JP2017143920A - Ophthalmologic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To improve visibility of an internal fixation mark presented to an eye to be examined by an ophthalmologic apparatus.SOLUTION: An ophthalmologic apparatus comprises an optical system, a specification unit, and a condition setting unit. The optical system includes an objective lens, an irradiation system, and a fixation system. The irradiation system irradiates an eye to be examined with light through the objective lens. The fixation system includes a luminous flux output unit for outputting a fixation luminous flux, and projects the fixation luminous flux output from the luminous flux output unit onto the eye to be examined through the objective lens. A movement mechanism moves a movable part which is at least part of the optical system including the objective lens in a first direction along an optical axis of the objective lens and a second direction orthogonal to the first direction. The specification unit has a configuration for specifying a part of the eye to be examined, which is irradiated with light by the irradiation system. The condition setting unit sets an output position of the fixation luminous flux by the luminous flux output unit and a movement route of the movable part by the movement mechanism on the basis of the part specified by the specification unit.SELECTED DRAWING: Figure 4

Description

  The present invention relates to an ophthalmic apparatus.

  In an ophthalmic examination (including any action for acquiring data of an eye to be examined, such as examination, measurement, and imaging), fixation is performed to examine a desired part of the eye to be examined. Fixation is realized by having the subject gaze at a fixation target presented in a predetermined direction.

  Fixation includes internal fixation, external fixation, and peripheral fixation. Internal fixation is a fixation method in which a bright spot image formed by a dot matrix liquid crystal display (LCD) or a matrix light emitting diode (LED) is projected onto the fundus through an objective lens of an inspection optical system. It has a feature that the shape and position of a mark (called an internal fixation target) can be set in detail. External fixation is performed using a light source (such as an LED) provided outside the housing in which the inspection optical system is stored, and when the internal fixation cannot be performed, the eye to be examined is guided by guiding the eyes of the fellow eyes This is a fixation method that adjusts the orientation of the camera. Peripheral fixation is performed using a plurality of light sources (LEDs, etc.) arranged around the objective lens, and is a fixation method in which the subject's eye is largely rotated in a desired direction by selectively lighting these light sources. is there. Peripheral fixation is used in the examination of the fundus periphery.

  Patent Document 1 discloses a technique for changing the size of an internal fixation target while moving the internal fixation target in order to prevent the subject from losing sight of the internal fixation target being moved.

JP 2004-141563 A

  The scene where the visibility of the internal fixation target should be considered is not limited to the movement. For example, when the examination optical system is aligned with the eye to be examined, the examination optical system (optical head) is brought closer to the eye to be examined while the internal fixation target is presented. When the internal fixation light beam passes through a position away from the optical axis of the objective lens as in the case of examining the optic nerve head, the internal fixation light beam reaches the fundus when the distance between the optical head and the eye to be examined is short, When the distance is long, the internal fixation light flux does not reach the fundus. That is, when the optical head is brought closer to the eye to be examined, the internal fixation target suddenly appears at the end of the visual field at a certain stage. For this reason, the subject may not be able to recognize the internal fixation target and may not be able to perform alignment properly. Further, when the internal fixation target enters the field of view, the subject's eye suddenly rotates and flare occurs in the observation image, which sometimes obstructs the observation or alignment of the subject's eye.

  One object of the ophthalmologic apparatus according to the present invention is to improve the visibility of the internal fixation target.

  The ophthalmologic apparatus of the embodiment includes an optical system, a designation unit, and a condition setting unit. The optical system includes an objective lens, an irradiation system, and a fixation system. The irradiation system irradiates light to the eye to be examined through the objective lens. The fixation system includes a light beam output unit that outputs a fixation light beam, and projects the fixation light beam output from the light beam output unit onto the eye to be examined via the objective lens. The moving mechanism moves a movable portion that is at least a part of an optical system including the objective lens in a first direction along the optical axis of the objective lens and a second direction orthogonal to the first direction. The designating unit has a configuration for designating a site of the eye to be examined that is irradiated with light by the illumination system. The condition setting unit sets the output position of the fixation light beam by the light beam output unit and the moving path of the movable unit by the moving mechanism based on the part specified by the specifying unit.

  According to the embodiment, it is possible to improve the visibility of the internal fixation target.

Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. The schematic diagram for demonstrating the conventional ophthalmologic apparatus. The schematic diagram for demonstrating the conventional ophthalmologic apparatus. The schematic diagram for demonstrating the ophthalmologic apparatus which concerns on embodiment. The schematic diagram for demonstrating the ophthalmologic apparatus which concerns on embodiment. The schematic diagram for demonstrating the ophthalmologic apparatus which concerns on embodiment. Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. The flowchart showing an example of operation | movement of the ophthalmologic apparatus which concerns on embodiment. Schematic for demonstrating an example of operation | movement of the ophthalmologic apparatus which concerns on embodiment.

  Several embodiments of the present invention will be described in detail with reference to the drawings. The embodiment may be any ophthalmologic apparatus including an irradiation system that irradiates light to the eye to be examined through the objective lens and a fixation system that projects a fixation light beam to the eye to be examined through the objective lens. Examples of such an ophthalmologic apparatus include an optical coherence tomography (OCT), a fundus camera, a scanning laser ophthalmoscope (SLO), a laser treatment apparatus (photocoagulation apparatus), and a perimeter. The OCT, the fundus camera, and the SLO are further provided with an optical system that detects return light from the eye to be inspected by the irradiation system. Hereinafter, although the ophthalmologic apparatus which combined the swept source OCT and the fundus camera will be described, the embodiment is not limited thereto.

<Constitution>
As shown in FIG. 1, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system that is substantially the same as that of a conventional fundus camera. The OCT unit 100 is provided with an optical system and a mechanism for performing OCT. The arithmetic control unit 200 includes a processor. A chin rest and a forehead support for supporting the face of the subject are provided at positions facing the fundus camera unit 2. Furthermore, the ophthalmologic apparatus 1 includes a pair of anterior eye cameras 5A and 5B.

  In this specification, the “processor” is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, SPLD (Simple LD). It means a circuit such as (Complex Programmable Logic Device) or FPGA (Field Programmable Gate Array). For example, the processor implements the functions according to the embodiment by reading and executing a program stored in a storage circuit or a storage device.

