JP7164328B2 - Ophthalmic device and control method for ophthalmic device - Google Patents

Description

The present invention relates to an ophthalmic apparatus and a control method for an ophthalmic apparatus.

2. Description of the Related Art An ophthalmologic apparatus capable of performing multiple examinations and measurements on an eye to be examined is known. There are subjective tests and objective measurements for the tests and measurements on the subject's eye. A subjective test is one in which results are obtained based on responses from the subject. Objective measurement acquires information about the subject's eye using mainly physical techniques without referring to responses from the subject.

For example, Patent Literature 1 discloses an ophthalmologic apparatus capable of subjective examination, refractive power measurement of an eye to be examined, and measurement using optical coherence tomography. In such an ophthalmologic apparatus, focusing control is performed by operating a plurality of focusing lenses provided in each optical system in a coordinated manner, and miniaturization and simplification of control are achieved.

JP 2017-136215 A

In order to further reduce the size and cost of an ophthalmologic apparatus, it is effective to configure the optical system with small and inexpensive optical members. For example, it is conceivable to employ a scanning device such as a MEMS (Micro Electro Mechanical Systems) scanner as the optical scanner.

When a small scanning device is used as an optical scanner, the effective diameter on the deflection surface becomes small. Accordingly, in order to project a light beam on the pupil of the subject's eye with the same diameter as in the conventional case, it is necessary to increase the optical magnification of the optical system from the optical scanner to the pupil.

However, when the optical magnification (β) is increased, the longitudinal magnification increases by the square of the optical magnification (β ² ). Therefore, when focusing on a measurement site such as the fundus of the eye, the amount of movement of the position optically conjugated to the optical scanner is greater than the movement of the focusing lens. As a result, the position of the scan center is shifted from the pupil of the eye to be inspected, and vignetting occurs in the light flux in the eye to be inspected, such as a small pupil.

SUMMARY OF THE INVENTION The present invention has been made in view of such circumstances, and an object thereof is to provide a new technique for realizing miniaturization and cost reduction of an ophthalmologic apparatus without affecting measurement accuracy. It is in.

A first aspect of some embodiments includes an objective lens, an inspection optical system for irradiating an eye to be inspected with light from a light source via the objective lens, and detecting light returned from the eye to be inspected, and the objective lens. and the inspection optical system, and is movable in the optical axis direction of the objective lens; an optical scanner arranged so as to position the plane and movable in the direction of the optical axis; and moving the focusing lens and the optical scanner so as to maintain the positional relationship between the focusing lens and the optical scanner. and a control unit for performing focusing control.

A second aspect of some embodiments is, in the first aspect, arranged between the inspection optical system and the optical scanner, guiding light from the inspection optical system to the optical scanner, and guiding light from the optical scanner. a deflection member that deflects the returned light in the direction of the optical axis and guides it to the inspection optical system; The focus control is performed by moving.

A third aspect of some embodiments is, in the second aspect, a first focusing unit including the focusing lens, the optical scanner, and the deflection member, and the first focusing unit arranged in the optical axis direction. and a first moving mechanism that moves, wherein the control unit controls the first moving mechanism.

In a fourth aspect of some embodiments, in any one of the first to third aspects, the inspection optical system divides light from a light source into reference light and measurement light, and transmits the measurement light to the subject. It includes an interference optical system that projects an eye to be examined and detects interference light between the return light of the measurement light from the eye to be examined and the reference light.

A fifth aspect of some embodiments is, in the first aspect, a light guide member having flexibility, one end of which is optically connected to the inspection optical system, and guides light from the inspection optical system; a collimator lens disposed between the other end of the light guide member and the optical scanner, wherein the controller controls the focusing lens, the light scanner, the other end of the light guide member and the collimator lens; The focusing control is performed by moving the .

A sixth aspect of some embodiments is, in the fifth aspect, a second focusing unit including the focusing lens, the optical scanner, and the collimator lens, and holding the other end of the light guide member; a second moving mechanism for moving a second focusing unit in the optical axis direction, wherein the control section controls the second moving mechanism.

In a seventh aspect of some embodiments, in the fifth aspect or the sixth aspect, the inspection optical system divides light from a light source into reference light and measurement light, and projects the measurement light onto the eye to be inspected. an optical path for changing at least one of the optical path length of the measurement light and the optical path length of the reference light, including an interference optical system for detecting interference light between the return light of the measurement light from the eye to be inspected and the reference light. and a length changing mechanism, wherein the control unit adjusts the optical path length changing mechanism according to the amount of movement of the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens in the optical axis direction. At least one of the optical path length of the measurement light and the optical path length of the reference light is changed by controlling.

In an eighth aspect of some embodiments, in any one of the first to seventh aspects, the optical scanner includes a MEMS (Micro Electro Mechanical Systems) scanner.

A ninth aspect of some embodiments includes an objective lens, an inspection optical system for irradiating an eye to be inspected with light from a light source via the objective lens, and detecting light returned from the eye to be inspected, and the objective lens and the inspection optical system, and is movable in the optical axis direction of the objective lens; and an optical scanner disposed so as to position the plane and movable in the direction of the optical axis. A control method for an ophthalmologic apparatus includes a focusing control step of performing focusing control by moving the focusing lens and the optical scanner such that a positional relationship between the focusing lens and the optical scanner is maintained; and a measuring step of irradiating the eye to be inspected with the light of the inspection optical system deflected by the optical scanner and detecting the returned light after the focus control step.

In a tenth aspect of some embodiments, in the ninth aspect, the ophthalmic device is disposed between the inspection optical system and the optical scanner, directs light from the inspection optical system to the optical scanner, a deflection member that deflects the return light from the optical scanner in the optical axis direction and guides it to the inspection optical system; and in the focus control step, the focusing lens, the optical scanner, and the deflection member are moved. Let

In an eleventh aspect of some embodiments, in the ninth aspect or the tenth aspect, the inspection optical system divides light from a light source into reference light and measurement light, and projects the measurement light onto the eye to be inspected. and an interference optical system for detecting interference light between the return light of the measurement light from the eye to be inspected and the reference light, and in the measuring step, the interference optical system and the optical scanner are controlled to control the optical scanner. The eye to be inspected is irradiated with the measurement light deflected by the , and interference light between the returned light and the reference light is detected.

ADVANTAGE OF THE INVENTION According to this invention, the new technique for implement|achieving size reduction and cost reduction of an ophthalmologic apparatus can be provided, without affecting measurement accuracy.

1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment; FIG. 4 is a schematic diagram showing a flow of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a schematic diagram showing a flow of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a schematic diagram showing a flow of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. 1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 4 is a schematic diagram showing a flow of an operation example of the ophthalmologic apparatus according to the embodiment; FIG.

Embodiments of an ophthalmologic apparatus and an ophthalmologic apparatus control method according to the present invention will be described in detail with reference to the drawings. It should be noted that the descriptions of the documents cited in this specification and any known techniques can be incorporated into the following embodiments.

An ophthalmologic apparatus according to an embodiment includes an inspection optical system, and can inspect (measure) an eye to be inspected by irradiating the eye to be inspected with light and detecting the returned light. In some embodiments, the inspection optical system performs measurement and imaging using Optical Coherence Tomography (OCT).

Hereinafter, in the embodiments, the case where the swept source type OCT method is used in the measurement using OCT will be described in detail. It is also possible to apply the configuration according to the embodiment.

The ophthalmologic apparatus according to some embodiments further includes a subjective test optical system for performing subjective tests and an objective measurement system for performing other objective measurements.

Subjective testing is a measurement technique that uses responses from subjects to obtain information. The subjective examination includes subjective refraction measurement such as distance examination, near examination, contrast examination, glare examination, and visual field examination.

Objective measurement is a measurement technique that obtains information about the subject's eye using mainly physical techniques without referring to responses from the subject. Objective measurement includes measurement for acquiring characteristics of the eye to be inspected and photographing for acquiring an image of the eye to be inspected. Other objective measurements include keratometry, tonometry, fundus photography, and the like.

Hereinafter, the fundus conjugate position is a position that is substantially optically conjugate with the fundus of the subject's eye after alignment is completed, and means a position that is optically conjugate with the fundus of the subject's eye or its vicinity. Similarly, the pupil conjugate position is a position that is approximately optically conjugate with the pupil of the eye to be inspected in a state in which alignment is completed, and means a position that is optically conjugate with the pupil of the eye to be inspected or in the vicinity thereof. .

[First embodiment]
<Configuration of optical system>
1 to 3 show configuration examples of the optical system of the ophthalmologic apparatus according to the first embodiment. FIG. 1 shows a configuration example of the entire optical system of an ophthalmologic apparatus 1000 according to the first embodiment. FIG. 2 shows a configuration example of the optical system of the OCT unit 100 of FIG. FIG. 3 shows an example configuration of the optical system of the focusing unit 80 of FIG. Note that FIG. 3 shows only part of the optical system for convenience of explanation.

