JP7133995B2 - Ophthalmic device and its control method - Google Patents

Description

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

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

For example, Patent Literature 1 discloses an ophthalmologic apparatus capable of subjective examination 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 and measurements using such an ophthalmologic apparatus have different optimum working distances. Therefore, setting the working distance of an ophthalmic device to be optimal for one examination or measurement may narrow the range of other examinations or measurements or reduce the accuracy of the measurement. 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 or measurement 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.

The present invention has been made in view of such circumstances, and an object of the present invention is to provide an ophthalmologic apparatus capable of performing a plurality of examinations and measurements at optimal working distances with a simple configuration, and a control method thereof. to provide.

A first aspect of some embodiments has an objective lens, a refractive power measuring optical system that projects light onto an eye to be inspected via the objective lens and detects light returned from the eye to be inspected, and an optical scanner. an inspection optical system for deflecting light from a light source by the optical scanner, projecting the light deflected by the optical scanner onto the eye to be inspected via the objective lens, and detecting light returned from the eye to be inspected; a moving mechanism for moving the objective lens, the refractive power measuring optical system, and the inspection optical system in the optical axis direction of the objective lens; and a controller for controlling the moving mechanism so that the working distance for the optical system becomes the first working distance, and the working distance becomes the second working distance when performing an inspection using the inspection optical system. .

A second aspect of some embodiments is an anterior eye including a relay lens that relays light from the anterior segment of the subject's eye and an imaging device that receives light that has passed through the relay lens in the first aspect. The controller moves the relay lens to a first lens position on the optical axis of the anterior eye observation system when performing the refractive power measurement, and moves the relay lens to a first lens position on the optical axis of the anterior eye segment when performing the examination. The relay lens is moved to the second lens position on the optical axis of the observation system.

A third aspect of some embodiments is, in the first aspect or the second aspect, including a fixation projection system that projects a fixation target onto the eye to be inspected, and the control unit, when performing the refractive power measurement, The fixation projection system is controlled such that a first fixation target is projected onto the eye to be inspected, and a second fixation target having a narrower visual angle than the first fixation target is projected onto the eye during the inspection.

In a fourth aspect of some embodiments, in the third aspect, the second fixation target is a dot target or a cross target.

A fifth aspect of some embodiments is, in any one of the first to fourth aspects, with respect to the first arrangement position of the eye to be examined on the optical axis of the objective lens, the a first alignment system that irradiates alignment light from a direction forming one angle and receives return light from the eye to be inspected; a second alignment system that irradiates alignment light from a direction forming a second angle with respect to the axis and receives return light from the eye to be inspected; The movement mechanism is controlled based on the light reception result obtained by the first alignment system, and the movement mechanism is controlled based on the light reception result obtained by the second alignment system when performing the inspection.

A sixth aspect of some embodiments is, in any one of the first to fourth aspects, for each of the two or more arrangement positions of the eye to be examined on the optical axis of the objective lens, an alignment system that irradiates alignment light from a direction forming a changeable angle with respect to the subject's eye and receives return light from the eye to be inspected; When force measurement is performed, the moving mechanism is controlled based on the light receiving result obtained by the alignment system in a state in which the angle is changed to the first irradiation angle by the angle changing mechanism, and when the inspection is performed, the angle changing mechanism controls the first irradiation angle. The moving mechanism is controlled based on the light reception result obtained by the alignment system with the irradiation angle changed to two.

According to a seventh aspect of some embodiments, in any one of the first to sixth aspects, an arc-shaped or circumferential a corneal shape measurement optical system for projecting a measurement pattern having a shape to the eye to be inspected and detecting light returned from the cornea of the eye to be inspected via the objective lens, wherein the corneal shape measurement optical system includes a keratolight source, A kerato-plate disposed between the kerato-light source and the eye to be examined, and having a light-transmitting portion formed in an arc shape or a circumference around the optical axis of the objective lens and transmitting light from the kerato-light source. and, where h is the height of the image based on the measurement pattern with respect to the optical axis of the objective lens, R is the corneal curvature radius of the eye to be examined, and the length from the optical axis of the objective lens to the translucent part When the height is H, the control unit determines that the first working distance is ((H−h)/tan(2×sin ⁻¹ (h/R))−(R−√(R ² −h ² ) )) to control the moving mechanism.

In an eighth aspect of some embodiments, in the seventh aspect, the height of the image based on the measurement pattern is 1.5 millimeters.

In the ninth aspect of some embodiments, in the seventh aspect or the eighth aspect, the distance from the pupil to the fundus of the eye to be examined is Le, the distance from the anterior surface of the cornea to the pupil is La, and the anterior surface of the keratoplate is to the main surface of the objective lens is Lk, the scanning range by the optical scanner is SA square, and the scanning diameter of the objective lens for scanning the scanning range is D, the control unit, The moving mechanism is controlled so that the second working distance is ((Le×D)/SA−(La+Lk)).

In a tenth aspect of some embodiments, in the ninth aspect, the scan range is a (6×√2) millimeter square range on the fundus of the subject's eye.

In an eleventh aspect of some embodiments, in any one of the first to tenth aspects, the inspection optical system splits the light from the OCT light source into reference light and measurement light, and divides the measurement light into the It includes an OCT optical system that is deflected by an optical scanner, projects the deflected measurement light onto the eye to be inspected, and detects interference light between the return light of the measurement light from the eye to be inspected and the reference light.

According to a twelfth aspect of some embodiments, in any one of the first to eleventh aspects, the inspection optical system deflects light from an SLO light source by the optical scanner, and directs the deflected light to the object. It includes an SLO optical system that projects an eye to be examined and receives return light from the eye to be examined.

A thirteenth aspect of some embodiments has an objective lens, a refractive power measurement optical system that projects light onto an eye to be inspected via the objective lens and detects light returned from the eye to be inspected, and an optical scanner. an inspection optical system for deflecting light from a light source by the optical scanner, projecting the light deflected by the optical scanner onto the eye to be inspected via the objective lens, and detecting light returned from the eye to be inspected; a control method for an ophthalmologic apparatus, comprising: a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens; and a control section for controlling the movement mechanism. a first control step in which the control unit controls the moving mechanism so that the working distance with respect to the eye to be examined becomes the first working distance; and in the first control step, the working distance is set to the first working distance. a first measuring step of performing refractive power measurement using the refractive power measuring optical system in the above state; and a second measuring step of performing an inspection using the inspection optical system in a state in which the working distance is set to the second working distance in the second control step.

In a fourteenth aspect of some embodiments, in the thirteenth aspect, the ophthalmologic apparatus includes a relay lens that relays light from the anterior segment of the eye to be examined, and an imaging device that receives light that has passed through the relay lens. wherein the first control step further moves the relay lens to a first lens position on the optical axis of the anterior eye observation system, and the second control step includes: Furthermore, the relay lens is moved to the second lens position on the optical axis of the anterior segment observation system.

