JP7281877B2 - ophthalmic equipment - Google Patents

Description

The present invention relates to an ophthalmic device .

2. Description of the Related Art An ophthalmologic apparatus capable of performing multiple examinations (including measurements) on an eye to be examined is known. A subjective test and an objective measurement are available as the test for 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 and objective measurement. This ophthalmologic apparatus can perform photographing and measurement using refractive power measurement, keratometry, and optical coherence tomography of the subject's eye as objective measurements.

A plurality of examinations using such an ophthalmologic apparatus have different optimum working distances. Therefore, setting the working distance for one inspection narrows the inspection range for another inspection, or lowers the inspection accuracy. For example, when the working distance of the ophthalmic apparatus is set so as to be optimal for refractive power measurement, the scan range in optical coherence tomography (OCT) measurement becomes narrow. For example, if the working distance of the ophthalmologic apparatus is set so as to be optimal for OCT measurement, it is susceptible to instrumental myopia. Therefore, it is necessary to increase the diameter of the objective lens. However, if the diameter of the objective lens is increased, it becomes difficult to project the measurement pattern used for keratometry, and the corneal shape cannot be measured with high accuracy.

2. Description of the Related Art An ophthalmologic apparatus capable of changing the working distance of the ophthalmologic apparatus according to the type of examination has been proposed. For example, Patent Literature 2 and Patent Literature 3 disclose an ophthalmologic apparatus including a measurement unit in which a refractive power/corneal shape measuring section and an intraocular pressure measuring section are vertically stacked. In this ophthalmologic apparatus, by moving the measurement unit in the vertical direction and moving the intraocular pressure measurement unit in the working distance direction with respect to the refractive power/corneal shape measurement unit, each of the refractive power/corneal shape measurement and the intraocular pressure measurement is performed. The optimum working distance can be set for For example, Patent Literature 4 discloses an ophthalmologic apparatus in which an optometric unit including a refractive power measuring section and an intraocular pressure measuring section is provided rotatably around a rotation axis with respect to a base. In this ophthalmologic apparatus, by rotating the optometric unit, measurement can be performed at the optimum working distance for each of refractive power measurement and intraocular pressure measurement.

JP 2017-136215 A Patent No. 4349934 specification Patent No. 4879632 specification Patent No. 6016445

However, the conventional ophthalmologic apparatus requires a plurality of measurement units to be stacked and requires a rotation mechanism for the optometric unit, resulting in an increase in the size of the apparatus.

SUMMARY OF THE INVENTION The present invention has been made in view of such circumstances, and an object of the present invention is to provide an ophthalmologic apparatus that has a simple configuration and is capable of performing a plurality of examinations at optimum working distances.

A first aspect of some embodiments includes an objective lens, a first inspection optical system for performing a first inspection on an eye to be inspected via the objective lens, and an eye to be inspected via the objective lens. a second inspection optical system for performing a second inspection different from the first inspection; , and a detection element, and deflects the alignment light according to the type of operation mode including a first mode for performing the first inspection and a second mode for performing the second inspection, thereby deflecting the optical axis of the objective lens. The eye to be inspected is irradiated at the first arrangement position or the second arrangement position above, and the light reflected from the eye to be inspected or the light obtained by deflecting the reflected light is detected by the detection element according to the type of the operation mode. a moving mechanism for moving the objective lens, the first inspection optical system, and the second inspection optical system in the optical axis direction of the objective lens; and the reflected light obtained by the alignment optical system controlling the moving mechanism so that the working distance with respect to the eye to be examined is the first working distance in the first mode and the working distance is the second working distance in the second mode, based on the detection result of and a controller for performing ophthalmologic apparatus.

In a second aspect of some embodiments, in the first aspect, the second inspection optical system has an optical scanner, deflects light from a light source by the optical scanner, and converts the light deflected by the optical scanner is projected onto the subject's eye via the objective lens, and light based on the return light from the subject's eye is detected.

In a third aspect of some embodiments, in the first aspect or the second aspect, the first inspection optical system projects light onto the subject's eye via the objective lens, and receives light returned from the subject's eye. Includes detecting refractive power measuring optics.

In a fourth aspect of some embodiments, in any one of the first to third aspects, the alignment optical system includes an alignment light source that outputs the alignment light, and a first deflection member that deflects the alignment light. , a detection element that detects the reflected light, and a second deflection member that deflects the reflected light from the eye to be inspected, irradiating the eye to be inspected with the alignment light deflected by the first deflection member, The detection element detects the reflected light deflected by the second deflection member.

In a fifth aspect of some embodiments, in the fourth aspect, the alignment optical system includes a third deflection member that deflects the alignment light deflected by the first deflection member toward the eye to be inspected; a fourth deflecting member that deflects the reflected light from the subject's eye toward the second deflecting member.

In a sixth aspect of some embodiments, in the fourth aspect or the fifth aspect, the first deflecting member is insertable/removable with respect to the optical path of the alignment light, and the second deflecting member is the reflecting beam. It can be inserted into and removed from the optical path of light.

A seventh aspect of some embodiments is, in any one of the first to sixth aspects, a relay lens that relays light from the anterior segment of the subject's eye, and receives light that has passed through the relay lens. an anterior eye observation system including an image sensor, wherein the controller moves the relay lens to a first lens position on the optical axis of the anterior eye observation system in the first mode; In the mode, the relay lens is moved to the second lens position on the optical axis of the anterior segment observation system.

An eighth aspect of some embodiments is any one of the first to seventh aspects, including a fixation projection system that projects a fixation target onto the eye to be inspected, wherein the controller controls the When the first fixation target is projected onto the eye to be examined, and in the second mode, the fixation projection system projects a second fixation target having a narrower visual angle than the first fixation target onto the eye to be examined. Control.

A ninth aspect of some embodiments includes an objective lens, a first inspection optical system for performing a first inspection on an eye to be inspected via the objective lens, and an eye to be inspected via the objective lens. a second inspection optical system for performing a second inspection different from the first inspection; , and a detection element, and deflects the alignment light according to the type of operation mode including a first mode for performing the first inspection and a second mode for performing the second inspection, thereby deflecting the optical axis of the objective lens. The eye to be inspected is irradiated at the first arrangement position or the second arrangement position above, and the light reflected from the eye to be inspected or the light obtained by deflecting the reflected light is detected by the detection element according to the type of the operation mode. an alignment optical system, a moving mechanism for moving the objective lens, the first inspection optical system, and the second inspection optical system in the optical axis direction of the objective lens, and a control unit for controlling the moving mechanism. In the first mode for performing the first examination, the method of controlling an ophthalmologic apparatus comprising: a first alignment light detection step of detecting reflected light obtained by deflecting light reflected by an eye examination; In the first control step of controlling the moving mechanism so that the distance becomes the first working distance, and in the second mode of performing the second examination, the eye to be examined is irradiated with the alignment light and the reflected light is emitted. a second alignment light detection step of detecting the reflected light by deflection; and a working distance to the eye to be examined based on the detection result of the reflected light in the second alignment light detection step so that the working distance becomes the second working distance. and a second control step of controlling the moving mechanism.

A tenth aspect of some embodiments is, in the ninth aspect, in the first control step, inserting and removing a first deflection member with respect to the optical path of the alignment light, and adjusting the second deflection member with respect to the optical path of the reflected light. Detach the deflecting member.

An eleventh aspect of some embodiments includes an objective lens, a first inspection optical system for performing a first inspection on an eye to be inspected via the objective lens, and an eye to be inspected via the objective lens. a second inspection optical system for performing a second inspection different from the first inspection; , and a detection element, and deflects the alignment light according to the type of operation mode including a first mode for performing the first inspection and a second mode for performing the second inspection, thereby deflecting the optical axis of the objective lens. The eye to be inspected is irradiated at the first arrangement position or the second arrangement position above, and the light reflected from the eye to be inspected or the light obtained by deflecting the reflected light is detected by the detection element according to the type of the operation mode. an alignment optical system, a moving mechanism for moving the objective lens, the first inspection optical system, and the second inspection optical system in the optical axis direction of the objective lens, and a control unit for controlling the moving mechanism. In the first mode of performing the first examination, the eye to be examined is irradiated with the alignment light and the reflected light is deflected to detect the reflected light. an alignment light detection step; and a first control step of controlling the moving mechanism so that a working distance with respect to the eye to be inspected becomes a first working distance based on a detection result of the reflected light in the first alignment light detection step. and deflecting the light reflected from the eye to be examined irradiated by deflecting the alignment light, or the light reflected by the eye to be examined irradiated with the alignment light, in the second mode of performing the second examination. a second alignment light detection step of detecting the reflected light obtained by the second alignment light detection step; and a second control step of controlling the moving mechanism.

A twelfth aspect of some embodiments is based on the eleventh aspect, wherein in the second control step, a first deflection member is inserted into or removed from the optical path of the alignment light, and a second deflection member is inserted into or removed from the optical path of the reflected light. Detach the deflecting member.

In a thirteenth aspect of some embodiments, in any one of the ninth to twelfth aspects, the ophthalmologic apparatus includes a relay lens that relays light from the anterior segment of the subject's eye, and an anterior eye observation system including an image pickup device for receiving the light from the anterior eye, and the first control step moves the relay lens to a first lens position on the optical axis of the anterior eye observation system; In the second control step, the relay lens is moved to the second lens position on the optical axis of the anterior segment observation system.

In a fourteenth aspect of some embodiments, in any one of the ninth to thirteenth aspects, the ophthalmologic apparatus includes a fixation projection system that projects a fixation target onto the eye to be inspected, and the first control step Then, the first fixation target is projected onto the eye to be examined, and in the second control step, the fixation projection is performed so that a second fixation target having a narrower visual angle than the first fixation target is projected onto the eye to be examined. control the system.

In a fifteenth aspect of some embodiments, in any one of the ninth to fourteenth aspects, the second inspection optical system has an optical scanner, deflects light from a light source with the optical scanner, and Light deflected by the optical scanner is projected onto the subject's eye via the objective lens, and light based on return light from the subject's eye is detected.

In a sixteenth aspect of some embodiments, in any one of the ninth to fifteenth aspects, the first inspection optical system projects light onto the eye to be inspected through the objective lens, and emits light from the eye to be inspected. Includes refractive power measurement optics for detecting returned light.

Advantageous Effects of Invention According to the present invention, it is possible to provide an ophthalmologic apparatus and a method of controlling the ophthalmologic apparatus that are capable of performing a plurality of examinations at optimal working distances with a simple configuration.

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

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 can perform a plurality of examinations including a first examination and a second examination while sharing an objective lens. Hereinafter, it is assumed that an inspection according to the embodiment includes at least one of measurement, measurement, and photography. 2. Description of the Related Art In an ophthalmologic apparatus capable of performing a plurality of examinations, it is possible to reduce the size and cost of the apparatus by sharing the objective lens with a plurality of optical systems corresponding to the types of examinations.

Hereinafter, the ophthalmologic apparatus according to the embodiment can perform refractive power measurement (reflection measurement) as a first examination and scan measurement as a second examination. In scan measurement, measurement results are obtained by deflecting light for measurement, projecting the deflected light onto the subject's eye, and detecting light returned from the subject's eye. Scan measurement includes measurement and photography using optical coherence tomography, measurement and photography using an SLO (Scanning Laser Ophthalmoscope) optical system, and the like. A case will be described below where the ophthalmologic apparatus according to the embodiment performs OCT on the anterior ocular segment and the fundus as scan measurement.

Hereinafter, in the embodiments, the case of using the swept source type OCT method will be described in detail. It is also possible to apply such a configuration.

