JP2019154986A - Ophthalmological device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a new technique for performing a plurality of measurements and inspections by performing wavelength separation. An ophthalmic apparatus includes an objective lens, an anterior eye observation system, an inspection optical system, an optical path synthesis member, and an anterior eye illumination system. The anterior eye portion observation system detects the first return light of the illumination light from the anterior segment of the eye to be inspected through the objective lens. The inspection optical system projects light onto the eye to be inspected through the objective lens and detects the second return light from the eye to be inspected. The optical path synthesis member synthesizes the optical path of the inspection optical system and the optical path of the anterior segment observation system on the optical path synthesis surface arranged at an angle with respect to the optical axis of the objective lens. The anterior segment illumination system illuminates the anterior segment with illumination light in a wavelength range including the transmission center wavelength corresponding to the incident angle of the first return light with respect to the optical path composite surface. [Selection diagram] Fig. 1

Description

  The present invention relates to an ophthalmologic apparatus.

  An ophthalmologic apparatus capable of performing a plurality of examinations and measurements on an eye to be examined is known. Examination and measurement for the eye to be examined include subjective examination and objective measurement. A subjective test is to obtain a result based on a response from the 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 Document 1 discloses an ophthalmologic apparatus capable of performing photographing and measurement using subjective examination, refractive power measurement of an eye to be examined, and optical coherence tomography. Such an ophthalmologic apparatus is provided with, for example, an observation optical system for observing the anterior eye portion and the fundus of the eye to be examined. By sharing the observation optical system with a plurality of optical systems each corresponding to the examination type (measurement type), the ophthalmologic apparatus can be miniaturized. The plurality of optical systems are wavelength-separated by, for example, a dichroic mirror.

  It is known that the transmission characteristic (reflection characteristic) of a dichroic mirror that performs wavelength separation changes according to the incident angle of light with respect to the dichroic mirror. When the transmission characteristics of the dichroic mirror change, the accuracy of wavelength separation decreases. For example, in Patent Document 2, the optical arrangement of an optical scanner that scans measurement light for performing optical coherence tomography and a dichroic mirror is devised, resulting in the dependency of the incident angle of the measurement light on the dichroic mirror. A technique for reducing fluctuations in wavelength separation characteristics is disclosed.

JP 2017-136215 A JP 2014-213155 A

  In examination and measurement using an ophthalmologic apparatus, light in the wavelength range of the near infrared region is often used to reduce the burden on the subject. Therefore, for example, the wavelength range of light used in optical coherence tomography may be close to the wavelength range of light used in the observation system. In this case, it is difficult to wavelength-separate light in a wavelength range optimum for each optical system using an optical member such as a dichroic mirror in the conventional method.

  The present invention has been made in view of such circumstances, and an object thereof is to provide a new technique for performing a plurality of measurements and inspections by performing wavelength separation.

  A first aspect of an ophthalmologic apparatus according to some embodiments includes an objective lens, and an anterior ocular segment observation system that detects a first return light of illumination light from the anterior ocular segment of the subject eye via the objective lens, In an inspection optical system that projects light onto the eye to be examined through the objective lens and detects second return light from the eye to be examined, and an optical path combining surface that is arranged to be inclined with respect to the optical axis of the objective lens An optical path combining member that combines the optical path of the inspection optical system and the optical path of the anterior ocular segment observation system, and illumination light in a wavelength range including a wavelength corresponding to an incident angle of the first return light with respect to the optical path combining surface An anterior segment illumination system that illuminates the anterior segment.

  In a second aspect of the ophthalmologic apparatus according to some embodiments, in the first aspect, the anterior ocular segment illumination system has an incident angle with respect to a reference transmission center wavelength based on light transmission characteristics on the optical path combining surface. The anterior segment is illuminated with illumination light in a wavelength range including a peak wavelength corresponding to the transmission center wavelength whose wavelength is shifted by the corresponding shift.

  In a third aspect of the ophthalmologic apparatus according to some embodiments, in the first aspect or the second aspect, the light path combining surface has an incident end surface of light so as to compensate for an incident angle dependency of the second return light. The optical film is formed so that the film thickness changes according to the position.

  In a fourth aspect of the ophthalmologic apparatus according to some embodiments, in the first aspect, the optical path combining surface has a light incident end face depending on a position of an incident end face of light so as to compensate for an incident angle dependency of the second return light. An optical film is formed so that the film thickness is changed, and the anterior ocular segment illumination system is configured to transmit the first return light with respect to the optical path combining surface with respect to a reference transmission center wavelength based on a light transmission characteristic of the optical path combining surface. A first peak wavelength corresponding to a first transmission center wavelength shifted by a shift corresponding to the upper end of the incident angle, and a shift corresponding to the lower end of the incident angle with respect to the optical path combining surface with respect to the reference transmission center wavelength. The anterior ocular segment is illuminated with illumination light in a wavelength range including the second peak wavelength corresponding to the second transmission center wavelength whose wavelength is shifted by a distance.

