JP2020174928A - Ophthalmologic apparatus and control method of the same - Google Patents

Abstract

To provide a novel technique for efficiently grasping a form or the like of a portion of interest in the eyeground or the like of a subject eye.SOLUTION: An ophthalmologic apparatus comprises an optical system and a control unit. The optical system includes an optical scanner, polarizes light from a light source by using the optical scanner, and thereby scans a predetermined scanning region to collect data on a subject eye. The control unit controls the optical scanner to execute plural scannings radially, centering a scanning center position different from the center of the scanning region.SELECTED DRAWING: Figure 3

Description

The present invention relates to an ophthalmic apparatus and a method for controlling the same.

In recent years, OCT that forms an image showing the surface morphology and internal morphology of an object to be measured by using a light beam from a laser light source or the like has attracted attention. Since OCT does not have invasiveness to the human body like X-ray CT (Computed Tomography), it is expected to be applied especially in the medical field and the biology field. For example, in the field of ophthalmology, devices for forming images of the fundus, cornea, etc. have been put into practical use. A device using such an OCT method (OCT device) can be applied to observation of various parts of the eye to be inspected, and can acquire high-definition images, so that it is applied to diagnosis of various ophthalmic diseases. ..

In OCT measurement by an OCT device, it is known that the measurement accuracy (image quality) and the measurement time (shooting time) have a negative correlation. The OCT apparatus can perform OCT measurement in various scanning modes. For example, the OCT apparatus can acquire data for grasping the morphology of the region of interest in detail while shortening the measurement time by performing a radial scan centering on the region of interest (for example, Patent Documents). 1).

Japanese Patent Application Laid-Open No. 2009-523563

A general radial scan is a rotationally symmetric scan with the area of interest as the center of the measurement range. However, when measuring the area around the macula of the fundus, it is necessary to project the fixation light flux so that the fixation position of the eye to be inspected is located away from the measurement optical axis, and the morphology of the attention portion is efficient. I can't figure it out.

The present invention has been made in view of such circumstances, and an object of the present invention is to provide a new technique for efficiently grasping the morphology of a region of interest on the fundus of an eye to be inspected.

A first aspect of some embodiments comprises an optical system comprising an optical scanner that scans a predetermined scan area by deflecting light from a light source by the optical scanner to collect data for the eye to be inspected, and said scanning. An ophthalmic apparatus including a control unit that controls the optical scanner to perform a plurality of scans radially around a scan center position different from the center of the region.

In the second aspect of some embodiments, the scan center position is modifiable in the first aspect.

The third aspect of some embodiments includes an operation unit in the first or second aspect, and the control unit sets the scan center position based on the operation content for the operation unit.

A fourth aspect of some embodiments is, in the first or second aspect, the eye to be inspected by analyzing an acquisition unit that acquires an image of the eye to be inspected and the image acquired by the acquisition unit. The control unit includes an analysis unit for specifying the feature region of the above, and the control unit sets a position in the feature region specified by the analysis unit as the scan center position.

A fifth aspect of some embodiments sets a scan start position based on the scan area and the scan center position for each of the plurality of scans in any of the first to fourth aspects. The control unit includes one setting unit and a second setting unit that sets a scan end position based on the scan area and the scan center position for each of the plurality of scans. For each, the optical scanner is controlled based on the scan start position set by the first setting unit and the scan end position set by the second setting unit.

In a sixth aspect of some embodiments, in any of the first to fifth aspects, the control unit performs the plurality of scans centered on each of two or more scan center positions within the same scan area. Control the optical scanner to perform.

In a seventh aspect of some embodiments, in any of the first to sixth aspects, the optical system divides the light from the light source into measurement light and reference light and deflects them by the optical scanner. The interference light obtained by the interference optical system includes an interference optical system that projects the measurement light onto the eye to be inspected and detects interference light between the return light of the measurement light from the eye to be inspected and the reference light. Includes an image forming portion that forms a tomographic image of the eye to be inspected based on the detection result of.

The eighth aspect of some embodiments was obtained by the image forming unit by performing the plurality of scans so that the plurality of scan center positions in the plurality of scans substantially coincide with each other in the seventh aspect. It includes an alignment unit for aligning a plurality of tomographic images and a compositing unit for synthesizing a plurality of tomographic images aligned by the alignment unit.

In the ninth aspect of some embodiments, in the eighth aspect, the control unit controls the optical scanner so that the scan center position and the scan direction of at least one of the plurality of scans substantially coincide with each other. This causes the plurality of scans to be performed on a plurality of scan areas that are different from each other.

In the tenth aspect of some embodiments, in any of the seventh to ninth aspects, the control unit has a plurality of obtained by the image forming unit such that the feature positions in each scan are substantially the same. The tomographic image is switched and displayed on the display means.

An eleventh aspect of some embodiments is a method of controlling an ophthalmic apparatus for collecting data on an eye to be examined. The control method of the ophthalmic apparatus includes a setting step of setting a scan center position different from the center of a predetermined scan area, and a plurality of scans radiating around the scan center position by deflecting light from a light source by an optical scanner. A control step that controls the optical scanner so as to do so.

In the twelfth aspect of some embodiments, in the eleventh aspect, the setting step sets the scan center position based on the operation content for the operation unit.

In the thirteenth aspect of some embodiments, in the eleventh or twelfth aspect, the eye to be inspected is obtained by analyzing the acquisition step of acquiring the image of the eye to be inspected and the image acquired in the acquisition step. The setting step includes an analysis step for specifying the feature region of the above, and the setting step sets a position in the feature region specified in the analysis step as the scan center position.

In a fourteenth aspect of some embodiments, in any of the eleventh to thirteenth aspects, the control step performs the plurality of scans centered on each of two or more scan center positions within the same scan area. Control the optical scanner to perform.

The fifteenth aspect of some embodiments is an image in which a tomographic image of the eye to be inspected is formed by performing optical coherence tomography using light from the light source in any of the eleventh to fourteenth aspects. Includes formation steps.

The sixteenth aspect of some embodiments was obtained in the image forming step by performing the plurality of scans so that the plurality of scan center positions in the plurality of scans substantially coincide with each other in the fifteenth aspect. It includes an alignment step for aligning a plurality of tomographic images and a synthesis step for synthesizing a plurality of tomographic images aligned in the alignment step.

In the 17th aspect of some embodiments, in the 16th aspect, the control step controls the optical scanner so that the scan center position coincides with at least one scan direction of the plurality of scans. This causes the plurality of scans to be performed on a plurality of scan areas that are different from each other.

In the 18th aspect of some embodiments, in the 16th or 17th aspect, the control step captures a plurality of tomographic images obtained in the image formation step so that the feature positions in each scan are substantially the same. Switch and display on the display means.

It is possible to arbitrarily combine the plurality of modes described above.

According to the present invention, it is possible to provide a new technique for efficiently grasping the morphology of the region of interest in the fundus of the eye to be inspected.

It is the schematic which shows an example of the structure of the ophthalmic apparatus which concerns on embodiment. It is the schematic which shows an example of the structure of the ophthalmic apparatus which concerns on embodiment. It is a schematic block diagram which shows an example of the structure of the ophthalmic apparatus which concerns on embodiment. It is a schematic block diagram which shows an example of the structure of the ophthalmic apparatus which concerns on embodiment. It is a schematic block diagram which shows an example of the structure of the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on the comparative example of Embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on the comparative example of Embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the process performed by the ophthalmic apparatus which concerns on embodiment. It is the schematic which shows the operation example of the ophthalmic apparatus which concerns on embodiment.

An example of an ophthalmic apparatus according to the present invention and an embodiment of a control method thereof will be described in detail with reference to the drawings. In addition, the description contents of the document cited in this specification and any known technique can be incorporated into the following embodiments.

The ophthalmic apparatus according to the embodiment can collect data of the eye to be inspected by scanning a predetermined scan area in the eye to be inspected by deflecting the light from the light source using an optical scanner. The ophthalmic apparatus sets an arbitrary position in the scan area as the scan center position, and controls the optical scanner to perform a plurality of scans radially around the set scan center position. The scan center position includes a position different from the center of the scan area (a position away from the center of the scan area, a position eccentric from the center of the scan area), and the like.

At least one of the plurality of radial scans includes a line scan in the B scan direction. The plurality of radial scans according to the embodiment is a radial scan (radial scan). The scan start position and scan end position of each scan are set at or near the boundary of the scan area. That is, in each scan, the first scan length in the B scan direction from the scan start position to the scan center position and the second scan length in the B scan direction from the scan center position to the scan end position may be different. For a plurality of radial scans, the ratio of the second scan length to the first scan length and the ratio of the first scan length or the second scan length to the sum of the first scan length and the second scan length may be different from each other.

It is possible to set the scan center position within the feature region identified by analyzing the image of the eye to be inspected (for example, the front image). In some embodiments, the scan center position is a predetermined position within the scan area.

As a result, by controlling the optical scanner according to the position of the feature region of the eye to be inspected, it is possible to perform a plurality of radial scans centered on the scan center position in the feature region. As a result, it becomes possible to collect the data of the feature region more efficiently than before.

The method of controlling an ophthalmic apparatus according to an embodiment includes one or more steps for realizing control executed by a processor (computer) in the ophthalmic apparatus according to the embodiment. The ophthalmic information processing method according to the embodiment includes one or more steps for realizing a process executed by a processor in the ophthalmic apparatus according to the embodiment. The program according to the embodiment causes the processor to execute each step of the control method of the ophthalmic apparatus according to the embodiment or the ophthalmic information processing method according to the embodiment.

In the present specification, the "processor" is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD (Simple Program)), a programmable logic device (for example, a SPLD) It means a circuit such as Programmable Logic Device) and FPGA (Field Programmable Gate Array). The processor realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

In this specification, images acquired by OCT may be collectively referred to as OCT images. Further, the measurement operation for forming an OCT image may be referred to as OCT measurement.

Hereinafter, in the embodiment, the case where the Swept source type OCT method is used in the measurement or imaging using the OCT will be described in particular detail. However, it is also possible to apply the configuration according to the embodiment to an ophthalmic apparatus using another type of OCT (eg, spectral domain type or time domain type). Further, the configuration according to the embodiment may be applied to an ophthalmic apparatus including an SLO optical system.

The ophthalmologic apparatus according to some embodiments includes any one or more of an ophthalmologic imaging apparatus, an ophthalmologic measuring apparatus, and an ophthalmic treatment apparatus. The ophthalmologic imaging apparatus included in some embodiments of the ophthalmologic apparatus is, for example, any one or more of a fundus camera, a scanning laser ophthalmoscope, a slit lamp ophthalmoscope, a surgical microscope, and the like. Further, the ophthalmic measuring device included in the ophthalmic device of some embodiments is, for example, any one or more of an ophthalmoflex test device, a tonometer, a specular microscope, a wavefront analyzer, a perimeter, a microperimeter and the like. Is. In addition, the ophthalmic treatment device included in the ophthalmic device of some embodiments is, for example, any one or more of a laser treatment device, a surgical device, a surgical microscope, and the like.