The ophthalmologic apparatus 1000 includes an optical system for observing an eye to be examined E, an optical system for examining the eye to be examined E, and a dichroic mirror for wavelength-separating the optical paths of these optical systems. An anterior segment observation system 5 is provided as an optical system for observing the eye E to be examined. An OCT optical system and a reflector measurement optical system (refractive power measurement optical system) are provided as an optical system for examining the eye E to be examined.

The ophthalmologic apparatus 1000 includes a Z alignment system 1, an XY alignment system 2, a keratometric measurement system 3, a fixation projection system 4, an anterior segment observation system 5, a reflector measurement projection system 6, a reflector measurement light receiving system 7, and an OCT optical system 8. including. In the following description, for example, the anterior ocular segment observation system 5 uses light of 940 nm to 1000 nm, the reflector measurement optical system (ref measurement projection system 6, reflector measurement light receiving system 7) uses light of 830 nm to 880 nm, and the fixation projection system 4 uses light of 400 nm to 700 nm, and the OCT optical system 8 uses light of 1000 nm to 1100 nm.

(Anterior segment observation system 5)
The anterior segment observation system 5 captures a moving image of the anterior segment of the eye E to be examined. In the optical system passing through the anterior segment observation system 5, the imaging surface of the imaging element 59 is arranged at the pupil conjugate position. The anterior segment illumination light source 50 irradiates the anterior segment of the eye E to be examined with illumination light (for example, infrared light). The light reflected by the anterior segment of the subject's eye E passes through the objective lens 51, passes through the dichroic mirror 52, passes through a hole formed in the diaphragm (telecentric diaphragm) 53, and passes through the half mirror 23. , the relay lenses 55 and 56 and the dichroic mirror 76 . The dichroic mirror 52 synthesizes (separates) the optical path of the reflex measurement optical system and the optical path of the anterior eye observation system 5 . The dichroic mirror 52 is arranged such that the optical path synthesizing surface for synthesizing these optical paths is inclined with respect to the optical axis of the objective lens 51 . The light transmitted through the dichroic mirror 76 is imaged on the imaging surface of the imaging element 59 (area sensor) by the imaging lens 58 . The imaging element 59 performs imaging and signal output at a predetermined rate. The output (video signal) of the imaging device 59 is input to the processing section 9 which will be described later. The processing unit 9 displays an anterior segment image E' based on this video signal on a display screen 10a of the display unit 10, which will be described later. The anterior segment image E' is, for example, an infrared moving image.

(Z alignment system 1)
The Z alignment system 1 projects light (infrared light) onto the subject's eye E for alignment in the optical axis direction (front-rear direction, Z direction) of the anterior segment observation system 5 . The light output from the Z alignment light source 11 is projected onto the cornea Cr of the eye E to be examined, reflected by the cornea Cr, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12 . When the position of the corneal vertex changes in the optical axis direction of the anterior segment observation system 5, the light projection position on the sensor surface of the line sensor 13 changes. The processing unit 9 obtains the position of the corneal vertex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13, and based on this, controls the mechanism for moving the optical system to perform Z alignment.

(XY alignment system 2)
The XY alignment system 2 applies light (infrared light) to the eye to be examined E for alignment in directions perpendicular to the optical axis of the anterior eye observation system 5 (horizontal direction (X direction) and vertical direction (Y direction)). to irradiate. The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22 provided in an optical path branched from the optical path of the anterior eye observation system 5 by a half mirror 23 . Light output from the XY alignment light source 21 passes through the collimator lens 22 , is reflected by the half mirror 23 , and is projected onto the subject's eye E through the anterior eye observation system 5 . Reflected light from the cornea Cr of the eye E to be inspected is guided to the imaging device 59 through the anterior segment observation system 5 .

The image (bright point image) Br based on this reflected light is included in the anterior segment image E'. The processing unit 9 causes the display screen of the display unit to display the anterior segment image E′ including the bright spot image Br and the alignment mark AL. When manually performing the XY alignment, the user moves the optical system so as to guide the bright spot image Br into the alignment mark AL. When the alignment is performed automatically, the processing unit 9 controls the mechanism for moving the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is cancelled.

(Kerato measurement system 3)
The keratometry system 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea Cr of the eye E to be examined onto the cornea Cr. The keratoplate 31 is arranged between the objective lens 51 and the eye E to be examined. A kerato ring light source 32 is provided on the back side of the kerato plate 31 (on the objective lens 51 side). The keratoplate 31 has a keratopattern (transmissive portion) formed along a circumference centered on the optical axis of the objective lens 51 to transmit the light from the keratometry light source 32 . Note that the keratopattern may be formed in an arc shape (part of the circumference) centering on the optical axis of the objective lens 51 . By illuminating the kerat plate 31 with light from the keratizing light source 32, a ring-shaped light flux (arc-shaped or circumferential measurement pattern) is projected onto the cornea Cr of the eye E to be examined. Reflected light (keratling image) from the cornea Cr of the subject's eye E is detected by the imaging element 59 together with the anterior segment image E'. The processing unit 9 calculates corneal shape parameters representing the shape of the cornea Cr by performing known calculations based on this keratling image.

(ref measurement projection system 6, ref measurement light receiving system 7)
The ref measurement optical system includes a ref measurement projection system 6 and a ref measurement light receiving system 7 used for refractive power measurement. The ref measurement projection system 6 projects a refractive power measurement light beam (for example, a ring-shaped light beam) (infrared light) onto the fundus oculi Ef. The ref measurement light-receiving system 7 receives the return light from the subject's eye E of this luminous flux. The reflector measurement projection system 6 is provided on an optical path branched by a perforated prism 65 provided in the optical path of the reflector measurement light receiving system 7 . The aperture formed in the apertured prism 65 is arranged at the pupil conjugate position. In the optical system passing through the ref measurement light-receiving system 7, the imaging surface of the imaging device 59 is arranged at the fundus conjugate position.

In some embodiments, the ref measurement light source 61 is an SLD (Superluminescent Diode) light source, which is a high luminance light source. The ref measurement light source 61 is movable in the optical axis direction. A reflex measurement light source 61 is arranged at a fundus conjugate position. The light output from the ref measurement light source 61 passes through the relay lens 62 and enters the conical surface of the conical prism 63 . Light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63 . Light emitted from the bottom surface of the conical prism 63 passes through a ring-shaped transparent portion of the ring aperture 64 . The light (ring-shaped luminous flux) that has passed through the transparent portion of the ring diaphragm 64 is reflected by the reflecting surface formed around the hole of the apertured prism 65, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. be. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the eye E to be examined. The rotary prism 66 is used for averaging the light quantity distribution of the ring-shaped light flux for blood vessels and diseased areas of the fundus oculi Ef and for reducing speckle noise caused by the light source.

The return light of the ring-shaped luminous flux projected onto the fundus oculi Ef passes through the objective lens 51 and is reflected by the dichroic mirrors 52 and 67 . The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the aperture of the perforated prism 65, passes through the relay lens 71, is reflected by the reflecting mirror 72, and passes through the relay lens 73 and the focusing lens. Pass 74. The focusing lens 74 is movable along the optical axis of the ref measurement light receiving system 7 . The light that has passed through the focusing lens 74 is reflected by the reflecting mirror 75 , reflected by the dichroic mirror 76 , and imaged on the imaging surface of the imaging element 59 by the imaging lens 58 . The processing unit 9 calculates the refractive power value of the subject's eye E by performing a known calculation based on the output from the imaging device 59 . For example, power values include spherical power, cylinder power and cylinder axis angle, or equivalent spherical power.

(Fixation projection system 4)
An OCT optical system 8, which will be described later, is provided in an optical path separated by a dichroic mirror 67 from the optical path of the reflective measurement optical system. A fixation projection system 4 is provided on an optical path branched from the optical path of the OCT optical system 8 by a dichroic mirror 83 .

A fixation projection system 4 presents a fixation target to the eye E to be examined. A fixation unit 40 is arranged in the optical path of the fixation projection system 4 . The fixation unit 40 can move along the optical path of the fixation projection system 4 under the control of the processing section 9 which will be described later. The fixation unit 40 includes a liquid crystal panel 41 . A relay lens 42 is arranged between the dichroic mirror 83 and the fixation unit 40 .

The liquid crystal panel 41 controlled by the processing unit 9 displays a pattern representing the fixation target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the subject's eye E can be changed. The fixation position of the subject's eye E includes a position for acquiring an image centered on the macula of the fundus oculi Ef, a position for acquiring an image centered on the optic papilla, and a position between the macula and the optic papilla. There is a position for acquiring an image centered on the center of the fundus in between. It is possible to arbitrarily change the display position of the pattern representing the fixation target.