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. Subjective tests include subjective refraction measurements such as distance tests, near vision tests, contrast tests, glare tests, and visual field tests.

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 intraocular pressure measurement, 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. .

Hereinafter, the working distance is assumed to be the distance from the subject's eye to the tip of the ophthalmologic apparatus. At the tip of the ophthalmic apparatus, for example, there is a lens surface on the object side of the objective lens, or a part of the main body (housing) of the apparatus such as a keratoplate. In some embodiments, the working distance is the distance in the optical axis of the objective lens. The arrangement position of the subject's eye at which alignment is performed includes the vicinity of the arrangement position.

<Configuration of optical system>
1 and 2 show configuration examples of an optical system of an ophthalmologic apparatus according to an embodiment. An ophthalmologic apparatus 1000 according to an embodiment 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 eye to be examined 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 . In an embodiment, the relay lens 56 is movable along the optical axis of the anterior eye observation system 5 (or the optical axis of the relay lens 56). 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 is used for alignment of the objective lens 51 (optical system such as the anterior ocular segment observation system 5) in the optical axis direction (front-rear direction, Z direction, working distance direction) before the reflex measurement or the OCT measurement. The Z alignment system 1 irradiates the eye E with alignment light (infrared light) for alignment in the optical axis direction of the objective lens 51 from a direction forming a predetermined angle with respect to the optical axis of the objective lens 51, The specularly reflected light (the reflected light of the alignment light) in the subject's eye E is detected. The Z alignment system 1 deflects the alignment light or its reflected light according to the type of operation mode of the ophthalmologic apparatus 1000, which will be described later, so that the objective lens 51 is positioned at the first arrangement position (or its vicinity) on the optical axis, or Alignment light is applied to the subject's eye E at a second arrangement position (or its vicinity) closer to the ophthalmologic apparatus 1000 than the first arrangement position, and the reflected light is detected. The operation modes include a first mode in which a refractometer measurement (first inspection) is performed using a refractometer optical system described later, and a second mode in which an OCT measurement (second inspection) is performed using an OCT optical system described later. be Thereby, according to the operation mode, alignment in the Z direction can be performed so that the eye to be examined E is arranged at the optimum position in the Z direction with respect to the optical system.

The Z alignment system 1 includes a Z alignment light source 11, an imaging lens 12, a line sensor 13, deflecting members 14A and 14B, and reflecting mirrors 15A and 15B. The deflection member 14A can be inserted into and removed from the optical path of the alignment light. The deflection member 14B can be inserted into and removed from the optical path of the reflected light of the alignment light. In some embodiments, at least one of deflection members 14A and 14B is a quick return mirror. In some embodiments, at least one of deflection members 14A and 14B is a reflective mirror that can be inserted into and removed from the optical path.

When performing Z alignment before the reflex measurement, the deflection member 14A is arranged in the optical path of the alignment light, and the deflection member 14B is arranged in the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is deflected by the deflecting member 14A toward the reflecting mirror 15A, and the reflecting mirror 15A illuminates the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51. deflected towards. The alignment light applied to the cornea Cr is reflected by the cornea Cr, deflected by the reflecting mirror 15B toward the deflecting member 14B, deflected by the deflecting member 14 toward the imaging lens 12, and detected by the imaging lens 12 as a line sensor. It is imaged on 13 sensor planes. When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13 changes. The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflecting member 14A is retracted from the optical path of the alignment light, and the deflecting member 14B is retracted from the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13 changes. The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

In some embodiments, at least one of deflection members 14A and 14B is a half mirror. In this case, the insertion/removal mechanism and the insertion/removal control of the deflecting members 14A and 14B can be eliminated.

(XY alignment system 2)
The XY alignment system 2 applies light (infrared light) to the eye to be examined E for alignment in the directions perpendicular to the optical axis of the anterior ocular 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 spot 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 amount 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 imaging 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 sweeping (wavelength scanning) light source capable of sweeping (scanning) the wavelength of emitted light, like a general swept source type OCT apparatus. Consists of A wavelength-swept 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 focused 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 the 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, converted into a parallel light beam by the collimator lens unit 89, and passes through the light scanner 88, the focusing lens 87, the relay lens 85, and the reflecting mirror 84. , and is reflected by the dichroic mirror 83 .

The light scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. Optical scanner 88 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 . Scanning modes of the measurement light LS by the optical scanner 88 include, for example, horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric scanning, and spiral scanning.

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, is refracted by the objective lens 51, and reaches the subject's eye E incident on 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 .

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. For example, the OCT light source 101 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 unit 9 moves the focusing lens 87 of the OCT optical system 8 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.

The ophthalmologic apparatus 1000 according to the embodiment uses a common objective lens in at least the Ref measurement optical system and the OCT optical system 8, and performs Ref measurement (refractive power measurement) using the Ref measurement optical system and OCT using the OCT optical system 8. It is possible to change the working distance with measurement. As a result, while ensuring the scanning range of the OCT optical system 8, it is possible to acquire highly accurate ref measurement results and highly accurate OCT measurement results with a simple configuration.

[Working distance for ref measurement]
In the ophthalmologic apparatus 1000 according to the embodiment, the working distance (first working distance) is set so as not to be affected by instrumental myopia when performing reflex measurement. If the ophthalmologic apparatus 1000 includes the keratometry system 3, this working distance is desirably a working distance at which keratometry results useful for corneal shape analysis can be obtained.

FIG. 3 shows an explanatory diagram of the working distance when performing the reflex measurement according to the embodiment. FIG. 3 is an enlarged view of part of the optical system of FIG. In FIG. 3, the same parts as in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The keratometry system 3 is telecentric optics so that a keratometry image whose height does not change even if the working distance changes can be obtained. When light is projected onto the cornea Cr by the keratometry system 3, the cornea acts as a convex mirror, and an image mainly reflected from the front surface of the cornea Cr appears.

Let R be the radius of curvature of the cornea Cr of the subject's eye E, h be the height of the keratling image with respect to the optical axis of the objective lens 51, and α be the projection angle of the ring-shaped light beam with respect to the optical axis. In order to arrange the ring pattern (measurement pattern) at the incident position of the ring-shaped light beam from the keratling light source 32, let β be the angle between the optical axis and the line connecting the center of curvature of the cornea Cr and the incident position. , the following formula holds:

h=R×sin(β) (1)
β=α/2 (2)

Let H be the radius of the keratopattern formed on the keratoplate 31, let WDref be the distance from the keratoplate 31 to the subject's eye E (corneal vertex), and let Δd (= Considering R−√(R ² −h ² )), the following equation holds.

H=(WDref+(R−√(R ² −h ² )))×tan(α)+h (3)

As described above, in the ophthalmologic apparatus 1000 according to the embodiment, the working distance WDref shown in the following equation (4) is set when the ref measurement is performed. Equation (4) is obtained by substituting Equation (1) and Equation (2) into Equation (3).

WDref=((H−h)/tan(2×sin ⁻¹ (h/R))−(R−√(R ² −h ² ))) (4)

In some embodiments, the radius of curvature R uses known data such as model eyes. Note that the effective diameter D of the objective lens 51 can be determined from the radius H of the keratling pattern.

For example, h=1.5 millimeters to measure the corneal topography of an area of φ3 on the cornea Cr useful for corneal topography analysis.

As described above, when the ref measurement is performed, by setting the working distance WDref shown in the formula (4), it is possible to increase the size of the kerato plate 31 while reducing the influence of instrumental myopia by increasing the working distance. can be prevented. As a result, it is possible to provide an ophthalmologic apparatus capable of acquiring highly accurate ref measurement results and keratometry results with a simple configuration.

[Working distance when performing OCT measurement]
In the ophthalmologic apparatus 1000 according to the embodiment, the working distance (second working distance) is set so that at least a scanning range useful for analysis using standard data can be scanned when performing OCT measurement. The standard data is statistically derived from a large number of measurement data of normal eyes and the information of the subject of the measurement data, and is called normal eye data (normative data) or the like. The working distance set when performing OCT measurement is the working distance that enables scanning of the scan range (or a wider range than the scan range) when the measurement data used to derive the above standard data was obtained. you can

FIG. 4 shows an explanatory diagram of the working distance when performing OCT measurement according to the embodiment. FIG. 4 is an enlarged view of part of the optical system of FIG. In FIG. 4, the same parts as those in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The light scanner 88 deflects the measurement light LS in the X direction and the Y direction, respectively, in order to acquire the data of the desired scan range without exhaustion. Assuming that the scanning range of the fundus oculi Ef is RA×RA, the optical scanner 88 must be deflected by at least RA×√2 (=SA) in each direction.

Here, the optical scanner 88 is arranged so as to be optically substantially conjugate with the pupil of the eye E to be examined. Let WDoct be the working distance, La be the distance from the anterior surface of the cornea to the pupil, Le be the distance from the pupil to the fundus, and Le be the distance from the keratoplate 31 (the surface on the side of the subject's eye E) to the main surface of the objective lens 51. Let Lk. From the relationship of similarity between a triangle whose vertex is the pupil and whose base is the radius of the objective lens 51, and a triangle whose vertex is the pupil and whose base is the scan range SA/2 in the fundus Ef, the scan range SA satisfies the following formula: .

SA=Le×D/(WDoct+La+Lk) (5)

As described above, in the ophthalmologic apparatus 1000 according to the embodiment, when performing OCT measurement, the working distance WDoct shown in the following equation (6) is set.

WDoct=(Le×D)/SA−(La+Lk) (6)

For example, the effective diameter D of the objective lens 51 is determined from the kerating pattern radius H as the diameter of the scanning range (scanning diameter) required for scanning the scanning range SA in the objective lens 51 . In some embodiments, the distances Le and La use standard eye data or known data such as an eye model. In some embodiments, distance Lk is known data in ophthalmic device 1000 . In some embodiments, distance Lk is approximately zero.

This makes it possible to compare the results obtained by OCT measurement with existing standard data, and to utilize the existing standard data to assist in making useful judgments on the OCT measurement results.

For example, the scan area SA is (6×√2) millimeters, (9×√2) millimeters, or (12×√2) millimeters to scan the scan area required for analysis using standard data.

In some embodiments, the ophthalmic device 1000 can set a working distance corresponding to a scan range selected from a plurality of scan ranges, and perform OCT measurements at the set working distance. The working distance corresponding to the scanning range may be calculated each time according to the formula (6), or may be obtained in advance.

As described above, when performing OCT measurement, by setting the working distance WDoct shown in Equation (6), it is possible to obtain scan results useful for analysis using standard data. As a result, it is possible to provide an ophthalmologic apparatus with a simple configuration that can utilize existing standard data to assist in making useful judgments on OCT measurement results.

As described above, the ophthalmologic apparatus 1000 relatively moves the optical system in the Z direction with respect to the subject's eye E so that the working distance WDref is obtained when performing the REF measurement, and the working distance WDref when performing the OCT measurement. The optical system is relatively moved in the Z direction with respect to the subject's eye E so as to be WDoct. At this time, in the ophthalmologic apparatus 1000, it is desirable that the fixation projection system 4 and the anterior ocular segment observation system 5 are controlled along with switching between the REF measurement and the OCT measurement.

In the fixation projection system 4, a visual target for reflex measurement (for example, a landscape chart) is projected onto the subject's eye E when performing reflex measurement. It is switched to project a target (for example, a dot target or a cross target) onto the eye E to be examined. In the anterior eye observation system 5, the relay lens 56 is moved to a position on the optical axis for the REF measurement (first lens position) when the REF measurement is performed. (second lens position).