The ophthalmic apparatus according to the following embodiment includes an OCT apparatus capable of OCT measurement and a fundus camera. It is also possible to incorporate the configuration according to the following embodiment into a single OCT device.

Hereinafter, an ophthalmic apparatus capable of OCT measurement on the fundus of the eye to be inspected will be mainly described as an example, but the ophthalmic apparatus according to the embodiment may be capable of OCT measurement on the anterior segment of the eye to be inspected. .. In some embodiments, the range of OCT measurement and the measurement site are changed by moving the lens that changes the focal position of the measurement light. In some embodiments, by adding one or more attachments (objective lens, anterior lens, etc.), OCT measurement for the fundus, OCT measurement for the anterior segment of the eye, and OCT for the entire eyeball including the fundus and anterior segment of the eye It is a configuration that can be measured. In some embodiments, in an ophthalmic apparatus for fundus measurement, a front lens is placed between the objective lens and the eye to be inspected so that the measurement light made into a parallel light beam is incident on the eye to be inspected. OCT measurement is performed for.

<Composition>
〔Optical system〕
As shown in FIG. 1, the ophthalmic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye E to be inspected. The OCT unit 100 is provided with a part of an optical system and a mechanism for executing OCT. The other part of the optical system and mechanism for performing OCT is provided in the fundus camera unit 2. The arithmetic and control unit 200 includes one or more processors that execute various arithmetic operations and controls. In addition to these, any element such as a member for supporting the subject's face (jaw holder, forehead pad, etc.) and a lens unit for switching the target part of OCT (for example, an attachment for anterior segment OCT). Or unit may be provided in the ophthalmic apparatus 1. In some embodiments, the lens unit is configured to be manually inserted and removed between the eye E to be inspected and the objective lens 22 described below. In some embodiments, the lens unit is automatically inserted and removed between the eye E to be inspected and the objective lens 22 described later under the control of the control unit 210 described later.

In some embodiments, the ophthalmic apparatus 1 includes a display device 3. The display device 3 displays a processing result (for example, an OCT image) by the arithmetic control unit 200, an image obtained by the fundus camera unit 2, operation guidance information for operating the ophthalmic device 1, and the like.

[Fundus camera unit]
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef of the eye to be inspected E. The acquired image of the fundus Ef (called a fundus image, a fundus photograph, etc.) is a front image such as an observation image, a photographed image, or the like. The observed image is obtained by taking a moving image using near infrared light. The captured image is a still image using flash light. Further, the fundus camera unit 2 can capture the anterior segment Ea of the eye E to be inspected and acquire a frontal image (anterior segment image).

The fundus camera unit 2 includes an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the eye E to be inspected with illumination light. The photographing optical system 30 detects the return light of the illumination light from the eye E to be inspected. The measurement light from the OCT unit 100 is guided to the eye E to be inspected through the optical path in the fundus camera unit 2, and the return light is guided to the OCT unit 100 through the same optical path.

The light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by the reflection mirror 12 having a curved reflecting surface, passes through the condenser lens 13, and passes through the visible cut filter 14. It becomes near infrared light. Further, the observation illumination light is once focused in the vicinity of the photographing light source 15, reflected by the mirror 16, and passes through the relay lenses 17, 18, the diaphragm 19, and the relay lens 20. Then, the observation illumination light is reflected by the peripheral portion of the perforated mirror 21 (the region around the perforated portion), passes through the dichroic mirror 46, is refracted by the objective lens 22, and is the eye to be inspected E (fundus Ef or anterior eye). Illuminate part Ea). The return light of the observation illumination light from the eye E to be inspected is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the perforated mirror 21, and passes through the dichroic mirror 55. .. The return light transmitted through the dichroic mirror 55 passes through the photographing focusing lens 31 and is reflected by the mirror 32. Further, this return light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the image sensor 35 by the condenser lens 34. The image sensor 35 detects the return light at a predetermined frame rate. The focus of the photographing optical system 30 is adjusted so as to match the fundus Ef or the anterior segment Ea.

The light output from the photographing light source 15 (photographing illumination light) is applied to the fundus Ef through the same path as the observation illumination light. The return light of the photographing illumination light from the eye E to be examined is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the condenser lens 37. An image is formed on the light receiving surface of the image sensor 38.

The LCD (Liquid Crystal Display) 39 displays a fixation target and a visual acuity measurement target. A part of the light flux output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, passes through the photographing focusing lens 31 and the dichroic mirror 55, and passes through the hole portion of the perforated mirror 21. The luminous flux that has passed through the hole of the perforated mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus Ef.

By changing the display position of the fixation target on the screen of the LCD 39, the fixation position of the eye E to be inspected can be changed. Examples of fixation positions include the fixation position for acquiring an image centered on the macula, the fixation position for acquiring an image centered on the optic nerve head, and the center of the fundus between the macula and the optic nerve head. There is a fixation position for acquiring an image centered on the macula, and a fixation position for acquiring an image of a portion (peripheral part of the fundus) far away from the macula. The ophthalmic apparatus 1 according to some embodiments includes a GUI (Graphical User Interface) and the like for designating at least one such fixation position. The ophthalmic apparatus 1 according to some embodiments includes a GUI or the like for manually moving the fixation position (display position of the fixation target).

The configuration for presenting the movable fixation target to the eye E is not limited to a display device such as an LCD. For example, a movable fixation target can be generated by selectively lighting a plurality of light sources in a light source array (light emitting diode (LED) array or the like). In addition, a movable fixation target can be generated by one or more movable light sources.

Further, the ophthalmic apparatus 1 may be provided with one or more external fixation light sources. One of the one or more external fixation light sources is capable of projecting fixation light onto the companion eye of the eye E to be inspected. The projection position of the fixation light in the companion eye can be changed. By changing the projection position of the fixation light with respect to the companion eye, the fixation position of the eye E to be inspected can be changed. The fixation position by the external fixation light source may be the same as the fixation position of the eye E to be inspected using the LCD 39. For example, a movable fixation target can be generated by selectively turning on a plurality of external fixation light sources. In addition, a movable fixation target can be generated by one or more movable external fixation light sources.

The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E to be inspected. The alignment light output from the LED 51 passes through the diaphragms 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, and passes through the hole portion of the perforated mirror 21. The light that has passed through the hole of the perforated mirror 21 passes through the dichroic mirror 46 and is projected onto the eye E to be inspected by the objective lens 22. The corneal reflected light of the alignment light is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment and auto alignment can be executed based on the received light image (alignment index image).

The focus optical system 60 generates a split index used for focus adjustment with respect to the eye E to be inspected. The focus optical system 60 is moved along the optical path (illumination optical path) of the illumination optical system 10 in conjunction with the movement of the photographing focusing lens 31 along the optical path (photographing optical path) of the photographing optical system 30. The reflection rod 67 is removable with respect to the illumination optical path. When adjusting the focus, the reflecting surface of the reflecting rod 67 is inclined and arranged in the illumination optical path. The focus light output from the LED 61 passes through the relay lens 62, is separated into two luminous fluxes by the split index plate 63, passes through the two-hole diaphragm 64, is reflected by the mirror 65, and is reflected by the condensing lens 66. Once imaged on the reflecting surface of, it is reflected. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus Ef. The fundus reflected light of the focus light is guided to the image sensor 35 through the same path as the corneal reflected light of the alignment light. Manual focus and autofocus can be executed based on the received light image (split index image).

The dichroic mirror 46 synthesizes a fundus photography optical path and an OCT optical path. The dichroic mirror 46 reflects light in the wavelength band used for OCT and transmits light for fundus photography. In the optical path for OCT (optical path of measurement light), the collimator lens unit 40, the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, the mirror 44, in this order from the OCT unit 100 side toward the dichroic mirror 46 side. And a relay lens 45 is provided.

The optical path length changing unit 41 is movable in the direction of the arrow shown in FIG. 1, and changes the length of the optical path for OCT. This change in the optical path length is used for correcting the optical path length according to the axial length and adjusting the interference state. The optical path length changing unit 41 includes a corner cube and a mechanism for moving the corner cube.

The optical scanner 42 is arranged at a position optically conjugate with the pupil of the eye E to be inspected. The optical scanner 42 deflects the measurement light passing through the OCT optical path. That is, the optical scanner 42 deflects the measurement light for scanning the inside of the eye of the eye E while changing the scan angle within a predetermined deflection angle range around the pupil (or its vicinity) of the eye E. The optical scanner 42 can deflect the measurement light one-dimensionally or two-dimensionally.

When one-dimensionally deflected, the optical scanner 42 includes a galvano scanner that deflects the measurement light in a predetermined deflection direction within a predetermined deflection angle range. In the case of two-dimensional deflection, the optical scanner 42 includes a first galvano scanner and a second galvano scanner. The first galvano scanner deflects the measurement light so as to scan the imaging region (fundus Ef or anterior segment) in the horizontal direction orthogonal to the optical axis of the OCT optical system 8. The second galvano scanner deflects the measurement light deflected by the first galvano scanner so as to scan the imaging region in the direction perpendicular to the optical axis of the OCT optical system 8. Examples of the scanning mode of the measured light by the optical scanner 42 include horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric circular scanning, and spiral scanning.

The OCT focusing lens 43 is moved along the optical path of the measurement light in order to adjust the focus of the optical system for OCT. The OCT focusing lens 43 has a first lens position for arranging a focal position of the measurement light at or near the fundus Ef of the eye E to be inspected, and a first lens position for making the measurement light irradiated to the eye E to be inspected a parallel light beam. It can move within the range of movement including the two lens positions. The movement of the photographing focusing lens 31, the movement of the focus optical system 60, and the movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

[OCT unit]
An example of the configuration of the OCT unit 100 is shown in FIG. The OCT unit 100 is provided with an optical system for acquiring an OCT image of the eye E to be inspected. This optical system divides the light from the wavelength sweep type (wavelength scanning type) light source into the measurement light and the reference light, and causes the return light of the measurement light from the eye E to be inspected to interfere with the reference light passing through the reference optical path. This is an interference optical system that generates interference light and detects this interference light. The detection result (detection signal) of the interference light by the interference optical system is an interference signal showing the spectrum of the interference light, and is sent to the arithmetic control unit 200.

The light source unit 101 is configured to include a wavelength sweep type (wavelength scanning type) light source capable of sweeping (scanning) the wavelength of emitted light, similarly to a general swept source type ophthalmic apparatus. The wavelength sweep type light source is configured to include a laser light source including a resonator. The light source unit 101 changes the output wavelength with time in a near-infrared wavelength band that is invisible to the human eye.

The light L0 output from the light source unit 101 is guided by the optical fiber 102 to the polarization controller 103, and its polarization state is adjusted. The polarization controller 103 adjusts the polarization state of the light L0 guided in the optical fiber 102 by, for example, applying stress from the outside to the looped optical fiber 102.

