generating an optical tomographic image of a living tissue, an optical tomographic image acquisition apparatus using OCT measurement may be used. In this optical tomographic image acquisition apparatus, the low-coherent light emitted from the light source is divided into measurement light and reference light, and then the reflected light and reference light from the measurement object when the measurement light is irradiated onto the measurement object. And an optical tomographic image is generated based on the intensity of the interference light between the reflected light and the reference light. In the optical tomographic image acquisition apparatus as described above, by changing the optical path length of the reference light, the position in the depth direction with respect to the measurement target (hereinafter referred to as the depth position) is changed to generate an optical tomographic image. There is an apparatus using (Time domain OCT) measurement.

  In recent years, an SD-OCT apparatus using SD-OCT (Spectral Domain OCT) measurement that generates an optical tomographic image at high speed without changing the optical path length of the reference light described above has been proposed (Patent Document 1). reference). This SD-OCT apparatus divides broadband low-coherent light into measurement light and reference light using a Michelson interferometer or the like, and then irradiates the measurement light on the measurement object, and the reflected light returned at that time. And the reference light are subjected to interference, and a channeled spectrum obtained by decomposing the interference light into each frequency component is Fourier-transformed to form an optical tomographic image without scanning in the depth direction. Further, Patent Document 1 discloses a method of separating interference light for each spectral band and detecting the separated interference light with separate photodetectors in order to improve the detection accuracy of the interference light.

  Patent Document 1 also proposes an optical tomographic imaging apparatus using SS-OCT (Swept source OCT) measurement as an apparatus that generates an optical tomographic image at high speed without changing the optical path length of the reference light. . This SS-OCT apparatus sweeps the frequency of laser light emitted from a light source, causes reflected light and reference light to interfere at each wavelength, and Fourier transforms the interference spectrum for a series of wavelengths, thereby measuring the depth of the object to be measured. The reflected light intensity at the position is detected, and this is used to construct an optical tomographic image.

  As a method for improving the spatial resolution in the above-described TD-OCT measurement, SS-OCT measurement, and SD-OCT measurement, it is known to use measurement light having a wide spectrum width (see Patent Document 2). As a light source that emits light having a broad spectrum width, Patent Document 2 discloses that a plurality of light sources that emit light having different spectral bands are combined with light emitted from each light source by an optical coupler. An apparatus that emits light of a light wave is disclosed.

The measurement light that reaches the living tissue is reflected where the refractive index changes when reaching the living tissue, and if there are a plurality of reflecting surfaces in the depth (optical axis) direction of the sample, the positions of the plurality of reflecting surfaces are determined. Observed. However, since the refractive index changes depending on the wavelength, and the reflected light is affected by dispersion due to the refractive index, the position of the reflective surface that does not change physically depends on the wavelength of the light in the measurement using light. Due to this, a reflection surface different from the actual position is observed. Without dispersion, it is known that the wider the spectral width of a low-coherence light source, the higher the resolution. However, if there is dispersion, the optical path difference between the same reference light and the reflected light is physically different depending on the wavelength, so that the resolution is lowered. As a factor of this dispersion, there is a refractive index of an optical component or a living tissue to be observed. Therefore, there has been proposed a method for storing the wavelength dependency wavelength dependency data of the refractive index of the optical component or biological tissue to be used and correcting the wavelength dependency of the refractive index based on the wavelength dependency data ( (See Patent Document 3).
JP-T-2005-516187 JP 2002-214125 A JP 2005-283155 A

  In an ideal state where the refractive index of the optical component or biological tissue is not affected by the OCT measurement, the intensity of the reflected light reflected from the reflecting surface at a certain depth is a component of a specific frequency in the spectrally separated interference signal. Should correspond to the strength of.

  However, in practice, there is a problem that the optical path length changes depending on the wavelength of the light source or the intensity is attenuated in the process in which the light from the light source propagates through the optical component or measurement object. Patent Document 3 discloses a method for performing conversion in consideration of the influence of dispersion, but does not consider attenuation of intensity. In order to obtain a tomographic image with good image quality, it is desired to realize a system capable of compensating not only the influence of dispersion but also the attenuation of intensity.

  SUMMARY OF THE INVENTION Accordingly, an object of the present invention is to improve the quality of tomographic information obtained by frequency analysis by compensating for deterioration of interference signals obtained by OCT measurement.

The optical tomographic imaging apparatus of the present invention divides light of a predetermined wavelength band emitted from a light source into measurement light and reference light, and the reflected measurement light and the reference light reflected from the measurement object by the divided measurement light. An interference signal detector that combines and detects the intensity of the interference light between the reflected light and the reference light combined as an interference signal;
At least one of an attenuation factor that changes according to the wave number when the measurement light propagates to a predetermined depth position and a refractive index of a substance having characteristics close to the measurement object is stored as compensation data. Compensation data storage means;
Compensation means for performing at least one of attenuation compensation of the intensity of the interference signal and dispersion compensation according to the refractive index of the interference signal, using the compensation data;
Tomographic information acquisition means for acquiring the tomographic information of the measurement object by performing frequency analysis on the interference signal compensated by the compensation means;
And a tomographic image generating means for generating a tomographic image using the tomographic information.

  The “compensation means” uses “attenuation compensation of interference signal intensity” for the compensation data using the attenuation rate, and “dispersion compensation according to the interference signal refractive index” uses the refractive index of the compensation data. Do it. Further, when only one of the attenuation rate and the refractive index is stored in the compensation data, only the compensation corresponding thereto is performed.

  The compensation data is preferably obtained by measuring in advance using a substance having characteristics close to the measurement object instead of the measurement object.

  The “substance having characteristics close to the measurement object” refers to a substance having a refractive index and an attenuation factor of interference light intensity that are close to each other. For example, when a living body is a measurement object, water is an example of a substance having characteristics.

The compensation data storage means stores compensation data for a plurality of substances having characteristics close to the measurement target,
A measurement object estimation means for estimating the substance close to the characteristic of the measurement object from the detected interference signal;
The compensation means may use the compensation data of the estimated substance.

