JP2019213751A - Ophthalmologic apparatus and control method thereof - Google Patents

Abstract

To provide an ophthalmologic apparatus capable of performing a plurality of examinations and measurements with a working distance optimum for each of them by a simple configuration, and a control method thereof.SOLUTION: An ophthalmologic apparatus includes an objective lens, a refractive power measurement optical system, an examination optical system, a movement mechanism, and a control unit. The refractive power measurement optical system projects a light onto an eye to be examined through the objective lens and detects a return light from the eye to be examined. The examination optical system includes an optical scanner, deflects a light from a light source by the optical scanner, projects a light deflected by the optical scanner onto the eye to be examined through the objective lens, and detects a return light from the eye to be examined. The movement mechanism moves the objective lens, the refractive power measurement optical system and the examination optical system in an optical axis direction of the objective lens. The control unit controls the movement mechanism so that a working distance for the eye to be examined becomes a first working distance when performing a refractive power measurement using the refractive power measurement optical system, and a working distance becomes a second working distance when performing an examination using the examination optical system.SELECTED DRAWING: Figure 1

Description

  The present invention relates to an ophthalmologic apparatus and a control method thereof.

  2. Related Art An ophthalmologic apparatus capable of performing a plurality of examinations and measurements on an eye to be examined is known. Inspections and measurements on the subject's eye include subjective tests and objective measurements. The subjective test obtains a result based on a response from a subject. The objective measurement is to acquire information about the eye to be examined mainly using a physical method without referring to a response from the subject.

  For example, Patent Literature 1 discloses an ophthalmologic apparatus capable of performing a subjective test and objective measurement. This ophthalmologic apparatus can perform, as objective measurement, measurement and measurement of refractive power, keratometry, and optical coherence tomography of the subject's eye.

  In a plurality of examinations and measurements using such an ophthalmologic apparatus, the optimum working distances are different from each other. Therefore, if the working distance of the ophthalmologic apparatus is set so as to be optimal for one examination or measurement, the range of another examination or measurement is narrowed, or the accuracy of measurement is reduced. For example, when the working distance of the ophthalmologic apparatus is set so as to be optimal for refractive power measurement, a scan range in optical coherence tomography (OCT) measurement becomes narrow. For example, when the working distance of the ophthalmic apparatus is set so as to be optimal for OCT measurement, the apparatus is easily affected by instrument myopia. Thus, it is necessary to increase the diameter of the objective lens. However, when the diameter of the objective lens is increased, it becomes difficult to project a measurement pattern used for keratometry, and it becomes impossible to measure the corneal shape with high accuracy.

  An ophthalmologic apparatus capable of changing the working distance of an 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 measurement unit and an intraocular pressure measurement unit are vertically stacked. In this ophthalmic apparatus, the measurement unit is moved in the up and down direction, and the tonometry part is moved in the working distance direction with respect to the refractive power and corneal shape measurement part, so that each of the refractive power and corneal shape measurement and the tonometry is performed Optimum working distance can be set. For example, Patent Literature 4 discloses an ophthalmologic apparatus in which an optometry unit including a refractive power measurement unit and an intraocular pressure measurement unit is provided to be rotatable around a rotation axis with respect to a base. In this ophthalmologic apparatus, by rotating the optometry unit, measurement can be performed at the optimum working distance for each of the refractive power measurement and the intraocular pressure measurement.

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

  However, in the conventional ophthalmologic apparatus, a plurality of measurement units are stacked and arranged, or a rotation mechanism of the optometry unit is required, so that the size of the apparatus is increased.

  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 includes an objective lens, a refractive power measurement optical system that projects light to the eye to be inspected through the objective lens, and detects return light from the eye to be inspected, and an optical scanner. And an inspection optical system that deflects light from the light source by the optical scanner, projects the light deflected by the optical scanner to the eye to be inspected through the objective lens, and detects return light 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 the eye to be inspected when performing the refractive power measurement using the refractive power measuring optical system. And a control unit that controls the moving mechanism so that the working distance becomes a first working distance and the working distance becomes a second working distance when performing an inspection using the inspection optical system. .

  A second aspect of some embodiments is an anterior eye that includes a relay lens that relays light from an anterior segment of the eye to be inspected and an imaging device that receives light passing through the relay lens in the first aspect. Part control system, wherein the control unit moves the relay lens to a first lens position on an optical axis of the anterior eye part observation system when performing the refractive power measurement, and performs the anterior eye part when performing the examination The relay lens is moved to a second lens position on the optical axis of the observation system.

  A third aspect of some embodiments is the first aspect or the second aspect, further including a fixation projection system that projects a fixation target to the eye to be inspected, wherein the control unit performs the refraction measurement when performing the refractive power measurement. The first fixation target is projected onto the eye to be inspected, and the fixation projection system is controlled so as to project a second fixation target having a narrower viewing angle than the first fixation target to the eye when performing the examination.

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

  According to a fifth aspect of some embodiments, in any one of the first aspect to the fourth aspect, a first arrangement position of the subject's eye on an optical axis of the objective lens corresponds to a first arrangement position with respect to the optical axis. A first alignment system that irradiates alignment light from a direction forming one angle and receives return light from the eye to be inspected, and the light that is emitted to a second arrangement position of the eye to be inspected on the optical axis of the objective lens. A second alignment system that irradiates alignment light from a direction forming a second angle with respect to an axis and receives return light from the eye to be inspected, the control unit includes: (1) The moving mechanism is controlled based on a light receiving result obtained by the first alignment system, and the moving mechanism is controlled based on a light receiving result obtained by the second alignment system when performing the inspection.

  According to a sixth aspect of some embodiments, in any one of the first to fourth aspects, for each of two or more arrangement positions of the subject's eye on the optical axis of the objective lens, An alignment system that irradiates alignment light from a direction that forms a changeable angle with respect to the eye and receives return light from the eye to be inspected, and an angle changing mechanism that changes the angle, the control unit includes: When performing force measurement, the moving mechanism is controlled based on a light receiving result obtained by the alignment system in a state where the angle is changed to the first irradiation angle by the angle changing mechanism. The moving mechanism is controlled based on the light receiving result obtained by the alignment system in a state where the irradiation angle has been changed to 2.

According to a seventh aspect of some embodiments, in any one of the first to sixth aspects, an arc or a circle around the optical axis of the objective lens in the cornea of the subject's eye from the outer edge side of the objective lens. A corneal shape measurement optical system that projects a measurement pattern in the shape of the eye to the subject, and detects return light from the cornea of the eye through the objective lens, the corneal shape measurement optical system includes a kerato light source, A kerato plate disposed between the kerato light source and the subject's eye, and formed with a light-transmitting portion formed in an arc or a circle around the optical axis of the objective lens and transmitting light from the kerato light source The height of an image based on the measurement pattern with respect to the optical axis of the objective lens is h, the radius of curvature of the cornea of the eye to be examined is R, and the length from the optical axis of the objective lens to the light transmitting portion is When H is defined as H , The first working distance - a ((H-h) / tan (2 × sin -1 (h / R)) (R-√ (R 2 -h 2))) the moving mechanism so as to Control.

  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 a ninth aspect of some embodiments, in the seventh aspect or the eighth aspect, the distance from the pupil of the subject's eye to the fundus is Le, the distance from the anterior corneal surface to the pupil is La, and the anterior surface of the keratoplate. When the distance from L to the main surface of the objective lens is Lk, the scan range of the optical scanner is SA square, and the scan diameter of the objective lens for scanning the scan range is D, the control unit: The moving mechanism is controlled such that the second working distance becomes ((Le × D) / SA− (La + Lk)).

  In a tenth mode of some embodiments, in the ninth mode, the scan range is a range of (6 × √2) mm square in 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 divides light from an OCT light source into reference light and measurement light, and divides the measurement light into the measurement light. An OCT optical system is included 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 and the reference light.

  In a twelfth aspect of some embodiments, the inspection optical system according to any one of the first to eleventh aspects, wherein the inspection optical system deflects light from an SLO light source by the optical scanner and deflects the deflected light. An SLO optical system that projects onto the optometry and receives the return light from the subject's eye is included.

  A thirteenth aspect of some embodiments includes an objective lens, a refractive power measurement optical system that projects light to the eye to be examined through the objective lens, and detects return light from the eye to be examined, and an optical scanner. And an inspection optical system that deflects light from the light source by the optical scanner, projects the light deflected by the optical scanner to the eye to be inspected through the objective lens, and detects return light from the eye to be inspected. A moving mechanism that moves 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 control unit that controls the moving mechanism, and a control method for an ophthalmologic apparatus. A first control step of controlling the moving mechanism so that a working distance with respect to the eye to be examined is a first working distance; and setting the working distance to the first working distance in the first control step. Sa A first measurement step of performing a refractive power measurement using the refractive power measurement optical system, and the control unit controls the moving mechanism such that a working distance with respect to the eye to be examined becomes a second working distance. A second control step; and a second measurement step of executing an inspection using the inspection optical system in a state where 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, in the thirteenth aspect, the ophthalmic apparatus includes a relay lens that relays light from an anterior segment of the eye to be inspected, and an image sensor that receives light passing through the relay lens. In the first control step, the relay lens is further moved to a first lens position on an optical axis of the anterior eye observation system, and in the second control step, Further, the relay lens is moved to a second lens position on the optical axis of the anterior ocular 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 on the eye to be inspected, and the first control step further includes: Controlling the fixation projection system so as to project a first fixation target to the eye to be inspected, and further comprising, in the second control step, a second fixation target having a narrower viewing angle than the first fixation target. The fixation projection system is controlled so as to project onto the eye to be inspected.

  In a sixteenth aspect of some embodiments, in any one of the thirteenth aspect to the fifteenth aspect, the ophthalmologic apparatus moves the light with respect to a first arrangement position of the subject's eye on an optical axis of the objective lens. A first alignment system that irradiates alignment light from a direction that forms a first angle with respect to an axis and receives return light from the eye to be inspected, and a second alignment position of the eye to be inspected on the optical axis of the objective lens 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 subject's eye, and the first control step includes: The moving mechanism is controlled based on a light receiving result obtained by one alignment system, and in the second control step, the moving mechanism is controlled based on a light receiving result obtained by the second alignment system.

  ADVANTAGE OF THE INVENTION According to this invention, it becomes possible to provide the ophthalmologic apparatus which can perform several test | inspections and measurement by a simple structure with the optimal working distance, respectively, and its control method.

It is a schematic diagram showing an example of composition of an optical system of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of an optical system of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram for explaining the optical system of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the optical system of the ophthalmologic apparatus according to the embodiment. FIG. 2 is a schematic diagram illustrating a configuration example of a processing system of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the optical system of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the optical system of the ophthalmologic apparatus according to the embodiment. It is the schematic which shows the flow of the example of an operation | movement of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the flow of the example of an operation | movement of the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic for demonstrating the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic for demonstrating the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic for demonstrating the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the processing system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the processing system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the processing system of the ophthalmologic apparatus which concerns on the modification of embodiment. It is the schematic which shows the example of a structure of the optical system of the ophthalmologic apparatus which concerns on the modification of embodiment.

  An embodiment of an ophthalmologic apparatus and a control method thereof according to the present invention will be described in detail with reference to the drawings. In addition, the description content of the document cited in this specification and any known technology can be used in the following embodiments.