In a fifteenth aspect of some embodiments, in the thirteenth aspect or the fourteenth aspect, the ophthalmologic apparatus includes a fixation projection system that projects a fixation target onto the eye, and the first control step further comprises and controlling the fixation projection system to project a first fixation target onto the eye, and in the second control step, further, projecting a second fixation target having a narrower visual angle than the first fixation target. The fixation projection system is controlled so as to project onto the subject's eye.

According to a sixteenth aspect of some embodiments, in any one of the thirteenth to fifteenth aspects, the ophthalmologic apparatus is configured such that the light a first alignment system that irradiates alignment light from a direction forming a first angle with respect to an axis and receives return light from the eye to be inspected; a second alignment system that irradiates alignment light from a direction forming a second angle with respect to the optical axis and receives return light from the eye to be inspected; The movement mechanism is controlled based on the light reception result obtained by the first alignment system, and in the second control step, the movement mechanism is controlled based on the light reception result obtained by the second alignment system.

Advantageous Effects of Invention According to the present invention, it is possible to provide an ophthalmologic apparatus capable of performing a plurality of examinations and measurements at optimum working distances with a simple configuration, and a control method thereof.

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. FIG. 10 is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to a modified example 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. FIG. 10 is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to a modified example 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. FIG. 10 is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to a modified example 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.

An ophthalmologic apparatus according to the present invention and an example of an embodiment of a control method thereof 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.

The ophthalmologic apparatus according to the embodiment can perform multiple examinations and measurements while sharing the objective lens. In an ophthalmologic apparatus capable of performing a plurality of examinations and measurements, 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 and measurements.

The ophthalmologic apparatus according to the embodiment can perform refractive power measurement (reflection measurement) and scan measurement. 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. The subjective examination includes subjective refraction measurement such as distance examination, near examination, contrast examination, glare examination, and visual field examination.

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

<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 subject's eye E passes through the objective lens 51, passes through the dichroic mirror 52, passes through a hole formed in the diaphragm (telecentric diaphragm) 53, and passes through the half mirror 23. , the relay lenses 55 and 56 and the dichroic mirror 76 . The dichroic mirror 52 synthesizes (separates) the optical path of the reflex measurement optical system and the optical path of the anterior eye observation system 5 . The dichroic mirror 52 is arranged such that the optical path synthesizing surface for synthesizing these optical paths is inclined with respect to the optical axis of the objective lens 51 . 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 includes a Z alignment system 1A and a Z alignment system 1B. Either of the Z alignment systems 1A and 1B is used for alignment of the objective lens 51 in the optical axis direction. The Z alignment system 1A is used for alignment of the objective lens 51 (optical system such as the anterior ocular observation system 5) in the optical axis direction (front-rear direction, Z direction, working distance direction) before the reflex measurement. The Z alignment system 1B is used for alignment of the objective lens 51 in the optical axis direction before OCT measurement.

The Z alignment system 1A irradiates the eye E to be examined at the first arrangement position on the optical axis of the objective lens 51 with alignment light from a direction forming a first angle with respect to the optical axis, and specularly reflected by the eye E to be examined. It is configured to receive light (returned light). The Z alignment system 1B irradiates the subject's eye E at a second position on the optical axis of the objective lens 51, which is farther from the ophthalmologic apparatus 1000 than the first position, with alignment light from a direction forming a second angle. It is configured to receive light specularly reflected in the eye E to be examined. In this embodiment, the first angle is approximately equal to the second angle.

The Z alignment system 1A projects light (infrared light) onto the subject's eye E for alignment of the objective lens 51 in the optical axis direction. The light output from the Z alignment light source 11A is projected onto the cornea Cr of the subject's eye E at the first arrangement position, reflected by the cornea Cr, and 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.

The Z alignment system 1B has the same configuration as the Z alignment system 1A. That is, the light output from the Z alignment light source 11B is projected onto the cornea Cr of the subject's eye E at the second arrangement position, 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.

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

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

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

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

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

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

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

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

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

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

(OCT optical system 8)
The OCT optical system 8 is an optical system for performing OCT measurement. The position of the focusing lens 87 is adjusted so that the end surface of the optical fiber f1 is conjugated to the 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-swept (wavelength scanning) light source capable of sweeping (scanning) the wavelength of emitted light, similar to a general swept-source type OCT apparatus. Consists of A swept-wavelength light source includes a laser light source including a resonator. The OCT light source 101 temporally changes the output wavelength in the near-infrared wavelength band invisible to the human eye.

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

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

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

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

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber f1, 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 light 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. The OCT light source 101, for example, optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then outputs the clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic processing section 220 of the processing section 9 . For example, for each series of wavelength scans (for each A line), the arithmetic processing unit 220 forms a reflection intensity profile for each A line by applying Fourier transform or the like to the spectral distribution based on the sampling data. Furthermore, the arithmetic processing unit 220 forms image data by imaging the reflection intensity profile of each A line.

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

The processing unit 9 calculates a refractive power value from the measurement result obtained using the reflector measurement optical system, and based on the calculated refractive power value, the fundus oculi Ef, the reflector measurement light source 61, and the image sensor 59 are conjugated. The ref measurement light source 61 and the focusing lens 74 are moved in the optical axis direction to the respective positions. In some embodiments, the processing 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 acquired. 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 optical 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 approximately 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, the distance Lk is data known to the ophthalmic device 1 . 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.プロセッサの機能は、例えば、ＣＰＵ（Ｃｅｎｔｒａｌ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＧＰＵ（Ｇｒａｐｈｉｃｓ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＡＳＩＣ（Ａｐｐｌｉｃａｔｉｏｎ Ｓｐｅｃｉｆｉｃ Ｉｎｔｅｇｒａｔｅｄ Ｃｉｒｃｕｉｔ）、プログラマブル論理デバイス（例えば、ＳＰＬＤ（Ｓｉｍｐｌｅ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ）、ＣＰＬＤ（Ｃｏｍｐｌｅｘ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ） , FPGA (Field Programmable Gate Array)). The processing unit 9 implements the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or storage device.