The light L0 whose polarization state is adjusted by the polarization controller 103 is guided by the optical fiber 104 to the fiber coupler 105 and divided into the measurement light LS and the reference light LR.

The reference optical LR is guided by the optical fiber 110 to the collimator 111, converted into a parallel luminous flux, passed through the optical path length correction member 112 and the dispersion compensation member 113, and is guided to the optical path length changing unit 114. The optical path length correction member 112 acts to match the optical path length of the reference light LR with the optical path length of the measurement light LS. The dispersion compensating member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS.

The optical path length changing unit 114 is movable in the direction of the arrow shown in FIG. 2, and changes the optical path length of the reference light LR. This movement changes the length of the optical path of the reference light LR. This change in the optical path length is used for correcting the optical path length according to the axial length of the eye E to be inspected, adjusting the interference state, and the like. The optical path length changing unit 114 is configured to include, for example, a corner cube and a moving mechanism for moving the corner cube. In this case, the corner cube of the optical path length changing portion 114 turns back the traveling direction of the reference light LR, which is made into a parallel luminous flux by the collimator 111, in the opposite direction. The optical path of the reference light LR incident on the corner cube and the optical path of the reference light LR emitted from the corner cube are parallel.

The reference optical LR that has passed through the optical path length changing unit 114 is converted from a parallel luminous flux to a focused luminous flux by a collimator 116 via a dispersion compensating member 113 and an optical path length correcting member 112, and is incident on the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided by the polarization controller 118 to adjust its polarization state. The polarization controller 118 has, for example, the same configuration as the polarization controller 103. The reference light LR whose polarization state is adjusted by the polarization controller 118 is guided to the attenuator 120 by the optical fiber 119, and the amount of light is adjusted under the control of the arithmetic control unit 200. The reference light LR whose light amount is adjusted by the attenuator 120 is guided to the fiber coupler 122 by the optical fiber 121.

In the configurations shown in FIGS. 1 and 2, the optical path length changing unit 41 for changing the length of the optical path (measurement optical path, measurement arm) of the measurement light LS and the optical path of the reference light LR (reference optical path, reference). Both of the optical path length changing portions 114 for changing the length of the arm) are provided. However, only one of the optical path length changing portions 41 and 114 may be provided. Further, it is also possible to change the difference between the reference optical path length and the measured optical path length by using an optical member other than these.

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber 127 and is converted into a parallel luminous flux by the collimator lens unit 40. The measurement light LS converted into a parallel luminous flux is guided to the dichroic mirror 46 via the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, the mirror 44, and the relay lens 45. The measurement light LS guided to the dichroic mirror 46 is reflected by the dichroic mirror 46, refracted by the objective lens 22, and irradiated to the eye E to be inspected. The measurement light LS is scattered (including reflection) at various depth positions of the eye E to be inspected. The return light of the measurement light LS including such backscattered light travels in the same path as the outward path in the opposite direction, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

The fiber coupler 122 combines (interferes with) the measurement light LS incidented through the optical fiber 128 and the reference light LR incidented via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference light LCs by branching the interference light between the measurement light LS and the reference light LR at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs emitted from the fiber coupler 122 are guided to the detector 125 by the optical fibers 123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode (Balanced Photo Diode) that has a pair of photodetectors that detect each pair of interference light LCs and outputs the difference between the detection results. The detector 125 sends the detection result (interference signal) to the DAQ (Data Acquisition System) 130. A clock KC is supplied to the DAQ 130 from the light source unit 101. The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept (scanned) within a predetermined wavelength range by the wavelength sweep type light source. The light source unit 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then sets the clock KC based on the result of detecting the combined light. Generate. The DATA 130 samples the detection result of the detector 125 based on the clock KC. The DAQ 130 sends the detection result of the sampled detector 125 to the arithmetic control unit 200. The arithmetic control unit 200 obtains a reflection intensity profile in each A line by, for example, performing a Fourier transform or the like on the spectral distribution based on the detection result obtained by the detector 125 for each series of wavelength scans (for each A line). Form. Further, the arithmetic control unit 200 forms image data by imaging the reflection intensity profile of each A line.

[Calculation control unit]
The arithmetic control unit 200 analyzes the detection signal input from the DAQ 130 to form an OCT image or scan data of the fundus Ef (or the anterior segment Ea). The arithmetic processing for that purpose is the same as that of the conventional Swept source type OCT apparatus.

Further, the arithmetic control unit 200 controls each part of the fundus camera unit 2, the display device 3, and the OCT unit 100.

As the control of the fundus camera unit 2, the arithmetic control unit 200 controls the operation of the observation light source 11, the photographing light source 15, and the LEDs 51 and 61, controls the operation of the LCD 39, controls the movement of the photographing focusing lens 31, and the OCT focusing lens 43. It performs movement control, movement control of the reflection rod 67, movement control of the focus optical system 60, movement control of the optical path length changing unit 41, operation control of the optical scanner 42, and the like.

As a control of the display device 3, the arithmetic control unit 200 causes the display device 3 to display the OCT image of the eye E to be inspected.

As the control of the OCT unit 100, the arithmetic control unit 200 controls the operation of the light source unit 101, the movement control of the optical path length changing unit 114, the operation control of the attenuator 120, the operation control of the polarization controllers 103 and 118, and the operation of the detector 125. Control, operation control of DAQ130, etc. are performed.

The arithmetic control unit 200 includes, for example, a processor, RAM, ROM, a hard disk drive, a communication interface, and the like, as in a conventional computer. A computer program for controlling the ophthalmic apparatus 1 is stored in a storage device such as a hard disk drive. The arithmetic control unit 200 may include various circuit boards, for example, circuit boards for forming OCT images. Further, the arithmetic control unit 200 may include an operation device (input device) such as a keyboard and a mouse, and a display device such as an LCD.

The fundus camera unit 2, the display device 3, the OCT unit 100, and the arithmetic control unit 200 may be integrally configured (that is, in a single housing), or may be separately configured in two or more housings. It may have been done.

[Control system]
3 to 5 show a configuration example of the control system of the ophthalmic apparatus 1. In FIGS. 3 to 5, some of the components included in the ophthalmic apparatus 1 are omitted. FIG. 4 shows a block diagram of a configuration example of the main control unit 211 of FIG. FIG. 5 shows a block diagram of a configuration example of the data processing unit 230 of FIG.

(Control unit)
The arithmetic control unit 200 includes a control unit 210. The control unit 210 executes various controls. The control unit 210 includes a main control unit 211 and a storage unit 212.

(Main control unit)
The main control unit 211 includes a processor and controls each unit of the ophthalmic apparatus 1. For example, the main control unit 211 includes focusing drive units 31A and 43A of the fundus camera unit 2, image sensors 35 and 38, LCD 39, an optical path length changing unit 41, an optical scanner 42, and a moving mechanism 150 for moving the optical system. Control. Further, the main control unit 211 controls the light source unit 101 of the OCT unit 100, the optical path length changing unit 114, the attenuator 120, the polarization controllers 103 and 118, the detector 125, the DATA 130, and the like.

For example, the main control unit 211 causes the fixation target to be displayed at a position on the screen of the LCD 39 corresponding to the fixation position set manually or automatically. In addition, the main control unit 211 can change the display position of the fixation target displayed on the LCD 39 (continuously or stepwise). Thereby, the fixation target can be moved (that is, the fixation position can be changed). The display position and movement mode of the fixation target are set manually or automatically. Manual settings are made using, for example, a GUI. The automatic setting is performed by, for example, the data processing unit 230.

The focusing drive unit 31A moves the photographing focusing lens 31 in the optical axis direction of the photographing optical system 30, and moves the focusing optical system 60 in the optical axis direction of the illumination optical system 10. As a result, the focusing position of the photographing optical system 30 is changed. The focusing drive unit 31A may individually have a mechanism for moving the photographing focusing lens 31 and a mechanism for moving the focus optical system 60. The focusing drive unit 31A is controlled when adjusting the focus or the like.

The focusing drive unit 43A moves the OCT focusing lens 43 in the optical axis direction of the measurement optical path. As a result, the focusing position of the measurement light LS is changed. For example, by moving the OCT focusing lens 43 to the first lens position, the focusing position of the measurement light LS can be arranged at or near the fundus Ef. For example, by moving the OCT focusing lens 43 to the second lens position, the focusing position of the measurement light LS can be arranged at a distant point position to make the measurement light LS a parallel luminous flux. The focusing position of the measurement light LS corresponds to the depth position (z position) of the beam waist of the measurement light LS.

The moving mechanism 150 moves at least the fundus camera unit 2 (optical system) three-dimensionally, for example. In a typical example, the moving mechanism 150 includes at least a mechanism for moving the fundus camera unit 2 in the x direction (horizontal direction), a mechanism for moving the fundus camera unit 2 in the y direction (vertical direction), and a z direction (depth direction). , Includes a mechanism for moving in the front-back direction). The mechanism for moving in the x direction includes, for example, an x stage that can move in the x direction and an x moving mechanism that moves the x stage. The mechanism for moving in the y direction includes, for example, a y stage capable of moving in the y direction and a y moving mechanism for moving the y stage. The mechanism for moving in the z direction includes, for example, a z stage capable of moving in the z direction and a z moving mechanism for moving the z stage. Each moving mechanism includes an actuator such as a pulse motor and operates under the control of the main control unit 211.

Control over the moving mechanism 150 is used in alignment and tracking. Tracking is to move the device optical system according to the eye movement of the eye E to be inspected. When tracking is performed, alignment and focus adjustment are performed in advance. Tracking is a function of maintaining a suitable positional relationship in which alignment and focus are achieved by making the position of the optical system of the device follow the movement of the eyeball. In some embodiments, the moving mechanism 150 is controlled to change the optical path length of the reference light (thus, the optical path length difference between the optical path of the measurement light and the optical path of the reference light).

In the case of manual alignment, the user operates the user interface 240 described later so that the displacement of the eye E to be inspected with respect to the optical system is canceled, so that the optical system and the eye E to be inspected are relatively moved. For example, the main control unit 211 controls the moving mechanism 150 by outputting a control signal corresponding to the operation content for the user interface 240 to the moving mechanism 150 to relatively move the optical system and the eye E to be inspected.

In the case of auto-alignment, the main control unit 211 controls the moving mechanism 150 so that the displacement of the eye E to be inspected with respect to the optical system is canceled, so that the optical system and the eye E to be inspected are relatively moved. In some embodiments, the main control unit 211 controls the optical system so that the optical axis of the optical system substantially coincides with the axis of the eye E to be inspected and the distance of the optical system to the eye E to be inspected is a predetermined working distance. Is output to the moving mechanism 150 to control the moving mechanism 150 to move the optical system and the eye E to be inspected relative to each other. Here, the working distance is a default value also called the working distance of the objective lens 22, and corresponds to the distance between the eye E to be inspected and the optical system at the time of measurement using the optical system (at the time of photographing).