  In a fifth aspect of the ophthalmologic apparatus according to some embodiments, in the fourth aspect, the inspection optical system divides light from a light source into reference light and measurement light, and the eye to be inspected via the objective lens. And an interference optical system for projecting the measurement light and detecting interference light between the return light of the measurement light from the eye to be examined and the reference light.

  In a sixth aspect of the ophthalmologic apparatus according to some embodiments, in the fifth aspect, the interference optical system divides light from a wavelength swept light source into reference light and measurement light, and applies the measurement light to the eye to be examined. And the interference light between the return light of the measurement light from the eye to be examined and the reference light is detected.

  In a seventh aspect of the ophthalmologic apparatus according to some embodiments, in any one of the fourth to sixth aspects, the anterior ocular segment illumination system irradiates illumination light in a wavelength range including the first peak wavelength. A first illumination light source; and a second illumination light source that emits illumination light in a wavelength range including the second peak wavelength.

  According to the present invention, it is possible to provide a new technique for performing a plurality of measurements and inspections by performing wavelength separation.

It is the schematic which shows the structural example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the incident angle dependence of the dichroic mirror which concerns on embodiment. It is the schematic for demonstrating the optical system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the optical system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the structure of the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the structure of the ophthalmologic apparatus which concerns on embodiment. It is the schematic for demonstrating the structure of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the processing system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the flow of the operation example of the ophthalmologic apparatus which concerns on embodiment.

  An example of an embodiment of an ophthalmologic apparatus according to the present invention will be described in detail with reference to the drawings. In addition, it is possible to use the description content of the literature referred in this specification, and arbitrary well-known techniques for the following embodiment.

  The ophthalmologic apparatus according to the embodiment can perform objective measurement while observing the eye to be examined. There are an anterior eye part, a posterior eye part, etc. as an observation part of a subject eye. The objective measurement is a measurement technique for acquiring information about the eye to be examined mainly using a physical technique without referring to a response from the subject. The objective measurement includes measurement for obtaining the characteristics of the eye to be examined and photographing for obtaining an image of the eye to be examined. The objective measurement includes objective refraction measurement, corneal shape measurement, intraocular pressure measurement, fundus photography, optical interference measurement and the like.

  The ophthalmologic apparatus according to some embodiments can perform a subjective examination while observing the eye to be examined. A subjective test is a measurement technique that acquires information using a response from a subject. The subjective examination includes a subjective examination measurement such as a distance examination, a near examination, a contrast examination, and a glare examination, and a visual field examination.

  Hereinafter, the fundus conjugate position is a position substantially optically conjugate with the fundus of the eye to be examined in a state where the alignment is completed, and means a position optically conjugate with the fundus of the eye to be examined or the vicinity thereof. Similarly, the pupil conjugate position is a position substantially optically conjugate with the pupil of the eye to be examined in a state where the alignment is completed, and means a position optically conjugate with the pupil of the eye to be examined or the vicinity thereof. .

<Configuration of optical system>
In FIG. 1, the structural example of the optical system of the ophthalmologic apparatus which concerns on embodiment is shown. The ophthalmologic apparatus 1000 according to the embodiment includes an optical system for observing the eye E, an optical system for inspecting the eye E, and a dichroic mirror that separates the optical paths of these optical systems. As an optical system for observing the eye E, an anterior ocular segment observation system 5 is provided. As an optical system for inspecting the eye E, an OCT optical system and a reflex measurement optical system (refractive power measurement optical system) are provided.

  The ophthalmic apparatus 1000 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a fixation projection system 4, an anterior ocular segment observation system 5, a reflex measurement projection system 6, 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 uses light of 940 nm to 1000 nm, the reflex measurement optical system (ref measurement measurement projection system 6, reflex measurement light receiving system 7) uses light of 830 nm to 880 nm, and the fixation projection system 4 Will be described using a light of 400 nm to 700 nm and the OCT optical system 8 using light of 1000 nm to 1100 nm.

(Anterior segment observation system 5)
The anterior segment observation system 5 captures a moving image of the anterior segment of the eye E. In the optical system that passes through the anterior ocular segment observation system 5, the imaging surface of the imaging element 59 is disposed at the 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 eye portion of the eye E passes through the objective lens 51, passes through the dichroic mirror 52, passes through the hole formed in the stop (telecentric stop) 53, and passes through the half mirror 23. , Passes through the relay lenses 55 and 56 and passes 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 disposed 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 later. The processing unit 9 displays the anterior segment image E ′ based on the video signal on a display screen 10a of the display unit 10 described later. The anterior segment image E ′ is, for example, an infrared moving image.

