JP2020025724A - Ophthalmologic apparatus and control method of the same - Google Patents

Abstract

To provide a new technique for reducing a burden on an examiner or a subject when performing OCT measurement.SOLUTION: The ophthalmologic apparatus includes an interference optical system, an operation unit, and a control unit. The interference optical system is configured to change the optical path length difference between a measurement optical path and a reference optical path, divides light from a light source into the measurement light and the reference light, irradiates an eye to be examined with the measurement light via the measurement optical path, and detects interference light between the return light from the eye to be examined and the reference light via the reference light path. The operation unit is used for specifying a reference position in a depth direction with respect to a B-scan for the eye to be examined. The control unit controls the interference optical system in each B-scan so that an image based on a detection result of the interference light is arranged at a reference position, and thereby changes an optical path length difference, so that a plurality of B-scans are executed for the eye to be examined.SELECTED DRAWING: Figure 3

Description

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

  In recent years, OCT (Optical Coherence Tomography) for imaging a surface morphology and an internal morphology of an object using light interference has attracted attention. Since OCT does not have invasiveness to a human body like X-ray CT, it is expected to be developed particularly in the medical field and the biological field. For example, in the field of ophthalmology, apparatuses for imaging the fundus and cornea have been put to practical use.

  In an ophthalmologic apparatus using OCT, the difference between the optical path length of the measurement light and the optical path length of the reference light is adjusted so that the target part of the eye to be examined is drawn at a suitable position in the imaging range by the OCT measurement.

  For example, Patent Literature 1 discloses an ophthalmologic apparatus that executes an automatic process (auto Z) for searching for a suitable optical path length difference so that a region of interest is drawn in an imaging range by OCT measurement. In this ophthalmologic apparatus, the attention site is drawn at a predetermined z position (depth position) of the imaging range by executing an automatic process (Z lock) for maintaining a suitable drawing position obtained by the auto Z. The control of the optical path length difference is performed so that the state of being maintained is maintained.

JP-A-2006-041221

  However, in the prior art, the z position maintained by the z lock is fixed. As a result, if the measurement range obtained by the OCT measurement becomes wider in the xy direction or becomes deeper in the z direction, the attention site may be drawn at the end of the imaging range or deviate from the imaging range depending on the curvature of the eyeball.

  In particular, when performing OCT measurement in a wide range for the intense myopic eye, the OCT measurement may be interrupted at the upper end or the lower end of the imaging range, or may be folded back and displayed. Therefore, it is necessary for the examiner to keep an eye on the state of the OCT measurement, and the burden on the examiner who performs the OCT measurement becomes heavy. Alternatively, it is necessary to confirm the measurement result and perform re-measurement as necessary, which increases the burden on the subject who receives the OCT measurement.

  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 reducing a burden on an examiner or a subject when performing OCT measurement.

  A first aspect of some embodiments is configured to be able to change an optical path length difference between a measurement optical path and a reference optical path, divides light from a light source into measurement light and reference light, and passes through the measurement optical path. An interference optical system that irradiates the measurement light to the eye to be inspected and detects interference light between the return light from the eye to be inspected and the reference light via the reference light path, and a depth direction with respect to the B scan for the eye to be inspected. An operation unit for designating a reference position of the light source, and controlling the interference optical system in each B scan to change the optical path length difference so that an image based on the detection result of the interference light is arranged at the reference position. A control unit configured to execute a plurality of B scans on the subject's eye.

  In a second aspect of some embodiments, in the first aspect, the plurality of B scans include a first B scan, a second B scan, and a third B scan, and A first reference position is set for the B scan using the operation unit, a second reference position is set for the second B scan using the operation unit, and the third B scan is set. , A third reference position specified based on the first reference position and the second reference position is set, and the control unit controls the interference optical system to control the first B scan. , The second B-scan and the third B-scan are executed.

  In a third aspect of some embodiments, in the first aspect, the plurality of B scans include a first B scan, a second B scan, and a third B scan, and A first reference position is set for the B scan using the operation unit, and a second reference position shifted in the depth direction with respect to the first reference position is set for the second B scan. And a third reference position specified based on the first reference position and the second reference position is set for the third B scan, and the control unit controls the interference optical system Thus, the first B scan, the second B scan, and the third B scan are executed.

  In a fourth aspect of some embodiments, in the third aspect, the second reference position is set according to a distance between a scan position of the first B scan and a scan position of the second B scan. You.

  In a fifth aspect of some embodiments, in the third aspect or the fourth aspect, the second reference position is a three-dimensional image including the second B-scan with respect to a three-dimensional scan range including the first B-scan. Set according to the scan range.

  In a sixth aspect of some embodiments, in any of the third to fifth aspects, the second reference position is set according to a refractive index of the eye to be inspected.

  In a seventh aspect of some embodiments, in any one of the third to sixth aspects, the second reference position is shifted by a first shift with respect to the first reference position when the subject's eye is a strongly myopic eye. When the eye to be inspected is not a myopic eye, it is set to a position shifted by a second shift value smaller than the first shift value with respect to the first reference position.

  In an eighth aspect of some embodiments, according to any of the third to seventh aspects, the second reference position is selected from a plurality of predetermined shift values with respect to the first reference position. Is set to shift by the shifted value.

  In a ninth aspect of some embodiments, in any of the third to eighth aspects, the second reference position is set based on an image based on a result of detecting the interference light.

  In a tenth aspect of some embodiments, in any one of the third to ninth aspects, the second reference position is obtained by a scan in a direction intersecting a scan direction of the first B scan. It is set based on the detection result of the interference light.

  In an eleventh aspect of some embodiments, in any one of the second aspect to the tenth aspect, the control unit may control the first B-scan in a direction intersecting a scan direction of the first B-scan, The third B scan and the second B scan are executed in this order.

  A twelfth aspect of some embodiments is configured to be capable of changing an optical path length difference between a measurement optical path and a reference optical path, splits light from a light source into measurement light and reference light, and passes through the measurement optical path. An interference optical system that irradiates the measurement light to the eye to be inspected and detects interference light between the return light from the eye to be inspected and the reference light via the reference light path, and a depth direction with respect to the B scan for the eye to be inspected. And a control unit for specifying a reference position of the ophthalmologic apparatus. A control method of the ophthalmologic apparatus, wherein a reference position setting step of setting the reference position specified by using the operation unit for a plurality of B scans with respect to the subject's eye; and an image based on a result of detecting the interference light, Controlling the interference optical system in each B scan so as to be arranged at a reference position to change the optical path length difference, thereby causing the subject's eye to execute a plurality of B scans.

  In a thirteenth aspect of some embodiments, in the twelfth aspect, the reference position setting step includes a step of setting a first reference position designated using the operation unit for a first B scan. Setting a second reference position specified by using the operation unit for a second B scan, and setting the first reference position and the second reference position for a third B scan. Setting the third reference position specified based on the first and second B-scans, the second B-scan, and the second B-scan by controlling the interference optical system. 3 is executed.