As described above, the main control unit 211 according to the embodiment sets the scan center position at an arbitrary position in the scan area, and sets the optical scanner 42 so as to execute the radial scan around the set scan center position. It is possible to control. As shown in FIG. 4, such a main control unit 211 includes a scan area setting unit 211A, a scan center position setting unit 211B, a scan start position setting unit 211C, a scan end position setting unit 211D, and a scan control unit 211E.

The scan area setting unit 211A sets a scan area in which an OCT scan is executed on the fundus Ef (or anterior eye portion Ea) of the eye E to be inspected. The scan area setting unit 211A can set the scan area at an arbitrary position within the OCT measurement range or the OCT imaging range uniquely determined by the optical arrangement of the optical system or the like. The scan area setting unit 211A sets the scan area at a position within the OCT measurement range or the OCT imaging range designated based on the operation content for the user interface 240 (operation unit 240B) described later. In some embodiments, the scan area setting unit 211A sets a scan area corresponding to a representative position of the designated scan area. In some embodiments, when the contour shape of the scan area is circular, the scan area setting unit 211A sets the scan area specified by a designated center position and radius (or diameter). In some embodiments, when the contour shape of the scan area is rectangular, the scan area setting unit 211A sets the scan area specified by the designated diagonal position. In some embodiments, the scan area setting unit 211A sets the scan area identified by the position information input using the user interface 240. In some embodiments, the scan area setting unit 211A sets the scan area at a position where an object corresponding to the scan area is arranged by a drag-and-drop operation.

The contour shape of the scan area is polygonal or circular. In some embodiments, the scan area is an area surrounded by a smooth curve. In some embodiments, the orientation and curvature can be changed at one or more positions of the contour of the scan area.

In some embodiments, the scan area comprises one or more scan prohibited areas. The scan control unit 211E, which will be described later, can perform scanning so as to avoid one or more scan prohibited areas.

The scan center position setting unit 211B sets the scan center position within the scan area set by the scan area setting unit 211A. The scan center position setting unit 211B sets the scan center position at a position within the scan area designated based on the operation content for the user interface 240 (operation unit 240B) described later. In some embodiments, the scan center position setting unit 211B can change the scan center position within the scan area by a drag operation.

The scan start position setting unit 211C sets the scan start position of each of the plurality of line scans executed in the radial scan. The scan end position setting unit 211D sets the scan end position of each of the plurality of line scans executed in the radial scan.

The scan start position setting unit 211C sets the scan start position based on the scan area set by the scan area setting unit 211A and the scan center position set by the scan center position setting unit 211B. For example, the scan start position setting unit 211C finds the position where the scan line passing through the scan center position intersects the boundary of the scan area for each of the plurality of line scans executed in the radial scan, and scans the obtained position. Set as the start position.

Similarly, the scan end position setting unit 211D sets the scan end position based on the scan area set by the scan area setting unit 211A and the scan center position set by the scan center position setting unit 211B. For example, the scan end position setting unit 211D determines the position where the scan line passing through the scan center position intersects the boundary of the scan area in the direction opposite to the scan start position for each of the plurality of line scans executed in the radial scan. Obtained and set the obtained position as the scan end position.

By controlling the optical scanner 42 according to a predetermined scan pattern, the scan control unit 211E can scan the eye E to be inspected in the scan mode specified by the scan pattern. As described above, the scanning modes include horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric circular scanning, and spiral scanning.

Further, the scan control unit 211E sets the optical scanner 42 so as to execute a radial scan centered on the scan center position set by the scan center position setting unit 211B on the scan area set by the scan area setting unit 211A. Control. Each of the plurality of line scans executed in the radial scan passes through the scan center position starting from the scan start position set by the scan start position setting unit 211C, and passes through the scan center position, and the scan end set by the scan end position setting unit 211D. This is a line scan with the position as the end point. For example, the number of multiple line scans performed in a radial scan is predetermined. In some embodiments, the number of line scans can be changed ex post facto. For example, the number of line scans is N (N is a natural number, for example, N is 12), and the scan control unit 211E is rotated by (180 / N × (n-1)) degrees around the scan center position to be the nth (N). 1 ≦ n ≦ N, n is an integer) The optical scanner 42 is controlled so as to sequentially execute the line scan.

Further, the main control unit 211 controls the fundus photography and the anterior eye part imaging by controlling the fundus camera unit 2 and the like. Further, the main control unit 211 controls the OCT measurement by controlling the fundus camera unit 2, the OCT unit 100, and the like. The main control unit 211 can perform a plurality of preliminary operations before performing the OCT measurement. Preliminary operations include alignment, coarse focus adjustment, polarization adjustment, and fine focus adjustment. The plurality of preliminary operations are performed in a predetermined order. In some embodiments, the plurality of preliminary operations are performed in the order described above.

The type and order of preliminary operations are not limited to this, and are arbitrary. For example, a preliminary operation (small pupil determination) for determining whether or not the eye E to be inspected is a small pupil eye can be added to the preliminary operation. The small pupil determination is performed, for example, between the coarse focus adjustment and the optical path length difference adjustment. In some embodiments, the small pupil determination comprises the following series of processes: the process of acquiring a frontal image (anterior segment image) of the eye E to be inspected; the process of identifying an image region corresponding to the pupil; identified. Processing to determine the size (diameter, circumference, etc.) of the pupillary region; processing to determine whether or not the eye is a small pupil based on the determined size (threshold processing); when it is determined to be a small pupil eye, the aperture 19 is set. The process to control. Some embodiments further include a circular or elliptical approximation of the pupil region to determine the pupil size.

The coarse focus adjustment is a focus adjustment using a split index. By determining the position of the photographing focusing lens 31 based on the information relating the eye refractive power acquired in advance and the position of the photographing focusing lens 31 and the measured value of the refraction force of the eye E to be inspected. It is also possible to perform coarse focus adjustment.

The focus fine adjustment is performed based on the interference sensitivity of the OCT measurement. For example, by monitoring the interference intensity (interference sensitivity) of the interference signal acquired by the OCT measurement of the eye E to be inspected, the position of the OCT focusing lens 43 that maximizes the interference intensity is obtained, and the OCT alignment is performed at that position. By moving the focusing lens 43, fine focus adjustment can be performed.

In the optical path length difference adjustment, the predetermined position in the eye E to be inspected is controlled so as to be the reference position of the measurement range in the depth direction. This control is performed on at least one of the optical path length changing units 41 and 114. Thereby, the optical path length difference between the measurement optical path and the reference optical path is adjusted. By setting the reference position by adjusting the optical path length difference, it becomes possible to accurately perform OCT measurement with respect to a desired measurement range in the depth direction only by changing the wavelength sweep speed.

In the polarization adjustment, the polarization state of the reference light LR is adjusted in order to optimize the interference efficiency between the measurement light LS and the reference light LR.

(Memory)
The storage unit 212 stores various types of data. Examples of the data stored in the storage unit 212 include image data of an OCT image, image data of a fundus image, a scan pattern, image data of an anterior segment image, and eye information to be inspected. The eye test information includes information about the subject such as the patient ID and name, and information about the test eye such as left eye / right eye identification information.

In addition, various programs and data for operating the ophthalmic apparatus 1 are stored in the storage unit 212.

(Image forming part)
The image forming unit 220 forms a reflection intensity profile in the A line by performing signal processing such as Fourier transform on the sampling data obtained by sampling the detection signal from the detector 125 with the DAQ 130. The signal processing includes noise removal (noise reduction), filter processing, FFT (Fast Fourier Transform), and the like. The reflection intensity profile on the A line is an example of A scan data. The image forming unit 220 forms a reflection intensity profile for each A line, and arranges the formed plurality of reflection intensity profiles in the B scan direction (intersection direction of the A scan direction) to obtain B scan data (two-dimensional scan). Data) can be formed.

In some embodiments, the image forming unit 220 (or the data processing unit 230 described below) performs a plurality of reflection intensity profiles formed for each A line in the B scan direction (for example, the x direction), the A scan direction, and the A scan direction. Three-dimensional scan data is formed by arranging the data in a direction intersecting the B scan direction (for example, the y direction).

Further, the image forming unit 220 can form an A scan image (OCT image, image data) of the eye E to be inspected by imaging the reflection intensity profile in the A line. The image forming unit 220 can form a B scan image by arranging a plurality of A scan images formed for each A line in the B scan direction (intersection direction of the A scan direction).

In some embodiments, the image forming unit 220 extracts data at a predetermined depth position (scan position) in each A scan data, and extracts a plurality of extracted data in the B scan direction (intersection direction of the A scan direction). ) Is arranged to form C scan data. In some embodiments, the image forming unit 220 extracts pixels at a predetermined depth position (scan position) in each A scan image, and extracts the extracted plurality of pixels in the B scan direction (intersection direction of the A scan direction). ) To form a C-scan image.

In some embodiments, the function of the image forming unit 220 is realized by a processor. In this specification, "image data" and "image" based on the "image data" may be equated.

(Data processing unit)
The data processing unit 230 processes the data acquired by photographing the eye E to be inspected and OCT measurement.

For example, the data processing unit 230 performs various image processing and analysis processing on the image formed by the image forming unit 220. For example, the data processing unit 230 executes various correction processes such as image brightness correction. In addition, the data processing unit 230 performs various image processing and analysis processing on the images (fundus image, anterior ocular segment image, etc.) obtained by the fundus camera unit 2.

The data processing unit 230 executes known image processing such as interpolation processing for interpolating pixels between tomographic images to form image data of a three-dimensional image of the fundus Ef. The image data of the three-dimensional image means the image data in which the positions of the pixels are defined by the three-dimensional coordinate system. As the image data of the three-dimensional image, there is image data composed of voxels arranged three-dimensionally. This image data is called volume data or voxel data. When displaying an image based on volume data, the data processing unit 230 performs rendering processing (volume rendering, MIP (Maximum Industry Projection: maximum value projection), etc.) on the volume data to see from a specific line-of-sight direction. Form the image data of the pseudo three-dimensional image at the time. This pseudo three-dimensional image is displayed on a display device such as the display unit 240A.

It is also possible to form stack data of a plurality of tomographic images as image data of a three-dimensional image. The stack data is image data obtained by three-dimensionally arranging a plurality of tomographic images obtained along a plurality of scan lines based on the positional relationship of the scan lines. That is, the stack data is image data obtained by expressing a plurality of tomographic images originally defined by individual two-dimensional coordinate systems by one three-dimensional coordinate system (that is, embedding them in one three-dimensional space). is there.