(Z alignment system 1)
The Z alignment system 1 projects light (infrared light) for alignment in the optical axis direction (front-rear direction, Z direction) of the anterior ocular segment observation system 5 onto the eye E. The light output from the Z alignment light source 11 is projected onto the cornea Cr of the eye E, reflected by the cornea Cr, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12. When the position of the corneal apex 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 corneal apex 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 execute Z alignment.

(XY alignment system 2)
The XY alignment system 2 emits light (infrared light) for alignment in a direction (left-right direction (X direction), vertical direction (Y direction)) orthogonal to the optical axis of the anterior ocular segment observation system 5. Irradiate. The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22 provided in an optical path branched from the optical path of the anterior 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 onto the eye E through the anterior ocular segment observation system 5. Reflected light from the cornea Cr of the eye E is guided to the image sensor 59 through the anterior segment 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 segment image E ′ including the bright spot image Br and the alignment mark AL on the display screen of the display unit. When performing 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 the alignment is performed automatically, the processing unit 9 controls a mechanism for moving the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is cancelled.

(Kerato measurement system 3)
The kerato measurement system 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea Cr of the eye E to the cornea Cr. The kerato plate 31 is disposed between the objective lens 51 and the eye E. A kerato ring light source 32 is provided on the back side of the kerato plate 31 (objective lens 51 side). By illuminating the kerato plate 31 with light from the kerato ring light source 32, a ring-shaped light beam is projected onto the cornea Cr of the eye E to be examined. Reflected light (keratling image) from the cornea Cr of the eye E is detected by the image sensor 59 together with the anterior segment image E ′. The processing unit 9 calculates a corneal shape parameter representing the shape of the cornea Cr by performing a known calculation based on the keratling image.

(Ref measurement projection system 6, Reflex 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 measuring refractive power (for example, a ring-shaped light beam) (infrared light) onto the fundus oculi Ef. The ref measurement light receiving system 7 receives the return light from the 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 hole 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 element 59 is disposed at the fundus conjugate position.

  In some embodiments, the reflex measurement light source 61 is a superluminous diode (SLD) 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 disposed at the 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. Light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63. The 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 diaphragm 64. The light (ring-shaped light beam) that has passed through the light transmitting portion of the ring diaphragm 64 is reflected by the reflecting surface formed around the hole portion of the apertured prism 65, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. The The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the eye E. The rotary prism 66 is used for averaging the light amount distribution of the ring-shaped light flux with respect to the blood vessel and diseased part of the fundus oculi Ef and for reducing speckle noise caused by the light source.

  The return light of the ring-shaped light beam projected onto the fundus oculi 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, and is reflected by the reflecting mirror 72, and the relay lens 73 and the focusing lens. Pass 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 reflecting mirror 75, reflected by the dichroic mirror 76, and imaged on the imaging surface of the imaging element 59 by the imaging lens 58. The processing unit 9 calculates the refractive power value of the eye E by performing a known calculation 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.

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

  The fixation projection system 4 presents the fixation target to the eye E. The liquid crystal panel 41 that is controlled by the processing unit 9 displays a pattern representing the fixation target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the eye E can be changed. As the fixation position of the eye E, a position for acquiring an image centered on the macular portion of the fundus oculi Ef, a position for acquiring an image centered on the optic nerve head, a position between the macula portion and the optic nerve head There is a position for acquiring an image centered on the center of the fundus. It is possible to arbitrarily change the display position of the pattern representing the fixation target.

  Light from the liquid crystal panel 41 passes through the relay lens 42, 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 onto the fundus oculi Ef. The liquid crystal panel 41 (or the liquid crystal panel 41 and the relay lens 42) is 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 with the fundus oculi Ef and the optical system.

  The OCT optical system 8 is provided in an optical path that is wavelength-separated from the optical path of the reflex measurement optical system by the dichroic mirror 67. 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 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, an OCT light source 101 is a wavelength sweep type (wavelength scanning type) light source capable of sweeping (scanning) the wavelength of emitted light, like a general swept source type OCT apparatus. It is comprised including. The swept wavelength light source includes a laser light source including a resonator. The OCT light source 101 temporally changes the output wavelength in the near-infrared wavelength band that cannot be visually recognized by the human eye.

  As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for executing the swept source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing light from a wavelength tunable light source (wavelength sweep type light source) into measurement light and reference light, return light of measurement light from the eye E and reference light via a reference light path, and Are provided with a function of generating interference light by superimposing 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 wavelength tunable laser that changes the wavelength of outgoing light (wavelength range of 1000 nm to 1100 nm) at high speed. The light L0 output from the OCT light source 101 is guided to the polarization controller 103 by the optical fiber 102 and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided to the fiber coupler 105 by the optical fiber 104 and split into the measurement light LS and the reference light LR.

