JP6713297B2 - Ophthalmic equipment - Google Patents

Description

The present invention relates to ophthalmic devices.

In an ophthalmologic examination (including an arbitrary action such as examination, measurement, and imaging for obtaining data of an eye to be inspected), fixation is performed to inspect a desired part of the eye to be inspected. The fixation is realized by causing the subject to gaze at the fixation target presented in a predetermined direction.

Fixation includes internal fixation, external fixation, and peripheral fixation. The 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 the feature that the shape and position of the target (called internal fixation target) can be set in detail. External fixation is performed using a light source (such as an LED) provided on the outside of a housing in which the inspection optical system is stored, and when internal fixation cannot be performed, the eye to be examined is guided by guiding the line of sight of a fellow eye. It is a fixation method that adjusts the direction of. Peripheral fixation is performed by using a plurality of light sources (LED, etc.) arranged around the objective lens, and is a fixation method in which these light sources are selectively turned on to largely rotate the eye to be examined in a desired direction. is there. Peripheral fixation is used in examinations around the fundus of the eye.

Patent Document 1 discloses a technique of 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 moving internal fixation target.

JP, 2004-141563, A

The scene where the visibility of the internal fixation target should be taken into consideration is not limited to the movement. For example, when the inspection optical system is aligned with the eye to be inspected, the inspection optical system (optical head) is brought close to the eye to be inspected while the internal fixation target is presented. When the internal fixation light flux passes through a position away from the optical axis of the objective lens as when inspecting the optic nerve head, the internal fixation light flux reaches the fundus when the distance between the optical head and the subject's eye 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 edge of the visual field at a certain stage. Therefore, the subject may not be able to recognize the internal fixation target and may not be able to perform the alignment properly. Further, when the internal fixation target enters the visual field, the eye to be examined may suddenly rotate, causing flare in the observed image, which may obstruct the observation and alignment of the eye to be examined.

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 moving mechanism, a control unit, and a designation unit . The optical system includes an objective lens, an irradiation optical system that irradiates the subject's eye with light through the objective lens, and a fixation system that projects a fixation light beam onto the subject's eye through the objective lens. The moving mechanism moves at least a part of the optical system including the objective lens. The control unit changes at least one of the projection position and the shape of the fixation light flux by controlling the fixation system according to the movement of at least a part of the optical system by the movement mechanism. The designating unit is a unit for designating a region of the subject's eye to which light is irradiated by the irradiation optical system. The control unit includes a setting unit. The setting unit sets an initial aspect and a final aspect of the fixation light flux based on the part designated by the designating unit. The control unit changes at least one of the projection position and the shape of the fixation light flux from the initial mode to the final mode.

According to the embodiment, the visibility of the internal fixation target can be improved.

The schematic diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The schematic diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The schematic diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The schematic diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The schematic diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The schematic diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The flowchart showing an example of operation|movement of the ophthalmologic apparatus which concerns on embodiment. FIG. 6 is a schematic diagram for explaining an example of the operation of the ophthalmologic apparatus according to the embodiment. FIG. 6 is a schematic diagram for explaining an example of the operation of the ophthalmologic apparatus according to the embodiment. FIG. 6 is a schematic diagram for explaining an example of the operation of the ophthalmologic apparatus according to the embodiment.

Some embodiments of the present invention will be described in detail with reference to the drawings. The embodiment may be any ophthalmologic apparatus that includes an irradiation optical system that irradiates the eye to be inspected with light through an objective lens, and a fixation system that projects a fixation light beam onto the eye to be inspected 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 the return light from the eye to be inspected of the light emitted by the irradiation optical system. Hereinafter, an ophthalmologic apparatus that combines a swept source OCT and a fundus camera will be described, but the embodiment is not limited to this.

<Constitution>
As shown in FIG. 1, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and a calculation control unit 200. The fundus camera unit 2 is provided with an optical system substantially similar to that of the conventional fundus camera. The OCT unit 100 is provided with an optical system and a mechanism for performing OCT. The arithmetic and control unit 200 includes a processor. A chin rest and a forehead support for supporting the subject's face are provided at positions facing the fundus camera unit 2.

In the present 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 (eg, SPLD (Simple Digital Prog)). It means a circuit such as (Complex Programmable Logic Device) or FPGA (Field Programmable Gate Array). The processor realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

<Ocular fundus camera unit 2>
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef of the eye E to be inspected. Images obtained by photographing the fundus Ef (called fundus images, fundus photographs, etc.) include observation images and photographed images. The observation image is obtained, for example, by shooting a moving image 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 capable of acquiring a fluorescein fluorescence image, an indocyanine green fluorescence image, a spontaneous fluorescence 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 to be inspected. The measurement light from the OCT unit 100 is guided to the subject's eye E through the optical path inside 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 condenser lens 13, passes through the visible cut filter 14, and becomes near-infrared light. Become. Further, the observation illumination light is once focused near the photographing light source 15, is 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 portion of the perforated mirror 21 (the area around the hole), 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 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. , Is reflected by the mirror 32 via the photographing focusing lens 31. Further, this return light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the CCD image sensor 35 by the condenser lens 34. The CCD image sensor 35 detects return light at a predetermined frame rate, for example. An observation image of the fundus Ef is obtained when the imaging optical system 30 is in focus on the fundus Ef, and an observation image of the anterior segment is obtained when the focus is on the anterior segment.