The data processing unit 230 performs various renderings on the acquired three-dimensional data set (volume data, stack data, etc.) to create a B-mode image (vertical cross-sectional image, axial cross-sectional image) in an arbitrary cross section, or in an arbitrary cross section. A C-mode image (cross-sectional image, horizontal cross-sectional image), projection image, shadow gram, etc. can be formed. An image of an arbitrary cross section, such as a B-mode image or a C-mode image, is formed by selecting pixels (pixels, voxels) on a designated cross section from a three-dimensional data set. The projection image is formed by projecting a three-dimensional data set in a predetermined direction (z direction, depth direction, axial direction). The shadow gram is formed by projecting a part of a three-dimensional data set (for example, partial data corresponding to a specific layer) in a predetermined direction. An image with the front side of the eye to be inspected as a viewpoint, such as a C-mode image, a projection image, and a shadow gram, is called a front image (en-face image).

The data processing unit 230 uses a B-mode image or a frontal image (blood vessel-enhanced image, angiogram) in which retinal blood vessels and choroidal blood vessels are emphasized based on data (for example, B-scan image data) collected in time series by OCT. Can be built. For example, time-series OCT data can be collected by repeatedly scanning substantially the same site of the eye E to be inspected.

In some embodiments, the data processing unit 230 compares time-series B-scan images obtained by B-scanning on substantially the same part, and sets the pixel value of the signal strength change portion to the pixel value corresponding to the change. By converting, a emphasized image in which the changed part is emphasized is constructed. Further, the data processing unit 230 forms an OCTA image by extracting information having a predetermined thickness at a desired portion from the constructed plurality of emphasized images and constructing it as an en-face image.

Images generated by the data processing unit 230 (eg, three-dimensional images, B-mode images, C-mode images, projection images, shadowgrams, OCTA images) are also included in the OCT images.

Further, the data processing unit 230 includes an analysis unit 231, an image alignment unit 232, and an image composition unit 233. The analysis unit 231 includes a feature region identification unit 231A.

(Analysis department)
The analysis unit 231 performs a predetermined analysis process on the detection result of the interference light obtained by the OCT measurement, the OCT image formed by the image forming unit 220, or the processing result by the data processing unit 230.

For example, the analysis unit 231 analyzes the detection result of the interference light obtained by the OCT measurement and determines the focus state of the measurement light LS in the focus fine adjustment control. For example, the main control unit 211 performs repetitive OCT measurement while controlling the focusing drive unit 43A according to a predetermined algorithm. The analysis unit 231 calculates a predetermined evaluation value regarding the image quality of the OCT image by analyzing the detection result of the interference light LC repeatedly acquired by the OCT measurement. The analysis unit 231 determines whether or not the calculated evaluation value is equal to or less than the threshold value. In some embodiments, the focus fine-tuning is continued until the calculated evaluation value is below the threshold. That is, when the evaluation value is equal to or less than the threshold value, it is determined that the focus state of the measurement light LS is appropriate, and the focus fine adjustment is continued until it is determined that the focus state of the measurement light LS is appropriate.

In some embodiments, the main control unit 211 monitors the strength (interference intensity, interference sensitivity) of the interference signals that are sequentially acquired while performing the repetitive OCT measurement as described above to acquire the interference signal. To do. Further, by moving the OCT focusing lens 43 while performing this monitoring process, the position of the OCT focusing lens 43 that maximizes the interference intensity is searched for. By such fine adjustment of the focus, the OCT focusing lens 43 can be guided to a position where the interference intensity is optimized.

Further, the analysis unit 231 analyzes the detection result of the interference light obtained by the OCT measurement, and determines the polarization state of at least one of the measurement light LS and the reference light LR. For example, the main control unit 211 performs repetitive OCT measurement while controlling at least one of the polarization controllers 103 and 118 according to a predetermined algorithm. In some embodiments, the main control unit 211 controls the attenuator 120 to change the amount of attenuation of the reference light LR. The analysis unit 231 calculates a predetermined evaluation value regarding the image quality of the OCT image by analyzing the detection result of the interference light LC repeatedly acquired by the OCT measurement. The analysis unit 231 determines whether or not the calculated evaluation value is equal to or less than the threshold value. This threshold is preset. The polarization adjustment is continued until the calculated evaluation value becomes equal to or less than the threshold value. That is, when the evaluation value is equal to or less than the threshold value, it is determined that the polarization state of the measurement light LS is appropriate, and the polarization adjustment is continued until it is determined that the polarization state of the measurement light LS is appropriate.

In some embodiments, the main control unit 211 can also monitor the interference strength in polarization adjustment.

In the analysis process by the analysis unit 231, the predetermined site (tissue, lesion) in the eye E to be inspected is specified; the distance between the designated sites (interlayer distance), the area, the angle, the ratio, and the density are calculated; Calculation by a calculation formula; identification of the shape of a predetermined part; calculation of these statistical values; calculation of measured values and distribution of statistical values; image processing based on these analysis processing results, etc. Predetermined tissues include blood vessels, optic discs, fovea centralis, macula and the like. Predetermined lesions include vitiligo, bleeding, and the like.

(Characteristic area identification part)
The feature region identification unit 231A is a front image of the eye E to be inspected obtained by the photographing optical system 30 (for example, a front image of the fundus of the eye, a front image of the anterior eye portion), a tomographic image of the eye E to be inspected formed by the image forming unit 220, Alternatively, the characteristic region of the eye E to be inspected is specified based on the front image (C mode image, projection image, or shadow gram) obtained by the data processing unit 230. Characteristic regions include the fovea centralis, macula, optic disc, lesions, and blood vessels in the fundus Ef.

For example, when the fovea centralis is specified as the feature region, the feature region identification portion 231A identifies the region corresponding to the macula of the eye E to be inspected based on the detection result of the interference light LC or the tomographic image of the eye E to be inspected. In some embodiments, the feature region specifying portion 231A identifies a region corresponding to the macula of the eye E to be inspected by identifying the morphology of the fundus Ef. For example, the feature region identification unit 231A is a region corresponding to the macula by analyzing the cross-sectional shape of the retina and the thickness of the retina from the tomographic image (B scan image) of the eye E to be inspected formed by the image forming unit 220. Can be identified. Further, the feature region specifying portion 231A can specify a region corresponding to the macula portion of the eye to be inspected E in the three-dimensional image based on the three-dimensional image of the eye to be inspected E. The feature region specifying portion 231A can identify the recessed portion of the identified macula as the fovea centralis.

In some embodiments, the feature region identifying portion 231A identifies a region corresponding to the macula based on a frontal image of the fundus Ef and identifies the central portion of the identified region as the region corresponding to the fovea centralis. The feature area specifying unit 231A can specify a region corresponding to the macula of a pixel group having a brightness equal to or less than a predetermined threshold value in the front image. Further, the feature region specifying portion 231A can specify a region corresponding to the macula in the front image with reference to the position of the optic nerve head identified in the front image.

For example, when the optic nerve head is specified as the feature region, the feature region specifying portion 231A specifies the contour portion of the optic nerve papilla based on the luminance information such as a projection image, and determines the center position (center of gravity position) of the specified contour portion. It can be specified as the papilla position. In some embodiments, the contour is identified by utilizing the circular (elliptical) shape of the contour of the teat. In some embodiments, the contour is identified by analyzing the shape of the tomographic image of the fundus Ef. In some embodiments, the process of identifying the contour of the optic nerve head is performed within the search region identified based on the distribution (running state) of blood vessels having a predetermined diameter or larger in the fundus Ef.

(Image alignment part)
The image alignment unit 232 aligns two or more tomographic images formed by the image forming unit 220. In some embodiments, the image alignment unit 232 identifies the feature areas depicted in each of the two or more tomographic images, and the amount of alignment of the two or more tomographic images so that the identified feature areas overlap. (Shift direction, shift amount) is calculated. Characteristic parts include predetermined layer areas, lesion parts, blood vessels, and the like. In some embodiments, the image alignment unit 232 obtains the correlation value of the superposed portion of two or more tomographic images while changing the alignment amount, and two or more so that the obtained correlation value is maximized. Obtain the amount of alignment of the tomographic image. The image alignment unit 232 can also perform two or more image alignments generated by data processing by the data processing unit 230 in the same manner.

(Image composition section)
The image synthesizing unit 233 synthesizes two or more tomographic images formed by the image forming unit 220 based on the alignment amount obtained by the image arranging unit 232. Further, the image synthesizing unit 233 can perform two or more image alignments generated by data processing by the data processing unit 230 based on the alignment amount obtained by the image alignment unit 232.

The data processing unit 230 that functions as described above includes, for example, the above-mentioned processor, RAM, ROM, hard disk drive, circuit board, and the like. A computer program that causes the processor to execute the above functions is stored in a storage device such as a hard disk drive in advance.

(User interface)
The user interface 240 includes a display unit 240A and an operation unit 240B. The display unit 240A includes the display device and the display device 3 of the arithmetic control unit 200 described above. The operation unit 240B includes the operation device of the arithmetic control unit 200 described above. The operation unit 240B may include various buttons and keys provided on the housing of the ophthalmic apparatus 1 or on the outside. For example, when the fundus camera unit 2 has a housing similar to that of a conventional fundus camera, the operation unit 240B may include a joystick, an operation panel, and the like provided on the housing. Further, the display unit 240A may include various display devices such as a touch panel provided on the housing of the fundus camera unit 2.

The display unit 240A and the operation unit 240B do not need to be configured as separate devices. For example, it is possible to use a device such as a touch panel in which a display function and an operation function are integrated. In that case, the operation unit 240B includes the touch panel and a computer program. The operation content for the operation unit 240B is input to the control unit 210 as an electric signal. Further, the graphical user interface (GUI) displayed on the display unit 240A and the operation unit 240B may be used to perform operations and information input.

Next, an outline of the operation of the embodiment will be described mainly by comparing with the comparative example of the embodiment.

<Scan center position>
As described above, the control unit 210 (scan center position setting unit 211B) can set an arbitrary position in the scan area as the scan center position of the radial scan. The scan control unit 211E controls the optical scanner 42 so as to execute the radial scan around the set scan center position.

FIG. 6A shows an explanatory diagram of the process executed by the ophthalmic apparatus according to the comparative example of the embodiment. FIG. 6B shows an explanatory diagram of the process executed by the ophthalmic apparatus 1 according to the embodiment. 6A and 6B schematically show the processing when performing a radial scan on the fundus Ef of the eye E to be inspected.

In the comparative example of the embodiment, as shown in FIG. 6A, the radial scan is executed with the center of the scan area SA0 as the scan center position C0. That is, the line scans SC01, SC02, SC03, ... Are sequentially executed with the scan center position C0 as the center. For example, when performing OCT measurement with the optic nerve head as a region of interest, it is necessary to eccentric the eyes of the subject, and OCT measurement of the region of interest cannot be performed efficiently.

