JP2020048772A - Ophthalmologic apparatus and control method thereof - Google Patents

Abstract

To provide a new technology for performing OCT measurement by using an optical scanner.SOLUTION: An ophthalmologic apparatus includes a data acquisition unit, a storage unit, and a correction unit. The data acquisition unit includes an optical scanner capable of deflecting a light in a predetermined deflection angle range, and acquires a first data set group in a scan direction A by executing optical coherence tomography to an eye to be examined by using a measurement light deflected in a predetermined deflection direction by the optical scanner. The storage unit stores correction data corresponding to operation characteristics of the optical scanner. The correction unit generates a second data set group by correcting at least part of the first data set group on the basis of the correction data stored in the storage unit.SELECTED DRAWING: Figure 3

Description

  The present invention relates to an ophthalmologic apparatus and a control method thereof.

  2. Description of the Related Art In recent years, optical coherence tomography (OCT), which measures and forms an image of an object to be measured using a light beam from a laser light source or the like, has attracted attention. Since OCT does not have invasiveness to a human body like X-ray CT (Computed Tomography), it is expected to be applied particularly in the medical field and the biological field. For example, in the field of ophthalmology, apparatuses for forming images of the fundus, the cornea, and the like have been put to practical use. An apparatus using such OCT (OCT apparatus) is applicable to observation of various parts (fundus and anterior segment) of the eye to be examined. Further, since high-definition images can be obtained, they are applied to diagnosis of various ophthalmic diseases.

  In measurement (imaging) using OCT, a scan is performed on a measurement site using measurement light deflected by an optical scanner. For example, Patent Literature 1 discloses a method of constantly performing correction calculation on a movement command value of a galvano scanner to ensure the linearity of a scanning trajectory.

JP 2011-170209 A

  In the measurement using OCT, it is required to obtain a wider-angle and higher-definition measurement result. Therefore, the optical scanner is required to operate at a higher speed in a wider deflection angle range. However, it is difficult for an optical scanner such as a galvano scanner to follow a high-speed operation.

  Thus, obtaining a desired measurement result in OCT measurement is restricted by the operating characteristics of the optical scanner.

  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 performing OCT measurement using an optical scanner.

  A first aspect of some embodiments includes an optical scanner capable of deflecting light in a predetermined deflection angle range, and irradiates an eye to be inspected with measurement light deflected by the optical scanner in a predetermined deflection direction. A data acquisition unit that acquires a first data set group in the A-scan direction by executing coherence tomography, a storage unit that stores correction data corresponding to an operation characteristic of the optical scanner, and a storage unit that is stored in the storage unit. A correction unit configured to correct at least a part of the first data set group based on the correction data to generate a second data set group.

  In a second aspect of some embodiments, in the first aspect, the correction unit is configured to convert the first data set group into a measurement beam that is deflected by the optical scanner at substantially equal intervals in the deflection angle range in the deflection angle range. One or more data sets corresponding to at least a part of the deflection angle range in the first data set group are corrected based on the correction data so that the data set group is obtained based on the correction data.

  In a third aspect of some embodiments, in the second aspect, the optical scanner includes a mirror that reflects the measurement light, and reciprocally swings the mirror in a swing direction corresponding to the deflection direction. Thereby, the measuring light is deflected in the deflection angle range, and at least a part of the deflection angle range is shifted in the first deflection angle or the swing direction at which the mirror starts to swing in the swing direction. A second deflection angle at which the swing of the mirror is ended.

  In a fourth aspect of some embodiments, in any one of the first to third aspects, the correction unit includes an extraction unit that extracts one or more data sets from at least a part of the first data set group. And replacing at least a part of the first data set group with the one or more data sets.

  According to a fifth aspect of some embodiments, in any one of the first to third aspects, the correction unit interpolates at least a part of the first data set group to calculate an interpolation data set. And replacing at least a part of the first data set group with an interpolation data set calculated by the interpolation unit.

  According to a sixth aspect of some embodiments, in any one of the first to third aspects, the correction unit may further include: a positioning unit that positions at least a part of the first data set group in the A-scan direction. An interpolation unit that calculates an interpolation data set by interpolating at least a part of the first data set group that has been aligned by the alignment unit, wherein at least a part of the first data set group is Replace with the interpolation data set calculated by the interpolation unit.

  In a seventh aspect of some embodiments, in any one of the first to third aspects, the correction unit adds a new data set to the first data set group.

  In an eighth aspect of some embodiments, in the seventh aspect, the new dataset is generated based on at least a portion of the first dataset.

  In a ninth aspect of some embodiments, the optical scanner according to any of the first to eighth aspects, wherein the optical scanner deflects the measurement light in a first deflection direction in a first deflection angle range, A second scanner that deflects the measurement light deflected by the first scanner toward the subject's eye in a second deflection direction in a second deflection direction, wherein the correction unit operates the first scanner. Correction processing for at least a part of the first data set group based on the first correction data corresponding to the characteristic, and at least one of the first data set group based on the second correction data corresponding to the operation characteristic of the second scanner; Any one of the correction processes for the units can be executed.

  In a tenth aspect of some embodiments, in any one of the first to ninth aspects, the storage unit corresponds to a plurality of scanning conditions in which at least one of a deflection angle range and a deflection speed of the optical scanner is different. A plurality of correction data are stored, and the correction unit corrects at least a part of the first data set group based on the correction data stored in the storage unit corresponding to the scan condition.

  An eleventh aspect of some embodiments is an image forming method according to any one of the first to tenth aspects, wherein the tomographic image of the subject's eye is formed based on the second data set group generated by the correction unit. Including parts.

  A twelfth aspect of some embodiments is a method for controlling an ophthalmic apparatus including an optical scanner capable of deflecting light within a predetermined deflection angle range. The control method of the ophthalmologic apparatus obtains a first data set group in the A-scan direction by performing optical coherence tomography on the subject's eye using measurement light deflected in a predetermined deflection direction by the optical scanner. A data acquisition step, and a correction step of correcting at least a part of the first data set group based on correction data corresponding to an operation characteristic of the optical scanner to generate a second data set group.

  In a thirteenth aspect of some embodiments, in the twelfth aspect, in the twelfth aspect, the correcting step includes the step of converting the first data set group into a measurement beam that is deflected by the optical scanner at substantially equal intervals in the deflection angle range. One or more data sets corresponding to at least a part of the deflection angle range in the first data set group are corrected based on the correction data so that the data set group is obtained based on the correction data.

  In a fourteenth aspect of some embodiments, in the thirteenth aspect, in the thirteenth aspect, the optical scanner includes a mirror that reflects the measurement light, and reciprocally swings the mirror in a swing direction corresponding to the deflection direction. Thereby, the measuring light is deflected in the deflection angle range, and at least a part of the deflection angle range is shifted in the first deflection angle or the swing direction at which the mirror starts to swing in the swing direction. A second deflection angle at which the swing of the mirror is ended.

  In a fifteenth aspect of some embodiments, in any one of the twelfth aspect to the fourteenth aspect, the optical scanner deflects the measurement light in a first deflection direction in a first deflection angle range, A second scanner that deflects the measurement light deflected by the first scanner toward the subject's eye in a second deflection direction in a second deflection angle range, wherein the correcting step includes an operation of the first scanner. Correction processing for at least a part of the first data set group based on the first correction data corresponding to the characteristic, and at least one of the first data set group based on the second correction data corresponding to the operation characteristic of the second scanner; Any one of the correction processes for the units can be executed.

  A sixteenth aspect of some embodiments is the image forming apparatus according to any one of the twelfth aspect to the fifteenth aspect, wherein a tomographic image of the subject's eye is formed based on the second data set group generated in the correction step. Including steps.

  In addition, it is possible to arbitrarily combine the configurations according to the plurality of claims described above.

  According to the present invention, a new technique for performing OCT measurement using an optical scanner can be provided.

FIG. 2 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. FIG. 2 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. FIG. 2 is a schematic block diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. It is a schematic diagram showing an example of operation characteristics of an optical scanner concerning an embodiment. It is a schematic diagram for explaining processing which an ophthalmologic apparatus concerning an embodiment performs. It is a schematic diagram for explaining processing which an ophthalmologic apparatus concerning an embodiment performs. FIG. 2 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. It is a schematic diagram for explaining processing which an ophthalmologic apparatus concerning an embodiment performs. FIG. 2 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. It is a schematic diagram for explaining processing which an ophthalmologic apparatus concerning an embodiment performs. FIG. 2 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. It is a schematic diagram for explaining processing which an ophthalmologic apparatus concerning an embodiment performs. FIG. 2 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to an embodiment. It is a schematic diagram for explaining processing which an ophthalmologic apparatus concerning an embodiment performs. 6 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment. 6 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment. FIG. 11 is a schematic block diagram illustrating an example of a configuration of an ophthalmologic apparatus according to a modified example of the embodiment.