Further, the interference signal is composed of an intensity component of the measurement light, an intensity component of the reflected light, and an interference component of the measurement light and the reflected light,
The compensation data includes the attenuation rate;
The measurement object estimation means is
Measurement light intensity storage means for storing the intensity of the measurement light measured in advance;
Interference component removing means for removing an interference component by smoothing a fine vibration component placed on a component of a wave with a large period on the interference signal;
Reflected light intensity extracting means for extracting the intensity of the reflected light by removing the intensity of the measurement light from the interference signal from which the interference component has been removed by the interference component removing means;
The substance to be measured is estimated by comparing the attenuation amount of the reflected light extracted by the reflected light intensity extracting means with the attenuation rate of the compensation data for the plurality of substances. You may do.

Further, the compensation data storage means stores compensation data when the measurement light is reflected from different depth positions of the substance, respectively.
The compensation means compensates the interference signal by using compensation data at each depth position;
The tomographic information acquisition means acquires a plurality of tomographic information by frequency analysis of each compensated interference signal,
It further comprises synthetic tomographic information acquisition means for acquiring tomographic information obtained by synthesizing the plurality of tomographic information so that the degree of influence at the depth position compensated for the interference signal from which the tomographic information has been acquired is greater than that of other tomographic information. ,
The tomographic image generation means may generate the tomographic image from the tomographic information synthesized by the synthetic tomographic information acquisition means.

Further, another optical tomographic imaging apparatus of the present invention divides light of a predetermined wavelength band emitted from a light source into measurement light and reference light, and the divided measurement light is reflected from the measurement object and the reflected light An interference signal detector that combines reference light and detects the intensity of interference light between the combined reflected light and the reference light as an interference signal;
Attenuation rate storage means for storing, for each depth position, an attenuation rate that changes according to the wave number when the measurement light propagates to a different depth position of a substance having characteristics close to the measurement target;
Frequency component separation means for separating the interference signal into components of a plurality of frequency bands;
Attenuation compensation of the intensity of each frequency band component using the attenuation rate stored in the attenuation rate storage means corresponding to the depth position of the tomographic information obtained by frequency analysis of the interference signal of each frequency band Intensity compensation means for performing
Frequency component synthesizing means for synthesizing the components of the respective frequency bands that have been attenuation-compensated by the intensity compensating means to obtain interference signals in all frequency bands;
A tomographic information acquisition means for acquiring the tomographic information of the measurement object by performing frequency analysis on the interference signals in the entire frequency band;
And a tomographic image generating means for generating a tomographic image using the tomographic information.

Refractive index storage means for storing the refractive index that changes according to the wave number when the measurement light of the substance having characteristics close to the measurement object propagates to a predetermined depth position, the other optical tomographic imaging device; ,
Dispersion compensation means for performing dispersion compensation of the combined interference signals in all frequency bands using the refractive index stored in the refractive index storage means,
The tomographic information acquisition unit may analyze the frequency of the interference signal in the entire frequency band that has been dispersion compensated by the dispersion compensation unit.

Alternatively, the other optical tomographic imaging apparatus stores a refractive index storage that stores a refractive index that changes according to a wave number when the measurement light of a substance having characteristics close to the measurement target propagates to a predetermined depth position. Means,
Dispersion compensation means for performing dispersion compensation of the interference signal detected by the interference signal detector using the refractive index stored in the refractive index storage means,
It is desirable that the frequency component separation unit separates the interference signal dispersion-compensated by the dispersion compensation unit into components of a plurality of frequency bands.

  The attenuation factor may be obtained by measuring in advance using a substance having characteristics close to the measurement object instead of the measurement object.

  Further, it is desirable that the refractive index is obtained by measuring in advance using a substance having characteristics close to the measurement object instead of the measurement object.

  According to the present invention, using a substance having characteristics close to the measurement target, compensation data such as an attenuation factor and a refractive index are prepared in advance so that the intensity of the interference signal is attenuated when the substance is reflected from a specific depth. In addition, the accuracy of tomographic information near a specific depth position can be improved by performing frequency analysis after obtaining attenuation compensation and dispersion compensation of interference signals to obtain tomographic information.

  By using a substance with characteristics close to the measurement target as a sample and measuring the guarantee data such as the attenuation rate and refractive index of the interference signal detector in advance, accurate compensation corresponding to the interference signal detector can be performed. Can do.

  In addition, by estimating the substance close to the characteristics of the object to be measured from the attenuation of the reflected light calculated from the detected interference signal and using compensation data for the substance having the characteristics close to the object to be measured, the accuracy of the tomographic information can be improved. Can be improved.

  Alternatively, compensation data when the measurement light is reflected from different depth positions are prepared, and the frequency of the data obtained by performing attenuation compensation or dispersion compensation of the intensity of the interference signal at each depth is subjected to frequency analysis. By generating multiple pieces of information and combining them so that the degree of influence at the depth position where the interference signal of each tomographic information source is compensated is greater than other tomographic information, it is not limited to a specific depth position The accuracy of tomographic images can be increased.

  Further, the interference signal is separated into a plurality of frequency band components, and the attenuation rate corresponding to the depth position of the tomographic information obtained by frequency analysis of the interference signal in each frequency band is used to determine the component of each frequency band. After performing intensity attenuation compensation, by acquiring tomographic information by frequency analysis, if the influence of dispersion does not change with depth, the accuracy of tomographic information is improved without being limited to a specific depth position Can be made.

  If the change in refractive index does not change greatly with depth, dispersion compensation is performed using a refractive index at a certain depth after compensating for attenuation using an attenuation factor corresponding to the depth position. By doing so, the accuracy of tomographic information can be further improved.

  Alternatively, if the change in refractive index does not change significantly with depth, the interference signal detected from the interference signal detector is compensated for dispersion using the refractive index at a certain depth, and then it corresponds to the depth position. The accuracy of the tomographic information can be further improved by performing the attenuation compensation of the intensity using the attenuation rate.

  Embodiments of an optical tomographic imaging apparatus according to the present invention will be described below in detail with reference to the drawings. FIG. 1 is a schematic view showing a preferred embodiment of the optical tomographic imaging apparatus of the present invention. The optical tomographic imaging apparatus 1 acquires, for example, a tomographic image of a measurement target such as a living tissue or a cell in a body cavity by SD-OCT (Spectral Domain OCT) measurement using a Mach-Zehnder interferometer, and an interference signal The tomographic information (reflectance) at each depth position of the measurement target is detected by frequency analysis of the detector 2 and the interference light L4 detected by the interference light detector 2, and a tomographic image that generates a tomographic image of the measurement target S An image processing means 50 and a display device 60 for displaying a tomographic image are provided.