<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. 5 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. Processor functions include, for example, CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), programmable logic device (e.g., 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 . The ophthalmologic apparatus 1000 also includes a moving mechanism 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.

(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 (including Z alignment light sources 11A and 11B described later), control of the line sensor 13 (including line sensors 13A and 13B described later), and control of the insertion/removal mechanism 14D. control, etc. 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 line sensor. 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 insertion/removal mechanism 14D inserts/removes the deflecting member 14A with respect to the optical path of the alignment light, and inserts/removes the deflecting member 14B with respect to the optical path of the reflected light of the alignment light. In some embodiments, the mechanism for inserting and removing bias member 14A and the mechanism for inserting and removing bias member 14B are the same mechanism. In some embodiments, the mechanism for inserting and removing bias member 14A is a separate mechanism from the mechanism for inserting and removing bias member 14B. The insertion/removal mechanism 14D receives control from the main control unit 211 and inserts/removes the deflection members 14A and 14B with respect to the respective optical paths. The insertion/removal mechanism 14D according to some embodiments includes a known mechanism for arranging a mirror that constitutes a quick return mirror in the optical path or withdrawing it from the optical path. The insertion/removal mechanism 14D according to some embodiments includes a solenoid having a movable portion coupled to the deflection member 14A or the deflection member 14B. By outputting a control signal to the insertion/removal mechanism 14D, the main control unit 211 arranges the deflection member 14A in the optical path of the alignment light and arranges the deflection member 14B in the optical path of the reflected light. , the deflecting member 14A is retracted from the optical path of the alignment light, and the deflecting member 14B is retracted from the optical path of the reflected light.

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 spot 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 known arithmetic operations 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.

FIG. 6A shows an explanatory diagram of a fixation target according to the first presentation example of the embodiment. FIG. 6A schematically shows a fixation target according to the first presentation example.

The main control unit 211 causes the liquid crystal panel 41 to display the fixation target FT1 shown in FIG. 6A when performing reflex measurement, and displays the fixation target FT2 or FT3 shown in FIG. 6A on the liquid crystal panel 41 when performing OCT measurement. 41. The fixation target FT1 is a landscape chart. The fixation target FT2 is a bright spot (dot target) with a smaller visual angle than the fixation target FT1. The fixation target FT3 is a cross target with a smaller visual angle than the fixation target FT1. In the first presentation example, the main control unit 211 switches and displays the fixation target FT1 and the fixation target FT2 according to the operation mode (inspection mode, measurement mode). In addition, the main control unit 211 can switch the display between the fixation target FT1 and the fixation target FT3 according to the operation mode.

The operation modes according to this embodiment include, for example, a reflex measurement mode, an OCT measurement mode, a mode in which reflex measurement is performed and then automatically transitions to OCT measurement, and the like.

By changing the fixation target displayed on the liquid crystal panel 41 in accordance with the operation mode in this manner, the fixation target is presented to the subject's eye without visual acuity adjustment in the REF measurement, and the fixation target is presented in the OCT measurement in accordance with the measurement site and the like. A fixation target can be presented so that a desired portion of the subject's eye is placed at a predetermined measurement position.

FIG. 6B shows an explanatory diagram of the fixation target according to the second presentation example of the embodiment. FIG. 6B schematically shows a fixation target according to the second presentation example.

The main control unit 211 displays the fixation target FT4 shown in FIG. 6B on the liquid crystal panel 41 when performing reflex measurement, and displays the fixation target FT4 shown in FIG. 6B so as to be superimposed on the fixation target FT4 when performing OCT measurement. BP1 is displayed on the liquid crystal panel 41 . The fixation target FT4 is a landscape chart similar to the fixation target FT1 shown in FIG. 6A. The fixation target BP1 is a bright spot (dot target) having a smaller visual angle than the fixation target FT4. In the second presentation example, the main control unit 211 displays the fixation target BP1 on the fixation target FT4 according to the operation mode (examination mode). The main control unit 211 can blink the fixation target BP1 and move the display position of the fixation target BP1. In some embodiments, the main control unit 211 increases the brightness of part of the fixation target FT4 or periodically increases or decreases the brightness of part of the fixation target FT4 when performing OCT measurement. In some embodiments, instead of fixation target BP1, fixation target FT3 shown in FIG. 6A is presented.

In the second presentation example, as in the first presentation example, the fixation target is presented so that the subject's eye does not adjust the visual acuity in the REF measurement, and the desired site in the subject's eye is specified according to the measurement site in the OCT measurement. The fixation target can be presented so as to be placed at the measurement position of .

In FIG. 5, for example, the fixation projection system 4 is provided with a moving mechanism for moving the liquid crystal panel 41 (or the fixation unit 40) 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 control signals to the actuators, 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 for the anterior segment observation system 5 includes control of the anterior segment illumination light source 50, control of the lens moving mechanism 56D that moves the relay lens 56, 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. Like the moving mechanism 200, the lens moving mechanism 56D is provided with an actuator that generates driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the lens moving mechanism 56D by sending a control signal to the actuator according to the operation mode (inspection mode) to move the relay lens 56 in the optical axis direction. For example, the storage unit 212 stores in advance information corresponding to the position of the relay lens 56 on the optical axis in association with the operation mode. The main control unit 211 refers to the information stored in the storage unit 212 and moves the relay lens 56 to a position on the optical axis corresponding to the operation mode. As a result, even when the working distance is changed according to the operation mode, the signal from the anterior eye segment can be imaged on the imaging surface of the imaging device 59, and the focus can be maintained even during the REF measurement and the OCT measurement. It becomes possible to observe a matching anterior segment image. 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/off the light source, adjusting the amount of light, and the like. Thereby, 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, control of the optical scanner 88, control of the focusing lens 87, control of the corner cube 114, control of the detector 125, control of the DAQ 130, and the like. 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 optical scanner 88 includes control of the scanning position, scanning range, and scanning speed by the first galvanomirror, and control of the scanning position, scanning range, and scanning speed by the second galvanomirror.

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 part, movement range (focusing) corresponding to the imaging part. movement control within the focal range). 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 retaining member that retains the focusing lenses 74 and 87 and a drive that drives the retaining member. The main control section 211 performs movement control of the focusing lenses 74 and 87 by controlling the driving section. For example, the main control unit 211 may move the focusing lens 87 in conjunction with the movement of the focusing lens 74, and then move only the focusing lens 87 based on the intensity of the interference signal.

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, tomographic image data, fundus image data, and control information referred to by the main control unit 211 (for example, the lens position of the relay lens 56). information), eye information 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)
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 principal meridian and the weak principal meridian 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. Further, 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 on 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.

The ref measurement projection system 6 and the ref measurement light receiving system 7 are examples of the "first inspection optical system" or the "refractive power measurement optical system" according to the embodiment. The OCT optical system 8 is an example of the "second inspection optical system" according to the embodiment. The working distance WDref is an example of the "first working distance" according to the embodiment. The working distance WDoct is an example of a "second working distance" according to the embodiment. The Z alignment system 1 is an example of the "alignment optical system" according to the embodiment. The Z alignment light source 11 is an example of the "alignment light source" according to the embodiment. The deflection member 14A is an example of a "first deflection member" according to the embodiment. The deflection member 14B is an example of a "second deflection member" according to the embodiment. The line sensor 13 is an example of a "detection element" according to the embodiment. The reflecting mirror 15A is an example of a "third deflection member" according to the embodiment. The reflecting mirror 15B is an example of a "fourth deflection member" according to the embodiment.

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

FIG. 7 shows an example of the operation of the ophthalmologic apparatus 1000. As shown in FIG. FIG. 7 shows a flow diagram of an operation example of the ophthalmologic apparatus 1000 when performing OCT measurement after REF measurement. A computer program for realizing the processing shown in FIG. 7 is stored in the storage unit 212 . The main control unit 211 executes the processing shown in FIG. 7 by operating according to this computer program.

(S1: lens movement)
When the examiner performs a predetermined operation on the operation unit 280 with the subject's face fixed to the face receiving unit (not shown), the main control unit 211 controls the lens moving mechanism 56D to , the relay lens 56 is moved to the lens position for the reflex measurement on the optical axis of the anterior segment observation system 5 . In some embodiments, the main control unit 211 refers to control information stored in advance in the storage unit 212, and based on the lens position information stored in association with the reflex measurement mode set before step S1. to control the lens moving mechanism 56D.

(S2: Alignment)
Subsequently, the main controller 211 executes alignment. In step S2, the main controller 211 controls the insertion/removal mechanism 14D to arrange the deflection member 14A in the optical path of the alignment light and the deflection member 14B in the optical path of the reflected light.

After that, 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 eye to be examined E is placed at the examination position through the above-described alignment (alignment by the Z alignment system 1 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. Further, this alignment is performed as needed until the reflex measurement (refractive power measurement) is completed.

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

(S3: Kerato measurement)
Next, the main control unit 211 causes the liquid crystal panel 41 to display the fixation target FT1 (landscape chart) shown in FIG. 6A.

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 . The operation of the ophthalmologic apparatus 1000 proceeds to step S4 according to an instruction from the main control unit 211 or a user's operation or instruction on the operation unit 280 . Note that the keratometry may be performed at the same time as or consecutively when the ring image is acquired in the next reflex measurement.

(S4: refractive power measurement)
Subsequently, the main control unit 211 executes refractive power measurement.

In the reflex measurement, the main control unit 211 projects the ring-shaped measurement pattern light flux for the reflex measurement onto the eye E to be examined as described above. 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. Based on the determined temporary spherical power S and cylindrical power C, 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) (temporary distance). position corresponding to the point). After that, the ring image is acquired again, analyzed, and the temporary spherical power S and the temporary astigmatism power C are obtained, and then finely adjusted by moving from the position moved in the first measurement. After moving the liquid crystal panel 41 further from that position to the fog position, the main control unit 211 controls the ref measurement projection system 6 and the ref measurement light receiving system 7 to acquire the ring image again as the main 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 obtained in the same manner as described above and the movement amount of the focusing lens 74 .

Further, the eye refractive power calculator 221 obtains the position corresponding to the far point of the subject's eye E (the position corresponding to the far point obtained by the main measurement) from the obtained spherical power and cylindrical power. The main control unit 211 moves the liquid crystal panel 41 to the position corresponding to the far point obtained. In the control unit 210 , the position of the focusing lens 74 and the calculated spherical power 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 S5.

When it is determined that the ring image cannot be acquired, the main control unit 211 considers the possibility of the eye being a highly ametropic eye, and moves the ref measurement light source 61 and the focusing lens 74 to the minus power side (for example, -10D), and move it to the plus power side (for example, +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. At this time, the operation of the ophthalmologic apparatus 1000 may proceed to step S5. In the control unit 210, information indicating that the result of the ref measurement was not obtained is stored in the storage unit 212. FIG.

The focusing lens 87 of the OCT optical system 8 is moved in the optical axis direction in conjunction with the movement of the reflector measurement light source 61 and the focusing lens 74 .

(S5: OCT measurement?)
Subsequently, the main control unit 211 determines whether or not to perform OCT measurement. For example, the main control unit 211 determines whether or not to perform OCT measurement by determining whether or not a predetermined operation has been performed on the operation unit 280 . In some embodiments, the main controller 211 determines whether to perform OCT measurement based on the operation mode set before step S1.

When it is determined to perform OCT measurement (S5: Y), the operation of the ophthalmologic apparatus 1000 proceeds to step S6. When it is determined not to perform OCT measurement (S5: N), the operation of the ophthalmologic apparatus 1000 ends (END).