The photographing light source 15 is, for example, a visible light source including a xenon lamp or an LED. The light (imaging illumination light) output from the imaging light source 15 passes through the same path as the observation illumination light and is applied to the fundus Ef. The return light of the photographing illumination light from the eye E to be examined is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is condensed 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 luminous flux (fixed luminous flux) output from the LCD 39 is reflected by the half mirror 33A and is reflected by the mirror 32, passes through the photographing focusing lens 31 and the dichroic mirror 55, and is then transmitted through the apertured mirror 21. Pass the section. The fixation light flux that has passed through the hole portion of the perforated mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus Ef. The fixation position of the eye E can be changed by changing the display position of the fixation target on the screen of the LCD 39.

The light flux output unit that outputs the fixation light flux is not limited to the LCD 39. The light flux output unit may be configured so that the fixation position can be changed, and is, for example, a matrix LED in which a plurality of LEDs are two-dimensionally arranged, a combination of a light source and a variable diaphragm (a liquid crystal diaphragm, etc.), or the like. You can

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 to be inspected. The focus optical system 60 generates a split index used for focus adjustment on the eye E to be inspected.

The alignment light output from the LED 51 of the alignment optical system 50 passes through the diaphragms 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, and passes through the hole portion of the perforated mirror 21. The light passing through the hole of the perforated mirror 21 passes through the dichroic mirror 46 and is projected onto the eye E to be inspected by the objective lens 22.

The corneal reflection light of the alignment light passes through the objective lens 22, the dichroic mirror 46 and the hole, and a part of the light passes through the dichroic mirror 55, passes through the photographing focusing lens 31, and is reflected by the mirror 32. 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 34. Based on the light-receiving image (alignment index image) by the CCD image sensor 35, it is possible to perform manual alignment and automatic alignment similar to the conventional one.

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 reflecting rod 67 can be inserted into and removed from the illumination optical path.

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

The fundus reflected light of the focus light is detected by the CCD image sensor 35 through the same path as the cornea reflected light of the alignment light. Based on the light-receiving image (split index image) by the CCD image sensor 35, manual alignment and automatic 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 in the photographing optical path between the perforated mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus (+) lens for correcting intense hyperopia, and is, for example, a +20D (diopter) convex lens. The diopter correction lens 71 is a minus (-) lens for correcting intense myopia, and is, for example, a -20D concave lens. The diopter correction lenses 70 and 71 are attached to, for example, a turret plate. The turret plate is formed with a hole for the case where neither of the diopter correction lenses 70 and 71 is applied.

The dichroic mirror 46 combines the optical path for fundus imaging and the optical path for OCT. The dichroic mirror 46 reflects light in the wavelength band used for OCT and transmits light for fundus imaging. On 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 OCT optical path. This change of the optical path length is used for correction of the optical path length according to the axial length of the eye E to be inspected, adjustment of the interference state, and the like. 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 arranged at a position optically conjugate with the pupil of the eye E to be inspected. The optical scanner 42 changes the traveling direction of the measurement light LS that passes through the optical path for OCT. As a result, the subject's eye E is scanned with the measurement light LS. The optical scanner 42 is capable of deflecting the measurement light LS in any direction on the xy plane, and includes, for example, a galvano mirror that deflects the measurement light LS in the x direction and a galvano 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 executing the OCT of the eye E to be inspected. The configuration of this optical system is similar to that of the conventional swept source OCT. That is, this optical system splits the light from the wavelength-swept (wavelength scanning) 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 passing through the reference optical path. It includes an interference optical system that causes interference to generate interference light and detects the interference light. The 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 and control unit 200.

The light source unit 101 includes a wavelength-swept (wavelength scanning) light source that changes the wavelength of emitted light at a high speed, similar to a general swept source OCT. The wavelength swept 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 the polarization state thereof is adjusted. Further, the light L0 is guided to the fiber coupler 105 by the optical fiber 104 and split 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, converted into a parallel light flux, and 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 compensating member 113 acts to match dispersion characteristics between the reference light LR and the measurement light LS.

The corner cube 114 turns back the traveling direction of the incident reference light LR in the opposite direction. The incident direction and the emitting direction of the reference light LR 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, whereby 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 of the measurement light LS (measurement optical path, measurement arm) and the optical path of the reference light LR (reference optical path, reference arm). Both of the 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. Further, it is possible to change the difference between the measurement optical path length and the reference optical path length by using an optical member other than these.

The reference light LR passing 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 flux into a focused light flux 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 to adjust its polarization state, guided to the attenuator 120 by the optical fiber 119 to adjust the light quantity, and guided to the fiber coupler 122 by the optical fiber 121. Get 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 flux 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 is reflected by the dichroic mirror 46 via the relay lens 45, is refracted by the objective lens 22, and enters the eye E to be inspected. The measurement light LS is scattered/reflected at various depth positions of the eye E to be inspected. 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 synthesizes (interferes) the measurement light LS incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121 to generate interference light. The fiber coupler 122 splits the interference light at a predetermined splitting ratio (for example, 1:1) to generate a pair of interference light LC. The pair of interference lights LC are guided to the detector 125 through the 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 detect a pair of interference lights LC, and outputs the difference between the detection results of these. The detector 125 sends the detection result (detection signal) to a DAQ (Data Acquisition System) 130.

