JP2019213752A - Ophthalmologic apparatus and control method of ophthalmologic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a new technique for realizing miniaturization and cost reduction of an ophthalmologic apparatus without affecting measurement accuracy. An ophthalmologic apparatus includes an objective lens, an inspection optical system, a focusing lens, an optical scanner, and a control unit. The inspection optical system irradiates the eye to be inspected with the light from the light source through the objective lens and detects the return light from the eye to be inspected. The focusing lens is arranged between the objective lens and the inspection optical system, and is movable in the optical axis direction of the objective lens. The optical scanner is arranged between the focusing lens and the inspection optical system so that the deflection surface is located at the focal position of the focusing lens, and is movable in the optical axis direction. The control unit performs focusing control by moving the focusing lens and the optical scanner so that the positional relationship between the focusing lens and the optical scanner is maintained. [Selection diagram] Fig. 3

Description

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

  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 examination, measurement of refractive power of an eye to be inspected, and measurement using optical coherence tomography. In such an ophthalmologic apparatus, focusing control is performed by operating a plurality of focusing lenses provided in each optical system in cooperation with each other, and downsizing and control simplification are achieved.

JP 2017-136215 A

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

  When a small scanning device is used as the optical scanner, the effective diameter on the deflection surface becomes small. Accordingly, in order to project a light beam on the pupil of the eye to be examined with the same diameter as that of the related art, it is necessary to increase the optical magnification of the optical system from the optical scanner to the pupil.

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

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

  A first aspect of some embodiments includes an objective lens, an inspection optical system configured to irradiate light from a light source to the subject's eye via the objective lens, and to detect return light from the subject's eye, and the objective lens A focusing lens disposed between the focusing optical system and the inspection optical system, the focusing lens being movable in an optical axis direction of the objective lens, and being deflected to a focal position of the focusing lens between the focusing lens and the inspection optical system. An optical scanner that is disposed so that a surface is located and is movable in the optical axis direction, and moves the focusing lens and the optical scanner such that a positional relationship between the focusing lens and the optical scanner is maintained. And a control unit for performing focusing control.

  According to a second aspect of some embodiments, in the first aspect, the optical device is disposed between the inspection optical system and the optical scanner, and guides light from the inspection optical system to the optical scanner, and guides light from the inspection optical system to the optical scanner. A deflection member that deflects the returned light in the optical axis direction and guides the returned light to the inspection optical system, wherein the control unit moves the focusing lens, the optical scanner, and the deflection member in the optical axis direction. The focusing control is performed by moving.

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

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

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

  According to a sixth aspect of some embodiments, in the fifth aspect, a second focusing unit that includes the focusing lens, the optical scanner, and the collimator lens, and that holds a second end of the light guide member; A second moving mechanism that moves a second focusing unit in the optical axis direction, wherein the control unit controls the second moving mechanism.

  In a seventh aspect of some embodiments, in the fifth aspect or the sixth aspect, the inspection optical system divides light from a light source into reference light and measurement light, and projects the measurement light to the eye to be inspected. An optical path that includes an interference optical system that detects interference light between the return light of the measurement light from the eye to be examined and the reference light, and that changes at least one of an optical path length of the measurement light and an optical path length of the reference light. A length changing mechanism, wherein the control unit controls the optical path length changing mechanism according to the amount of movement of the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens in the optical axis direction. By controlling, at least one of the optical path length of the measurement light and the optical path length of the reference light is changed.

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

  A ninth aspect of some embodiments includes an objective lens, an inspection optical system configured to irradiate light from a light source to the subject's eye via the objective lens, and to detect return light from the subject's eye, and the objective lens A focusing lens disposed between the focusing optical system and the inspection optical system, the focusing lens being movable in an optical axis direction of the objective lens, and being deflected to a focal position of the focusing lens between the focusing lens and the inspection optical system. An optical scanner arranged so that a surface is located and movable in the optical axis direction. A control method of the ophthalmologic apparatus, wherein a focusing control step of performing focusing control by moving the focusing lens and the optical scanner such that a positional relationship between the focusing lens and the optical scanner is maintained; After the focusing control step, a measuring step of irradiating the eye to be inspected with the light of the inspection optical system deflected by the optical scanner and detecting a return light thereof is included.