On the other hand, in the embodiment, as shown in FIG. 6B, an arbitrary position of the scan area SA1 can be set as the scan center position. For example, by setting the scan center position C1 at the optic nerve head, which is the site of interest, line scans SC1, SC2, SC3, ... Are sequentially executed around the scan center position C1. Therefore, when the OCT measurement is performed with the optic nerve head as the region of interest, the OCT measurement of the region of interest can be efficiently performed without eccentricity of the eyes of the subject. This makes it possible to efficiently perform OCT measurement of the region of interest regardless of the position of the region of interest. In particular, it is useful when performing OCT measurement with the eyes of the subject eccentric, or when performing OCT measurement centered on an arbitrary position.

<Two or more scan center positions in the same scan area>
The control unit 210 (scan control unit 211E) can control the optical scanner 42 so as to sequentially execute radial scans centered on two or more scan center positions in the same scan area.

FIG. 7 shows an explanatory diagram of the process executed by the ophthalmic apparatus 1 according to the embodiment. FIG. 7 schematically shows an explanatory diagram when a radial scan is executed centering on two scan center positions C2 and C3 in the same scan area. FIG. 7 schematically shows a process when performing a radial scan on the fundus Ef of the eye E to be inspected.

The scan area setting unit 211A sets the scan area SA0. The scan center position setting unit 211B sets, for example, the center of the scan area SA0 as the scan center position C2. The scan start position setting unit 211C and the scan end position setting unit 211D set the scan start position and the scan end position of a plurality of line scans executed in the radial scan. The scan control unit 211E executes the first radial scan (line scans SC21, SC22, SC23, ...) Centering on the scan center position C2.

Next, with the scan region SA0 fixed, the scan center position setting unit 211B sets, for example, the optic disc identified by the feature region identification unit 231A as the scan center position C3. The scan start position setting unit 211C and the scan end position setting unit 211D set the scan start position and the scan end position of a plurality of line scans executed in the radial scan. The scan control unit 211E executes a second radial scan (line scan SC31, SC32, SC33, ...) Centering on the scan center position C3.

In some embodiments, scan center positions are set for each of the two or more sites of interest within the scan area SA0, and radial scans are performed sequentially. In some embodiments, scan center positions are set in each of the two or more sites of interest (eg, bifurcations) according to the traveling state of blood vessels in the scan region SA0, and radial scans are sequentially performed.

By executing two or more radial scans centered on two or more scan center positions in the same scan area in this way, it is possible to grasp the morphology in the area in detail without changing the scan area. become.

<Scan area>
In the embodiment, the scan start position and the scan end position are set based on the scan center position and the scan area for each of the plurality of line scans executed in the radial scan. Thereby, the contour shape of the scan area can be made into an arbitrary shape.

8A and 8B schematically show an example of a scan region according to the embodiment. 8A and 8B schematically show the processing when performing a radial scan on the fundus Ef of the eye E to be inspected.

For example, as shown in FIG. 8A, the scan area setting unit 211A sets the scan area SA4 having an arbitrary contour shape. The scan center position setting unit 211B sets the position of the optic nerve head in the scan area SA4 as the scan center position C4. The scan start position setting unit 211C and the scan end position setting unit 211D set the scan start position and the scan end position of a plurality of line scans executed in the radial scan. The scan control unit 211E executes a radial scan (line scans SC41, SC42, SC43, ...) Centering on the scan center position C4.

For example, the scan area setting unit 211A sets the scan area SA5 having a rectangular contour shape, as shown in FIG. 8B. The scan center position setting unit 211B sets the position of the optic nerve head in the scan area SA5 as the scan center position C5. The scan start position setting unit 211C and the scan end position setting unit 211D set the scan start position and the scan end position of a plurality of line scans executed in the radial scan. The scan control unit 211E executes a radial scan (line scans SC51, SC52, SC53, ...) Centering on the scan center position C5.

By setting the contour shape of the scan region to a desired shape in this way, the shape of the desired region can be grasped in detail.

<Wide-angle image>
The ophthalmic apparatus 1 according to the embodiment can acquire a wide-angle image of the eye E to be inspected. In the embodiment, the image alignment unit 232 obtains the alignment amount of a plurality of images obtained by scanning a plurality of scan areas, and the image synthesis unit 233 obtains a plurality of alignment amounts based on the obtained alignment amount. It is possible to combine images to generate a wide-angle image.

FIG. 9 shows an explanatory diagram of the process executed by the ophthalmic apparatus according to the comparative example of the embodiment. FIG. 10 shows an explanatory diagram of the process executed by the ophthalmic apparatus 1 according to the embodiment. 9 and 10 schematically show a process in which a wide-angle image is acquired by performing a radial scan on the fundus Ef of the eye E to be inspected.

In the comparative example of the embodiment, in order to acquire a wide-angle image, a radial scan is performed for each of the scan center positions C01 to C03 as shown in FIG. That is, as the first OCT measurement (center portion), a radial scan is executed with the center of the scan area SA01 as the scan center position C01. Subsequently, as the second OCT measurement (upward of the peripheral portion), a radial scan is executed with the center of the scan area SA02 as the scan center position C02. Further, as the third OCT measurement (peripheral nasal side), a radial scan is executed with the center of the scan area SA03 as the scan center position C03. Tomographic images are obtained in each of the scan areas SA01, SA02, and SA03.

When the tomographic images obtained in each of the scan areas SA01, SA02, and SA03 are combined in order to generate a wide-angle image, the scan positions (scan lines) do not match as shown in FIG. That is, in order to synthesize the tomographic images obtained in each of the scan areas SA01, SA02, and SA03, image processing due to the mismatch of the scan positions and the like is required, and the tomographic image synthesis processing becomes very complicated.

On the other hand, in the embodiment, as shown in FIG. 10, a radial scan is executed for each of the scan center positions C11 to C13, as in the above comparative example. That is, as the first OCT measurement, a radial scan is executed with the center of the scan area SA11 as the scan center position C11. Subsequently, as the second OCT measurement, a radial scan is executed with the center of the scan area SA12 as the scan center position C12. Further, as the third OCT measurement, a radial scan is executed with the center of the scan area SA13 as the scan center position C13. Tomographic images are obtained in each of the scan areas SA11, SA12, and SA13.

When synthesizing the tomographic images obtained in each of the scan areas SA11, SA12, and SA13 in order to generate a wide-angle image, the scan positions (scan lines) can be matched as shown in FIG. Therefore, it becomes possible to easily synthesize the tomographic images obtained in each of the scan regions SA11, SA12, and SA13 centering on the region of interest, and the morphology of the region of interest can be grasped at a wide angle.

It should be noted that it may not be possible to synthesize the tomographic images obtained by the radial scan of the two scan regions with high accuracy due to the deviation of the scan position (scan line), the inclination of the tomographic image due to the alignment error, and the like. In this case, it is possible to perform alignment using overlapping portions of tomographic images of substantially the same site obtained by radial scans of different scan regions, and to synthesize two tomographic images.

11A to 11C show explanatory views of the processing executed by the ophthalmic apparatus 1 according to the embodiment. 11A to 11C show explanatory views of the tomographic image synthesis process obtained by the radial scan in the scan areas SA12 and SA13.

In the embodiment, as described above, the radial scan can be executed for each of the scan areas SA12 and SA13 with the scan center position fixed. For example, substantially the same portion is visualized in the tomographic image IMG11 obtained by scanning the scan area SA12 and the tomographic image IMG13 obtained by scanning the scan area SA13. The image alignment unit 232 obtains the alignment amount using the overlapping portions of the tomographic images IMG 11 and IMG 13. The image synthesizing unit 233 superimposes the overlapping portions of the tomographic images IMG11 and IMG13 using the obtained alignment amount to generate a wide-angle composite image IMG20 as shown in FIG. 11B.

In some embodiments, the image synthesizing unit 233 generates a composite image IMG 20 so that one of the tomographic images IMG 11 and IMG 13 is drawn in the overlapping portion of the tomographic images IMG 11 and IMG 13.

In some embodiments, the image synthesizing unit 233 generates a composite image IMG20 of the tomographic images IMG11 and IMG13 so that the display area of the tomographic image IMG11 and the display area of the tomographic image IMG13 in the overlapping portion can be changed. For example, the control unit 210 causes the display unit 240A to display the composite image IMG 20 as a display control unit. At this time, as shown in FIG. 11C, the control unit 210 sets the operation object SLD for changing the display area of the tomographic image IMG11 and the display area of the tomographic image IMG13 in the overlapping portion of the composite image IMG20 around the composite image IMG20. Display in the area. The operation object SLD can be moved in the horizontal direction of the overlapping portion, for example, by operating the operation unit 240B. The image composition unit 233 generates the composite image IMG 20 by changing the display area of the tomographic image IMG 11 and the display area of the tomographic image IMG 13 in the overlapping portion according to the position of the operation object SLD. As a result, the user can grasp in detail the morphology of the fundus Ef depicted in the desired tomographic image.

Further, in the embodiment, since the scan length varies depending on the line scan performed in the radial scan, the size of the image acquired with the same shooting resolution varies. Therefore, in the embodiment, a plurality of tomographic images obtained by a plurality of line scans can be switched and displayed based on the position of the characteristic region of the eye E to be inspected.

FIG. 12 shows an explanatory diagram of the process executed by the ophthalmic apparatus 1 according to the embodiment. FIG. 12 shows an explanatory diagram of display control of a plurality of tomographic images obtained by a radial scan.

For example, it is assumed that a radial scan (line scan SC61, SC62, SC63, SC64, ..., SC70) is performed with the optic disc as a characteristic region and the scan center position is set. The tomographic images IMG61, IMG62, ..., IMG70 are formed by each of the line scans SC61, SC62, SC63, SC64, ..., SC70.

The control unit 210 switches any of the tomographic images IMG61, IMG62, ..., IMG70 and displays them on the display unit 240A so that the positions of the optic nerve heads drawn on each tomographic image match. For example, the control unit 210 causes the display unit 240A to display a tomographic image selected based on the operation content for the operation unit 240B among the tomographic images IMG61, IMG62, ..., IMG70. As a result, the user can easily observe changes in the morphology and the like centering on the feature region in the plurality of tomographic images obtained by the radial scan.

The optical system in the path from the interference optical system to the objective lens 22 included in the OCT unit 100 is an example of the “optical system” according to the embodiment. The photographing optical system 30 is an example of the “acquisition unit” according to the embodiment. The scan start position setting unit 211C is an example of the "first setting unit" according to the embodiment. The scan end position setting unit 211D is an example of the "second setting unit" according to the embodiment. The image alignment unit 232 is an example of the “alignment unit” according to the embodiment. The image compositing unit 233 is an example of the "compositing unit" according to the embodiment.

[motion]
The operation of the ophthalmic apparatus 1 according to the embodiment will be described.

FIG. 13 shows an operation example of the ophthalmic apparatus 1 according to the embodiment. FIG. 13 shows a flowchart of an operation example of the ophthalmic apparatus 1 according to the embodiment. A computer program for realizing the process shown in FIG. 13 is stored in the storage unit 212. The main control unit 211 executes the process shown in FIG. 13 by operating according to this computer program.