Light from the liquid crystal panel 41 passes through the relay lens 42 , dichroic mirror 83 , relay lens 82 , reflection mirror 81 , dichroic mirror 67 , and dichroic mirror 52 . . The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus oculi Ef. In some embodiments, each of the liquid crystal panel 41 and the relay lens 42 is independently movable in the optical axis direction.

(OCT optical system 8)
The OCT optical system 8 is an optical system for performing OCT measurement. The position of the focusing lens 87 is adjusted so that the end surface of the optical fiber f1 is conjugated to the measurement site (fundus oculi Ef or anterior segment) and the optical system based on the results of the reflex measurement performed prior to the OCT measurement. .

The OCT optical system 8 is provided in an optical path separated by a dichroic mirror 67 from the optical path of the ref measurement optical system. The optical path of the fixation projection system 4 is coupled to the optical path of the OCT optical system 8 by a dichroic mirror 83 . Thereby, the respective optical axes of the OCT optical system 8 and the fixation projection system 4 can be coaxially coupled.

OCT optical system 8 includes an OCT unit 100 . As shown in FIG. 2, in the OCT unit 100, the OCT light source 101 is a wavelength-swept (wavelength scanning) light source capable of sweeping (scanning) the wavelength of emitted light, similar to a general swept-source type OCT apparatus. Consists of A swept-wavelength light source includes a laser light source including a resonator. The OCT light source 101 temporally changes the output wavelength in the near-infrared wavelength band invisible to the human eye.

As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing swept-source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing light from a wavelength tunable light source (wavelength swept light source) into measurement light and reference light, return light of the measurement light from the subject's eye E, and reference light passing through the reference light path. and a function of generating interference light and a function of detecting this interference light. A detection result (detection signal) of the interference light obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the processing unit 9 .

The OCT light source 101 includes, for example, a near-infrared tunable laser that changes the wavelength of emitted light (wavelength range of 1000 nm to 1100 nm) at high speed. The light L0 output from the OCT light source 101 is guided to the polarization controller 103 by the optical fiber 102, and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided by the optical fiber 104 to the fiber coupler 105 and split into the measurement light LS and the reference light LR.

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

The reference light LR that has passed through the corner cube 114 passes through the dispersion compensating member 113 and the optical path length correcting member 112 , is converted by the collimator 116 from a parallel beam to a converged beam, 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 amount, and guided to the fiber coupler 122 by the optical fiber 121.

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber f1 and converted by the collimator lens unit 89 into a parallel light beam. The measurement light LS converted into a parallel light flux passes through the focusing unit 80 , the relay lens 85 and the reflection mirror 84 and is reflected by the dichroic mirror 83 .

Focusing unit 80 includes a focusing lens 87 and an optical scanner 88 . A light scanner 88 is arranged between the collimating lens unit 89 and the focusing lens 87 . The focusing lens 87 is movable in the optical axis direction (the optical axis direction of the objective lens 51 and the optical axis direction of the OCT optical system 8). For example, the focusing unit 80 includes a stage movable in the optical axis direction, and a focusing lens 87 and an optical scanner 88 are held on the stage. Thereby, the focusing lens 87 and the optical scanner 88 can be moved in the optical axis direction while maintaining the optical positional relationship. The focusing unit 80 moves in the optical axis direction under the control of the control section 210, which will be described later.

In some embodiments, the focusing lens 87 and the optical scanner 88 are independently moved along the optical axis within the focusing unit 80 unit under control from the controller 210 . In some embodiments, the focusing lens 87 and the optical scanner 88 are independently or integrally moved along the optical axis under the control of the controller 210 .

As shown in FIG. 3 , the pupil of the subject's eye E is arranged at the focal position of the objective lens 51 , and the deflection surface of the optical scanner 88 is arranged at the focal position of the focusing lens 87 . That is, the deflection surface of the optical scanner 88 is arranged at the pupil conjugate position. In some embodiments, the focal length F 1 of objective lens 51 is approximately equal to the focal length of focusing lens 87 . The optics between objective lens 51 and focusing lens 87 may be Telecentric optics.

A reflecting mirror 88A as a deflection member is arranged between the optical scanner 88 and the collimator lens unit 89 . The reflecting mirror 88A reflects the measurement light LS (light from the inspection optical system) toward the optical scanner 88, deflects the return light of the measurement light LS guided by the optical scanner 88 in the optical axis direction, and sends it to the OCT unit. lead to 100.

By moving the focusing unit 80, the controller 210 can move the focusing lens 87, the optical scanner 88, and the reflecting mirror 88A in the optical axis direction.

By integrally moving the focusing lens 87 and the optical scanner 88 in this way, the conjugate relationship between the optical scanner 88 and the subject's eye E can be maintained. As a result, even if a scan device with a small effective diameter is used, it is possible to reduce the size and cost of the apparatus without affecting measurement.

Furthermore, by arranging the reflecting mirror 88A between the optical scanner 88 and the collimator lens unit 89, the optical members constituting the OCT optical system 8 do not need to be moved for focus control. can be separated into the optical members. As a result, there is no need to move the collimator lens unit 89 or the like for focus control, and the number of optical members that move together with the focusing lens 87 can be reduced.

The light scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. The optical scanner 88 is a MEMS scanner (MEMS mirror scanner) that two-dimensionally deflects the measurement light LS. The MEMS scanner deflects the measurement light LS so as to scan the imaging region (fundus oculi Ef or anterior segment) in horizontal and vertical directions perpendicular to the optical axis of the OCT optical system 8 . Scanning modes of the measurement light LS by such a MEMS scanner include, for example, horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric scanning, and spiral scanning.

The optical scanner 88 according to some embodiments includes, for example, a first galvanometer mirror and a second galvanometer mirror. The first galvanomirror deflects the measurement light LS so as to scan the imaging region (fundus oculi Ef or anterior segment) in the horizontal direction perpendicular to the optical axis of the OCT optical system 8 . The second galvanomirror deflects the measurement light LS deflected by the first galvanomirror so as to scan the imaging region in the vertical direction perpendicular to the optical axis of the OCT optical system 8 .

In FIG. 1, the measurement light LS reflected by the dichroic mirror 83 passes through the relay lens 82, is reflected by the reflecting mirror 81, passes through the dichroic mirror 67, is reflected by the dichroic mirror 52, and is refracted by the objective lens 51. incident on the eye E to be examined. The measurement light LS is scattered and reflected at various depth positions of the eye E to be examined. The return light of the measurement light LS from the subject's eye E travels in the opposite direction along 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 (see FIG. 2).

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

Detector 125 is, for example, a balanced photodiode. A balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between a pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to a DAQ (Data Acquisition System) 130 .

A clock KC is supplied from the OCT light source 101 to the DAQ 130 . The clock KC is generated in the OCT light source 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength tunable light source. The OCT light source 101, for example, optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then outputs the 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 processing section 220 of the processing section 9 . For example, for each series of wavelength scans (for each A line), the arithmetic processing unit 220 forms a reflection intensity profile for each A line by applying Fourier transform or the like to the spectral distribution based on the sampling data. Furthermore, the arithmetic processing unit 220 forms image data by imaging the reflection intensity profile of each A line.

In this example, a corner cube 114 is provided for changing the length of the optical path (reference optical path, reference arm) of the reference light LR. It is also possible to change the difference between

The processing unit 9 calculates a refractive power value from the measurement result obtained using the reflector measurement optical system, and based on the calculated refractive power value, the fundus oculi Ef, the reflector measurement light source 61, and the image sensor 59 are conjugated. The ref measurement light source 61 and the focusing lens 74 are moved in the optical axis direction to the respective positions. In some embodiments, the processing section 9 moves the focusing unit 80 (focusing lens 87 and optical scanner 88) along its optical axis in conjunction with the movement of the focusing lens 74 . In some embodiments, the processing section 9 moves the liquid crystal panel 41 (fixation unit 40) along its optical axis in conjunction with the movement of the ref measurement light source 61 and the focusing lens 74. FIG.

<Configuration of processing system>
The configuration of the processing system of the ophthalmologic apparatus 1000 will be described. An example of the functional configuration of the processing system of the ophthalmologic apparatus 1000 is shown in FIG. FIG. 4 shows an example of a functional block diagram of the processing system of the ophthalmologic apparatus 1000. As shown in FIG.