  The ophthalmologic apparatus according to the embodiment can execute a plurality of inspections 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 an objective lens with a plurality of optical systems corresponding to the types of examinations and measurements.

  The ophthalmologic apparatus according to the embodiment can execute refractive power measurement (reflection measurement) and scan measurement. In scan measurement, measurement results are obtained by deflecting measurement light, projecting the deflected light onto the subject's eye, and detecting return light from the subject's eye. The scan measurement includes measurement and imaging using optical coherence tomography, and measurement and imaging using an SLO (Scanning Laser Ophthalmoscope) optical system. Hereinafter, a case will be described in which the ophthalmologic apparatus according to the embodiment performs OCT on the anterior segment and the fundus as scan measurement.

  Hereinafter, in the embodiment, a case in which a swept source type OCT technique is used will be described in detail. However, the embodiment is applied to an ophthalmologic apparatus using another type (for example, a spectral domain type, a time domain type) OCT. Such a configuration can be applied.

  The ophthalmologic apparatus according to some embodiments further includes a subjective examination optical system for performing a subjective examination, and another objective measurement system for performing another objective measurement.

  The subjective test is a measurement technique for acquiring information using a response from a subject. The subjective test includes a subjective refraction measurement such as a distance test, a near test, a contrast test, and a glare test, and a visual field test.

  Objective measurement is a measurement technique for acquiring information about an eye to be examined mainly using a physical technique without referring to a response from the subject. Objective measurement includes measurement for acquiring the characteristics of the eye to be inspected and imaging for acquiring an image of the eye to be inspected. Other objective measurements include intraocular pressure measurement and fundus photography.

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

  Hereinafter, the working distance is a 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 apparatus main body (housing) such as a kerato plate. In some embodiments, the working distance is a distance in the optical axis of the objective lens.

<Configuration of optical system>
FIG. 1 and FIG. 2 show a configuration example of an optical system of the ophthalmologic apparatus according to the embodiment. The ophthalmologic apparatus 1000 according to the embodiment includes an optical system for observing the eye E, an optical system for inspecting the eye E, and a dichroic mirror that separates the optical path of these optical systems by wavelength. An anterior ocular segment observation system 5 is provided as an optical system for observing the eye E to be examined. An OCT optical system and a reflex measuring optical system (refractive power measuring optical system) are provided as an optical system for inspecting the eye E to be inspected.

  The ophthalmologic apparatus 1000 includes a Z alignment system 1, an XY alignment system 2, a keratometry system 3, a fixation projection system 4, an anterior segment observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an OCT optical system 8. including. In the following, for example, the anterior ocular segment observation system 5 uses light of 940 nm to 1000 nm, the reflex measurement optical system (reflection measurement projection system 6 and reflex 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 eye observation system 5)
The anterior segment observation system 5 captures a moving image of the anterior segment of the subject's eye E. In the optical system passing through the anterior ocular segment observation system 5, the imaging surface of the imaging element 59 is arranged at a pupil conjugate position. The anterior segment illumination light source 50 irradiates the anterior segment of the eye E with illumination light (for example, infrared light). The light reflected by the anterior segment of the eye E passes through the objective lens 51, passes through the dichroic mirror 52, passes through a hole formed in a diaphragm (telecentric diaphragm) 53, and passes through the half mirror 23. Pass through the relay lenses 55 and 56 and pass through the dichroic mirror 76. The dichroic mirror 52 combines (separates) the optical path of the reflex measurement optical system and the optical path of the anterior ocular segment observation system 5. The dichroic mirror 52 is arranged such that an optical path combining surface for combining these optical paths is inclined with respect to the optical axis of the objective lens 51. In the embodiment, the relay lens 56 is movable along the optical axis of the anterior ocular segment observation system 5 (or the optical axis of the relay lens 56). The light transmitted through the dichroic mirror 76 is imaged by the imaging lens 58 on the imaging surface of the imaging element 59 (area sensor). The imaging element 59 performs imaging and signal output at a predetermined rate. The output (video signal) of the image sensor 59 is input to the processing unit 9 described below. The processing unit 9 displays an anterior ocular segment image E ′ based on the video signal on a display screen 10a of the display unit 10 described later. The anterior eye image E ′ is, for example, an infrared moving image.

(Z alignment system 1)
Z alignment system 1 includes a Z alignment system 1A and a Z alignment system 1B. One 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 segment observation system 5) in the optical axis direction (front-back 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 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 is specularly reflected at the eye E. It is configured to receive the reflected light (return light). The Z alignment system 1B irradiates the eye E at the second arrangement position on the optical axis of the objective lens 51 that is farther from the ophthalmologic apparatus 1000 than the first arrangement position with alignment light from a direction forming a second angle. It is configured to receive light specularly reflected at the optometry E. In this embodiment, the first angle is substantially equal to the second angle.

  The Z alignment system 1A projects light (infrared light) for performing alignment in the optical axis direction of the objective lens 51 onto the eye E to be inspected. The light output from the Z alignment light source 11A is projected onto the cornea Cr of the 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 cornea vertex changes in the optical axis direction of the anterior ocular segment observation system 5 (the optical axis direction of the objective lens 51), the light projection position on the sensor surface of the line sensor 13A changes. The processing unit 9 obtains the position of the apex of the cornea of the eye E based on the projection position of the light on the sensor surface of the line sensor 13A before the reflex measurement, and controls the mechanism for moving the optical system based on the obtained position to obtain the Z alignment. Execute

  Z alignment system 1B has the same configuration as Z alignment system 1A. That is, the light output from the Z alignment light source 11B is projected onto the cornea Cr of the eye E at the second arrangement position, reflected by the cornea Cr, and imaged on the sensor surface of the line sensor 13B by the imaging lens 12B. . The processing unit 9 obtains the position of the vertex of the cornea of the eye E based on the projection position of the light on the sensor surface of the line sensor 13B before the OCT measurement, and controls the mechanism for moving the optical system based on the position to obtain the Z alignment. Execute

(XY alignment system 2)
The XY alignment system 2 applies light (infrared light) for alignment in a direction (horizontal direction (X direction), vertical direction (Y direction)) orthogonal to the optical axis of the anterior eye observation system 5 to the eye E. Irradiation. The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22 provided in an optical path branched from an optical path of the anterior ocular segment observation system 5 by a half mirror 23. The 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 to the eye E through the anterior eye observation system 5. Light reflected by the cornea Cr of the eye E is guided to the image sensor 59 through the anterior eye observation system 5.

  The image (bright spot image) Br based on the reflected light is included in the anterior segment image E ′. The processing unit 9 displays the anterior eye image E ′ including the bright spot image Br and the alignment mark AL on the display screen of the display unit. When performing the XY alignment manually, the user performs an operation of moving the optical system so as to guide the bright spot image Br in the alignment mark AL. When performing automatic alignment, the processing unit 9 controls a mechanism that moves the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is canceled.

(Kerato measurement system 3)
The kerat measuring system 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea Cr of the eye E to be inspected onto the cornea Cr. The kerato plate 31 is disposed between the objective lens 51 and the eye E to be inspected. On the back side (the objective lens 51 side) of the kerato plate 31, a kerat ring light source 32 is provided. The kerato plate 31 is formed with a kerato pattern (transmitting portion) that transmits light from the kerat ring light source 32 along a circumference around the optical axis of the objective lens 51. Note that the kerato pattern may be formed in an arc shape (part of the circumference) centered on the optical axis of the objective lens 51. By illuminating the kerato plate 31 with light from the kerat ring light source 32, a ring-shaped light beam (arc-shaped or circumferential measurement pattern) is projected on the cornea Cr of the eye E to be examined. The reflected light (kerattling image) from the cornea Cr of the eye E is detected by the imaging device 59 together with the anterior eye image E ′. The processing unit 9 calculates a corneal shape parameter representing the shape of the cornea Cr by performing a known operation based on the kerattling image.

(Ref measurement projection system 6, Reflect measurement light receiving system 7)
The reflex measurement optical system includes a reflex measurement projection system 6 and a reflex measurement light receiving system 7 used for refractive power measurement. The reflex measurement projection system 6 projects a light beam (for example, a ring-shaped light beam) (infrared light) for refractive power measurement onto the fundus oculi Ef. The reflex measurement light receiving system 7 receives the return light of this light beam from the eye E to be examined. The reflex measurement projection system 6 is provided in an optical path branched by a perforated prism 65 provided in the optical path of the reflex measurement light receiving system 7. The aperture formed in the apertured prism 65 is arranged at the pupil conjugate position. In the optical system that passes through the reflex measurement light receiving system 7, the imaging surface of the imaging device 59 is arranged at a fundus conjugate position.

  In some embodiments, the reflex measurement light source 61 is an SLD (Superluminous Diode) light source that is a high brightness light source. The reflex measurement light source 61 is movable in the optical axis direction. The reflex measurement light source 61 is arranged at a fundus conjugate position. The light output from the reflex measurement light source 61 passes through the relay lens 62 and enters the conical surface of the conical prism 63. The light incident on the conical surface is deflected and exits from the bottom surface of the conical prism 63. Light emitted from the bottom surface of the conical prism 63 passes through a light transmitting portion formed in a ring shape on the ring stop 64. The light (ring-shaped luminous flux) that has passed through the light transmitting portion of the ring stop 64 is reflected by a 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. You. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected on the eye E to be inspected. The rotary prism 66 is used for averaging the light amount distribution of the ring-shaped light beam with respect to the blood vessel or the diseased part of the fundus oculi Ef and reducing speckle noise caused by the light source.

  The return light of the ring-shaped light beam projected on the fundus Ef passes through the objective lens 51, and is reflected by the dichroic mirror 52 and the dichroic mirror 67. The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the hole of the perforated prism 65, passes through the relay lens 71, is reflected by the reflection mirror 72, and passes through the relay lens 73 and the focusing lens. Go through 74. The focusing lens 74 is movable along the optical axis of the reflex measurement light receiving system 7. The light that has passed through the focusing lens 74 is reflected by the reflection mirror 75, reflected by the dichroic mirror 76, and is 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 eye E by performing a known operation based on the output from the image sensor 59. For example, the refractive power value includes a spherical power, an astigmatic power and an astigmatic axis angle, or an equivalent spherical power.

(Fixation projection system 4)
An OCT optical system 8 described later is provided in an optical path separated from the optical path of the reflex measurement optical system by the dichroic mirror 67. The fixation projection system 4 is provided in an optical path branched from the optical path of the OCT optical system 8 by the dichroic mirror 83.

  The fixation projection system 4 presents a fixation target to the eye E. A fixation unit 40 is arranged in the optical path of the fixation projection system 4. The fixation unit 40 is movable along the optical path of the fixation projection system 4 under the control of the processing unit 9 described below. The fixation unit 40 includes a liquid crystal panel 41. The 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 a fixation target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the eye E can be changed. As the fixation position of the eye E, 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 disc, and a position between the macula and the optic disc. There is a position for acquiring an image centered on the center of the fundus in between. The display position of the pattern representing the fixation target can be arbitrarily changed.