  In a tenth aspect of some embodiments, in the ninth aspect, the ophthalmic apparatus is disposed between the inspection optical system and the optical scanner, and guides light from the inspection optical system to the optical scanner, A deflecting member that deflects the return light from the optical scanner in the optical axis direction and guides the returned light to the inspection optical system, wherein the focusing control step includes moving the focusing lens, the optical scanner, and the deflecting member. Let it.

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

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

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 showing an example of composition of an optical system of an ophthalmologic apparatus concerning an 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 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 which shows the flow of the example of an operation | movement of the ophthalmologic apparatus which concerns on 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 showing an example of composition of an optical system of an ophthalmologic apparatus concerning an embodiment. It is the schematic which shows the flow of the example of an operation | movement of the ophthalmologic apparatus which concerns on embodiment.

  An example of an embodiment of an ophthalmologic apparatus and a control method of the ophthalmologic apparatus 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 includes an examination optical system, and can execute examination (measurement) of the subject's eye by irradiating the subject's eye with light and detecting the return light. In some embodiments, the inspection optical system performs measurement and imaging using optical coherence tomography (hereinafter, OCT).

  Hereinafter, in the embodiment, a case where a swept source type OCT technique is used in measurement or the like using OCT will be described in detail, but an ophthalmologic apparatus using another type (for example, a spectral domain type) OCT will be described. It is also possible to apply the configuration according to the embodiment.

  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 keratometry, intraocular pressure measurement, fundus photography, and the like.

  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. .

[First Embodiment]
<Configuration of optical system>
1 to 3 show examples of the configuration of the optical system of the ophthalmologic apparatus according to the first embodiment. FIG. 1 illustrates an overall configuration example of an optical system of an ophthalmologic apparatus 1000 according to the first embodiment. FIG. 2 illustrates a configuration example of an optical system of the OCT unit 100 in FIG. FIG. 3 illustrates a configuration example of an optical system of the focusing unit 80 in FIG. In FIG. 3, only a part of the optical system is illustrated for convenience of explanation.

  The ophthalmologic apparatus 1000 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 paths 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. 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)
The Z alignment system 1 projects light (infrared light) for performing alignment in the optical axis direction (front-back direction, Z direction) of the anterior ocular segment observation system 5 to the eye E to be inspected. The light output from the Z alignment light source 11 is projected onto the cornea Cr of the subject's eye E, reflected by the cornea Cr, and imaged by the imaging lens 12 on the sensor surface of the line sensor 13. When the position of the corneal vertex changes in the optical axis direction of the anterior ocular segment observation system 5, the light projection position on the sensor surface of the line sensor 13 changes. The processing unit 9 obtains the position of the apex of the cornea of the eye E based on the light projection position on the sensor surface of the line sensor 13, and controls the mechanism for moving the optical system based on this to perform Z alignment.

(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 so that the end face of the optical fiber f1 is conjugate to the measurement site (the fundus oculi Ef or the anterior eye) 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 is converted into a parallel light beam by the collimator lens unit 89. The measurement light LS converted into the parallel light flux passes through the focusing unit 80, the relay lens 85, and the reflection mirror 84, and is reflected by the dichroic mirror 83.

  The focusing unit 80 includes a focusing lens 87 and an optical scanner 88. An optical scanner 88 is arranged between the collimator lens unit 89 and the focusing lens 87. The focusing lens 87 is movable in the optical axis direction (the optical axis direction of the objective lens 51, the optical axis direction of the OCT optical system 8). For example, the focusing unit 80 includes a stage movable in the optical axis direction, and the focusing lens 87 and the optical scanner 88 are held on the stage. This allows the optical lens to move in the optical axis direction while maintaining the optical positional relationship between the focusing lens 87 and the optical scanner 88. The focusing unit 80 moves in the optical axis direction under the control of the control unit 210 described later.