The clock KC is supplied from the light source unit 101 to the DAQ 130. The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept within the predetermined wavelength range by the wavelength swept light source. The light source unit 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then determines the clock KC based on the result of detecting the combined light. To 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 and control unit 200.

<Arithmetic control unit 200>
The arithmetic and 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 also executes various arithmetic processes. For example, the arithmetic and control unit 200 performs signal processing such as Fourier transform on the spectral distribution based on the detection result obtained by the detector 125 for each series of wavelength scanning (for each A line), and thereby, in each A line. Form a reflection intensity profile. Further, the arithmetic and control unit 200 forms image data by imaging the reflection intensity profile of each A line. The arithmetic processing therefor is similar to that of the conventional swept source OCT.

The arithmetic and 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 and control unit 200 may include an operation device, an input device, a display device, and the like.

<Control system>
An example of the configuration 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. The control unit 210 includes a processor. The control unit 210 includes a main control unit 211, a storage unit 212, a fixation setting unit 213, and a position information generation unit 214.

<Main control unit 211>
The main control unit 211 performs various controls. For example, the main control unit 211 includes a photographing 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. Further, 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 drive 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, for example, the fundus camera unit 2 (or at least a part of the optical system stored therein). The moving mechanism 150 may be capable of moving the OCT unit 100 (or at least a part of the optical system stored therein). The moving mechanism 150 includes one or more actuators 151. The actuator 151 includes, for example, a pulse motor controlled by the main controller 211, and generates a driving force for moving the fundus camera unit 2 and the like. The driving force generated by the pulse motor 151 is transmitted by a mechanism (not shown) to move the fundus camera unit 2 and the like. As a result, the fundus camera unit 2 and the like are moved three-dimensionally. The moving mechanism 150 is, for example, an x moving mechanism including a first actuator and a mechanism for converting the first driving force generated by the first actuator into movement in the x direction, the second actuator, and the second driving force generated by the second actuator. To a movement in the y direction, and a z movement mechanism including a third actuator and a mechanism for converting the third driving force generated by the third actuator into movement in the z direction. ..

<Memory unit 212>
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, OCT image data, fundus image data, and eye information. The eye information includes subject information such as a patient ID and name, left/right eye identification information, electronic medical record information, and the like.

Further, the storage unit 212 may store in advance information (fixation information) for performing control related to fixation. In an example of the fixation information, the part of the eye and the mode of the fixation target are associated with each other. This fixation information associates the display position of the fixation target on the LCD 39 with each of two or more parts of the eye. Alternatively, this fixation information associates the shape of the fixation target displayed on the LCD 39 with each of two or more parts of the eye.

The mode of the fixation target recorded in the fixation information may include a mode of change of the fixation target. In the present embodiment, at least one of the projection position and the shape of the fixation light beam on the eye E is changed according to the movement of the fundus camera unit 2 or the like. In order to realize such control, the fixation information associates the position of the fundus camera unit 2 and the like with the projection position and/or shape of the fixation light flux. The position of the fundus camera unit 2 or the like is detected by any method. This position detection is performed using, for example, the moving mechanism 150 or an encoder provided in the fundus camera unit 2 or the like. Alternatively, this position detection may be performed by referring to the control history of the moving mechanism 150 by the main control unit 211. Alternatively, this position detection may be performed by a method using two or more anterior eye cameras disclosed in Japanese Patent Laid-Open No. 2013-248376.

FIG. 4 shows an example of the configuration of the screen of the LCD 39. 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. The x-direction (horizontal direction) array is assigned coordinates 0 to 50 from left to right, and the y-direction (vertical direction) array is assigned coordinates 0 to 50 from bottom to top. Is given.

Characters attached to some pixels of the screen 39a indicate the position of the fixation target (bright spot) corresponding to the part of the eye. When the eye to be inspected is the right eye, the pixel “M” at (x, y)=(25, 25) indicates a fixation target corresponding to the macula, and the pixel “C at (x, y)=(20, 26)”. ] Indicates a fixation target corresponding to the center of the fundus, a pixel "W" of (x, y)=(17, 26) indicates a fixation target corresponding to wide scan, and (x, y)=(10, Pixel “C” in 26) indicates a fixation target corresponding to the optic disc. When the eye to be inspected is the left eye, the pixel “M” of (x, y)=(25, 25) indicates the 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, a pixel “W” at (x, y)=(33, 26) indicates a fixation target corresponding to wide scan, and (x, y)=( The pixel "C" in 40, 26) indicates the fixation target corresponding to the optic disc. Further, eight pixels “2” to “9” arranged in a circular shape indicate fixation targets corresponding to eight positions in the fundus peripheral portion. The optical axis of the objective lens 22 (objective optical axis) is arranged at the lower left corner of the pixel “M”.