(S1: Alignment)
The main control unit 211 executes alignment.

That is, the main control unit 211 controls the alignment optical system 50 to project the alignment index on the eye E to be inspected. At this time, the fixation target by the LCD 39 is also projected on the eye E to be inspected. The main control unit 211 controls the moving mechanism 150 based on the moving amount of the optical system specified based on, for example, the light receiving image acquired by the image sensor 35, and moves the optical system with respect to the eye E to be inspected by the moving amount. Move relatively. The main control unit 211 repeatedly executes this process.

In some embodiments, after the alignment in step S1 is completed, the above-mentioned coarse alignment adjustment and fine alignment adjustment are performed.

(S2: Get front image)
Subsequently, the main control unit 211 acquires a front image of the eye E to be inspected by controlling the photographing optical system 30.

That is, the main control unit 211 acquires a front image of the fundus Ef acquired by, for example, the image sensor 35. As described above, the main control unit 211 may control the OCT unit 100 to acquire an en-face image of the fundus Ef as a frontal image.

(S3: Obtain a tomographic image for adjustment)
The main control unit 211 displays a fixation target for OCT measurement at a predetermined position on the LCD 39. The main control unit 211 can display the fixation target at the display position of the LCD 39 corresponding to the position of the optical axis of the optical system on the fundus Ef.

Subsequently, the main control unit 211 controls the OCT unit 100 to execute the OCT provisional measurement, and acquires an adjustment tomographic image for adjusting the reference position of the measurement range in the depth direction. Specifically, the main control unit 211 deflects the measurement light LS generated based on the light L0 emitted from the light source unit 101 by controlling the optical scanner 42, and is covered with the deflected measurement light LS. A predetermined site (for example, fundus) of optometry E is scanned. The detection result of the interference light obtained by scanning the measurement light LS is sampled in synchronization with the clock KC and then sent to the image forming unit 220. The image forming unit 220 forms a tomographic image (OCT image) of the eye E to be inspected from the obtained interference signal.

(S4: Adjust the reference position in the depth direction)
Subsequently, the main control unit 211 adjusts the reference position of the measurement range in the depth direction (z direction).

For example, the main control unit 211 causes the data processing unit 230 to specify a predetermined part (for example, sclera) in the tomographic image obtained in step S3, and makes the data processing unit 230 specify the predetermined part in the depth direction with respect to the position of the specified predetermined part. A position separated by a predetermined distance is set as a reference position of the measurement range. The main control unit 211 controls at least one of the optical path length changing units 41 and 114 according to the reference position. Further, a predetermined position determined in advance so that the optical path lengths of the measurement light LS and the reference light LR substantially match may be set as the reference position of the measurement range.

(S5: Focus adjustment, polarization adjustment)
Next, the main control unit 211 executes focus adjustment control and polarization adjustment control.

For example, the main control unit 211 controls the focusing drive unit 43A to move the OCT focusing lens 43 by a predetermined distance, and then controls the OCT unit 100 to execute the OCT measurement. As described above, the main control unit 211 causes the data processing unit 230 to determine the focus state of the measurement light LS based on the detection result of the interference light obtained by the OCT measurement. When it is determined that the focus state of the measurement light LS is not appropriate based on the determination result by the data processing unit 230, the main control unit 211 controls the focusing drive unit 43A again, and determines that the focus state is appropriate. Repeat until determined.

Further, for example, the main control unit 211 controls at least one of the polarization controllers 103 and 118 to change the polarization state of at least one of the light L0 and the measurement light LS by a predetermined amount, and then controls the OCT unit 100. Then, the OCT measurement is executed, and the image forming unit 220 is formed with an OCT image based on the detection result of the acquired interference light. As described above, the main control unit 211 causes the data processing unit 230 to determine the image quality of the OCT image obtained by the OCT measurement. When it is determined that the polarization state of the measurement light LS is not appropriate based on the determination result by the data processing unit 230, the main control unit 211 controls the polarization controllers 103 and 118 again, and the polarization state is appropriate. Repeat until it is determined to be.

(S6: Specify the feature area)
Subsequently, the main control unit 211 analyzes the frontal image of the fundus Ef acquired in step S2 by controlling the feature region specifying unit 231A to specify the feature region in the fundus Ef. It is sufficient that step S6 is executed between step S2 and step 5.

(S7: Set the scan area)
Next, the main control unit 211 causes the scan area setting unit 211A to set the scan area for the fundus Ef as described above.

(S8: Set the scan center position)
Subsequently, the main control unit 211 causes the scan center position setting unit 211B to set the position in the feature area specified in step S6 as the scan center position in the scan area set in step S7.

(S9: Determine the scan start position, determine the scan end position)
The main control unit 211 sets the scan start position of each of the plurality of line scans executed in the radial scan based on the scan area set in step S7 and the scan center position set in step S8. Let the setting unit 211C set.

Similarly, the main control unit 211 determines the scan end position of each of the plurality of line scans executed in the radial scan based on the scan area set in step S7 and the scan center position set in step S8. The scan end position setting unit 211D is set.

(S10: Radial scan)
The main control unit 211 controls the optical scanner 42 in the scan control unit 211E so as to execute the radial scan centered on the scan center position set in step S8 with respect to the scan area set in step S7. In the radial scan, a plurality of line scans are executed according to the scan start position and the scan end position determined in step S9.

The detection result of the interference light acquired by each line scan is sampled in the DAQ 130 and stored as an interference signal in the storage unit 212 or the like.

(S11: Next scan area?)
The main control unit 211 determines whether or not to execute a radial scan for the next scan area. The main control unit 211 can determine whether or not to execute a radial scan for the next scan area based on the operation mode (measurement mode, scan mode) specified in advance or the operation content for the operation unit 240B.

When it is determined to execute the radial scan for the next scan area (S11: Y), the operation of the ophthalmic apparatus 1 shifts to step S7. When it is determined not to execute the radial scan for the next scan area (S11: N), the operation of the ophthalmic apparatus 1 shifts to step S12.

In some embodiments, the above alignment is performed when transitioning from step S11 to step S7.

(S12: Form a tomographic image)
When it is determined in step S11 that the radial scan is not executed for the next scan area (S11: N), the main control unit 211 receives the A scan image data of the eye E to be inspected based on the interference signal acquired in step S10. The data set group is formed in the image forming unit 220. The image forming unit 220 forms a tomographic image by arranging the formed A scan images in the B scan direction. The main control unit 211 similarly forms a tomographic image for a plurality of line scans.

(S13: Alignment)
Next, the main control unit 211 causes the image alignment unit 232 to calculate the alignment amount of the two tomographic images in which substantially the same portion is drawn among the plurality of tomographic images formed in step S12.

(S14: Synthesis)
The main control unit 211 synthesizes the above two tomographic images based on the alignment amount calculated in step S13 to generate a composite image as shown in FIG. 11B or FIG. 11C. The main control unit 211 causes the display unit 240A to display the composite image generated in step S14.

In some embodiments, the main control unit 211 aligns the positions of the feature regions drawn on each of the plurality of tomographic images formed in step S12, and selectively displays the plurality of tomographic images on the display unit 240A. Display it.

This completes the operation of the ophthalmic apparatus 1 (end).

In the above embodiment, the case where the first scan direction from the scan start position to the scan center position and the second scan direction from the scan center position to the scan end position are the same has been described, but the configuration according to the embodiment is described. Not limited to this. For example, the first scan direction may be opposite to the second scan direction.

In the above embodiment, the case where a plurality of linear line scans are executed in the radial scan has been described, but the configuration according to the embodiment is not limited to this. In some embodiments, at least one of the plurality of scans performed in the radial scan includes a scan that draws a curved trajectory in the B scan direction.

In some embodiments, a program is provided for causing a computer to perform the control method of the ophthalmic apparatus described above. Such a program can be stored in any computer-readable recording medium. Examples of the recording medium include semiconductor memory, optical disk, magneto-optical disk (CD-ROM / DVD-RAM / DVD-ROM / MO, etc.), magnetic storage medium (hard disk / floppy (registered trademark) disk / ZIP, etc.), and the like. Can be used. It is also possible to send and receive this program through a network such as the Internet or LAN.

[effect]
The ophthalmic apparatus according to the embodiment and the control method thereof will be described.

The ophthalmic apparatus (1) according to some embodiments includes an optical system (an optical system in the path from the interference optical system included in the OCT unit 100 to the objective lens 22) and a control unit (210, main control unit 211). including. The optical system includes an optical scanner (42), scans a predetermined scan area by deflecting the light (measurement light LS) from the light source (light source unit 101) with the optical scanner, and obtains the data of the eye (E) to be inspected. collect. The control unit controls the optical scanner so as to execute a plurality of scans radially around a scan center position different from the center of the scan area.

According to such a configuration, by controlling the optical scanner according to the position of the region of interest of the eye to be inspected, the region of interest is set as the scan center position, and a plurality of radial parts centered on the set scan center position. You can scan. As a result, it becomes possible to collect data of the site of interest more efficiently than before.

In the ophthalmic apparatus according to some embodiments, the scan center position is variable.

According to such a configuration, a desired position can be set as a scan center position, and a plurality of radial scans centered on the desired position can be performed. As a result, it becomes possible to efficiently and easily collect data at a desired position.

The ophthalmic apparatus according to some embodiments includes an operation unit (240B), and the control unit sets the scan center position based on the operation content for the operation unit.

According to such a configuration, the user can easily collect data at a desired position by performing an operation on the operation unit.

The ophthalmic apparatus according to some embodiments is an analysis that identifies a characteristic region of the eye to be inspected by analyzing an acquisition unit (photographing optical system 30) that acquires an image of the eye to be inspected and an image acquired by the acquisition unit. The control unit sets the position in the feature region specified by the analysis unit as the scan center position, including the unit (231).

According to such a configuration, the feature region of the eye to be inspected can be set as the scan center position, and a plurality of radial scans centered on the position in the feature region can be performed. As a result, it becomes possible to efficiently and easily collect the data of the feature region.

The ophthalmic apparatus according to some embodiments includes a first setting unit (scan start position setting unit 211C) that sets a scan start position based on a scan area and a scan center position for each of a plurality of scans, and a plurality of scan start positions. For each scan, the control unit includes a second setting unit (scan end position setting unit 211D) that sets the scan end position based on the scan area and the scan center position, and the control unit sets the scan end position for each of the plurality of scans. The optical scanner is controlled based on the scan start position set by the 1 setting unit and the scan end position set by the second setting unit.

According to such a configuration, since the scan start position and the scan end position are obtained for a plurality of scans to be executed radially, it is possible to easily execute a plurality of scans radially in any mode. become.

In an ophthalmic apparatus according to some embodiments, the control unit controls the optical scanner to perform a plurality of scans centered on each of two or more scan center positions within the same scan area.