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

  As shown in FIG. 3, the pupil of the eye E is arranged at the focal position of the objective lens 51, and the deflection surface of the optical scanner 88 is arranged at the focal position of the focusing lens 87. That is, the deflection surface of the optical scanner 88 is located at the pupil conjugate position. In some embodiments, the focal length F1 of the objective lens 51 is substantially equal to the focal length of the focusing lens 87. The optical system between the objective lens 51 and the focusing lens 87 may be a telecentric optical system.

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

  The control unit 210 can move the focusing lens 87, the optical scanner 88, and the reflection mirror 88A in the optical axis direction by moving the focusing unit 80.

  As described above, by moving the focusing lens 87 and the optical scanner 88 integrally, the conjugate relationship between the optical scanner 88 and the eye E can be maintained. Thus, even if a scan device having a small effective diameter is used, the size and cost of the apparatus can be reduced without affecting the measurement.

  Further, by disposing the reflection mirror 88A between the optical scanner 88 and the collimator lens unit 89, the optical members constituting the OCT optical system 8 need not be moved with the optical members that need to be moved for focusing control. Optical members. As a result, it is not necessary to move the collimator lens unit 89 and the like for focusing control, and the number of optical members that move integrally with the focusing lens 87 can be reduced.

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

  The optical scanner 88 according to some embodiments includes, for example, a first galvanometer mirror and a second galvanometer mirror. The first galvanomirror deflects the measurement light LS so as to scan 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.

  In FIG. 1, 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, and is refracted by the objective lens 51. And enters the eye E to be examined. 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 (see FIG. 2).

  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 unit 80 (the focusing lens 87 and the optical scanner 88) 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.

<Configuration of processing system>
The configuration of the processing system of the ophthalmologic apparatus 1000 will be described. FIG. 4 shows an example of a functional configuration of the processing system of the ophthalmologic apparatus 1000. FIG. 4 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 moving mechanisms 40D, 80D, 200, a display unit 270, an operation unit 280, and a communication unit 290.

  The moving mechanism 200 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement 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, an OCT optical system 8, and the like. This is a mechanism for moving the head unit in which the optical system is stored in the front-rear and left-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.

  The moving mechanism 40D is a mechanism for moving the fixation unit 40 in the optical axis direction of the fixation projection system 4 (the optical axis direction of the objective lens 51). For example, similarly to the moving mechanism 200, the moving mechanism 40D includes an actuator that generates a driving force for moving the fixation unit 40, 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 40D by sending a control signal to the actuator.

  The moving mechanism 80D is a mechanism for moving the focusing unit 80 in the optical axis direction of the OCT optical system 8 (the optical axis direction of the objective lens 51). For example, similarly to the moving mechanism 200, the moving mechanism 80D includes an actuator that generates a driving force for moving the focusing unit 80, 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 80D by sending a control signal to the actuator.

(Control unit 210)
The control unit 210 includes a processor and controls each unit of the ophthalmologic apparatus. 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 1 includes control of the Z alignment light source 11, control of the line sensor 13, and the like.

  The control of the Z alignment light source 11 includes turning on and off the light source, adjusting the light amount, adjusting the aperture, and the like. The control of the line sensor 13 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. Thereby, the lighting and non-lighting of the Z alignment light source 11 are switched, or the light amount is changed. The main control unit 211 captures a signal detected by the line sensor 13 and specifies a light projection position on the line sensor 13 based on the captured signal. The main control unit 211 obtains the position of the cornea vertex of the eye E based on the specified projection position, and controls the moving mechanism 200 based on the obtained position to move the head unit in the front-rear direction (Z alignment).

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

  The control of the XY alignment light source 21 includes turning on 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. The main control unit 211 controls the moving mechanism 40D by sending a control signal to the actuator, and moves at least the liquid crystal panel 41 in the optical axis direction. Thereby, the position of the liquid crystal panel 41 is adjusted so that the liquid crystal panel 41 and the fundus oculi Ef are optically 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 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. 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 amount of light, adjusting the aperture, 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.