  An embodiment of an ophthalmologic apparatus and a method of controlling the ophthalmic apparatus according to the present invention will be described in detail with reference to the drawings. In addition, the description content of the literature and any known technology cited in this specification can be used in the following embodiments.

  The ophthalmologic apparatus according to the embodiment includes an optical scanner capable of deflecting measurement light within a predetermined deflection angle range, and performs OCT on the subject's eye using the measurement light deflected by the optical scanner in a predetermined deflection direction. It is possible. The ophthalmologic apparatus acquires a data set group (first data set group) in the A-scan direction by executing OCT, and based on correction data corresponding to the operation characteristics (eg, deflection angle versus time characteristics) of the optical scanner. A new data set group (second data set group) is generated by correcting at least a part of the data set group. In some embodiments, the data set group is a data set group of the reflection intensity profile data in the A-scan direction obtained by performing a Fourier transform or the like on the detection data (detection result) of the interference light. In some embodiments, the data set is a data set of A-scan image data obtained by imaging the reflection intensity profile. In some embodiments, the data set is a data set of interference light detection data.

  This makes it possible to acquire a data set group in the A-scan direction in consideration of the operation characteristics of the optical scanner. For example, it becomes possible to generate a data set group at uniformly arranged scanning positions from a data set group acquired at scanning positions unevenly distributed due to the nonlinear operation of the optical scanner. Here, the non-linear operation of the optical scanner means an operation in which the deflection angle of the optical scanner does not linearly change with respect to a change in time (data collection timing). Further, for example, it is possible to generate a data set group obtained at a high density only for a desired part from a data set group obtained by the linear operation of the optical scanner.

  Hereinafter, a case will be described in which the optical scanner includes a galvano scanner, performs a linear operation in a predetermined deflection angle range, and performs a non-linear operation in another deflection angle range. However, the following embodiment can also be applied to a case where the optical scanner performs a linear operation. In the following, the deflection angle vs. time characteristic will be described as an example of the operation characteristics of the optical scanner, but the following embodiments can be applied to other operation characteristics of the optical scanner.

  In the following, a case where a data set group of A-scan image data is corrected will be described. However, the following embodiment can also be applied to a case where a data set group such as reflection intensity profile data is corrected.

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

  An ophthalmologic apparatus according to some embodiments includes at least one of an ophthalmologic photographing apparatus, an ophthalmologic measuring apparatus, and an ophthalmic treatment apparatus. The ophthalmologic imaging apparatus included in the ophthalmologic apparatus according to some embodiments is, for example, one or more of a fundus camera, a scanning laser ophthalmoscope, a slit lamp ophthalmoscope, a surgical microscope, and the like. Further, the ophthalmologic measurement apparatus included in the ophthalmologic apparatus according to some embodiments includes, for example, any one or more of an eye refraction test apparatus, a tonometer, a specular microscope, a wavefront analyzer, a perimeter, a microperimeter, and the like. It is. Further, the ophthalmic treatment device included in the ophthalmologic devices of some embodiments is, for example, any one or more of a laser treatment device, a surgical device, a surgical microscope, and the like.

  An ophthalmologic apparatus according to the following embodiments includes an OCT apparatus capable of OCT measurement and a fundus camera. Further, the configuration according to the following embodiment can be incorporated in a single OCT device.

  Hereinafter, an ophthalmologic apparatus capable of performing OCT measurement on the fundus of the eye to be inspected will be described as an example. However, the ophthalmologic apparatus according to the embodiment may be capable of performing OCT measurement on the anterior segment of the eye to be inspected. In some embodiments, the OCT measurement range and the measurement site are changed by moving a lens that changes the focal position of the measurement light. In some embodiments, the addition of one or more attachments (objective lens, anterior lens, etc.) provides OCT measurement for the fundus, OCT measurement for the anterior segment, and OCT measurement for the whole eye including the fundus and the anterior segment. It is a configuration that allows measurement. In some embodiments, in an ophthalmologic apparatus for fundus measurement, the anterior ocular segment may be configured such that the measurement light converted into a parallel light beam is incident on the subject's eye by disposing a head lens between the objective lens and the subject's eye. OCT measurement is performed.

<Structure>
〔Optical system〕
As shown in FIG. 1, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic and control unit 200. The retinal 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 performing the OCT. Another part of the optical system and the mechanism for performing the OCT is provided in the fundus camera unit 2. The arithmetic and control unit 200 includes one or more processors that execute various calculations and controls. In addition to these, arbitrary elements such as a member for supporting the subject's face (chin rest, forehead support, etc.) and a lens unit for switching the target site of OCT (for example, an anterior segment OCT attachment) And a unit may be provided in the ophthalmologic apparatus 1. In some embodiments, the lens unit is configured to be manually inserted and removed between the subject's eye E and an objective lens 22 described later. In some embodiments, the lens unit is configured to be automatically inserted and removed between the subject's eye E and the objective lens 22 described below under the control of the control unit 210 described below.

  In this specification, a “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, an SPLD (Simple Graphical Programmable Programmable Programmable Logic), or a programmable logic device (for example, an SPLD (Simple Programmable Programmable Programmable Logic Programmable Programmable Logic)). It means a circuit such as a programmable logic device (FPGA) or a field programmable gate array (FPGA). The processor realizes the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or a storage device.

[Fundus camera unit]
The retinal camera unit 2 is provided with an optical system for photographing the fundus oculi Ef of the eye E. The acquired image of the fundus oculi Ef (referred to as a fundus image, a fundus photograph, or the like) is a front image such as an observation image or a photographed image. The observation image is obtained by moving image shooting using near-infrared light. The photographed image is a still image using flash light. Further, the fundus camera unit 2 can photograph the anterior segment Ea of the eye E to acquire a front image (anterior segment image).

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

  Light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by a reflection mirror 12 having a curved reflection surface, passes through a condenser lens 13, and passes through a visible cut filter 14. It becomes near infrared light. Further, the observation illumination light is once focused near the imaging light source 15, reflected by the mirror 16, and passes through the relay lenses 17 and 18, the diaphragm 19 and the relay lens 20. Then, the observation illumination light is reflected at the periphery of the apertured mirror 21 (the area around the aperture), passes through the dichroic mirror 46, is refracted by the objective lens 22, and is refracted by the eye E (the fundus Ef or the anterior eye). The part Ea) is illuminated. The return light of the observation illumination light from the eye E 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 imaging 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 forms an image on the light receiving surface of the image sensor 35 by the condenser lens. The image sensor 35 detects return light at a predetermined frame rate. Note that the focus of the imaging optical system 30 is adjusted so as to match the fundus oculi Ef or the anterior ocular segment Ea.

  Light (photographing illumination light) output from the photographing light source 15 is applied to the fundus oculi Ef through the same path as the observation illumination light. The return light of the imaging illumination light from the eye E 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.

  An LCD (Liquid Crystal Display) 39 displays a fixation target and a visual acuity measurement target. A part of the light beam output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, passes through the imaging focusing lens 31 and the dichroic mirror 55, and passes through the hole of the perforated mirror 21. The light beam 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 on 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 can be changed. As an example of the fixation position, a fixation position for acquiring an image centered on the macula, a fixation position for acquiring an image centered on the optic disc, and a fundus center between the macula and the optic disc. There is a fixation position for acquiring an image centered on, and a fixation position for acquiring an image of a part (peripheral part of the fundus) far away from the macula. The ophthalmologic apparatus 1 according to some embodiments includes a GUI (Graphical User Interface) for specifying at least one of such fixation positions. The ophthalmologic apparatus 1 according to some embodiments includes a GUI or the like for manually moving a fixation position (a display position of a 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 (such as a light emitting diode (LED) array). In addition, a movable fixation target can be generated by one or more movable light sources.

  Further, the ophthalmologic 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 to a concomitant eye of the eye E to be inspected. The projection position of the fixation light in the concomitant eye can be changed. The fixation position of the eye E can be changed by changing the projection position of the fixation light on the contributing eye. The fixation position by the external fixation light source may be the same as the fixation position of the subject's eye E using the LCD 39. For example, a movable fixation target can be generated by selectively lighting 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 the eye E. The alignment light output from the LED 51 passes through the apertures 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, and passes through the hole 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 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 or automatic alignment can be performed based on the received light image (alignment index image).