Processing unit 9 includes control unit 210 and arithmetic processing unit 220 . 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 (Z alignment systems 1A and 1B), an XY alignment system 2, a keratometry system 3, a fixation projection system 4, an anterior segment observation system 5, a reflector measurement projection system 6, and a reflector measurement light receiving system. This is a mechanism for moving a head portion in which optical systems such as the optical system 7 and the OCT optical system 8 are housed in the front-rear and left-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 1A includes control of the Z alignment light source 11A, control of the line sensor 13A, and the like. Control of the Z alignment system 1B includes control of the Z alignment light source 11B, control of the line sensor 13B, and the like. The control of the Z alignment light sources 11A and 11B includes turning on/off the light sources, adjusting the amount of light, and adjusting the aperture. Control of the line sensors 13A and 13B includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection elements. As a result, the Z alignment light sources 11A and 11B are 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 13A and specifies the projection position of the light with respect to the line sensor 13A based on the captured signal. The main control unit 211 captures the signal detected by the line sensor 13B, and specifies the projection position of the light with respect to the line sensor 13B based on the captured signal. The main control unit 211 obtains the position of the corneal vertex of the subject's eye E using the projection position specified by the Z alignment system 1A when performing the reflex measurement, and based on this, controls the moving mechanism 200 to move the head unit forward and backward. (Z alignment). The main control unit 211 obtains the position of the corneal vertex of the subject's eye E using the projection position specified by the Z alignment system 1B when performing OCT measurement, and based on this, controls the movement mechanism 200 to move the head unit in the front-rear direction. move to

Control of the XY alignment system 2 includes control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the XY alignment light source 21 are switched, or the amount of light is changed. The main control unit 211 captures the signal detected by the imaging element 59 and identifies the position of the bright spot image based on the return light from the XY alignment light source 21 based on the captured signal. The main control unit 211 controls the moving mechanism 200 so as to cancel the displacement of the position of the bright point image Br with respect to a predetermined target position (for example, the center position of the alignment mark AL), and moves the head unit in left, right, up and down directions. Move (XY alignment).

Control of the keratometry system 3 includes control of the keratometry light source 32 and the like. The control of the keratling light source 32 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the keratling light source 32 are switched, or the amount of light is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform a known arithmetic operation on the keratling image detected by the imaging device 59 . Thereby, the corneal shape parameter of the eye E to be examined is obtained.

The control of the fixation projection system 4 includes control of the liquid crystal panel 41, movement control of the fixation unit 40, and the like. The control of the liquid crystal panel 41 includes turning on/off the display of the fixation target, switching the fixation target according to the type of examination or measurement, and switching the display position of the fixation target.

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 displays the fixation target FT1 shown in FIG. 6A on the liquid crystal panel 41 when performing the reflex measurement, and displays the fixation target FT2 or FT3 shown in FIG. 6A on the liquid crystal panel when performing the 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 inspection mode (measurement mode). In addition, the main control unit 211 can switch between the fixation target FT1 and the fixation target FT3 according to the examination mode.

Inspection 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.

In this way, by changing the fixation target displayed on the liquid crystal panel 41 according to the examination mode, 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 according to 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 in accordance with the inspection mode (measurement 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 inspection mode (measurement 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 inspection 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 inspection mode. As a result, even when the working distance is changed according to the examination mode, it is possible to form an image of the signal from the anterior segment on the imaging surface of the imaging device 59, and the focus is 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. As a result, lighting and non-lighting of the ref measurement light source 61 are switched, or the amount of light is changed. For example, the reflector measurement projection system 6 includes a moving mechanism that moves the reflector measurement light source 61 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the movement mechanism by sending a control signal to the actuator to move the ref measurement light source 61 in the optical axis direction. The control of the rotary prism 66 includes rotation control of the rotary prism 66 and the like. For example, a rotating mechanism for rotating the rotary prism 66 is provided, and the main controller 211 rotates the rotary prism 66 by controlling this rotating mechanism.

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

Control of the OCT optical system 8 includes control of the OCT light source 101, 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 only the focusing lens 87 based on the intensity of the interference signal after moving the focusing lens 87 in conjunction with the movement of the focusing lens 74 .

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

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

(storage unit 212)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, objective measurement results, 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)
The arithmetic processing unit 220 includes an eye refractive power calculation unit 221 , an image forming unit 222 and a data processing unit 223 .

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

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

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

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

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

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

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

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

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

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

The ref measurement projection system 6 and the ref measurement light receiving system 7 are examples of the "refractive power measurement optical system" according to the embodiment. The OCT optical system 8 is an example of the "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 1A is an example of the "first alignment system" according to the embodiment. Z alignment system 1B is an example of a "second alignment system" according to the embodiment. The keratometry system 3 is an example of a "corneal shape measurement optical system" according to the embodiment. The keratizing light source 32 is an example of a "kerat light source" 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, Z alignment is performed using the Z alignment system 1A.

Specifically, the main controller 211 turns on the Z alignment light source 11A and the XY alignment light source 21 . Further, the main controller 211 turns on the anterior segment illumination light source 50 . The processing unit 9 acquires the imaging signal of the anterior segment image on the imaging surface of the imaging element 59 and causes the display unit 270 to display the anterior segment image. After that, the optical system shown in FIG. 1 is moved to the examination position of the eye E to be examined. The inspection position is a position at which the eye to be inspected E can be inspected with sufficient accuracy. The subject's eye E is placed at the inspection position through the above-described alignment (alignment by the Z alignment system 1A and the XY alignment system 2 and the anterior segment observation system 5). Movement of the optical system is executed by the control unit 210 according to an operation or instruction by the user or an instruction by the control unit 210 . That is, the movement of the optical system to the inspection position of the subject's eye E and the preparation for objective measurement are performed. 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 . 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 S4. 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 examination 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 inspection 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, Z alignment is performed using the Z alignment system 1B.

Specifically, the main controller 211 turns on the Z alignment light source 11B and the XY alignment light source 21 . Further, the main controller 211 turns on the anterior segment illumination light source 50 . The processing unit 9 acquires the imaging signal of the anterior segment image on the imaging surface of the imaging element 59 and causes the display unit 270 to display the anterior segment image. After that, the optical system shown in FIG. 1 is moved to the examination position of the eye E to be examined. The inspection position is a position at which the eye to be inspected E can be inspected with sufficient accuracy. The subject's eye E is placed at the inspection position through the aforementioned alignment (alignment by the Z alignment system 1B, the XY alignment system 2, and the anterior segment observation system 5). Movement of the optical system is executed by the control unit 210 according to an operation or instruction by the user or an instruction by the control unit 210 . That is, the movement of the optical system to the inspection position of the subject's eye E and the preparation for objective measurement are performed. 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 performs alignment using the Z alignment system 1A, 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 Z alignment using the Z alignment system 1B, 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 while preventing the size of the kerato plate 31 from increasing in size. 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.

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 eye E to be inspected, 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 examination mode, visual acuity adjustment for the eye to be examined can be achieved in the ref 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 subject's eye E, and representing landscape charts such as fixation targets FT1 and FT4. 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 arranged 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 controller 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, a transmissive optotype chart 46c representing a landscape chart and a transmissive optotype chart 48c representing a dot optotype or a cross optotype are provided, and illumination is performed according to the inspection 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 the 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 1A for refractometer measurement and the Z alignment system 1B for OCT measurement are provided, but the configuration of the ophthalmologic apparatus according to the embodiment is limited to this. is not.