  The light from the liquid crystal panel 41 passes through the relay lens 42, passes through the dichroic mirror 83, passes through the relay lens 82, is reflected by the reflection mirror 81, passes through the dichroic mirror 67, and is reflected by the dichroic mirror 52. . The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected on 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. Based on the result of the reflex measurement performed before the OCT measurement, the position of the focusing lens 87 is adjusted such that the end face of the optical fiber f1 is conjugate to the imaging part (the fundus oculi Ef or the anterior segment) and the optical system. .

  The OCT optical system 8 is provided on an optical path separated by a dichroic mirror 67 from the optical path of the reflex 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 coupled coaxially.

  The 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, similarly to a general swept-source OCT device. It is comprised including. The wavelength-swept light source includes a laser light source including a resonator. The OCT light source 101 temporally changes the output wavelength in a near-infrared wavelength band that cannot be visually recognized by human eyes.

  As exemplified 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 variable light source (wavelength sweep type light source) into measurement light and reference light, and a function of returning measurement light from the eye E to be examined and reference light passing through a reference optical path. And a function of detecting the interference light. The 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 output light (a wavelength range of 1000 nm to 1100 nm) at high speed. The light L0 output from the OCT light source 101 is guided to a polarization controller 103 by an optical fiber 102, and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided to the fiber coupler 105 by the optical fiber 104, and is split into the measurement light LS and the reference light LR.

  The reference light LR is guided by an optical fiber 110 to a collimator 111, converted into a parallel light flux, and guided to a corner cube 114 via an optical path length correction member 112 and a dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR and the optical path length of the measurement light LS. The dispersion compensating member 113 acts to match 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, and thereby changes 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 from a parallel light beam into a focused light beam by the collimator 116, and enters the optical fiber 117. The reference light LR that has entered the optical fiber 117 is guided to a polarization controller 118 to adjust its polarization state, guided to an attenuator 120 by an optical fiber 119, adjusted in light amount, and guided to a fiber coupler 122 by an optical fiber 121.

  On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber f1 and converted into a parallel light beam by the collimator lens unit 89, and passes through the optical scanner 88, the focusing lens 87, the relay lens 85, and the reflection mirror 84. Then, the light is reflected by the dichroic mirror 83.

  The optical scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. The 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 an imaging region (the fundus oculi Ef or the anterior segment) in a horizontal direction orthogonal 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 an imaging region in a vertical direction orthogonal to the optical axis of the OCT optical system 8. Examples of the scanning mode of the measurement light LS by the optical scanner 88 include a horizontal scan, a vertical scan, a cross scan, a radiation scan, a circle scan, a concentric scan, and a spiral scan.

  The measurement light LS reflected by the dichroic mirror 83 passes through the relay lens 82, is reflected by the reflection mirror 81, passes through the dichroic mirror 67, is reflected by the dichroic mirror 52, is refracted by the objective lens 51, and is refracted by the objective lens E. Incident on. The measurement light LS is scattered and reflected at various depth positions of the eye E. The return light of the measurement light LS from the subject's eye E travels in the same path as the outward path in the opposite direction, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

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

  The detector 125 is, for example, a balanced photodiode. The 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 the photodetectors. The detector 125 sends this output (detection signal) to a DAQ (Data Acquisition System) 130.

  The DAQ 130 is supplied with a clock KC from the OCT light source 101. 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 variable wavelength light source. The OCT light source 101, for example, after optically delaying one of the two split lights obtained by splitting the light L0 of each output wavelength, generates the clock KC based on the result of detecting the combined light. 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 unit 220 of the processing unit 9. The arithmetic processing unit 220 forms a reflection intensity profile in each A line by performing a Fourier transform or the like on the spectral distribution based on the sampling data, for example, for each series of wavelength scans (for each A line). Further, the arithmetic processing unit 220 forms image data by imaging the reflection intensity profile of each A line.

  In this example, the corner cube 114 for changing the length of the optical path (reference optical path, reference arm) of the reference light LR is provided. However, using other optical members, the measurement optical path length and the reference optical path length are used. It is also possible to change the difference from.

  The processing unit 9 calculates a refractive power value from a measurement result obtained using the reflex measurement optical system, and based on the calculated refraction power value, determines whether the fundus oculi Ef, the reflex measurement light source 61 and the image sensor 59 are conjugated. Then, the reflex measurement light source 61 and the focusing lens 74 are moved in the optical axis direction to a certain position. In some embodiments, the processing unit 9 moves the focusing lens 87 of the OCT optical system 8 in the optical axis direction in conjunction with the movement of the focusing lens 74. In some embodiments, the processing unit 9 moves the liquid crystal panel 41 (the fixation unit 40) in the optical axis direction in conjunction with the movement of the reflex measurement light source 61 and the focusing lens 74.

  The ophthalmologic apparatus 1000 according to the embodiment uses at least the reflex measurement optical system and the OCT optical system 8 while sharing the objective lens, and performs the reflex measurement (refractive power measurement) using the reflex measurement optical system and the OCT using the OCT optical system 8. It is possible to change the working distance between measurement and measurement. Thereby, it is possible to acquire a highly accurate reflex measurement result and a highly accurate OCT measurement result with a simple configuration while securing a scan range by the OCT optical system 8.

[Working distance for reflex 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 instrument myopia when performing reflex measurement. When the ophthalmologic apparatus 1000 includes the kerato-measurement system 3, the working distance is desirably a working distance at which a kerato-measurement result useful for corneal shape analysis can be obtained.

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

  The kerato measuring system 3 is telecentric optics so that a kerat ring image whose height does not change even when the working distance changes can be obtained. When light is projected on the cornea Cr by the kerato-measurement system 3, the cornea acts as a convex mirror, and an image mainly reflected on the front surface of the cornea Cr appears.

  Let R be the radius of curvature of the cornea Cr of the eye E, h be the height of the keratoling 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 for the ring pattern (measurement pattern) to be arranged at the incident position of the ring-shaped light beam from the kerat ring light source 32, if an angle between a line connecting the center of curvature of the cornea Cr and the incident position to the optical axis is β, , The following equation is established.

h = R × sin (β) (1)
β = α / 2 (2)

The radius of the kerato pattern formed on the kerato plate 31 is H, the distance from the kerato plate 31 to the eye E (corneal vertex) is the working distance WDref, and the distance Δd between the incident position of the ring-shaped light beam and the corneal vertex. Considering R− Ｒ (R ² −h ² )), the following equation is established.

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

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

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

  In some embodiments, known data such as a model eye is used for the radius of curvature R. The effective diameter D of the objective lens 51 can be determined from the keratling pattern radius H.

  For example, h = 1.5 mm to measure the corneal shape in the area of φ3 on the cornea Cr which is useful for the corneal shape analysis.

  As described above, when performing reflex measurement, by setting the working distance WDref shown in Expression (4), it is possible to increase the working distance to reduce the influence of instrument myopia and to increase the size of the kerato plate 31. Can be prevented. Thus, it is possible to provide an ophthalmologic apparatus that can acquire highly accurate reflex measurement results and kerato measurement results with a simple configuration.

[Working distance when performing OCT measurement]
In the ophthalmologic apparatus 1000 according to the embodiment, a working distance (second working distance) is set so that at least a scan range useful for analysis using standard data can be scanned when performing OCT measurement. The standard data is statistically derived from measurement data of a large number of normal eyes and information of a subject of the measurement data, and is referred to as normal eye data (normal data). The working distance set when performing the OCT measurement is a working distance that can scan a scan range (or a range wider than the scan range) when the measurement data used for deriving the standard data is acquired. May be.

  FIG. 4 is an explanatory diagram of a working distance when performing OCT measurement according to the embodiment. FIG. 4 is an enlarged view of a 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 the description will be appropriately omitted.

  The optical scanner 88 deflects the measurement light LS in each of the X direction and the Y direction in order to acquire data of a desired scan range without covering. Assuming that the scan range in the fundus oculi Ef is RA × RA, the optical scanner 88 needs to deflect at least RA × √2 (= SA) in each direction.

  Here, the optical scanner 88 is disposed so as to be optically substantially conjugate with the pupil of the eye E. The working distance is WDoct, the distance from the anterior cornea to the pupil is La, the distance from the pupil to the fundus is Le, and the distance from the keratoplate 31 (the surface on the side of the eye E to be examined) to the principal surface of the objective lens 51 is Lk. The scan range SA satisfies the following equation based on the similarity between a triangle having the pupil at the top and the base having the radius of the objective lens 51 and a triangle having the pupil at the top and the base having the scan range SA / 2 in the fundus oculi Ef. .

  SA = Le × D / (WDoct + La + Lk) (5)

  As described above, in the ophthalmologic apparatus 1000 according to the embodiment, when performing the OCT measurement, the working distance WDoct shown in the following Expression (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 kerattling pattern radius H as the diameter of the scan range (scan diameter) necessary for scanning the scan range SA in the objective lens 51. In some embodiments, known data such as standard eye data or a model eye is used for the distances Le and La. In some embodiments, the distance Lk is data known in the ophthalmologic apparatus 1. In some embodiments, the distance Lk is substantially zero.

  As a result, it is possible to compare the result obtained by the OCT measurement with the existing standard data, and to use the existing standard data to assist a useful judgment on the OCT measurement result.

  For example, to scan a scan range required for analysis using standard data, the scan range SA is (6 × ６2) mm, (9 × √2) mm, or (12 × √2) mm.

  In some embodiments, the ophthalmologic apparatus 1000 can set a working distance corresponding to a scan range selected from a plurality of scan ranges, and execute OCT measurement at the set working distance. The working distance corresponding to the scan range may be calculated each time according to the equation (6), or may be obtained in advance.

  As described above, when OCT measurement is performed, a scan result useful for analysis using standard data can be obtained by setting the working distance WDect shown in Expression (6). Thus, it is possible to provide an ophthalmologic apparatus that has a simple configuration and can assist useful judgment on the OCT measurement result using existing standard data.

  As described above, the ophthalmologic apparatus 1000 moves the optical system relative to the subject's eye E in the Z direction so that the working distance becomes the working distance WDref when performing reflex measurement, and the working distance when performing OCT measurement. The optical system is relatively moved in the Z direction with respect to the eye E so as to be WDect. 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 be controlled in accordance with the switching between the reflex measurement and the OCT measurement.

  The fixation projection system 4 projects a reflex measurement target (for example, a landscape chart) onto the eye E when performing reflex measurement, and has a narrower viewing angle than the reflex measurement target when performing OCT measurement. Switching is performed so that a target (for example, a dot target or a cross target) is projected onto the eye E to be examined. In the anterior ocular segment observation system 5, the relay lens 56 is moved to a position (first lens position) on the optical axis for reflex measurement when performing reflex measurement, and is moved on the optical axis for OCT measurement when performing OCT measurement. The relay lens 56 is moved to the position (second lens position).

<Configuration of processing system>
The configuration of the processing system of the ophthalmologic apparatus 1000 will be described. FIG. 5 shows an example of a functional configuration of the processing system of the ophthalmologic apparatus 1000. FIG. 5 illustrates an example of a functional block diagram of a processing system of the ophthalmologic apparatus 1000.

  The processing unit 9 controls each unit of the ophthalmologic apparatus 1000. The processing unit 9 can execute various arithmetic processes. The processing unit 9 includes a processor. The functions of the processor include, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, an SPLD (Simple Programmable Programmable LPG), and a programmable logic device). , FPGA (Field Programmable Gate Array) and the like. The processing unit 9 realizes the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or a storage device.