  The interference signal detector 2 includes a light source unit 10 that emits a plurality of light beams L, a light splitting unit 3 that splits the light beams L emitted from the light source unit 10 into measurement light L1 and reference light L2, respectively, and light splitting unit 3 is combined by the combining means 4 and the combining means 4 for combining the reflected light L3 from the measuring object S and the reference light L2 when the measuring light S1 divided by 3 is irradiated onto the measuring object S. Interference light detection means 40 for detecting the interference light L4 between the reflected light L3 and the reference light L2 is provided.

  The light source unit 10 has a continuous spectrum in the wavelength band λ as shown in FIG. For example, it can be configured using an ASE (Amplified Spontaneous Emission) light source such as a rare earth doped fiber amplifier laser.

  1 comprises, for example, a 2 × 2 optical fiber coupler, and splits the light beam L guided from the light source unit 10 through the optical fiber FB1 into the measurement light L1 and the reference light L2. It has become. At this time, the light dividing means 3 divides the light at a ratio of, for example, measurement light L1: reference light L2 = 90: 10. The light splitting means 3 is optically connected to each of the two optical fibers FB2 and FB3. The split measurement light L1 is incident on the optical fiber FB2 side, and the reference light L2 is incident on the optical fiber FB3 side. It is like that.

  An optical circulator 11 is connected to the optical fiber FB2, and optical fibers FB4 and FB5 are connected to the optical circulator 11, respectively. A probe 30 that guides the measurement light L1 to the measurement object S is connected to the optical fiber FB4. The probe 30 can be inserted into a body cavity from, for example, a forceps opening through a forceps channel, and the measurement light L1 emitted from the probe 30 is guided from the optical fiber FB2 to the probe 30 and simultaneously to the same part of the measurement target S. Will be irradiated. The reflected light L3 reflected from the measuring object S is incident on the optical circulator 11 via the optical fiber FB4 and is emitted from the optical circulator 11 to the optical fiber FB5 side.

  The multiplexing means 4 is composed of a 2 × 2 optical fiber coupler, and combines the reflected light L3 guided in the optical fiber FB5 and the reference light L2 guided in the optical fiber FB3. The multiplexing unit 4 emits the interference light L4 between the reflected light L3 and the reference light L2 to the optical fiber FB6 side. The length of the optical fiber FB3 is such that the optical path length of the measurement light L1 from the light splitting means 3 through the measurement start position of the measuring object S to the multiplexing means 4 is equal to the optical path length of the reference light L2. Is set.

  The interference light detecting means 40 has a function of photoelectrically converting the interference light L4 guided through the optical fiber FB6 and detecting the interference signal I. Specifically, the interference light detection means 40 includes a spectroscopic element 42 that splits the interference light L4 having the wavelength band λ, and a light detection unit 44 that detects the interference light L4 split by the spectroscopic element 42. Yes. The spectroscopic element 42 is composed of, for example, a diffractive optical element, etc., and splits the interference light L4 incident from the optical fiber FB6 via the collimator lens 41 and emits it to the light detection unit 44 side via the optical lens 43. It is like that.

  The light detection unit 44 has a structure in which a plurality of light detection elements 44a such as an InGaAs photodiode array, a Si photodiode array, a CCD (Charge Coupled Device) image sensor, and the like are arranged one-dimensionally or two-dimensionally. The light detection element 44a detects the interference light L4 that has been split by the spectral element 42 for each wavelength and entered via the optical lens 43. The light detection unit 44 detects the interference signal I from the interference light L4.

  FIG. 3 is a block diagram showing a preferred embodiment of the tomographic image processing apparatus (tomographic image processing means) of the present embodiment. The tomographic image processing apparatus (tomographic image processing means) 50 will be described with reference to FIG. . The configuration of the tomographic image processing apparatus 50 as shown in FIG. 3 is realized by executing a tomographic image processing program read into the auxiliary storage device on a computer (for example, a personal computer). At this time, the tomographic image processing program is stored in an information storage medium such as a CD-ROM or distributed via a network such as the Internet and installed in a computer. In addition, the configuration of the tomographic image processing apparatus 50 is incorporated in the tomographic imaging apparatus 1 itself without being limited to being realized on the above-described computer, and imaging with an endoscope and display of processed images are processed in real time. There may be.

  When the tomographic image processing apparatus 50 propagates to a predetermined depth position z = L of a specific substance having characteristics close to the measurement target, the measurement light L1 has an attenuation rate g (k that changes according to its wave number k. ) And refractive index n (k) as compensation data C in advance, and compensation for compensating the interference signal I according to the wave number k and the refractive index n (k) using the compensation data. A tomographic image using means 52, tomographic information acquisition means 53 for acquiring tomographic information r (z) by frequency analysis of the compensated interference signal Ic, and tomographic information r (z) generated by the frequency analyzing means 53 And a tomographic image generation means 54 for generating.

  The compensation data storage means 51 is a table of attenuation rate g (k), refractive index n (k), etc. measured by the interference signal detector 2 using a sample of a known material having characteristics close to the material to be measured. Is stored as compensation data C. Specifically, as shown in FIG. 4, the light that has passed through the substance (thickness z) imitating the measurement target is reflected by the total reflection mirror M, and the attenuation rate g (k), refractive index n (k), etc. Measure. When the measurement target is a living body, since most of the living body is occupied by water, compensation data obtained by measuring water can be used.

  Here, a method for compensating the interference signal I by the compensation means 52 will be described. When the measurement light L1 having a spectral intensity distribution as shown in FIG. 2 is irradiated onto the measurement object S, the interference signal I detected by the interference light detection means 40 is superimposed on the interference light fringe intensity due to each spectral component. A combined interferogram as shown in FIG. 5 appears. The spectral spectrum of the interference light L4 is obtained by performing frequency analysis by Fourier transform on the interferogram detected by the interference light detection means 40, and information on the depth position z and the tomographic information of the measurement target S as shown in FIG. r (z) is acquired.