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, 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 ophthalmologic apparatus 1000a according to the sixth modification differs from the configuration of the ophthalmologic apparatus 1000 according to the embodiment in that a Z alignment system 1a is provided instead of the Z alignment systems 1A and 1B. The Z alignment system 1a irradiates alignment light onto each of two or more arrangement positions of the eye to be inspected E on the optical axis of the objective lens 51 from a direction forming a changeable angle with respect to the optical axis. The return light from the eye examination E is received. An angle changing mechanism (not shown) changes at least one of the irradiation angle of the alignment light with respect to the optical axis of the objective lens 51 and the reflection direction of the return light from the eye E to be examined. In some embodiments, the angle changing mechanism can be controlled by the main controller 211a (controller 210a) to change the irradiation angle and reflection direction (FIG. 13). In some embodiments, the angle changing mechanism changes the irradiation angle around a predetermined position on the optical axis of the alignment light irradiated to the first arrangement position (or the second arrangement position), The reflection direction is changed around a predetermined position on the optical axis of the returned light.

FIG. 14 shows a configuration example of a processing system of an ophthalmologic apparatus according to a sixth modification of the embodiment. In FIG. 14, the same parts as those in FIG. 5 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the processing system shown in FIG. 14 differs from the configuration of the processing system shown in FIG. 5 in that a Z alignment system 1a is provided instead of the Z alignment systems 1A and 1B, The point is that the portion 9a is provided. The Z alignment system 1 a includes an alignment light source 11 , an imaging lens 12 and a line sensor 13 . The Z alignment system 1a operates similarly to the Z alignment system 1A or Z alignment system 1B.

The processing unit 9a differs from the processing unit 9 in that a control unit 210a is provided instead of the control unit 210. FIG. Control unit 210a includes a main control unit 211a and a storage unit 212a. The storage unit 212a differs from the storage unit 212 in that programs and control information for controlling the angle changing mechanism 14, which will be described later, are stored. The main control unit 211a can control each unit of the ophthalmologic apparatus 1000a based on the information stored in the storage unit 212a, as in the embodiment.

The angle changing mechanism 14 changes the angle between the optical axis of the objective lens 51 and the illumination optical axis of the alignment light connecting the position of the eye to be inspected on the optical axis of the objective lens 51 and the alignment light source 11 . Also, the angle changing mechanism 14 changes the angle formed by the optical axis of the objective lens 51 and the reflected optical axis of the alignment light that connects the position of the objective lens 51 on the optical axis and the line sensor 13 .

The main control unit 211a controls the moving mechanism 200 based on the light reception result obtained by the Z alignment system 1a in a state where the angle changing mechanism 14 changes the irradiation angle to the first irradiation angle when performing the reflex measurement. Thereby, alignment in the Z direction can be performed with respect to the subject's eye E at the first arrangement position on the optical axis of the objective lens 51 .

Further, the main control unit 211a controls the moving mechanism 200 based on the light reception result obtained by the Z alignment system 1a with the angle changing mechanism 14 changing the irradiation angle to the second irradiation angle when performing OCT measurement. Thereby, alignment in the Z direction can be performed for the subject's eye E at the second arrangement position different from the first arrangement position on the optical axis of the objective lens 51 .

Since the operation of the ophthalmologic apparatus 1000a according to the sixth modification is the same as the operation of the ophthalmologic apparatus 1000 according to the embodiment, detailed description thereof will be omitted.

According to the sixth modified example, the configuration of the Z alignment system can be simplified compared to the embodiment.

[Seventh modification]
FIG. 15 shows a configuration example of an optical system of an ophthalmologic apparatus according to a seventh modification of the embodiment. In FIG. 15, the same parts as those in FIG.

The configuration of the ophthalmologic apparatus 1000b according to the seventh modification differs from the configuration of the ophthalmologic apparatus 1000 according to the embodiment in that anterior eye cameras 15A and 15B are provided instead of the Z alignment systems 1A and 1B. be. The anterior segment cameras 15A and 15B photograph the anterior segment of the eye E to be examined. The anterior eye cameras 15A and 15B are, for example, video cameras that shoot moving images at a predetermined frame rate. Anterior segment cameras 15A and 15B image the anterior segment from different directions substantially simultaneously.

Although the number of anterior segment cameras may be any number of two or more, it is sufficient that the anterior segment cameras can be photographed substantially simultaneously from two different directions. Also, one anterior eye camera may be the imaging device 59 in the anterior eye observation system 5 .

“Substantially simultaneously” means that, in photographing with two or more anterior eye cameras, a deviation in photographing timing to the extent that eye movement can be ignored is allowed. As a result, images of the subject's eye E at the same position (orientation) can be acquired by two or more anterior eye cameras.

FIG. 16 shows a configuration example of a processing system of an ophthalmologic apparatus according to a seventh modification of the embodiment. In FIG. 16, the same parts as those in FIG. 5 are denoted by the same reference numerals, and the description thereof is omitted as appropriate.

The configuration of the processing system shown in FIG. 16 differs from the configuration of the processing system shown in FIG. The difference is that the processing unit 9b is provided instead, and that the calculation processing unit 220b is provided instead of the calculation processing unit 220. FIG.

The processing unit 9b differs from the processing unit 9 in that a control unit 210b is provided instead of the control unit 210. FIG. The control unit 210a includes a main control unit 211b and a storage unit 212b. The storage unit 212b differs from the storage unit 212 in that programs and control information for executing Z alignment using the anterior eye cameras 15A and 15B are stored. The main control unit 211b can control each unit of the ophthalmologic apparatus 1000b based on the information stored in the storage unit 212b, as in the embodiment.

The arithmetic processing unit 220 b is provided with a data processing unit 223 b instead of the data processing unit 223 of the arithmetic processing unit 220 . As disclosed in JP-A-2013-248376, the data processing unit 223b analyzes each of the two captured images substantially simultaneously obtained by the anterior eye cameras 15A and 15B to A feature position corresponding to a feature part of the part is specified. The characteristic site of the anterior segment is, for example, the center of the pupil. Further, the data processing unit 223b identifies the position of the subject's eye E based on the identified characteristic positions. In this example, the position of the center of the pupil approximates the position of the eye E to be examined. By using the distance between the corneal vertex and the pupil in the subject's eye E, or the distance between the corneal vertex and the pupil in a standard eye (model eye, average value, etc.), the position of the corneal vertex can be obtained as the position of the eye E to be examined.

The main control unit 211b performs Z alignment based on the position of the characteristic region of the anterior segment identified by the data processing unit 223b.

Since the operation of the ophthalmologic apparatus 1000b according to the seventh modification is the same as the operation of the ophthalmologic apparatus 1000 according to the embodiment, detailed description thereof will be omitted.

According to the seventh modification, the configuration of the Z alignment system can be omitted, so the configuration of the ophthalmologic apparatus can be simplified.

[Eighth modification]
In the sixth modification, a case has been described in which the irradiation angle of alignment light and the reflection direction of return light are changed by the angle changing mechanism, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this.