An example of the fixation information is shown in FIG. The fixation information 212a associates the initial position and the final position of the fixation target with the part of the eye (fixation position) to be inspected. The pixel “M” is associated with both the initial position and the final position in the part “macular”. The initial position “M” and the final position “C” are associated with the region “center of the fundus”. An initial position “M” and a final position “W” are associated with the part “wide”. The initial position “M” and the final position “D” are associated with the part “optic disc”.

In this example, the position of the fixation target for the region "macular" is unchanged, but the fixation target is moved for the regions "center of the fundus", "wide", and "optic disc". Similarly, for the pixels “2” to “9” corresponding to the peripheral part of the fundus, the pixel “M” can be similarly set as the initial position. It should be noted that the position of the fixation target may be invariable with respect to a region where the final position is relatively close to the objective optical axis, such as “center of fundus” or “wide”.

The initial positions of the regions “center of the fundus”, “wide”, “optic nerve head” and the peripheral part of the fundus may be other than the pixel “M”. For example, the initial position may be set to any position on the macula “M” side of the final position.

Another example of fixation information is shown in FIG. The fixation information 212b associates the initial form and the final form of the fixation target with the part of the eye (fixation position) to be examined. The pixel “M” is associated with both the initial form and the final form in the part “macular”. The initial form “Line MC” and the final form “C” are associated with the region “center of the fundus”. “Line MC” indicates a straight line (segment) connecting the pixel “M” and the pixel “C”. The initial form “Line MW” and the final form “W” are associated with the part “wide”. “Line MW” indicates a straight line connecting the pixel “M” and the pixel “W”. The initial form “Line MD” and the final form “D” are associated with the region “optic disc”. “Line MD” indicates a straight line (segment) connecting the pixel “M” and the pixel “D”.

In this example, the shape of the fixation target remains unchanged for the region "macular", but the shape of the fixation target changes for the regions "center of the fundus", "wide", and "optic disc". Specifically, for these parts, the shape of the fixation target changes from the bright line connecting the initial position and the final position shown in FIG. 5 to the bright point showing the final position. The same applies to the pixels "2" to "9" corresponding to the fundus peripheral portion. Note that the shape of the fixation target may be invariable with respect to a portion whose final position is relatively close to the objective optical axis, such as “center of the fundus” or “wide”.

The fixation information is not limited to these. For example, the form of the fixation target is not limited to a straight line or a point, and may be any one-dimensional shape or any two-dimensional shape. It is also possible to display information different from the fixation target on the LCD 39. For example, an image of an arrow pointing to the final position of the fixation target is displayed using the pixel “M” and the pixels around it.

<Fixation setting unit 213>
In this embodiment, the part of the eye to be inspected (fixed position) is designated. The designation of the part is manually performed using the user interface 240, for example. Alternatively, the control unit 210 may specify the part based on the selection result of the inspection mode or the analysis mode. In addition, in follow-up observation, pre-operative and post-operative observation, etc., the control unit 210 can acquire the site designated in the past examination from the electronic medical record information or the like and designate it again.

The fixation setting unit 213 sets the initial form and the final form of the fixation target (fixation light flux) based on the part of the eye thus designated. This processing is performed with reference to the fixation information (for example, the fixation information 212a or 212b) stored in the storage unit 212. For example, when the optic disc is designated as the part of the eye, the fixation setting unit 213 acquires the initial position “M” and the final position “D” associated with the “optic disc” in the fixation information 212a. .. These are set as information for controlling the fixation target.

The fixation setting unit 213 may be configured to set further information for controlling the fixation target. For example, it is possible to set information indicating the timing of changing the fixation target. When the fixation information 212a illustrated in FIG. 5 is applied, the fixation setting unit 213 sets, for example, the movement timing of each stage when the fixation target is gradually moved pixel by pixel from the initial position to the final position. .. As a specific example thereof, a distance (distance in the z direction) between a position (last retracted position) such as the fundus camera unit 2 where the distance from the eye E to be inspected is the longest and a position corresponding to a working distance (working distance). , By associating a plurality of positions between the last retracted position and the working distance position with a plurality of pixels between the initial position and the final position by dividing by the number of pixels between the initial position and the final position You can

Similarly, when the fixation information 212b shown in FIG. 6 is applied, the timing of shortening the length of the bright line is set to a plurality of positions in the z direction (for example, a plurality of positions between the last retracted position and the working distance position). Position). Further, it is possible to set the timing of displaying the arrow image indicating the final position of the fixation target and the timing of not displaying it in association with a plurality of positions in the z direction. For example, when the fundus camera unit 2 or the like is located within a predetermined distance from the last retracted position, an arrow image is displayed, and when the fundus camera unit 2 or the like is located outside this range, the arrow image is not displayed. Can be controlled.

<Position information generation unit 214>
The position information generation unit 214 generates position information indicating the position of the fundus camera unit 2 or the like.
When the moving mechanism 150, the fundus camera unit 2 or the like is provided with an encoder, the position information generation unit 214 can obtain the position of the fundus camera unit 2 or the like based on the signal output from the encoder. When the main controller 211 controls the moving mechanism 150, the position information generator 214 can obtain the position of the fundus camera unit 2 or the like based on the control history of the moving mechanism 150 by the main controller 211. Further, when two or more anterior eye cameras are provided, the position information generation unit 214 executes the arithmetic processing disclosed in Japanese Patent Laid-Open No. 2013-248376, so that the fundus camera unit 2 and the eye to be examined. The relative position with respect to E can be determined.