  The focus optical system 60 generates a split index used for focus adjustment on the eye E. 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 imaging focusing lens 31 along the optical path (illumination optical path) of the imaging optical system 30. The reflection bar 67 is insertable into and removable from the illumination optical path. When performing the focus adjustment, the reflection surface of the reflection bar 67 is arranged obliquely in the illumination optical path. Focus light output from the LED 61 passes through a relay lens 62, is split into two light beams by a split indicator plate 63, passes through a two-hole aperture 64, is reflected by a mirror 65, and is reflected by a condensing lens 66 on a reflecting rod 67. Is once imaged on the reflecting surface of and is reflected. Further, the focus light passes through the relay lens 20, is reflected by the aperture mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected on the fundus Ef. The fundus reflection light of the focus light is guided to the image sensor 35 through the same path as the corneal reflection light of the alignment light. Manual focus or auto focus can be executed based on the received light image (split index image).

  The dichroic mirror 46 combines the optical path for fundus imaging and the optical path for OCT. The dichroic mirror 46 reflects light in a wavelength band used for OCT and transmits light for fundus imaging. On the optical path for OCT (optical path of the measurement light), in order from the OCT unit 100 side to the dichroic mirror 46 side, the collimator lens unit 40, the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, the mirror 44, And a relay lens 45.

  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 OCT optical path. This change in the optical path length is used for correcting the optical path length according to the axial length of the eye, adjusting the interference state, and the like. 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. The optical scanner 42 deflects the measurement light LS passing through the OCT optical path. The optical scanner 42 can deflect the measurement light LS one-dimensionally or two-dimensionally.

  When deflecting one-dimensionally, the optical scanner 42 includes a galvano scanner that deflects the measurement light LS in a predetermined deflection angle range in a predetermined deflection direction. When deflecting two-dimensionally, the optical scanner 42 includes a first galvano scanner and a second galvano scanner. The first galvano scanner deflects the measurement light LS so as to scan an imaging part (the fundus oculi Ef or the anterior eye part) in a horizontal direction orthogonal to the optical axis of the OCT optical system 8. The second galvano scanner deflects the measurement light LS deflected by the first galvano scanner so as to scan an imaging region in a vertical direction perpendicular to the optical axis of the OCT optical system 8. The scanning mode of the measurement light LS by the optical scanner 42 includes, for example, a horizontal scan, a vertical scan, a cross scan, a radiation scan, a circular scan, a concentric scan, and a spiral scan.

  The OCT focusing lens 43 is moved along the optical path of the measurement light LS in order to adjust the focus of the optical system for OCT. The OCT focusing lens 43 is used to arrange the first lens position for arranging the focal position of the measurement light LS at or near the fundus oculi Ef of the eye E, and to convert the measurement light LS applied to the eye E into a parallel light flux. And the second lens position. The movement of the photographing focusing lens 31, the movement of the focusing optical system 60, and the movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

[OCT unit]
FIG. 2 shows an example of the configuration of the OCT unit 100. 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 splits light from a wavelength-swept (wavelength-scanning) light source into measurement light and reference light, and causes the return light of the measurement light from the subject's eye E to interfere with the reference light passing through the reference light path. This is an interference optical system that generates interference light and detects the interference light. The detection result (detection signal) of the interference light by the interference optical system is an interference signal indicating the spectrum of the interference light, and is sent to the arithmetic and 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-swept light source includes a laser light source including a resonator. The light source unit 101 temporally changes the output wavelength in a near-infrared wavelength band that cannot be visually recognized by human eyes.

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

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

  The reference light LR is guided to the collimator 111 by the optical fiber 110 and becomes a parallel light beam. The reference light LR that has become a parallel light flux is guided to the optical path length changing unit 114. 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, adjusting the interference state, and the like. The optical path length changing unit 114 includes, for example, a corner cube and a moving mechanism that moves the corner cube. In this case, the corner cube of the optical path length changing unit 114 turns the traveling direction of the reference light LR converted into a parallel light beam by the collimator 111 in the opposite direction. The optical path of the reference light LR incident on the corner cube is parallel to the optical path of the reference light LR emitted from the corner cube.

  In the configuration shown in FIGS. 1 and 2, an 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 (reference optical path, reference An optical path length changing unit 114 for changing the length of the arm is provided. However, only one of the optical path length changing units 41 and 114 may be provided. It is also possible to change the difference between the reference optical path length and the measured optical path length by using other optical members.

  The reference light LR that has passed through the optical path length changing unit 114 is converted from a parallel light beam into a converged light beam by the collimator 116 and enters the optical fiber 117.

  An optical path length correction member may be arranged on at least one of the reference optical path between the collimator 111 and the optical path length changing unit 114 and the reference optical path between the collimator 116 and the optical path length changing unit 114. The optical path length correction member functions as a delay unit for adjusting the optical path length (optical distance) of the reference light LR and the optical path length of the measurement light LS.

  The reference light LR that has entered the optical fiber 117 is guided to the polarization controller 118, and its polarization state is adjusted. The polarization controller 118 has, for example, a configuration similar to that of the polarization controller 103. The reference light LR whose polarization state has been adjusted by the polarization controller 118 is guided to the attenuator 120 by the optical fiber 119, and the light amount is adjusted under the control of the arithmetic and control unit 200. The reference light LR whose light amount has been adjusted by the attenuator 120 is guided to the fiber coupler 122 by the optical fiber 121.

  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 light beam by the collimator lens unit 40. The measurement light LS converted into a parallel light beam is guided to a dichroic mirror 46 via an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, a mirror 44, and a 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. The measurement light LS is scattered (including reflection) at various depth positions of the eye E. 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 the measurement light LS incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121 to generate (interfere with) the interference light. The fiber coupler 122 generates a pair of interference lights LC by splitting the interference light between the measurement light LS and the reference light LR at a predetermined split ratio (for example, 1: 1). The pair of interference lights LC emitted from the fiber coupler 122 is 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 respectively detect a pair of interference lights LC and outputs a difference between detection results obtained by the pair of photodetectors. The detector 125 sends the detection result (interference signal) to a DAQ (Data Acquisition System) 130. The DAQ 130 is supplied with a clock KC 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, for example, optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then generates the clock KC based on the result of detecting the combined light. Generate. The DAQ 130 samples the detection result of the detector 125 based on the clock KC. The DAQ 130 sends the sampled detection result of the detector 125 to the arithmetic and control unit 200. The arithmetic and control unit 200 performs a Fourier transform or the like on the spectral distribution based on the detection result obtained by the detector 125, for example, for each series of wavelength scans (for each A line), thereby obtaining a reflection intensity profile in each A line. Form. Further, the arithmetic and control unit 200 forms image data by imaging the reflection intensity profile of each A line.

[Operation control unit]
The arithmetic and control unit 200 analyzes the detection signal input from the DAQ 130 and forms an OCT image of the fundus oculi Ef. The arithmetic processing for that is the same as in a conventional swept-source OCT apparatus.

  Further, the arithmetic and control unit 200 controls each unit 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 and control unit 200 controls the operation of the observation light source 11, the imaging light source 15, and the LEDs 51 and 61, the operation control of the LCD 39, the movement control of the imaging focus lens 31, and the control of the OCT focus lens 43. It performs movement control, movement control of the reflecting 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 control of the display device 3, the arithmetic and control unit 200 causes the display device 3 to display an OCT image of the eye E to be inspected.

  As control of the OCT unit 100, the arithmetic and control unit 200 controls the operation of the light source unit 101, the movement of the optical path length changing unit 114, the operation of the attenuator 120, the operation of the polarization controllers 103 and 118, and the operation of the detector 125. Control and operation control of the DAQ 130 are performed.

  The arithmetic and control unit 200 includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a communication interface, and the like, similarly to a conventional computer. A storage device such as a hard disk drive stores a computer program for controlling the ophthalmologic apparatus 1. The arithmetic and control unit 200 may include various circuit boards, for example, a circuit board for forming an OCT image. Further, the arithmetic and 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 and control unit 200 may be configured integrally (that is, in a single housing), or may be configured separately in two or more housings. It may be.

(Control system)
FIG. 3 shows a configuration example of a control system of the ophthalmologic apparatus 1. In FIG. 3, some of the components included in the ophthalmologic apparatus 1 are omitted.

(Control unit)
The control unit 210 performs various controls. 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 ophthalmologic apparatus 1. For example, the main control unit 211 includes the focusing driving units 31A and 43A of the fundus camera unit 2, the image sensors 35 and 38, the LCD 39, the optical path length changing unit 41, the optical scanner 42, and the entire optical system (moving mechanism 150). Control. Further, the main control unit 211 controls the light source unit 101, the optical path length changing unit 114, the attenuator 120, the polarization controllers 103 and 118, the detector 125, the DAQ 130, and the like of the OCT unit 100.