The processing unit 9 controls each unit of the ophthalmologic apparatus 1000 . In addition, the processing unit 9 can execute various arithmetic processing. The processing unit 9 includes a processor.プロセッサの機能は、例えば、ＣＰＵ（Ｃｅｎｔｒａｌ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＧＰＵ（Ｇｒａｐｈｉｃｓ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＡＳＩＣ（Ａｐｐｌｉｃａｔｉｏｎ Ｓｐｅｃｉｆｉｃ Ｉｎｔｅｇｒａｔｅｄ Ｃｉｒｃｕｉｔ）、プログラマブル論理デバイス（例えば、ＳＰＬＤ（Ｓｉｍｐｌｅ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ）、ＣＰＬＤ（Ｃｏｍｐｌｅｘ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ） , FPGA (Field Programmable Gate Array)). The processing unit 9 implements the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or storage device.

Processing unit 9 includes control unit 210 and arithmetic processing unit 220 . Further, the ophthalmologic apparatus 1000 includes moving mechanisms 40D, 80D, 200, a display section 270, an operation section 280, and a communication section 290.

The moving mechanism 200 includes a Z alignment system 1, an XY alignment system 2, a keratometric measurement system 3, a fixation projection system 4, an anterior segment observation system 5, a reflector measurement projection system 6, a reflector measurement light receiving system 7, an OCT optical system 8, and the like. This is a mechanism for moving the head section in which the optical system is housed in the front, rear, left, and right directions. For example, the moving mechanism 200 is provided with an actuator that generates driving force for moving the head section and a transmission mechanism that transmits this driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is configured by, for example, a combination of gears, a rack and pinion, or the like. The control unit 210 (main control unit 211) controls the movement mechanism 200 by sending control signals to the actuators.

The moving mechanism 40D is a mechanism for moving the fixation unit 40 in the optical axis direction of the fixation projection system 4 (the optical axis direction of the objective lens 51). For example, similar to the movement mechanism 200, the movement mechanism 40D is provided with an actuator that generates driving force for moving the fixation unit 40 and a transmission mechanism that transmits this driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is configured by, for example, a combination of gears, a rack and pinion, or the like. The control unit 210 (main control unit 211) controls the moving mechanism 40D by sending a control signal to the actuator.

The moving mechanism 80D is a mechanism for moving the focusing unit 80 in the optical axis direction of the OCT optical system 8 (the optical axis direction of the objective lens 51). For example, similar to the moving mechanism 200, the moving mechanism 80D is provided with an actuator that generates driving force for moving the focusing unit 80 and a transmission mechanism that transmits this driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is configured by, for example, a combination of gears, a rack and pinion, or the like. The controller 210 (main controller 211) controls the moving mechanism 80D by sending a control signal to the actuator.

(control unit 210)
The control unit 210 includes a processor and controls each unit of the ophthalmologic apparatus. Control unit 210 includes a main control unit 211 and a storage unit 212 . A computer program for controlling the ophthalmologic apparatus is stored in advance in the storage unit 212 . The computer programs include a light source control program, a detector control program, an optical scanner control program, an optical system control program, an arithmetic processing program, a user interface program, and the like. The main control unit 211 operates according to such a computer program, so that the control unit 210 executes control processing.

A main control unit 211 performs various controls of the ophthalmologic apparatus as a measurement control unit. Control of the Z alignment system 1 includes control of the Z alignment light source 11, control of the line sensor 13, and the like.

The control of the Z alignment light source 11 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Control of the line sensor 13 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. As a result, the Z alignment light source 11 is switched between lighting and non-lighting, or the amount of light is changed. The main control unit 211 captures the signal detected by the line sensor 13 and identifies the projection position of the light on the line sensor 13 based on the captured signal. The main control unit 211 obtains the position of the corneal vertex of the subject's eye E based on the specified projection position, and based on this, controls the movement mechanism 200 to move the head unit in the front-rear direction (Z alignment).

Control of the XY alignment system 2 includes control of the XY alignment light source 21 and the like.

The control of the XY alignment light source 21 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the XY alignment light source 21 are switched, or the amount of light is changed. The main control unit 211 captures the signal detected by the imaging element 59 and identifies the position of the bright spot image based on the return light from the XY alignment light source 21 based on the captured signal. The main control unit 211 controls the moving mechanism 200 so as to cancel the displacement of the position of the bright point image Br with respect to a predetermined target position (for example, the center position of the alignment mark AL), and moves the head unit in left, right, up and down directions. Move (XY alignment).

Control of the keratometry system 3 includes control of the keratometry light source 32 and the like.

The control of the keratling light source 32 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the keratling light source 32 are switched, or the amount of light is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform a known arithmetic operation on the keratling image detected by the imaging device 59 . Thereby, the corneal shape parameter of the eye E to be examined is obtained.

The control of the fixation projection system 4 includes control of the liquid crystal panel 41, movement control of the fixation unit 40, and the like.

The control of the liquid crystal panel 41 includes turning on/off the display of the fixation target, switching the fixation target according to the type of examination or measurement, and switching the display position of the fixation target. The main controller 211 controls the moving mechanism 40D by sending a control signal to the actuator, and moves at least the liquid crystal panel 41 in the optical axis direction. Thereby, the position of the liquid crystal panel 41 is adjusted so that the liquid crystal panel 41 and the fundus oculi Ef are optically conjugated.

The control of the anterior segment observation system 5 includes control of the anterior segment illumination light source 50, control of the imaging element 59, and the like.

The control of the anterior ocular segment illumination light source 50 includes turning on/off the light source, light amount adjustment, aperture adjustment, and the like. As a result, the lighting and non-lighting of the anterior segment illumination light source 50 is switched, or the amount of light is changed. Control of the imaging element 59 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the imaging element 59 . The main control unit 211 captures the signals detected by the imaging device 59 and causes the arithmetic processing unit 220 to execute processing such as formation of an image based on the captured signals.

The control of the ref measurement projection system 6 includes control of the ref measurement light source 61, control of the rotary prism 66, and the like.

The control of the ref measurement light source 61 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, lighting and non-lighting of the ref measurement light source 61 are switched, or the amount of light is changed. For example, the reflector measurement projection system 6 includes a moving mechanism that moves the reflector measurement light source 61 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the movement mechanism by sending a control signal to the actuator to move the ref measurement light source 61 in the optical axis direction. The control of the rotary prism 66 includes rotation control of the rotary prism 66 and the like. For example, a rotating mechanism for rotating the rotary prism 66 is provided, and the main controller 211 rotates the rotary prism 66 by controlling this rotating mechanism.

Control of the ref measurement light-receiving system 7 includes control of the focusing lens 74 and the like.

Control of the focusing lens 74 includes movement control of the focusing lens 74 in the optical axis direction. For example, the ref measurement light-receiving system 7 includes a moving mechanism that moves the focusing lens 74 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator to move the focusing lens 74 in the optical axis direction. The main control unit 211 controls the refractometer measurement light source 61 and the focusing lens 74 according to the refractive power of the subject's eye E, for example, so that the refractometer light source 61, the fundus oculi Ef, and the imaging device 59 are optically conjugate. Axial movement is possible.

Control of the OCT optical system 8 includes control of the OCT light source 101, movement control of the focusing unit 80, control of the optical scanner 88, control of the focusing lens 87, control of the corner cube 114, control of the detector 125, and control of the DAQ 130. control, etc.

The control of the OCT light source 101 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. Control of the focusing unit 80 includes movement control of the focusing unit 80 in the optical axis direction. The main control section 211 controls the moving mechanism 80D by sending a control signal to the actuator to move the focusing unit 80 in the optical axis direction. Control of the optical scanner 88 includes control of the scanning position, scanning range, and scanning speed by the MEMS scanner.

In some embodiments, the control of the focusing lens 87 includes movement control of the focusing lens 87 in the optical axis direction, movement control of the focusing lens 87 to the focus reference position corresponding to the imaging region, There is movement control within a movement range (focusing range) corresponding to . For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 87 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator to move the focusing lens 87 in the optical axis direction.

In some embodiments, the ophthalmic device is provided with a holding member that holds the focusing lens 74 and the focusing unit 80, and a drive that drives the holding member. The main control section 211 performs movement control of the focusing lens 74 and the focusing unit 80 by controlling the driving section. For example, the main control section 211 may move only the focusing lens 87 based on the intensity of the interference signal after moving the focusing unit 80 in conjunction with the movement of the focusing lens 74 .

The control of the corner cube 114 includes movement control of the corner cube 114 along the optical path. For example, the OCT optical system 8 includes a moving mechanism that moves the corner cube 114 along the optical path. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending control signals to the actuators to move the corner cube 114 along the optical path. Control of the detector 125 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. The main control unit 211 samples the signal detected by the detector 125 by the DAQ 130, and causes the arithmetic processing unit 220 (image forming unit 222) to perform processing such as formation of an image based on the sampled signal.