In this way, the position information generation unit 214 may generate position information of the fundus camera unit 2 and the like expressed in a predetermined coordinate system (for example, an xyz coordinate system that represents the moving state of the moving mechanism 150), Alternatively, position information indicating the relative position between the fundus camera unit 2 or the like and the eye E to be inspected may be generated.

<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), similar to 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 the reflection intensity profile of a plurality of A lines (lines in the z direction) arranged along the scan line. A data set including 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" may be equated with "image" based on it. Further, the part of the eye E to be inspected may be identified with the image representing the part.

<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 brightness correction and dispersion correction. Further, the data processing unit 230 performs image processing and analysis processing on the image (fundus image, anterior segment 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.

<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 may be constructed that do not include at least a portion of user interface 240. For example, the display device may be an external device connected to the ophthalmic device.

<motion>
The operation of the ophthalmologic apparatus 1 will be described. An example of the operation is shown in FIG.

(S1: Designate a region to be imaged)
First, the part of the eye E to be inspected, which is the target of OCT or fundus imaging, is designated. The designation of the imaging region is performed by the user (inspector) or the control unit 210 as described above.

(S2: Setting the initial form and final form of the fixation target)
The fixation setting unit 213 sets the initial form and the final form of the fixation target (fixation light flux) based on the part of the eye designated in step S1. This processing is performed with reference to the fixation information stored in the storage unit 212. For example, when the imaging region “optic disc” is designated in step S1, the fixation setting unit 213 sets the initial position “M” and the final position “D” corresponding to the “optic disc” in the fixation information 212a illustrated in FIG. To get.

(S3: Display the fixation mark in the initial form)
The main control unit 211 causes the LCD 39 to display the fixation target in the initial form set in step S2. For example, when the initial position “M” is set in step S2, the main control unit 211 determines that the pixel “(x, y)=(25, 25)” among the plurality of pixels arranged on the screen 39a of the LCD 39 is displayed. Only M” is turned on. As previously mentioned, pixel "M" is located on the objective optical axis (more specifically, pixel "M" is one of the four pixels closest to the objective optical axis).

(S4: retract the optical system to observe the anterior segment)
The user or the main control unit 211 causes the optical system (fundus camera unit 2 or the like) to move backward to observe the anterior segment of the subject's eye E by operating the moving mechanism 150, and arranges it, for example, at the last retracted position. The anterior segment observation is performed by the main control unit 211 displaying a moving image on the display unit 241 as an observation image (moving image) of the anterior segment obtained using the observation illumination light (near infrared light) described above. Alternatively, it may be a moving image of the anterior segment obtained by at least one of the anterior segment cameras 5A and 5B. The anterior segment cameras 5A and 5B will be described later.

The presentation state of the fixation target when the optical system is retracted is shown in FIG. 8A. At this stage, the pixel “M” is lit as the initial form fixation target (initial fixation target T _S ). Since the initial fixation target T _S is arranged on the objective optical axis 22 a, the fixation light flux output from the pixel “M” is projected onto the fundus Ef of the eye E through the objective lens 22. Therefore, the subject can visually recognize the initial fixation target T _S.

The fixation target T _E is the pixel “D” corresponding to the “optic disc” and is used as the final fixation target in this example. In this example, the initial fixation target T _S is displayed first, but in the conventional ophthalmologic apparatus, the pixel “D” is displayed from the beginning to the end. At the stage of step S4, the fixation light flux DP output from the pixel “D” cannot pass through the objective lens 22 and thus is not projected onto the fundus Ef. Therefore, in the case of the conventional ophthalmologic apparatus, the subject cannot visually recognize the fixation target at this stage.

Note that reference numeral 4 in FIG. 8A represents a housing in which the optical system is stored. The housing 4 stores, for example, the fundus camera unit 2 and the OCT unit 100. On the surface (front surface) of the housing 4 on the eye E side, two anterior segment cameras 5A and 5B disclosed in JP2013-248376A are provided. The position information generation unit 214 obtains the three-dimensional position of the eye E to be inspected by analyzing two anterior ocular segment images acquired substantially simultaneously from different directions by the anterior ocular segment cameras 5A and 5B. This three-dimensional position is a relative position of the eye E to be inspected with respect to the anterior segment cameras 5A and 5B (that is, the optical system stored in the fundus camera unit 2 and the like). The analysis of the two anterior ocular segment images may be the same as the analysis disclosed in JP2013-248376A.

(S5: Align the pupil center with the center of the anterior segment image)
The user or the main control unit 211 analyzes the observation image of the anterior segment of the eye so that the center of the pupil of the eye E is located at the frame center of the observation image (or within a predetermined range including the frame center). 4 is moved in the x direction or the y direction. Thereby, the x position and the y position of the optical system are adjusted so that the objective optical axis 22a is arranged at the center of the pupil of the eye E to be inspected.