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

  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 focusing unit 80 includes control of movement of the focusing unit 80 in the optical axis direction. The main control unit 211 controls the moving mechanism 80D by sending a control signal to the actuator, and moves the focusing unit 80 in the optical axis direction. The control of the optical scanner 88 includes control of a scanning position, a scanning range, and a scanning speed by the MEMS scanner.

  In some embodiments, the control of the focusing lens 87 includes controlling the movement of the focusing lens 87 in the optical axis direction, controlling the movement of the focusing lens 87 to a focusing reference position corresponding to the imaging region, and controlling the imaging region. There is movement control within a movement range (focusing range) corresponding to. For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 87 in the optical axis direction. 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 ophthalmologic apparatus includes a holding member that holds the focusing lens 74 and the focusing unit 80, and a driving unit that drives the holding member. The main control unit 211 controls the movement of the focusing lens 74 and the focusing unit 80 by controlling the driving unit. For example, the main control unit 211 may move the focusing unit 80 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, the measurement result of the objective measurement (OCT measurement result), the image data of the tomographic image, the image data of the fundus image, the result of the subjective examination, the 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.

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

  5 to 7 show an example of the operation of the ophthalmologic apparatus 1000. FIG. 5 is a flowchart illustrating an operation example of the ophthalmologic apparatus 1000. FIG. 6 shows a flowchart of an operation example of step S3 in FIG. FIG. 7 shows a flowchart of an operation example of step S4 in FIG. The storage unit 212 stores a computer program for implementing the processes shown in FIGS. The main control unit 211 executes the processing shown in FIGS. 5 to 7 by operating according to the computer program.

(S1: alignment)
When the examiner performs a predetermined operation on the operation unit 280 in a state where the subject's face is fixed to a face receiving unit (not shown), the ophthalmologic apparatus 1000 executes the alignment.

  Specifically, the main control unit 211 turns on the Z alignment light source 11 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 1 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.

  In addition, 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 of the origin (for example, a position corresponding to 0D (diopter)) along each optical axis.

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

  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 S3 in response to an instruction from the main control unit 211 or a user operation or instruction on the operation unit 280. This kerato analysis may be performed simultaneously or continuously at the time of the main measurement in step S5.

(S3: provisional measurement)
Next, the main controller 211 controls the liquid crystal panel 41 to project the fixation target onto the eye E to start the reflex measurement. In this embodiment, the reflex measurement includes a provisional measurement and a main measurement. In the provisional measurement, the focusing state in the reflex measurement optical system is changed according to the refractive power of the eye E. In the main measurement, the refractive power of the eye E is acquired while the cloud of the eye E is promoted based on the in-focus state changed by the provisional measurement.

  In step S3, each of the reflex measurement light source 61, the focusing lens 74, and the focusing unit 80 is moved in the optical axis direction and is arranged at a position corresponding to the refractive power of the eye E. Details of step S3 will be described later.

(S4: OCT measurement)
Subsequently, the main control unit 211 moves the corner cube 114 while the focusing unit 80 is moved in step S3, corrects the optical path length, and obtains a desired OCT image of the eye E, The OCT measurement is executed by controlling the OCT optical system 8. That is, the OCT measurement is performed between the reflex measurements. Thereby, the OCT measurement is performed before the cloud of the eye E is urged, so that the focus control for performing the OCT measurement becomes unnecessary, and the measurement time can be shortened. The correction of the optical path length by moving the corner cube 114 may be performed in parallel by automatically adjusting the position of the OCT image in step S3. Details of step S4 will be described later.

  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.