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

  The reference light LR passing through the corner cube 114 is converted from a parallel light beam into a focused light beam by the collimator 116 via the dispersion compensation member 113 and the optical path length correction member 112, and enters the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 and its polarization state is adjusted, guided to the attenuator 120 by the optical fiber 119, the amount of light is adjusted, and guided to the fiber coupler 122 by the optical fiber 121.

  On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber f1 and converted into a parallel light beam by the collimator lens unit 89, and the optical scanner 88, the focusing lens 87, the relay lenses 86 and 85, and the reflection mirror 84. And is reflected by the dichroic mirror 83.

  The optical scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. The optical scanner 88 includes, for example, a first galvanometer mirror and a second galvanometer mirror. The first galvanometer mirror deflects the measurement light LS so as to scan the fundus oculi Ef in the horizontal direction orthogonal to the optical axis of the OCT optical system 8. The second galvanometer mirror deflects the measurement light LS deflected by the first galvanometer mirror so as to scan the fundus oculi Ef in the vertical direction orthogonal to the optical axis of the OCT optical system 8. Examples of the scanning mode of the measurement light LS by the optical scanner 88 include horizontal scanning, vertical scanning, cross scanning, radiation scanning, circular scanning, concentric scanning, and helical scanning.

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

  The fiber coupler 122 combines (interferes) 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 light LC by branching the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference lights LC are guided to the detector 125 through 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 the pair of interference lights LC, and outputs a difference between a pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to a DAQ (Data Acquisition System) 130.

  The clock 130 is supplied from the OCT light source 101 to the DAQ 130. The clock KC is generated in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the variable wavelength light source in the OCT light source 101. For example, the OCT light source 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then generates a clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic processing unit 220 of the processing unit 9. For example, for each series of wavelength scans (for each A line), the arithmetic processing unit 220 performs a Fourier transform or the like on the spectrum distribution based on the sampling data, thereby forming a reflection intensity profile 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, the measurement optical path length and the reference optical path length are obtained using optical members other than these. It is also possible to change the difference.

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

  As described above, the OCT optical system 8 is provided in an optical path that is wavelength-separated from the optical path of the reflex measurement optical system by the dichroic mirror 67. That is, the inspection optical system provided in the optical path wavelength-separated from the optical path of the reflex measurement optical system by the dichroic mirror 67 includes an interference optical system. The interference optical system divides light in a predetermined wavelength range from a light source into reference light and measurement light, projects the measurement light onto the eye to be examined, and interference light between the return light of the measurement light from the eye to be examined and the reference light Is detected.

  For example, when the optical path of the OCT optical system 8 is separated from the optical path of the reflex measurement optical system using a perforated prism, the optical system is configured to allow the measurement light to pass through a hole formed in the perforated prism. Therefore, it is necessary to consider vignetting of the measurement light and its return light. On the other hand, by performing wavelength separation with the dichroic mirror 67, the amount of light used in each optical system can be increased as compared with the case of using a perforated prism.

  By the way, the transmission characteristic (reflection characteristic) of the dichroic mirror 52 changes according to the incident angle of light with respect to the optical path combining surface. For example, when the dichroic mirror 52 is configured by a dielectric multilayer filter, the transmission characteristics change as described above.

  FIG. 3 schematically shows a change in transmission characteristics of the dichroic mirror 52. In FIG. 3, the vertical axis represents the transmittance, and the horizontal axis represents the wavelength of incident light.

  As shown in FIG. 3, when the transmission characteristics of a plurality of lights having different incident angles with respect to the optical path combining surface change, the cut-on wavelength (cut-off wavelength) changes according to the incident angle.

  When the anterior ocular segment observation system 5 is a telecentric optical system and the light refracted by the objective lens 51 is incident on the optical path combining surface of the dichroic mirror 52, the light is incident within a predetermined range on the optical path combining surface. Therefore, it means that the incident angle of light changes within a predetermined range. For example, the incident angle of light incident on a position near the optical axis of the objective lens 51 on the optical path combining surface is different from the incident angle of light incident on a position off the optical axis. That is, the transmission characteristic of light incident on a position near the optical axis is different from the transmission characteristic of light incident on a position off the optical axis.