FIG. 17 shows a configuration example of an optical system of an ophthalmologic apparatus according to an eighth modification of the embodiment. In FIG. 17, the same parts as those in FIG. 13 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the ophthalmic apparatus 1000d according to the eighth modified example differs from the configuration of the ophthalmic apparatus 1000a according to the sixth modified example in that a Z alignment system 1c is provided instead of the Z alignment system 1a, and that the Z alignment system 1c is provided instead of the Z alignment system 1a. 1 c is configured to be movable in the optical axis direction of the objective lens 51 . The configuration of the Z alignment system 1c includes an alignment light source 11, an imaging lens 12, and a line sensor 13, similar to the Z alignment system 1a. The Z alignment system 1c is configured to move integrally in the optical axis direction of the objective lens 51 while maintaining the optical positional relationship between the alignment light source 11, imaging lens 12, and line sensor 13. FIG.

FIG. 18 shows a configuration example of a processing system of an ophthalmologic apparatus according to an eighth modification of the embodiment. 18, the same parts as in FIG. 14 are denoted by the same reference numerals, and the description thereof is omitted as appropriate.

The configuration of the processing system shown in FIG. 18 differs from the configuration of the processing system shown in FIG. 14 in that a moving mechanism 14c is provided instead of the angle changing mechanism 14, and that the processing unit 9c is provided instead of the processing unit 9a. It is a point that is provided. The Z alignment system 1c operates similarly to the Z alignment system 1a.

The processing unit 9c differs from the processing unit 9a in that a control unit 210c is provided instead of the control unit 210a. The control unit 210c includes a main control unit 211c and a storage unit 212c. The storage unit 212c differs from the storage unit 212a in that programs and control information for controlling the moving mechanism 14c, which will be described later, are stored. The main control unit 211c can control each unit of the ophthalmologic apparatus 1000c based on the information stored in the storage unit 212c, as in the sixth modification.

The moving mechanism 14 c moves the Z alignment system 1 c in the optical axis direction of the objective lens 51 . As described above, the moving mechanism 14c moves the Z alignment system 1c while maintaining the optical positional relationship among the alignment light source 11, imaging lens 12, and line sensor 13. FIG.

The main control unit 211c moves the Z alignment system 1c to a first position where the alignment light is irradiated to the first arrangement position on the optical axis of the objective lens 51 when performing the REF measurement, and moves the objective lens 51 when performing the OCT measurement. The Z alignment system 1c is moved to a second position where alignment light is applied to a second arrangement position on the optical axis of .

For example, the storage unit 212c stores control information in which movement information of the Z alignment system 1c is associated in advance with the operation mode. The control information includes movement information for moving the objective lens 51 to the first position on the optical axis when the Ref measurement is designated as the operation mode, and movement information for moving the objective lens 51 to the first position on the optical axis when the OCT measurement is designated as the operation mode. and movement information for moving to a second position on the optical axis. The main control section 211c can control the Z alignment system 1c as described above based on the control information stored in the storage section 212c.

The main controller 211c controls the movement mechanism 200 based on the light reception result obtained by the Z alignment system 1c moved to the first position by the movement mechanism 14c when performing the ref measurement. Thereby, alignment in the Z direction can be performed with respect to the subject's eye E at the first arrangement position on the optical axis of the objective lens 51 .

Further, the main control unit 211a controls the moving mechanism 200 based on the light reception result obtained by the Z alignment system 1c moved to the second position by the moving mechanism 14c when performing OCT measurement. Thereby, alignment in the Z direction can be performed for the subject's eye E at the second arrangement position different from the first arrangement position on the optical axis of the objective lens 51 .

Since the operation of the ophthalmologic apparatus 1000c according to the eighth modification is the same as the operation of the ophthalmologic apparatus 1000a according to the sixth modification, detailed description thereof will be omitted.

According to the eighth modified example, the configuration of the Z alignment system can be simplified as in the sixth modified example.

[Ninth Modification]
In the above-described embodiment or its modification, the case where the alignment light source or line sensor is moved or the irradiation angle of the alignment light is changed is described, but the configuration of the ophthalmologic apparatus according to the embodiment is limited to this. not something.

FIG. 19 shows a configuration example of an optical system of an ophthalmologic apparatus according to a ninth modification of the embodiment. In FIG. 19, 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 ophthalmologic apparatus 1000d according to the ninth modification differs from the configuration of the ophthalmologic apparatus 1000 according to the embodiment in that a Z alignment system 1d is provided instead of the Z alignment systems 1A and 1B. The Z alignment system 1d includes an alignment light source 11d, an imaging lens 12, and a line sensor 13. The alignment light source 11d is a light source with a wide light distribution angle. The alignment light source 11 d 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 main control unit 211 causes the alignment light source 11d to irradiate the eye to be inspected E placed at the first arrangement position with alignment light when performing the reflex measurement, and based on the result of light reception of the return light from the eye to be inspected E, the movement mechanism 200 control. Thereby, alignment in the Z direction can be performed with respect to the subject's eye E at the first arrangement position on the optical axis of the objective lens 51 .

In addition, when performing OCT measurement, the main control unit 211a causes the alignment light source 11d to irradiate alignment light to the subject's eye E placed at the second placement position, and based on the result of receiving the return light from the subject's eye E, It controls the moving mechanism 200 . Thereby, alignment in the Z direction can be performed for the subject's eye E at the second arrangement position different from the first arrangement position on the optical axis of the objective lens 51 .

Since the operation of the ophthalmologic apparatus 1000d according to the ninth modification is the same as the operation of the ophthalmologic apparatus 1000 according to the embodiment, detailed description thereof will be omitted.

As described above, according to the ninth modification, even when the REF measurement or the OCT measurement is performed, the eye to be examined E is irradiated with the alignment light, and the returned light is passed through the imaging lens 12. The light can be received by the line sensor 13 via the line sensor 13 . Thereby, the configuration of the ophthalmologic apparatus can be simplified from the embodiment.

[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, 1000a to 1000d) according to some embodiments includes an objective lens (51), a refractive power measurement optical system (Ref measurement projection system 6, Reflection measurement light receiving system 7), and an inspection optical system (OCT optical system 8, SLO optical system), a moving mechanism (200), and controllers (210, 210a-210c, main controller 211, main controllers 211a-211c). The refractive power measurement optical system projects light onto the subject's eye (E) via an objective lens, and detects light returned from the subject's eye. The inspection optical system has an optical scanner (88), deflects the light from the light source with the optical scanner, projects the light deflected by the optical scanner onto the eye to be inspected via the objective lens, and returns light from the eye to be inspected. to detect The moving mechanism moves the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens. The control unit sets the working distance to the subject's eye to be the first working distance (WDref) when performing refractive power measurement (reflection measurement) using the refractive power measurement optical system, and sets the working distance to the first working distance (WDref) when performing inspection using the inspection optical system. is the second working distance (WDoct).