  For example, the main control unit 211 displays the fixation target at a position on the screen of the LCD 39 corresponding to the fixation position set manually or automatically. 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 the movement mode of the fixation target are set manually or automatically. The manual setting is performed using, for example, a GUI. The automatic setting is performed by the data processing unit 230, for example.

  The focusing drive unit 31 </ b> A moves the focusing lens 31 in the optical axis direction of the imaging optical system 30 and also moves the focusing optical system 60 in the optical axis direction of the illumination optical system 10. Thereby, the focus position of the photographing optical system 30 is changed. The focusing drive unit 31A may individually have a mechanism for moving the imaging focusing lens 31 and a mechanism for moving the focusing optical system 60. The focus drive unit 31A is controlled when performing focus adjustment or the like.

  The focusing drive unit 43A moves the OCT focusing lens 43 in the optical axis direction of the measurement optical path. Thereby, the focus 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 oculi 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 far point position, and the measurement light LS can be converted into a parallel light beam. The focus 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 a mechanism for moving at least the fundus camera unit 2 in the x direction (lateral direction), a mechanism for moving in the y direction (vertical direction), and a mechanism for moving the fundus camera unit 2 in the z direction (depth direction). , A 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 that can move in the y direction, and a y moving mechanism that moves the y stage. The mechanism for moving in the z direction includes, for example, a z stage that can move in the z direction, and a z moving mechanism that moves 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 for the moving mechanism 150 is used in alignment and tracking. The tracking is to move the apparatus optical system in accordance with the eye movement of the eye E to be inspected. When performing tracking, alignment and focus adjustment are performed in advance. Tracking is a function of maintaining a suitable positional relationship where alignment and focus are achieved by causing the position of the apparatus optical system to follow eye movement. In some embodiments, it is configured to control the moving mechanism 150 to change the optical path length of the reference light (and 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 moves the optical system and the eye E relatively by operating the user interface 240 described below so that the displacement of the eye E with respect to the optical system is canceled. For example, the main control unit 211 controls the moving mechanism 150 by outputting a control signal corresponding to the operation content on 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 such that the displacement of the eye E with respect to the optical system is canceled, thereby causing the optical system and the eye E to move relatively. In some embodiments, the main control unit 211 controls the control signal so that the optical axis of the optical system substantially coincides with the axis of the eye E and the distance of the optical system to the eye E is a predetermined working distance. Is output to the moving mechanism 150 to control the moving mechanism 150 to relatively move the optical system and the eye E to be examined. Here, the working distance is a predetermined value also called a working distance of the objective lens 22, and corresponds to a distance between the subject's eye E and the optical system at the time of measurement (at the time of photographing) using the optical system.

  The main control unit 211 controls fundus photographing and anterior segment photographing 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 execute a plurality of preliminary operations before performing the OCT measurement. Preliminary operations include alignment, coarse focus adjustment, polarization adjustment, and focus fine adjustment. The plurality of preliminary operations are performed in a predetermined order. In some embodiments, the preliminary actions are performed in the order described above.

  Note that the types and order of the preliminary operations are not limited to these, and are arbitrary. For example, a preliminary operation (small pupil determination) for determining whether or not the eye E to be examined 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 includes the following series of processes: a process of acquiring a front image (anterior eye image) of the eye E; a process of identifying an image region corresponding to the pupil; Processing for determining the size (diameter, perimeter, etc.) of the pupil region obtained; processing for determining whether or not the eye is a small pupil based on the obtained size (threshold processing); The process to control. Some embodiments further include a process of approximating the pupil region with a circle or an ellipse to determine the pupil size.

  The focus rough adjustment is a focus adjustment using a split index. By determining the position of the focusing lens 31 based on the information obtained by associating the eye refractive power and the position of the focusing lens 31 acquired in advance and the measured value of the refractive power of the eye E, Focus coarse adjustment can also be performed.

  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, the position of the OCT focusing lens 43 that maximizes the interference intensity is obtained, and the OCT focusing lens 43 is located at that position. By moving the focusing lens 43, fine focus adjustment can be performed.

  In the optical path length difference adjustment, control is performed such that a predetermined position in the eye E is a reference position of a measurement range in the depth direction. This control is performed for 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, OCT measurement can be accurately performed in 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.

(Storage unit)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, image data of an OCT image, image data of a fundus image, image data of an anterior segment image, eye information to be examined, and the like. The subject's eye information includes information about the subject, such as a patient ID and a name, and information about the subject's eye, such as left / right eye identification information.

  Further, the storage unit 212 stores correction data 212A. The correction data 212A is data for correcting a data set group in the A-scan direction acquired by executing the OCT. The correction data 212A is data corresponding to the deflection angle versus time characteristic (operating characteristic in a broad sense) of the optical scanner 42. In some embodiments, the storage unit 212 stores a plurality of correction data 212A corresponding to a plurality of scan conditions in which at least one of the deflection angle range and the deflection speed (scanning frequency) of the optical scanner 42 is different.

  Further, the storage unit 212 stores various programs and data for operating the ophthalmologic apparatus 1.

(Data processing unit)
The data processing unit 230 processes data acquired by imaging of the eye E and OCT measurement. The data processing section 230 includes an image forming section 231 and a correction section 232.

(Image forming unit)
The image forming unit 231 forms an OCT image (image data) of the eye E based on sampling data obtained by sampling the detection signal from the detector 125 with the DAQ 130. The OCT image formed by the image forming unit 231 includes an A-scan image, a B-scan image (tomographic image), a C-scan image, and the like. This processing includes processing such as noise removal (noise reduction), filtering, dispersion compensation, and FFT (Fast Fourier Transform), as in the conventional swept-source OCT. In the case of another type of OCT apparatus, the image forming unit 231 executes a known process according to the type.

  The image forming unit 231 includes, for example, the above-described circuit board. In this specification, “image data” and “image” based on the image data may be identified.

  For example, the data processing unit 230 performs various image processing and analysis processing on the image formed by the image forming unit 231. For example, the data processing unit 230 executes various correction processes such as brightness correction of an image. Further, the data processing unit 230 performs various image processing and analysis processing on the image (fundus image, anterior eye image, etc.) obtained by the fundus camera unit 2.

  The data processing unit 230 performs known image processing such as interpolation processing for interpolating pixels between tomographic images, and forms image data of a three-dimensional image of the fundus oculi Ef. Note that the image data of a three-dimensional image refers to image data in which the positions of pixels are defined by a three-dimensional coordinate system. As image data of a 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 the volume data, the data processing unit 230 performs rendering processing (such as volume rendering or MIP (Maximum Intensity Projection: maximum value projection)) on the volume data to view the volume data from a specific line of sight. The image data of the pseudo three-dimensional image at the time of being formed is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 240A.

  Also, stack data of a plurality of tomographic images can be formed as image data of a three-dimensional image. 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 in 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, and the like), and thereby performs a B-mode image (vertical cross-sectional image, axial cross-sectional image) on an arbitrary cross section, and a B-mode image on an arbitrary cross section. A C-mode image (transverse cross-sectional image, horizontal cross-sectional image), a projection image, a shadowgram, and the like 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 a pixel (pixel, voxel) on a specified cross section from a three-dimensional data set. The projection image is formed by projecting the three-dimensional data set in a predetermined direction (z direction, depth direction, axial direction). The shadowgram is formed by projecting a part of the three-dimensional data set (for example, partial data corresponding to a specific layer) in a predetermined direction. An image, such as a C-mode image, a projection image, or a shadowgram, which is viewed from the front side of the subject's eye is referred to as a front image (en-face image).

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

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

  An image (for example, a three-dimensional image, a B-mode image, a C-mode image, a projection image, a shadowgram, and an OCTA image) generated by the data processing unit 230 is also included in the OCT image.

  Further, the data processing unit 230 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 focus driving unit 43A according to a predetermined algorithm. The data processing unit 230 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 data processing unit 230 determines whether the calculated evaluation value is equal to or smaller than a threshold. In some embodiments, the focus fine adjustment is continued until the calculated evaluation value falls 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 strengths (interference strength, interference sensitivity) of the sequentially obtained interference signals while performing the above-described repetitive OCT measurement to obtain the interference signals. I 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. According to such fine focus adjustment, the OCT focusing lens 43 can be guided to a position where the interference intensity is optimized.

  Further, the data processing unit 230 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 data processing unit 230 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 data processing unit 230 determines whether the calculated evaluation value is equal to or smaller than a threshold. This threshold is set in advance. The polarization adjustment is continued until the calculated evaluation value becomes equal to or less than the threshold. 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 monitor the interference intensity even in polarization adjustment.