  The processing unit 9 includes a control unit 210 and an arithmetic processing unit 220. Further, the ophthalmologic apparatus 1000 includes a moving mechanism 200, a display unit 270, an operation unit 280, and a communication unit 290.

  The moving mechanism 200 includes a Z alignment system 1 (Z alignment systems 1A and 1B), an XY alignment system 2, a kerato measurement system 3, a fixation projection system 4, an anterior ocular segment observation system 5, a reflex measurement projection system 6, and a reflex measurement light reception. This is a mechanism for moving a head unit in which optical systems such as the system 7 and the OCT optical system 8 are housed in the front, rear, left and right directions. For example, the moving mechanism 200 includes an actuator that generates a driving force for moving the head unit, and a transmission mechanism that transmits the driving force. The actuator is constituted by, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears or a rack and pinion. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending a control signal to the actuator.

(Control unit 210)
The control unit 210 includes a processor and controls each unit of the ophthalmologic apparatus. The 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 the storage unit 212 in advance. 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. When the main control unit 211 operates according to such a computer program, the control unit 210 executes control processing.

  The main control unit 211 performs various controls of the ophthalmologic apparatus as a measurement control unit. The control for the Z alignment system 1A includes control of the Z alignment light source 11A, control of the line sensor 13A, and the like. The control for 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 and off the light sources, adjusting the light amount, adjusting the aperture, and the like. The control of the line sensors 13A and 13B includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. Thereby, the lighting and non-lighting of the Z alignment light sources 11A and 11B are switched or the light amount is changed. The main control unit 211 captures a signal detected by the line sensor 13A, and specifies a projection position of light on the line sensor 13A based on the captured signal. The main control unit 211 captures a signal detected by the line sensor 13B, and specifies a light projection position on the line sensor 13B based on the captured signal. The main control unit 211 obtains the position of the apex of the cornea of the eye E using the projection position specified by the Z alignment system 1A when performing the reflex measurement, and controls the moving mechanism 200 based on this to move the head unit in the front-back direction. (Z alignment). The main control unit 211 obtains the position of the vertex of the cornea of the eye E using the projection position specified by the Z alignment system 1B when performing the OCT measurement, and controls the moving mechanism 200 based on this to move the head unit in the front-back 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 and off the light source, adjusting the amount of light, adjusting the aperture, and the like. Thereby, the lighting and non-lighting of the XY alignment light source 21 are switched, or the light amount is changed. The main controller 211 captures the signal detected by the image sensor 59 and specifies the position of the bright spot image based on the return light of the light from the XY alignment light source 21 based on the captured signal. The main control unit 211 controls the moving mechanism 200 to cancel the displacement of the bright spot image Br with respect to a predetermined target position (for example, the center position of the alignment mark AL) and moves the head unit in the left, right, up, and down directions. Move (XY alignment).

  The control for the kerato-measuring system 3 includes the control of the kerato-ring light source 32 and the like. The control of the kerattling light source 32 includes turning on and off the light source, adjusting the light amount, adjusting the aperture, and the like. Thereby, the lighting and non-lighting of the kerattling light source 32 are switched, or the light amount is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform a known operation on the kerattling image detected by the image sensor 59. Thereby, the corneal shape parameter of the eye E is obtained.

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

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

  The main control unit 211 causes the liquid crystal panel 41 to display the fixation target FT1 shown in FIG. 6A when performing the reflex measurement, and displays the fixation target FT2 or the fixation target FT3 shown in FIG. 6A when performing the OCT measurement. 41 is displayed. The fixation target FT1 is a landscape chart. The fixation target FT2 is a bright point (dot target) having a smaller viewing angle than the fixation target FT1. The fixation target FT3 is a cross target having a smaller viewing 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 examination mode (measurement mode). Further, the main control unit 211 can switch and display the fixation target FT1 and the fixation target FT3 according to the examination mode.

  The inspection mode according to this embodiment includes, for example, a reflex measurement mode, an OCT measurement mode, and a mode in which the reflex measurement is performed and then the mode automatically shifts to the OCT measurement.

  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 so that the eye to be inspected does not adjust the visual acuity in the reflex measurement, and the fixation target according to the measurement site or the like in the OCT measurement. Thus, a fixation target can be presented so that a desired part of the eye to be examined is arranged at a predetermined measurement position.

  FIG. 6B is an explanatory diagram of a fixation target according to the second presented example of the embodiment. FIG. 6B schematically illustrates a fixation target according to the second presented example.

  The main control unit 211 causes the liquid crystal panel 41 to display the fixation target FT4 shown in FIG. 6B when performing the reflex measurement, and superimposes the fixation target FT4 shown in FIG. 6B when performing the 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 point (dot target) having a smaller viewing angle than the fixation target FT4. In the second presentation example, the main control unit 211 causes the fixation target BP1 to be displayed on the fixation target FT4 according to the examination mode (measurement mode). The main control unit 211 can blink the fixation target BP1 or move the display position of the fixation target BP1. In some embodiments, when performing the OCT measurement, the main control unit 211 increases the luminance of a part of the fixation target FT4 or periodically increases or decreases the luminance of a part of the fixation target FT4. In some embodiments, a fixation target FT3 shown in FIG. 6A is presented instead of the fixation target BP1.

  In the second example of presentation, as in the first example of presentation, a fixation target is presented to the subject's eye in the reflex measurement so as not to adjust the visual acuity, and a desired part in the subject's eye is determined in the OCT measurement according to the measurement part or the like. The fixation target can be presented so as to be arranged at the measurement position.

  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. Like the moving mechanism 200, the moving mechanism includes an actuator that generates a driving force for moving the moving mechanism, and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves at least the liquid crystal panel 41 in the optical axis direction. Thereby, the position of the liquid crystal panel 41 is adjusted so that the liquid crystal panel 41 and the fundus oculi Ef are optically conjugate.

  The control for the anterior ocular segment observation system 5 includes control of the anterior ocular segment illumination light source 50, control of the lens moving mechanism 56D that moves the relay lens 56, control of the image sensor 59, and the like. The control of the anterior segment illumination light source 50 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. Thereby, the lighting and non-lighting of the anterior segment illumination light source 50 are switched or the light amount is changed. Similarly to the moving mechanism 200, the lens moving mechanism 56D is provided with an actuator that generates a driving force for moving the moving mechanism, and a transmission mechanism that transmits the 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), and moves the relay lens 56 in the optical axis direction. For example, the storage unit 212 previously stores information corresponding to the position on the optical axis of the relay lens 56 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. Thereby, even when the working distance is changed in accordance with the inspection mode, it is possible to form a signal from the anterior ocular segment on the imaging surface of the imaging element 59, so that the focus can be maintained even during the reflex measurement or the OCT measurement. The combined anterior eye image can be observed. The control of the image sensor 59 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the image sensor 59. The main control unit 211 captures a signal detected by the image sensor 59 and causes the arithmetic processing unit 220 to execute processing such as image formation based on the captured signal.

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

  The control for the reflex measurement light receiving system 7 includes the control of the focusing lens 74 and the like. The control of the focusing lens 74 includes control of movement of the focusing lens 74 in the optical axis direction. For example, the reflex measurement light receiving system 7 includes a moving mechanism that moves the focusing lens 74 in the optical axis direction. Like the moving mechanism 200, the moving mechanism includes an actuator that generates a driving force for moving the moving mechanism, and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 74 in the optical axis direction. The main controller 211 controls the reflex measurement light source 61 and the focusing lens 74 according to, for example, the refractive power of the eye E so that the reflex measurement light source 61, the fundus oculi Ef, and the imaging device 59 are optically conjugate. It is possible to move in the axial direction.

  The control for 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. The control of the optical scanner 88 includes control of the scanning position, scanning range, and scanning speed by the first galvanomirror, control of the scanning position, scanning range, and scanning speed by the second galvanomirror.

  The control of the focusing lens 87 includes moving control of the focusing lens 87 in the optical axis direction, movement control of the focusing lens 87 to a focusing reference position corresponding to the imaging region, and moving range (focusing range) corresponding to the imaging region. Movement control within the focus range). For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 87 in the optical axis direction. Like the moving mechanism 200, the moving mechanism includes an actuator that generates a driving force for moving the moving mechanism, and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 87 in the optical axis direction. In some embodiments, the ophthalmic apparatus includes a holding member that holds the focusing lenses 74 and 87, and a driving unit that drives the holding member. The main control unit 211 controls the movement of the focusing lenses 74 and 87 by controlling the driving unit. For example, the main controller 211 may move the focusing lens 87 in conjunction with the movement of the focusing lens 74, and then move only the focusing lens 87 based on the intensity of the interference signal.

  The control of the corner cube 114 includes a 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 in a direction along the optical path. Like the moving mechanism 200, the moving mechanism includes an actuator that generates a driving force for moving the moving mechanism, and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the corner cube 114 in a direction 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 using the DAQ 130, and causes the arithmetic processing unit 220 (image forming unit 222) to execute processing such as image formation based on the sampled signal.

  The main control unit 211 performs a process of writing data to the storage unit 212 and a process 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, measurement results of objective measurement, image data of a tomographic image, image data of a fundus image, 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 subject's eye information includes information about the subject, such as a patient ID and a name, and information about the subject's eye, such as left / right eye identification information. Further, the storage unit 212 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 calculating unit 221 generates a ring image (pattern image) obtained by the imaging device 59 receiving return light of a ring-shaped light beam (ring-shaped measurement pattern) projected on the fundus oculi Ef by the reflex measurement projection system 6. ) To analyze. For example, the eye-refractive-power calculating unit 221 obtains the position of the center of gravity of the ring image from the luminance distribution in the image in which the obtained ring image is drawn, and obtains the luminance distribution along a plurality of scanning directions extending radially from the position of the center of gravity. The ring image is specified from the luminance distribution. Subsequently, the eye-refractive-power calculating unit 221 obtains an approximate ellipse of the specified ring image, and obtains a spherical power, an astigmatic power, and an astigmatic axis angle by substituting the major axis and the minor axis of the approximate ellipse into a known equation. . Alternatively, the eye-refractive-power calculating unit 221 can calculate the parameters of the eye-refractive power based on the deformation and displacement of the ring image with respect to the reference pattern.

  Further, the eye-refractive-power calculating unit 221 calculates the corneal refractive power, the corneal astigmatism, and the corneal astigmatic axis angle based on the kerattling image acquired by the anterior ocular segment observation system 5. For example, the eye-refractive-power calculating unit 221 calculates the corneal curvature radius of the strong principal meridian or the weak principal meridian of the front surface of the cornea by analyzing the kerattling image, and calculates the above-mentioned parameter based on the corneal curvature radius.

  The image forming section 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 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), similarly to the conventional spectral domain type OCT. The image data obtained in this manner is a data set including a group of image data formed by imaging the reflection intensity profiles in a plurality of A lines (the paths of the respective measurement lights LS in the eye E). is there.

  In order to improve the image quality, a plurality of data sets acquired by repeating scanning with the same pattern a plurality of times can be superimposed (averaged).

  The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 222. For example, the data processing unit 223 performs correction processing such as luminance correction and dispersion correction of the image. The data processing unit 223 performs various types of image processing and analysis processing on an image (an anterior ocular segment image or the like) obtained using the anterior ocular segment observation system 5.