<Fundus camera unit 2>
The fundus camera unit 2 is provided with an optical system for photographing the fundus oculi Ef of the eye E to be examined. Images obtained by photographing the fundus oculi Ef (called fundus images, fundus photographs, etc.) include observation images and photographed images. The observation image is obtained, for example, by moving image shooting using near infrared light. The captured image is, for example, a color image or monochrome image obtained using visible flash light, or a monochrome image obtained using near-infrared flash light. The fundus camera unit 2 may further be able to acquire a fluorescein fluorescent image, an indocyanine green fluorescent image, a spontaneous fluorescent image, or the like.

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

  The observation light source 11 of the illumination optical system 10 is, for example, a halogen lamp or an LED (Light Emitting Diode). The light (observation illumination light) output from the observation light source 11 is reflected by the reflection mirror 12 having a curved reflection surface, passes through the condensing lens 13, passes through the visible cut filter 14, and is converted into near infrared light. Become. Further, the observation illumination light is once converged in the vicinity of the photographing 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 by the peripheral part of the perforated mirror 21 (area around the perforated part), passes through the dichroic mirror 46, and is refracted by the objective lens 22 so as to pass through the eye E (especially the fundus oculi Ef). Illuminate.

  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 light is reflected by the mirror 32 via the photographing focusing lens 31. Further, the 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 CCD image sensor 35 by the condenser lens. The CCD image sensor 35 detects the return light at a predetermined frame rate, for example. Note that an observation image of the fundus oculi Ef is obtained when the photographing optical system 30 is focused on the fundus oculi Ef, and an anterior eye observation image is obtained when the focus is on the anterior eye segment.

  The imaging light source 15 is a visible light source including, for example, a xenon lamp or an LED. The light (imaging illumination light) output from the imaging 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 CCD image sensor 38.

  The LCD 39 displays a fixation target for fixing the eye E to be examined. A part of the light beam (fixed light beam) output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, and passes through the photographing focusing lens 31 and the dichroic mirror 55, and then the hole of the aperture mirror 21. Pass through the department. The fixation light beam that has passed through the hole of the aperture mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi 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.

  The light flux output unit that outputs a fixation light flux is not limited to the LCD 39. The light beam output unit may be configured so that the fixation position can be changed. For example, the light beam output unit may be a matrix LED in which a plurality of LEDs are two-dimensionally arranged, a combination of a light source and a variable aperture (liquid crystal aperture, etc.) It's okay.

  The fundus camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60. The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E. The focus optical system 60 generates a split index used for focus adjustment with respect to the eye E.

  The alignment light output from the LED 51 of the alignment optical system 50 is reflected by the dichroic mirror 55 via the apertures 52 and 53 and the relay lens 54, 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 cornea-reflected light of the alignment light passes through the objective lens 22, the dichroic mirror 46, and the hole, part of which passes through the dichroic mirror 55, passes through the photographing focusing lens 31, is reflected by the mirror 32, and is half The light passes through the mirror 33A, is reflected by the dichroic mirror 33, and is projected onto the light receiving surface of the CCD image sensor 35 by the condenser lens. Based on the received light image (alignment index image) by the CCD image sensor 35, manual alignment and auto alignment similar to the conventional one can be performed.

  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 (imaging optical path) of the imaging optical system 30. The reflection bar 67 can be inserted into and removed from the illumination optical path.

  When performing the focus adjustment, the reflection surface of the reflection bar 67 is obliquely provided in the illumination optical path. The focus light output from the LED 61 passes through the relay lens 62, is separated into two light beams by the split target plate 63, passes through the two-hole aperture 64, is reflected by the mirror 65, and is reflected by the condenser lens 66. An image is once formed on the reflection surface 67 and reflected. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef.

  The fundus reflection light of the focus light is detected by the CCD image sensor 35 through the same path as the corneal reflection light of the alignment light. Based on the received image (split index image) by the CCD image sensor 35, manual alignment and auto-alignment similar to the conventional one can be performed.

  The photographing optical system 30 includes diopter correction lenses 70 and 71. The diopter correction lenses 70 and 71 can be selectively inserted into a photographing optical path between the perforated mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus (+) lens for correcting intensity hyperopia, for example, a + 20D (diopter) convex lens. The diopter correction lens 71 is a minus (−) lens for correcting intensity myopia, for example, a −20D concave lens. The diopter correction lenses 70 and 71 are mounted on, for example, a turret plate. The turret plate is formed with a hole for the case where none of the diopter correction lenses 70 and 71 is applied.

  The dichroic mirror 46 combines the fundus imaging optical path and the OCT optical path. The dichroic mirror 46 reflects light in a wavelength band used for OCT and transmits light for fundus photographing. In the optical path for OCT, a collimator lens unit 40, an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, a mirror 44, and a relay lens 45 are provided in this order from the OCT unit 100 side.

  The optical path length changing unit 41 is movable in the direction of the arrow shown in FIG. 1, and changes the optical path length of the optical path for OCT. This change in the optical path length is used for correcting the optical path length according to the axial length of the eye E or adjusting the interference state. The optical path length changing unit 41 includes, for example, 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. The optical scanner 42 changes the traveling direction of the measurement light LS that passes through the optical path for OCT. Thereby, the eye E is scanned with the measurement light LS. The optical scanner 42 can deflect the measurement light LS in an arbitrary direction on the xy plane, and includes, for example, a galvanometer mirror that deflects the measurement light LS in the x direction and a galvanometer mirror that deflects the measurement light LS in the y direction.

<OCT unit 100>
As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing OCT of the eye E. The configuration of this optical system is the same as that of the conventional swept source OCT. That is, this optical system divides the light from the wavelength sweep type (wavelength scanning type) light source into the measurement light and the reference light, and returns the return light of the measurement light from the eye E and the reference light via the reference light path. An interference optical system that generates interference light by causing interference and detects the interference light is included. A detection result (detection signal) obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic control unit 200.

  The light source unit 101 includes a wavelength swept type (wavelength scanning type) light source that changes the wavelength of the emitted light at a high speed, like a general swept source OCT. The wavelength sweep type light source is, for example, a near infrared laser light source.

  The light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102 and its polarization state is adjusted. Further, the light L0 is guided to the fiber coupler 105 by the optical fiber 104 and is divided into the measurement light LS and the reference light LR.

  The reference light LR is guided to the collimator 111 by the optical fiber 110 and converted into a parallel light beam, and is guided to the corner cube 114 via the optical path length correction member 112 and the dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR and the optical path length of the measurement light LS. The dispersion compensation member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS.