  However, since the interference signal I detected by the interference light detector 2 is affected by the absorption characteristics and scattering characteristics of the substance of the measurement object S, the accurate depth position z and tomographic information can be obtained when the frequency analysis is performed as it is. r (z) cannot be acquired.

Here, first, the influence of the intensity (interference signal) I of the interference light L4 in which the reference light L2 and the reflected light L3 interfere with each other, the refractive index n, and the attenuation rate g will be examined. The reference light L2 having the wave number k is E r (k), the measurement light L1 is E o (k), and the reflected light L3 reflected from the depth z of the measurement object S is E o (k, z). In this case, the intensity I (k) of the interference light L4 obtained by the interference between the reflected light L3 reflected from the plurality of depths z of the measurement object S and the reference light L2 is expressed by the following equation (1). The third term of Equation (1) is the interference component between the reflected light L3 and the reference light L2.

The intensity I (k) is attenuated by being affected by the absorption characteristics and the scattering characteristics of the substance of the measuring object S. It is known that these absorption characteristics and scattering characteristics change depending on the wave number (wavelength), and the attenuation becomes g (k, z) because the intensity increases as the depth z of each layer increases. Can be represented. Further, the refractive index n depends only on the wave number k when the layer through which the measurement light L1 propagates is a single substance, but since the measurement target S is generally composed of a plurality of layers, the depth z of each layer The refractive index changes depending on the above. Therefore, the refractive index is expressed as n (k, z). Therefore, Formula (1) becomes like the following Formula (2).

The third term of equation (2) is the interference component, but the intensity is attenuated depending on the wave number, so that the shape of the entire interference signal is deformed, resulting in a decrease in resolution and a pseudo signal such as a side lobe. Become. In particular, paying attention to the third term of the equation (2), the following equation (3) is obtained, which is an equation depending on the wave number k and the depth z.

  However, if the measurement target is a living body and attention is paid only to the tomographic image in the vicinity of the depth position z = L, the refractive index and intensity at z = L when the measurement target substance is assumed to be water. It is considered that the quality of tomographic images in the vicinity of z = L can be improved by performing compensation using the attenuation rate.

Therefore, considering the case where the observation depth is fixed to L, the refractive index depends only on the wave number k, so it is expressed as n (k, L) = n (k), and the attenuation factor of the intensity is also set to the wave number k. Therefore, g (k, L) = g (k) is expressed. That is, Expression (3) can be rewritten as the following Expression (4).

  As can be seen from equation (4), in order to compensate for the intensity attenuation, the interference signal I is multiplied by 1 / g (k) using the attenuation rate table of the compensation data C. (Here, assuming that the depth L is somewhat distant from z = 0, the first and second terms that mainly affect the fault information near z = 0 are ignored. In addition, by subtracting the first and second terms from the signal detected by the interference light detector, only the third term is extracted from each signal detected by providing a means for detecting only the reference light and only the reflected light. You may do that.)

  Further, as shown in FIG. 7 (a), the intensity of the observed interference signal changes according to k × n (k), and therefore, the compensation data C table is used in FIG. 7 (c). The correspondence between k × n (k) and k as shown in FIG. 7 is obtained, and the dispersion compensation of the interference signal can be performed by converting FIG. 7 (a) to FIG. 7 (b).

  The tomographic information acquisition means 53 acquires the tomographic information r (z) by performing frequency analysis on the interference signal Ic that has been subjected to intensity attenuation compensation and dispersion compensation. By performing frequency analysis on the compensated interference signal Ic obtained by compensating the interference signal I using the attenuation rate g (k) and the refractive index n (k) at the depth position L using FFT or the maximum entropy method, In the vicinity of the depth L, accurate tomographic information r (z) can be obtained.

  Next, an operation example of the optical tomographic imaging apparatus 1 will be described with reference to FIGS. First, a light beam L having a continuous spectrum in the wavelength band λ is emitted from the light source unit 10 and is incident on the light splitting means 3. In the light splitting means 3, the light beam L is split into measurement light L1 and reference light L2. The measurement light L1 is emitted to the optical fiber FB2 side, and the reference light L2 is emitted to the optical fiber FB3 side.

  The measurement light L1 is guided through the optical circulator 11, the optical fiber FB4, and the probe 30, and is irradiated onto the measurement object S. Then, the reflected light L3 reflected at each depth position z of the measuring object S and the backscattered light are incident on the probe 30 again. The reflected light L3 is incident on the multiplexing means 4 via the probe 30, the optical circulator 11, and the optical fiber FB5. On the other hand, the reference light L2 is guided to the optical fiber FB3 and incident on the multiplexing means 4.

  In the multiplexing means 4, interference light L4 obtained by interference between the reflected light L3 and the reference light L2 is emitted to the optical fiber FB6. The interference light L4 is photoelectrically converted by the light detection unit 44 of the interference light detection means 40, and the interference signal I is detected (S100).

  The compensation means 52 multiplies the interference signal I by the value of the 1 / g (k) table stored at the depth position z = L stored in the compensation data storage means 51 to compensate for attenuation of the intensity, and n ( k) With reference to a table representing the correspondence between * k and k, as shown in FIG. 7, the horizontal axis is converted to obtain the dispersion-compensated interference signal Ic (S101).

  The tomographic information acquisition unit 53 performs frequency analysis on the compensated interference signal Ic to acquire tomographic information r (z) (S102). Further, the tomographic image generation means 54 generates a two-dimensional optical tomographic image using the tomographic information r (z) near the depth L and displays it on the display device 60 (S103).

  As described above, it is preferable to use the compensation data actually measured by the interference signal detector 2 using the sample, but if there is data obtained by another method, use it as compensation data. Also good.

  In the above-described compensation means, the case where the dispersion compensation is performed after the intensity attenuation compensation has been described. However, the intensity attenuation compensation may be performed after the dispersion compensation is performed.

  As described above in detail, the compensation data of a specific depth is measured using a sample of a known substance having characteristics close to the substance to be measured, and the interference signal is compensated using the measurement result. Thus, the accuracy of the fault information at that depth can be improved.