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

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

  The operation unit 280 is used as a user interface unit to operate the ophthalmologic apparatus. The operation unit 280 includes various hardware keys (joysticks, buttons, switches, and the like) provided in the ophthalmologic apparatus. The operation unit 280 may include various software keys (buttons, icons, menus, and the like) displayed on the display screen 10a of the touch panel type.

  At least a part of the display unit 270 and the operation unit 280 may be integrally configured. 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 includes a communication interface according to a connection mode with an external device. An example of the external device is a spectacle lens measuring device for measuring optical characteristics of a lens. The spectacle lens measuring device measures the power of the spectacle lens worn by the subject, and inputs the measurement data to the ophthalmologic apparatus 1000. The external device may be any ophthalmic device, a device (reader) that reads information from a recording medium, or a device (writer) that writes information on a recording medium. Further, 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, for example, the processing unit 9.

  The reflex measurement projection system 6 and the reflex 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 a “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. The Z alignment system 1B is an example of the “second alignment system” according to the embodiment. The kerato measuring system 3 is an example of the “corneal shape measuring optical system” according to the embodiment. The kerato ring light source 32 is an example of the “kerato light source” according to the embodiment.

<Operation example>
An 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. FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic apparatus 1000 when the OCT measurement is performed after the reflex measurement. The storage unit 212 stores a computer program for implementing the processing illustrated in FIG. The main control unit 211 executes the processing shown in FIG. 7 by operating according to the computer program.

(S1: lens movement)
When the examiner performs a predetermined operation on the operation unit 280 in a state in which the subject's face is fixed to a face receiving unit (not shown), the main control unit 211 controls the lens moving mechanism 56D. Then, the relay lens 56 is moved to a lens position for reflex measurement on the optical axis of the anterior ocular segment observation system 5. In some embodiments, the main control unit 211 refers to the 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 control unit 211 executes the alignment. In step S2, Z alignment using the Z alignment system 1A is performed.

  Specifically, the main controller 211 turns on the Z alignment light source 11A and the XY alignment light source 21. In addition, the main control unit 211 turns on the anterior segment illumination light source 50. The processing unit 9 acquires an image signal of the anterior ocular segment image on the imaging surface of the image sensor 59 and causes the display unit 270 to display the anterior ocular segment image. Thereafter, the optical system shown in FIG. The inspection position is a position where the inspection of the eye E can be performed with sufficient accuracy. The subject's eye E is arranged at the examination position via the above-described alignment (alignment by the Z alignment system 1A and the XY alignment system 2 and the anterior eye observation system 5). The movement of the optical system is executed by the control unit 210 in accordance with an operation or instruction by a user or an instruction by the control unit 210. That is, movement of the optical system to the examination position of the eye E and preparation for performing objective measurement are performed. This alignment is performed as needed until the reflex measurement (refractive power measurement) is completed.

  Further, the main control unit 211 moves the reflex measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to a position of the origin (for example, a position corresponding to 0D) along each optical axis.

(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.

  Thereafter, the main control unit 211 turns on the kerattling light source 32. When light is output from the kerattling light source 32, a ring-shaped light beam for corneal shape measurement is projected on the cornea Cr of the eye E to be examined. The eye-refractive-power calculating unit 221 calculates a corneal curvature radius by performing arithmetic processing on the image acquired by the imaging element 59, and calculates corneal refractive power, corneal astigmatism, and corneal astigmatism from the calculated corneal curvature radius. Calculate the shaft angle. In the control unit 210, the calculated corneal refractive power and the like are stored in the storage unit 212. The operation of the ophthalmologic apparatus 1000 proceeds to step S4 according to an instruction from the main control unit 211 or a user operation or instruction to the operation unit 280. The kerato measurement may be performed simultaneously or continuously when a ring image is acquired in the next reflex measurement.

(S4: Refractive power measurement)
Subsequently, the main control unit 211 causes a refractive power measurement to be executed.

  In the reflex measurement, the main control unit 211 causes the eye E to project a ring-shaped measurement pattern light beam for the reflex measurement as described above. A ring image based on the return light of the measurement pattern light flux from the eye E is formed on the imaging surface of the imaging element 59. The main controller 211 determines whether a ring image based on the return light from the fundus oculi Ef detected by the image sensor 59 has been obtained. 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 image sensor 59 and determines whether the width of the image (the 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 a point (image) having a predetermined height (ring diameter) or more. Is also good.

  When it is determined that the ring image has been obtained, the eye-refractive-power calculating unit 221 analyzes the ring image based on the return light of the measurement pattern light beam projected on the subject's eye E by a known method, and calculates the provisional spherical power S and A temporary astigmatic power C is obtained. The main control unit 211 moves the reflex measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to the position (temporary distance) of the equivalent spherical power (S + C / 2) based on the obtained temporary spherical power S and astigmatic power C. (A position corresponding to a point). Thereafter, a ring image is acquired once again and analyzed to obtain a temporary spherical power S and a temporary astigmatic power C, and fine adjustment is made by moving from the position moved in the first measurement. After moving the liquid crystal panel 41 further from that position to the cloud fog position, the main control unit 211 controls the reflex measurement projection system 6 and the reflex measurement light receiving system 7 as the main measurement to obtain a ring image again. The main control unit 211 causes the eye-refractive-power calculating unit 221 to calculate the spherical power, the astigmatic power, and the astigmatic axis angle from the analysis result of the ring image obtained as described above and the movement amount of the focusing lens 74.

  Further, the eye refractive power calculation unit 221 obtains a position corresponding to the far point of the eye E (a position corresponding to the far point obtained by the main measurement) from the obtained spherical power and astigmatic power. The main control unit 211 moves the liquid crystal panel 41 to a position corresponding to the obtained far point. In the control unit 210, the position of the focusing lens 74, the calculated spherical power, and the like are stored in the storage unit 212. The operation of the ophthalmologic apparatus 1000 proceeds to step S5 in response to an instruction from the main control unit 211 or a user operation or instruction on the operation unit 280.

  When it is determined that a ring image cannot be obtained, the main control unit 211 considers the possibility that the eye is an abnormally refractive eye and sets the reflex measurement light source 61 and the focusing lens 74 in the minus power side (for example, at a preset step). -10D), and move to the plus side (for example, + 10D). The main control unit 211 controls the reflex measurement light receiving system 7 to detect a ring image at each position. When it is determined that the ring image cannot be obtained, the main control unit 211 executes a predetermined measurement error process. At this time, the operation of the ophthalmologic apparatus 1000 may shift to Step S5. In the control unit 210, information indicating that the reflex measurement result was not obtained is stored in the storage unit 212.

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

(S5: OCT measurement?)
Subsequently, the main control unit 211 determines whether to execute the OCT measurement. For example, the main control unit 211 determines whether to perform the OCT measurement by determining whether a predetermined operation is performed on the operation unit 280. In some embodiments, the main control unit 211 determines whether to execute the OCT measurement based on the inspection mode set before step S1.

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

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

(S7: fixation target switching)
Next, the main control unit 211 causes the liquid crystal panel 41 to display the dot chart or the cross chart shown in FIG. 6A. Accordingly, the fixation target FT2 or the fixation target FT3 is presented to the eye E.

(S8: alignment)
Subsequently, the main control unit 211 executes the alignment. In step S8, Z alignment using the Z alignment system 1B is performed.

  Specifically, the main controller 211 turns on the Z alignment light source 11B and the XY alignment light source 21. In addition, the main control unit 211 turns on the anterior segment illumination light source 50. The processing unit 9 acquires an image signal of the anterior ocular segment image on the imaging surface of the image sensor 59 and causes the display unit 270 to display the anterior ocular segment image. Thereafter, the optical system shown in FIG. The inspection position is a position where the inspection of the eye E can be performed with sufficient accuracy. The subject's eye E is arranged at the examination position through the above-described alignment (alignment by the Z alignment system 1B and the XY alignment system 2 and the anterior ocular segment observation system 5). The movement of the optical system is executed by the control unit 210 in accordance with an operation or instruction by a user or an instruction by the control unit 210. That is, movement of the optical system to the examination position of the eye E and preparation for performing objective measurement are performed. This alignment is performed as needed until the OCT measurement is completed.

(S9: OCT measurement)
Next, the main control unit 211 controls the OCT optical system 8 to execute OCT measurement.

  Specifically, the main control unit 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, a detection signal obtained by scanning the measurement light LS is sent to the image forming unit 222. The image forming unit 222 forms a tomographic image of the fundus oculi Ef from the obtained detection signals. Thus, the operation of the ophthalmologic apparatus 1000 ends (end).

  FIG. 7 illustrates an operation example in which the scan range of the OCT measurement is determined before the reflex measurement. However, the operation of the ophthalmologic apparatus 1000 according to the embodiment is not limited to the flow illustrated in FIG. In some embodiments, the ophthalmologic apparatus 1000 can specify a scan range of the measurement light LS in OCT measurement, and can set a working distance corresponding to the specified scan range. In some embodiments, the ophthalmologic apparatus 1000 can set a working distance corresponding to a scan range selected from a plurality of scan ranges.

  FIG. 8 shows another example of the operation of the ophthalmologic apparatus 1000. FIG. 8 is a flowchart illustrating an operation example of the ophthalmologic apparatus 1000 in a case where OCT measurement is performed after reflex measurement, similarly to FIG. The storage unit 212 stores a computer program for implementing the processing illustrated in FIG. The main control unit 211 executes the processing shown in FIG. 8 by operating according to the computer program.

(S21: Specify scan range)
The main control unit 211 receives designation of a scan range of the measurement light LS in OCT measurement. The main control unit 211 receives a scan range specified by a predetermined operation using the operation unit 280. In some embodiments, the designation of the scan range is performed by directly inputting a numerical value or information corresponding to the scan range to the operation unit 280. In some embodiments, the designation of the scan range is performed 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 specifies a working distance corresponding to the specified scan range. In some embodiments, the main control unit 211 specifies the working distance for OCT measurement by substituting the specified scan range into Equation (6). In some embodiments, the main control unit 211 specifies a working distance corresponding to the designated scan range from a plurality of working distances calculated in advance for the plurality of scan ranges.

(S22: lens movement)
When the examiner performs a predetermined operation on the operation unit 280 in a state in which the subject's face is fixed to a face receiving unit (not shown), the main control unit 211 executes the lens moving mechanism similarly to 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 control unit 211 executes alignment using the Z alignment system 1A, as in step S2.

(S24: 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.

  Thereafter, the main control unit 211 controls the kerato measurement system 3 to execute kerato measurement as in step S3.

(S25: refractive power measurement)
Subsequently, the main control unit 211 causes a refractive power measurement to be performed, as in step S4.

(S26: lens movement)
Subsequently, the main control unit 211 controls the lens moving mechanism 56D to move the relay lens 56 to a lens position for OCT measurement on the optical axis of the anterior ocular 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 lens position information in which a plurality of lens positions are stored in advance in association with a plurality of working distances. The lens moving mechanism 56D is controlled.

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

(S28: alignment)
Subsequently, the main control unit 211 performs the Z alignment using the Z alignment system 1B as in step S8. At this time, the main control unit 211 relatively moves the optical system with respect to the eye E so as to have the working distance specified in step S21. This alignment is performed as needed until the OCT measurement is completed.