  In a fourteenth aspect of some embodiments, in the twelfth aspect, in the twelfth aspect, the reference position setting step includes: setting a first reference position specified using the operation unit for a first B scan. Setting a second reference position shifted in the depth direction with respect to the first reference position for a second B scan, and setting the first reference position and the second reference position for a third B scan. Setting a third reference position specified based on a second reference position, and wherein the control step controls the interference optical system to control the first B scan and the second B position. Scan and the third B scan are executed.

  According to the present invention, it is possible to reduce the burden on the examiner or the subject when performing the OCT measurement.

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. 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 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. 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. 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. 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. 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.

  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 can form a tomographic image, a front image, and a three-dimensional image of an eye to be inspected using OCT. 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, any 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. In addition, the ophthalmic treatment device included in the ophthalmologic device of some embodiments is, for example, 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. Although the swept source OCT is applied to this OCT apparatus, the type of OCT is not limited to this, and other types of OCT (spectral domain OCT, time domain OCT, amphus OCT, etc.) may be applied. Further, the configuration according to the following embodiment can be incorporated in a single OCT device.

  In the following, a case where an image of the fundus is acquired will be described in detail, but the part of the eye to be photographed is not limited to the fundus. For example, the configuration according to this embodiment can be applied to an apparatus for performing OCT measurement of an anterior ocular segment such as a cornea. Further, the configuration of this embodiment can be applied to an apparatus that can perform OCT measurement of both the fundus and the anterior segment. As an example of this case, a configuration in which an attachment for anterior ocular segment imaging (an objective lens, a front lens, or the like) is added to an apparatus for fundus imaging described below can be employed.

<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 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 reflecting surface of the reflecting rod 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. The OCT optical path (the optical path of the measurement light) includes a collimator lens unit 40, an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, a mirror 44, in order from the OCT unit 100 side to the dichroic mirror 46 side. 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 disposed at a position optically conjugate with the pupil of the eye E to be examined. The optical scanner 42 deflects the measurement light LS passing through the OCT optical path. The optical scanner 42 is, for example, a galvano scanner capable of two-dimensional scanning.

  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 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]
As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing swept source OCT. This optical system includes an interference optical system. This interference optical system has a function of splitting light from a wavelength variable light source (wavelength sweep type light source) into measurement light and reference light, and a function of returning measurement light from the eye E to be examined and reference light passing through a reference optical path. And a function of generating interference light by superimposing the interference light, and a function of detecting the interference light. The detection result (detection signal) of the interference light obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic and control unit 200.

  The light source unit 101 includes, for example, a near-infrared tunable laser that changes the wavelength of emitted light at high speed. 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 light L0 whose polarization state has been adjusted is guided to the fiber coupler 105 by the optical fiber 104, and is split into the measurement light LS and the reference light LR.

  The reference light LR is guided by an optical fiber 110 to a collimator 111, converted into a parallel light flux, and guided to a corner cube 114 via an optical path length correction member 112 and a dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR with the optical path length of the measurement light LS. The dispersion compensating member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The corner cube 114 is movable in the direction of incidence of the reference light LR, thereby changing the optical path length of the reference light LR.

  The reference light LR that has passed through the corner cube 114 passes through the dispersion compensating member 113 and the optical path length correcting member 112, is converted from a parallel light beam into a focused light beam by the collimator 116, and enters the optical fiber 117. The reference light LR that has entered the optical fiber 117 is guided to the polarization controller 118 to adjust its polarization state, is guided to the attenuator 120 by the optical fiber 119, adjusts the light amount, and is guided to the fiber coupler 122 by the optical fiber 121. I will

  On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber 127 and converted into a parallel light flux by the collimator lens unit 40, and is changed into an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, and a mirror 44. And a relay lens 45. The measurement light LS that has passed through the relay lens 45 is reflected by the dichroic mirror 46, refracted by the objective lens 22, and enters the eye E to be inspected. The measurement light LS is scattered and reflected at various depth positions of the eye E. The return light of the measurement light LS from the subject's eye E 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 at a predetermined split ratio (for example, 1: 1). The pair of interference lights LC is guided to the detector 125 through the optical fibers 123 and 124, respectively.

  The detector 125 is, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between a pair of detection results obtained by the photodetectors. The detector 125 sends this output (detection 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 within a predetermined wavelength range by the variable wavelength 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 signal input from the detector 125 based on the clock KC. The DAQ 130 sends a sampling result of the detection signal from the detector 125 to the arithmetic and control unit 200.

  In this example, 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 for changing the length of the optical path (reference optical path, reference arm) of the reference light LR. Corner cube 114 is provided. However, only one of the optical path length changing unit 41 and the corner cube 114 may be provided. It is also possible to change the difference between the measured optical path length and the reference optical path length by using other optical members.

[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 reflection bar 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 OCT unit 100, the arithmetic and control unit 200 performs operation control of the light source unit 101, operation control of the polarization controllers 103 and 118, operation control of the attenuator 120, operation control of the detector 125, operation control of the DAQ 130, and the like. .

  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)
3 and 4 show a configuration example of a control system of the ophthalmologic apparatus 1. FIG. 3 and 4, some of the components included in the ophthalmologic apparatus 1 are omitted. The control unit 210, the image forming unit 220, and the data processing unit 230 are provided in, for example, the arithmetic and control unit 200.

(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 optical path length changing unit 41 of the retinal camera unit 2, the optical scanner 42, the photographing focusing lens 31 (focus driving unit 31A), the focusing optical system 60, and the OCT focusing lens 43 (focusing). The controller 43A controls the image sensors 35 and 38, the LCD 39, the entire optical system (moving mechanism 150), and the like. Further, the main control unit 211 controls the light source unit 101, the corner cube 114 (reference driving unit 114A), 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 300 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. 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 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, optical path length difference 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 the above-described 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.

  On the other hand, the focus fine adjustment is performed based on the interference sensitivity of the OCT measurement. For example, by performing OCT measurement of the eye E and acquiring an interference signal to monitor the interference intensity (interference sensitivity), the position of the OCT focusing lens 43 that maximizes the interference intensity is obtained, and the position is determined. By moving the OCT focusing lens 43, fine focus adjustment can be performed.

  In the optical path length difference adjustment, control is performed so that the target portion of the eye E to be examined is drawn at a predetermined z position in the frame of the OCT image. This control is performed for at least one of the optical path length changing unit 41 and the reference driving unit 114A. Thereby, the optical path length difference between the measurement optical path and the reference optical path is adjusted. As a target portion serving as a reference for adjusting the optical path length difference, a portion exhibiting a characteristic luminance in the OCT image (or a portion exhibiting a characteristic reflection intensity in the reflection intensity profile) is set in advance. As a specific example, the OCT measurement of the fundus can be set based on the retinal pigment epithelium layer, and the OCT measurement of the anterior eye can be set based on the corneal surface. Such automatic processing for searching for a suitable optical path length difference is called auto Z.