  Further, the data processing unit 230 performs a predetermined analysis process on the detection result of the interference light obtained by the OCT measurement or the OCT image formed based on the detection result. In the predetermined analysis processing, a specified part (tissue, lesion) in the eye E to be examined is specified; a distance (interlayer distance), an area, an angle, a ratio, and a density between the specified parts are calculated; Calculation of a predetermined part; calculation of these statistical values; calculation of the distribution of measured values and statistical values; image processing based on the results of these analysis processes. Certain tissues include blood vessels, optic disc, fovea, macula, and the like. Predetermined lesions include vitiligo, bleeding, and the like.

(Correction unit)
The correction unit 232 generates a new data set in the A-scan direction by correcting the data set in the A-scan direction formed by the image forming unit 231 based on the correction data 212A. In some embodiments, the correction unit 232 can correct at least a part of the data set group in the A-scan direction based on the correction data stored in the storage unit 212 corresponding to the scan condition.

  4 to 6 are explanatory diagrams of the operation of the correction unit 232 according to the embodiment. FIG. 4 schematically illustrates the deflection angle versus time characteristic of the optical scanner 42. In FIG. 4, the horizontal axis represents the time corresponding to the A-scan execution timing (data set acquisition timing), and the vertical axis represents the deflection angle. FIG. 5 is a diagram for explaining a correction operation by the correction unit 232. FIG. 6 schematically shows a tomographic image of the fundus oculi Ef of the eye E. In FIG. 6, the number of A-scans in the tomographic images IMG0 and IMG1 is an example, and is not limited to the number.

  The optical scanner 42 includes a mirror that reflects the measurement light LS, and deflects the measurement light LS within a predetermined deflection angle range by reciprocatingly swinging the mirror in a swing direction corresponding to a predetermined deflection direction. The deflection angle range is a range between the deflection start angle rs (first deflection angle) and the deflection end angle re (second deflection angle), as shown in FIG. Such an optical scanner 42 includes a galvano scanner, a resonant mirror, and the like. That is, as shown in FIG. 4, the deflection angle range by the optical scanner 42 includes a linear operation range R0 in which the change in the deflection angle operates almost linearly with respect to the change (time change) in the acquisition timing of the data set; Non-linear operation ranges R1 and R2 in which the change in the deflection angle does not operate linearly with respect to the change in the acquisition timing of the data set. The non-linear operation range R1 includes the deflection start angle rs. The non-linear operation range R2 includes the deflection end angle re.

  A tomographic image IMG0 as shown in FIG. 6 is obtained from the data set group in the A-scan direction obtained by deflecting the measurement light LS in the deflection angle range shown in FIG. In the tomographic image IMG0 shown in FIG. 6, the change in the deflection angle in the non-linear operation ranges R1 and R2 is reduced due to the non-linear operation of the optical scanner 42, so that the scanning position of the data set group acquired at equal time intervals is obtained. The spacing becomes smaller. On the other hand, since the deflection angle changes at substantially equal intervals in the linear operation range R0, the scanning positions of the data set group acquired at equal time intervals become equal. Therefore, in practice, it is not possible to form a tomographic image using the data set group acquired in the non-linear operation ranges R1 and R2, and to form a tomographic image using the data set group acquired in the linear operation range R0. I have no choice. Increasing the deflection speed required for wide-angle, high-definition OCT measurement leads to an expansion of the non-linear operation range. This means that it is not possible to cope with a further increase in the deflection speed.

  On the other hand, as shown in FIG. 5, the correction unit 232 corrects the data set group so as to cancel the uneven distribution of the scanning position according to the operation characteristics of the optical scanner 42. That is, the correction unit 232 causes the data set group obtained by the OCT to be a data set group acquired based on the measurement light LS deflected by the optical scanner 42 at substantially equal intervals in the deflection angle range. One or more data sets corresponding to at least a part of the deflection angle range (non-linear operation ranges R1 and R2) in the data set group are corrected based on the correction data.

  A tomographic image IMG1 as shown in FIG. 6 is obtained from the new data set group generated by the correction unit 232. The tomographic image IMG1 shown in FIG. 6 is formed from a data set group acquired by the measurement light LS deflected at substantially equal intervals in the deflection angle range regardless of the nonlinear operation of the optical scanner 42. Therefore, a tomographic image can be formed using a data set group acquired not only in the linear operation range R0 but also in (at least a part of) the non-linear operation ranges R1 and R2. This means that even if the deflection speed is increased, a part of the non-linear operation range can be utilized, so that the deflection speed can be further increased.

  The correction unit 232 can correct the data set group by various methods.

(First operation example)
FIG. 7 is a block diagram illustrating a configuration example of the correction unit 232 according to a first operation example of the embodiment.

  The correction unit 232 includes an extraction unit 232A. The extracting unit 232A extracts one or more data sets from at least a part of the data set group obtained by executing the OCT. The correction unit 232 generates a new data set group by replacing at least a part of the data set group obtained by executing the OCT with one or more data sets extracted by the extraction unit 232A.

  FIG. 8 is an operation explanatory diagram of the correction unit 232 according to the first operation example of the embodiment. In FIG. 8, the same parts as those in FIG. 5 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

  The extraction unit 232A extracts one or more data sets so that the deflection angles are at equal intervals. At this time, the extraction unit 232A can extract the data set closest to the data set corresponding to the desired deflection angle in the non-linear operation range R1 or R2 in the deflection angle versus time characteristic of the optical scanner 42. That is, the extraction unit 232A can extract one or more data sets selected by the nearest neighbor method.

(Second operation example)
FIG. 9 is a block diagram illustrating a configuration example of the correction unit 232 according to the second operation example of the embodiment.

  The correction unit 232 includes an interpolation unit 232B. The interpolation unit 232B calculates an interpolation data set by interpolating at least a part of the data set group obtained by executing the OCT. The correction unit 232 generates a new data set group by replacing at least a part of the data set group obtained by executing the OCT with the interpolation data set calculated by the interpolation unit 232B.

  FIG. 10 is an operation explanatory diagram of the correction unit 232 according to the second operation example of the embodiment. 10, the same parts as those in FIG. 5 are denoted by the same reference numerals, and the description will be appropriately omitted.

  The interpolation unit 232B calculates an interpolation data set by interpolating at least a part of the data set group obtained by executing the OCT so that the deflection angles are at equal intervals. At this time, the interpolation unit 232B linearly interpolates the data sets on both sides adjacent to the data set corresponding to the desired deflection angle in the non-linear operation range R1 or R2 in the deflection angle versus time characteristic of the optical scanner 42, thereby obtaining the interpolation data set. Is calculated. In some embodiments, the interpolator 232B averages data sets within a predetermined range including a data set corresponding to a desired deflection angle in the non-linear operation range R1 or R2 in the deflection angle versus time characteristic of the optical scanner 42. Thereby, an interpolation data set is calculated.

(Third operation example)
FIG. 11 is a block diagram illustrating a configuration example of the correction unit 232 according to the third operation example of the embodiment.

  The correction unit 232 includes a positioning unit 232C and an interpolation unit 232D. The positioning unit 232C positions at least a part of the data set group obtained by executing the OCT in the A-scan direction. The interpolation unit 232D calculates an interpolation data set by interpolating at least a part of the data set group that has been aligned by the alignment unit 232C. The correction unit 232 generates a new data set group by replacing at least a part of the data set group obtained by executing the OCT with the interpolation data set calculated by the interpolation unit 232D.

  FIG. 12 illustrates an operation explanatory diagram of the correction unit 232 according to the third operation example of the embodiment. FIG. 12 schematically illustrates a graph of a deflection angle versus time characteristic according to the embodiment. 12, the same components as those in FIG. 5 are denoted by the same reference numerals, and the description will be appropriately omitted. FIG. 12 schematically shows the operation of the interpolation processing of the data set of the reflection intensity profile data of the A-line, but the operation of the interpolation processing of the data set of the A-scan image data is the same.

  The alignment unit 232C selects two data sets so that the deflection angles are equally spaced in the non-linear operation range R1 or R2 in the deflection angle versus time characteristic of the optical scanner 42, and determines the depth of the two selected data sets. A predetermined range in the direction is specified. In some embodiments, the alignment unit 232C specifies a range in the depth direction corresponding to a predetermined layer region by a segmentation process. The positioning unit 232C specifies the range in the depth direction for the two data sets in the non-linear operation range R1 or R2, and specifies the z position of the interpolation data set so that the deflection angles are at equal intervals. The positioning unit 232C positions the two data sets in the non-linear operation range R1 or R2 to the specified z position.