(S5: Main measurement)
In step S5, the main control unit 211 further moves the liquid crystal panel 41 from the position obtained in the provisional measurement to the fog position, thereby prompting the fog of the eye E to be examined. Thereafter, when the reflex measurement light source 61 is off, the main control unit 211 turns on the reflex measurement light source 61. When the rotation of the rotary prism 66 is stopped, the main control unit 211 starts the rotation of the rotary prism 66. Subsequently, the main control unit 211 controls the reflex measurement projection system 6 and the reflex measurement light receiving system 7 to acquire a ring image again, similarly to the provisional measurement. The main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, the astigmatic power, and the astigmatic axis angle from the analysis result of the ring image and the moving amount of the focusing lens 74. The calculated spherical power, astigmatic power, and astigmatic axis angle are stored in the storage unit 212.

(S6: Obtain OCT image?)
Next, the main control unit 211 determines whether to acquire an OCT image. The main control unit 211 determines whether to acquire an OCT image based on an instruction from the main control unit 211 or a user operation or instruction on the operation unit 280. For example, when the time required for OCT measurement such as 3D scanning becomes long, the burden on the subject can be reduced by acquiring an OCT image after step S5.

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

(S7: Obtain OCT image)
When it is determined in step S6 that an OCT image is to be acquired (S6: Y), the main control unit 211 moves the liquid crystal panel 41 moved to the fog position in step S5 to the in-focus position obtained in the provisional measurement in step S3. Return to After that, the main control unit 211 controls the liquid crystal panel 41 to project the fixation target onto the eye E to execute the OCT measurement.

  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. 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).

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

(S11: Turn on the reflex measurement light source and start rotating the rotary prism)
First, the main control unit 211 turns on the reflex measurement light source 61 and starts the rotation of the rotary prism 66.

(S12: Analyze ring image)
Next, the main control unit 211 causes the eye E to project the ring-shaped measurement pattern light beam. 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.

(S13: Move focusing lens)
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 of the equivalent spherical power (S + C / 2) based on the temporary spherical power S and the astigmatic power C obtained in step S12. Move. In this embodiment, the focusing unit 80 is moved in conjunction with the focusing lens 74 and the like.

(S14: Analyze ring image)
Again, the main control unit 211 projects the ring-shaped measurement pattern light beam onto the eye E as in step S12. 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.

  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.

(S15: Move focusing lens)
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 of the equivalent spherical power (S + C / 2) based on the temporary spherical power S and the astigmatic power C obtained in step S14. Move. The position moved to step S15 is a position corresponding to a temporary far point. In this embodiment, the focusing unit 80 is moved in conjunction with the focusing lens 74 and the like.

(S16: Turn off the reflex measurement light source, stop the rotation of the rotary prism)
Next, the main controller 211 turns off the reflex measurement light source 61 and stops the rotation of the rotary prism 66. This is the end of step S3 in FIG. 5 (end).

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

(S21: Turn on the OCT light source and start the operation of the optical scanner)
First, the main control unit 211 turns on the reflex measurement light source 61 and starts the operation of the optical scanner 88. Thereby, a predetermined part (anterior part, fundus, or both) of the eye E is scanned with the measurement light LS. In step S21, alignment may be performed by a known method. Further, tracking may be started.

(S22: forming a tomographic image)
Next, the main control unit 211 sends a detection signal obtained by scanning the measurement light LS to the image forming unit 222. The image forming unit 222 forms a tomographic image of the eye E from the obtained detection signal. When the tomographic image is not obtained at an appropriate position, the position of the tomographic image may be adjusted by adjusting the corner cube 114.

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

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

  When it is determined in step S12 or step S14 that a ring image cannot be obtained, the main control unit 211 sets the reflex measurement light source 61 and the focusing lens 74 in advance in consideration of the possibility of an abnormally refractive eye. At this step, it is moved to the minus power side (for example, -10D) and the plus power 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.

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

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

  8 and 9 show a configuration example of an optical system of an ophthalmologic apparatus according to the second embodiment. FIG. 8 illustrates an overall configuration example of an optical system of an ophthalmologic apparatus 1000a according to the second embodiment. 8, the same components as those in FIG. 1 are denoted by the same reference numerals, and the description will be appropriately omitted. FIG. 9 illustrates a configuration example of an optical system of the focusing unit 80a in FIG. FIG. 9 shows only a part of the optical system for convenience of explanation.