  The corner cube 114 turns the traveling direction of the incident reference light LR in the reverse direction. The incident direction and the emitting direction of the reference light LR with respect to the corner cube 114 are parallel to each other. The corner cube 114 is movable in the incident direction of the reference light LR, and thereby the optical path length of the reference light LR is changed.

  1 and 2, the optical path length changing unit 41 for changing the length of the optical path (measurement optical path, measurement arm) of the measurement light LS and the optical path (reference optical path, reference arm) of the reference light LR are used. Both corner cubes 114 for changing the length are provided, but 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 measurement optical path length and the reference optical path length using optical members other than these.

  The reference light LR that has passed through the corner cube 114 passes through the dispersion compensation member 113 and the optical path length correction member 112, is converted from a parallel light beam to a focused light beam by the collimator 116, and enters the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 and its polarization state is adjusted. The reference light LR is guided to the attenuator 120 by the optical fiber 119 and the amount of light is adjusted, and is guided to the fiber coupler 122 by the optical fiber 121. It is burned.

  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 beam by the collimator lens unit 40, and the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, and the mirror 44. Then, the light passes through the relay lens 45, is reflected by the dichroic mirror 46, is refracted by the objective lens 22, and enters the eye E to be examined. 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 eye E travels in the reverse direction on the same path as the forward path, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

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

  The detector 125 is, for example, a balanced photodiode (Balanced Photo Diode). The balanced photodiode has a pair of photodetectors that respectively detect the pair of interference lights LC, and outputs a difference between detection results obtained by these. The detector 125 sends the detection result (detection signal) to a DAQ (Data Acquisition System) 130.

  The clock 130 is supplied from the light source unit 101 to the DAQ 130. The clock KC is generated in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength sweep type light source in the light source unit 101. For example, the light source unit 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then generates a clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic control unit 200.

<Calculation control unit 200>
The arithmetic control unit 200 controls each part of the fundus camera unit 2, the display device 3, and the OCT unit 100. The arithmetic control unit 200 executes various arithmetic processes. For example, the arithmetic control unit 200 performs signal processing such as Fourier transform on the spectrum distribution based on the detection result obtained by the detector 125 for each series of wavelength scans (for each A line). A reflection intensity profile is formed. Furthermore, the arithmetic control unit 200 forms image data by imaging the reflection intensity profile of each A line. The arithmetic processing for that is the same as the conventional swept source OCT.

  The arithmetic control unit 200 includes, for example, a processor, a RAM (Random Access Memory), a ROM (Read Only Memory), a hard disk drive, a communication interface, and the like. Various computer programs are stored in a storage device such as a hard disk drive. The arithmetic control unit 200 may include an operation device, an input device, a display device, and the like.

<Anterior Eye Cameras 5A and 5B>
The anterior eye cameras 5A and 5B are used to obtain the relative position between the optical system of the ophthalmologic apparatus 1 and the eye E as in the invention disclosed in Japanese Patent Laid-Open No. 2013-248376. The anterior eye cameras 5A and 5B are provided on the surface on the eye E side of a housing (such as the fundus camera unit 2) in which an optical system is stored. Although details will be described later, the ophthalmologic apparatus 1 analyzes the two anterior segment images acquired substantially simultaneously from different directions by the anterior segment cameras 5A and 5B, thereby comparing the relative relationship between the optical system and the eye E to be examined. This is a three-dimensional position. The analysis of two anterior segment images acquired substantially simultaneously from different directions by the anterior segment cameras 5A and 5B may be the same as the analysis disclosed in Japanese Patent Laid-Open No. 2013-248376. Further, the number of anterior eye camera may be any number of 2 or more.

  In this example, the relative position between the optical system and the eye E to be examined (that is, the position of the optical system) is obtained using two or more anterior eye cameras, but this is the method for obtaining the position of the optical system. It is not limited. For example, referring to a configuration in which the position of the optical system is specified using an encoder provided in a moving mechanism 150 or a fundus camera unit 2 described later, or a control history of the moving mechanism 150 (actuator 151) by the main control unit 211. A configuration for specifying the position of the optical system can be applied.

<Control system>
A configuration example of the control system of the ophthalmologic apparatus 1 is shown in FIG.

<Control unit 210>
The control unit 210 controls each unit of the ophthalmologic apparatus 1. Control unit 210 includes a processor. The control unit 210 is provided with a main control unit 211 and a storage unit 212.

<Main control unit 211>
The main control unit 211 performs various controls. For example, the main control unit 211 includes an imaging focusing lens 31, CCDs (image sensors) 35 and 38, an LCD 39, an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, a focus optical system 60, a reflecting rod 67, and the like. To control. The main control unit 211 controls the light source unit 101, the reference driving unit 114A, the detector 125, the DAQ 130, and the like. The reference driving unit 114A moves the corner cube 114 provided in the reference optical path. Thereby, the length of the reference optical path is changed.

  The ophthalmologic apparatus 1 includes a moving mechanism 150. The moving mechanism 150 moves at least a part of the optical system of the ophthalmologic apparatus 1. Of the optical system of the ophthalmologic apparatus 1, a portion (a part or all of the optical system) moved by the moving mechanism 150 may be referred to as a movable portion. The moving mechanism 150 includes one or more actuators 151. The actuator 151 includes, for example, a pulse motor controlled by the main control unit 211, and generates a driving force for moving the movable unit. The driving force generated by the pulse motor 151 is transmitted by a mechanism (not shown) to move the movable part. Thereby, the movable part is moved three-dimensionally. The moving mechanism 150 includes, for example, an x moving mechanism including a first actuator and a mechanism that converts the first driving force generated thereby into movement in the x direction, a second actuator, and a second driving force generated thereby. And a z movement mechanism comprising a third actuator and a mechanism for converting the third driving force generated thereby into a movement in the z direction. .

  In the main control unit 211 shown in FIG. 3, the fixation control unit 2111 is an element that performs control related to fixation (control of the LCD 39 and the like), and the movement control unit 2112 controls the movement of the optical system (control of the movement mechanism 150 and the like). The display control unit 2113 is an element that performs control related to information display (such as control of the display unit 241).

<Storage unit 212>
The storage unit 212 stores various data. Examples of the data stored in the storage unit 212 include image data of an OCT image, image data of a fundus image, and eye information to be examined. The eye information includes subject information such as patient ID and name, left / right eye identification information, electronic medical record information, and the like.