According to such a configuration, at least the refractive power measurement optical system and the inspection optical system share the objective lens, and the working distance is changed between the refractive power measurement and the inspection using the inspection optical system. With such a configuration, highly accurate refractive power measurement results and highly accurate inspection results using the inspection optical system can be obtained.

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 device (5) that receives light via the relay lens. Includes an observation system (5). The controller moves the relay lens to the first lens position on the optical axis of the anterior eye observation system when performing refractive power measurement, and moves the anterior ocular segment observation system when performing an inspection (inspection using the inspection optical system). Move the relay lens to the second lens position on the optical axis.

According to such a configuration, even when the working distance is changed according to the refractive power measurement or the inspection using the inspection optical system, it is possible to form an image of the signal from the anterior segment on the imaging surface of the imaging device. This makes it possible to observe an in-focus image of the anterior segment even during refractive power measurement or inspection using an inspection optical system.

An ophthalmologic apparatus according to some embodiments includes a fixation projection system (4) that projects a fixation target onto an eye to be examined. The control unit projects the first fixation target (FT1) onto the subject's eye when performing refractive power measurement, and projects the second fixation target (FT1) with a narrower visual angle than the first fixation target when performing an inspection (inspection using an inspection optical system). The fixation projection system is controlled so as to project the visual targets (FT2, FT3) onto the subject's eye.

According to such a configuration, since a fixation target with a different visual angle is presented to the subject's eye according to the refractive power measurement and the inspection using the inspection optical system, the visual acuity of the subject's eye is not adjusted in the refractive power measurement. is presented with a fixation target, and in an inspection using an inspection optical system, the fixation target can be presented so that a desired portion of the eye to be inspected is placed on a predetermined inspection device.

In ophthalmic devices according to some embodiments, the second fixation target is a dot target (FT2) or a cross target (FT3).

According to such a configuration, it is possible to reliably fix the subject's eye on the second fixation target with a simple configuration.

An ophthalmic apparatus according to some embodiments includes a first alignment system (Z alignment system 1A) and a second alignment system (Z alignment system 1B). The first alignment system irradiates a first arrangement position of the eye to be inspected on the optical axis of the objective lens with alignment light from a direction forming a first angle with respect to the optical axis, and emits return light from the eye to be inspected. receive light. The second alignment system irradiates alignment light from a direction forming a second angle with respect to the optical axis to a second arrangement position of the eye to be inspected on the optical axis of the objective lens, and receives return light from the eye to be inspected. do. The control unit controls the movement mechanism based on the light reception result obtained by the first alignment system when performing refractive power measurement, and controls the movement mechanism based on the light reception result obtained by the second alignment system when performing inspection (inspection using the inspection optical system). A movement mechanism is controlled based on the light reception result.

According to such a configuration example, since the alignment system corresponding to the refractive power measurement and the inspection using the inspection optical system is provided, alignment can be performed with high precision in each of the refractive power measurement and the inspection using the inspection optical system. It can be performed.

An ophthalmic apparatus according to some embodiments includes an alignment system (Z alignment system 1a) and an angle changing mechanism (14). The alignment system irradiates each of two or more arrangement positions of the eye to be inspected on the optical axis of the objective lens with alignment light from a direction forming a changeable angle with respect to the optical axis, and returns from the eye to be inspected. receive light. An angle changing mechanism changes the angle. The control unit controls the moving mechanism based on the light reception result obtained by the alignment system in a state where the angle changing mechanism changes the irradiation angle to the first irradiation angle when performing the refractive power measurement, and performs inspection (inspection using the inspection optical system ) is performed, the movement mechanism is controlled based on the light reception result obtained by the alignment system in the state that the angle change mechanism has changed the irradiation angle to the second irradiation angle.

According to such a configuration, since the angle changing mechanism is provided, by changing the irradiation angle according to the inspection using the refractive power measurement and inspection optical system, the refractive power measurement and inspection optical system can be performed with a simple configuration. Alignment can be performed with high accuracy in each inspection using the system.

An ophthalmic device according to some embodiments includes a corneal topography measurement system (keratometry system 3). The corneal topography measurement optical system projects an arc-shaped or circumferential measurement pattern on the cornea of the subject's eye from the outer edge side of the objective lens, centering on the optical axis of the objective lens. Detect light returned from the cornea. The corneal topography measurement optical system is arranged between a kerat light source (kerat ring light source 32) and the kerat light source and the eye to be examined, and is formed in an arc shape or a circle shape centering on the optical axis of the objective lens. and a keratoplate (31) formed with a translucent portion that transmits light. Let h be the height of the image based on the measurement pattern with respect to the optical axis of the objective lens, R be the corneal curvature radius of the eye to be examined, and H be the length from the optical axis of the objective lens to the translucent part. controls the movement mechanism so that the first working distance is ((H−h)/tan(2×sin ⁻¹ (h/R))−(R−√(R ² −h ² ))) .

According to such a configuration, it is possible to prevent an increase in the size of the keratoplate while increasing the working distance to reduce the influence of instrumental myopia. As a result, it is possible to provide an ophthalmologic apparatus capable of obtaining highly accurate refractive power measurement results and keratometry results with a simple configuration.

In some embodiments of the ophthalmic device, the image height based on the measurement pattern is 1.5 millimeters.

According to such a configuration, it is possible to measure the shape of the cornea for 3 millimeters, so that it is possible to measure the shape of the cornea useful for analyzing the shape of the cornea.

In the ophthalmic apparatus according to some embodiments, the distance from the pupil to the fundus of the eye to be examined is Le, the distance from the anterior surface of the cornea to the pupil is La, and the distance from the front surface of the keratoplate to the principal surface of the objective lens is Lk. When the scanning range by the optical scanner is SA square, and the scanning diameter of the objective lens for scanning the scanning range is D, the control unit determines that the second working distance is ((Le × D) / SA - (La + Lk )).

According to such a configuration, since it is possible to scan the SA four-sided area, it is compared with the existing standard data obtained by scanning the SA four-sided area, and the existing standard data is used to obtain the inspection result. be able to assist in making useful judgments against

In the ophthalmic apparatus according to some embodiments, the scan range is a (6×√2) millimeter square range on the fundus of the eye to be examined.

According to such a configuration, it is possible to utilize existing standard data generally acquired from the fundus of the eye to be inspected to assist in making useful judgments on the test results.

In the ophthalmic apparatus according to some embodiments, the inspection optical system splits light (L0) from the OCT light source (101) into reference light (LR) and measurement light (LS), and the measurement light is scanned by an optical scanner. It includes an OCT optical system (8) that deflects and projects the deflected measurement light onto the subject's eye, and detects interference light (LC) between the return light of the measurement light from the subject's eye and the reference light.

According to such a configuration, it is possible to provide an ophthalmologic apparatus capable of obtaining useful tomographic analysis results by scanning a desired scan range of the fundus.

In the ophthalmologic apparatus according to some embodiments, the inspection optical system includes an SLO optical system that deflects light from an SLO light source with an optical scanner, projects the deflected light onto an eye to be inspected, and receives return light from the eye to be inspected. including system.