(S29: OCT measurement)
Next, the main control unit 211 controls the OCT optical system 8 to execute the OCT measurement as in step S9. Thus, the operation of the ophthalmologic apparatus 1000 ends (end).

  As described above, while the objective lens 51 is shared between the reflex measurement optical system and the OCT optical system 8, the working distance is switched between the reflex measurement and the OCT measurement, so that a highly accurate An ophthalmologic apparatus capable of acquiring a measurement result and a highly accurate OCT measurement result can be provided.

  In particular, when the reflex measurement is performed, the working distance is set to the formula (4), so that the working distance is increased so as to reduce the influence of instrumental myopia, and the size of the kerato plate 31 is prevented from increasing. be able to. Thus, it is possible to provide an ophthalmologic apparatus that can acquire highly accurate reflex measurement results and kerato measurement results with a simple configuration.

  Further, when the OCT measurement is performed, the working distance is set to the expression (6), so that a scan result useful for analysis using standard data can be obtained. Thus, it is possible to provide an ophthalmologic apparatus that has a simple configuration and can assist useful judgment on the OCT measurement result using existing standard data.

  In the embodiment, the OCT optical system is described as an example of the inspection optical system having the optical scanner, but 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 using an optical scanner and detecting the returned light with a light receiving device. In some embodiments, the SLO optics obtains a frontal image 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 to the eye E, and an SLO light receiving system that receives the returned light.

  Even in this case, a scan result useful for analysis using the standard data can be obtained. Thus, it is possible to provide an ophthalmologic apparatus capable of assisting a useful judgment on the SLO measurement result by utilizing existing standard data with a simple configuration.

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

[First Modification]
In the above-described embodiment, the fixation target displayed on the liquid crystal panel 41 is switched to present the fixation target suitable for the examination or the like to the subject's eye E. However, the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. It is not limited.

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

  The fixation unit 40 provided in the fixation projection system 4 is provided with an illumination light source 45a, a target chart 46a, and a fixation light source 47a instead of the liquid crystal panel 41. The fixation light source 47a, the optotype chart 46a, and the relay lens 42 are arranged in this order from the illumination light source 45a toward the dichroic mirror 83. The optotype chart 46a is a transmissive optotype chart arranged between the illumination light source 45a and the eye E, and showing a landscape chart of the fixation targets FT1 and FT4. In some embodiments, the optotype chart 46a is a transparent film on which a landscape chart is printed. In some embodiments, the 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 performing reflex measurement, and illuminates the optotype chart 46a with light from the illumination light source 45a, thereby displaying a landscape chart (first fixation target) on the subject's eye E. Project. In addition, the main control unit 211 projects a bright point (dot target) (second fixation target) to the eye E by turning on the fixation light source 47a when performing OCT measurement. In some embodiments, the main control unit 211 turns off the fixation light source 47a when performing reflex measurement, and turns off the illumination light source 45a when performing OCT measurement. Thereby, a landscape chart is presented to the eye E when performing reflex measurement, and a bright spot is presented to the eye E when performing OCT measurement.

  In some embodiments, the fixation light source 47a blinks when performing OCT measurement. 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. I do. In some embodiments, the size of the luminescent spot can be changed by the main controller 211 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 modification of the embodiment. 10, the same reference numerals are given to the same parts as those in FIG. 1 or FIG. 9, and the description will be appropriately omitted.

  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 instead of the liquid crystal panel 41. Is provided. The half mirror 48b couples the optical path of the light from the illumination light source 45a with the optical path of the light from the fixation light source 47a. From the illumination light source 45a to the dichroic mirror 83, the half mirror 48b, the optotype chart 46a, and the relay lens 42 are arranged in this order. The relay lens 49b, the half mirror 48b, the optotype chart 46a, and the relay lens 42 are arranged in this order from the fixation light source 47a toward the dichroic mirror 83. The optotype chart 46a is a transmissive optotype chart arranged on the optical path connected by the half mirror 48b and showing a landscape chart 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 45a passes through 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 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 performing reflex measurement, and illuminates the optotype chart 46a with light from the illumination light source 45a, thereby displaying a landscape chart (first fixation target) on the subject's eye E. Project. In addition, the main control unit 211 projects a bright point (dot target) (second fixation target) to the eye E 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 and becomes a luminescent spot.

  In some embodiments, the main control unit 211 turns off the fixation light source 47a when performing reflex measurement, and turns off the illumination light source 45a when performing OCT measurement. Thereby, a landscape chart is presented to the eye E when performing reflex measurement, and a bright spot is presented to the eye E when performing OCT measurement.

  As described above, by providing the transmissive optotype chart 46a representing the landscape chart and controlling the illumination light source 45a and the fixation light source 47a according to the inspection mode, the visual acuity is adjusted to the eye to be examined in the reflex measurement. The fixation target can be presented so as not to cause the fixation target, and in the OCT measurement, the fixation target can be presented such that a desired part of the subject's eye is arranged at a predetermined measurement position according to a measurement part or the like.

[Third Modification]
In the above-described embodiment or its modification, the case where the fixation target is projected using one target chart at the time of reflex measurement and at the time of OCT measurement has been described. However, the configuration of the ophthalmologic apparatus according to the embodiment is not limited thereto. It is not done.

  FIG. 11 shows a configuration example of a fixation projection system 4 according to a third modification of the embodiment. 11, the same reference numerals are given to the same parts as those in FIG. 1, and the description will be appropriately omitted.

  The fixation projection system 4 projects a first fixation projection system for projecting the landscape chart to the eye E, and a bright point (dot target, cross target) having a smaller viewing angle than the landscape chart to the eye E. 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 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 arranged between the illumination light source 45c and the subject's eye E and showing a landscape chart such as the fixation targets FT1 and FT4. In some embodiments, the optotype chart 46c is a transparent film on which a landscape chart is printed. The optotype chart 48c is a transmissive optotype chart that is arranged between the illumination light source 47c and the eye E to be inspected and displays dot optotypes such as fixation targets FT2 and FT3 and cross optotypes. In some embodiments, the optotype chart 48c is a transparent film on which dot optotypes and cross optotypes are printed.

  The main control unit 211 controls the first fixation projection system and the second fixation projection system to project at least one of the landscape chart and the bright spot (dot target, cross target) to the eye E. Specifically, the main control unit 211 turns on the illumination light source 45c when performing the reflex measurement, and illuminates the optotype chart 46c with light from the illumination light source 45c to thereby provide a landscape chart (first fixation target). To the eye E to be examined. Further, the main control unit 211 turns on the illumination light source 47c when performing OCT measurement, and illuminates the optotype chart 48c with light from the illumination light source 47c to thereby provide a bright point (dot optotype, cross optotype) or The cross target (second fixation target) is projected onto the eye E to be examined. In some embodiments, the main control unit 211 turns off the illumination light source 47c when performing reflex measurement, and turns off the illumination light source 45c when performing OCT measurement. Thereby, a landscape chart is presented to the eye E when performing reflex measurement, and a bright spot is presented to the eye E when performing OCT measurement. In some embodiments, the illumination light source 47c blinks when performing OCT measurement.

[Fourth Modification]
FIG. 12 shows a configuration example of a fixation projection system 4 according to a fourth modification of the embodiment. In FIG. 12, the same parts as those in FIG. 1 or FIG.

  The fixation projection system 4 includes a first fixation projection system for projecting the landscape chart to the eye E, and a bright point having a smaller viewing angle than the landscape chart to the eye E, as in FIG. 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 the reflex measurement, turns on the illumination light source 45c, By illuminating the optotype chart 46c with light from 45c, a landscape chart (first fixation target) is projected onto the eye E. In addition, 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 performs illumination. By illuminating the optotype chart 48c with light from the light source 47c, a bright point (dot optotype, cross optotype) (second fixation target) is projected onto the eye E.

  In some embodiments, the main control unit 211 turns off the illumination light source 47c when performing reflex measurement, and turns off the illumination light source 45c when performing OCT measurement. Thereby, a landscape chart is presented to the eye E when performing reflex measurement, and a bright spot is presented to the eye E when performing OCT measurement. In some embodiments, the illumination light source 47c blinks when performing OCT measurement.

[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 moving mechanism selectively moves the first fixation projection system and the second fixation projection system to the optical path of the fixation projection system 4 by moving the first fixation projection system and the second fixation projection system. .

  For example, the main control unit 211 selectively arranges the first fixation projection system and the second fixation projection system on the optical path of the fixation projection system 4 by controlling the moving mechanism. That is, the illumination light source and the optotype chart for reflex measurement and the illumination light source and the optotype chart for OCT measurement are selectively arranged on the optical path of the fixation projection system 4. The main control unit 211 controls the moving mechanism so that the first fixation projection system is arranged in the optical path of the fixation projection system 4 when performing the reflex measurement, turns on the illumination light source 45c, and controls the illumination light source 45c. By illuminating the optotype chart 46c with this light, the landscape chart (first fixation target) is projected onto the eye E to be inspected. 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 the OCT measurement, turns on the illumination light source 47c, By illuminating the optotype chart 48c with light from 47c, a bright point (dot optotype) or a cross optotype (second fixation target) is projected onto the eye E.

  In some embodiments, the moving 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, thereby moving the fixation projection system 4. The first fixation projection system and the second fixation projection system are selectively arranged on the optical path.

  As described above, the transmissive optotype chart 46c showing the landscape chart and the transmissive optotype chart 48c showing the dot optotype and the cross optotype are provided. By controlling the light sources 45a and 47c, in the reflex measurement, a fixation target is presented to the subject's eye so as not to adjust the visual acuity, and in the OCT measurement, a desired part of the subject's eye is arranged at a predetermined measurement position according to a measurement part or the like. A fixation target can be presented to the user.

[Sixth Modification]
In the above-described embodiment or its modification, the Z alignment system 1A for reflex measurement and the Z alignment system 1B for OCT measurement are provided, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. is not.

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

  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 each of two or more positions of the subject's eye E on the optical axis of the objective lens 51 with alignment light from a direction at an angle that can be changed with respect to the optical axis. The return light from the optometry E is received. The 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. In some embodiments, the angle changing mechanism can change the irradiation angle and the reflection direction under the control of the main control unit 211a (the control unit 210a) (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), and performs the alignment. The reflection direction is changed around a predetermined position on the optical axis of the return light of the light.

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

  The configuration of the processing system shown in FIG. 14 is different from the configuration of the processing system shown in FIG. 5 in that a Z alignment system 1a is provided instead of Z alignment systems 1A and 1B, and processing is performed in place of processing unit 9. The point is that a portion 9a is provided. The Z alignment system 1a includes an alignment light source 11, an imaging lens 12, and a line sensor 13. Z alignment system 1a operates similarly to 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. The control unit 210a includes a main control unit 211a and a storage unit 212a. The storage unit 212a is different from the storage unit 212 in that a program and control information for controlling the angle changing mechanism 14 described below 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 irradiation optical axis of the alignment light connecting the arrangement position of the subject's eye on the optical axis of the objective lens 51 and the alignment light source 11. In addition, the angle changing mechanism 14 changes the angle between the optical axis of the objective lens 51 and the reflected optical axis of the alignment light connecting the arrangement 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 is changed to the first irradiation angle by the angle changing mechanism 14 when performing the reflex measurement. Thereby, alignment in the Z direction can be performed on the subject's eye E at the first arrangement position on the optical axis of the objective lens 51.