The main control unit 211 also performs processing of writing data to the storage unit 212 and processing of reading data from the storage unit 212 .

(storage unit 212)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, objective measurement results (OCT measurement results), tomographic image data, fundus image data, results of subjective examinations, information on the eye to be examined, and the like. The eye information to be examined includes information about the subject such as patient ID and name, and information about the eye to be examined such as left/right eye identification information. The storage unit 212 also stores various programs and data for operating the ophthalmologic apparatus.

(Arithmetic processing unit 220)
The arithmetic processing unit 220 includes an eye refractive power calculation unit 221 , an image forming unit 222 and a data processing unit 223 .

The eye refractive power calculation unit 221 calculates a ring image (pattern image ). For example, the eye refractive power calculator 221 obtains the barycentric position of the ring image from the luminance distribution in the obtained image in which the ring image is rendered, and obtains the luminance distribution along a plurality of scanning directions radially extending from this barycentric position. , the ring image is specified from this luminance distribution. Subsequently, the eye refractive power calculation unit 221 obtains an approximated ellipse of the specified ring image, and obtains the spherical power, the cylindrical power, and the cylindrical axis angle by substituting the major axis and minor axis of the approximated ellipse into a known formula. . Alternatively, the eye refractive power calculator 221 can obtain parameters of the eye refractive power based on deformation and displacement of the ring image with respect to the reference pattern.

The eye refractive power calculator 221 also calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism axis angle based on the keratling image acquired by the anterior eye observation system 5 . For example, the eye refractive power calculator 221 calculates the corneal curvature radii of the strong and weak principal meridians of the corneal front surface by analyzing the keratling image, and calculates the above parameters based on the corneal curvature radii.

The image forming unit 222 forms image data of a tomographic image of the fundus oculi Ef based on the signal detected by the detector 115 . That is, the image forming unit 222 forms image data of the subject's eye E based on the detection result of the interference light LC by the interference optical system. This processing includes processing such as filter processing and FFT (Fast Fourier Transform), as in conventional spectral domain type OCT. The image data acquired in this manner is a data set containing a group of image data formed by imaging reflection intensity profiles in a plurality of A-lines (paths of each measuring light LS in the eye E to be examined). be.

To improve image quality, multiple data sets collected by scanning the same pattern multiple times can be superimposed (averaged).

The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomogram formed by the image forming unit 222 . For example, the data processing unit 223 executes correction processing such as image luminance correction and dispersion correction. In addition, the data processing unit 223 performs various image processing and analysis processing on the image (anterior segment image, etc.) obtained using the anterior segment observation system 5 .

The data processing unit 223 can form volume data (voxel data) of the subject's eye E by executing known image processing such as interpolation processing for interpolating pixels between tomographic images. When displaying an image based on volume data, the data processing unit 223 performs rendering processing on this volume data to form a pseudo-three-dimensional image when viewed from a specific line-of-sight direction.

(Display unit 270, operation unit 280)
Display unit 270 displays information as a user interface unit under the control of control unit 210 . Display unit 270 includes display unit 10 shown in FIG. 1 and the like.

The operation unit 280 is used as a user interface unit to operate the ophthalmologic apparatus. The operation unit 280 includes various hardware keys (joystick, button, switch, etc.) provided in the ophthalmologic apparatus. The operation unit 280 may also include various software keys (buttons, icons, menus, etc.) displayed on the touch panel display screen 10a.

At least part of the display unit 270 and the operation unit 280 may be configured integrally. A typical example is a touch panel display screen 10a.

(Communication unit 290)
The communication unit 290 has a function for communicating with an external device (not shown). The communication unit 290 has a communication interface according to a connection form with an external device. An example of an external device is a spectacle lens measuring device for measuring the optical properties of lenses. The spectacle lens measuring device measures the dioptric power of the spectacle lens worn by the subject, and inputs this measurement data to the ophthalmologic device 1000 . Also, the external device may be any ophthalmologic device, a device (reader) that reads information from a recording medium, or a device (writer) that writes information to a recording medium. Furthermore, the external device may be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, or the like. The communication unit 290 may be provided in the processing unit 9, for example.

<Operation example>
The operation of the ophthalmologic apparatus 1000 according to the first embodiment will be described.

5 to 7 show an example of the operation of the ophthalmologic apparatus 1000. FIG. FIG. 5 depicts a flow diagram of an example operation of the ophthalmic device 1000 . FIG. 6 shows a flow diagram of an operation example of step S3 in FIG. FIG. 7 shows a flow diagram of an operation example of step S4 in FIG. The storage unit 212 stores computer programs for realizing the processes shown in FIGS. The main control unit 211 executes the processes shown in FIGS. 5 to 7 by operating according to this computer program.

(S1: Alignment)
The ophthalmologic apparatus 1000 performs alignment when the examiner performs a predetermined operation on the operation unit 280 while the subject's face is fixed to a face receiving unit (not shown).

Specifically, the main controller 211 turns on the Z alignment light source 11 and the XY alignment light source 21 . Further, the main controller 211 turns on the anterior segment illumination light source 50 . The processing unit 9 acquires the imaging signal of the anterior segment image on the imaging surface of the imaging element 59 and causes the display unit 270 to display the anterior segment image. After that, the optical system shown in FIG. 1 is moved to the examination position of the eye E to be examined. The inspection position is a position at which the eye to be inspected E can be inspected with sufficient accuracy. The subject's eye E is placed at the inspection position through the above-described alignment (alignment by the Z alignment system 1, the XY alignment system 2, and the anterior segment observation system 5). Movement of the optical system is executed by the control unit 210 according to an operation or instruction by the user or an instruction by the control unit 210 . That is, the movement of the optical system to the inspection position of the subject's eye E and the preparation for objective measurement are performed.

The main control unit 211 also moves the ref measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to their origin positions (for example, positions corresponding to 0D (diopter)) along their respective optical axes.

(S2: Kerato analysis)
Next, the main control unit 211 causes the liquid crystal panel 41 to display a pattern indicating a fixation target at a display position corresponding to a desired fixation position. Thereby, the subject's eye E is gazed at the desired fixation position.

After that, the main controller 211 turns on the keratling light source 32 . When light is emitted from the keratizing light source 32, a ring-shaped light beam for corneal shape measurement is projected onto the cornea Cr of the eye E to be examined. The eye refractive power calculator 221 calculates the corneal curvature radius by performing arithmetic processing on the image acquired by the imaging device 59, and calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism from the calculated corneal curvature radius. Calculate the axis angle. In the control unit 210 , the calculated corneal refractive power and the like are stored in the storage unit 212 . In response to an instruction from the main control unit 211 or a user's operation or instruction to the operation unit 280, the operation of the ophthalmologic apparatus 1000 proceeds to step S3. Note that this keratometry may be performed simultaneously or continuously with the main measurement in step S5.

(S3: Temporary measurement)
Next, the main controller 211 controls the liquid crystal panel 41 to project the fixation target onto the subject's eye E, and starts the reflex measurement. In this embodiment, a ref measurement includes a provisional measurement and a main measurement. In the temporary measurement, the focus state of the ref measurement optical system is changed according to the refractive power of the eye E to be examined. In the main measurement, the refractive power of the subject's eye E is acquired while promoting fogging of the subject's eye E based on the in-focus state changed by the temporary measurement.

In step S3, the ref measurement light source 61, the focusing lens 74, and the focusing unit 80 are moved in the optical axis direction and placed at positions corresponding to the refractive power of the eye E to be examined. Details of step S3 will be described later.

(S4: OCT measurement)
Next, in step S3, the main control unit 211 moves the corner cube 114 to correct the optical path length while the focusing unit 80 is moved, so that a desired OCT image of the subject's eye E can be obtained. OCT measurement is performed by controlling the OCT optical system 8 . That is, OCT measurement is performed between ref measurements. As a result, the OCT measurement is performed before the fogging of the subject's eye E is promoted, so that the focusing control for performing the OCT measurement becomes unnecessary, and the measurement time can be shortened. The correction of the optical path length by moving the corner cube 114 may be performed in parallel by automatically adjusting the position of the OCT image in step S3. Details of step S4 will be described later.

In response to an instruction from the main control unit 211 or a user's operation or instruction to the operation unit 280, the operation of the ophthalmologic apparatus 1000 proceeds to step S5.