  4A and 4B schematically show light incident on the optical path combining surface of the dichroic mirror 52. FIG. 4A and 4B are views showing the incident angles with respect to the incident positions on the dichroic mirror 52 by the OCT optical system 8 and the anterior ocular segment observation system 5, respectively, and are enlarged views of a part of the optical system in FIG. 4A and 4B, the same parts as those in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

  For example, light incident from below the optical axis of the objective lens 51, such as the incident light IL1 in FIG. 4A and the incident light IL2 in FIG. 4B, has a larger incident angle with respect to the normal of the optical path combining surface. In this case, the transmission center wavelength of the light is shifted to the short wavelength side with respect to the transmission center wavelength (reference transmission center wavelength) on the optical axis.

  For example, light incident from above the optical axis of the objective lens 51, such as the incident light IL11 in FIG. 4A and the incident light IL12 in FIG. 4B, has a smaller incident angle with respect to the normal of the optical path combining surface. In this case, the transmission center wavelength of the light is shifted to the longer wavelength side with respect to the transmission center wavelength on the optical axis. As described above, the incident angles of the OCT optical system 8 and the anterior ocular segment observation system 5 with respect to the incident position on the dichroic mirror 52 are different, and an optical film that optimizes the transmittance cannot be formed for both optical systems. .

  As described above, the transmission characteristics (transmission center wavelength) differ depending on the light incident position on the optical path combining surface of the dichroic mirror 52. Such incident angle dependence of the transmission characteristics of the dichroic mirror 52 causes, for example, a reduction in the transmittance of light in a predetermined incident angle range among the return light to the anterior ocular segment observation system 5.

  FIG. 5 shows an explanatory view of the incident angle dependence of the return light to the anterior ocular segment observation system 5. In FIG. 5, the vertical axis represents the transmittance, and the horizontal axis represents the wavelength.

  For example, when the anterior segment illumination light source 50 illuminates the anterior segment with illumination light ILZ having a single wavelength λ1, the transmission characteristic of the incident light IL1 on the lower side of the optical axis is relative to the optical path synthesis surface of the dichroic mirror 52. Depending on the incident angle, T1 to T1 ′ are obtained. Similarly, the transmission characteristics of the incident light IL11 above the optical axis are T11 to T11 ′ according to the incident angle with respect to the optical path combining surface. The transmission characteristic T0 ′ represents the transmission characteristic of incident light on the optical axis. In other words, the wavelength distribution of the transmittance of the return light deviates from the wavelength distribution of the transmittance of the illumination light ILZ from the anterior segment illumination light source 50 according to the incident angle with respect to the optical path combining surface of the dichroic mirror 52. Therefore, the anterior ocular segment observation system 5 detects light transmitted with mutually different transmission characteristics on the lower side and the upper side of the optical axis with respect to the return light of the illumination light ILZ, and part of the light becomes dark. The image quality of the acquired anterior ocular segment image deteriorates.

  The anterior segment illumination light source 50 according to some embodiments illuminates the anterior segment with illumination light in a wavelength range including a transmission center wavelength corresponding to the incident angle of the return light of illumination light with respect to the optical path combining surface of the dichroic mirror 52. To do. For example, the anterior segment illumination light source 50 has a transmission center whose wavelength is shifted by a shift corresponding to the incident angle with respect to the reference transmission center wavelength λ0 based on the transmission characteristic of the light at the reference incident angle on the optical path combining surface of the dichroic mirror 52. The anterior segment is illuminated with illumination light in a wavelength range including a peak wavelength corresponding to the wavelength λs. The reference incident angle is, for example, an incident angle of light incident on the optical axis position of the objective lens 51 on the optical path combining surface. In some embodiments, the peak wavelength is the same wavelength as the transmission center wavelength λs. In some embodiments, the peak wavelength is a peak wavelength of a light source that outputs light in a wavelength range including a transmission center wavelength λs among a plurality of light sources. This makes it possible to obtain a uniformly bright anterior segment image by compensating the amount of light transmitted with different transmission characteristics on the lower side and the upper side of the optical axis of the objective lens 51. Become.

  Further, the incident angle dependency of the dichroic mirror 52 similarly causes a decrease in the transmittance of light in a predetermined incident angle range for the return light to the reflex measurement optical system and the OCT optical system 8. As a result, the accuracy of measurement and OCT measurement is reduced. In this case, by combining the change of the wavelength of the illumination light and the inclined film formed on the optical path combining surface of the dichroic mirror 52 as described above, the light in the optimum wavelength range for both optical systems is wavelength-separated. It becomes possible.

  The dichroic mirror 52 according to some embodiments is a tilted membrane filter. That is, an optical film is formed on the dichroic mirror 52 according to some embodiments so that the film thickness changes according to the position of the light incident end face on the optical path combining surface. By forming the optical film so that the film thickness is inclined, it is possible to compensate the incident angle dependency on the optical path combining surface of the dichroic mirror 52.