  Further, when performing OCT measurement, 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 changed by the angle changing mechanism 14 to the second irradiation angle. Thereby, the alignment in the Z direction can be performed on the eye E at the second arrangement position different from the first arrangement position on the optical axis of the objective lens 51.

  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, and a detailed description thereof will be omitted.

  According to the sixth modification, the configuration of the Z alignment system can be simplified as compared with the embodiment.

[Seventh Modification]
FIG. 15 illustrates a configuration example of an optical system of an ophthalmologic apparatus according to a seventh modification example of the embodiment. 15, 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 1000b according to the seventh modification is different 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. is there. The anterior eye cameras 15A and 15B image the anterior eye of the eye E to be inspected. The anterior eye cameras 15A and 15B are, for example, video cameras that shoot moving images at a predetermined frame rate. The anterior segment cameras 15A and 15B photograph the anterior segment substantially simultaneously from different directions.

  The number of anterior eye cameras may be any number equal to or more than two, but may be any configuration as long as the anterior eye part can be photographed substantially simultaneously from two different directions. Further, one anterior eye camera may be the image sensor 59 in the anterior eye observation system 5.

  “Substantially simultaneous” indicates that, in imaging by two or more anterior eye cameras, a shift in imaging timing that allows negligible eye movement is allowed. Thereby, an image when the eye E is at the same position (direction) can be acquired by two or more anterior eye cameras.

  FIG. 16 illustrates a configuration example of a processing system of an ophthalmologic apparatus according to a seventh modified example of the embodiment. In FIG. 16, the same parts as those in FIG.

  The configuration of the processing system shown in FIG. 16 differs from the configuration of the processing system shown in FIG. 5 in that anterior eye cameras 15A and 15B are provided instead of the Z alignment systems 1A and 1B, and The difference is that a processing unit 9b is provided instead, and that an arithmetic processing unit 220b is provided instead of the arithmetic processing unit 220.

  The processing unit 9b is different from the processing unit 9 in that a control unit 210b is provided instead of the control unit 210. The control unit 210a includes a main control unit 211b and a storage unit 212b. The storage unit 212b is different from the storage unit 212 in that a program 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 220b is different from the arithmetic processing unit 220 in that a data processing unit 223b is provided instead of the data processing unit 223. As disclosed in Japanese Patent Application Laid-Open No. 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, thereby forming an anterior eye. The characteristic position corresponding to the characteristic 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 specifies the position of the eye E based on the specified characteristic position. In this example, the position of the pupil center approximates the position of the eye E to be examined. The distance between the corneal vertex and the pupil in the eye E or the distance between the corneal vertex and the pupil in a standard eye (model eye, average value, etc.) is used to determine the position of the corneal vertex. Can be obtained as the position of the subject's eye E.

  The main control unit 211b executes the Z alignment based on the position of the characteristic region of the anterior eye part specified by the data processing unit 223b.

  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, and a detailed description will be omitted.

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

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

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

  The configuration of the ophthalmologic apparatus 1000d according to the eighth modification is different from the configuration of the ophthalmologic apparatus 1000a according to the sixth modification in that a Z alignment system 1c is provided instead of the Z alignment system 1a, and a Z alignment system is provided. 1c 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, similarly 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 among the alignment light source 11, the imaging lens 12, and the line sensor 13.

  FIG. 18 illustrates a configuration example of a processing system of an ophthalmologic apparatus according to an eighth modification of the embodiment. In FIG. 18, the same parts as those in FIG.

  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 used instead of the processing unit 9a. It is a point provided. Z alignment system 1c operates similarly to Z alignment system 1a.

  The processing unit 9c is different 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 is different from the storage unit 212a in that a program and control information for controlling a moving mechanism 14c described below 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 14c moves the Z alignment system 1c 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, the imaging lens 12, and the line sensor 13.

  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 reflex measurement, and performs the objective lens 51 when performing the OCT measurement. Then, the Z alignment system 1c is moved to a second position where the alignment light is applied to the second arrangement position on the optical axis.

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

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

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

  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, and a detailed description thereof will be omitted.

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

[Ninth Modification]
In the above-described embodiment or its modified example, the case where the alignment light source or the line sensor is moved or the irradiation angle of the alignment light or the like is changed is described. However, the configuration of the ophthalmologic apparatus according to the embodiment is not limited thereto. Not something.

  FIG. 19 illustrates 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 the description will be appropriately omitted.

  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 having a wide light distribution angle. The alignment light source 11d 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 alignment light to the eye E arranged at the first arrangement position when performing the reflex measurement, and based on the light receiving result of the return light from the eye E, the moving mechanism 200 is controlled. Thereby, alignment in the Z direction can be performed on 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 causes the alignment light source 11d to irradiate alignment light to the eye E arranged at the second arrangement position when performing the OCT measurement, and based on the result of receiving the return light from the eye E. The moving mechanism 200 is controlled. Thereby, the alignment in the Z direction can be performed on the eye E at the second arrangement position different from the first arrangement position on the optical axis of the objective lens 51.

  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, and a detailed description thereof will be omitted.

  As described above, according to the ninth modification, even when performing reflex measurement or OCT measurement, the eye E is irradiated with alignment light, and the returned light is transmitted through the imaging lens 12. The light can be received by the line sensor 13 via the control unit. Thereby, the configuration of the ophthalmologic apparatus can be simplified as compared with the embodiment.

[Action / Effect]
The operation and effect of the ophthalmologic apparatus according to the embodiment and the control method thereof 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 (reflection measurement projection system 6, a reflex measurement light receiving system 7), and an inspection optical system (OCT). The optical system 8 includes an SLO optical system), a moving mechanism (200), and control units (210, 210a to 210c, a main control unit 211, and main control units 211a to 211c). The refractive power measuring optical system projects light to the eye to be inspected (E) via the objective lens, and detects light returned from the eye to be inspected. The inspection optical system has an optical scanner (88), deflects light from a light source by the optical scanner, projects the light deflected by the optical scanner to the eye to be inspected via the objective lens, and returns light from the eye to be inspected. Is detected. The moving mechanism moves the objective lens, the refractive power measuring optical system, and the inspection optical system in the optical axis direction of the objective lens. The control unit determines that the working distance to the eye to be examined is the first working distance (WDref) when performing the refractive power measurement (reflection measurement) using the refractive power measurement optical system, and the working distance when performing the examination using the examination optical system. Is controlled to be the second working distance (WDoct).

  According to such a configuration, the working distance is changed between the refractive power measurement and the inspection using the inspection optical system while the objective lens is shared in at least the refractive power measurement optical system and the inspection optical system. With this configuration, it is possible to acquire a highly accurate refractive power measurement result and a highly accurate inspection result using the inspection optical system.

  An ophthalmologic apparatus according to some embodiments includes a relay lens (56) that relays light from an anterior eye of an eye to be examined and an imaging element (5) that receives light passing through the relay lens. An observation system (5) is included. The control unit moves the relay lens to the first lens position on the optical axis of the anterior ocular segment observation system when performing the refractive power measurement, and performs the inspection (inspection using the inspection optical system) of the anterior ocular segment observation system. The relay lens is moved 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 a signal from the anterior eye on the imaging surface of the imaging element. Thus, the focused anterior ocular segment image can be observed even at the time of 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 to an eye to be examined. The control unit projects the first fixation target (FT1) to the subject's eye when performing the refractive power measurement, and the second fixation target having a narrower viewing angle than the first fixation target when performing the inspection (inspection using the inspection optical system). The fixation projection system is controlled so that the targets (FT2, FT3) are projected onto the eye to be examined.

  According to such a configuration, a fixation target having a different visual angle is presented to the subject's eye in accordance with the refractive power measurement or the examination using the examination optical system, so that the subject's eye does not adjust the vision in the refractive power measurement. The fixation target can be presented so that a desired part of the eye to be inspected is arranged in a predetermined examination place in the examination using the examination optical system.

  In the ophthalmologic apparatus 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 ensure that the eye to be inspected gazes at the second fixation target with a simple configuration.

  An ophthalmologic 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 the first arrangement position of the subject's eye 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 returns the return light from the subject's eye. Receive light. The second alignment system irradiates the second arrangement position of the subject's eye on the optical axis of the objective lens with alignment light from a direction forming a second angle with respect to the optical axis, and receives return light from the subject's eye. I do. 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 is obtained by the second alignment system when performing the inspection (inspection using the inspection optical system). The moving mechanism is controlled based on the light reception result.

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

  An ophthalmologic 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 subject's eye 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 subject's eye. Receives light. The angle changing mechanism changes the angle. The control unit controls the moving mechanism based on the light receiving result obtained by the alignment system in a state where the angle is changed to the first irradiation angle by the angle changing mechanism when performing the refractive power measurement, and performs the inspection (inspection using the inspection optical system). When performing (2), the moving mechanism is controlled based on the light receiving result obtained by the alignment system in a state where the second irradiation angle is changed by the angle changing mechanism.

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

An ophthalmologic apparatus according to some embodiments includes a corneal shape measurement optical system (keratometry system 3). The corneal shape measurement optical system projects an arc-shaped or circumferential measurement pattern on the cornea of the eye from the outer edge side of the objective lens around the optical axis of the objective lens to the eye to be inspected. The return light from the cornea is detected. The corneal shape measurement optical system is disposed between the kerato light source (kerat ring light source 32) and the kerato light source and the eye to be inspected, and is formed in an arc shape or a circumference around the optical axis of the objective lens, and is provided with a kerato light source. A kerato plate (31) on which a light transmitting part that transmits light is formed. When the height of the image based on the measurement pattern with respect to the optical axis of the objective lens is h, the radius of curvature of the cornea of the eye to be examined is R, and the length from the optical axis of the objective lens to the translucent portion is H, the control unit Controls the movement mechanism such that the first working distance is ((Hh) / 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 reducing the influence of instrumental myopia by increasing the working distance. Thus, it is possible to provide an ophthalmologic apparatus that can acquire a highly accurate refractive power measurement result and a kerato measurement result with a simple configuration.

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

  According to such a configuration, it is possible to measure the shape of the cornea of 3 mm, so that the corneal shape measurement useful for corneal shape analysis can be performed.

  In the ophthalmologic apparatus according to some embodiments, the distance from the pupil of the subject's eye to the fundus is Le, the distance from the anterior corneal surface to the pupil is La, and the distance from the anterior surface of the keratoplate to the principal surface of the objective lens is Lk. When the scan range of the optical scanner is SA square and the scan diameter of the objective lens for scanning the scan range is D, the control unit determines that the second working distance is ((Le × D) / SA− (La + Lk). )) To control the moving mechanism.

  According to such a configuration, since the SA square area can be scanned, it is compared with the existing standard data obtained by scanning the SA square area, and the inspection result is obtained by utilizing the existing standard data. To help make useful decisions

  In the ophthalmologic apparatus according to some embodiments, the scan range is a range of (6 ×） 2) mm square in the fundus of the subject's eye.

  According to such a configuration, it is possible to use the existing standard data generally acquired in the fundus of the eye to be examined to assist a useful judgment on the test result.