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

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

  Since the operation of the ophthalmologic apparatus 1000a according to the second embodiment is substantially the same as the operation of the ophthalmologic apparatus 1000 according to the first embodiment, an operation example of the ophthalmologic apparatus 1000a according to the second embodiment is different from that of the first embodiment. The following description focuses on the differences.

  The difference between the operation of the ophthalmologic apparatus 1000a according to the second embodiment and the operation of the ophthalmologic apparatus 1000 according to the first embodiment is that the change in the optical path length of the measurement light LS due to the movement of the focusing unit 80a is canceled. The point is that optical path length correction is performed. The optical path length correction is performed on at least one of the optical path lengths of the measurement light LS and the reference light LR.

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

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

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

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

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

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

(S33: forming a tomographic image)
Next, the main control unit 211 sends a detection signal obtained by scanning the measurement light LS to the image forming unit 222. The image forming unit 222 forms a tomographic image of the eye E from the obtained detection signal. When the tomographic image is not obtained at an appropriate position, the position of the tomographic image may be adjusted by adjusting the corner cube 114.

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

  Note that, similarly to the first embodiment, the main control unit 211 may cause the data processing unit 223 to calculate an intraocular parameter from a tomographic image obtained in step S33 or a detection signal obtained by scanning, for example.

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

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

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

  According to such a configuration, the focusing control can be performed so that the positional relationship between the focusing lens and the optical scanner is maintained, so that the conjugate relationship between the optical scanner and the subject's eye can be maintained. Thus, even when a scanning device having a small effective diameter is used as the optical scanner, the luminous flux does not occur in the eye to be examined, such as a small pupil, and the size and the size of the ophthalmic apparatus can be reduced without affecting the measurement accuracy. Costs can be reduced.

  An ophthalmologic apparatus according to some embodiments is disposed between an inspection optical system and an optical scanner, guides light from the inspection optical system to the optical scanner, and returns light guided by the optical scanner in the optical axis direction. The control unit includes a deflecting member (reflection mirror 88A) for deflecting and guiding to the inspection optical system, and the control unit performs focusing control by moving the focusing lens, the optical scanner, and the deflecting member in the optical axis direction.

  According to such a configuration, the deflecting member is arranged between the inspection optical system and the optical scanner, and the optical member group to be moved is separated, so that other optical members are used for focusing control. There is no need to move, and the number of components of the moving optical member can be reduced. As a result, the size and cost of the ophthalmologic apparatus can be further reduced.

  An ophthalmologic apparatus according to some embodiments includes a first focusing unit (a focusing unit 80) including a focusing lens, an optical scanner, and a deflecting member, and a first focusing unit that moves the first focusing unit in an optical axis direction. And a moving mechanism (moving mechanism 80D), and the control unit controls the first moving mechanism.

  According to such a configuration, the first focusing unit including the focusing lens, the optical scanner, and the deflecting member is provided, and the first focusing unit is moved by the first moving mechanism. Focus control can be performed while maintaining the positional relationship between the focusing lens and the optical scanner.

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

  According to such a configuration, even when a scanning device having a small effective diameter is used as the optical scanner, the size and cost of the ophthalmologic apparatus can be reduced without affecting the OCT measurement accuracy.

  An ophthalmologic apparatus according to some embodiments has flexibility, one end of which is optically connected to an inspection optical system, and a light guide member (optical fiber f1) that guides light from the inspection optical system, and a light guide member. And a collimator lens (collimator lens unit 89) disposed between the other end of the optical scanner and the optical scanner. The control unit moves the other end of the focusing lens, the optical scanner, the light guide member, and the collimator lens. To perform focusing control.