(S6: Start advance of optical system)
The user or the main control unit 211 starts moving the housing 4 forward by operating the moving mechanism 150. Thereby, the housing 4 is moved in the +z direction from the most retracted position toward the eye E to be inspected.

The two anterior segment cameras 5A and 5B capture a moving image at a predetermined time interval (imaging rate), and the position information generation unit 214 sequentially calculates the relative position between the eye E to be inspected and the optical system in real time.

(S7: The morphological change of the fixation target is started)
The main control unit 211 changes the form of the fixation target based on the position information sequentially acquired by the position information generation unit 214. In this example, the main control unit 211 changes the position of the fixation target displayed on the LCD 39 according to the change in the relative position between the eye E to be inspected and the optical system. For example, the main control unit 211 moves the display position of the fixation target by a predetermined unit distance in response to a change in the z-direction distance between the eye E to be inspected and the optical system by a predetermined unit amount. .. As a specific example, the main control unit 211 changes the display position of the fixation target to the initial fixation target T each time the distance in the z direction between the eye E to be inspected and the optical system decreases (or increases) by a unit amount. moving from _S side by one pixel in the final fixation target T _E side. Here, the predetermined unit amount and the predetermined unit distance are recorded in advance in the fixation information, for example.

FIG. 8B shows a state in which the fixation target is displayed between the initial fixation target T _S and the final fixation target T _E. At this stage, the housing 4 is located between the last retracted position and the position corresponding to the working distance (working distance position), and the LCD 39 is located between the initial fixation target T _S and the final fixation target T _E. intermediate fixation target T _H is displayed. At any time during the movement of the housing 4, the display position of the intermediate fixation target T _H is the fixation light beam HP, so as to pass through the objective lens 22 (i.e. the eye E is visually recognized an intermediate fixation target T _H Controlled). This control is performed based on the fixation information, for example. Note that in the state shown in FIG. 8B, the fixation light flux DP output from the pixel “D” cannot still pass through the objective lens 22. Therefore, in the case of the conventional ophthalmologic apparatus, the subject cannot visually recognize the fixation target even at this stage.

(S8: Did you reach the WD position (nearby)?)
The forward movement of the optical system and the morphological change of the fixation target are executed until it is determined that the housing 4 has reached (in the vicinity of) the working distance position. Whether or not the housing 4 has reached (in the vicinity of) the working distance position is determined based on the position information obtained in real time by the position information generation unit 214.

The “vicinity” of the working distance is set in advance at least in the range in which the fixation light flux DP output from the pixel “D” passes through the objective lens 22. Further, in response to the housing 4 being advanced to a predetermined position, the main control unit 211 causes the main lens unit 211 to move the focus of the optical system from the anterior ocular segment observation focus to the fundus observation focus (not shown). ) Is inserted. Before the housing 4 reaches the working distance position, the displayed observation image switches from the anterior segment observation image to the fundus observation image.

(S9: The final target fixation target is displayed)
When the housing 4 reaches (in the vicinity of) the working distance position, the main control unit 211 lights the pixel “D” to display the final fixation target T _E. The final fixation target T _E is the position of the fixation target corresponding to the optic disc that is the imaging region (that is, the target region for OCT or fundus imaging) designated in step S1.

The state where the final fixation target T _E is displayed is shown in FIG. 8C. At this stage, the housing 4 is placed at the working distance position, and the final fixation target T _E is displayed on the LCD 39. Thus, in this example, the subject can always view the fixation target while moving the housing 4 from the last retracted position to the working distance position. Specifically, the subject first visually recognizes the initial fixation target T _S displayed at the center (pixel “M”) of the LCD 39, and gradually increases toward the final fixation target T _E in the intermediate stage. viewing the moving intermediate fixation target T _H. As a result, the fixation position of the eye E to be examined is guided to the final fixation target T _E corresponding to the imaging region.

It should be noted that the housing 4 may be moved backward after the forward movement is started. In that case, the main control unit 211 sets the display position of the fixation target T to the initial fixation target T according to the distance (the amount of increase in the relative distance between the eye E to be inspected and the optical system) that the housing 4 has moved backward. It can be moved to the _S side.

(S10: Fine adjustment of alignment)
The user or the ophthalmologic apparatus 1 performs alignment of the optical system with respect to the eye E to be inspected, for example, based on the alignment index. As a result, the result of the alignment performed in steps S6 to S9 is finely adjusted. It is also possible to perform fine adjustment of alignment based on a pair of anterior segment observation images obtained by the two anterior segment cameras 5A and 5B.

(S11: Adjust shooting conditions)
The user or the ophthalmologic apparatus 1 adjusts various imaging conditions such as fine adjustment of scan position, fine adjustment of measurement arm length and reference arm length, fine adjustment of presentation position of fixation target, focus adjustment, insertion of small pupil diaphragm. To do.

(S12: Photograph the fundus)
The ophthalmologic apparatus 1 executes OCT and imaging of the fundus Ef. The acquired data is stored in the storage unit 212 or an external storage. Further, the ophthalmologic apparatus 1 or another apparatus executes an imaging process and an analysis process based on the acquired data.

