An eye surgery surgical system includes a device for displaying a relative position of a section of a surgery object in a 3D reconstruction of a region of an eye, a device for continuously providing at least two data records relating to at least partly overlapping portions of the region of the eye and of the section of the surgery object to a computer, a computer program for continuously ascertaining the relative position of the section of the surgery object and continuously ascertaining the 3D reconstruction of the eye from the data records provided. The program includes a first routine for continuously ascertaining the relative position of the section of the surgery object and the 3D reconstruction of the region of the eye from the data records provided via a registration method and a second routine for adapting the registration method based on a criterion.

A photocoagulation apparatus of some embodiment examples is configured to apply both treatment light for subthreshold coagulation and an OCT scan to a retina via a probe inserted in an eye. Upon receiving a user's instruction, the apparatus applies the treatment light to the retina, and applies an OCT scan to the retina at least after the treatment light application. The apparatus compares the first OCT image constructed from OCT data of the retina acquired prior to the treatment light application and the second OCT image constructed from OCT data of the retina acquired after the treatment light application, thereby acquiring change information that represents a tissue change in the retina caused by the treatment light. The apparatus displays a change image based on the change information together with a retinal image.

An OCT data processing device includes a processor that performs acquiring three-dimensional OCT data. The three-dimensional OCT data is OCT data of a tissue of a subject's eye acquired by an OCT device and is obtained by irradiating measurement light on a two-dimensional measurement region. The two-dimensional measurement region extends in a direction intersecting an optical axis of the measurement light. The processor further preforms setting a line pattern, from among a plurality of types of line pattern, with respect to the two-dimensional measurement region for which the three-dimensional OCT data is obtained, at least one of an arrangement, a number, or a shape of one or more lines being different for the plurality of types of line pattern, and extracting, from the three-dimensional OCT data, a two-dimensional tomographic image of a cross section intersecting each of the one or more lines of the set line pattern.

A 3-D imaging system including a computer determining a plurality of coherence factors measuring an intensity contrast between a first intensity of a first region of an interference comprising constructive interference between a sample wavefront and a reference wavefront, and a second intensity of a second region of the interference comprising destructive interference between the sample wavefront and the reference wavefront, wherein the interference between a reference wavefront and a reflection from different locations on a surface of an object. From the coherence factors, the computer determines height data comprising heights of the surface with respect to an x-y plane perpendicular to the heights and as a function of the locations in the x-y plane. The height data is useful for generating a three dimensional topological image of the surface.

A technique capable of providing a user with information obtained by OCT imaging in a useful way, particularly for assisting in assessment of an embryo effectively. The image processing method includes acquiring original signal data indicating an intensity distribution of signal light from each position in three-dimensional space including a cultured embryo obtained by optical coherence tomography imaging, generating spherical coordinate data based on the original signal data, the spherical coordinate data indicating a relationship between each position in the three-dimensional space represented using spherical coordinates having an origin set inside the embryo and the intensity of the signal light from the position, and outputting the intensity distribution of the signal light as a two-dimensional map based on the spherical coordinate data using two deflection angles of the spherical coordinates as coordinate axes.

A method of generating a look-up table, LUT, for constructing a dewarped B-scan image from A-scans of a cropped part of a sequence of acquired OCT A-scans, the LUT associating each of a plurality of pixel arrays that are to form the dewarped B-scan image with a respective A-scan in the cropped part. The method comprises: using an indication of a spatial distribution of scan locations of A-scans to determine a dewarp function for selecting, from among acquired A-scans, A-scans having uniformly spaced scan locations; using the function and cropping information, in accordance with which the cropped part is cropped from the acquired sequence, to select, for each array, a respective A-scan from the sequence such that A-scans are selected from the cropped part and have uniformly spaced scan locations; and storing, for each array, a respective pixel array identifier in association with a respective identifier of the selected A-scan.

A method of generating a look-up table, LUT, for constructing a dewarped B-scan image from A-scans of a cropped part of a sequence of acquired OCT A-scans, the LUT associating each of a plurality of pixel arrays that are to form the dewarped B-scan image with a respective A-scan in the cropped part. The method comprises: using an indication of a spatial distribution of scan locations of A-scans to determine a dewarp function for selecting, from among acquired A-scans, A-scans having uniformly spaced scan locations; using the function and cropping information, in accordance with which the cropped part is cropped from the acquired sequence, to select, for each array, a respective A-scan from the sequence such that A-scans are selected from the cropped part and have uniformly spaced scan locations; and storing, for each array, a respective pixel array identifier in association with a respective identifier of the selected A-scan.

A target image to be corrected is generated by arranging partial images acquired by scanning a tissue of a living body with light and temporally continuously receiving the light from the tissue. A processor of a medical image processing device performs detecting position shift amounts, acquiring a component, and correcting. In the process of detecting position shift amounts, the processor detects the position shift amounts between the partial images (S3). In the process of acquiring, the processor acquires an assumed result of at least one of a component in the position shift amount caused by movement of the tissue, and a component in the position shift amount caused by a shape of the tissue (S4). In the process of correcting, the processor corrects a position of each of the partial images based on the component in the position shift amount (S7).

A system for non-contact imaging of corneal tissue stored in a viewing chamber using Gabor-domain optical coherence microscopy (GDOCM), wherein a 3D numerical flattening procedure is applied to the image data to produce an at least substantially artifact-free en face view of the endothelium.

An ophthalmic imaging apparatus includes: a detector arranged to detect, as an interference signal, interference light resulting from returning light and reference light, the returning light being light from an object to be inspected to which measurement light is radiated, the reference light corresponding to the measurement light; a converter arranged to convert the detected interference signal that is an analog signal to a digital signal; and an arithmetic processing unit configured to generate a tomographic image of the object to be inspected by using the converted interference signal. The arithmetic processing unit uses a plurality of components obtained from the converted interference signal to generate the tomographic image, the plurality of components including a component having a frequency higher than a Nyquist frequency of the converter and a component having a frequency lower than the Nyquist frequency of the converter.