  FIG. 9 is a schematic view showing a second embodiment of the optical tomographic imaging apparatus of the present invention. In the optical tomographic imaging apparatus 1a of FIG. 9, parts having the same configurations as those of the optical tomographic imaging apparatus 1 of FIG. The optical tomographic imaging apparatus 1a in FIG. 9 is different from the optical tomographic imaging apparatus 1 in FIG. 1 in a tomographic image processing means 50a. In the above-described embodiment, the case where the compensation data is prepared assuming that the substance to be measured is a specific substance has been described. However, in this embodiment, compensation data for a plurality of substances is prepared in advance. A case will be described in which the substance to be measured is estimated from the detected interference signal I and the interference signal is compensated using the compensation data corresponding to the estimated substance.

  FIG. 10 is a block diagram showing a preferred embodiment of the tomographic image processing apparatus of the present embodiment. The tomographic image processing apparatus 50a will be described with reference to FIG.

  When the tomographic image processing apparatus 50a propagates to a position at a depth L for each of a plurality of substances, the attenuation rate g (k) and the refractive index n (k) at which the measurement light L1 changes according to the wave number k Compensation data storage means 51a for preliminarily storing compensation data C including, measurement object estimation means 55 for estimating a substance to be measured from interference signal I, and interference signal I using compensation data C for the estimated substance. Is compensated according to the wave number k and the refractive index n (k), the tomographic information obtaining means 53 for obtaining the tomographic information r (z) by analyzing the frequency of the compensated interference signal Ic, and the tomographic information obtaining. And a tomographic image generation means for generating a tomographic image using the tomographic information r (z) generated by the means 53.

The measurement object estimation unit 55 includes a reference light intensity storage unit 551 that stores the intensity of the reference light L2 of the interference signal detector 2, and a measurement light intensity storage unit 552 that stores in advance the intensity of the measurement light L1 of the interference signal detector 2. With. Since the intensity | E r (k) | of the reference light L2 and the intensity | E o (k) | of the measurement light L1 are fixed by the interference signal detector 2, they are measured using the interference signal detector 2 in advance. The light intensity storage means 551 and the measurement light intensity storage means 552 are stored.

  Here, an estimation method for estimating the measurement target substance by the measurement target estimation means 55 will be described. As shown in Expression (1), the interference signal I includes a measurement light intensity component (first term), reflected light intensity component (second term), and measurement light and reflected light interference components (third term). ). As shown in FIG. 11, the interference signal I has a shape in which a small vibration component is placed on a wave component having a large period. The small vibration component is due to the vibration component of the third term of the equation (1). However, the signal I1 from which the vibration component of the third term has been removed has a wave shape with a large period. Therefore, for example, a small peak vibration component is smoothed using an average value filter value, or an average value of a maximum value filter value and a minimum value filter value, and the large period of FIG. Extract the wave component.

In the first term of the equation (1), the intensity | E r (k) | of the reference light L2 is a fixed value corresponding to the interference signal detector 2, and the intensity | E o (k) | This is a fixed value corresponding to the interference signal detector 2. Therefore, using the intensity of the reference light L2 stored in the reference light intensity storage unit 551 from the signal I1 from which the vibration component of the third term has been removed, the first term component (| E r ( k) Find the signal I2 from which | 2 ) is removed. This signal I2 substantially coincides with the component | ΣE o (k) × r (z) | 2 in the second term of the equation (1). Further, the attenuation amount of the measurement light L1 is obtained from the intensity | E o (k) | of the measurement light L1 stored in the measurement light intensity storage means 552 and the signal I2. The substance to be measured is estimated by comparing the obtained attenuation amount with the attenuation rate g of the compensation data C for a plurality of substances stored in the compensation data storage unit 51a.

  Next, an operation example of the optical tomographic imaging apparatus 1a will be described with reference to FIG. Since the operation of the interference signal detector 2 is the same as that of the first embodiment described above, it will be omitted and only the operation of the tomographic image processing apparatus 50a will be described.

  The interference signal detector 2 detects the interference signal I (S200), and the measurement target estimation means 55 estimates the measurement target substance from the detected interference signal I (S201).

  The compensation data C corresponding to the estimated substance is retrieved from the compensation data storage means 51, and the compensation means 52 multiplies the interference signal I by the value in the 1 / g (k) table of the retrieved compensation data C to obtain the intensity. The interference signal Ic having the dispersion compensation is acquired by converting the horizontal axis with reference to the n (k) * k table (S202).

  The tomographic information acquisition means 53 obtains tomographic information r (z) by frequency analysis of the compensated interference signal Ic (S203), and the tomographic image generation means 54 obtains tomographic information r (z) near the depth L. A two-dimensional optical tomographic image is generated and displayed on the display device 60 (S204).

  As explained in detail above, compensation data of a specific depth is prepared using a sample of a plurality of known substances having characteristics close to the substance to be measured, and the substance constituting the measurement object is estimated from the interference signal Thus, by compensating the interference signal using the compensation data corresponding to the estimated substance, the accuracy of tomographic information at a certain depth can be further improved.

  In the first and second embodiments described above, by matching the depth to be compensated with the focus position of the measurement system, the quality in the scanning direction in which the probe scans the measurement object is good as well as the quality in the depth direction of the measurement object. An image can be obtained.

  FIG. 13 is a schematic view showing a third embodiment of the optical tomographic imaging apparatus of the present invention. In the optical tomographic imaging apparatus 1b shown in FIG. 12, parts having the same configuration as those of the optical tomographic imaging apparatus 1 shown in FIG. The optical tomographic imaging apparatus 1b in FIG. 13 is different from the optical tomographic imaging apparatus 1 in FIG. 1 in tomographic image processing means. The optical tomographic imaging apparatus 1 in FIG. 1 has prepared the compensation data of a specific depth and explained the method of improving the quality of the tomographic image of the specific depth. If it is reflected, it cannot be compensated well. Therefore, in the present embodiment, a method for preparing compensation data for a plurality of depths and combining the results of compensation for a plurality of depth positions so as to perform appropriate compensation will be described.

  FIG. 14 is a block diagram showing a preferred embodiment of the tomographic image processing apparatus of the present embodiment. The tomographic image processing apparatus 50b will be described with reference to FIG.