(S6: lens movement)
When it is determined in step S5 that OCT measurement is to be performed (S5: Y), the main controller 211 controls the lens moving mechanism 56D to position the lens for OCT measurement on the optical axis of the anterior eye observation system 5. , the relay lens 56 is moved. In some embodiments, the main control unit 211 refers to control information stored in advance in the storage unit 212, and based on lens position information stored in association with the operation mode set before step S1. It controls the lens moving mechanism 56D.

(S7: Fixation target switching)
Next, the main controller 211 causes the liquid crystal panel 41 to display the dot target or cross target shown in FIG. 6A. Thereby, the fixation target FT2 or the fixation target FT3 is presented to the eye E to be examined.

(S8: alignment)
Subsequently, the main controller 211 executes alignment. In step S8, the main controller 211 controls the insertion/removal mechanism 14D to retract the deflecting member 14A from the optical path of the alignment light and retract the deflecting member 14B from the optical path of the reflected light.

After that, 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 eye to be examined E is placed at the examination position through the above-described alignment (alignment by the Z alignment system 1 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. Also, this alignment is performed at any time until the OCT measurement is completed.

(S9: OCT measurement)
Next, the main controller 211 controls the OCT optical system 8 to perform OCT measurement.

Specifically, 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. For example, detection signals obtained by scanning with the measurement light LS are 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).

FIG. 7 shows an operation example when the scan range for OCT measurement is predetermined before the ref measurement, but the operation of the ophthalmologic apparatus 1000 according to the embodiment is not limited to the flow shown in FIG. In some embodiments, the ophthalmologic apparatus 1000 can specify the scan range of the measurement light LS in OCT measurement, and can set the working distance corresponding to the specified scan range. In some embodiments, ophthalmic device 1000 can be set to a working distance corresponding to a scan range selected from among multiple scan ranges.

FIG. 8 shows another example of the operation of the ophthalmologic apparatus 1000. As shown in FIG. FIG. 8, like FIG. 7, represents a flow diagram of an operation example of the ophthalmologic apparatus 1000 when performing OCT measurement after reflex measurement. A computer program for realizing the processing shown in FIG. 8 is stored in the storage unit 212 . The main control unit 211 executes the processing shown in FIG. 8 by operating according to this computer program.

(S21: Specify scan range)
The main control unit 211 receives designation of the scanning range of the measurement light LS in OCT measurement. The main control unit 211 receives a scan range designated by a predetermined operation using the operation unit 280 . In some embodiments, the scan range is specified by directly inputting numerical values or information corresponding to the scan range to the operation unit 280 . In some embodiments, the scan range is specified by selecting one scan range using the operation unit 280 from a plurality of predetermined scan ranges.

For example, in step S21, the main control unit 211 identifies the working distance corresponding to the designated scan range. In some embodiments, the main controller 211 identifies the working distance for OCT measurement by substituting the designated scan range into Equation (6). In some embodiments, the main controller 211 identifies the working distance corresponding to the designated scan range from a plurality of working distances calculated in advance for a plurality of scan ranges.

(S22: lens movement)
When the examiner performs a predetermined operation on the operation unit 280 with the subject's face fixed to the face receiving unit (not shown), the main control unit 211 operates the lens moving mechanism as in step S1. By controlling 56D, the relay lens 56 is moved to the lens position for reflex measurement on the optical axis of the anterior ocular segment observation system 5 .

(S23: Alignment)
Subsequently, the main controller 211 executes alignment using the Z alignment system 1 and the like, as in step S2.

(S24: Kerato measurement)
Next, the main controller 211 causes the liquid crystal panel 41 to display the fixation target FT1 (landscape chart) shown in FIG. 6A, as in step S3.

Thereafter, the main controller 211 causes the keratometry to be performed by controlling the keratometry system 3 in the same manner as in step S3.

(S25: refractive power measurement)
Subsequently, the main control unit 211 executes refractive power measurement as in step S4.

(S26: lens movement)
Subsequently, the main control unit 211 moves the relay lens 56 to the lens position for OCT measurement on the optical axis of the anterior eye observation system 5 by controlling the lens moving mechanism 56D. In some embodiments, the main control unit 211 refers to control information stored in advance in the storage unit 212, and based on lens position information in which a plurality of lens positions are stored in advance in association with a plurality of working distances. It controls the lens moving mechanism 56D.

(S27: Fixation target switching)
Next, the main control unit 211 causes the liquid crystal panel 41 to display the dot optotype or cross optotype shown in FIG. 6A, as in step S7.

(S28: Alignment)
Subsequently, the main controller 211 performs alignment using the Z alignment system 1 and the like, as in step S8. At this time, the main controller 211 relatively moves the optical system with respect to the subject's eye E so as to achieve the working distance specified in step S21. Also, this alignment is performed at any time until the OCT measurement is completed.

(S29: OCT measurement)
Next, the main controller 211 causes the OCT optical system 8 to be controlled to perform OCT measurement, as in step S9. With this, the operation of the ophthalmologic apparatus 1000 ends (end).

As described above, the objective lens 51 is shared by the reflector measurement optical system and the OCT optical system 8, and the working distance is switched between the reflector measurement and the OCT measurement. It is possible to provide an ophthalmologic apparatus capable of obtaining measurement results and highly accurate OCT measurement results.

In particular, since the working distance is set to the one shown in the formula (4) when the ref measurement is performed, the working distance is lengthened so as to reduce the influence of instrumental myopia and the size of the kerato plate 31 is prevented from increasing. be able to. As a result, it is possible to provide an ophthalmologic apparatus capable of acquiring highly accurate ref measurement results and keratometry results with a simple configuration.

In addition, since the working distance is set to the one shown in Equation (6) when performing OCT measurement, it is possible to obtain scan results that are useful for analysis using standard data. As a result, it is possible to provide an ophthalmologic apparatus with a simple configuration that can utilize existing standard data to assist in making useful judgments on OCT measurement results.

Furthermore, according to the operation mode, the alignment light is deflected to irradiate the subject's eye E, and the reflected light is deflected and detected by the line sensor 13. Therefore, one light source and one line sensor are used. Alignment can be performed for multiple placement positions in the Z direction. As a result, it is possible to adjust the working distance with high precision in the REF measurement and the OCT measurement with a simple configuration.

Although the OCT optical system has been described as an example of an inspection optical system having an optical scanner in the embodiment, the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. Inspection optics according to some embodiments include SLO optics. The SLO optical system is an optical system for scanning the fundus oculi Ef with light from an optical scanner and detecting the returned light with a light receiving device. In some embodiments, the SLO optics obtain en face images of the fundus oculi Ef by laser scanning using confocal optics. The SLO optical system includes an optical scanner, an SLO projection system that deflects light from the SLO light source by the optical scanner and projects the deflected light onto the subject's eye E, and an SLO light receiving system that receives the returned light.

Even in this case, it is possible to obtain scan results useful for analysis using standard data. As a result, it is possible to provide an ophthalmologic apparatus with a simple configuration that can utilize existing standard data to assist in making useful judgments on SLO measurement results.

[Modification]
The configuration of the ophthalmologic apparatus 1000 according to the embodiment is not limited to the configuration described in the above embodiment. A configuration of an ophthalmologic apparatus according to a modification of the embodiment will be described below, focusing on differences from the embodiment.

[First modification]
In the above embodiment, a fixation target suitable for examination or the like is presented to the subject's eye E by switching the fixation target displayed on the liquid crystal panel 41. However, the configuration of the ophthalmic apparatus according to the embodiment is similar to this. It is not limited.

FIG. 9 shows a configuration example of a fixation projection system 4 according to a first modified example of the embodiment. In FIG. 9, the same parts as in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

Instead of the liquid crystal panel 41, the fixation unit 40 provided in the fixation projection system 4 is provided with an illumination light source 45a, an optotype chart 46a, and a fixation light source 47a. A fixation light source 47a, an optotype chart 46a, and a relay lens 42 are arranged in this order from the illumination light source 45a toward the dichroic mirror 83. FIG. The optotype chart 46a is a transmissive optotype chart placed between the illumination light source 45a and the subject's eye E, and representing landscape charts such as fixation targets FT1 and FT4. In some embodiments, the visual target chart 46a is a transmissive film with a landscape chart printed on it. In some embodiments, fixation light source 47a is a point light source having a predetermined emission size.

The main control unit 211 turns on the illumination light source 45a when the reflex measurement is performed, and illuminates the optotype chart 46a with the light from the illumination light source 45a so that the scenery chart (first fixation target) is displayed on the eye E to be examined. project it. Further, the main control unit 211 projects a bright spot (dot target) (second fixation target) onto the eye E to be examined by turning on the fixation light source 47a when performing OCT measurement. In some embodiments, the main controller 211 turns off the fixation light source 47a when performing REF measurement, and turns off the illumination light source 45a when performing OCT measurement. As a result, the scenery chart is presented to the subject's eye E when the reflex measurement is performed, and the bright spots are presented to the subject's eye E when the OCT measurement is performed.

In some embodiments, the fixation light source 47a blinks when taking OCT measurements. In some embodiments, a plurality of fixation light sources 47a are provided, and the main control unit 211 selectively turns on the plurality of fixation light sources 47a to change or move the projection position of the bright spot. do. In some embodiments, the main control unit 211 can change the size of the bright spots by turning on some or all of the plurality of fixation light sources 47a.

[Second modification]
FIG. 10 shows a configuration example of a fixation projection system 4 according to a second modified example of the embodiment. In FIG. 10, parts similar to those in FIG. 1 or 9 are given the same reference numerals, and descriptions thereof are omitted as appropriate.

Instead of the liquid crystal panel 41, the fixation unit 40 provided in the fixation projection system 4 includes an illumination light source 45a, a half mirror 48b, a target chart 46a, a fixation light source 47a, and a relay lens 49b. is provided. The half mirror 48b couples the optical path of light from the illumination light source 45a and the optical path of light from the fixation light source 47a. A half mirror 48b, an optotype chart 46a, and a relay lens 42 are arranged in this order from the illumination light source 45a toward the dichroic mirror 83. As shown in FIG. A relay lens 49b, a half mirror 48b, an optotype chart 46a, and a relay lens 42 are arranged in this order from the fixation light source 47a toward the dichroic mirror 83. FIG. The optotype chart 46a is a transmissive optotype chart that is arranged on the optical path coupled by the half mirror 48b and that represents landscape charts such as the fixation targets FT1 and FT4. The optotype chart 46a is arranged at the focal position of the relay lens 49b.

Light from the illumination light source 45 a passes through the half mirror 48 b , passes through the optotype chart 46 a , passes through the relay lens 42 , and is guided to the dichroic mirror 83 . Light from the fixation light source 47a passes through the relay lens 49b, is reflected by the half mirror 48b, passes through the optotype chart 46a, passes through the relay lens 42, and is guided to the dichroic mirror 83.

The main control unit 211 turns on the illumination light source 45a when the reflex measurement is performed, and illuminates the optotype chart 46a with the light from the illumination light source 45a so that the scenery chart (first fixation target) is displayed on the eye E to be examined. project it. Further, the main control unit 211 projects a bright spot (dot target) (second fixation target) onto the eye E to be examined by turning on the fixation light source 47a when performing OCT measurement. At this time, the light from the fixation light source 47a is condensed at a predetermined position on the optotype chart 46a to form a bright spot.