<Action/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, and a control unit. The optical system includes an objective lens, an irradiation optical system that irradiates the subject's eye with light through the objective lens, and a fixation system that projects a fixation light beam onto the subject's eye through the objective lens. In the above embodiment, the objective lens 22 corresponds to the objective lens, the illumination optical system 10 and the measurement arm correspond to the irradiation optical system, and the optical path from the LCD 39 to the objective lens 22 corresponds to the fixation system.

The moving mechanism operates to move at least a part of the optical system including the objective lens. In the above embodiment, the moving mechanism 150 corresponds to the moving mechanism.

The control unit changes at least one of the projection position and the shape of the fixation light flux by controlling the fixation system according to the movement of at least a part of the optical system by the movement mechanism. In the above embodiment, the control unit 210 corresponds to the control unit.

According to such an embodiment, when the optical system is moved in a state where the fixation target is presented in alignment or the like, the projection position and shape of the fixation light flux can be changed according to the movement of the optical system. .. Therefore, the visibility of the fixation target can be improved so that the subject can visually recognize the fixation target continuously. Thereby, alignment etc. can be performed appropriately. Further, there is no inconvenience that the eye to be examined suddenly rotates when the fixation target enters the visual field and flare occurs in the observed image.

The ophthalmologic apparatus of the embodiment may include a designating unit for designating a region of the subject's eye to which the irradiation optical system emits light. In this case, the control unit can switch the mode of change in at least one of the projection position and the shape of the fixation light flux, according to the region designated by the designation unit. The designation of the part is performed manually or automatically.

In the above embodiment, the user interface 240 and the control unit 210 correspond to the designation unit. Further, the control unit 210 of the above-described embodiment refers to the fixation information 212a illustrated in FIG. 5 to refer to the fixation information 212a shown in FIG. Position) and the last projection position (final position) can be switched. Here, the fixation information 212a can include one or more projection positions arranged between the initial position and the final position and information indicating the timing of changing the projection position. In this case, the control unit 210 executes control for sequentially projecting the fixation light flux at three or more projection positions according to the fixation information 212a and control for changing the projection position at a timing according to the fixation information 212a. ..

As another example, the control unit 210 refers to the fixation information 212b illustrated in FIG. 6 to determine the initial shape (initial form) of the fixation light flux in accordance with the designated part (macular spot, optic disc, etc.). And the last form (final form) can be switched. Here, the fixation information 212b may include one or more intermediate forms applied between the initial form and the final form, and information indicating the timing of changing the form. In this case, the control unit 210 performs control for changing the form of the fixation light flux into three or more forms according to the fixation information 212b and control for changing the form of the fixation light flux at a timing according to the fixation information 212b. Execute.

With such a configuration, it is possible to change the projection position and the shape of the fixation light flux in a mode according to the designated site (imaging site or the like). Therefore, the control for allowing the subject to continuously view the fixation target can be executed according to the designated region. Thereby, it is possible to improve the visibility regardless of the designated portion.

In the embodiment, the control unit may include a setting unit that sets an initial mode and a final mode of the fixation light flux based on the site designated by the designating unit. In this case, the control unit can change at least one of the projection position and the shape of the fixation light flux from the initial mode to the final mode.

In the above embodiment, the fixation setting unit 213 corresponds to the setting unit. Further, examples of the initial mode include the initial position of FIG. 5 and the initial form of FIG. 6, and examples of the final mode include the final position of FIG. 5 and the final form of FIG.

With such a configuration, it is possible to automatically set the manner of change of the fixation target according to the movement of the optical system according to the designated portion. Therefore, the operability and convenience of the ophthalmologic apparatus are improved.

The setting unit sets the initial mode and the initial mode so that the distance between the fixation beam in the initial mode and the optical axis of the objective lens is shorter than the distance between the fixation beam in the final mode and the optical axis of the objective lens. It may be configured to set the final aspect.

In the above-described embodiment, for example, when the designated site is the optic disc, the fixation setting unit 213 sets the pixel “M” on the objective optical axis 22a as the initial position, and sets the pixel “M” at a position away from the objective optical axis 22a. Pixel "D" can be set as the final position. Similarly, when the designated portion is the optic disc, the fixation setting unit 213 sets a straight line connecting the pixel “M” on the objective optical axis 22a and the pixel “D” located away from it as an initial form. Further, the pixel “D” at a position apart from the objective optical axis 22a can be set as the final position.

With such a configuration, it is possible to guide the fixation to the designated site while starting the change of the form (projection position, shape) of the fixation target from the vicinity of the objective optical axis with high visibility.

In the embodiment, the control unit is configured to change at least one of the projection position and the shape of the fixation light flux from the initial aspect to the final aspect according to the reduction in the distance between the objective lens and the eye to be inspected by the moving mechanism. May be done.

In the above-described embodiment, for example, when the designated portion is the optic nerve head, the control unit 210 changes the display position of the fixation target from the pixel “M” to the pixel “C” as the housing 4 approaches the eye E to be inspected. Can be made.