According to such a configuration, it is possible to provide an ophthalmologic apparatus capable of obtaining a useful analysis result of a fundus image by scanning a desired scan range of the fundus.

Some embodiments include an objective lens (51) and a refractive power measurement optical system (Ref measurement projection system 6 , a reflector measurement light-receiving system 7), and an optical scanner (88). An inspection optical system (OCT optical system 8, SLO optical system) for detecting return light from a moving mechanism (200) for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens. and control units (210, 210a to 210c, main control unit 211, main control units 211a to 211c) that control the moving mechanism. A control method for an ophthalmologic apparatus includes a first control step in which a control unit controls a moving mechanism so that a working distance with respect to an eye to be examined becomes a first working distance (WDref); in a state set to , a first measurement step of performing refractive power measurement (reflection measurement) using a refractive power measurement optical system; a second control step of controlling the moving mechanism to a second control step, and a second measurement step of performing an inspection (OCT measurement) using an inspection optical system in a state in which the working distance is set to the second working distance in the second control step; ,including.

According to such control, in an ophthalmologic apparatus in which the objective lens is shared at least in the refractive power measurement optical system and the inspection optical system, the working distance is changed between the refractive power measurement and the inspection using the inspection optical system. It becomes possible to acquire an accurate refractive power measurement result and a highly accurate inspection result using the inspection optical system.

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. ), wherein the first control step further moves the relay lens to a first lens position on the optical axis of the anterior eye observation system, and the second control step includes: Furthermore, the relay lens is moved to the second lens position on the optical axis of the anterior segment observation system.

According to such control, even when the working distance is changed according to the diffraction measurement or the inspection using the inspection optical system, it is possible to form an image of the signal from the anterior segment on the imaging surface of the imaging device. This makes it possible to observe an in-focus image of the anterior segment even during refractive power measurement or inspection using an inspection optical system.

In the method of controlling an ophthalmic apparatus according to some embodiments, the ophthalmic apparatus includes a fixation projection system (4) that projects a fixation target onto the eye to be examined, and the first control step further includes: (FT1) is projected onto the subject's eye, and in the second control step, second fixation targets (FT2, FT3) having a narrower visual angle than the first fixation target are projected onto the subject's eye. Control the fixation projection system to project.

According to such control, in refractive power measurement, a fixation target is presented to the eye to be inspected so as not to adjust visual acuity, and in inspection using an inspection optical system, a desired portion of the eye to be inspected is arranged at a predetermined examination position. can be made to present a fixation target.

In the method of controlling an ophthalmic apparatus according to some embodiments, the ophthalmic apparatus aligns a first arrangement position of an eye to be examined on an optical axis of an objective lens from a direction forming a first angle with respect to the optical axis. A first alignment system (Z alignment system 1A) that irradiates light and receives return light from the eye to be inspected, and a second arrangement position of the eye to be inspected on the optical axis of the objective lens. and a second alignment system (Z alignment system 1B) that irradiates alignment light from directions forming two angles and receives return light from the eye to be inspected. The moving mechanism is controlled based on the light receiving result, and in the second control step, the moving mechanism is controlled based on the light receiving result obtained by the second alignment system.

According to such control, highly accurate alignment can be performed in each of the refractive power measurement and the inspection using the inspection optical system.

<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.

1, 1A, 1B, 1a-1d Z alignment system 2 XY alignment system 3 Keratometry system 4 Fixation projection system 5 Anterior segment observation system 6 Reflector measurement projection system 7 Reflector measurement light receiving system 8 OCT optical system 9, 9a, 9b Processing unit 14 Angle changing mechanism 31 Kerato plate 32 Keratoring light source 51 Objective lens 88 Optical scanner 14c, 200 Moving mechanism 210, 210a to 210c Control unit 211, 211a to 210c Main control unit 1000, 1000a to 1000d Ophthalmic device

Claims (14)