In some embodiments, the main controller 211 turns off the fixation light source 47a when performing REF measurement, and turns off the illumination light source 45a when performing OCT measurement. As a result, the scenery chart is presented to the subject's eye E when the reflex measurement is performed, and the bright spots are presented to the subject's eye E when the OCT measurement is performed.

As described above, by providing the transmissive optotype chart 46a representing a landscape chart and controlling the illumination light source 45a and the fixation light source 47a according to the operation mode, visual acuity adjustment for the subject's eye can be achieved in the reflex measurement. In the OCT measurement, the fixation target can be presented so as to arrange a desired portion of the subject's eye at a predetermined measurement position according to the measurement portion or the like.

[Third modification]
In the above embodiment or its modification, the case where a single optotype chart is used to project a fixation target during REF measurement and OCT measurement has been described, but the configuration of the ophthalmologic apparatus according to the embodiment is limited to this. not to be

FIG. 11 shows a configuration example of a fixation projection system 4 according to a third modified example of the embodiment. In FIG. 11, the same parts as in FIG. 1 are denoted by the same reference numerals, and the description thereof is omitted as appropriate.

The fixation projection system 4 includes a first fixation projection system for projecting a scenery chart onto the eye E to be examined, and a bright point (dot target, cross target) having a smaller visual angle than the scenery chart, etc., projected onto the eye E to be inspected. and a second fixation projection system for. The optical path of the first fixation projection system and the optical path of the second fixation projection system are coupled by a half mirror 49c. The first fixation projection system includes an illumination light source 45c and a transmissive optotype chart 46c. The second fixation projection system includes an illumination light source 47c and a transmissive optotype chart 48c.

The optotype chart 46c is a transmissive optotype chart placed between the illumination light source 45c and the eye E to be examined, and on which scenery charts such as the fixation targets FT1 and FT4 are displayed. In some embodiments, the visual target chart 46c is a transmissive film with a landscape chart printed on it. The optotype chart 48c is a transmissive optotype chart placed between the illumination light source 47c and the eye to be examined E, and showing dot or crossed optotypes such as the fixation targets FT2 and FT3. In some embodiments, the optotype chart 48c is a transmissive film printed with dot or cross optotypes.

The main control unit 211 projects at least one of the landscape chart and the bright spots (dot targets and cross targets) onto the subject's eye E by controlling the first fixation projection system and the second fixation projection system. Specifically, the main control unit 211 turns on the illumination light source 45c when the reflex measurement is performed, and illuminates the optotype chart 46c with the light from the illumination light source 45c to obtain the scenery chart (first fixation target). is projected onto the eye E to be examined. In addition, the main control unit 211 turns on the illumination light source 47c when performing OCT measurement, and illuminates the optotype chart 48c with the light from the illumination light source 47c to produce bright spots (dot optotypes, cross optotypes) or A cross target (second fixation target) is projected onto the eye E to be examined. In some embodiments, the main controller 211 turns off the illumination light source 47c when performing REF measurement, and turns off the illumination light source 45c when performing OCT measurement. As a result, the scenery chart is presented to the subject's eye E when the reflex measurement is performed, and the bright spots are presented to the subject's eye E when the OCT measurement is performed. In some embodiments, the illumination light source 47c is flashed when performing OCT measurements.

[Fourth modification]
FIG. 12 shows a configuration example of a fixation projection system 4 according to a fourth modified example of the embodiment. In FIG. 12, parts similar to those in FIG. 1 or FIG. 11 are given the same reference numerals, and description thereof will be omitted as appropriate.

As in FIG. 11, the fixation projection system 4 includes a first fixation projection system for projecting a landscape chart onto the eye E to be examined, and a projection system for projecting a bright spot or the like having a smaller visual angle than the landscape chart onto the eye E to be examined. and a second fixation projection system. The optical path of the first fixation projection system and the optical path of the second fixation projection system are switched by the quick return mirror 49d. That is, the quick return mirror 49d selectively arranges the first fixation projection system and the second fixation projection system on the optical path of the fixation projection system.

The main control unit 211 controls the quick return mirror 49d so that the first fixation projection system is placed in the optical path of the fixation projection system 4 when performing reflex measurement, turns on the illumination light source 45c, and turns on the illumination light source. The landscape chart (first fixation target) is projected onto the subject's eye E by illuminating the optotype chart 46c with the light from 45c. Further, the main control unit 211 controls the quick return mirror 49d so that the second fixation projection system is arranged in the optical path of the fixation projection system 4 when performing OCT measurement, turns on the illumination light source 47c, and turns on the illumination light source 47c. A bright spot (dot target, cross target) (second fixation target) is projected onto the subject's eye E by illuminating the optotype chart 48c with light from the light source 47c.

In some embodiments, the main controller 211 turns off the illumination light source 47c when performing REF measurement, and turns off the illumination light source 45c when performing OCT measurement. As a result, the scenery chart is presented to the subject's eye E when the reflex measurement is performed, and the bright spots are presented to the subject's eye E when the OCT measurement is performed. In some embodiments, the illumination light source 47c is flashed when performing OCT measurements.

[Fifth Modification]
A moving mechanism for moving the first fixation projection system and the second fixation projection system may be provided instead of the quick return mirror 49d as the switching mechanism according to the fourth modification. The movement mechanism selectively arranges the first fixation projection system and the second fixation projection system in the optical path of the fixation projection system 4 by moving the first fixation projection system and the second fixation projection system. .

For example, the main control unit 211 selectively arranges the first fixation projection system and the second fixation projection system in the optical path of the fixation projection system 4 by controlling the movement mechanism. That is, the illumination light source and optotype chart for REF measurement and the illumination light source and optotype chart for OCT measurement are selectively arranged in the optical path of the fixation projection system 4 . The main control unit 211 controls the movement mechanism so that the first fixation projection system is placed in the optical path of the fixation projection system 4 when performing reflex measurement, turns on the illumination light source 45c, and turns on the illumination light source 45c. The landscape chart (first fixation target) is projected onto the subject's eye E by illuminating the optotype chart 46c with the light of . In addition, the main control unit 211 controls the moving mechanism so that the second fixation projection system is arranged in the optical path of the fixation projection system 4 when performing OCT measurement, turns on the illumination light source 47c, and turns on the illumination light source 47c. A bright spot (dot target) or cross target (second fixation target) is projected onto the subject's eye E by illuminating the optotype chart 48c with the light from 47c.

In some embodiments, the movement mechanism moves the first fixation projection system and the second fixation projection system in a direction that intersects the optical path of the fixation projection system 4 . A first fixation projection system and a second fixation projection system are selectively arranged in an optical path.

As described above, the transmissive optotype chart 46c representing a landscape chart and the transmissive optotype chart 48c representing a dot optotype or a cross optotype are provided, and illumination is performed according to the operation mode. By controlling the light sources 45a and 47c, a fixation target is presented to the eye to be inspected so as not to adjust visual acuity in the REF measurement, and a desired part of the eye to be inspected is arranged at a predetermined measurement position in the OCT measurement according to the measurement part and the like. The fixation target can be presented so as to

[Sixth modification]
In the above embodiment or its modification, the Z alignment system 1 is configured to irradiate alignment light with reference to the arrangement position (second arrangement position) for OCT measurement, but the ophthalmologic apparatus according to the embodiment is not limited to this.

FIG. 13 shows a configuration example of an optical system of an ophthalmologic apparatus according to a sixth modification of the embodiment. In FIG. 13, parts similar to those in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmic apparatus according to the sixth modification differs from the configuration of the ophthalmic apparatus according to the embodiment in the configuration of the Z alignment system 1 . The Z alignment system 1 according to the sixth modification is configured to irradiate alignment light with reference to the arrangement position (first arrangement position) of the subject's eye E for reflex measurement on the optical axis of the objective lens 51 . Similar to the Z alignment system 1 according to the embodiment, the Z alignment system 1 according to the sixth modification includes a Z alignment light source 11, an imaging lens 12, a line sensor 13, deflecting members 14A and 14B, and reflecting mirrors. 15A and 15B.

In the embodiment, the deflection member 14A is arranged in the optical path of the alignment light for the REF measurement, the deflection member 14B is arranged in the optical path of the reflected light, the deflection member 14A is retracted from the optical path of the alignment light for the OCT measurement, and the deflection member 14B is retracted from the optical path of the reflected light. On the other hand, in the sixth modification, the deflecting member 14A is retracted from the optical path of the alignment light for ref measurement, the deflecting member 14B is retracted from the optical path of the reflected light, and the deflecting member 14A is retracted from the optical path of the alignment light for OCT measurement. , and the deflection member 14B is arranged in the optical path of the reflected light.

That is, when performing Z alignment before the reflex measurement, the deflecting member 14A is retracted from the optical path of the alignment light, and the deflecting member 14B is retracted from the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14A is arranged in the optical path of the alignment light, and the deflection member 14B is arranged in the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is deflected by the deflecting member 14A toward the reflecting mirror 15A, and the reflecting mirror 15A illuminates the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51. deflected towards. The alignment light applied to the cornea Cr is reflected by the cornea Cr, deflected by the reflecting mirror 15B toward the deflection member 14B, deflected by the deflection member 14B toward the imaging lens 12, and detected by the imaging lens 12 as a line sensor. It is imaged on 13 sensor planes. The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the sixth modification is the same as the operation of the ophthalmologic apparatus according to the embodiment, so detailed description thereof will be omitted.

According to the sixth modification, the same effects as those of the embodiment can be obtained.

[Seventh modification]
In the above embodiment or its modification, the case where the Z alignment system 1 includes the deflecting members 14A and 14B and the reflecting mirrors 15A and 15B has been described, but the configuration of the ophthalmologic apparatus according to the embodiment is limited to this. isn't it.

FIG. 14 shows a configuration example of an optical system of an ophthalmologic apparatus according to a seventh modification of the embodiment. In FIG. 14, the same parts as those in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmic apparatus according to the seventh modification differs from the configuration of the ophthalmic apparatus according to the embodiment in the configuration of the Z alignment system 1 . The Z alignment system 1 according to the seventh modification has a configuration in which the reflecting mirrors 15A and 15B are omitted from the Z alignment system 1 according to the embodiment.

In the seventh modification, the deflection member 14A is arranged in the optical path of the alignment light for ref measurement, the deflection member 14B is arranged in the optical path of the reflected light, the deflection member 14A is retracted from the optical path of the alignment light for OCT measurement, The deflection member 14B is retracted from the optical path of the reflected light.

That is, when performing Z alignment before the ref measurement, the deflection member 14A is arranged in the optical path of the alignment light, and the deflection member 14B is arranged in the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is deflected by the deflection member 14A toward the cornea Cr of the subject's eye E near the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, deflected toward the imaging lens 12 by the deflecting member 14B, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflecting member 14A is retracted from the optical path of the alignment light, and the deflecting member 14B is retracted from the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the seventh modification is the same as the operation of the ophthalmologic apparatus according to the embodiment, so detailed description thereof will be omitted.

According to the seventh modification, it is possible to obtain the same effect as the embodiment while simplifying the configuration of the Z alignment system compared to the embodiment.

[Eighth modification]
In the seventh modification, the Z alignment system 1 is configured to irradiate the alignment light with reference to the placement position for OCT measurement (second placement position). is not limited to

FIG. 15 shows a configuration example of an optical system of an ophthalmologic apparatus according to an eighth modification of the embodiment. In FIG. 15, the same parts as those in FIG. 14 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmic apparatus according to the eighth modification differs from the configuration of the ophthalmic apparatus according to the seventh modification in the configuration of the Z alignment system 1 . The Z alignment system 1 according to the eighth modification is configured to irradiate alignment light with reference to the arrangement position (first arrangement position) of the subject's eye E for reflex measurement on the optical axis of the objective lens 51 . Similar to the Z alignment system 1 according to the seventh modification, the Z alignment system 1 according to the eighth modification includes a Z alignment light source 11, an imaging lens 12, a line sensor 13, and deflection members 14A and 14B. include.