  Since the incident angle of the return light of the measurement light LS with respect to the optical path combining surface of the dichroic mirror 52 and the incident angle of the return light of the anterior ocular segment observation system 5 are different, the incident angle dependency on both return lights can be obtained only by the inclined film filter. There is no compensation. For example, when an inclined film is formed on the optical path combining surface of the dichroic mirror 52 so as to compensate for the incident angle dependence of the return light of the measurement light LS of the OCT optical system 8, to the anterior ocular segment observation system 5 having a close wavelength range. The transmission characteristic of the return light is affected, and the transmittance of light in a predetermined incident angle range is lowered.

  Therefore, in this embodiment, by forming an inclined film on the optical path combining surface of the dichroic mirror 52, the incident angle dependency of the measurement light LS of the OCT optical system 8 on the return light is compensated. Further, the anterior ocular segment illumination light source 50 illuminates the anterior ocular segment with illumination light in a wavelength range including a transmission center wavelength corresponding to the incident angle of the return light of the illumination light with respect to the optical path combining surface of the dichroic mirror 52. The incident angle dependency on the return light to the eye observation system 5 is compensated.

  FIG. 6 is an explanatory diagram of the anterior segment illumination light source 50 according to the embodiment. FIG. 6 is an enlarged view of a part of the optical system of FIG. In FIG. 6, the same parts as those in FIG.

  When the return light to the anterior ocular segment observation system 5 on the optical path synthesis surface of the dichroic mirror 52 enters a predetermined range, the incident angle of the return light with respect to the optical path synthesis surface changes within the predetermined range. The predetermined range of the incident angle of the return light is specified by the upper end UP and the lower end LW.

  It is assumed that the optical path combining surface of the dichroic mirror 52 is inclined with respect to the optical axis of the objective lens 51 at an angle D0. The range of the incident angle of the return light to the anterior ocular segment observation system 5 on the optical path combining surface is represented by D0 ± d. The transmission center wavelength (first transmission center wavelength) at the upper end UP (angle D0 + d) is shifted by a shift corresponding to the upper end UP with respect to the reference transmission center wavelength λ0 based on the transmission characteristics of light at the reference incident angle on the optical path combining surface. Wavelength. Similarly, the transmission center wavelength (second transmission center wavelength) at the lower end LW (angle D0-d) corresponds to the lower end LW with respect to the reference transmission center wavelength λ0 based on the transmission characteristics of light at the reference incident angle on the optical path combining surface. The wavelength is shifted by the shift amount.

  The anterior segment illumination light source 50 includes a first peak wavelength λp1 corresponding to the transmission center wavelength (first transmission center wavelength) at the upper end UP and a second peak corresponding to the transmission center wavelength (second transmission center wavelength) at the lower end LW. The anterior segment is illuminated with illumination light in a wavelength range including the wavelength λp2. In some embodiments, the first peak wavelength λp1 is the same wavelength as the first transmission center wavelength. In some embodiments, the first peak wavelength λp1 is a peak wavelength of a light source that outputs light in a wavelength range including the first transmission center wavelength among the plurality of light sources. In some embodiments, the second peak wavelength λp2 is the same wavelength as the second transmission center wavelength. In some embodiments, the second peak wavelength λp2 is a peak wavelength of a light source that outputs light in a wavelength range including the second transmission center wavelength among the plurality of light sources.

  In some embodiments, the anterior segment illumination light source 50 includes a first illumination light source 50A and a second illumination light source 50B. The first illumination light source 50A emits illumination light in a wavelength range including the first peak wavelength λp1. The second illumination light source 50B emits illumination light in a wavelength range including the second peak wavelength λp2.

  In some embodiments, the anterior segment illumination light source 50 is constituted by a single light source that emits illumination light in a wavelength range including the first peak wavelength λp1 and the second peak wavelength λp2. In some embodiments, the anterior segment illumination light source 50 includes three or more light sources that emit illumination light in a wavelength range that includes a first peak wavelength λp1 and a second peak wavelength λp2.

  7A and 7B are explanatory diagrams of the first illumination light source 50A and the second illumination light source 50B. FIG. 7A schematically shows the light source characteristics of the first illumination light source 50A. FIG. 7B schematically shows the light source characteristics of the second illumination light source 50B. 7A and 7B, the vertical axis represents transmittance, and the horizontal axis represents wavelength.

  As shown in FIG. 7A, the first illumination light source 50A emits illumination light IL20 in a wavelength range including the first peak wavelength λp1 shifted to the longer wavelength side with respect to the reference transmission center wavelength λ0. As shown in FIG. 7B, the second illumination light source 50B emits illumination light IL21 in a wavelength range including the second peak wavelength λp2 shifted to the short wavelength side with respect to the reference transmission center wavelength λ0.