  The optical path length difference adjustment is not limited to the auto Z. For example, it is possible to execute an automatic process for maintaining a suitable image rendering position achieved by Auto Z. Such a process is called Z lock. In the Z lock, for example, at least one of the optical path length changing unit 41 and the reference drive unit 114A so that a state in which a target portion serving as a reference for adjusting the optical path length difference is drawn at a predetermined z position in the frame is maintained. Is performed.

  In this embodiment, the reference position (z position) of the Z lock can be designated. That is, the optical path length difference adjustment is performed so that the state where the target portion of the subject's eye is drawn at the specified reference position (or the Z lock position specified based on the reference position) is maintained. In some embodiments, a reference position of the Z lock is designated using the operation unit 240B with respect to the OCT image displayed on the display unit 240A.

  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, eye information of an examinee, 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 various programs and data for operating the ophthalmologic apparatus 1.

(Image forming unit)
The image forming unit 220 forms an OCT image 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 220 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 type optical coherence tomography. In the case of another type of OCT apparatus, the image forming unit 220 executes a known process according to the type.

  The image forming unit 220 includes, for example, the above-described circuit board. In this specification, “image data” and “image” based on the image data may be identified.

(Data processing unit)
The data processing unit 230 processes data acquired by imaging of the eye E and OCT measurement. For example, the data processing unit 230 performs various image processing and analysis processing on the image formed by the image forming unit 220. For example, the data processing unit 230 executes various correction processes such as 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, and 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.

  The data processing unit 230 includes a part specifying unit 231, a Z lock position obtaining unit 233, and an optical path length difference change amount obtaining unit 234.

  The part specifying unit 231 specifies a predetermined part of the eye E by analyzing the interference light detection result obtained by the OCT unit 100, and specifies the z position (depth position) of the specified part. In this embodiment, the part specifying unit 231 analyzes the OCT image formed by the image forming unit 220 based on the detection result of the interference light, and specifies the z position of the predetermined part. As the predetermined part, a part having high interference intensity in the eye E to be examined is desirable. In some embodiments, the predetermined site is a retinal pigment epithelium layer in the fundus oculi Ef. In some embodiments, the predetermined site is the anterior cornea in the anterior segment.

  The Z lock position acquisition unit 233 acquires (specifies) a Z lock position (z position) for a B scan in a scan area set in advance. As described above, in this embodiment, the reference position of the Z lock can be specified. When a plurality of B scans are performed in the scan area, a Z lock position of another B scan is acquired based on a Z lock reference position designated for at least one B scan. In some embodiments, when the Z-lock reference position z0 is specified, the Z-lock position acquisition unit 233 determines the Z-lock positions (z0 + Δz) and (z0−Δz) for any of the other B scans. Get at least one. The remaining Z lock positions for the B scan are specified based on the designated Z lock reference position or the Z lock position acquired by the Z lock position acquisition unit 233. The Z lock position is specified according to linear interpolation, a quadratic or higher spline curve, or a predetermined function.

  In some embodiments, Δz is a fixed value. In some embodiments, Δz is a scan position, a scan range, a refractive index of the eye E, information indicating whether the eye E is strong myopia, an OCT image (B scan image) of the eye E, The setting is made in accordance with at least one of the B-scan images of the eye E obtained by the B-scan in a direction intersecting with the B-scan. For example, control information in which Δz is associated with a scan position or the like is stored in advance in, for example, the Z lock position acquisition unit 233 or the storage unit 212. The Z lock position acquisition unit 233 acquires the Z lock position by referring to the control information.

  The optical path length difference change amount acquiring section 234 specifies the amount of change in the difference between the optical path length of the measurement optical path and the optical path length of the reference optical path in order to control the auto Z or the Z lock.

  When performing the auto Z, the ophthalmologic apparatus 1 controls the optical system to execute the OCT measurement of the eye E (for example, the fundus oculi Ef). In the OCT measurement, for example, the eye E is repeatedly scanned at a predetermined frequency. That is, the OCT measurement with the same scan pattern is repeatedly performed on the eye E to be examined on which the fixation target is presented. In some embodiments, substantially the same cross section of the eye E is scanned. The optical path length change amount acquisition section 234 analyzes the detection result (reflection intensity profile, OCT image, etc.) of the interference light LC repeatedly acquired by the OCT measurement, and thereby forms an image (an image of the fundus oculi Ef) based on the detection result. ) Is obtained at the specific position of the frame.

  In some embodiments, the optical path length difference change amount acquisition unit 234 obtains the difference between the z position and the Z lock position of the predetermined part specified by the part specifying unit 231 and determines the optical path length corresponding to the obtained difference. Get the change amount of the difference.

  The information acquired by the optical path length difference change amount acquisition unit 234 is not limited to the change amount itself of the optical path length difference (optical path length). For example, the control contents (such as the number of transmission pulses) of the optical path length changing unit 41 or the reference driving unit 114A, and information obtained during the process of acquiring the amount of change (eg, the amount of displacement of the image in the z direction within the frame, etc.) ), The information may be substantially equivalent to the change amount of the optical path length difference.

  In some embodiments, the control information in which the change amount of the optical path length difference (or the control information corresponding to the change amount) is previously associated with the optical path corresponding to the difference between the z-lock position and the z position of the predetermined portion. It is stored in the length difference change amount acquisition unit 234 (or the storage unit 212). The optical path length difference change amount acquisition unit 234 acquires the change amount of the optical path length difference to be changed by referring to the control information.

  The main control unit 211 executes the auto-Z by controlling at least one of the optical path length changing unit 41 and the reference drive unit 114A based on the change amount acquired by the optical path length difference change amount acquiring unit 234. Since the control of the auto Z is the same as that of JP-A-2006-041221, a detailed description is omitted.

  In the Z lock, as in the case of the auto Z, the cross section of the eye E (for example, the fundus oculi Ef) is repeatedly scanned at a predetermined frequency. In some embodiments, substantially the same cross section of the eye E is scanned. Further, the optical path length difference change amount acquisition unit 234 analyzes the detection result of the interference light LC repeatedly acquired by the OCT measurement, and thereby obtains the optical path length difference for arranging an image of a predetermined part at the Z lock position. Get the change amount.

  In some embodiments, the optical path length difference change amount acquisition unit 234 obtains the difference between the Z lock position set for the immediately preceding scan and the Z lock position set for the scan. The change amount of the optical path length difference corresponding to the difference is obtained. In some embodiments, the optical path length difference change amount obtaining unit 234 obtains a difference between the z position and the Z lock position of the predetermined part specified by the part specifying unit 231 for each scan, and corresponds to the obtained difference. The change amount of the changed optical path length difference is obtained.

  The main control unit 211 executes the Z lock by controlling at least one of the optical path length changing unit 41 and the reference driving unit 114A based on the change amount obtained by the optical path length difference change amount obtaining unit 234. The control of such a Z lock is the same as in JP-A-2006-041221, and a detailed description thereof will be omitted.

  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.

[Scanning of measurement light and OCT image]
Here, the scan of the measurement light LS and the OCT image will be described.