(S5: main measurement)
In step S5, the main control unit 211 moves the liquid crystal panel 41 from the position obtained in the provisional measurement to the fog position, thereby prompting the subject's eye E to be fogged. After that, the main control unit 211 turns on the ref measurement light source 61 when the ref measurement light source 61 is turned off. Further, the main control unit 211 starts the rotation of the rotary prism 66 when the rotation of the rotary prism 66 is stopped. Subsequently, the main control unit 211 acquires the ring image again by controlling the ref measurement projection system 6 and the ref measurement light receiving system 7 in the same manner as in the provisional measurement. The main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, the cylindrical power, and the cylindrical axis angle from the analysis result of the ring image and the movement amount of the focusing lens 74 . The calculated spherical power, cylinder power, and cylinder axis angle are stored in the storage unit 212 .

(S6: Obtain OCT image?)
Next, the main controller 211 determines whether or not to acquire an OCT image. The main control unit 211 determines whether or not to acquire an OCT image based on an instruction from the main control unit 211 or a user's operation or instruction on the operation unit 280 . For example, when the time required for OCT measurement such as 3D scanning is long, the burden on the subject can be reduced by acquiring the OCT image after step S5.

When it is determined to acquire an OCT image (S6: Y), the operation of the ophthalmologic apparatus 1000 proceeds to step S7. When it is determined not to acquire an OCT image (S6: N), the operation of the ophthalmologic apparatus 1000 ends (END).

(S7: Acquire OCT image)
When it is determined to acquire an OCT image in step S6 (S6: Y), the main control unit 211 moves the liquid crystal panel 41 moved to the fog position in step S5 to the in-focus position obtained by the temporary measurement in step S3. back to Thereafter, the main control unit 211 controls the liquid crystal panel 41 to project the fixation target onto the subject's eye E, thereby executing OCT measurement.

The main controller 211 turns on the OCT light source 101 and controls the optical scanner 88 to scan a predetermined portion of the fundus oculi Ef with the measurement light LS. A detection signal obtained by scanning with the measurement light LS is sent to the image forming section 222 . The image forming unit 222 forms a tomographic image of the fundus oculi Ef from the obtained detection signal. With this, the operation of the ophthalmologic apparatus 1000 ends (end).

The temporary measurement in step S3 is performed as shown in FIG.

(S11: Turn on the ref measurement light source and start rotating the rotary prism)
First, the main controller 211 turns on the ref measurement light source 61 and starts rotating the rotary prism 66 .

(S12: Analyze ring image)
Next, the main controller 211 projects the ring-shaped measurement pattern light beam onto the eye E to be examined. A ring image is formed on the imaging surface of the imaging device 59 based on the return light of the measurement pattern light flux from the eye E to be inspected. The main control unit 211 determines whether or not the ring image based on the return light from the fundus oculi Ef detected by the imaging element 59 has been acquired. For example, the main control unit 211 detects the position (pixel) of the edge of the image based on the return light detected by the imaging device 59, and determines whether the width of the image (difference between the outer diameter and the inner diameter) is equal to or greater than a predetermined value. determine whether or not Alternatively, the main control unit 211 determines whether a ring image can be obtained by determining whether a ring can be formed based on points (images) having a predetermined height (ring diameter) or more. good too.

When it is determined that the ring image has been acquired, the eye refractive power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern light flux projected onto the subject's eye E by a known method, and calculates the temporary spherical power S and A temporary astigmatism power C is obtained.

(S13: Move focus lens)
The main control unit 211 moves the ref measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to the position of the equivalent spherical power (S+C/2) based on the temporary spherical power S and the cylindrical power C obtained in step S12. move. In this embodiment, the focusing unit 80 is moved in conjunction with the focusing lens 74 and the like.

(S14: Analyze ring image)
Again, the main control unit 211 causes the ring-shaped measurement pattern light beam to be projected onto the subject's eye E, as in step S12. A ring image is formed on the imaging surface of the imaging device 59 based on the return light of the measurement pattern light flux from the eye E to be inspected. The main control unit 211 determines whether or not the ring image based on the return light from the fundus oculi Ef detected by the imaging element 59 has been acquired.

When it is determined that the ring image has been acquired, the eye refractive power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern light flux projected onto the subject's eye E by a known method, and calculates the temporary spherical power S and A temporary astigmatism power C is obtained.

(S15: Move focusing lens)
The main control unit 211 moves the ref measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to the position of the equivalent spherical power (S+C/2) based on the temporary spherical power S and the cylindrical power C obtained in step S14. move. The position moved to step S15 is the position corresponding to the temporary far point. In this embodiment, the focusing unit 80 is moved in conjunction with the focusing lens 74 and the like.

(S16: turning off the light source for measurement of the reflector and stopping the rotation of the rotary prism)
Next, the main controller 211 turns off the ref measurement light source 61 and stops the rotation of the rotary prism 66 . Thus, step S3 in FIG. 5 is completed (end).

Step S4 in FIG. 5 is executed as shown in FIG.

(S21: Turn on the OCT light source and start the operation of the optical scanner)
First, the main controller 211 turns on the reflector measurement light source 61 and starts the operation of the optical scanner 88 . Thereby, a predetermined portion (the anterior segment, the fundus, or both) of the subject's eye E is scanned with the measurement light LS. In step S21, alignment may be performed by a known method. Also, tracking may be initiated.

(S22: Form a tomogram)
Next, the main control section 211 sends detection signals obtained by scanning with the measurement light LS to the image forming section 222 . The image forming unit 222 forms a tomographic image of the subject's eye E from the obtained detection signals. If the tomogram is not obtained at an appropriate position, the corner cube 114 may be adjusted to adjust the position of the tomogram.

(S23: Turn off the OCT light source and stop the operation of the optical scanner)
Next, the main controller 211 turns off the OCT light source 101 and stops the operation of the optical scanner 88 . Thus, step S4 in FIG. 5 is completed (end).

Note that the main control unit 211 may cause the data processing unit 223 to calculate the intraocular parameter from the tomographic image obtained in step S22 or the detection signal obtained by scanning, for example. Intraocular parameters include axial length, corneal thickness, anterior chamber depth, lens thickness, radius of curvature of the anterior corneal strong principal meridian, radius of curvature of the anterior corneal weak principal meridian, radius of curvature of the posterior corneal strong principal meridian, and posterior corneal weakness. At least one of a principal meridian radius of curvature, an anterior lens strong principal meridian radius of curvature, an anterior lens weak principal meridian radius of curvature, a posterior lens strong principal meridian radius of curvature, and a posterior lens weak principal meridian radius of curvature.

Note that when it is determined in step S12 or step S14 that the ring image cannot be obtained, the main control unit 211 presets the ref measurement light source 61 and the focusing lens 74 in consideration of the possibility of the eye being a highly ametropic eye. In the steps above, it is moved to the negative power side (eg -10D) and the positive power side (eg +10D). The main control unit 211 controls the ref measurement light-receiving system 7 to detect the ring image at each position. If it is still determined that the ring image cannot be acquired, the main control unit 211 executes predetermined measurement error processing.

In the above embodiments, at least one function of the relay lens 42 and the focusing lenses 74, 87 may be realized by a liquid crystal lens or a liquid lens.

[Second embodiment]
The configuration of the ophthalmologic apparatus according to the embodiment is not limited to the configuration of the ophthalmologic apparatus 1000 according to the first embodiment. The configuration of the ophthalmologic apparatus according to the second embodiment will be described below, focusing on differences from the first embodiment.

8 and 9 show configuration examples of an optical system of an ophthalmologic apparatus according to the second embodiment. FIG. 8 shows a configuration example of the entire optical system of an ophthalmologic apparatus 1000a according to the second embodiment. In FIG. 8, the same parts as in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate. FIG. 9 shows a configuration example of the optical system of the focusing unit 80a of FIG. In FIG. 9, only part of the optical system is illustrated for convenience of explanation.

In the ophthalmologic apparatus 1000a, the focusing lens 87, the optical scanner 88, the collimator lens unit 89, and the fiber end of the flexible optical fiber f1 (the emission end of the measurement light LS) are integrated in the optical axis direction of the objective lens 51. be moved. The main controller 211 (controller 210) performs focusing control by moving the focusing lens 87, the optical scanner 88, the fiber end of the optical fiber f1, and the collimator lens unit 89 integrally in the optical axis direction.

The configuration of the ophthalmologic apparatus 1000a differs from the configuration of the ophthalmologic apparatus 1000 in that a focusing unit 80a is provided instead of the focusing unit 80. FIG. The focusing unit 80a includes a focusing lens 87, an optical scanner 88, and a collimator lens unit 89, and holds the fiber end of the optical fiber f1. The main control unit 211 controls the moving mechanism 80D by sending a control signal to the actuator, and controls the focusing unit 80a (focusing lens 87, optical scanner 88, collimator lens unit 89, and fiber end of optical fiber f1). is moved along the optical axis.