Thus, the embodiment may be configured as follows: the fixation system includes a light flux output unit (LCD 39) that outputs the fixation light flux; the setting unit outputs the fixation light flux initially by the light flux output unit. Setting the position and the final output position; the control unit changes the output position of the fixation light flux by the light flux output unit from the initial output position to the final output position according to the shortening of the distance between the objective lens and the eye to be examined. Let

Further, in the above-described embodiment, when the designated portion is the optic nerve head, the control unit 210 determines the pixel “C” from the bright line connecting the pixel “M” and the pixel “C” as the housing 4 approaches the subject's eye E. It is possible to change the fixation target up to the bright spot in ".

Thus, the embodiment may be configured as follows: the fixation system includes a light flux output unit (LCD 39) that outputs the fixation light flux; the setting unit outputs the fixation light flux initially by the light flux output unit. The shape and the final output shape are set; the control unit changes the output shape of the fixation light flux by the light flux output unit from the initial output shape to the final output shape according to the reduction in the distance between the objective lens and the eye to be examined. Let

The ophthalmologic apparatus of the embodiment may include an operation unit (for example, the operation unit 242). Furthermore, the moving mechanism may be configured to move at least a part of the optical system in response to an operation performed using the operation unit. That is, the ophthalmologic apparatus of the embodiment may be configured to move the optical system by manual operation. Thereby, the visibility of the fixation target in the manual alignment can be improved.

In the embodiment, the movement mechanism may include an actuator (for example, the actuator 151) controlled by the control unit. Further, the control unit may be configured to coordinately control the actuator and the fixation system. As a result, the movement of the optical system and the movement or deformation of the fixation target can be linked, and the visibility of the fixation target in the automatic alignment can be improved.

The ophthalmologic apparatus of the embodiment may include a position specifying unit that specifies the position of at least part of the optical system moved by the moving mechanism. In the above-described embodiment, the position specifying unit includes the position information generating unit 214, and the position of the optical system is specified by, for example, using the encoder provided in the moving mechanism 150 or the fundus camera unit 2 or the main control. This is performed by referring to the control history of the moving mechanism 150 by the unit 211, or by using two or more anterior segment cameras. Further, the control unit controls the fixation system based on the position of the optical system specified by the position specifying unit.

According to this configuration, it is possible to preferably change the projection position and shape of the fixation light flux while monitoring the position of the optical system.

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 (omissions, substitutions, additions, etc.) within the scope of the gist of the present invention.

1 Ophthalmologic apparatus 10 Illumination optical system 22 Objective lens 39 LCD
100 OCT unit 150 Moving mechanism 210 Control unit

Claims (9)

An optical system including an objective lens, an irradiation optical system that irradiates the eye to be inspected with light through the objective lens, and a fixation system that projects a fixation light beam onto the eye to be inspected through the objective lens,
A moving mechanism for moving at least a part of the optical system including the objective lens;
By controlling the fixation system according to the movement of at least a part of the optical system by the movement mechanism, a control unit that changes at least one of the projection position and the shape of the fixation light beam ,
A designating unit for designating a region of the subject's eye to which light is irradiated by the irradiation optical system ,
The control unit is
A setting unit that sets an initial aspect and a final aspect of the fixation light flux based on the region designated by the designation unit;
At least one of the projection position and the shape of the fixation light beam is changed from the initial mode to the final mode.
An ophthalmologic apparatus characterized by the above . The setting unit is configured such that the distance between the fixation light flux in the initial mode and the optical axis of the objective lens is shorter than the distance between the fixation light flux and the optical axis in the final mode. the ophthalmic apparatus according to claim 1, characterized in that to set the initial mode and the final mode. The ophthalmologic apparatus according to claim 2 , wherein the setting unit sets the initial mode so that the fixation light flux in the initial mode is located on the optical axis. The control unit changes at least one of a projection position and a shape of the fixation light flux from the initial mode to the final mode in accordance with the reduction in the distance between the objective lens and the eye to be inspected by the moving mechanism. The ophthalmologic apparatus according to claim 1 , wherein The fixation system includes a light flux output unit that outputs the fixation light flux,
The setting unit sets an initial output position and a final output position of the fixation light flux by the light flux output unit,
The control unit changes the output position of the fixation light flux by the light flux output unit from the initial output position to the final output position in accordance with the reduction in the distance between the objective lens and the eye to be inspected. The ophthalmic device according to claim 4 , characterized in that The fixation system includes a light flux output unit that outputs the fixation light flux,
The setting unit sets an initial output shape and a final output shape of the fixation light flux by the light flux output unit,
The control unit changes the output shape of the fixation light flux by the light flux output unit from the initial output shape to the final output shape in accordance with the shortening of the distance between the objective lens and the eye to be examined. The ophthalmic device according to claim 4 , characterized in that Equipped with an operation part,
The moving mechanism, ophthalmologic apparatus according to any one of claims 1 to 6, characterized in that moving at least a portion of said optical system in response to an operation performed using the operation unit. The moving mechanism includes an actuator controlled by the control unit,
Wherein, ophthalmologic apparatus according to any one of claims 1 to 6, characterized in that cooperating controlling said fixation system and the actuator. A position specifying unit that specifies the position of at least a part of the optical system moved by the moving mechanism;
Wherein, ophthalmologic apparatus according to any one of claims 1 to 8, characterized in that to perform the control of the fixation system on the basis of the position specified by the position specifying unit.