  The scanning mode of the measurement light LS by the ophthalmologic apparatus 1 includes, for example, a horizontal scan, a vertical scan, a cross scan, a radiation scan, a circular scan, a concentric scan, and a spiral (spiral) scan. These scan modes are selectively used as appropriate in consideration of the observation site of the eye E to be inspected, the analysis target (such as the retinal thickness), the time required for the scan, the precision of the scan, and the like.

  The horizontal scan is to scan a scan portion in the horizontal direction (x direction) with the measurement light LS. The horizontal scan includes a mode in which the measurement light LS is scanned along a plurality of horizontally extending scan lines arranged in a vertical direction (y direction). In this embodiment, the scan line interval can be set arbitrarily. Further, by sufficiently narrowing the interval between adjacent scan lines, the above-described three-dimensional image can be formed (three-dimensional scan). The same applies to vertical scanning.

  The cross scan scans a scan area with the measurement light LS along a cross-shaped locus composed of two linear locuses (linear locus) orthogonal to each other. In the radial scan, the scanning region is scanned with the measurement light LS along a radial trajectory including a plurality of linear trajectories arranged at predetermined angles. The cross scan is an example of a radiation scan.

  In the circular scan, a scan site is scanned with the measurement light LS along a circular locus. The concentric scan scans a scan region with the measurement light LS along a plurality of circular trajectories arranged concentrically around a predetermined center position. A circle scan is an example of a concentric scan. The helical scan is to scan a scan portion with the measurement light LS along a spiral (spiral) trajectory while gradually reducing (or increasing) the radius of rotation.

  Since the optical scanner 42 is configured to scan the scan area with the measurement light LS in directions orthogonal to each other, the optical scanner 42 can independently scan in the x direction and the y direction with the measurement light LS. Furthermore, by simultaneously controlling the directions of the two galvanometer mirrors included in the optical scanner 42, it is possible to scan with the measurement light LS along an arbitrary trajectory on the xy plane. Thereby, various scan modes as described above can be realized.

  By scanning with the measurement light LS in the above-described manner, a tomographic image on a plane stretched between a direction along a scan line (scanning locus) and a fundus depth direction (z direction) can be obtained. Further, particularly when the interval between scan lines is narrow, the above-described three-dimensional image can be obtained.

  The area on the eye E to be scanned by the measurement light LS as described above, that is, the area on the eye E to be subjected to OCT measurement is referred to as a scan area. The scan area in the three-dimensional scan is a rectangular area in which a plurality of horizontal scans are arranged. The scan area in the concentric scan is a disc-shaped area surrounded by the locus of the circle scan having the largest diameter. The scan area in the radiation scan is a disk-shaped (or polygonal) area connecting both end positions of each scan line.

[Specifying the Z lock position]
For example, the main control unit 211 causes the display unit 240A to display a live image of the image being scanned.

  FIG. 5 shows an example of an image displayed on the display unit 240A. FIG. 5 schematically shows a tomographic image display area DR1 and a front image display area DR2 provided in the display area DR on the display screen of the display unit 240A.

  For example, the main control unit 211 causes the display unit 240A to display a fundus image acquired by controlling the fundus camera unit 2. By performing a predetermined operation on the operation unit 240B, the user can specify a scan area at a desired position in the fundus image displayed on the display unit 240A. The main control unit 211 performs OCT measurement on the designated scan area by controlling the OCT unit 100 and the like. The main control unit 211 causes the image forming unit 220 to form a B-scan image based on the obtained scan result (detection result of interference light), and causes the data processing unit 230 to form a projection image using the scan result. . The main control unit 211 displays the formed B-scan image live in the tomographic image display area DR1. In addition, the main control unit 211 displays the formed projection image in the front image display area DR2.

  In some embodiments, a scan area is specified for the fundus image or the projection image displayed in the front image display area DR2 by operating the operation unit 240B.

(First designation example of Z lock position)
FIG. 6 is a schematic diagram illustrating an example of specifying a Z lock position according to the embodiment.

  For example, for a front image (fundus image or projection image) FI of the fundus oculi Ef of the eye E, a scan area SA and a plurality of B scans B1 to BN performed in the scan area SA (N is an integer of 2 or more) Is set. Each B scan is a line scan. The main control unit 211 sequentially executes a plurality of B scans B1 to BN (N is an integer of 2 or more) on a portion corresponding to the set scan area SA. For convenience of explanation, it is assumed that the scans are executed in the order of B scan B1 to B scan BN. The user designates a Z-lock reference position zj for a B-scan Bj (1 ≦ j ≦ N, j is an integer), which is one of the plurality of B-scans B1 to BN. In some embodiments, the user specifies a Z-lock reference position zj by performing a predetermined operation on the operation unit 240B on a tomographic image obtained by preliminary OCT temporary measurement or the like.

  The main control unit 211 sets the Z lock position zj for the other B scans B1 to B (j-1) and B (j + 1) to BN based on the designated Z lock reference position zj. The optical path length difference change amount acquiring unit 234 acquires an optical path length difference change amount for arranging an image of a predetermined portion at the designated Z-lock position zj. The main control unit 211 sequentially executes the plurality of B scans B1 to BN by controlling at least one of the optical path length changing unit 41 and the reference driving unit 114A based on the acquired change amount in each B scan.

(Second specified example of Z lock position)
FIG. 7 is a schematic diagram illustrating an example of specifying a Z lock position according to the embodiment.

  In this specification example, as in the first specification example, the Z lock reference position zj is specified for the B scan Bj that is one of the plurality of B scans B1 to BN.

  The Z lock position acquisition unit 233 performs a B scan Bi (1 ≦ i <j, i is an integer) and a B scan k (j <k ≦ N, k is an integer) based on the designated Z lock reference position zj. (Zj-Δz) (Δz is a positive number) (or (zj + Δz)). The Z lock position acquisition unit 233 includes a z lock position (zj−Δz) set for the B scan Bi, a z lock position zj set for the B scan Bj, and a z lock position (zj−z) set for the B scan Bk. By performing a predetermined interpolation process (for example, linear interpolation or spline interpolation) based on Δz), the Z lock position for the remaining B scans is obtained. Here, the remaining B scans are B scans B1 to B (i-1), B (i + 1) to B (j-1), B (j + 1) to B (k-1), B (k + 1) to BN It is.

  That is, when the Z lock reference position zj (first reference position) is set for the B scan Bj (first B scan), the reference position zj is set for the B scan Bi (second B scan). On the other hand, the Z-lock position zi (second reference position) shifted in the depth direction is set, and the Z-lock position Zk is determined based on the reference position zj and the Z-lock position zi with respect to the B-scan Bk (third B-scan). (Third reference position) is set.

  The main control unit 211 performs the other B scans B1 to B (i-1) and B (i + 1) to B (j-1) based on the designated Z lock reference position zj and the acquired Z lock position. , B (j + 1) to B (k-1) and B (k + 1) to BN are set with the Z lock position. The optical path length difference change amount acquiring section 234 acquires, for each B scan, an amount of change in the optical path length difference for arranging an image of a predetermined portion at the designated Z lock position. The main control unit 211 sequentially executes the plurality of B scans B1 to BN by controlling at least one of the optical path length changing unit 41 and the reference driving unit 114A based on the acquired change amount in each B scan.