  The storage unit 212 (or a condition setting unit 232 described later) may be configured to store in advance information for setting control conditions in the present embodiment. The control conditions include conditions relating to fixation (fixation conditions) and conditions relating to movement of the optical system (movement conditions). The control condition may further include a condition related to information display (display condition). The control condition is set for each part of the eye to be examined.

  The configuration of the LCD 39 will be described as a premise for explaining the control conditions. An example of the screen configuration of the LCD 39 is shown in FIG. The LCD 39 of this example is a dot matrix LCD, and 51 pixels (x direction) × 51 pixels (y direction) are arranged on the screen 39a. Coordinates 0 to 50 are assigned to the x direction (horizontal direction) array in order from the left to the right, and the y direction (vertical direction) array has coordinates 0 to 50 in order from the bottom to the top. Is granted.

  Characters attached to some pixels of the screen 39a indicate positions of fixation targets (bright spots) corresponding to the eye part (OCT scan area). When the eye to be examined is the right eye, the pixel “M” of (x, y) = (25, 25) indicates a fixation target corresponding to the macula, and the pixel “C” of (x, y) = (20, 26) "Indicates a fixation target corresponding to the center of the fundus, pixel" W "of (x, y) = (17, 26) indicates a fixation target corresponding to wide scan, and (x, y) = (10, A pixel “D” in 26) shows a fixation target corresponding to the optic disc. When the eye to be examined is the left eye, the pixel “M” of (x, y) = (25, 25) indicates a fixation target corresponding to the macula, and the pixel of (x, y) = (30, 26) “C” indicates a fixation target corresponding to the center of the fundus, pixel “W” of (x, y) = (33, 26) indicates a fixation target corresponding to the wide scan, and (x, y) = ( A pixel “D” in 40, 26) indicates a fixation target corresponding to the optic disc. In addition, the eight pixels “2” to “9” arranged in a circular shape indicate fixation targets corresponding to eight positions in the fundus periphery. Note that the optical axis (objective optical axis) of the objective lens 22 is arranged at the lower left corner of the pixel “M”.

  Furthermore, in order to describe the control conditions, the operation of the conventional ophthalmic apparatus will be described with reference to FIGS. 5A and 5B. FIG. 5A shows a screen (alignment screen) 300 displayed by a conventional ophthalmic apparatus for alignment. On the alignment screen 300, a moving image of the anterior segment (anterior segment observation image) 310 obtained by a fundus camera or the like is displayed. A target image 320 that is a target for moving the optical system in alignment is displayed on the anterior ocular segment observation image 310 in an overlapping manner. The target image 320 is a square image, and the center thereof coincides with the center of the anterior ocular segment observation image 310. That is, the center of the target image 320 coincides with the optical axis (objective optical axis) of the optical system for acquiring the anterior ocular segment observation image 310. Although not described, the alignment screen 300 presents other images (for example, an anterior segment image acquired by the anterior segment camera 5A and / or 5B) and software keys.

  FIG. 5B schematically shows an aspect in the case where the conventional alignment operation is executed by the ophthalmologic apparatus 1 of the present embodiment. Reference numeral 4 in FIG. 5B represents a housing in which the optical system (movable part) is stored. For example, the fundus camera unit 2 and the OCT unit 100 are stored in the housing 4. Although illustration is omitted, anterior eye cameras 5A and 5B are provided on the surface (front surface) of the housing 4 on the eye E side. Reference numeral 22a indicates the optical axis (objective optical axis) of the objective lens 22, reference numeral Ea indicates the axis (visual axis) of the non-eye E, and reference numeral F indicates a fixation target displayed on the LCD 39. In the example shown in FIG. 5B, the fixation target F is displayed at a position away from the objective optical axis 22a (for example, a pixel “D” corresponding to the optic disc).

In a state where the housing 4 is retracted (a state where the distance to the eye E is long), the xy direction of the housing 4 is set so that the pupil depicted in the anterior ocular segment observation image 310 is arranged inside the target image 320. The position of is adjusted. The state after such position adjustment is the housing 4 shown on the right side in FIG. 5B. In this state, the objective optical axis 22a is substantially coincident with the visual axis Ea. In this state, the eye E cannot recognize the fixation target F. In the conventional alignment, the housing 4 is advanced along the objective optical axis 22a from this state. Indicating the movement direction of the housing 4 in this case by the arrow T _0. When the casing 4 is brought closer to the eye E, the fixation target F suddenly appears at the end of the visual field of the eye E at a certain stage, and reaches the position of the casing 4 shown on the left side in FIG. Is moved forward. The position of the housing 4 shown on the left side is a predetermined inspection position (position where alignment is matched) where the eye E should be placed in order to perform an inspection using an optical system. The distance from the optical system (such as the front surface of the objective lens 22) is a predetermined working distance (working distance). In such conventional alignment, since the subject can recognize the fixation target F only from the middle, there is a possibility that the alignment cannot be properly performed.

  Unlike such conventional alignment, in this embodiment, alignment is performed in the manner shown in FIGS. 6A and 6B. In the present embodiment, the anterior ocular segment observation image 310 similar to the conventional one is displayed on the alignment screen 300 similar to the conventional one, while the target image 321 is displayed at a position different from the conventional one. Specifically, in the present embodiment, the target image 321 is displayed at a position corresponding to the fixation target display position (fixation position) on the LCD 39. For example, when the fixation position is macular, a fixation target is displayed on the pixel “M” of the LCD 39, and the center of the target image 320 and the center of the anterior ocular segment observation image 310 coincide with each other. An image 321 is displayed. When the fixation position is the optic disc, a fixation target is displayed on the pixel “D” of the LCD 39, and the previous position is displayed according to the displacement of the pixel “D” with respect to the pixel “M”. A target image 321 is displayed at a position displaced from the center of the eye part observation image 310. The displacement (displacement amount and displacement direction) of the target image 321 is set in advance according to the display position (fixation position) of the fixation target.

  FIG. 6B schematically shows an aspect of the alignment operation of the present embodiment. In the example shown in FIG. 6B, the fixation target F is displayed at a position away from the objective optical axis 22a (for example, a pixel “D” corresponding to the optic disc).

  In the alignment according to the present embodiment, the pupil depicted in the anterior ocular segment observation image 310 is arranged inside the target image 321 displayed eccentrically with respect to the objective optical axis 22a in a state where the housing 4 is retracted. As described above, the position of the housing 4 in the xy direction is adjusted. The state after such position adjustment is the housing 4 shown on the right side in FIG. 6B. At this time, the housing 4 is arranged at a position displaced by Δ in the xy direction from the conventional state shown in FIG. 5B. The displacement Δ of the housing 4 is set in advance according to the display position (fixation position) of the fixation target so that the fixation target is presented in the visual field of the eye E (details will be described later). .