In the seventh modification, the deflection member 14A is arranged in the optical path of the alignment light for ref measurement, the deflection member 14B is arranged in the optical path of the reflected light, the deflection member 14A is retracted from the optical path of the alignment light for OCT measurement, The deflection member 14B is retracted from the optical path of the reflected light. On the other hand, in the eighth modified example, the deflecting member 14A is retracted from the optical path of the alignment light for the reflector measurement, the deflecting member 14B is retracted from the optical path of the reflected light, and the deflecting member 14A is retracted from the optical path of the alignment light for the OCT measurement. , and the deflection member 14B is arranged in the optical path of the reflected light.

That is, when performing Z alignment before the reflex measurement, the deflecting member 14A is retracted from the optical path of the alignment light, and the deflecting member 14B is retracted from the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14A is arranged in the optical path of the alignment light, and the deflection member 14B is arranged in the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is deflected by the deflection member 14A toward the cornea Cr of the subject's eye E near the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, deflected toward the imaging lens 12 by the deflecting member 14B, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the eighth modified example is the same as the operation of the ophthalmic apparatus according to the seventh modified example, so detailed description thereof will be omitted.

According to the eighth modification, the same effects as those of the seventh modification can be obtained.

[Ninth Modification]
In the above embodiment or its modification, the case where the Z alignment system 1 inserts and removes both the deflecting members 14A and 14B has been described, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. .

FIG. 16 shows a configuration example of an optical system of an ophthalmologic apparatus according to a ninth modification of the embodiment. In FIG. 16, the same parts as in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmologic apparatus according to the ninth modification differs from the configuration of the ophthalmologic apparatus according to the embodiment in the Z alignment system 1 . The Z alignment system 1 according to the ninth modification is configured to irradiate alignment light based on the arrangement position (second arrangement position) for OCT measurement on the optical axis of the objective lens 51 . A Z alignment system 1 according to the ninth modification includes a Z alignment light source 11, imaging lenses 12A and 12B, line sensors 13A and 13B, a deflecting member 14A, and a reflecting mirror 15A. The imaging lens 12A and the line sensor 13A are arranged so as to detect the reflected light of the alignment light from the subject's eye E arranged near the arrangement position for the reflex measurement on the optical axis of the objective lens 51 . The imaging lens 12B and the line sensor 13B are arranged to detect the reflected light of the alignment light from the subject's eye E arranged near the arrangement position for OCT measurement on the optical axis of the objective lens 51 .

In the ninth modification, the deflection member 14A is arranged in the optical path of the alignment light for the REF measurement, and the deflection member 14A is retracted from the optical path of the alignment light for the OCT measurement.

That is, when performing Z alignment before the ref measurement, the deflection member 14A is arranged in the optical path of the alignment light. Alignment light output from the Z alignment light source 11 is deflected by the deflecting member 14A toward the reflecting mirror 15A, and the reflecting mirror 15A illuminates the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51. deflected towards. The alignment light applied to the cornea Cr is reflected by the cornea Cr, and is imaged on the sensor surface of the line sensor 13A by the imaging lens 12A. When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13A changes. The processing unit 9 obtains the position of the corneal apex of the eye to be examined E based on the light projection position on the sensor surface of the line sensor 13A before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14A is retracted from the optical path of the alignment light. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image on the sensor surface of the line sensor 13B by the imaging lens 12B. When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13B changes. Before the OCT measurement, the processing unit 9 determines 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 13B, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the ninth modification is the same as the operation of the ophthalmologic apparatus according to the embodiment, so detailed description will be omitted.

According to the ninth modification, since the deflection member 14B and its insertion/removal mechanism can be omitted, the same effects as those of the embodiment can be obtained while simplifying the configuration of the Z alignment system compared to the embodiment. can.

[Tenth Modification]
In the ninth modification, the Z alignment system 1 is configured to irradiate alignment light with reference to the placement position for OCT measurement (second placement position), but the configuration of the ophthalmologic apparatus according to the embodiment is this. is not limited to

FIG. 17 shows a configuration example of an optical system of an ophthalmologic apparatus according to a tenth modification of the embodiment. In FIG. 17, the same parts as those in FIG. 16 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmic apparatus according to the tenth modification differs from the configuration of the ophthalmic apparatus according to the ninth modification in the configuration of the Z alignment system 1 . The Z alignment system 1 according to the tenth modification is configured to irradiate alignment light with reference to the arrangement position (first arrangement position) of the subject's eye E for reflex measurement on the optical axis of the objective lens 51 . Similar to the Z alignment system 1 according to the ninth modification, the Z alignment system 1 according to the tenth modification includes a Z alignment light source 11, imaging lenses 12A and 12B, line sensors 13A and 13B, and a deflection member 14A. and a reflecting mirror 15A.

In the tenth modification, the deflecting member 14A is retracted from the optical path of the alignment light for the REF measurement, and the deflecting member 14A is arranged in the optical path of the alignment light for the OCT measurement.

That is, when performing Z alignment before the ref measurement, the deflection member 14A is retracted from the optical path of the alignment light. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, and is imaged on the sensor surface of the line sensor 13A by the imaging lens 12A. The processing unit 9 obtains the position of the corneal apex of the eye to be examined E based on the light projection position on the sensor surface of the line sensor 13A before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14A is arranged in the optical path of the alignment light. Alignment light output from the Z alignment light source 11 is deflected by the deflecting member 14A toward the reflecting mirror 15A, and the reflecting mirror 15A illuminates the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51. deflected towards. The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image on the sensor surface of the line sensor 13B by the imaging lens 12B. Before the OCT measurement, the processing unit 9 determines 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 13B, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the tenth modification is the same as the operation of the ophthalmologic apparatus according to the ninth modification, so detailed description thereof will be omitted.

According to the tenth modification, the same effects as those of the ninth modification can be obtained.

[11th Modification]
Although the line sensors 13A and 13B are provided in the ninth and tenth modified examples, the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. The configuration of the ophthalmologic apparatus according to the eleventh modification will be described below, focusing on differences from the configuration of the ophthalmologic apparatus according to the ninth modification. The configuration of the ophthalmologic apparatus according to the eleventh modification can be applied to the configuration of the ophthalmologic apparatus according to the tenth modification.

FIG. 18 shows a configuration example of an optical system of an ophthalmologic apparatus according to an eleventh modification of the embodiment. In FIG. 18, the same parts as in FIG. 16 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmologic apparatus according to the eleventh modification differs from the configuration of the ophthalmologic apparatus according to the ninth modification in that a line sensor 13 is provided instead of the line sensors 13A and 13B. In the eleventh modification, the imaging lens 12A and the line sensor 13 are configured to detect the reflected light of the alignment light from the subject's eye E, which is arranged near the arrangement position for the ref measurement on the optical axis of the objective lens 51. placed. The imaging lens 12B and the line sensor 13 are arranged so as to detect the reflected light of the alignment light from the subject's eye E arranged near the arrangement position for OCT measurement on the optical axis of the objective lens 51 .

That is, when performing Z alignment before the ref measurement, the alignment light irradiated to the cornea Cr is reflected by the cornea Cr and is imaged on the sensor surface of the line sensor 13 by the imaging lens 12A. When the position of the corneal vertex changes in the optical axis direction of the anterior ocular segment observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13 changes to the first projection reference position for reflector measurement. Change to standards. The processing unit 9 obtains the position of the corneal vertex of the subject's eye E based on the light projection position with reference to the first projection reference position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, the optical system is adjusted. Z alignment is performed by controlling the moving mechanism.

Further, when performing Z alignment before OCT measurement, the alignment light irradiated to the cornea Cr is reflected by the cornea Cr, and is imaged on the sensor surface of the line sensor 13 by the imaging lens 12B. When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13 changes to the second projection reference position for OCT measurement. Change to standards. Before the OCT measurement, the processing unit 9 obtains the position of the corneal vertex of the eye to be examined E based on the light projection position with reference to the second projection reference position on the sensor surface of the line sensor 13, and adjusts the optical system based on this. Z alignment is performed by controlling the moving mechanism.

According to the eleventh modified example, since it is not necessary to provide a plurality of line sensors, it is possible to reduce the size and cost of the ophthalmologic apparatus.

[Twelfth Modification]
In the ninth to eleventh modified examples, the case where the Z alignment system 1 inserts and removes the deflection member 14A has been described, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this.

FIG. 19 shows a configuration example of an optical system of an ophthalmologic apparatus according to a twelfth modification of the embodiment. In FIG. 19, the same parts as those in FIG. 1 are assigned the same reference numerals, and the description thereof is omitted as appropriate.

The configuration of the ophthalmologic apparatus according to the twelfth modification differs from the configuration of the ophthalmologic apparatus according to the embodiment in the Z alignment system 1 . A Z alignment system 1 according to the twelfth modification includes Z alignment light sources 11A and 11B, an imaging lens 12, a line sensor 13, a deflecting member 14B, and a reflecting mirror 15B. The Z alignment light source 11A is arranged so as to irradiate the alignment light with reference to the arrangement position for the reflex measurement on the optical axis of the objective lens 51 . The Z alignment light source 11B is arranged so as to irradiate alignment light with reference to the arrangement position for OCT measurement on the optical axis of the objective lens 51 . The imaging lens 12 and the line sensor 13 are arranged so as to detect the reflected light of the alignment light from the subject's eye E arranged near the arrangement position for OCT measurement on the optical axis of the objective lens 51 .

In the twelfth modification, the deflecting member 14B is arranged in the optical path of the reflected light for REF measurement, and the deflecting member 14B is retracted from the optical path of the reflected light for OCT measurement.

That is, when performing Z alignment before the ref measurement, the deflection member 14B is arranged in the optical path of the reflected light. The alignment light output from the Z alignment light source 11A is irradiated toward the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, reflected by the reflecting mirror 15B toward the deflecting member 14B, deflected by the deflecting member 14B toward the imaging lens 12, and detected by the imaging lens 12 as a line sensor. It is imaged on 13 sensor planes. The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14B is retracted from the optical path of the reflected light. The alignment light output from the Z alignment light source 11B is irradiated onto the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the twelfth modification is the same as the operation of the ophthalmologic apparatus according to the embodiment, so detailed description thereof will be omitted.

According to the twelfth modification, since the deflecting member 14A and its insertion/removal mechanism can be omitted, it is possible to obtain the same effect as the embodiment while simplifying the configuration of the Z alignment system compared to the embodiment. can.

[Thirteenth Modification]
In the twelfth modification, the Z alignment system 1 is configured to irradiate the alignment light with reference to the placement position for OCT measurement (second placement position). is not limited to

FIG. 20 shows a configuration example of an optical system of an ophthalmologic apparatus according to a thirteenth modification of the embodiment. 20, the same parts as in FIG. 19 are denoted by the same reference numerals, and the description thereof is omitted as appropriate.

The configuration of the ophthalmic apparatus according to the thirteenth modification differs from the configuration of the ophthalmic apparatus according to the twelfth modification in the configuration of the Z alignment system 1 . Similar to the Z alignment system 1 according to the 12th modification, the Z alignment system 1 according to the 13th modification includes Z alignment light sources 11A and 11B, an imaging lens 12, a line sensor 13, a deflection member 14B, and a reflecting mirror 15B.