Since the operation of the ophthalmologic apparatus 1000a according to the second embodiment is substantially the same as the operation of the ophthalmologic apparatus 1000 according to the first embodiment, the operation example of the ophthalmologic apparatus 1000a according to the second embodiment is similar to that of the first embodiment. The following description will focus on the points of difference.

The operation of the ophthalmologic apparatus 1000a according to the second embodiment differs from the operation of the ophthalmologic apparatus 1000 according to the first embodiment in that the amount of change in the optical path length of the measurement light LS that accompanies the movement of the focusing unit 80a is canceled. This is the point of correcting the optical path length. Optical path length correction is performed on the optical path length of at least one of the measurement light LS and the reference light LR.

For example, the main control unit 211 moves the corner cube 114 in the incident direction of the reference light LR to change the optical path length of the reference light LR, thereby determining the amount of change in the optical path length corresponding to the amount of movement of the focusing unit 80a. Cancel. In this case, the storage unit 212 stores control information in which movement control information for the corner cube 114 is associated in advance with the movement amount of the focusing unit 80a. The main control unit 211 refers to the control information stored in the storage unit 212, and moves the corner cube 114 based on the movement control information corresponding to the amount of movement of the focusing unit 80a.

In some embodiments, the main controller 211 changes the optical path length of the measurement light LS by a known technique, thereby canceling the amount of change in the optical path length corresponding to the amount of movement of the focusing unit 80a.

The second embodiment is executed as shown in FIGS. In the second embodiment, step S4 in FIG. 5 is executed as shown in FIG.

FIG. 10 shows a flowchart of an operation example of the ophthalmologic apparatus 1000a according to the second embodiment.

(S31: Turn on the OCT light source and start the operation of the optical scanner)
First, the main controller 211 turns on the reflector measurement light source 61 and starts the operation of the optical scanner 88, as in step S21. In addition, in step S31, alignment may be performed by a known method. Also, tracking may be initiated.

(S32: Optical path length correction)
Next, the main controller 211 specifies the amount of movement of the focusing unit 80a moved in step S3 of FIG. 5, and cancels the amount of change in the optical path length of the measurement light LS corresponding to the specified amount of movement. Correct the optical path length as follows. In step S32, as described above, the main control unit 211 moves the corner cube 114 in the incident direction of the reference light LR to change the optical path length of the reference light LR, thereby corresponding to the movement amount of the focusing unit 80a. cancels the amount of change in the optical path length. Thus, the OCT unit 100 detects the interference light LC even if the optical path length of the measurement light LS changes due to the movement of the focusing unit 80a.

(S33: Form a tomogram)
Next, the main control section 211 sends detection signals obtained by scanning with the measurement light LS to the image forming section 222 . The image forming unit 222 forms a tomographic image of the subject's eye E from the obtained detection signals. If the tomogram is not obtained at an appropriate position, the corner cube 114 may be adjusted to adjust the position of the tomogram.

(S34: Turn off the OCT light source and stop the operation of the optical scanner)
Next, the main controller 211 turns off the OCT light source 101 and stops the operation of the optical scanner 88 . Thus, step S4 in FIG. 5 is completed (end).

As in the first embodiment, the main control unit 211 may cause the data processing unit 223 to calculate intraocular parameters from the tomographic image obtained in step S33 or the detection signal obtained by scanning, for example.

The optical system included in the OCT unit 100 is an example of the "inspection optical system" according to the embodiment. Reflecting mirror 88A is an example of a "deflection member" according to the embodiment. The focusing unit 80 is an example of the "first focusing unit" according to the embodiment. The moving mechanism 80D is an example of the "first moving mechanism" according to the embodiment. The optical system (the optical system shown in FIG. 2) included in the OCT unit 100 is an example of the "interference optical system" according to the embodiment. The optical fiber f1 is an example of the "light guide member" according to the embodiment. The emission end of the measurement light LS of the optical fiber f1 (the incident end of the return light of the measurement light LS) is an example of the "other end of the light guide member" according to the embodiment. The collimator lens unit 89 is an example of a "collimator lens" according to the embodiment. The focusing unit 80a is an example of the "second focusing unit" according to the embodiment. A moving mechanism 80D that moves the focusing unit 80a is an example of a "second moving mechanism" according to the embodiment. The collimator 111, the corner cube 114, and the collimator 116 are examples of the "optical path length changing mechanism" according to the embodiment.

[Action/effect]
The actions and effects of the ophthalmologic apparatus and the control method for the ophthalmic apparatus according to the embodiment will be described.

An ophthalmic device (1000, 1000a) according to some embodiments includes an objective lens (51), an examination optical system (optical system included in the OCT unit 100), a focusing lens (87), an optical scanner (88 ) and a control unit (210, main control unit 211). The inspection optical system irradiates an eye (E) to be inspected with light from a light source via an objective lens, and detects light returned from the eye to be inspected. The focusing lens is arranged between the objective lens and the inspection optical system and is movable along the optical axis of the objective lens. The optical scanner is arranged between the focusing lens and the inspection optical system so that the deflection surface is positioned at the focal position of the focusing lens, and is movable in the optical axis direction. The control unit performs focusing control by moving the focusing lens and the optical scanner so that the positional relationship between the focusing lens and the optical scanner is maintained.

With such a configuration, focus control can be performed so as to maintain the positional relationship between the focusing lens and the optical scanner, so the conjugate relationship between the optical scanner and the subject's eye can be maintained. As a result, even when a scanning device with a small effective diameter is used as an optical scanner, there is no vignetting in the light flux in the eye to be examined, such as a small pupil, and the ophthalmologic apparatus can be made smaller and lower without affecting the measurement accuracy. Cost can be reduced.

An ophthalmologic apparatus according to some embodiments is arranged between an inspection optical system and an optical scanner, guides light from the inspection optical system to the optical scanner, and directs return light guided by the optical scanner in the optical axis direction. It includes a deflecting member (reflecting mirror 88A) that deflects and guides the light to the inspection optical system, and the control unit performs focusing control by moving the focusing lens, the optical scanner, and the deflecting member in the optical axis direction.

According to such a configuration, since the deflection member is arranged between the inspection optical system and the optical scanner to separate the optical member group to be moved, other optical members can be used for focus control. Since there is no need to move the optical member, the number of parts of the optical member to be moved can be reduced. As a result, it becomes possible to further reduce the size and cost of the ophthalmic apparatus.

An ophthalmic apparatus according to some embodiments includes a first focusing unit (focusing unit 80) that includes a focusing lens, an optical scanner, and a deflection member; and a moving mechanism (moving mechanism 80D), and the control unit controls the first moving mechanism.

According to such a configuration, since the first focusing unit including the focusing lens, the optical scanner, and the deflection member is provided, and the first focusing unit is moved by the first moving mechanism, the moving mechanism can be minimized. Focusing control can be performed so as to maintain the positional relationship between the focusing lens and the optical scanner, while limiting the distance.

In the ophthalmologic apparatus according to some embodiments, the inspection optical system divides light (L0) from the light source (OCT light source 101) into reference light (LR) and measurement light (LS), and directs the measurement light to the eye to be inspected. and detects interference light (LC) between the return light of the measurement light from the eye to be inspected and the reference light.

According to such a configuration, even when a scan device with a small effective diameter is used as an optical scanner, it is possible to reduce the size and cost of the ophthalmologic apparatus without affecting the OCT measurement accuracy.

An ophthalmologic apparatus according to some embodiments includes a flexible light guide member (optical fiber f1) having one end optically connected to an inspection optical system and guiding light from the inspection optical system; and a collimator lens (collimator lens unit 89) arranged between the other end and the optical scanner, and the controller moves the focusing lens, the optical scanner, the other end of the light guide member and the collimator lens. Focus control is performed by

With such a configuration, focus control can be performed so as to maintain the positional relationship between the focusing lens and the optical scanner, so the conjugate relationship between the optical scanner and the subject's eye can be maintained. As a result, even when a scanning device with a small effective diameter is used as an optical scanner, there is no vignetting in the light flux in the eye to be examined, such as a small pupil, and the ophthalmologic apparatus can be made smaller and lower without affecting the measurement accuracy. Cost can be reduced.

The ophthalmic apparatus according to some embodiments includes a focusing lens, an optical scanner, and a collimating lens, and includes a second focusing unit (focusing unit 80a) holding the other end of the light guide member, and a second focusing unit 80a. and a second moving mechanism (moving mechanism 80D) that moves the unit in the optical axis direction, and the control section controls the second moving mechanism.

According to such a configuration, the second focusing unit including the focusing lens, the optical scanner, and the collimator lens is provided and holds the other end of the light guide member, and the second moving mechanism moves the second focusing unit. This makes it possible to perform focusing control so as to maintain the positional relationship between the focusing lens and the optical scanner while minimizing the movement mechanism.