In the alignment of the present embodiment, the advancement of the housing 4 is started from the state in which the subject recognizes the fixation target F in this way. The moving direction of the housing 4 is a direction oblique to the objective optical axis 22a. Indicating the movement direction of the housing 4 in this case by the arrow T _1. Direction indicated by arrow T ₁ is, for example, a direction indicated by the straight line connecting the forward starting position of the housing 4 and the forward end position. The advance end position is, for example, an inspection position (position where alignment is matched). By bringing the casing 4 close to the eye E along such a straight path, the subject can recognize the fixation target from the beginning to the end, and can perform the alignment appropriately. Become.

  The advance start position, that is, the displacement Δ of the housing 4 will be described with reference to FIG. Although the displacement Δx in the x direction will be described here, the displacement Δy in the y direction can be calculated in the same manner.

P _E = (x _E , z _E ) indicates the position of the eye E to be examined. P ₀ = (x ₀ , z ₀ ) indicates the current position of the housing 4. Here, it is assumed that z = z ₀ is a position (last retracted position) at which the distance from the eye E is maximum in the movable range in the z direction by the moving mechanism 150. x = x ₀ is arbitrary. P ₁ = (x ₁ , z ₁ ) represents the forward start position. In this example, this coordinate is obtained. P ₂ indicates a leg of a perpendicular line that is lowered from the position P _{E of the} eye E to the straight line z = z ₀ indicating the last retracted position (that is, the intersection of the straight line = z ₀ and the perpendicular line). The coordinates of P ₂ are (x _E , z ₀ ).

When the fixation position is other than the macula, the fixation target F is displayed at a position displaced from the objective optical axis 22a. The angle formed by the position on the LCD 39 where the objective optical axis 22a intersects and the display position of the fixation target F is θ. The angle θ is defined around the position P _E = (x _E , z _E ) of the eye E. Then, the forward start position P ₁ = (x ₁ , z ₁ ) is obtained by the following formula: x ₁ = (z _E −z ₀ ) tan θ + x ₁ , z ₁ = z ₀ . Therefore, Δx = vector (P ₂ → P ₁ ) = x ₁ −x _E is obtained.

  By performing the above calculation, control condition information 212a as shown in FIG. 8 is created in advance. In the control condition information 212a, a fixation condition, a movement condition, and a display condition are associated with an eye part (fixation position, scan target part). As the fixation condition, the position (coordinates) of the fixation target displayed on the LCD 39 is set. As the movement condition, a forward start position (its coordinates) is set. As the display condition, the display position of the target image (alignment frame) is set. Note that the display position of the target image is defined as the center position of the target image, for example. The display condition may include the size and shape of the target image.

In the example shown in FIG. 7, “M = (25, 25)” is set as the fixation condition for the eye part “macular”, and “(x _M , z _M ) = (0, 0) is set as the movement condition. Is set, and “H _M = (0, 0) (displacement from the frame center of the anterior ocular segment observation image)” is set as the display condition. In addition, “D = (10, 26)” is set as the fixation condition for the part “optic nerve head” of the eye (right eye), and “(x _D , z _D ) = (Δx _D , Δz” is set as the movement condition. _D ) ”is set, and“ H _M ”is set as the display condition.

  The control condition information 212a includes control condition information that is applied when the eye E is the right eye, and control condition information that is applied when the eye E is the left eye. The control condition information for the right eye and the control condition information for the left eye are created so as to be targeted in the x direction, for example. Also, control condition information can be provided according to the pupil size, disease type, and the like. For example, with respect to the pupil size, it is possible to provide control condition information for normal pupil eyes and control condition information for small pupil eyes created so that the displacement amounts are different from each other.

  In this example, the destination (advance end position) to which the housing 4 (optical system) is moved by the alignment operation is a predetermined inspection position that is a position where the optical system is aligned with the eye E, and The housing 4 is moved along a straight path connecting the advance start position and the advance end position. Therefore, as in the control condition information 212a in FIG. 7, only the advance start position is set as the movement condition, both the advance start position and the advance end position are set as the movement conditions, and the advance start position and the advance end position. Is set as a movement condition is equivalent to each other.

<Image forming unit 220>
The image forming unit 220 forms image data of a cross-sectional image of the fundus oculi Ef based on the sampling result of the detection signal input from the DAQ 130. This processing includes signal processing such as noise removal (noise reduction), filter processing, and FFT (Fast Fourier Transform) as in the case of the conventional swept source OCT. The image data formed by the image forming unit 220 is a group of image data (a group of image data) formed by imaging reflection intensity profiles in a plurality of A lines (lines in the z direction) arranged along the scan line. A scan image data).

  The image forming unit 220 includes, for example, at least one of a processor and a dedicated circuit board. In the present specification, “image data” and “image” based thereon may be identified. Further, the part of the eye E to be examined and the image representing it may be identified.

<Data processing unit 230>
The data processing unit 230 performs image processing and analysis processing on the image formed by the image forming unit 220. For example, the data processing unit 230 executes correction processing such as image luminance correction and dispersion correction. Further, the data processing unit 230 performs image processing and analysis processing on an image (fundus image, anterior eye image, etc.) obtained by the fundus camera unit 2. The data processing unit 230 includes, for example, at least one of a processor and a dedicated circuit board. The data processing unit 230 includes a position information generation unit 231 and a condition setting unit 232.

<Position information generation unit 231>
The position information generation unit 231 generates position information representing the position of the optical system (movable unit). The position information generation unit 231 analyzes the two anterior eye images of the eye E acquired substantially simultaneously from different directions by the anterior eye cameras 5A and 5B, so that the optical system and the eye E can be analyzed. Relative position (especially relative position in the z direction). At this time, the arithmetic processing disclosed in JP2013-248376A is executed. When the moving mechanism 150 or the fundus camera unit 2 or the like is provided with an encoder, the position information generation unit 231 can obtain the position of the movable unit based on a signal output from the encoder. Further, when the main control unit 211 executes control of the movement mechanism 150, the position information generation unit 231 can obtain the position of the movable part based on the control history of the movement mechanism 150 by the main control unit 211.