  As described above, Δz is a fixed value or a variable value.

(Third designation example of Z lock position)
FIG. 8 is a schematic diagram illustrating an example of specifying a Z lock position according to the embodiment.

  In the present specification example, the Z lock reference positions zi and zk are respectively specified for any two of the plurality of B scans B1 to BN.

  The Z lock position acquisition unit 233 acquires the Z lock position zj for the B scan Bj with respect to the designated Z lock reference positions zi and zk. The Z lock position acquisition unit 233 performs a predetermined interpolation process (for example, linear interpolation or spline interpolation) based on the z lock position zi set for the B scan Bi and the z lock position zk set for the B scan Bk. By doing so, the Z lock position zj of the B scan Bj is obtained. Similarly, the Z lock position acquisition unit 233 outputs the B scans B1 to B (i-1), B (i + 1) to B (j-1), B (j + 1) to B (k-1), and B (k + 1). To BN for each Z lock position.

  That is, the Z lock reference position zi (first reference position) is set for the B scan Bi (first B scan), and the Z lock reference position zk is set for the B scan Bk (second B scan). (Second reference position) is set. Further, a Z lock position zj (third reference position) specified based on the reference positions zi and zk is set for the B scan Bj (third B scan).

  The main control unit 211 performs the other B scans B1 to B (i−1) and B (i + 1) to B (k−) based on the designated Z lock reference positions zi and zk and the acquired Z lock position. 1) The Z lock position is set for B (k + 1) to BN. The optical path length difference change amount acquiring section 234 acquires, for each B scan, an amount of change in the optical path length difference for arranging an image of a predetermined portion at the designated Z lock position. The main control unit 211 sequentially executes the plurality of B scans B1 to BN by controlling at least one of the optical path length changing unit 41 and the reference driving unit 114A based on the acquired change amount in each B scan.

(Fourth specified example of Z lock position)
FIG. 9 is a schematic diagram illustrating an example of specifying a Z lock position according to the embodiment.

  In this specification example, the Z lock reference positions zi, zj, and zk are respectively specified for any three of the plurality of B scans B1 to BN, that is, B scans Bi, Bj, and Bk. For example, when a plurality of B scans B1 to BN sequentially executed are divided into the first half, the middle half, and the second half, the Z lock reference position zi is designated for the B scan Bi executed in the first half, and executed in the middle half. The Z-lock reference position zj is designated for the B-scan Bj, and the Z-lock reference position zk is designated for the B-scan Bk to be executed later.

  In some embodiments, in the second designation example, when the Z lock reference position zj is designated for the B scan Bj executed in the middle term, the Z lock is not applied to the B scan Bi executed in the first term. The Z-lock position (zj-Δz1) (or (zj + Δz1)) is set as the reference position zi, and the Z-lock position (zj-Δz2) (or) is set as the Z-lock reference position zk for the B scan Bk executed at a later stage. (Zj + Δz2)) may be set. In some embodiments, Δz1 is equal to Δz2. Similarly to Δz, Δz1 and Δz2 may be fixed values or variable values.

  The remaining Z lock positions for the B scan are specified based on the designated Z lock reference position or the Z lock position acquired by the Z lock position acquisition unit 233.

  That is, a Z lock reference position zj (first reference position) is set for the B scan Bj (first B scan), and a Z lock reference position zk is set for the B scan Bk (second B scan). (Second reference position) is set. Further, for any one of the B scans B (j + 1) to B (k-1) (third B scan), the Z lock position (third reference position) specified based on the reference positions zj, zk is Is set.

  The main control unit 211 performs the other B scans B1 to B (i-1) and B (i + 1) to B based on the designated Z lock reference positions zi, zj, zk and the acquired Z lock positions. The Z lock position is set for (j-1), B (j + 1) to B (k-1), and B (k + 1) to BN. The optical path length difference change amount acquiring section 234 acquires, for each B scan, an amount of change in the optical path length difference for arranging an image of a predetermined portion at the designated Z lock position. The main control unit 211 sequentially executes the plurality of B scans B1 to BN by controlling at least one of the optical path length changing unit 41 and the reference driving unit 114A based on the acquired change amount in each B scan.

(Other)
In some embodiments, Δz, Δz1, and Δz2 are, as described above, the scan position, the scan range, the refraction of the eye E, the information indicating whether the eye E is intense myopia, and the eye E Are set in accordance with at least one of the OCT image (B scan image) and the B scan image of the eye E obtained by the B scan in a direction intersecting the B scan.

  The ophthalmologic apparatus 1 according to the embodiment collects scan data of a wider range by providing one or more scan areas in which the scan center position is displaced from the scan center position after the alignment of the apparatus optical system with the eye E is completed. It is possible to

  10 to 12 show an example of a scan range that can be set by the ophthalmologic apparatus 1 according to the embodiment.

  In FIG. 10, scan areas SC1 to SC4 are set to include scan center position O with respect to scan area SC0 defined by scan center position O after the completion of alignment. Each scan area is arranged such that the peripheral area overlaps with the peripheral area of the adjacent scan area. In some embodiments, the scan areas SC0 to SC5 have the same scan area size.

  In FIG. 11, scan areas SC1 to SC4 are set such that peripheral areas of scan area SC0 defined by scan center position O after the completion of alignment overlap. In some embodiments, the scan areas SC0 to SC5 have the same scan area size.

  In FIG. 12, scan areas SC1 to SC4 are set such that peripheral areas of scan area SC0 defined by scan center position O after the completion of alignment overlap, as in FIG. The peripheral area on the right side of the scan area SC3 is arranged so as to overlap the peripheral area on the left side of the scan areas SC2 and SC4. The peripheral area on the left side of the scan area SC1 is arranged so as to overlap the peripheral area on the right side of the scan areas SC2 and SC4. In some embodiments, the scan areas SC0, SC2, SC4 have the same scan area size, the scan areas SC1, SC3 have the same scan area size, and the scan area SC1 has the same size as the scan area SC0. Greater than.

  In some embodiments, the above-described Δz, Δz1, and Δz2 are determined in advance corresponding to the scan area positions (scan position, photographing position, photographing site) illustrated in FIGS.

  In some embodiments, Δz, Δz1, and Δz2 for setting the Z lock position for the B scan in any of the scan areas SC1 to SC4 include the scan position of the predetermined B scan in the scan area SC0 and the B position. This is set according to the distance from the scan position of the scan.

  In some embodiments, Δz, Δz1, Δz2 for setting the Z lock position for the B scan in any of the scan areas SC1 to SC4 are representative positions of the scan area SC0 (for example, the scan center position O). Is set according to the distance between the scan area and the representative position of the scan area.

  In some embodiments, Δz, Δz1, Δz2 for setting the Z lock position for the B scan in any of the scan areas SC1 to SC4 are the same as those of the ophthalmologic apparatus 1 for scanning the scan areas SC1 to SC4. It is set according to the control information. Examples of the control information include control information for the LCD 39 for changing the fixation position for scanning the scan areas SC1 to SC4, and control information for controlling the optical scanner 42 for scanning the scan areas SC1 to SC4. There is.