an objective lens;
a refractive power measurement optical system for projecting light onto an eye to be inspected via the objective lens and detecting light returned from the eye to be inspected;
An optical scanner is provided, light from a light source is deflected by the optical scanner, the light deflected by the optical scanner is projected onto the eye to be inspected via the objective lens, and light returned from the eye to be inspected is detected. an inspection optical system;
a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens;
When performing refractive power measurement using the refractive power measurement optical system, the working distance with respect to the eye to be inspected is the first working distance, and when performing inspection using the inspection optical system, the working distance is the second working distance. a control unit that controls the moving mechanism such that
an anterior segment observation system including a relay lens that relays light from the anterior segment of the subject's eye, and an imaging device that receives the light that has passed through the relay lens;
including
The control unit moves the relay lens to a first lens position on the optical axis of the anterior eye observation system when performing the refractive power measurement, and moves the relay lens to a first lens position on the optical axis of the anterior eye observation system when performing the inspection. moving said relay lens to a 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 when performing the refractive power measurement, and projects a second fixation target having a narrower visual angle than the first fixation target onto the eye to be inspected when performing the inspection. The ophthalmologic apparatus according to claim 1 , wherein the fixation projection system is controlled to project. The ophthalmologic apparatus according to claim 2, wherein the second fixation target is a dot target or a cross target. an objective lens;
a refractive power measurement optical system for projecting light onto an eye to be inspected via the objective lens and detecting light returned from the eye to be inspected;
An optical scanner is provided, light from a light source is deflected by the optical scanner, the light deflected by the optical scanner is projected onto the eye to be inspected via the objective lens, and light returned from the eye to be inspected is detected. an inspection optical system;
a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens;
When performing refractive power measurement using the refractive power measurement optical system, the working distance with respect to the eye to be inspected is the first working distance, and when performing inspection using the inspection optical system, the working distance is the second working distance. a control unit that controls the moving mechanism such that
A first arrangement position of the eye to be inspected on the optical axis of the objective lens is irradiated with alignment light from a direction forming a first angle with respect to the optical axis, and a return light from the eye to be inspected is received. 1 alignment system;
A second arrangement position of the eye to be inspected on the optical axis of the objective lens is irradiated with alignment light from a direction forming a second angle with respect to the optical axis, and light returned from the eye to be inspected is received. 2 alignment system;
including
The control unit controls the moving mechanism based on the light receiving result obtained by the first alignment system when performing the refractive power measurement, and controls the light receiving result obtained by the second alignment system when performing the inspection. an ophthalmic device that controls the moving mechanism based on an objective lens;
a refractive power measurement optical system for projecting light onto an eye to be inspected via the objective lens and detecting light returned from the eye to be inspected;
An optical scanner is provided, light from a light source is deflected by the optical scanner, the light deflected by the optical scanner is projected onto the eye to be inspected via the objective lens, and light returned from the eye to be inspected is detected. an inspection optical system;
a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens;
When performing refractive power measurement using the refractive power measurement optical system, the working distance with respect to the eye to be inspected is the first working distance, and when performing inspection using the inspection optical system, the working distance is the second working distance. a control unit that controls the moving mechanism such that
irradiating each of two or more arrangement positions of the eye to be inspected on the optical axis of the objective lens with alignment light from a direction forming a changeable angle with respect to the optical axis, and returning light from the eye to be inspected; an alignment system that receives the
an angle changing mechanism for changing the angle;
including
The control unit controls the moving mechanism based on the light reception result obtained by the alignment system in a state where the angle changing mechanism changes the irradiation angle to the first irradiation angle when performing the refractive power measurement, and performs the inspection. The ophthalmologic apparatus controls the moving mechanism based on the light reception result obtained by the alignment system in a state where the angle changing mechanism has changed the irradiation angle to the second irradiation angle. an objective lens;
a refractive power measurement optical system for projecting light onto an eye to be inspected via the objective lens and detecting light returned from the eye to be inspected;
An optical scanner is provided, light from a light source is deflected by the optical scanner, the light deflected by the optical scanner is projected onto the eye to be inspected via the objective lens, and light returned from the eye to be inspected is detected. an inspection optical system;
a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens;
When performing refractive power measurement using the refractive power measurement optical system, the working distance with respect to the eye to be inspected is the first working distance, and when performing inspection using the inspection optical system, the working distance is the second working distance. a control unit that controls the moving mechanism such that
An arc-shaped or circumferential measurement pattern is projected onto the cornea of the eye to be inspected from the outer edge side of the objective lens, centering on the optical axis of the objective lens, and the cornea of the eye to be inspected through the objective lens. a corneal shape measurement optical system for detecting light returned from the
including
The corneal shape measurement optical system comprises:
a kerat light source;
A kerato-plate disposed between the kerato-light source and the eye to be examined, and having a light-transmitting portion formed in an arc shape or a circumference around the optical axis of the objective lens and transmitting light from the kerato-light source. When,
including
Let h be the height of the image based on the measurement pattern with respect to the optical axis of the objective lens, let R be the corneal curvature radius of the eye to be examined, and let H be the length from the optical axis of the objective lens to the transparent portion. when
^The control unit ^controls the above ^- described An ophthalmic device that controls a movement mechanism. 7. The ophthalmic apparatus of claim 6, wherein the image height based on the measurement pattern is 1.5 millimeters. Let Le be the distance from the pupil to the fundus of the eye to be examined, La be the distance from the anterior surface of the cornea to the pupil, and Lk be the distance from the anterior surface of the keratoplate to the main surface of the objective lens. is SA square, and the scanning diameter of the objective lens for scanning the scanning range is D, the control unit determines that the second working distance is ((Le × D) / SA - (La + Lk)) The ophthalmologic apparatus according to claim 6 or 7 , wherein the movement mechanism is controlled such that 9. The ophthalmologic apparatus according to claim 8, wherein the scan range is a (6×√2) mm square range on the fundus of the subject's eye. The inspection optical system divides light from an OCT light source into reference light and measurement light, deflects the measurement light by the optical scanner, projects the deflected measurement light onto the eye to be inspected, and The ophthalmologic apparatus according to any one of claims 1 to 9, further comprising an OCT optical system for detecting interference light between the return light of the measurement light from and the reference light. The inspection optical system includes an SLO optical system that deflects light from an SLO light source by the optical scanner, projects the deflected light onto the eye to be inspected, and receives light returned from the eye to be inspected. The ophthalmologic apparatus according to any one of claims 1 to 10, wherein: an objective lens;
a refractive power measurement optical system for projecting light onto an eye to be inspected via the objective lens and detecting light returned from the eye to be inspected;
An optical scanner is provided, light from a light source is deflected by the optical scanner, the light deflected by the optical scanner is projected onto the eye to be inspected via the objective lens, and light returned from the eye to be inspected is detected. an inspection optical system;
a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens;
a control unit that controls the movement mechanism;
an anterior segment observation system including a relay lens that relays light from the anterior segment of the subject's eye, and an imaging device that receives the light that has passed through the relay lens;
A control method for an ophthalmic device comprising:
a first control step in which the control unit controls the moving mechanism so that a working distance with respect to the eye to be examined becomes a first working distance;
a first measuring step of performing refractive power measurement using the refractive power measurement optical system in a state in which the working distance is set to the first working distance in the first control step;
a second control step in which the control unit controls the moving mechanism so that the working distance with respect to the eye to be examined becomes a second working distance;
a second measuring step of performing an inspection using the inspection optical system in a state in which the working distance is set to the second working distance in the second control step;
including
In the first control step, the relay lens is further moved to a first lens position on the optical axis of the anterior segment observation system;
The method of controlling an ophthalmologic apparatus, wherein the second control step further moves the relay lens to a second lens position on the optical axis of the anterior segment observation system . The ophthalmologic apparatus includes a fixation projection system that projects a fixation target onto the eye to be examined,
The first control step further controls the fixation projection system to project a first fixation target onto the eye to be examined,
13. The method according to claim 12, wherein the second control step further controls the fixation projection system to project a second fixation target having a narrower visual angle than the first fixation target onto the eye to be inspected. A method of controlling the described ophthalmic device. an objective lens;
a refractive power measurement optical system for projecting light onto an eye to be inspected via the objective lens and detecting light returned from the eye to be inspected;
An optical scanner is provided, light from a light source is deflected by the optical scanner, the light deflected by the optical scanner is projected onto the eye to be inspected via the objective lens, and light returned from the eye to be inspected is detected. an inspection optical system;
a movement mechanism for moving the objective lens, the refractive power measurement optical system, and the inspection optical system in the optical axis direction of the objective lens;
a control unit that controls the movement mechanism;
A first arrangement position of the eye to be inspected on the optical axis of the objective lens is irradiated with alignment light from a direction forming a first angle with respect to the optical axis, and a return light from the eye to be inspected is received. 1 alignment system;
A second arrangement position of the eye to be inspected on the optical axis of the objective lens is irradiated with alignment light from a direction forming a second angle with respect to the optical axis, and light returned from the eye to be inspected is received. 2 alignment system;
A control method for an ophthalmic device comprising:
a first control step in which the control unit controls the moving mechanism so that a working distance with respect to the eye to be examined becomes a first working distance;
a first measuring step of performing refractive power measurement using the refractive power measurement optical system in a state in which the working distance is set to the first working distance in the first control step;
a second control step in which the control unit controls the moving mechanism so that the working distance with respect to the eye to be examined becomes a second working distance;
a second measuring step of performing an inspection using the inspection optical system in a state in which the working distance is set to the second working distance in the second control step;
including
In the first control step, the movement mechanism is controlled based on the light reception result obtained by the first alignment system;
The method of controlling an ophthalmologic apparatus, wherein, in the second control step, the moving mechanism is controlled based on a light receiving result obtained by the second alignment system.

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