<Condition setting unit 232>
The condition setting unit 232 sets a control condition based on a part designated by the user or the ophthalmologic apparatus 1. In the present embodiment, fixation conditions, movement conditions, and display conditions are set. Further, in the present embodiment, as described above, the movement path is a straight path, and this straight path includes an advance start position, a combination of an advance start position and an advance end position, or an advance start position and an advance end position. It is defined as the position of the connecting straight line.

  The movement route is not limited to a straight route, and may be a broken line route or a curved route, for example. A broken line path is defined by, for example, the position of each end point and the position of each vertex. The curved path is defined by, for example, a path pattern and parameters of each end point and a curve (curvature, curvature radius, mathematical expression representing a curve, etc.).

The condition setting unit 232 selects a control condition corresponding to the designated part from the control condition information 212a. For example, when the optic disc is designated, the condition setting unit 232 selects the fixation condition “D”, the movement condition “(x _D , z _D )”, and the display condition “H _M ”. The selected fixation condition is sent to the fixation control unit 2111 and used for controlling the LCD 39. The selected movement condition is used for controlling the movement mechanism 150 sent to the movement control unit 2112. The selected display condition is sent to the display control unit 2113 and used for controlling the display unit 241.

  A configuration and operation for designating an eye part will be described. As a first example, the display control unit 2113 displays a software key for setting a fixation position on the display unit 241, and the user can set a desired fixation position using the operation unit 242. As a second example, the condition setting unit 232 analyzes past examination data (such as electronic medical record information) of the subject eye E input from the outside to identify a fixation position applied in the past. It can be specified as a fixation position. As a third example, the condition setting unit 232 analyzes an observation image or a photographed image of the fundus oculi Ef to identify a site of interest (lesion site or the like), and designates a fixation position corresponding to a scan area including the site of interest. be able to.

  The condition setting unit 232 can execute processing for determining whether the eye E is the right eye or the left eye. This process is executed based on, for example, the state of the moving mechanism 150 when the optical system is facing the eye E, that is, the position of the housing 4 when the optical system is facing the eye E. . The state of the moving mechanism 150 and the position of the housing 4 are detected based on the anterior eye image obtained by the anterior eye camera 5A and / or 5B, the position detected by the encoder, or the control history of the moving mechanism 150. Is done. The condition setting unit 232 acquires control conditions by selecting control condition information corresponding to the right eye / left eye discrimination result.

  The condition setting unit 232 can execute a process of determining whether the eye E is a normal pupil eye or a small pupil eye. For example, this processing is performed by analyzing the anterior ocular segment image obtained by the fundus camera unit 2 or the anterior ocular segment image obtained by the anterior ocular camera 5A and / or 5B, and the pupil size (diameter, radius) of the eye E to be examined. , Circumference, area, etc.) and comparing this measured value to a predetermined threshold. Alternatively, the pupil size of the eye E (or whether or not it is a small pupil eye) acquired by a past examination can be acquired from electronic medical record information or the like. The condition setting unit 232 selects control condition information according to the normal pupil eye / small pupil eye discrimination result, and acquires the control condition.

<User Interface 240>
The user interface 240 includes a display unit 241 and an operation unit 242. The display unit 241 includes the display device 3. The operation unit 242 includes various operation devices and input devices. The user interface 240 may include a device such as a touch panel in which a display function and an operation function are integrated. Embodiments that do not include at least a portion of the user interface 240 can also be constructed. For example, the display device may be an external device connected to the ophthalmologic apparatus.

<Operation>
The operation of the ophthalmologic apparatus 1 will be described. Hereinafter, auto-alignment (first operation mode) and manual alignment (second operation mode) will be described.

<First operation mode>
An example of the auto alignment operation is shown in FIG.

(S1: Designate an imaging region)
First, the region of the eye E to be subjected to OCT or fundus imaging is specified together with the patient ID of the subject and identification information of the left eye / right eye. The imaging part is designated by the user (examiner) or the control unit 210.

(S2: Select a control condition according to the designated part)
The condition setting unit 232 selects, from the control condition information 212a, a fixation condition, a movement condition, and a display condition corresponding to the imaging region designated in step S1.

(S3: A target image is displayed based on display conditions)
By this stage, acquisition of the observation image of the anterior segment of the eye E is started. The display control unit 2113 displays the alignment screen 300 on the display unit 241, displays the anterior ocular segment observation image 310 on the alignment screen 300, and displays the anterior ocular segment observation image 310 according to the display condition selected in step S2. The target image 321 is displayed at the upper position.

(S4: Display a fixation target based on fixation conditions)
The fixation control unit 2111 displays a fixation target at the position of the LCD 39 (screen 39a) corresponding to the fixation condition selected in step S2. When the anterior segment imaging lens is arranged in the optical path, the fixation target image projected onto the fundus oculi Ef is blurred, so a large fixation target is displayed instead of the fixation target composed of bright spots. Can do. This large fixation target has, for example, an X shape, and its center (intersection of two line segments) is arranged at a position (coordinates indicated by the fixation condition) according to the fixation condition.

(S5: The optical system is moved to the forward start position based on the movement condition)
The movement control unit 2112 controls the movement mechanism 150 to move the optical system (housing 4) to the advance start position indicated by the movement condition selected in step S2.

(S6: Align pupil with target image)
The user or the ophthalmologic apparatus 1 refers to the anterior ocular segment observation image 310 as necessary, so that the pupil of the eye E is arranged in the frame-shaped target image 321 of the optical system (housing 4). Adjust the position in the xy direction. The position of the optical system after adjustment becomes the advance start position. Further, the route indicated by the movement condition can be adjusted based on the new advance start position. At this time, the forward end position is fixed.

  Note that the pupil region in the anterior ocular segment observation image 310 is specified by analyzing the anterior ocular segment observation image 310, for example. Alternatively, the user may specify the pupil center position depicted in the anterior ocular segment observation image 310 using the operation unit 242. This designation operation is, for example, a touch operation on the anterior ocular segment observation image 310 displayed on the touch panel display.

(S7: Start the advance of the optical system)
When the optical system is arranged at the advance start position, the movement control unit 2112 controls the movement mechanism 150 to start the advance of the optical system (housing 4). Accordingly, the optical system is moved from the advance start position toward the advance end position along the path indicated by the movement condition. When the imaging region is macular, the optical system is moved in the + z direction. When other imaging regions (for example, the optic nerve head) are designated, the optical system is moved in an oblique direction with respect to the z axis.