In the ophthalmologic apparatus according to some embodiments, the inspection optical system divides light (L0) from the light source (OCT light source 101) into reference light (LR) and measurement light (LS), and directs the measurement light to the eye to be inspected. and detects interference light (LC) between the return light of the measurement light from the eye to be inspected and the reference light, and the ophthalmologic apparatus includes at least one of the optical path length of the measurement light and the optical path length of the reference light The control unit controls the amount of movement of the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens in the optical axis direction. At least one of the optical path length of the measurement light and the optical path length of the reference light is changed by controlling the optical path length changing mechanism accordingly.

According to such a configuration, even when a scan device with a small effective diameter is used as an optical scanner, it is possible to reduce the size and cost of the ophthalmologic apparatus without affecting the OCT measurement accuracy.

In some embodiments of the ophthalmic device, the optical scanner comprises a Micro Electro Mechanical Systems (MEMS) scanner.

According to such a configuration, by using an inexpensive and small MEMS scanner as the optical scanner, it is possible to reduce the size and cost of the ophthalmologic apparatus.

A method of controlling an ophthalmic device (1000, 1000a) according to some embodiments comprises an objective lens (51), an examination optical system (optical system included in the OCT unit 100), a focusing lens (87), an optical A control method for an ophthalmologic apparatus including a scanner (88) and a controller (210, main controller 211). The inspection optical system irradiates an eye (E) to be inspected with light from a light source via an objective lens, and detects light returned from the eye to be inspected. The focusing lens is arranged between the objective lens and the inspection optical system and is movable along the optical axis of the objective lens. The optical scanner is arranged between the focusing lens and the inspection optical system so that the deflection surface is positioned at the focal position of the focusing lens, and is movable in the optical axis direction. A control method for an ophthalmologic apparatus includes a focus control step and a measurement step. The focus control step performs focus control by moving the focus lens and the optical scanner so that the positional relationship between the focus lens and the optical scanner is maintained. In the measurement step, after the focus control step, the eye to be inspected is irradiated with the light of the inspection optical system deflected by the optical scanner, and the returned light is detected.

According to such control, focusing control can be performed so as to maintain the positional relationship between the focusing lens and the optical scanner, so that the conjugate relationship between the optical scanner and the subject's eye can be maintained. As a result, even when a scan device with a small effective diameter is used as an optical scanner, it is possible to suppress deterioration in measurement accuracy.

In the method of controlling an ophthalmic device according to some embodiments, the ophthalmic device is arranged between an inspection optical system and an optical scanner, guides light from the inspection optical system to the optical scanner, and directs return light from the optical scanner. It includes a deflection member (reflecting mirror 88A) that deflects in the optical axis direction and guides it to the inspection optical system.

Such control eliminates the need to move other optical members for focus control in an ophthalmologic apparatus in which a deflection member is arranged between the inspection optical system and the optical scanner.

In the method of controlling an ophthalmologic apparatus according to some embodiments, the inspection optical system divides light (L0) from the light source (OCT light source 101) into reference light (LR) and measurement light (LS), and divides the measurement light into is projected onto the eye to be examined, and an interference optical system for detecting interference light (LC) between the return light of the measurement light from the eye to be examined and the reference light. The eye to be inspected is irradiated with measurement light deflected by the scanner, and interference light between the return light and the reference light is detected.

According to such a configuration, even when a scanning device with a small effective diameter is used as an optical scanner, it is possible to obtain OCT measurement results without causing deterioration in measurement accuracy.

<Others>
The embodiment shown above is merely an example for carrying out the present invention. A person who intends to implement this invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of this invention.

In the above embodiment, the optical scanner 88 can be a galvanomirror, a polygon mirror, a rotating mirror, a dowel prism, a double dowel prism, a rotation prism, or the like.

1 Z alignment system 2 XY alignment system 3 Kerato measurement system 4 Fixation projection system 5 Anterior eye observation system 6 Reflex measurement projection system 7 Reflex measurement light receiving system 8 OCT optical system 9 Processing unit 51 Objective lenses 80 and 80a Focusing unit 80D Moving mechanism 87 Focusing lens 88 Optical scanner 88A Reflecting mirror 89 Collimator lens units 111 and 116 Collimator 114 Corner cube 210 Control unit 211 Main control unit 1000 Ophthalmic apparatus

Claims (9)

an objective lens;
an inspection optical system that irradiates an eye to be inspected with light from a light source via the objective lens and detects light returned from the eye to be inspected;
a focusing lens disposed between the objective lens and the inspection optical system and movable in an optical axis direction of the objective lens;
an optical scanner disposed between the focusing lens and the inspection optical system such that a deflection surface is positioned at a focal position of the focusing lens and movable in the optical axis direction;
arranged between the inspection optical system and the optical scanner, guides light from the inspection optical system to the optical scanner, deflects the return light guided by the optical scanner in the optical axis direction, and deflects the a deflection member leading to the inspection optical system;
a control unit that performs focusing control by moving the focusing lens and the optical scanner so that the positional relationship between the focusing lens and the optical scanner is maintained;
including
The ophthalmologic apparatus, wherein the control unit performs the focusing control by moving the focusing lens, the optical scanner, and the deflecting member in the optical axis direction . a first focusing unit including the focusing lens, the optical scanner, and the deflection member;
a first moving mechanism that moves the first focusing unit in the optical axis direction;
including
The ophthalmologic apparatus according to claim 1 , wherein the control unit controls the first moving mechanism. The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light onto the eye to be inspected, and causes interference between return light of the measurement light from the eye to be inspected and the reference light. 3. The ophthalmic apparatus according to claim 1, further comprising an interferometric optical system for detecting light. an objective lens;
an inspection optical system that irradiates an eye to be inspected with light from a light source via the objective lens and detects light returned from the eye to be inspected;
a focusing lens disposed between the objective lens and the inspection optical system and movable in an optical axis direction of the objective lens;
an optical scanner disposed between the focusing lens and the inspection optical system such that a deflection surface is positioned at a focal position of the focusing lens and movable in the optical axis direction;
a control unit that performs focusing control by moving the focusing lens and the optical scanner so that the positional relationship between the focusing lens and the optical scanner is maintained;
a light guide member having flexibility, one end of which is optically connected to the inspection optical system, and guides light from the inspection optical system;
a collimator lens arranged between the other end of the light guide member and the light scanner;
including
The control unit performs the focusing control by moving the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens. a second focusing unit including the focusing lens, the optical scanner, and the collimator lens and holding the other end of the light guide member;
a second moving mechanism that moves the second focusing unit in the optical axis direction;
including
The ophthalmologic apparatus according to claim 4 , wherein the control unit controls the second moving mechanism. The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light onto the eye to be inspected, and causes interference between return light of the measurement light from the eye to be inspected and the reference light. including an interferometric optical system that detects light;
an optical path length changing mechanism that changes at least one of the optical path length of the measurement light and the optical path length of the reference light;
including
The control unit controls the optical path length changing mechanism according to the amount of movement of the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens in the optical axis direction, thereby controlling the measurement light. 6. The ophthalmologic apparatus according to claim 4 , wherein at least one of an optical path length and an optical path length of the reference light is changed. The ophthalmic apparatus according to any one of claims 1 to 6 , wherein the optical scanner includes a MEMS (Micro Electro Mechanical Systems) scanner. an objective lens;
an inspection optical system that irradiates an eye to be inspected with light from a light source via the objective lens and detects light returned from the eye to be inspected;
a focusing lens disposed between the objective lens and the inspection optical system and movable in an optical axis direction of the objective lens;
an optical scanner disposed between the focusing lens and the inspection optical system such that a deflection surface is positioned at a focal position of the focusing lens and movable in the optical axis direction;
is disposed between the inspection optical system and the optical scanner, guides light from the inspection optical system to the optical scanner, deflects the return light from the optical scanner in the optical axis direction, and deflects the inspection optical system a deflection member leading to
A control method for an ophthalmic device comprising:
a focusing control step of performing focusing control by moving the focusing lens and the optical scanner such that the positional relationship between the focusing lens and the optical scanner is maintained;
a measurement step of irradiating the eye to be inspected with the light of the inspection optical system deflected by the optical scanner after the focus control step and detecting the returned light;
including
The method of controlling an ophthalmologic apparatus, wherein the focusing control step moves the focusing lens, the optical scanner, and the deflection member . The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light onto the eye to be inspected, and causes interference between return light of the measurement light from the eye to be inspected and the reference light. including an interferometric optical system that detects light;
In the measuring step, the interference optical system and the optical scanner are controlled to irradiate the subject's eye with the measurement light deflected by the optical scanner, and the interference light between the returned light and the reference light is detected. The method for controlling an ophthalmologic apparatus according to claim 8 , characterized by:

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