The tomographic image processing apparatus 50b is a compensation data storage means for storing a plurality of compensation data C L1 , C L2 ,..., C Ln for different depth positions z = L1, L2 ,. 51b, compensation means 52 for compensating the interference signal I using compensation data C L1 , C L2 ,..., C Ln for each of the depth positions z = L1, L2,. , And Ic Ln , respectively, to obtain a plurality of pieces of tomographic information r (z) L1 , r (z) L2 ,... R (z) Ln by frequency analysis of the interference signals Ic L1 , Ic L2 ,. Information acquisition means 53 and a plurality of tomographic information r (z) L1 , r (z) L2 ,... R (z) Ln , a depth position z = Li (i) that compensates for the interference signal that acquired the tomographic information. = 1,2, ..., degree of influence by n) is a tomographic information r (z) Li except Combined tomographic information acquisition means 57 for acquiring tomographic information R (z) obtained by combining the plurality of tomographic information so as to be larger than other tomographic information, and a tomographic image for generating a tomographic image using the tomographic information R (z) Generating means 54.

The combined tomographic information acquisition means 57 uses the tomographic information acquisition means 53 to obtain the tomographic information r (z) L1 , r (z) L2 obtained from each of the compensated signals Ic L1 , Ic L2 ,..., Ic Ln. ,..., R (z) Ln is synthesized. The tomographic information r (z) L1 obtained from the signal Ic L1 compensated using the compensation data at the depth z = L1 is predicted to have the highest reliability of information near the depth z = L1. The tomographic information r (z) L2 obtained from the signal Ic L2 compensated using the compensation data with the depth z = L2 is predicted to have the highest reliability of information near the depth z = L2. Therefore, the tomographic information r (z) L1, r ( z) L2, ··· r (z) depth has been compensated for the interference signal acquired an Ln location z = L1, L2, · · ·, the influence on the Ln The plurality of pieces of tomographic information are synthesized so that the degree is larger than that of other pieces of tomographic information. For example, as shown in FIG. 15, a Gaussian function δ L1 that becomes 1 at the position z = L1 is multiplied by the tomographic information r (z) L1 , and a Gaussian function δ L2 that becomes 1 at the position z = L2 is obtained. Multiplying to the tomographic information r (z) L2 ,..., And multiplying the tomographic information r (z) Ln by a Gaussian function δLn which becomes 1 at the position of z = Ln, Such combined tomographic information R (z) is generated.

  Next, an operation example of the optical tomographic imaging apparatus 1b will be described with reference to FIG. Since the operation of the interference signal detector 2 is the same as that of the first embodiment described above, it will be omitted and only the operation of the tomographic image processing apparatus 50b will be described.

The interference signal I is detected by the interference signal detector 2 (S300). The compensation signal acquisition unit 56 compensates the compensation data C L1 , C L2 ,..., C Ln of the depth positions z = L1, L2 ,. Interference signals Ic L1 , Ic L2 ,..., Ic Ln that are used in the means 52 and compensate for intensity attenuation and dispersion are acquired (S301).

The tomographic information acquisition means 53 performs frequency analysis on the compensated interference signals Ic L1 , Ic L2 ,..., Ic Ln (S302), and the tomographic information r (z) L1 , r (z) L2 ,. r (z) Ln is acquired (S303). Further, in the synthetic tomographic information acquisition means 57, the depth at which each of the tomographic information r (z) L1 , r (z) L2 ,..., R (z) Ln compensates the interference signal from which each tomographic information is acquired. .., Ln is multiplied by weights δ L1 , δ L2 ,..., Δ Ln such that the degree of influence at the positions z = L1, L2,. The tomographic information r (z) L1 , r (z) L2 ,..., R (z) Ln multiplied by each weight is added to obtain R (z) (S305). The tomographic image generation means 54 generates a two-dimensional optical tomographic image using the tomographic information R (z) and displays it on the display device 60 (S306).

  As described above in detail, in the present embodiment, by performing compensation in consideration of the case of reflection at various depth positions, not only the quality of a tomographic image at a specific depth is improved, The quality of tomographic images of various depths can be improved.

  FIG. 17 is a schematic view showing a fourth embodiment of the optical tomographic imaging apparatus of the present invention. In the optical tomographic imaging apparatus 1c of FIG. 16, parts having the same configurations as those of the optical tomographic imaging apparatus 1 of FIG. The optical tomographic imaging apparatus 1c in FIG. 17 is different from the optical tomographic imaging apparatus 1 in FIG. 1 in tomographic image processing means. In the second and third embodiments described above, the study has been made on the assumption that the refractive index changes depending on the material constituting the layer constituting the measurement object. However, in this embodiment, the refractive index does not change significantly between the layers. Consider the methods that can be used for this.

  FIG. 18 is a block diagram showing a preferred embodiment of the tomographic image processing apparatus of the present embodiment. The tomographic image processing apparatus 50c will be described with reference to FIG.

The tomographic image processing means 50c includes compensation data storage means 51c for storing compensation data, frequency component separation means 58 for separating the interference signal into a plurality of frequency bands, and interference signals I 1 , I 2 ,. ..., an intensity compensation means 522 by using the attenuation factor corresponding to the depth position of the tomographic information obtained by performing frequency analysis on each I n, the attenuation compensation of the intensity of the interference signals of each frequency band, the intensity compensation means , Ic1 n which synthesizes the interference signals Ic1 1 , Ic1 2 ,..., Ic1 n of each frequency band compensated by 522, and frequency component synthesizing means 59 for obtaining the compensated interference signal Ic1 including all frequency bands, and a specific depth Dispersion compensation means 521 for compensating for the dispersion of the compensated interference signal Ic1 including the entire frequency band using the refractive index when the measurement light L1 is reflected from the position, and the dispersion compensated interference signal I A tomographic information acquisition unit 53 that acquires the tomographic information of the measurement target by performing frequency analysis of c2 and a tomographic image generation unit 54 that generates a tomographic image using the tomographic information are provided.

  Further, the compensation data storage unit 51c changes the measurement light L1 according to the wave number k when the measurement light L1 propagates to a predetermined depth of the measurement target when the measurement target substance is a specific substance. When the refractive index storage means 511 that stores the refractive index n in advance and the measurement target substance is a specific substance, when the measurement light L1 propagates to different depths of the measurement target, the measurement light L1 has the wave number k. And an attenuation rate storage means 512 for storing an attenuation rate g that attenuates accordingly.