  The anterior eye cameras 5A and 5B capture moving images at a predetermined time interval (imaging rate), and the position information generation unit 231 determines the relative position between the eye E and the optical system (especially the relative position in the z direction) in real time. The operation is performed sequentially. The movement control unit 2112 can determine whether the optical system is moved along the path indicated by the movement condition by comparing the acquired relative position with the path indicated by the movement condition. The main control unit 211 can notify the determination result. Further, when the actual position of the optical system is out of the path, the movement control unit 2112 can control the movement mechanism 150 so as to return the optical system to the path.

(S8: Has the vehicle reached the forward end position?)
The optical system is moved until it is determined that the optical system has reached the forward end position (inspection position). Whether or not the optical system has reached the forward end position is determined based on, for example, position information obtained in real time by the position information generation unit 231. Alternatively, it can be determined that the forward end position has been reached in response to the completion of control of the moving mechanism 150 for moving the optical system from the forward start position to the forward end position along the path indicated by the movement condition. .

  In response to the advance of the optical system to a predetermined position, the main control unit 211 performs control for switching the focus of the optical system from the anterior ocular segment observation focus to the fundus observation focus. This control includes, for example, a process of retracting the above-described anterior ocular segment imaging lens from the optical path or a process of inserting a fundus oculi observation lens into the optical path.

  Before the optical system reaches the forward end position, the displayed observation image is switched from the anterior ocular segment observation image to the fundus oculi observation image. When the anterior ocular segment observation image is displayed, the movement control unit 2112 can finely adjust the operation of the moving mechanism 150 so that the pupil of the eye E is always placed in the target image 231. Further, the operation of the moving mechanism 150 is finely adjusted so that the portion of the fundus oculi Ef drawn at a predetermined position (for example, a position in the target image 231) of the frame when the fundus observation image is switched is always arranged at the position. can do.

(S9: Adjust shooting conditions)
For example, the user or the ophthalmologic apparatus 1 can finely adjust the alignment of the optical system with respect to the eye E based on the alignment index. It is also possible to finely adjust the alignment based on the pair of anterior eye observation images obtained by the anterior eye cameras 5A and 5B. Further, necessary adjustment of the imaging conditions such as fine adjustment of the scan position, fine adjustment of the measurement arm length and reference arm length, fine adjustment of the fixation target presentation position, focus adjustment, and insertion of a small pupil stop is performed.

(S10: photographing the fundus)
The ophthalmologic apparatus 1 performs OCT and imaging of the fundus oculi Ef. The acquired data is stored in the storage unit 212 or an external storage. The ophthalmologic apparatus 1 or another apparatus executes an imaging process and an analysis process based on the acquired data. The above is an example of auto alignment.

<Second operation mode>
Manual alignment will be described. When manual alignment is performed, the ophthalmologic apparatus 1 provides support for manually moving the optical system (housing 4) along the path indicated by the movement condition. For example, the movement mechanism 150 and the user interface 240 are controlled so as not to deviate from the route indicated by the movement condition. Such control is called operation support control.

  In manual alignment, the moving mechanism 150 operates according to an operation performed by the user using the operation unit 242. An example of operation support control using the moving mechanism 150 will be described. In the control condition information, an allowable range set based on the movement path of the optical system is recorded for each eye part. For example, the allowable range is set as a strip-like (band-like) region including a straight line connecting the advance start position and the advance end position. In addition, a strip-shaped region including a straight line connecting the current position of the optical system (housing 4) and the advance start position can be set as an allowable range.

An example of the allowable range is shown in FIG. Optics (housing 4) the current position indicated by Q _0, indicates the forward starting position in Q _1, showing a forward end position in Q _2. In this example, the optical system is moved from the current position Q ₀ to the advance start position Q ₁ along the first path A ₁ , and then from the advance start position Q ₁ to the advance end position along the second path A _2. the is moved to _{Q 2.} In such a case, the first allowable range w ₁ when the optical system is moved along the first path A ₁ and the second allowable range when the optical system is moved along the second path A _2. w ₂ and is set.

The width _{d 1} of the first tolerance range _{w 1,} second width _{d 2} of the allowable range _{w 2} is, for example, set in advance. The width of the allowable range may be a constant value or a set value according to a predetermined attribute. As an example of the latter, there is a value set in advance for each user. It is also possible to set an allowable range each time. For example, the width can be set according to the length of the route.

  The main control unit 211 (movement control unit 2112) can perform operation support control so that the optical system moves within an allowable range. For example, an operation that causes the optical system to be out of the allowable range can be invalidated (not accepted). In addition, the operation unit 242 can be controlled so that an operation that causes the optical system to be out of the allowable range cannot be performed. When the optical system is out of the allowable range, the movement control unit 2112 can control the moving mechanism 150 so as to return the optical system to the allowable range. Note that the operation support control is not limited to these, and any mode may be used as long as the purpose is to support the operation so that the optical system is moved along a predetermined route.

<Action and effect>
The operation and effect of the ophthalmologic apparatus according to the embodiment will be described.

  The ophthalmologic apparatus of the embodiment includes an optical system, a moving mechanism, a designation unit, and a condition setting unit.

  The optical system includes an objective lens, an irradiation system, and a fixation system. The irradiation system irradiates light to the eye to be examined through the objective lens. The fixation system includes a light beam output unit that outputs a fixation light beam, and projects the fixation light beam output from the light beam output unit onto the eye to be examined via the objective lens.

  In the above embodiment, the objective lens 22 corresponds to the objective lens. The illumination optical system 10 that irradiates the eye E with the illumination light and the OCT optical system (OCT unit 100, measurement arm, etc.) that irradiates the eye E with the measurement light LS for OCT correspond to the illumination system. The LCD 39 corresponds to a light beam output unit, and an optical element group that forms an optical path that guides the light beam output from the LCD 39 to the eye E corresponds to a fixation system.

  The moving mechanism moves the movable part, which is at least part of the optical system including the objective lens, into a first direction (z direction) along the optical axis of the objective lens and a second direction (x direction, y) orthogonal to the first direction. Direction). In the above embodiment, the portion of the optical system stored in the housing 4 corresponds to the movable part. Further, the moving mechanism 150 corresponds to a moving mechanism.

  The designation unit is used for designating a region of the eye to be examined that is irradiated with light by the irradiation system. In the above embodiment, the user interface 240 corresponds to a designation unit for manually designating a region of the eye to be examined. The data processing unit 230 (particularly the condition setting unit 232) corresponds to a designation unit for automatically designating a region of the eye to be examined.