  The interpolation unit 232D calculates an interpolation data set by interpolating between the two data sets that have been aligned by the alignment unit 232C with respect to the specified range in the depth direction. At this time, the interpolation unit 232D calculates an interpolation data set by linear interpolation processing, averaging processing, or weighted averaging processing.

(Fourth operation example)
FIG. 13 is a block diagram illustrating a configuration example of the correction unit 232 according to the fourth operation example of the embodiment.

  The correction unit 232 includes an addition unit 232E. The adding unit 232E generates a new data set so that the deflection angles are equally spaced. In some embodiments, the adding unit 232E adds a data set corresponding to the deflection angle of the linear operation range R0 in the deflection angle versus time characteristic of the optical scanner 42. In some embodiments, the adding unit 232E duplicates the dataset of the adjacent A-line. That is, the adding unit 232E adds a data set based on the data set corresponding to the deflection angle of the linear operation range R0.

  FIG. 14 is an operation explanatory diagram of the correction unit 232 according to the fourth operation example of the embodiment. 14, the same parts as those in FIG. 5 are denoted by the same reference numerals, and the description will be appropriately omitted.

  The adding unit 232E adds a data set corresponding to the deflection angle in the linear operation range R0 so that the deflection angles are equally spaced. In some embodiments, the correction unit 232 thins out a data set corresponding to a deflection angle in the non-linear operation range R1 or R2 such that the deflection angles are equally spaced.

  The data processing unit 230 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like. In a storage device such as a hard disk drive, a computer program for causing the microprocessor to execute the above functions is stored 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 and control unit 200 described above. The operation unit 240B includes the operation device of the arithmetic and control unit 200 described above. The operation unit 240B may include various buttons and keys provided on the housing of the ophthalmologic apparatus 1 and on the outside. For example, when the fundus camera unit 2 has a housing similar to a conventional fundus camera, the operation unit 240B may include a joystick, an operation panel, and the like provided in this housing. The display unit 240A may include various display devices such as a touch panel provided on the housing of the retinal camera unit 2.

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

  The optical system in the path from the interference optical system to the objective lens 22 included in the OCT unit 100, or the optical system and the image forming unit 231 are an example of a “data acquisition unit” according to the embodiment.

[motion]
An operation of the ophthalmologic apparatus 1 according to the embodiment will be described.

  In the first operation example, the data set group of the A-scan image data is corrected.

  FIG. 15 illustrates a first operation example of the ophthalmologic apparatus 1 according to the embodiment. FIG. 15 illustrates a flowchart of a first operation example of the ophthalmologic apparatus 1 according to the embodiment. The storage unit 212 stores a computer program for implementing the processing illustrated in FIG. The main control unit 211 executes the processing shown in FIG. 15 by operating according to the computer program.

(S1: alignment)
The main controller 211 executes the 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, a fixation target by the LCD 39 is also projected onto the eye E to be examined. 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 received light image acquired by the image sensor 35, and moves the optical system to the eye E by the moving amount. Move relatively. The main control unit 211 repeatedly executes this processing.

  In some embodiments, the above-described rough alignment adjustment and fine alignment adjustment are performed after the completion of the alignment in step S1.

(S2: 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 in the fundus oculi Ef.

  Subsequently, the main control unit 211 controls the OCT unit 100 to execute the OCT temporary measurement, and acquires an adjustment tomographic image for adjusting the reference position of the measurement range in the depth direction. Specifically, the main controller 211 controls the optical scanner 42 to deflect the measurement light LS generated based on the light L0 emitted from the light source unit 101, and receives the measurement light LS with the deflected measurement light LS. A predetermined part of the optometry E (for example, the fundus) is scanned. The detection result of the interference light obtained by the scanning of the measurement light LS is sent to the image forming unit 231 after being sampled in synchronization with the clock KC. The image forming unit 231 forms a tomographic image (OCT image) of the eye E from the obtained interference signal.

(S3: 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 S2, and moves the position of the specified predetermined part in the depth direction. A position separated by a predetermined distance is set as a reference position of the measurement range. In addition, a predetermined position determined so that the optical path lengths of the measurement light LS and the reference light LR substantially match may be set as a reference position of the measurement range.

(S4: 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 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 based on the determination result by the data processing unit 230 that the focus state of the measurement light LS is not appropriate, the main control unit 211 controls the focus driving unit 43A again, and determines that the focus state is appropriate. Repeat until judged.

  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 231 forms an OCT image based on the obtained interference light detection result. 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 as described above. When it is determined based on the determination result by the data processing unit 230 that the polarization state of the measurement light LS is not appropriate, the main control unit 211 controls the polarization controllers 103 and 118 again, and determines that the polarization state is appropriate. Repeat until it is determined that

(S5: Obtain interference signal)
Subsequently, the main control unit 211 controls the OCT unit 100 to execute the OCT measurement. The detection result of the interference light obtained by the OCT measurement is sampled by the DAQ 130 and stored in the storage unit 212 or the like as an interference signal.

(S6: forming a tomographic image)
Next, the main control unit 211 causes the image forming unit 231 to form a data set group of A-scan image data of the eye E based on the interference signal acquired in step S5.

(S7: tomographic image is corrected)
The main control unit 211 causes the correction unit 232 to correct at least a part of the data set group of the A-scan image data formed in step S <b> 6 based on the correction data 212 </ b> A stored in the storage unit 212 to generate a new A. A data set group of the scan image data is generated. The main control unit 211 can display the B-scan image (tomographic image IMG1 in FIG. 6) on the display unit 240A based on the data set group of the newly generated A-scan image data.

  This is the end of the operation of the ophthalmologic apparatus 1 (end).

  In the second operation example, the data set group of the reflection intensity profile data is corrected.

  FIG. 16 illustrates a second operation example of the ophthalmologic apparatus 1 according to the embodiment. FIG. 16 illustrates a flowchart of a second operation example of the ophthalmologic apparatus 1 according to the embodiment. The storage unit 212 stores a computer program for implementing the processing illustrated in FIG. The main control unit 211 executes the processing shown in FIG. 16 by operating according to the computer program.

(S11: alignment)
The main control unit 211 executes the alignment as in step S1.

(S12: Obtain adjustment tomographic image)
The main control unit 211 controls the OCT unit 100 to execute the OCT temporary measurement and obtains an adjustment tomographic image for adjusting the reference position of the measurement range in the depth direction, similarly to step S2.

(S13: 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) as in step S3.

(S14: focus adjustment, polarization adjustment)
Next, the main control unit 211 executes focus adjustment control and polarization adjustment control as in step S4.

(S15: Obtain interference signal)
Subsequently, the main control unit 211 controls the OCT unit 100 to execute the OCT measurement as in step S5.

(S16: Data set group is corrected)
The main control unit 211 causes the correction unit 232 to correct at least a part of the data set group of the reflection intensity profile data acquired in step S15 based on the correction data 212A stored in the storage unit 212, thereby obtaining a new reflection. A data set group of the intensity profile data is generated.

(S17: forming a tomographic image)
Next, the main controller 211 causes the image forming unit 231 to form a data set of A-scan image data of the eye E based on the new data set of reflection intensity profile data generated in step S16. The main control unit 211 can display the B-scan image (tomographic image IMG1 in FIG. 6) on the display unit 240A based on the data set group of the A-scan image data formed by the image forming unit 231.

  This is the end of the operation of the ophthalmologic apparatus 1 (end).

<Modification>
In the above embodiment, when the optical scanner 42 includes the first galvanometer scanner and the second galvanometer scanner, the storage unit 212 may store the correction data for each galvanometer scanner. Hereinafter, the configuration of the ophthalmologic apparatus according to the modified example of the embodiment will be described focusing on differences from the configuration of the ophthalmologic apparatus 1 according to the embodiment.

  FIG. 17 is a block diagram illustrating a configuration example of an ophthalmologic apparatus according to a modification of the embodiment. 17, the same components as those in FIG. 3 are denoted by the same reference numerals, and the description will be appropriately omitted.

  The configuration of the ophthalmologic apparatus according to the modification of the embodiment is different from the configuration of the ophthalmologic apparatus 1 according to the embodiment illustrated in FIG. 3 in correction data 212A stored in the storage unit 212. The correction data 212A includes first correction data 2121 and second correction data 2122.

  The first correction data 2121 is correction data corresponding to the deflection angle versus time characteristic (operating characteristic) of the first galvano scanner. The second correction data 2122 is correction data corresponding to the deflection angle versus time characteristic (operating characteristic) of the second galvano scanner. The correction unit 232 can switch and execute one of a correction process for at least a part of the data set group based on the first correction data 2121 and a correction process for at least a part of the data set group based on the second correction data 2122. is there.