In the thirteenth modification, the deflection member 14B is retracted from the optical path of the reflected light for the REF measurement, and the deflection member 14B is arranged in the optical path of the reflected light for the OCT measurement.

That is, when performing Z alignment before the ref measurement, the deflecting member 14B is retracted from the optical path of the reflected light. Alignment light output from the Z alignment light source 11A is applied to the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14B is arranged in the optical path of the reflected light. The alignment light output from the Z alignment light source 11B is irradiated onto the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, reflected by the reflecting mirror 15B toward the deflecting member 14B, deflected by the deflecting member 14B toward the imaging lens 12, and detected by the imaging lens 12 as a line sensor. It is imaged on 13 sensor planes. The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the thirteenth modification is the same as the operation of the ophthalmologic apparatus according to the twelfth modification, and detailed description thereof will be omitted.

According to the thirteenth modification, the same effects as those of the twelfth modification can be obtained.

[14th Modification]
In the ninth modification, a case has been described in which the deflection member 14A is inserted into and removed from the optical path of the alignment light, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this.

FIG. 21 shows a configuration example of an optical system of an ophthalmologic apparatus according to a fourteenth modification of the embodiment. In FIG. 21, the same parts as those in FIG. 16 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmologic apparatus according to the fourteenth modification differs from the configuration of the ophthalmologic apparatus according to the ninth modification in the Z alignment system 1 . In the Z alignment system 1 according to the fourteenth modification, the alignment light source 11 is a light source with a wide light distribution angle. The alignment light source 11 has a light distribution angle capable of irradiating light to the first arrangement position and the second arrangement position on the optical axis of the objective lens 51 . The imaging lens 12A and the line sensor 13A are arranged so as to detect the reflected light of the alignment light from the subject's eye E arranged near the first arrangement position on the optical axis of the objective lens 51 . The imaging lens 12B and the line sensor 13B are arranged to detect the reflected light of the alignment light from the subject's eye E arranged near the second arrangement position on the optical axis of the objective lens 51 .

That is, when performing Z alignment before the ref measurement, the alignment light output from the Z alignment light source 11 is irradiated toward the cornea Cr of the eye E to be examined near the first arrangement position on the optical axis of the objective lens 51. be done. The alignment light applied to the cornea Cr is reflected by the cornea Cr, and is imaged on the sensor surface of the line sensor 13A by the imaging lens 12A. When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13A changes. The processing unit 9 obtains the position of the corneal apex of the eye to be examined E based on the light projection position on the sensor surface of the line sensor 13A before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E near the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image on the sensor surface of the line sensor 13B by the imaging lens 12B. When the position of the corneal vertex changes in the optical axis direction of the anterior eye observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13B changes. Before the OCT measurement, the processing unit 9 determines 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 13B, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the fourteenth modification is the same as the operation of the ophthalmologic apparatus according to the ninth modification, and detailed description thereof will be omitted.

According to the fourteenth modified example, since the deflection member 14A and its insertion/removal mechanism can be omitted, the configuration of the Z alignment system can be simplified compared to the ninth modified example, and the same effects as in the ninth modified example can be obtained. can be obtained.

[Fifteenth Modification]
In the eighth modified example, the deflection member 14A is inserted into and removed from the optical path of the alignment light, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this.

FIG. 22 shows a configuration example of an optical system of an ophthalmologic apparatus according to a fifteenth modification of the embodiment. In FIG. 22, the same parts as those in FIG. 15 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmologic apparatus according to the fifteenth modification differs from the configuration of the ophthalmologic apparatus according to the eighth modification in the configuration of the Z alignment system 1 . In the Z alignment system 1 according to the fifteenth modification, the alignment light source 11 is a light source with a wide light distribution angle. The alignment light source 11 has a light distribution angle capable of irradiating light to the first arrangement position and the second arrangement position on the optical axis of the objective lens 51 . Therefore, in this modification, the deflection member 14A is not required. Further, in this modification, alignment light is emitted with reference to the arrangement position (first arrangement position) of the subject's eye E for reflex measurement on the optical axis of the objective lens 51 . The imaging lens 12 and the line sensor 13 are arranged so as to detect the reflected light of the alignment light from the subject's eye E arranged near the first arrangement position.

In the fifteenth modification, the deflecting member 14B is retracted from the optical path of the reflected light for REF measurement, and the deflecting member 14B is arranged in the optical path of the reflected light for OCT measurement.

That is, when performing Z alignment before the ref measurement, the deflection member 14B is retracted from the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14B is arranged in the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, deflected toward the imaging lens 12 by the deflecting member 14B, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the fifteenth modification is the same as the operation of the ophthalmologic apparatus according to the eighth modification, so detailed description thereof will be omitted.

According to the fifteenth modified example, since the deflection member 14A and its insertion/removal mechanism can be omitted, the configuration of the Z alignment system can be simplified compared to the eighth modified example, and the same effects as in the eighth modified example can be obtained. can be obtained.

[16th Modification]
In the fifteenth modification, the Z alignment system 1 is configured to detect the reflected light of the alignment light from the placement position for the reflector measurement (first placement position). is not limited to this.

FIG. 23 shows a configuration example of an optical system of an ophthalmologic apparatus according to a sixteenth modification of the embodiment. In FIG. 23, the same parts as those in FIG. 22 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmologic apparatus according to the sixteenth modification differs from the configuration of the ophthalmologic apparatus according to the fifteenth modification in the configuration of the Z alignment system 1 . In the Z alignment system 1 according to the sixteenth modification, the alignment light source 11 is a light source with a wide light distribution angle, as in the fifteenth modification. The alignment light source 11 has a light distribution angle capable of irradiating light to the first arrangement position and the second arrangement position on the optical axis of the objective lens 51 . Therefore, in this modification, the deflection member 14A is not required. Further, in this modified example, alignment light is emitted based on the arrangement position (second arrangement position) of the eye E for OCT measurement on the optical axis of the objective lens 51 . The imaging lens 12 and the line sensor 13 are arranged so as to detect the reflected light of the alignment light from the subject's eye E arranged near the second arrangement position.

In the sixteenth modification, the deflection member 14B is arranged in the optical path of the reflected light for REF measurement, and the deflection member 14B is retracted from the optical path of the reflected light for OCT measurement.

That is, when performing Z alignment before the ref measurement, the deflection member 14B is arranged in the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the first arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr, deflected toward the imaging lens 12 by the deflecting member 14B, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the reflex measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

When performing Z alignment before OCT measurement, the deflection member 14B is retracted from the optical path of the reflected light from the eye E to be examined. Alignment light output from the Z alignment light source 11 is applied to the cornea Cr of the subject's eye E in the vicinity of the second arrangement position on the optical axis of the objective lens 51 . The alignment light applied to the cornea Cr is reflected by the cornea Cr and formed into an image by the imaging lens 12 on the sensor surface of the line sensor 13 . The processing unit 9 obtains the position of the corneal apex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13 before the OCT measurement, and based on this, controls the mechanism for moving the optical system to perform Z alignment. to run.

Other than that, the operation of the ophthalmologic apparatus according to the sixteenth modification is the same as the operation of the ophthalmologic apparatus according to the fifteenth modification, so detailed description thereof will be omitted.

According to the sixteenth modified example, as in the fifteenth modified example, the deflecting member 14A and its insertion/removal mechanism can be omitted. Effects similar to those of the eighth modified example can be obtained.

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

An ophthalmologic apparatus (1000) according to some embodiments includes an objective lens (51), a first inspection optical system (ref measurement projection system 6, a reflection measurement light receiving system 7), and a second inspection optical system (OCT optical system 8, SLO optical system), an alignment optical system (Z alignment system 1), a moving mechanism (200), and a controller (210, main controller 211). The first inspection optical system is used to perform a first inspection on the subject's eye (E) via the objective lens. The second inspection optical system is used to perform a second inspection different from the first inspection on the subject's eye via the objective lens. The alignment optical system deflects the alignment light according to the type of operation mode including a first mode for performing a first inspection and a second mode for performing a second inspection, thereby reflecting light from the irradiated subject's eye, Alternatively, the reflected light obtained by deflecting the light reflected by the eye to be inspected irradiated with the alignment light is detected. The moving mechanism moves the objective lens, the first inspection optical system, and the second inspection optical system in the optical axis direction of the objective lens. Based on the detection result of the reflected light obtained by the alignment optical system, the control unit sets the working distance to the subject's eye to be the first working distance in the first mode, and sets the working distance to the second working distance in the second mode. Control the movement mechanism so that

According to such a configuration, since the objective lens is shared between the first inspection optical system and the second inspection optical system, and the working distance is changed between the first inspection and the second inspection, the configuration is simple. Multiple inspections can be performed at their respective optimum working distances. Accordingly, it is possible to provide an ophthalmologic apparatus capable of obtaining highly accurate test results in each test.

In the ophthalmologic apparatus according to some embodiments, the second inspection optical system has an optical scanner (88), deflects light (measurement light LS) from the light source (OCT light source 101) by the optical scanner, The light deflected by is projected onto the subject's eye via the objective lens, and the light (interference light LC) based on the return light from the subject's eye is detected.

According to such a configuration, it is possible to perform a plurality of examinations including OCT measurement, SLO measurement, etc. at the optimum working distance for each with a simple configuration. As a result, it becomes possible to acquire highly accurate measurement results by OCT and high-quality images by SLO.

In the ophthalmologic apparatus according to some embodiments, the first inspection optical system includes a refractive power measurement optical system (a refractometer projection system) that projects light onto the subject's eye via an objective lens and detects light returned from the subject's eye. 6, including a ref measurement light receiving system 7).

According to such a configuration, it is possible to perform a plurality of inspections including refractive power measurement at the optimum working distances with a simple configuration. As a result, it is possible to acquire highly accurate measurement results by refractive power measurement.

In the ophthalmologic apparatus according to some embodiments, the alignment optical system includes an alignment light source (Z alignment light source 11) that outputs alignment light, a first deflection member (deflection member 14A) that deflects the alignment light, and a reflected light. It includes a detection element (line sensor 13) for detection and a second deflecting member (deflecting member 14B) for deflecting the reflected light from the eye to be inspected, and irradiates the eye to be inspected with the alignment light deflected by the first deflecting member. , the detecting element detects the reflected light deflected by the second deflecting member.

According to such a configuration, since the alignment light and its reflected light are deflected, it is possible to provide an ophthalmologic apparatus capable of performing a plurality of examinations at the respective optimum working distances with a simple configuration. become.

In the ophthalmologic apparatus according to some embodiments, the alignment optical system includes a third deflection member (reflecting mirror 15A) that deflects the alignment light deflected by the first deflection member toward the eye to be examined, and a fourth deflection member (reflective mirror 15B) that deflects light toward the second deflection member.

According to such a configuration, in addition to the first deflecting member and the second deflecting member, the alignment light and its reflected light are deflected by providing the third deflecting member and the fourth deflecting member. The configuration makes it possible to provide an ophthalmic apparatus capable of performing a plurality of examinations at respective optimum working distances.

In the ophthalmic apparatus according to some embodiments, the first deflecting member is insertable/removable with respect to the optical path of the alignment light, and the second deflecting member is insertable/removable with respect to the optical path of the reflected light.

According to such a configuration, it is possible to provide an ophthalmologic apparatus capable of performing a plurality of examinations at optimum working distances for each with a simple configuration and control.