  FIG. 13 shows another example of a scan range that can be set by the ophthalmologic apparatus 1 according to the embodiment.

  In FIG. 13, the scan area SC1 is set to include the scan center position O with respect to the scan area SC0 defined by the scan center position O after the completion of the alignment. The size of the scan area SC1 is larger than the size of the scan area SC0.

  In some embodiments, Δz, Δz1, and Δz2 are predetermined according to the size of the scan area.

  In some embodiments, Δz, Δz1, and Δz2 for setting the Z lock position for the B scan in the scan area SC1 are the size of the scan area SC1 (3D scan range) with respect to the size of the scan area SC0 (three-dimensional scan range). (Dimension scan range). In FIG. 12, similarly, Δz, Δz1, and Δz2 for setting the Z lock position for the B scan in the scan area SC1 (SC3) correspond to the scan area SC1 with respect to the size of the scan area SC0 (three-dimensional scan range). This is set according to the size of (SC3) (three-dimensional scan range).

  In some embodiments, the above-described Δz, Δz1, and Δz2 are predetermined in accordance with information on the eye E to be inspected. Examples of the information of the eye E include, for example, a reflex measurement result (refractive index) obtained by a reflex measurement performed on the eye E separately, information indicating whether the eye E is a strongly myopic eye, and the like. is there. That is, the Z lock position is set to a position shifted by the first shift value with respect to the reference position z0 when the eye E to be examined is an intense myopic eye for B scans other than the B scan in which the Z lock reference position z0 is set. When the eye E is not the myopic eye, a Z-lock position is set which is shifted from the reference position z0 by a second shift value smaller than the first shift value. In some embodiments, the reflex measurement result or the information indicating whether or not the eye E is the severely myopic eye is included in the eye information.

  In some embodiments, the above Δz, Δz1, Δz2 are obtained based on standard data statistically derived from the measurement results of a large number of normal eyes.

  In some embodiments, for a B scan other than the B scan in which the Z lock reference position z0 is set, the reference position z0 is shifted by a shift value selected from a plurality of predetermined shift values with respect to the reference position z0. It is set as follows. The plurality of shift values may be determined in advance based on the standard data.

  In some embodiments, Δz, Δz1, and Δz2 are predetermined in accordance with the analysis result of the OCT image (B-scan image) of the eye E. As an OCT image of the eye E, for example, a B scan image obtained by a B scan performed during the three-dimensional scan, a B scan image of the eye E obtained by a B scan in a direction intersecting the B scan and so on. That is, in some embodiments, the Z-lock position is set based on the image based on the interference light detection result obtained by the OCT measurement for the B-scan other than the B-scan in which the Z-lock reference position z0 is set. Is done. Further, in some embodiments, for a B scan other than the B scan in which the Z lock reference position z0 is set, a scan in a direction intersecting the scan direction of the B scan in which the Z lock reference position z0 is set is performed. This is set based on the obtained interference light detection result. As a scan mode of the B scan in a direction intersecting the B scan, for example, a horizontal scan, a vertical scan, a cross scan, a radiation scan, a circle scan, a concentric scan, and a spiral (spiral) scan are used.

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

  FIG. 14 illustrates a flowchart of an operation example of the ophthalmologic apparatus 1 according to the embodiment.

(S1: Set scan area)
First, the user sets a scan area for the eye E using the operation unit 240B.

(S2: 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 relative to the eye E by the moving amount. Move relatively. The main control unit 211 repeatedly executes this processing.

(S3: focus)
When the alignment is completed, the main control unit 211 starts the focus adjustment. For example, the main control unit 211 starts acquisition of a front image of the fundus oculi Ef, and controls the focus optical system 60 to project a split index on the fundus oculi Ef. The main control unit 211 controls the focusing driving unit 31A based on the moving amount of the optical system specified based on the received light image acquired by the image sensor 35, for example, and moves the photographing focusing lens 31 by the moving amount. Let it. Here, the main control unit 211 controls the focusing driving unit 43A to move the OCT focusing lens 43 by the moving amount. The main control unit 211 repeatedly executes this processing.

  In some embodiments, a plurality of preliminary operations are performed in step S2 or step S3. Preliminary operations include alignment, coarse focus adjustment, optical path length difference adjustment, polarization adjustment, and focus fine adjustment.

(S4: Auto Z)
The main control unit 211 starts the OCT measurement. In the OCT measurement, substantially the same cross section of the eye E (for example, the fundus oculi Ef) is repeatedly scanned at a predetermined frequency. Subsequently, the main control unit 211 executes Auto-Z based on the acquired OCT image (or the reflection intensity profile or the like), similarly to the method disclosed in JP-A-2006-041221.

  Here, the main control unit 211 causes the display unit 240A to display the OCT image live.

(S5: Specify Z lock reference position)
Subsequently, the main control unit 211 receives designation of a reference position of the Z lock performed on the operation unit 240B by the user.

(S6: Acquire Z lock position)
The main control unit 211 causes the Z lock position acquisition unit 233 to acquire the Z lock position for another B scan as described above, based on the Z lock reference position specified in step S5.

(S7: Change optical path length difference)
Subsequently, the main control unit 211 sequentially executes the B scan. For example, the main control unit 211 causes the optical path length difference change amount acquisition unit 234 to acquire the change amount of the optical path length difference based on the Z lock position acquired in step S6. Thereafter, the main control unit 211 controls at least one of the optical path length changing unit 41 and the reference driving unit 114A based on the acquired change amount of the optical path length difference.

(S8: Scan)
The main control unit 211 deflects the measurement light LS by controlling the optical scanner 42, and executes the B scan on the eye E to be inspected.

(S9: forming a tomographic image)
The main control unit 211 causes the image forming unit 220 to form a tomographic image based on the scan result obtained in step S8.

(S10: display)
The main control unit 211 causes the tomographic image formed in step S9 to be displayed in the tomographic image display area DR1 of the display unit 240A.

(S11: next?)
The main control unit 211 determines whether to execute the next B scan. The main control unit 211 determines whether to execute the next B scan based on the scan area set in step S1 or the operation content on the operation unit 240B.

  When it is determined that the next B scan is to be performed (S11: Y), the operation of the ophthalmologic apparatus 1 proceeds to step S7. When it is determined that the next B scan is not to be performed (S11: N), the operation of the ophthalmologic apparatus 1 proceeds to step S12.

(S12: Form a front image)
When it is determined in step S11 that the next B scan is not to be performed (S11: N), the main control unit 211 forms a projection image in the data processing unit 230 based on the scan data of the scan area set in step S1. Let it.

(S13: display)
Subsequently, the main control unit 211 causes the projection image formed in step S12 to be displayed in the front image display area DR2 of the display unit 240A. This is the end of the operation of the ophthalmologic apparatus 1 (end).