  The first overlapping range between the light source characteristic by the illumination light IL20 in FIG. 7A and the light transmission characteristic T20 at the upper end UP of the range of incident light on the optical path combining surface is relative to the optical axis detected in the anterior ocular segment observation system 5. Corresponding to the amount of return light above. Similarly, the second overlapping range between the light source characteristic by the illumination light IL21 in FIG. 7B and the light transmission characteristic T21 at the lower end LW of the range of incident light on the optical path combining plane is detected by the anterior ocular segment observation system 5. This corresponds to the amount of return light below the axis. By setting the first peak wavelength λp1 and the second peak wavelength λp2 so that the first overlapping range and the second overlapping range have the same area, the brightness of the acquired anterior ocular segment image can be made uniform. it can.

<Configuration of processing system>
The configuration of the processing system of the ophthalmologic apparatus 1000 will be described. An example of the functional configuration of the processing system of the ophthalmologic apparatus 1000 is shown in FIG. FIG. 8 shows 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 are, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, SPLD (Simple Programmable L). And a circuit such as a field programmable gate array (FPGA). The processing unit 9 realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

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

  The moving mechanism 200 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a fixation projection system 4, an anterior ocular segment observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, an OCT optical system 8, and the like. This is a mechanism for moving the head portion in which the optical system is housed in the front-rear and left-right directions. For example, the moving mechanism 200 is provided with 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 configured by, for example, a combination of gears, a rack and pinion, or the like. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending a control signal to the actuator.

(Control unit 210)
The control unit 210 includes a processor and controls each unit of the ophthalmologic apparatus. The control unit 210 includes a main control unit 211 and a storage unit 212. The storage unit 212 stores in advance a computer program for controlling the ophthalmologic apparatus. The computer program includes 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. Controls for the Z alignment system 1 include control of the Z alignment light source 11 and control of the line sensor 13. 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. Control of the line sensor 13 includes exposure adjustment of the detection element, gain adjustment, detection rate adjustment, and the like. Thereby, lighting and non-lighting of the Z alignment light source 11 are switched, or the amount of light is changed. The main control unit 211 captures a signal detected by the line sensor 13 and specifies a projection position of light on the line sensor 13 based on the captured signal. The main control unit 211 obtains the position of the corneal apex of the eye E based on the specified projection position, and controls the moving mechanism 200 based on this to move the head unit in the front-rear direction (Z alignment).

  Control for the XY alignment system 2 includes control of the XY alignment light source 21 and the like. Control of the XY alignment light source 21 includes turning on / off the light source, adjusting the light amount, adjusting the aperture, and the like. Thereby, lighting and non-lighting of the XY alignment light source 21 are switched, or the light amount is changed. The main control unit 211 captures a signal detected by the image sensor 59 and identifies 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 so that 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) is canceled, so that the head unit moves in the horizontal and vertical directions. Move (XY alignment).

  Control for the kerato measurement system 3 includes control of the kerato ring light source 32 and the like. Control of the kerating 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 kerato ring light source 32 are switched or the light amount is changed. The main control unit 211 causes the arithmetic processing unit 220 to execute a known calculation on the keratling image detected by the image sensor 59. Thereby, the corneal shape parameter of the eye E is obtained.

  Control for the fixation projection system 4 includes control of the liquid crystal panel 41. Control of the liquid crystal panel 41 includes turning on and off the display of the fixation target and switching the display position of the fixation target. Thereby, the fixation target is projected onto the fundus oculi Ef of the eye E to be examined. For example, the fixation projection system 4 includes a moving mechanism that moves the liquid crystal panel 41 (or the liquid crystal panel 41 and the relay lens 42) in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves at least the liquid crystal panel 41 in the optical axis direction. Thereby, the position of the liquid crystal panel 41 is adjusted so that the liquid crystal panel 41 and the fundus oculi Ef are optically conjugate.

  Controls for the anterior ocular segment observation system 5 include control of the anterior ocular segment illumination light source 50 and control of the image sensor 59. Control of the anterior segment illumination light source 50 includes turning on and off the light source, adjusting the light amount, adjusting the aperture, and the like. Thereby, lighting and non-lighting of the anterior ocular segment illumination light source 50 (first illumination light source 50A, second illumination light source 50B) are switched or the light amount is changed. The main controller 211A can control lighting, extinguishing, light amount adjustment, aperture adjustment, and the like for only one of the first illumination light source 50A and the second illumination light source 50B. 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.