  In OCT measurement, a measurement site is scanned in various scanning modes. Since the deflection angle range and the deflection speed vary depending on the scanning area and the scanning pattern, control is performed such that one of the first galvano scanner and the second galvano scanner operates at a high speed and the other operates at a low speed according to the scanning conditions. According to this modification, the data set group can be corrected for the non-linear operation of one of the first galvano scanner and the second galvano scanner according to the scanning conditions. It is possible to cope with speeding up.

  In addition, in the above embodiment or the modified example, the case where the optical scanner 42 is configured by the galvano scanner has been described, but the configuration according to the embodiment or the modified example is not limited to this. For example, the optical scanner 42 may be constituted by a resonant mirror.

[effect]
An ophthalmologic apparatus according to an embodiment and a control method thereof will be described.

  An ophthalmologic apparatus (1) according to some embodiments includes a data acquisition unit (an optical system in a path from an interference optical system included in the OCT unit 100 to the objective lens 22, or an optical system and an image forming unit 231); A storage unit (212) and a correction unit (232) are included. The data acquisition unit includes an optical scanner (42) capable of deflecting light within a predetermined deflection angle range, and uses the measurement light (LS) deflected in a predetermined deflection direction by the optical scanner to the subject's eye (E). By executing optical coherence tomography, a first data set group in the A-scan direction is obtained. The storage unit stores correction data (212A) corresponding to the operation characteristics (deflection angle versus time characteristics) of the optical scanner. The correction unit generates a second data set group by correcting at least a part of the first data set group based on the correction data stored in the storage unit.

  According to such a configuration, at least a part of the plurality of first data sets in the A-scan direction acquired by performing the OCT using the optical scanner is converted into correction data corresponding to the operating characteristics of the optical scanner. Since the second data set group is generated by performing correction based on the above, it is possible to acquire a data set group in the A-scan direction in consideration of the operation characteristics of the optical scanner. For example, it becomes possible to generate a data set group at uniformly arranged scanning positions from a data set group acquired at scanning positions unevenly distributed due to the nonlinear operation of the optical scanner. Further, for example, it is possible to generate a data set group obtained at a high density only for a desired part from a data set group obtained by the linear operation of the optical scanner. As a result, it becomes possible to use a part of the nonlinear operation range of the optical scanner, so that it is possible to cope with an increase in the deflection speed of the optical scanner, and to perform OCT measurement with high accuracy at a wide angle. become able to.

  In the ophthalmologic apparatus according to some embodiments, the correction unit may be configured to convert the first data set into a data set acquired based on the measurement light deflected by the optical scanner at substantially equal intervals in the deflection angle range in the deflection angle range. Thus, one or more data sets corresponding to at least a part of the deflection angle range in the first data set group are corrected based on the correction data.

  According to such a configuration, it is possible to generate a data set group at uniformly arranged scanning positions from a data set group acquired at scanning positions unevenly distributed due to the nonlinear operation of the optical scanner. Accordingly, even when the deflection speed (scanning frequency) of the optical scanner is increased, it is possible to form an image using the non-linear operation range, so that it is possible to cope with an increase in the deflection speed.

  In the ophthalmologic apparatus according to some embodiments, the optical scanner includes a mirror that reflects the measurement light, and reciprocally swings the mirror in a swing direction corresponding to the deflection direction, so that the measurement light is emitted in a deflection angle range. At least a part of the deflection angle range is a first deflection angle (rs) at which the mirror starts to swing in the swing direction or a second deflection angle at which the mirror swing in the swing direction ends. (Re).

  According to such a configuration, an image can be formed using the non-linear operation range of an optical scanner such as a galvano scanner, so that it is possible to cope with an increase in the deflection speed.

  In the ophthalmologic apparatus according to some embodiments, the correction unit includes an extraction unit (232A) that extracts one or more data sets from at least a part of the first data set group, and at least a part of the first data set group. With one or more data sets.

  According to such a configuration, it is possible to form an image using the non-linear operation range of the optical scanner by a simple extraction process for the data set group, so that it is possible to cope with an increase in the deflection speed. .

  In the ophthalmologic apparatus according to some embodiments, the correction unit includes an interpolation unit (232B) that calculates an interpolation data set by interpolating at least a part of the first data set group, and includes at least one of the first data set group. Is replaced with the interpolation data set calculated by the interpolation unit.

  According to such a configuration, it is possible to form an image using the non-linear operation range of the optical scanner by a simple interpolation process on the data set group, so that it is possible to cope with an increase in the deflection speed. .

  In the ophthalmologic apparatus according to some embodiments, the correction unit performs positioning using the positioning unit (232C) that positions at least a part of the first data set group in the A-scan direction and the positioning unit. An interpolation unit (232D) for calculating an interpolation data set by interpolating at least a part of the first data set group, and replacing at least a part of the first data set group with the interpolation data set calculated by the interpolation unit. .

  According to such a configuration, it is possible to form an image using the non-linear operation range of the optical scanner by a simple alignment process and an interpolation process with respect to the data set group. become able to.

  In the ophthalmologic apparatus according to some embodiments, the correction unit adds a new data set to the first data set group.

  According to such a configuration, it is possible to form an image using the non-linear operation range of the optical scanner by a simple additional process for the data set group, so that it is possible to cope with an increase in the deflection speed. .

  In the ophthalmologic apparatus according to some embodiments, the new data set is generated based on at least a part of the first data set group.

  According to such a configuration, a new data set is obtained based on at least a part of the first data set group, and the obtained new data set is added. Additional processing can be performed.

  In the ophthalmologic apparatus according to some embodiments, the optical scanner includes a first scanner (first galvano scanner) that deflects measurement light in a first deflection direction in a first deflection angle range, and a measurement device that is deflected by the first scanner. A second scanner (second galvano scanner) for deflecting the light in the second deflecting direction toward the subject's eye in the second deflecting angle range, wherein the correcting unit performs a first correction corresponding to an operation characteristic of the first scanner. Correction processing for at least a part of the first data set group based on the data (2121) and correction processing for at least a part of the first data set group based on the second correction data (2122) corresponding to the operation characteristics of the second scanner It can be executed by switching any of the above.

  According to such a configuration, the data set group can be corrected for the non-linear operation of one of the first scanner and the second scanner in accordance with the scanning conditions, so that the OCT performed in various scanning modes can be performed. It is possible to cope with an increase in the deflection speed in measurement.

  In the ophthalmologic apparatus according to some embodiments, the storage unit stores a plurality of correction data corresponding to a plurality of scan conditions in which at least one of the deflection angle range and the deflection speed of the optical scanner is different, and the correction unit stores the scan condition. And at least a part of the first data set group is corrected based on the correction data stored in the storage unit.

  According to such a configuration, the second data set group can be generated by correcting at least a part of the first data set group based on the correction data corresponding to the scan condition. However, it becomes possible to obtain a data set group in consideration of the operation characteristics of the optical scanner.

  An ophthalmologic apparatus according to some embodiments includes an image forming unit (231) that forms a tomographic image of the subject's eye based on the second data set group generated by the correction unit.

  According to such a configuration, a new data set group can be generated by correcting the data set group of the reflection intensity profile data in the A-scan direction according to the operation characteristics of the optical scanner.

  Some embodiments are a method for controlling an ophthalmic device (1) that includes an optical scanner (42) capable of deflecting light within a predetermined deflection angle range. The method for controlling the ophthalmologic apparatus includes a data acquisition step and a correction step. The data acquisition step includes performing a first coherence tomography on the subject's eye (E) using the measurement light (LS) deflected in a predetermined deflection direction by the optical scanner to thereby obtain a first data set group in the A-scan direction. To get. The correction step generates a second data set group by correcting at least a part of the first data set group based on correction data (212A) corresponding to the operation characteristics (deflection angle versus time characteristics) of the optical scanner.

  According to such a method, at least a part of the plurality of first data sets in the A-scan direction obtained by performing the OCT using the optical scanner is converted into correction data corresponding to the operating characteristics of the optical scanner. Since the second data set group is generated by performing correction based on the above, it is possible to acquire a data set group in the A-scan direction in consideration of the operation characteristics of the optical scanner. For example, it becomes possible to generate a data set group at uniformly arranged scanning positions from a data set group acquired at scanning positions unevenly distributed due to the nonlinear operation of the optical scanner. Further, for example, it is possible to generate a data set group obtained at a high density only for a desired part from a data set group obtained by the linear operation of the optical scanner. As a result, it becomes possible to use a part of the nonlinear operation range of the optical scanner, so that it is possible to cope with an increase in the deflection speed of the optical scanner, and to perform OCT measurement with high accuracy at a wide angle. become able to.