According to such a configuration, it becomes possible to execute a plurality of radial scans of two or more in the same scan area, and it is possible to efficiently grasp the morphology of the region of interest in the fundus of the eye to be inspected. Will be able to.

In the ophthalmic apparatus according to some embodiments, the optical system divides the light (L0) from the light source (light source unit 101) into measurement light (LS) and reference light (LR) and deflects them by an optical scanner. The interference optical system that projects the measurement light onto the eye to be inspected and detects the interference light (LC) between the return light of the measurement light from the eye to be inspected and the reference light is included in the detection result of the interference light obtained by the interference optical system. Includes an image forming section (220) that forms a tomographic image of the eye to be examined based on it.

With such a configuration, it is possible to obtain a tomographic image capable of efficiently grasping the morphology of the region of interest in the fundus of the eye to be inspected.

The ophthalmic apparatus according to some embodiments aligns a plurality of tomographic images obtained by an image forming unit by performing a plurality of scans so that the positions of the plurality of scan centers in the plurality of scans are substantially the same. It includes an alignment unit (image alignment unit 232) and a composition unit (image composition unit 233) that synthesizes a plurality of tomographic images aligned by the alignment unit.

According to such a configuration, a plurality of tomographic images are combined by aligning the scan center positions so as to be substantially the same, so that a wide-angle tomographic image can be easily obtained from the scan results executed radially. It becomes possible to do.

In the ophthalmic apparatus according to some embodiments, the control unit controls the optical scanner so that the scan center position and the scan direction of at least one of the plurality of scans substantially coincide with each other. Have multiple scans performed on the area.

According to such a configuration, a plurality of scans are executed for a plurality of scan areas different from each other so that the scan center position and at least one scan direction of the plurality of scans substantially coincide with each other, which is simple. The process makes it possible to easily obtain wide-angle tomographic images from the results of radial scans.

In the ophthalmic apparatus according to some embodiments, the control unit switches and displays a plurality of tomographic images obtained by the image forming unit so that the feature positions (feature area, scan center position) in each scan are substantially the same. It is displayed on the means (display unit 240A).

With such a configuration, it becomes easy to observe changes in morphology and the like of a plurality of tomographic images obtained by a plurality of radial scans with reference to a feature region.

The control method of the ophthalmic apparatus (1) according to some embodiments is a control method of the ophthalmic apparatus for collecting data of the eye to be inspected (E). The control method of the ophthalmic apparatus includes a setting step of setting a scan center position different from the center of a predetermined scan area, and deflecting the light (measurement light LS) from the light source (light source unit 101) with an optical scanner to determine the scan center position. Includes a control step that controls the optical scanner to perform multiple scans radially in the center.

According to such a method, by controlling the optical scanner according to the position of the region of interest of the eye to be inspected, the region of interest is set as the scan center position, and a plurality of radial parts centered on the set scan center position. You can scan. As a result, it becomes possible to collect data of the site of interest more efficiently than before.

In the method of controlling the ophthalmic apparatus according to some embodiments, the setting step sets the scan center position based on the operation content for the operation unit (240B).

According to such a method, the user can easily collect data at a desired position by performing an operation on the operation unit.

The control method of the ophthalmic apparatus according to some embodiments includes an acquisition step of acquiring an image of the eye to be inspected, an analysis step of identifying a characteristic region of the eye to be inspected by analyzing the image acquired in the acquisition step, and an analysis step. The setting step sets the position in the feature region specified in the analysis step as the scan center position.

According to such a method, the characteristic area of the eye to be inspected can be set as the scan center position, and a plurality of radial scans centered on the position in the characteristic area can be performed. As a result, it becomes possible to efficiently and easily collect the data of the feature region.

In the method of controlling an ophthalmic apparatus according to some embodiments, the control step controls the optical scanner to perform a plurality of scans around each of two or more scan center positions within the same scan area.

According to such a method, it is possible to execute a plurality of radial scans of two or more in the same scan area, and it is possible to efficiently grasp the morphology of the region of interest in the fundus of the eye to be inspected. Will be able to.

A method of controlling an ophthalmic apparatus according to some embodiments comprises an image forming step of forming a tomographic image of the eye to be inspected by performing optical coherence tomography using light from a light source.

According to such a method, it is possible to obtain a tomographic image capable of efficiently grasping the morphology of the region of interest in the fundus of the eye to be inspected.

A method of controlling an ophthalmic apparatus according to some embodiments is a method of controlling a plurality of tomographic images obtained in an image formation step by performing a plurality of scans so that the positions of the plurality of scan centers in the plurality of scans are substantially the same. It includes an alignment step for aligning and a synthesis step for synthesizing a plurality of tomographic images aligned in the alignment step.

According to such a method, a plurality of tomographic images are combined by aligning the scan center positions so as to be substantially the same, so that a wide-angle tomographic image can be easily obtained from the scan results executed radially. It becomes possible to do.

In the method of controlling an ophthalmic apparatus according to some embodiments, the control steps differ from each other by controlling the optical scanner so that the scan center position and the scan direction of at least one of the plurality of scans are substantially aligned. Perform multiple scans on multiple scan areas.

According to such a method, a plurality of scans are executed for a plurality of scan areas different from each other so that the scan center position and at least one scan direction of the plurality of scans substantially coincide with each other, which is simple. The process makes it possible to easily obtain wide-angle tomographic images from the results of radial scans.

In the control method of the ophthalmic apparatus according to some embodiments, the control step switches a plurality of tomographic images obtained in the image formation step so that the feature positions in each scan substantially match, and the display means (display unit 240A). ) Is displayed.

According to such a method, it becomes easy to observe changes in morphology and the like of a plurality of tomographic images obtained by a plurality of radial scans with reference to a feature region.

<Others>
The embodiment shown above or a modification thereof is only an example for carrying out the present invention. A person who intends to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of the present invention.

1 Ophthalmology device 100 OCT unit 210 Control unit 211 Main control unit 211A Scan area setting unit 211B Scan center position setting unit 211C Scan start position setting unit 211D Scan end position setting unit 211E Scan control unit 212 Storage unit 220 Image forming unit 230 Data processing Part 231 Analysis part 231A Feature area identification part 232 Image alignment part 233 Image synthesis part E Eye to be inspected LS measurement light

Claims (18)

An optical system including an optical scanner, which scans a predetermined scan area by deflecting light from a light source by the optical scanner and collects data of an eye to be inspected.
A control unit that controls the optical scanner to execute a plurality of scans radially around a scan center position different from the center of the scan area.
Ophthalmic equipment including. The ophthalmic apparatus according to claim 1, wherein the scan center position can be changed. Including the operation unit
The ophthalmic apparatus according to claim 1 or 2, wherein the control unit sets the scan center position based on the operation content for the operation unit. An acquisition unit that acquires an image of the eye to be inspected,
An analysis unit that identifies a characteristic region of the eye to be inspected by analyzing the image acquired by the acquisition unit, and an analysis unit.
Including
The ophthalmic apparatus according to claim 1 or 2, wherein the control unit sets a position in the feature region specified by the analysis unit as the scan center position. For each of the plurality of scans, a first setting unit that sets a scan start position based on the scan area and the scan center position, and
For each of the plurality of scans, a second setting unit that sets a scan end position based on the scan area and the scan center position, and
Including
The control unit controls the optical scanner for each of the plurality of scans based on the scan start position set by the first setting unit and the scan end position set by the second setting unit. The ophthalmic apparatus according to any one of claims 1 to 4, wherein the ophthalmic apparatus is characterized by the above. Claims 1 to 5, wherein the control unit controls the optical scanner so as to execute the plurality of scans around each of two or more scan center positions in the same scan area. The ophthalmic apparatus according to any one of the following items. The optical system divides the light from the light source into a measurement light and a reference light, projects the measurement light deflected by the optical scanner onto the eye to be inspected, and uses the return light of the measurement light from the eye to be inspected. Includes an interference optical system that detects interference light with the reference light.
The invention according to any one of claims 1 to 6, wherein an image forming portion that forms a tomographic image of the eye to be inspected is included based on the detection result of the interference light obtained by the interference optical system. Ophthalmic equipment. An alignment unit that aligns a plurality of tomographic images obtained by the image forming unit by executing the plurality of scans so that the positions of the plurality of scan centers in the plurality of scans substantially match.
A compositing unit that synthesizes a plurality of tomographic images aligned by the alignment unit, and a compositing unit.
7. The ophthalmic apparatus according to claim 7, wherein the ophthalmic apparatus comprises. The control unit executes the plurality of scans for a plurality of different scan areas by controlling the optical scanner so that the scan center position and the scan direction of at least one of the plurality of scans substantially coincide with each other. The ophthalmic apparatus according to claim 8, wherein the ophthalmic apparatus is made to be used. Claims 7 to 9, wherein the control unit switches a plurality of tomographic images obtained by the image forming unit and displays them on the display means so that the feature positions in each scan are substantially the same. The ophthalmic apparatus according to any one of the following items. It is a control method of an ophthalmic device for collecting data of an eye to be inspected.
A setting step to set a scan center position different from the center of a predetermined scan area,
A control step that controls the optical scanner so that the light from the light source is deflected by the optical scanner and a plurality of scans are executed radially around the scan center position.
Methods of controlling ophthalmic devices, including. The control method for an ophthalmic apparatus according to claim 11, wherein the setting step sets the scan center position based on the operation content for the operation unit. The acquisition step of acquiring the image of the eye to be inspected, and
An analysis step of identifying the characteristic region of the eye to be inspected by analyzing the image acquired in the acquisition step,
Including
The method for controlling an ophthalmic apparatus according to claim 11 or 12, wherein the setting step sets a position in the feature region specified in the analysis step as the scan center position. The control step of claims 11 to 13 is characterized in that the optical scanner is controlled so as to execute the plurality of scans around each of two or more scan center positions in the same scan area. The method for controlling an ophthalmic apparatus according to any one of the following items. The invention according to any one of claims 11 to 14, wherein an image forming step of forming a tomographic image of the eye to be inspected by performing optical coherence stromography using the light from the light source is included. How to control an ophthalmic device. An alignment step of aligning the plurality of tomographic images obtained in the image formation step by executing the plurality of scans so that the positions of the plurality of scan centers in the plurality of scans substantially match.
In the synthesis step of synthesizing a plurality of tomographic images aligned in the alignment step,
15. The method for controlling an ophthalmic apparatus according to claim 15, wherein the method comprises. The control step executes the plurality of scans for a plurality of different scan areas by controlling the optical scanner so that the scan center position and the scan direction of at least one of the plurality of scans substantially coincide with each other. The method for controlling an ophthalmic apparatus according to claim 16, wherein the method of controlling the ophthalmic apparatus. The 16th or 17th claim is characterized in that the control step switches a plurality of tomographic images obtained in the image forming step and displays them on a display means so that the feature positions in each scan are substantially the same. The method of controlling an ophthalmic apparatus according to the description.

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