Abstract: An information processing device according to an embodiment includes a learning unit that performs learning on a machine learning model having one or more non-polarization OCT images that are OCT images without polarization information as inputs and a pseudo polarization OCT image corresponding to a polarization OCT image that is an OCT image with polarization information as output; and a storage unit that stores a learning result of the learning unit.

Abstract: In a scanning imaging apparatus of some aspect examples, a scanner applies an optical scan to a sample to acquire data. A scan controller controls the scanner to sequentially apply, to the sample, pattern scans according to a two-dimensional pattern including cycles. A movement unit relatively moves a scan area corresponding to the two-dimensional pattern and the sample. A movement controller controls the movement unit such that cycles in first and second scans of the pattern scans cross each other. An image constructing unit constructs an image based on data acquired under controls performed by the scan controller and the movement controller. The scan controller and the movement controller perform controls of the scanner and the movement unit respectively such that first and second cycles in a pattern scan cross each other at least at one point.

Abstract: An image generation device includes a tomographic image acquisition unit configured to acquire an OCTA tomographic image that captures a distribution of a blood flow of an object, a light attenuation acquisition unit configured to acquire a light attenuation of measurement light emitted to the object in a direction in which the tomographic image is layered, and an image generation unit configured to generate a light attenuation-blood flow distribution chart indicating a distribution of the light attenuation based on the acquired OCTA tomographic image and the light attenuation.

Abstract: A model learning unit determines a model parameter for calculating an estimated value for each of a plurality of training sets, each including a measurement signal and at least one type of predetermined characteristic value indicating characteristics of the measurement signal as a target value, to minimize a difference between the estimated value calculated for the measurement signal using a predetermined mathematical model and the target value is minimized, determines characteristic value sets, each being a set of a plurality of types of characteristic values indicating characteristics of the measurement signal including the target value, with which, for each target value, the target value is common to a plurality of characteristic value sets, and generates, for each of the characteristic value sets, each of the plurality of training sets including the target value and a measurement signal having characteristics indicated by the plurality of types of characteristic values.

Abstract: A phase gradient calculation unit calculates a phase gradient on a plane intersecting an irradiation direction of light corresponding to an optical coherence tomography signal indicating a state of a sample for each of sample points arranged on the plane. A bulk phase error calculation unit integrates, for each of plurality of paths from an origin that is a sample point where a bulk phase error is determined to a destination that is a sample point where the bulk phase error is not determined, the phase gradient for each of the sample points along each of the plurality of corresponding paths to calculate a path specific phase error at the destination, and combines the path specific phase errors among the plurality of corresponding paths to determine the bulk phase error at the destination.

Abstract: Provided is an evaluation method for a biological tissue that enables dynamics of the biological tissue to be quantitatively evaluated. In the evaluation method of the present embodiment, an optical coherence tomography (OCT) signal indicating a state of a biological tissue provided as a sample is acquired, a signal value based on the OCT signal is acquired at an observation point in the sample, and a temporal variation characteristic value indicating a temporal variation characteristic of the signal value within a predetermined period is calculated. The present embodiment can also be implemented with an evaluation device or even with a program.

Abstract: A method of processing ophthalmic data of some embodiment examples includes preparing a data set acquired by applying optical scanning of a two-dimensional pattern to a subject's eye. The two-dimensional pattern of the optical scanning includes a series of cycles that intersects each other. The method further includes generating position history data based on the data set. The position history data represents a temporal change in a position of the subject's eye.

Abstract: In a scanning imaging apparatus of some aspect examples, a scanner applies an optical scan to a sample to acquire data. A scan controller controls the scanner to sequentially apply, to the sample, pattern scans according to a two-dimensional pattern including cycles. A movement unit relatively moves a scan area corresponding to the two-dimensional pattern and the sample. A movement controller controls the movement unit such that cycles in first and second scans of the pattern scans cross each other. An image constructing unit constructs an image based on data acquired under controls performed by the scan controller and the movement controller. The scan controller and the movement controller perform controls of the scanner and the movement unit respectively such that first and second cycles in a pattern scan cross each other at least at one point.

Abstract: A Jones matrix OCT offers improved image stability, image quality, and depth range of image, wherein light from a wavelength-scanning light source is split into two optical paths, and a reference arm is provided along one optical path, while a probe arm that irradiates and reflects light onto the measuring target to generate object light is provided along the other optical path. The probe arm has a polarization delay unit that linearly polarizes the light and then splits it into S-wave component and P-wave component, where the S-wave component and P-wave component are superimposed through optical paths of different optical path lengths, respectively, after which optical detectors are used to detect different spectral interference beams in the depth direction of the measuring target corresponding to the vertically polarized component and horizontally polarized component, which respectively correspond to the S-wave component and P-wave component, to obtain four spectral interference signals.

Abstract: From OCT-measured data, only the image data of the choroidal vascular network present in the layer of the choroidal layer is selectively extracted, thereby accurately obtaining the thickness of the choroidal vessels and thickness of the choroidal vascular network from the image data, to allow for quantitative evaluation of the choroidal vascular network. The optical coherence tomography apparatus has an optical coherence tomography device, and a computer that processes the three-dimensional OCT tomographic images obtained based on the OCT-measured data acquired by the optical coherence tomography device. The computer functions as a means for selectively separating out only the images of the choroidal vessels from the three-dimensional OCT tomographic images to acquire image data of the choroidal vessels, and also as a means for obtaining the data to be used in the quantitative evaluation of the shape of the choroidal vessels based on the image data of the choroidal vessels.