  In the control method of the ophthalmologic apparatus according to some embodiments, the correction step includes the step of: obtaining the first data set based on the measurement light deflected by the optical scanner at substantially equal intervals in the deflection angle range. One or more data sets corresponding to at least a part of the deflection angle range in the first data set group are corrected based on the correction data so as to form a set group.

  According to such a method, it is possible to generate a group of data sets at uniformly arranged scanning positions from a group of data sets acquired at scanning positions unevenly distributed by the nonlinear operation of the optical scanner. Accordingly, even when the deflection speed (scanning frequency) of the optical scanner is increased, it is possible to form an image using the non-linear operation range, so that it is possible to cope with an increase in the deflection speed.

  In the control method of the ophthalmologic apparatus according to some embodiments, the optical scanner includes a mirror that reflects the measurement light, and swings the mirror reciprocally in a swinging direction corresponding to the deflection direction, so that the mirror can be rotated in a deflection angle range. The measurement light is deflected, and at least a part of the deflection angle range is a first deflection angle (rs) at which the mirror starts to swing in the swing direction or a second deflection angle at which the mirror swing in the swing direction ends. Includes two deflection angles (re).

  According to such a method, it is possible to form an image using the non-linear operation range of an optical scanner such as a galvano scanner, so that it is possible to cope with an increase in the deflection speed.

  In the control method of the ophthalmologic apparatus according to some embodiments, the optical scanner deflects the measuring light in the first deflecting direction in the first deflecting angle range and the first scanner (first galvano scanner). A second scanner (second galvano scanner) for deflecting the measured measurement light in the second deflecting direction toward the subject's eye in the second deflecting angle range, and the correction step corresponds to the operating characteristics of the first scanner. Correction processing for at least a part of the first data set group based on the first correction data (2121), and at least part of the first data set group based on the second correction data (2122) corresponding to the operation characteristics of the second scanner Can be executed by switching any of the correction processes for.

  According to such a method, the data set group can be corrected for the non-linear operation of one of the first scanner and the second scanner according to the scanning conditions, so that the OCT performed in various scanning modes can be performed. It is possible to cope with an increase in the deflection speed in measurement.

  A control method of an ophthalmologic apparatus according to some embodiments includes an image forming step of forming a tomographic image of an eye to be inspected based on the second data set group generated in the correction step.

  According to such a method, a new data set group can be generated by correcting the data set group of the reflection intensity profile data in the A-scan direction according to the operation characteristics of the optical scanner.

<Others>
The above-described embodiment or its modification is merely an example for embodying the present invention. Those who intend to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the present invention.

  In some embodiments, a program for causing a computer to execute the above-described method for controlling an ophthalmologic apparatus is provided. Such a program can be stored on any computer-readable recording medium. Examples of the recording medium include a semiconductor memory, an optical disk, a magneto-optical disk (CD-ROM / DVD-RAM / DVD-ROM / MO, etc.), a 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 a LAN.

Reference Signs List 1 ophthalmic apparatus 2 fundus camera unit 42 optical scanner 100 OCT unit 200 arithmetic control unit 210 control unit 211 main control unit 212 storage unit 212A correction data 230 data processing unit 231 image forming unit 232 correction unit E Eye to be inspected LS measurement light

Claims (16)

The optical scanner includes an optical scanner capable of deflecting light in a predetermined deflection angle range, and performs optical coherence tomography on the subject's eye using measurement light deflected in a predetermined deflection direction by the optical scanner, thereby performing an A scan direction. A data acquisition unit for acquiring a first data set group of
A storage unit that stores correction data corresponding to the operation characteristics of the optical scanner,
A correction unit that generates a second data set group by correcting at least a part of the first data set group based on the correction data stored in the storage unit;
Ophthalmic equipment including. The correction unit is configured to set the first data set group so that the first data set group is a data set group acquired based on the measurement light deflected by the optical scanner at substantially equal intervals in the deflection angle range. The ophthalmologic apparatus according to claim 1, wherein at least one data set corresponding to at least a part of the deflection angle range in a data set group is corrected based on the correction data. The optical scanner includes a mirror that reflects the measurement light, and deflects the measurement light in the deflection angle range by reciprocatingly swinging the mirror in a swing direction corresponding to the deflection direction,
At least a part of the deflection angle range is a first deflection angle at which the mirror starts to swing in the swing direction or a second deflection angle at which the mirror swing in the swing direction ends. The ophthalmic apparatus according to claim 2, comprising: The correction unit includes an extraction unit that extracts one or more data sets from at least a part of the first data set group, and replaces at least a part of the first data set group with the one or more data sets. The ophthalmologic apparatus according to any one of claims 1 to 3, wherein The correction unit includes an interpolation unit that calculates an interpolation data set by interpolating at least a part of the first data set group, and interpolates the interpolation data calculated by the interpolation unit at least a part of the first data set group. The ophthalmologic apparatus according to any one of claims 1 to 3, wherein the ophthalmologic apparatus is replaced with a set. The correction unit,
An alignment unit that aligns at least a part of the first data set group in the A-scan direction;
An interpolation unit that calculates an interpolation data set by interpolating at least a part of the first data set group that has been aligned by the alignment unit;
Including
The ophthalmologic apparatus according to any one of claims 1 to 3, wherein at least a part of the first data set group is replaced with an interpolation data set calculated by the interpolation unit. The ophthalmologic apparatus according to any one of claims 1 to 3, wherein the correction unit adds a new data set to the first data set group. The ophthalmologic apparatus according to claim 7, wherein the new data set is generated based on at least a part of the first data set group. The optical scanner is
A first scanner that deflects the measurement light in a first deflection direction in a first deflection angle range;
A second scanner that deflects the measurement light deflected by the first scanner toward the subject's eye in a second deflection angle range in a second deflection direction;
Including
The correction unit corrects at least a part of the first data set group based on first correction data corresponding to an operation characteristic of the first scanner, and a second correction data corresponding to an operation characteristic of the second scanner. The ophthalmologic apparatus according to any one of claims 1 to 8, wherein any one of the correction processes for at least a part of the first data set group based on the correction is switched and executed. The storage unit stores a plurality of correction data corresponding to a plurality of scan conditions different in at least one of the deflection angle range and the deflection speed of the optical scanner,
The said correction part corrects at least one part of the said 1st data set group based on the correction data memorize | stored in the said memory | storage part corresponding to the said scanning condition. The Claims 1-9 characterized by the above-mentioned. The ophthalmic apparatus according to any one of the preceding claims. 11. The image forming apparatus according to claim 1, further comprising: an image forming unit configured to form a tomographic image of the eye to be inspected based on the second data set group generated by the correction unit. 12. Ophthalmic equipment. A method for controlling an ophthalmic apparatus including an optical scanner capable of deflecting light in a predetermined deflection angle range,
A data acquisition step of acquiring a first data set group in the A-scan direction by performing optical coherence tomography on the subject's eye using measurement light deflected in a predetermined deflection direction by the optical scanner;
A correction step of generating a second data set group by correcting at least a part of the first data set group based on correction data corresponding to an operation characteristic of the optical scanner;
A method for controlling an ophthalmic apparatus including: The correcting step is such that the first data set group is the first data set group acquired based on the measurement light deflected by the optical scanner at substantially equal intervals in the deflection angle range in the deflection angle range. The method according to claim 12, wherein one or more data sets corresponding to at least a part of the deflection angle range in a data set group are corrected based on the correction data. The optical scanner includes a mirror that reflects the measurement light, and deflects the measurement light in the deflection angle range by reciprocatingly swinging the mirror in a swing direction corresponding to the deflection direction,
At least a part of the deflection angle range is a first deflection angle at which the mirror starts to swing in the swing direction or a second deflection angle at which the mirror swing in the swing direction ends. The method for controlling an ophthalmologic apparatus according to claim 13, comprising: The optical scanner is
A first scanner that deflects the measurement light in a first deflection direction in a first deflection angle range;
A second scanner that deflects the measurement light deflected by the first scanner toward the subject's eye in a second deflection angle range in a second deflection direction;
Including
The correction step includes: a correction process for at least a part of the first data set group based on first correction data corresponding to an operation characteristic of the first scanner; and a second correction data corresponding to an operation characteristic of the second scanner. The method of controlling an ophthalmologic apparatus according to any one of claims 12 to 14, wherein any one of the correction processes for at least a part of the first data set group based on the correction is switched and executed. . An image forming step of forming a tomographic image of the subject's eye based on the second data set group generated in the correction step. The method according to any one of claims 12 to 15, wherein: A method for controlling an ophthalmologic apparatus.

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