  The condition setting unit sets the output position of the fixation light beam by the light beam output unit of the fixation system and the movement path of the movable part of the optical system by the movement mechanism based on the part of the eye to be examined designated by the designation unit. . In the above embodiment, the condition setting unit 232 (and the control condition information 212a) corresponds to the condition setting unit.

  According to such an embodiment, the fixation target can be presented at a position corresponding to the part of the eye to be examined, and the optical system can be moved along a path corresponding to the part of the eye to be examined. Accordingly, the fixation target can be recognized by the subject from the beginning to the end of the movement of the optical system, and the visibility of the fixation target can be improved.

  The ophthalmologic apparatus of the embodiment may include a control unit that performs control based on information set by the condition setting unit. The control unit controls the light beam output unit based on the output position set by the condition setting unit. Further, the control unit controls the movement mechanism based on the movement route set by the condition setting unit. In the above embodiment, the main control unit 211 (fixation control unit 2111 and movement control unit 2112) corresponds to the control unit.

  According to such a configuration, it is possible to automatically present the fixation target according to the part of the eye to be examined, and to automatically move the optical system along the path according to the part of the eye to be examined. Can do.

  In the embodiment, the condition setting unit is an initial position (advance start position) displaced in the second direction (x direction, y direction) from the optical axis of the objective lens (objective optical axis 22a) as a moving path of the movable part of the optical system. ) Can be set. Further, the control unit can control the moving mechanism so as to move the movable part of the optical system to the initial position.

  According to such a configuration, the initial position of the movement path of the optical system can be automatically set, and further, the optical system can be automatically arranged at this initial position.

  In the embodiment, the condition setting unit can set a straight path connecting the initial position and the inspection position as the moving path of the movable part of the optical system. The examination position is a position away from the eye to be examined by a predetermined working distance (working distance) in the first direction (z direction), and the forward end position in the above embodiment is an example.

  According to such a configuration, it is possible to automatically set a straight path along which the optical system is moved.

  In the embodiment, the control unit may be configured to control the moving mechanism so as to move the movable unit along the set straight path after moving the movable unit of the optical system to the initial position.

  According to such a configuration, the optical system can be automatically moved along a linear path that is automatically set.

  The ophthalmologic apparatus of the embodiment may include an operation unit and a control unit. The moving mechanism operates in response to an operation using the operation unit. The control unit can control the light beam output unit based on the output position set by the condition setting unit. Furthermore, the control unit can perform operation support control for supporting an operation for moving the movable unit of the optical system along the movement path set by the condition setting unit. In the above embodiment, the user interface 240 corresponds to the operation unit. The main control unit 211 corresponds to the control unit.

  As the operation support control, the control unit can control at least one of the moving mechanism and the operation unit so that the movable unit is moved within a preset allowable range based on the set movement route.

  According to such a configuration, when manually moving the optical system, it is possible to automatically present the fixation target according to the region of the eye to be examined and to support the movement operation of the optical system. Can do. Thereby, it is possible to facilitate the moving operation of the optical system.

  The ophthalmologic apparatus of the embodiment may include an imaging unit and a display control unit. The imaging unit captures a moving image of the anterior segment of the eye to be examined. The display control unit causes the display unit to display the moving image acquired by the photographing unit, and designates a target image as a target for moving the movable unit of the optical system based on the set movement path by the designation unit. Displayed on the moving image corresponding to the selected part.

  In the above embodiment, the illumination optical system 10 and the photographing optical system 30 correspond to a photographing unit. Alternatively, the anterior eye cameras 5A and 5B correspond to the photographing unit. The display control unit 2113 (and control condition information 212a) corresponds to the display control unit. The display means may be provided in the ophthalmologic apparatus (display unit 241), or the display means may be provided outside the ophthalmologic apparatus.

  According to such a configuration, it is possible to move the optical system with reference to the target image provided at a position corresponding to the designated region while referring to the anterior segment image.

  The embodiment described above is merely an example of the present invention. A person who intends to implement the present invention can arbitrarily make modifications (omission, substitution, addition, etc.) within the scope of the present invention.

DESCRIPTION OF SYMBOLS 1 Ophthalmology apparatus 10 Illumination optical system 22 Objective lens 39 LCD
100 OCT unit 150 moving mechanism 210 control unit 232 condition setting unit 240 user interface

Claims (8)

An objective lens, an irradiation system that irradiates light to the eye to be examined through the objective lens, and a light flux output unit that outputs a fixation light flux, and the fixation light flux output from the light flux output unit via the objective lens An optical system including a fixation system that projects onto the eye to be examined;
A moving mechanism for moving a movable part that is at least a part of the optical system including the objective lens in a first direction along the optical axis of the objective lens and a second direction orthogonal to the first direction;
A designating unit for designating a part of the eye to be inspected that is irradiated with light by the irradiation system;
An ophthalmologic apparatus comprising: a condition setting unit that sets an output position of the fixation light beam by the light beam output unit and a moving path of the movable unit by the moving mechanism based on a part specified by the specifying unit. A controller that controls the light flux output unit based on the output position set by the condition setting unit and controls the moving mechanism based on the movement path set by the condition setting unit. The ophthalmic apparatus according to claim 1. The condition setting unit sets at least an initial position displaced in the second direction from the optical axis of the objective lens as the movement path,
The ophthalmologic apparatus according to claim 2, wherein the control unit controls the moving mechanism to move the movable unit to the initial position. The condition setting unit sets, as the movement route, a linear route that connects the initial position and an examination position that is separated from the eye to be examined by a predetermined working distance in the first direction. An ophthalmic device according to claim 1. The said control part controls the said moving mechanism so that the said movable part may be moved along the said linear path | route after moving the said movable part to the said initial position. Ophthalmic equipment. It has an operation part,
The moving mechanism operates according to an operation using the operation unit,
The light flux output unit is controlled based on the output position set by the condition setting unit, and supports an operation for moving the movable unit along the moving path set by the condition setting unit. The ophthalmologic apparatus according to claim 1, further comprising a control unit that performs operation support control. The control unit controls, as the operation support control, at least one of the movement mechanism and the operation unit so that the movable unit is moved within an allowable range set in advance based on the movement route. The ophthalmic apparatus according to claim 6. An imaging unit that captures a moving image of the anterior segment of the eye;
The moving image acquired by the imaging unit is displayed on a display unit, and the target image for moving the movable unit based on the moving path is the moving image corresponding to the part designated by the designation unit The ophthalmologic apparatus according to claim 1, further comprising: a display control unit that displays the image at a position on the image.