Abstract: In polarization-sensitive optical image measurement, noise-containing OCT signals obtained by polarization OCT are processed using a birefringence calculation algorithm, to obtain measured birefringence, after which noise is statistically adjusted to simulate a measured birefringence distribution and determine the noise characteristics of the measured birefringence values, and then Monte Carlo calculations are repeated by assuming different values for the noise level and the true birefringence value, respectively, to form three-dimensional histogram of combinations of true birefringence values, SN ratios, and measured birefringence values, after which specified measured birefringence values and SN ratios are assumed from the three-dimensional histogram information to obtain a true birefringence probability density distribution, and true birefringence values are estimated from the true birefringence probability density distribution.

Abstract: In polarization-sensitive optical image measurement, noise-containing OCT signals obtained by polarization OCT are processed using a birefringence calculation algorithm, to obtain measured birefringence, after which noise is statistically adjusted to simulate a measured birefringence distribution and determine the noise characteristics of the measured birefringence values, and then Monte Carlo calculations are repeated by assuming different values for the noise level and the true birefringence value, respectively, to form three-dimensional histogram of combinations of true birefringence values, SN ratios, and measured birefringence values, after which specified measured birefringence values and SN ratios are assumed from the three-dimensional histogram information to obtain a true birefringence probability density distribution, and true birefringence values are estimated from the true birefringence probability density distribution.

Abstract: Data measured by PS-OCT is corrected in a non-linear manner to enhance the quantitative analysis capability of PS-OCT and permit accurate quantitative diagnosis, including diagnosis of disease stage of lesions, as a useful means for computer diagnosis. Even when retardation per PS-OCT 1 contains error and becomes noise and its distribution is not normal or symmetrical around the true value, measured data is converted using a distribution conversion function obtained by analyzing the characteristics of noise via Monte Carlo simulation to remove the systematic error and estimate the true value otherwise buried in noise and thereby correct the PS-OCT 1 image more clearly.

Abstract: In an embodiment, a computer 16, which generates tomographic images based on spectral interference signals detected by a light detector 15 from overlaid reference light emitted by a swept-source type light source 2 of a SS-OCT, split, and then reflected by a fixed reference mirror 8 on one hand and object light reflected by an object to be measured 6 on the other, is caused to function to apply rough correction using a first correction means and then apply detailed correction using a second correction means, to stabilize the phases of the SS-OCT. The phases can be stabilized by eliminating, without adding any expensive, complex hardware, the jitter between the wavelength scanning of a light source of SS-OCT and the timing of collecting the scan data with the light detector as spectral interference signals.

Abstract: From OCT-measured data, only the image data of the choroidal vascular network present in the layer of the choroidal layer is selectively extracted, thereby accurately obtaining the thickness of the choroidal vessels and thickness of the choroidal vascular network from the image data, to allow for quantitative evaluation of the choroidal vascular network. The optical coherence tomography apparatus has an optical coherence tomography device, and a computer that processes the three-dimensional OCT tomographic images obtained based on the OCT-measured data acquired by the optical coherence tomography device. The computer functions as a means for selectively separating out only the images of the choroidal vessels from the three-dimensional OCT tomographic images to acquire image data of the choroidal vessels, and also as a means for obtaining the data to be used in the quantitative evaluation of the shape of the choroidal vessels based on the image data of the choroidal vessels.

Abstract: A Jones matrix OCT offers improved image stability, image quality, and depth range of image, wherein light from a wavelength-scanning light source is split into two optical paths, and a reference arm is provided along one optical path, while a probe arm that irradiates and reflects light onto the measuring target to generate object light is provided along the other optical path. The probe arm has a polarization delay unit that linearly polarizes the light and then splits it into S-wave component and P-wave component, where the S-wave component and P-wave component are superimposed through optical paths of different optical path lengths, respectively, after which optical detectors are used to detect different spectral interference beams in the depth direction of the measuring target corresponding to the vertically polarized component and horizontally polarized component, which respectively correspond to the S-wave component and P-wave component, to obtain four spectral interference signals.

Abstract: In an embodiment, a computer 16, which generates tomographic images based on spectral interference signals detected by a light detector 15 from overlaid reference light emitted by a swept-source type light source 2 of a SS-OCT, split, and then reflected by a fixed reference mirror 8 on one hand and object light reflected by an object to be measured 6 on the other, is caused to function to apply rough correction using a first correction means and then apply detailed correction using a second correction means, to stabilize the phases of the SS-OCT. The phases can be stabilized by eliminating, without adding any expensive, complex hardware, the jitter between the wavelength scanning of a light source of SS-OCT and the timing of collecting the scan data with the light detector as spectral interference signals.

Abstract: The scanning speed of a sample in Doppler OCT, etc., is increased to enable quick measurement of blood flow rate, blood flow volume, etc.

Abstract: Data measured by PS-OCT is corrected in a non-linear manner to enhance the quantitative analysis capability of PS-OCT and permit accurate quantitative diagnosis, including diagnosis of disease stage of lesions, as a useful means for computer diagnosis. Even when retardation per PS-OCT 1 contains error and becomes noise and its distribution is not normal or symmetrical around the true value, measured data is converted using a distribution conversion function obtained by analyzing the characteristics of noise via Monte Carlo simulation to remove the systematic error and estimate the true value otherwise buried in noise and thereby correct the PS-OCT 1 image more clearly.

Abstract: The scanning speed of a sample in Doppler OCT, etc., is increased to enable quick measurement of blood flow rate, blood flow volume, etc.