The frequency component separating means 58 separates the interference signal I into a plurality of frequency bands using an algorithm such as a Laplacian pyramid. As shown in FIG. 6, since the frequency of the interference signal and the depth position z of the tomographic information have a correspondence relationship, the depth position z of the tomographic information obtained from the component of the specific frequency band can be estimated. Therefore, intensity compensation means 522, the interference signal component I 1 of each frequency band separated from I, I 2, · · ·, a depth position of the tomographic information obtained from I n z = L1, L2, ···, using the compensation data corresponding to ln, component I 1, I 2 of each frequency band, ..., component Ic1 1 of each frequency band to compensate for the effect of attenuation of the intensity of I n, Ic1 2, · ·・, Ic1 n is obtained.

The frequency component synthesizing unit 59 synthesizes the compensated interference signals Ic1 1 , Ic1 2 ,..., Ic1 n of a plurality of frequency bands to obtain an interference signal Ic1 including all the bands.

  The dispersion compensator 521 assumes that the refractive index does not change greatly between a plurality of layers constituting the measurement target, and uses the refractive index when the measurement light is reflected from a specific depth position L to disperse the interference signal Ic1. Compensate. Specifically, as in the case described in the first embodiment, as shown in FIG. 7C, the interference signal I is generated based on the correspondence between k × n (k) and k as shown in FIG. The interference signal Ic2 subjected to dispersion compensation is generated by converting from (a) to FIG. 7 (b).

  The tomographic information acquisition unit 53 acquires the tomographic information r (z) from the interference signal Ic2.

  The tomographic image generation means 54 generates a tomographic image from the tomographic information r (z) and displays it on the display device 60.

  Next, an operation example of the optical tomographic imaging apparatus 1c will be described with reference to FIG. Since the operation of the interference signal detector 2 is the same as that of the first embodiment described above, it will be omitted and only the operation of the tomographic image processing apparatus 50c will be described.

The interference signal I is detected by the interference signal detector 2 (S400). First, using an algorithm, such as Laplacian pyramid interference signal I by the frequency component separating means 58, component I 1 of a plurality of frequency bands, I 2, · · ·, separated into I n (S401). In intensity compensation means 522, component I 1 of each frequency band separated from the interference signal I, I 2, · · ·, a depth position of the tomographic information obtained from I n z = L1, L2, ···, the Ln Using the corresponding compensation data, components Ic1 1 , Ic1 2 ,..., Ic1 n of each frequency band compensated for the influence of intensity attenuation are obtained (S402).

Further, the frequency component synthesizing unit 59 synthesizes the compensated interference signals Ic1 1 , Ic1 2 ,..., Ic1 n of a plurality of frequency bands to obtain an interference signal Ic1 including all the bands (S403).

  Next, an interference signal Ic2 in which the influence of dispersion of the interference signal Ic1 compensated for the influence of the attenuation of the intensity using the refractive index when the measurement light is reflected from the specific depth position L is compensated by the dispersion compensation means 521. Generate. (S404).

  The tomographic information acquisition means 53 obtains tomographic information r (z) by frequency analysis of the interference signal Ic2 (S405). The tomographic image generation means 54 generates a two-dimensional optical tomographic image using the tomographic information r (z) (S406).

  In the present embodiment, the interference signal detected from the interference light detector 2 is separated into components of a plurality of frequency bands, and the interference signal compensated for the intensity attenuation at each depth corresponding to each frequency band is obtained. After the calculation, the case where the influence of the dispersion is further compensated has been described. After the influence of the dispersion of the interference signal detected from the interference light detector 2 is compensated, the frequency is separated into components of a plurality of frequency bands. You may make it obtain | require the interference signal which compensated the influence of attenuation | damping of intensity | strength in each depth corresponding to a zone | band.

  As described above in detail, in this embodiment, when the refractive index does not change greatly between the layers constituting the measurement object, dispersion of the obtained interference signal is uniformly compensated, and the interference signal is frequency-converted. It is possible to improve the quality of the tomographic image by accurately performing the attenuation compensation of the intensity in each band.

  In each of the above-described embodiments, the case of SD-OCT measurement has been specifically described. However, SS-OCT can be similarly compensated to improve the accuracy of tomographic information.

  Further, in each of the above-described embodiments, the case where the object surface matches the optical path length difference 0 (z = 0) has been described for convenience of explanation, but the case where the object surface does not match z = 0. Although it is necessary to consider the relationship between the depth from the object surface and the frequency component, the same concept can be applied. Specifically, for example, when the object surface is at the position of the optical path length difference a, it is necessary to obtain the information on the depth L from the surface in consideration of the fact that it appears as a frequency component of L + a. Alternatively, when a is negative, a reflection component from a shallow position becomes a high-frequency component, so that the relationship between the position and frequency must be taken into consideration.

  Further, as described in the above embodiments, it is preferable to perform both attenuation compensation and dispersion compensation of the interference signal intensity as described above in order to improve the accuracy of tomographic information. Even if the tomographic information is obtained using the compensated interference signal, the accuracy of the tomographic information can be improved.

1 is a schematic configuration diagram of an optical tomographic imaging apparatus according to a first embodiment of the present invention. Schematic diagram showing an example of the light beam emitted from the light source unit Block diagram showing an example of the tomographic image processing means of FIG. Diagram for explaining how to measure compensation data from a substance that mimics the measurement target The figure which shows an example of the interference signal detected in an interference light detector The figure which shows the tomographic information of each depth position when analyzing the frequency of the interference light detected in the interference light detector Diagram for explaining dispersion compensation method The figure for demonstrating the flow of a process of the tomographic image processing means of FIG. Schematic configuration diagram of an optical tomographic imaging apparatus according to a second embodiment of the present invention Block diagram showing an example of the tomographic image processing means of FIG. Diagram for explaining the method for estimating the interference signal and the substance to be measured The figure for demonstrating the flow of a process of the tomographic image processing means of FIG. Schematic configuration diagram of an optical tomographic imaging apparatus according to a third embodiment of the present invention Block diagram showing an example of the tomographic image processing means of FIG. The figure which shows an example of the weight of the tomographic information of each depth position The figure for demonstrating the flow of a process of the tomographic image processing means of FIG. Schematic configuration diagram of an optical tomographic imaging apparatus according to a fourth embodiment of the present invention Block diagram showing an example of the tomographic image processing means of FIG. The figure for demonstrating the flow of a process of the tomographic image processing means of FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1, 1a, 1b, 1c Optical tomographic imaging apparatus 2 Interference signal detector 3 Light splitting means 4 Multiplexing means 10 Light source unit 40 Interference light detection means 50, 50a, 50b, 50c Tomographic image processing means 51 Compensation data storage means 52 Compensation means 53 Tomographic information acquisition means 54 Tomographic image generation means 55 Measurement object estimation means 56 Compensation signal acquisition means 57 Synthetic tomographic information acquisition means 58 Frequency component separation means 59 Frequency component synthesis means 60 Display device