  In the ophthalmologic apparatus according to some embodiments, the inspection optical system divides the light (L0) from the OCT light source (101) into the reference light (LR) and the measurement light (LS), and divides the measurement light by an optical scanner. An OCT optical system (8) that deflects and projects the deflected measurement light onto the eye to be inspected and detects interference light (LC) between the return light of the measurement light from the eye and the reference light.

  According to such a configuration, it is possible to provide an ophthalmologic apparatus capable of scanning a desired scan range on the fundus and acquiring a useful tomographic analysis result.

  In the ophthalmologic apparatus according to some embodiments, the inspection optical system deflects light from the SLO light source by an optical scanner, projects the deflected light to the subject's eye, and receives return light from the subject's eye. Including system.

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

  Some embodiments include an objective lens (51) and a refractive power measurement optical system (ref measurement projection system 6) for projecting light to the eye (E) through the objective lens and detecting return light from the eye. , A reflex measurement light receiving system 7) and an optical scanner (88). The light from the light source is deflected by the optical scanner, and the light deflected by the optical scanner is projected on the eye to be inspected through the objective lens. Inspection optical system (OCT optical system 8, SLO optical system) for detecting the return light from the lens, and a moving mechanism (200) 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 control unit (210, 210a to 210c, main control unit 211, main control units 211a to 211c) for controlling a moving mechanism. The control method of the ophthalmologic apparatus includes a first control step in which the control unit controls the moving mechanism so that a working distance to the subject's eye becomes a first working distance (WDref); In the state set as (1), the first measurement step of executing the refractive power measurement (reflection measurement) using the refractive power measurement optical system, and the control unit causes the working distance to the eye to be examined to be the second working distance (WDoct). A second control step of controlling the moving mechanism, and a second measurement step of performing an inspection (OCT measurement) using an inspection optical system in a state where the working distance is set to the second working distance in the second control step. ,including.

  According to such control, the working distance is changed between the refractive power measurement and the inspection using the inspection optical system at least in an ophthalmologic apparatus in which the objective lens is shared by at least the refractive power measurement optical system and the inspection optical system. An accurate refractive power measurement result and a highly accurate inspection result using the inspection optical system can be obtained.

  In the control method of the ophthalmologic 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 inspected, and an imaging device (59) that receives light passing through the relay lens. )), The first control step further moves the relay lens to the first lens position on the optical axis of the anterior eye observation system, and the second control step includes: Further, the relay lens is moved to the second lens position on the optical axis of the anterior ocular segment observation system.

  According to such control, it is possible to form a signal from the anterior segment on the imaging surface of the image sensor even when the working distance is changed in accordance with the bending force measurement or the inspection using the inspection optical system. Thus, the focused anterior ocular segment image can be observed even at the time of refractive power measurement or inspection using an inspection optical system.

  In a control method for an ophthalmologic apparatus according to some embodiments, the ophthalmologic apparatus includes a fixation projection system (4) that projects a fixation target on the eye to be inspected, and further includes a first fixation target in the first control step. The fixation projection system is controlled so as to project (FT1) to the eye to be inspected. In the second control step, a second fixation target (FT2, FT3) having a narrower viewing angle than the first fixation target is further applied to the eye to be examined. The fixation projection system is controlled to project.

  According to such control, a fixation target is presented to the eye to be inspected so as not to adjust the visual acuity in the refractive power measurement, and a desired part in the eye to be inspected is arranged in a predetermined inspection place in the inspection using the inspection optical system. Can be presented with a fixation target.

  In the method for controlling an ophthalmologic apparatus according to some embodiments, the ophthalmic apparatus aligns a first position of the subject's eye on the optical axis of the objective lens from a direction forming a first angle with respect to the optical axis. A first alignment system (Z-alignment system 1A) for irradiating light and receiving return light from the eye to be inspected; and a second alignment position for the eye to be inspected on the optical axis of the objective lens, A second alignment system (Z alignment system 1B) that irradiates alignment light from two directions and receives return light from the subject's eye. In the first control step, the second alignment system is obtained by the first alignment system. The moving mechanism is controlled based on the light receiving result. 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, alignment can be performed with high precision in each of the refractive power measurement and the inspection using the inspection optical system.

<Others>
The embodiments described above are merely examples for embodying the present invention. Those who intend to implement the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the present invention.

  Further, in the above embodiment, the case where the ophthalmologic apparatus 1000 performs the 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.

1, 1A, 1B, 1a to 1d Z alignment system 2 XY alignment system 3 Kerato measurement system 4 Fixation projection system 5 Anterior eye observation system 6 Ref measurement projection system 7 Ref measurement light receiving system 8 OCT optical system 9, 9a, 9b Processing unit 14 Angle changing mechanism 31 Kerato board 32 Kerato ring 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 apparatus

Claims (16)

An objective lens,
Projecting light to the eye to be examined via the objective lens, a refractive power measuring optical system for detecting return light from the eye to be examined,
Having an optical scanner, deflecting light from a light source by the optical scanner, projecting the light deflected by the optical scanner to the subject's eye via the objective lens, and detecting return light from the subject's eye Inspection optics,
A moving mechanism that moves 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 the refractive power measurement using the refractive power measurement optical system, the working distance to the eye to be inspected becomes the first working distance, and when performing the inspection using the inspection optical system, the working distance becomes the second working distance. A control unit for controlling the moving mechanism,
Ophthalmic devices including. A relay lens that relays light from the anterior segment of the subject's eye, and includes an anterior segment observation system including an imaging device that receives light passing through the relay lens,
The controller moves the relay lens to a first lens position on the optical axis of the anterior ocular segment observation system when performing the refractive power measurement, and moves the relay lens on the optical axis of the anterior ocular segment observation system when performing the inspection. The ophthalmologic apparatus according to claim 1, wherein the relay lens is moved to a second lens position. Including a fixation projection system that projects a fixation target on the eye to be examined,
The control unit projects a first fixation target to the subject's eye when performing the refractive power measurement, and a second fixation target having a narrower viewing angle than the first fixation target to the subject's eye when performing the test. The ophthalmologic apparatus according to claim 1, wherein the fixation projection system is controlled to perform projection. The ophthalmologic apparatus according to claim 3, wherein the second fixation target is a dot target or a cross target. 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 a return light from the eye to be inspected is received. 2 alignment system,
Including
The control unit controls the moving mechanism based on the light reception result obtained by the first alignment system when performing the refractive power measurement, and controls the movement mechanism based on the light reception result obtained by the second alignment system when performing the inspection. The ophthalmologic apparatus according to any one of claims 1 to 4, wherein the movement mechanism is controlled based on the movement. For each of two or more arrangement positions of the subject's eye on the optical axis of the objective lens, alignment light is irradiated from a direction forming a changeable angle with respect to the optical axis, and return light from the subject's eye An alignment system that receives light
An angle changing mechanism for changing the angle,
Including
The control unit controls the moving mechanism based on a light receiving result obtained by the alignment system in a state where the angle is changed to the first irradiation angle by the angle changing mechanism when performing the refractive power measurement, and performs the inspection. The moving mechanism is controlled based on a light reception result obtained by the alignment system when the angle is changed to the second irradiation angle by the angle changing mechanism. An ophthalmologic apparatus according to the item. An arc-shaped or circumferential measurement pattern is projected from the outer edge side of the objective lens on the cornea of the subject's eye around the optical axis of the objective lens to the subject's eye, and the cornea of the subject's eye is projected through the objective lens. Includes a corneal shape measurement optical system that detects return light from
The corneal shape measurement optical system,
A kerato light source,
A kerato plate disposed between the kerato light source and the subject's eye, and formed with a light-transmitting portion formed in an arc or a circle around the optical axis of the objective lens and transmitting light from the kerato light source When,
Including
The height of the image based on the measurement pattern with respect to the optical axis of the objective lens is h, the radius of the corneal curvature of the eye to be inspected is R, and the length from the optical axis of the objective lens to the light transmitting portion is H. When
The control unit controls the first working distance to be ((H−h) / tan (2 × sin ⁻¹ (h / R)) − (R−√ (R ² −h ² ))). The ophthalmologic apparatus according to any one of claims 1 to 6, which controls a moving mechanism. The ophthalmologic apparatus according to claim 7, wherein the height of the image based on the measurement pattern is 1.5 mm. The distance from the pupil to the fundus of the eye to be examined is Le, the distance from the anterior corneal surface to the pupil is La, the distance from the anterior surface of the keratoplate to the main surface of the objective lens is Lk, and the scan range by the optical scanner is Is SA square, and the scanning diameter of the objective lens for scanning the scan range is D, and the control unit determines that the second working distance is ((Le × D) / SA− (La + Lk)). The ophthalmologic apparatus according to claim 7, wherein the movement mechanism is controlled to be as follows. The ophthalmologic apparatus according to claim 9, wherein the scan range is a range of (6 × ミ リ メ ー ト ル 2) mm square in a 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 to the eye to be inspected, and The ophthalmologic apparatus according to any one of claims 1 to 10, further comprising an OCT optical system configured to detect an interference light between the reference light and the return light of the measurement 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 to the eye to be inspected, and receives return light from the eye to be inspected. The ophthalmologic apparatus according to any one of claims 1 to 11, wherein An objective lens,
Projecting light to the eye to be examined via the objective lens, a refractive power measuring optical system for detecting return light from the eye to be examined,
Having an optical scanner, deflecting light from a light source by the optical scanner, projecting the light deflected by the optical scanner to the subject's eye via the objective lens, and detecting return light from the subject's eye Inspection optics,
A moving mechanism that moves 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 for controlling the moving mechanism;
A method of controlling an ophthalmologic apparatus, comprising:
A first control step in which the control unit controls the moving mechanism so that a working distance to the eye to be examined becomes a first working distance;
In a state where the working distance is set to the first working distance in the first control step, a first measurement step of performing a refractive power measurement using the refractive power measurement optical system;
A second control step in which the control unit controls the moving mechanism so that a working distance to the eye to be examined becomes a second working distance;
A second measurement step of performing an inspection using the inspection optical system in a state where the working distance is set to the second working distance in the second control step;
A control method for an ophthalmologic apparatus including: The ophthalmic apparatus includes a relay lens that relays light from the anterior segment of the subject's eye, and an anterior ocular segment observation system that includes an imaging device that receives light passing through the relay lens.
In the first control step, further, the relay lens is moved to a first lens position on an optical axis of the anterior ocular segment observation system,
The control method of the ophthalmologic apparatus according to claim 13, wherein, in the second control step, the relay lens is further moved to a second lens position on an optical axis of the anterior ocular segment observation system. The ophthalmic apparatus includes a fixation projection system that projects a fixation target to the eye to be inspected,
In the first control step, further, the fixation projection system is controlled to project a first fixation target to the eye to be inspected,
The second control step further controls the fixation projection system so as to project a second fixation target having a narrower viewing angle than the first fixation target onto the subject's eye. A method for controlling an ophthalmologic apparatus according to claim 14. The ophthalmic apparatus,
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 a return light from the eye to be inspected is received. 2 alignment system,
Including
In the first control step, the moving mechanism is controlled based on a light reception result obtained by the first alignment system,
The ophthalmologic apparatus according to any one of claims 13 to 15, wherein, in the second control step, the moving mechanism is controlled based on a light reception result obtained by the second alignment system. Control method.

Images