  According to such a configuration, the focusing control can be performed so that the positional relationship between the focusing lens and the optical scanner is maintained, so that the conjugate relationship between the optical scanner and the subject's eye can be maintained. Thus, even when a scanning device having a small effective diameter is used as the optical scanner, the luminous flux does not occur in the eye to be examined, such as a small pupil, and the size and the size of the ophthalmic apparatus can be reduced without affecting the measurement accuracy. Costs can be reduced.

  An ophthalmologic apparatus according to some embodiments includes a focusing lens, an optical scanner, and a collimator lens, and includes a second focusing unit (focusing unit 80a) that holds the other end of the light guide member, and a second focusing unit. A second moving mechanism (moving mechanism 80D) for moving the unit in the optical axis direction, and the control unit controls the second moving mechanism.

  According to such a configuration, the second focusing unit including the focusing lens, the optical scanner, and the collimator lens and holding the other end of the light guide member is provided, and the second focusing unit is moved by the second moving mechanism. With this configuration, it is possible to perform focusing control so as to maintain the positional relationship between the focusing lens and the optical scanner while minimizing the moving mechanism.

  In the ophthalmologic apparatus according to some embodiments, the inspection optical system divides the light (L0) from the light source (OCT light source 101) into the reference light (LR) and the measurement light (LS), and divides the measurement light into the eye to be inspected. And an interference optical system that detects an interference light (LC) between the return light of the measurement light from the subject's eye and the reference light, and the ophthalmologic apparatus includes at least one of an optical path length of the measurement light and an optical path length of the reference light. The optical path length changing mechanism (collimator 111, corner cube 114, and collimator 116), and the control unit controls the focusing lens, the optical scanner, the other end of the light guide member, and the moving amount of the collimator lens in the optical axis direction. By controlling the optical path length changing mechanism accordingly, at least one of the optical path length of the measurement light and the optical path length of the reference light is changed.

  According to such a configuration, even when a scanning device having a small effective diameter is used as the optical scanner, the size and cost of the ophthalmologic apparatus can be reduced without affecting the OCT measurement accuracy.

  In the ophthalmologic apparatus according to some embodiments, the optical scanner includes a MEMS (Micro Electro Mechanical Systems) scanner.

  According to such a configuration, by using an inexpensive and small MEMS scanner as the optical scanner, the size and cost of the ophthalmic apparatus can be reduced.

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

  According to such control, since the focusing control can be performed so that the positional relationship between the focusing lens and the optical scanner is maintained, the conjugate relationship between the optical scanner and the subject's eye can be maintained. As a result, even when a scanning device having a small effective diameter is used as the optical scanner, a decrease in measurement accuracy can be suppressed.

  In the control method of the ophthalmologic apparatus according to some embodiments, the ophthalmic apparatus is disposed between the inspection optical system and the optical scanner, guides light from the inspection optical system to the optical scanner, and returns light from the optical scanner. It includes a deflecting member (reflection mirror 88A) for deflecting in the optical axis direction and guiding it to the inspection optical system. In the focusing control step, the focusing lens, the optical scanner, and the deflecting member are moved.

  According to such control, in an ophthalmologic apparatus in which a deflecting member is disposed between an inspection optical system and an optical scanner, it is not necessary to move another optical member for focus control.

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

  According to such a configuration, even when a scanning device having a small effective diameter is used as the optical scanner, it is possible to acquire the OCT measurement result without lowering the measurement accuracy.

<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.

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

Reference Signs List 1 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 Processing unit 51 Objective lenses 80, 80a Focusing unit 80D Moving mechanism 87 Focusing lens 88 Optical scanner 88A Reflecting mirror 89 Collimator lens unit 111, 116 Collimator 114 Corner cube 210 Control unit 211 Main control unit 1000 Ophthalmologic apparatus

Claims (11)