Claims (10)

  1. The reflected light emitted from the light source is divided into measurement light and reference light, and the divided measurement light is reflected from the object to be measured and combined with the reference light. An interference signal detector for detecting the intensity of interference light between the reference light and the reference light as an interference signal;
    At least one of an attenuation factor that changes according to the wave number when the measurement light propagates to a predetermined depth position and a refractive index of a substance having characteristics close to the measurement object is stored as compensation data. Compensation data storage means;
    Compensation means for performing at least one of attenuation compensation of the intensity of the interference signal and dispersion compensation according to the refractive index of the interference signal, using the compensation data;
    Tomographic information acquisition means for acquiring the tomographic information of the measurement object by performing frequency analysis on the interference signal compensated by the compensation means;
    An optical tomographic imaging apparatus comprising: a tomographic image generating means for generating a tomographic image using the tomographic information.
  2.   The optical tomographic imaging apparatus according to claim 1, wherein the compensation data is obtained by measuring in advance using a substance having characteristics close to the measurement target instead of the measurement target.
  3. The compensation data storage means stores compensation data for a plurality of substances having characteristics close to the measurement object,
    A measurement object estimation means for estimating the substance close to the characteristic of the measurement object from the detected interference signal;
    The optical tomographic imaging apparatus according to claim 1, wherein the compensation means uses the compensation data of the estimated substance.
  4. The interference signal is composed of an intensity component of the measurement light, an intensity component of the reflected light, and an interference component of the measurement light and the reflected light,
    The compensation data includes the attenuation rate;
    The measurement object estimation means is
    Measurement light intensity storage means for storing the intensity of the measurement light measured in advance;
    Interference component removing means for removing an interference component by smoothing a fine vibration component placed on a component of a wave with a large period on the interference signal;
    Reflected light intensity extracting means for extracting the intensity of the reflected light by removing the intensity of the measurement light from the interference signal from which the interference component has been removed by the interference component removing means;
    The substance to be measured is estimated by comparing the attenuation amount of the reflected light extracted by the reflected light intensity extracting means with the attenuation rate of the compensation data for the plurality of substances. The optical tomographic imaging apparatus according to claim 3, wherein:
  5. The compensation data storage means stores compensation data when the measurement light is reflected from different depth positions of the substance, respectively.
    The compensation means compensates the interference signal by using compensation data at each depth position;
    The tomographic information acquisition means acquires a plurality of tomographic information by frequency analysis of each compensated interference signal,
    It further comprises synthetic tomographic information acquisition means for acquiring tomographic information obtained by synthesizing the plurality of tomographic information so that the degree of influence at the depth position compensated for the interference signal from which the tomographic information has been acquired is greater than that of other tomographic information. ,
    The optical tomographic imaging apparatus according to claim 1, wherein the tomographic image generation unit generates the tomographic image from the tomographic information synthesized by the synthetic tomographic information acquisition unit.
  6. The reflected light emitted from the light source is divided into measurement light and reference light, and the divided measurement light is reflected from the object to be measured and combined with the reference light. An interference signal detector for detecting the intensity of interference light between the reference light and the reference light as an interference signal;
    Attenuation rate storage means for storing, for each depth position, an attenuation rate that changes according to the wave number when the measurement light propagates to a different depth position of a substance having characteristics close to the measurement target;
    Frequency component separation means for separating the interference signal into components of a plurality of frequency bands;
    Attenuation compensation of the intensity of each frequency band component using the attenuation rate stored in the attenuation rate storage means corresponding to the depth position of the tomographic information obtained by frequency analysis of the interference signal of each frequency band Intensity compensation means for performing
    Frequency component synthesizing means for synthesizing the components of the respective frequency bands that have been attenuation-compensated by the intensity compensating means to obtain interference signals in all frequency bands;
    A tomographic information acquisition means for acquiring the tomographic information of the measurement object by performing frequency analysis on the interference signals in the entire frequency band;
    An optical tomographic imaging apparatus comprising: a tomographic image generating means for generating a tomographic image using the tomographic information.
  7. Refractive index storage means for storing a refractive index that changes according to the wave number when the measurement light of the substance having characteristics close to the measurement object propagates to a predetermined depth position;
    Dispersion compensation means for performing dispersion compensation of the combined interference signals in all frequency bands using the refractive index stored in the refractive index storage means,
    7. The optical tomographic imaging apparatus according to claim 6, wherein the tomographic information acquisition unit performs frequency analysis on the interference signal in the entire frequency band that has been dispersion-compensated by the dispersion compensation unit.
  8. Refractive index storage means for storing a refractive index that changes according to the wave number when the measurement light of the substance having characteristics close to the measurement object propagates to a predetermined depth position;
    Dispersion compensation means for performing dispersion compensation of the interference signal detected by the interference signal detector using the refractive index stored in the refractive index storage means,
    7. The optical tomographic imaging apparatus according to claim 6, wherein the frequency component separation means separates the interference signal dispersion-compensated by the dispersion compensation means into a plurality of frequency band components.
  9.   9. The optical tomography according to claim 6, wherein the attenuation factor is obtained by measuring in advance using a substance having characteristics close to the measurement object instead of the measurement object. Imaging device.
  10.   The optical tomography according to any one of claims 7 to 9, wherein the refractive index is obtained by measuring in advance using a substance having characteristics close to the measurement object instead of the measurement object. Imaging device.
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