An ophthalmologic apparatus according to some embodiments includes a relay lens (56) that relays light from the anterior segment of an eye to be examined, and an imaging element (59) that receives light via the relay lens. An observation system (5) is included, and the controller moves the relay lens to the first lens position on the optical axis of the anterior eye observation system in the first mode, and moves the light of the anterior eye observation system in the second mode. Move the relay lens to the second lens position on axis.

According to such a configuration, even when the working distance is changed according to the examination, it is possible to form an image of the signal from the anterior segment on the imaging surface of the imaging element, thereby achieving the first examination and the second examination. It becomes possible to observe an anterior segment image that is in focus in both.

An ophthalmologic apparatus according to some embodiments includes a fixation projection system (4) that projects a fixation target onto an eye to be examined, and a controller projects the first fixation target onto the eye to be examined in the first mode. , in the second mode, the fixation projection system is controlled so as to project the second fixation target, which has a narrower visual angle than the first fixation target, onto the subject's eye.

According to such a configuration, the fixation target having a different visual angle depending on the examination is presented to the eye to be examined. In the second examination, for example, a fixation target can be presented such that a desired portion of the subject's eye is placed at a predetermined examination position.

Some embodiments include an objective lens (51) and a first inspection optical system (Ref measurement projection system 6, Reflect measurement light receiving system 7), a second inspection optical system (OCT optical system 8, SLO optical system) for performing a second inspection different from the first inspection on the eye to be inspected via the objective lens, and irradiating the eye to be inspected with alignment light. Then, the alignment optical system (Z alignment system 1) for detecting the reflected light of the alignment light from the eye to be inspected, and the objective lens, the first inspection optical system, and the second inspection optical system are moved in the optical axis direction of the objective lens. A control method for an ophthalmologic apparatus including a moving mechanism (200) and a control unit (210, main control unit 211) that controls the moving mechanism. A method for controlling an ophthalmologic apparatus, in a first mode for performing a first examination, deflects light reflected from an eye to be inspected irradiated with alignment light or light reflected by an eye to be inspected irradiated with alignment light. a first alignment light detection step for detecting the reflected light obtained by the above, and based on the detection result of the reflected light in the first alignment light detection step, the working distance to the eye to be examined is moved to the first working distance. a first control step of controlling the mechanism; and a second alignment light detection step of detecting the reflected light by irradiating the eye to be inspected with the alignment light and deflecting the reflected light in the second mode of performing the second inspection; and a second control step of controlling the moving mechanism so that the working distance with respect to the subject's eye becomes the second working distance, based on the detection result of the reflected light in the second alignment light detecting step.

According to such control, while sharing the objective lens between the first inspection optical system and the second inspection optical system, the working distance is changed according to the inspection based on the optimal arrangement position for the second inspection. Therefore, with a simple configuration, a plurality of inspections can be performed at their respective optimum working distances.

In a method for controlling an ophthalmologic apparatus according to some embodiments, in the first control step, the first deflection member is inserted into and removed from the optical path of the alignment light, and the second deflection member is inserted into and removed from the optical path of the reflected light. Let

According to such control, it becomes possible to perform a plurality of inspections with a simple configuration and control, each at an optimum working distance.

Some embodiments include an objective lens (51) and a first inspection optical system (Ref measurement projection system 6, Reflect measurement light receiving system 7), a second inspection optical system (OCT optical system 8, SLO optical system) for performing a second inspection different from the first inspection on the eye to be inspected via the objective lens, and irradiating the eye to be inspected with alignment light. Then, the alignment optical system (Z alignment system 1) for detecting the reflected light of the alignment light from the eye to be inspected, and the objective lens, the first inspection optical system, and the second inspection optical system are moved in the optical axis direction of the objective lens. A control method for an ophthalmologic apparatus including a moving mechanism (200) and a control unit (210, main control unit 211) that controls the moving mechanism. A method for controlling an ophthalmologic apparatus includes, in a first mode for performing a first examination, a first alignment light detection step of irradiating an eye to be inspected with alignment light and deflecting the reflected light to detect the reflected light; In the first control step of controlling the moving mechanism so that the working distance with respect to the eye to be examined becomes the first working distance based on the detection result of the reflected light in the alignment light detection step, and in the second mode of performing the second inspection, the alignment a second alignment light detection step of detecting reflected light obtained by deflecting the reflected light from the eye to be inspected irradiated with the light or the reflected light obtained by deflecting the light reflected by the eye to be inspected irradiated with the alignment light; and a second control step of controlling the moving mechanism so that the working distance with respect to the subject's eye becomes the second working distance, based on the detection result of the reflected light in the second alignment light detecting step.

According to such control, while sharing the objective lens between the first inspection optical system and the second inspection optical system, the working distance is changed according to the inspection based on the optimal arrangement position for the first inspection. Therefore, with a simple configuration, a plurality of inspections can be performed at their respective optimum working distances.

In the method of controlling an ophthalmologic apparatus according to some embodiments, in the second control step, the first deflection member is inserted/removed with respect to the optical path of the alignment light, and the second deflection member is inserted/removed with respect to the optical path of the reflected light. Let

According to such control, it becomes possible to perform a plurality of inspections at their respective optimum working distances with a simple configuration and control.

In the method of controlling an ophthalmic apparatus according to some embodiments, the ophthalmic apparatus includes a relay lens (56) that relays light from the anterior segment of the eye to be examined, and an imaging device (59) that receives light that has passed through the relay lens. ), the first control step moving the relay lens to a first lens position on the optical axis of the anterior eye observation system, and the second control step moving the anterior eye The relay lens is moved to the second lens position on the optical axis of the partial observation system.

According to such a configuration, even when the working distance is changed according to the examination, it is possible to form an image of the signal from the anterior segment on the imaging surface of the imaging element, thereby achieving the first examination and the second examination. It becomes possible to observe an anterior segment image that is in focus in both.

In the method of controlling an ophthalmologic apparatus according to some embodiments, the ophthalmologic apparatus includes a fixation projection system (4) that projects a fixation target onto the eye to be examined, and in the first control step, the first fixation target is projected onto the subject's eye. In the second control step, the fixation projection system is controlled so that the second fixation target having a narrower visual angle than the first fixation target is projected onto the eye to be examined.

According to such a configuration, the fixation target having a different visual angle depending on the examination is presented to the eye to be examined. In the second examination, for example, a fixation target can be presented such that a desired portion of the subject's eye is placed at a predetermined examination position.

In the method of controlling an ophthalmologic apparatus according to some embodiments, the second inspection optical system has an optical scanner (88), and the optical scanner deflects light (measurement light LS) from the light source (OCT light source 101). , the light deflected by the optical scanner is projected onto the subject's eye via the objective lens, and the light (interference light LC) based on the return light from the subject's eye is detected.

According to such control, it is possible to perform a plurality of examinations including OCT measurement, SLO measurement, etc. at the optimum working distance for each with simple control.

In the method of controlling an ophthalmologic apparatus according to some embodiments, the first inspection optical system projects light onto an eye to be inspected via an objective lens and detects light returned from the eye to be inspected. It includes a measurement projection system 6 and a reflector measurement light receiving system 7).

According to such control, it is possible to perform a plurality of examinations including refractive power measurement at respective optimum working distances with simple control.

<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.

Also, in the above embodiment, the case where the ophthalmologic apparatus 1000 performs OCT on the fundus oculi Ef has been described, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. For example, the present invention can be applied to an ophthalmologic apparatus that performs OCT on the fundus oculi Ef and the anterior segment of the eye.

In the above embodiment, at least one of the first inspection optical system and the second inspection optical system includes a fundus camera for photographing the fundus, an eye refraction inspection device (refractometer, keratometer) for measuring the refractive characteristics of the eye to be inspected, Optical systems such as a tonometer, a specular microscope for obtaining corneal characteristics (corneal thickness, cell distribution, etc.), and a wavefront analyzer for obtaining aberration information of the subject's eye using a Hartmann-Shack sensor can be included.

1 Z alignment system 2 XY alignment system 3 Kerato measurement system 4 Fixation projection system 5 Anterior eye observation system 6 Reflector measurement projection system 7 Reflector measurement light receiving system 8 OCT optical system 9 Processing units 11, 11A, 11B Z alignment light source 12, 12A, 12B imaging lenses 13, 13A, 13B line sensors 14A, 14B deflecting members 15A, 15B reflecting mirror 51 objective lens 88 optical scanner 200 moving mechanism 210 control unit 211 main control unit 1000 ophthalmic apparatus

Claims (8)

an objective lens;
a first inspection optical system for performing a first inspection on an eye to be inspected via the objective lens;
a second inspection optical system for performing a second inspection different from the first inspection on the eye to be inspected via the objective lens;
an alignment light source for irradiating the eye to be inspected with alignment light from a direction forming a predetermined angle with respect to the optical axis of the objective lens; The alignment light is deflected according to the type of operation mode including the second mode to irradiate the eye at the first arrangement position or the second arrangement position on the optical axis of the objective lens, and the operation mode an alignment optical system for detecting reflected light from the eye to be inspected or light obtained by deflecting the reflected light with the detection element according to the type of
a movement mechanism for moving the objective lens, the first inspection optical system, and the second inspection optical system in the optical axis direction of the objective lens;
Based on the detection result of the reflected light obtained by the alignment optical system, the working distance with respect to the eye to be examined is the first working distance in the first mode, and the working distance is the second working distance in the second mode. a control unit that controls the movement mechanism so as to achieve the working distance;
including
In one of the first mode and the second mode, the alignment optical system irradiates the eye to be inspected with the alignment light without deflection and detects the reflected light with the detection element without deflection. An ophthalmic device that deflects the alignment light and/or the reflected light in the other of the first mode and the second mode . The second inspection optical system has an optical scanner, deflects light from a light source by the optical scanner, projects the light deflected by the optical scanner onto the eye to be inspected via the objective lens, and 2. The ophthalmologic apparatus according to claim 1, wherein light based on light returned from eye examination is detected. 3. The first inspection optical system includes a refractive power measurement optical system that projects light onto the eye to be inspected via the objective lens and detects light returned from the eye to be inspected. 3. The ophthalmic device according to 2. The alignment optical system is
a first deflection member that deflects the alignment light;
a second deflection member that deflects the reflected light from the eye to be inspected;
including
Alignment light deflected by the first deflecting member is applied to the eye to be inspected, and reflected light deflected by the second deflecting member is detected by the detecting element. An ophthalmic device according to any one of the preceding paragraphs. The alignment optical system is
a third deflection member that deflects the alignment light deflected by the first deflection member toward the eye to be examined;
a fourth deflecting member that deflects the reflected light from the eye to be inspected toward the second deflecting member;
5. The ophthalmic device of claim 4, comprising: The first deflection member is insertable and removable with respect to the optical path of the alignment light,
6. The ophthalmologic apparatus according to claim 4, wherein the second deflecting member is insertable into and removable from the optical path of the reflected light. an anterior segment observation system including a relay lens that relays light from the anterior segment of the eye to be inspected and an imaging device that receives light that has passed through the relay lens;
The controller moves the relay lens to a first lens position on the optical axis of the anterior eye observation system in the first mode, and moves the relay lens on the optical axis of the anterior eye observation system in the second mode. The ophthalmologic apparatus according to any one of claims 1 to 6, wherein the relay lens is moved to the second lens position of . including a fixation projection system that projects a fixation target onto the eye to be examined;
The control unit projects a first fixation target onto the eye to be inspected in the first mode, and projects a second fixation target having a narrower visual angle than the first fixation target onto the eye to be inspected in the second mode. The ophthalmologic apparatus according to any one of claims 1 to 7, wherein the fixation projection system is controlled to project.

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