An objective lens,
An inspection optical system that irradiates light from a light source to the subject's eye via the objective lens and detects return light from the subject's eye,
A focusing lens disposed between the objective lens and the inspection optical system and movable in an optical axis direction of the objective lens;
An optical scanner that is arranged between the focusing lens and the inspection optical system so that a deflection surface is located at a focal position of the focusing lens, and is movable in the optical axis direction,
A control unit that performs focusing control by moving the focusing lens and the optical scanner so that the positional relationship between the focusing lens and the optical scanner is maintained,
Ophthalmic devices including. It is arranged between the inspection optical system and the optical scanner, guides light from the inspection optical system to the optical scanner, deflects the return light guided by the optical scanner in the optical axis direction, and Including a deflecting member leading to the inspection optical system,
The ophthalmologic apparatus according to claim 1, wherein the control unit performs the focusing control by moving the focusing lens, the optical scanner, and the deflecting member in the optical axis direction. A first focusing unit including the focusing lens, the optical scanner, and the deflection member;
A first moving mechanism that moves the first focusing unit in the optical axis direction;
Including
The ophthalmologic apparatus according to claim 2, wherein the control unit controls the first moving mechanism. The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light to the eye to be inspected, and causes interference between the return light of the measurement light from the eye to be inspected and the reference light. The ophthalmologic apparatus according to claim 1, further comprising an interference optical system that detects light. A light guide member having flexibility, one end of which is optically connected to the inspection optical system and guides light from the inspection optical system,
A collimator lens disposed between the other end of the light guide member and the optical scanner,
Including
The ophthalmologic apparatus according to claim 1, wherein the control unit performs the focusing control by moving the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens. A second focusing unit that includes the focusing lens, the optical scanner, and the collimator lens, and that holds the other end of the light guide member;
A second moving mechanism that moves the second focusing unit in the optical axis direction;
Including
The ophthalmologic apparatus according to claim 5, wherein the control unit controls the second moving mechanism. The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light to the eye to be inspected, and causes interference between the return light of the measurement light from the eye to be inspected and the reference light. Including interference optics to detect light,
An optical path length changing mechanism that changes at least one of the optical path length of the measurement light and the optical path length of the reference light,
Including
The control unit controls the optical path length changing mechanism according to the amount of movement of the focusing lens, the optical scanner, the other end of the light guide member, and the collimator lens in the optical axis direction, thereby controlling the measurement light. The ophthalmologic apparatus according to claim 5, wherein at least one of an optical path length and an optical path length of the reference light is changed. The ophthalmologic apparatus according to any one of claims 1 to 7, wherein the optical scanner includes a MEMS (Micro Electro Mechanical Systems) scanner. An objective lens,
An inspection optical system that irradiates light from a light source to the subject's eye via the objective lens and detects return light from the subject's eye,
A focusing lens disposed between the objective lens and the inspection optical system and movable in an optical axis direction of the objective lens;
An optical scanner that is arranged between the focusing lens and the inspection optical system so that a deflection surface is located at a focal position of the focusing lens, and is movable in the optical axis direction,
A method of controlling an ophthalmologic apparatus, comprising:
A focusing control step of performing focusing control by moving the focusing lens and the optical scanner so that a positional relationship between the focusing lens and the optical scanner is maintained;
After the focusing control step, irradiating the light of the inspection optical system deflected by the optical scanner to the eye to be inspected, a measurement step of detecting the return light thereof,
A control method for an ophthalmologic apparatus including: The ophthalmic apparatus is disposed between the inspection optical system and the optical scanner, guides light from the inspection optical system to the optical scanner, and deflects the return light from the optical scanner in the optical axis direction. Including a deflecting member for guiding to the inspection optical system,
The control method of the ophthalmologic apparatus according to claim 9, wherein, in the focusing control step, the focusing lens, the optical scanner, and the deflection member are moved. The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light to the eye to be inspected, and causes interference between the return light of the measurement light from the eye to be inspected and the reference light. Including interference optics to detect light,
In the measuring step, controlling the interference optical system and the optical scanner to irradiate the measurement light deflected by the optical scanner to the subject's eye, and detecting interference light between the return light and the reference light. The method for controlling an ophthalmologic apparatus according to claim 9, wherein:

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