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

  Some embodiments are an ophthalmologic apparatus (1) including an interference optical system (an optical system included in the OCT unit 100), an operation unit (240B), and a control unit (210). The interference optical system is configured to be able to change the optical path length difference between the measurement optical path and the reference optical path. The interference optical system divides light (L0) from the light source (light source unit 101) into measurement light (LS) and reference light (LR), and irradiates the eye to be inspected (E) with measurement light via a measurement optical path. Then, an interference light (LC) between the return light from the subject's eye and the reference light passing through the reference light path is detected. The control unit is used to designate a reference position in the depth direction (Z lock reference position) for the B scan with respect to the subject's eye. The control unit controls the interference optical system in each B scan so as to change the optical path length difference in each B scan so that an image based on the detection result of the interference light is located at the reference position, thereby performing a plurality of B scans on the eye to be inspected. Is executed.

  In such a configuration, a reference position in the depth direction is designated for the B scan performed on the eye to be inspected, and the eye based on the detection result of the interference light is positioned at the reference position with respect to the eye. To execute a plurality of B scans. Thereby, even when the measurement range by the OCT measurement is widened in the xy direction or deepened in the z direction, depending on the state of curvature of the eyeball, the attention site is drawn at the end of the imaging range or deviates from the imaging range. Can be avoided. As a result, it is possible to reduce the burden on the examiner and the subject when performing the OCT measurement.

  In some embodiments, the plurality of B scans include a first B scan, a second B scan, and a third B scan, and the operation unit is used for the first B scan. A first reference position is set, a second reference position is set using the operation unit for the second B scan, and a first reference position and a second reference position are set for the third B scan. The third reference position specified based on the third reference position is set. The control unit controls the interference optical system to execute the first B scan, the second B scan, and the third B scan.

  According to such a configuration, since at least two reference positions can be specified, depending on the curved state of the eyeball, the attention site is drawn at the end of the imaging range or deviates from the imaging range. The situation can be easily avoided. As a result, it is possible to reduce the burden on the examiner and the subject when performing the OCT measurement.

  In some embodiments, the plurality of B scans include a first B scan, a second B scan, and a third B scan, and the operation unit is used for the first B scan. A first reference position is set, a second reference position shifted in the depth direction with respect to the first reference position is set for the second B scan, and a first reference position is set for the third B scan. A third reference position specified based on and the second reference position is set. The control unit controls the interference optical system to execute the first B scan, the second B scan, and the third B scan.

  According to such a configuration, since at least two reference positions can be specified, depending on the curved state of the eyeball, the attention site is drawn at the end of the imaging range or deviates from the imaging range. The situation can be easily avoided. As a result, it is possible to reduce the burden on the examiner and the subject when performing the OCT measurement.

  In some embodiments, the second reference position is set according to a distance between the scan position of the first B scan and the scan position of the second B scan.

  According to such a configuration, since the Z lock position is set according to the scan position, even when the measurement range is widened or the degree of curvature of the eyeball is large such as in the case of intense myopia, the region of interest is displayed as an image. It is possible to avoid a situation where the image is drawn at the end of the imaging range or deviates from the imaging range.

  In some embodiments, the second reference position is set according to a three-dimensional scan range including the second B scan with respect to the three-dimensional scan range including the first B scan.

  According to such a configuration, since the Z lock position is set according to the scan range, even if the measurement range is widened or the degree of curvature of the eyeball is large such as in the case of intense myopia, the region of interest is an image. It is possible to avoid a situation where the image is drawn at the end of the imaging range or deviates from the imaging range.

  In some embodiments, the second reference position is set according to the refraction of the subject's eye.

  According to such a configuration, the Z-lock position is set according to the refraction of the eye to be inspected. Therefore, even when the measurement range is widened or the degree of curvature of the eyeball is large as in the case of a strongly myopic eye, attention is paid. It is possible to avoid a situation where a part is drawn at the end of the imaging range or goes out of the imaging range.

  In some embodiments, the second reference position is set to a position shifted by a first shift value with respect to the first reference position when the subject's eye is a severely myopic eye, and is set to a first position when the subject's eye is not a severe myopic eye. The position is set to a position shifted by a second shift value smaller than the first shift value with respect to the reference position.

  According to such a configuration, the Z-lock position is set according to the information indicating whether or not the eye to be examined is a strongly myopic eye, so that the measurement range is widened or the degree of curvature of the eyeball is increased as in the case of strongly myopic eyes. Even if it becomes larger, it is possible to avoid a situation where the target site is drawn at the end of the imaging range or goes out of the imaging range.

  In some embodiments, the second reference position is set to shift by a shift value selected from a plurality of predetermined shift values with respect to the first reference position.

  According to such a configuration, the Z-lock position is set using a shift value selected from a plurality of predetermined shift values, so that the measurement range is widened or the eyeball is intensified as in the case of intense myopia. Even when the degree of curvature increases, it is possible to easily avoid a situation in which the target portion is drawn at the end of the imaging range or deviates from the imaging range.

  In some embodiments, the second reference position is set based on an image based on a result of detecting the interference light.

  According to such a configuration, since the Z lock position is set based on the image based on the detection result of the interference light, a situation in which the target part is drawn at the end of the imaging range or deviates from the imaging range may occur. It is easier to guess. As a result, even when the measurement range is widened or the degree of curvature of the eyeball is large, such as in the case of intense myopia, it is ensured that the region of interest is drawn at the end of the imaging range or deviates from the imaging range. Can be avoided.

  In some embodiments, the second reference position is set based on a detection result of interference light obtained by a scan in a direction that intersects the scan direction of the first B scan.

  According to such a configuration, the Z lock position is set based on the detection result of the interference light obtained by the scan in the direction intersecting with the scan direction of the first B scan. It is easier to guess the situation where the image is drawn at the edge or goes out of the imaging range. As a result, even when the measurement range is widened or the degree of curvature of the eyeball is large, such as in the case of intense myopia, it is ensured that the region of interest is drawn at the end of the imaging range or deviates from the imaging range. Can be avoided.

  In some embodiments, the control unit causes the control unit to execute the first B scan, the third B scan, and the second B scan in the direction intersecting the scan direction of the first B scan.

  According to such a configuration, even when the reference position specified for the third B scan is used, a situation in which the target part is drawn at the end of the imaging range or deviates from the imaging range is avoided. Easier to do.

  Some embodiments are a method for controlling an ophthalmologic apparatus (1) including an interference optical system (an optical system included in the OCT unit 100) and an operation unit (240B). The interference optical system is configured to be able to change the optical path length difference between the measurement optical path and the reference optical path. The interference optical system divides light (L0) from the light source (light source unit 101) into measurement light (LS) and reference light (LR), and irradiates the eye to be inspected (E) with measurement light via a measurement optical path. Then, an interference light (LC) between the return light from the subject's eye and the reference light passing through the reference light path is detected. The operation unit is used to specify a reference position in the depth direction for the B scan with respect to the subject's eye. The method of controlling an ophthalmologic apparatus includes: a reference position setting step of setting a reference position designated using an operation unit for a plurality of B scans with respect to an eye to be inspected; And controlling the interference optical system in each B scan to change the optical path length difference so as to execute a plurality of B scans on the subject's eye.

  According to such control, even when the measurement range of the OCT measurement is widened in the xy direction or deepened in the z direction, the target region is drawn at the end of the imaging range depending on the curved state of the eyeball, It is possible to avoid a situation in which the information is out of the conversion range. As a result, it is possible to reduce the burden on the examiner and the subject when performing the OCT measurement.

  In some embodiments, the reference position setting step includes the steps of: setting a first reference position specified by using the operation unit for the first B scan; Setting a second reference position specified by using the unit, and setting a third reference position specified based on the first reference position and the second reference position for the third B scan And the control step controls the interference optical system to execute the first B scan, the second B scan, and the third B scan.

  According to such control, since at least two reference positions can be designated, depending on the state of curvature of the eyeball, the region of interest is drawn at the end of the imaging range or deviates from the imaging range. The situation can be easily avoided. As a result, it is possible to reduce the burden on the examiner and the subject when performing the OCT measurement.

  In some embodiments, the reference position setting step includes a step of setting a first reference position designated using the operation unit for the first B scan, and a step of setting the first reference position specified using the operation unit. Setting a second reference position shifted in the depth direction with respect to one reference position; and a third reference position specified based on the first reference position and the second reference position for the third B scan And the control step controls the interference optical system to execute the first B scan, the second B scan, and the third B scan.

  According to such control, since at least two reference positions can be designated, depending on the state of curvature of the eyeball, the region of interest is drawn at the end of the imaging range or deviates from the imaging range. The situation can be easily avoided. As a result, it is possible to reduce the burden on the examiner and the subject when performing the OCT measurement.

  The above embodiment can be applied to the case where the Z lock reference position is specified for an arbitrary number of B scans in the scan area. For example, it is possible to specify the Z lock reference position for four or more arbitrary B scans.

  A computer program for implementing the above-described embodiment can be stored in any computer-readable recording medium. As the recording medium, for example, 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.), etc. 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 10 illumination optical system 30 imaging optical system 31 imaging focus lens 41 optical path length changing unit 42 optical scanner 50 alignment optical system 60 focusing optical system 100 OCT unit 101 light source unit 200 arithmetic control unit 210 control unit 211 Main control unit 212 Storage unit 220 Image forming unit 230 Data processing unit 231 Site identification unit 233 Z lock position acquisition unit 234 Optical path length difference change acquisition unit 240A Display unit 240B Operation unit E Eye to be inspected LS Measurement light LR Reference light LC Interference light

Claims (14)

An optical path length difference between the measurement optical path and the reference optical path is configured to be changeable, the light from the light source is split into the measurement light and the reference light, and the measurement light that has passed through the measurement optical path is irradiated on the eye to be inspected. An interference optical system that detects interference light between the reference light and the return light from the optometry and the reference light path,
An operation unit for designating a reference position in the depth direction with respect to the B scan for the eye to be inspected;
By controlling the interference optical system and changing the optical path length difference in each B scan so that an image based on the detection result of the interference light is arranged at the reference position, a plurality of B light beams can be detected with respect to the subject's eye. A control unit for executing a scan,
Ophthalmic equipment including. The plurality of B scans include a first B scan, a second B scan, and a third B scan,
A first reference position is set for the first B scan using the operation unit;
A second reference position is set for the second B scan using the operation unit;
A third reference position specified based on the first reference position and the second reference position is set for the third B scan,
The ophthalmologic apparatus according to claim 1, wherein the control unit controls the interference optical system to execute the first B scan, the second B scan, and the third B scan. apparatus. The plurality of B scans include a first B scan, a second B scan, and a third B scan,
A first reference position is set for the first B scan using the operation unit;
A second reference position shifted in the depth direction with respect to the first reference position is set for the second B scan,
A third reference position specified based on the first reference position and the second reference position is set for the third B scan,
The ophthalmologic apparatus according to claim 1, wherein the control unit controls the interference optical system to execute the first B scan, the second B scan, and the third B scan. apparatus. The ophthalmologic apparatus according to claim 3, wherein the second reference position is set according to a distance between a scan position of the first B scan and a scan position of the second B scan. The said 2nd reference position is set according to the three-dimensional scan range containing the said 2nd B scan with respect to the three-dimensional scan range containing the said 1st B scan. The Claim 3 or Claim 4 characterized by the above-mentioned. An ophthalmologic apparatus according to item 1. The ophthalmologic apparatus according to any one of claims 3 to 5, wherein the second reference position is set according to a refractive index of the eye to be inspected. The second reference position is set to a position shifted by a first shift value with respect to the first reference position when the eye to be examined is a strongly myopic eye, and is set to a first reference position when the eye to be examined is not a strongly myopic eye. The ophthalmologic apparatus according to any one of claims 3 to 6, wherein the position is set to a position shifted by a second shift value smaller than the first shift value. The second reference position is set so as to shift by a shift value selected from a plurality of predetermined shift values with respect to the first reference position. The ophthalmic apparatus according to any one of the above. The ophthalmologic apparatus according to any one of claims 3 to 8, wherein the second reference position is set based on an image based on a result of the detection of the interference light. The said 2nd reference position is set based on the detection result of the said interference light obtained by the scan of the direction which intersects with the scan direction of the said 1st B scan. The Claims 3-9 characterized by the above-mentioned. The ophthalmic apparatus according to any one of the above. The control unit executes the first B scan, the third B scan, and the second B scan in a direction intersecting with a scan direction of the first B scan. The ophthalmologic apparatus according to any one of claims 2 to 10, wherein An optical path length difference between the measurement optical path and the reference optical path is configured to be changeable, the light from the light source is split into the measurement light and the reference light, and the measurement light that has passed through the measurement optical path is irradiated on the eye to be inspected. An interference optical system that detects interference light between the reference light and the return light from the optometry and the reference light path,
An operation unit for designating a reference position in the depth direction with respect to the B scan for the eye to be inspected;
A method for controlling an ophthalmologic apparatus, comprising:
A reference position setting step of setting the reference position specified using the operation unit for a plurality of B scans with respect to the subject's eye;
By controlling the interference optical system and changing the optical path length difference in each B scan so that an image based on the detection result of the interference light is arranged at the reference position, a plurality of B light beams can be detected with respect to the subject's eye. A control step for performing a scan;
A method for controlling an ophthalmic apparatus including: The reference position setting step includes:
Setting a first reference position designated using the operation unit for a first B scan;
Setting a second reference position specified using the operation unit for a second B scan;
Setting a third reference position specified based on the first reference position and the second reference position for a third B scan;
Including
The ophthalmologic apparatus according to claim 12, wherein the control step controls the interference optical system to execute the first B scan, the second B scan, and the third B scan. How to control the device. The reference position setting step includes:
Setting a first reference position designated using the operation unit for a first B scan;
Setting a second reference position shifted in the depth direction with respect to the first reference position for a second B scan;
Setting a third reference position specified based on the first reference position and the second reference position for a third B scan;
Including
The ophthalmologic apparatus according to claim 12, wherein the control step controls the interference optical system to execute the first B scan, the second B scan, and the third B scan. How to control the device.

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