  Controls for the reflex measurement projection system 6 include control of the reflex measurement light source 61 and control of the rotary prism 66. Control of the reflex measurement light source 61 includes turning on / off the light source, adjusting the light amount, adjusting the aperture, and the like. Thereby, lighting and non-lighting of the reflex measurement light source 61 are switched, or the light quantity 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. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the 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 rotation control of the rotary prism 66 and the like. For example, a rotation mechanism that rotates the rotary prism 66 is provided, and the main control unit 211 rotates the rotary prism 66 by controlling the rotation mechanism.

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

  Control for the OCT optical system 8 includes control of the OCT light source 101, control of the optical scanner 88, control of the focusing lens 87, control of the corner cube 114, control of the detector 125, control of the DAQ 130, and the like. Control of the OCT light source 101 includes turning on / off the light source, adjusting the light amount, adjusting the aperture, and the like. Control of the optical scanner 88 includes control of the scanning position, scanning range, and scanning speed by the first galvanometer mirror, and control of the scanning position, scanning range, and scanning speed by the second galvanometer mirror. Control of the focusing lens 87 includes movement control of the focusing lens 87 in the optical axis direction. For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 87 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 87 in the optical axis direction. For example, the main control unit 211 may move only the focusing lens 87 based on the intensity of the interference signal after moving the focusing lens 87 in conjunction with the movement of the focusing lens 74. Control of the corner cube 114 includes movement control of the corner cube 114 along the optical path. For example, the OCT optical system 8 includes a moving mechanism that moves the corner cube 114 in a direction along the optical path. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the corner cube 114 in the direction along the optical path. Control of the detector 125 includes exposure adjustment of the detection element, gain adjustment, detection rate adjustment, and the like. The main control unit 211 samples the signal detected by the detector 125 by the DAQ 130 and causes the arithmetic processing unit 220 (image forming unit 222) to execute processing such as image formation based on the sampled signal.

  Further, the main control unit 211 performs processing for writing data into the storage unit 212 and processing for reading data from the storage unit 212.

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

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

  The eye refractive power calculation unit 221 is a ring image (pattern image) obtained by the imaging element 59 receiving the return light of the ring-shaped light beam (ring-shaped measurement pattern) projected onto the fundus oculi Ef by the reflex measurement projection system 6. ). For example, the eye refractive power calculation unit 221 obtains the barycentric position 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 barycentric position. The ring image is specified from this luminance distribution. Subsequently, the eye refractive power calculation unit 221 obtains an approximate ellipse of the identified ring image, and obtains the spherical power, the astigmatism power, and the astigmatism axis angle by substituting the major axis and minor axis of the approximate ellipse into known equations. . Alternatively, the eye refractive power calculation unit 221 can obtain the eye refractive power parameter based on the deformation and displacement of the ring image with respect to the reference pattern.

  Further, the eye refractive power calculation unit 221 calculates the corneal refractive power, the corneal astigmatism, and the corneal astigmatism axis angle based on the keratoling image acquired by the anterior eye part observation system 5. For example, the eye refractive power calculation unit 221 calculates the corneal curvature radius of the strong main meridian and the weak main meridian on the front surface of the cornea by analyzing the keratling image, and calculates the parameter based on the corneal curvature radius.

  The image forming unit 222 forms tomographic image data 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 process includes processes such as filter processing and FFT (Fast Fourier Transform) as in the conventional spectral domain type OCT. The image data acquired in this way is a data set including a group of image data formed by imaging reflection intensity profiles in a plurality of A lines (paths of the measurement light LS in the eye E). is there.

  In order to improve the image quality, it is possible to superimpose (addition average) a plurality of data sets acquired by repeating scanning with the same pattern a plurality of times.

  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 executes correction processing such as image luminance correction and dispersion correction. In addition, the data processing unit 223 performs various image processing and analysis processing on an image (anterior segment image or the like) obtained using the anterior 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 line-of-sight direction.

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

  The operation unit 280 is used as a user interface unit for operating the ophthalmologic apparatus. The operation unit 280 includes various hardware keys (joysticks, buttons, switches, etc.) provided in the ophthalmologic apparatus. The operation unit 280 may include various software keys (buttons, icons, menus, etc.) displayed on the touch-panel display screen 10a.

  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 corresponding to a connection form with an external device. As an example of the external device, there is a spectacle lens measurement device for measuring optical characteristics of a lens. The spectacle lens measurement device measures the power of the spectacle lens worn by the subject and inputs this measurement data to the ophthalmologic apparatus 1000. The external device may be an arbitrary ophthalmic device, a device that reads information from a recording medium (reader), a device that writes information to a recording medium (writer), or the like. 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 the processing unit 9, for example.

  The ref measurement optical system or the OCT optical system 8 is an example of the “inspection optical system” according to the embodiment. The dichroic mirror 52 is an example of an “optical path combining member” according to the embodiment. The anterior segment illumination light source 50 is an example of the “anterior segment illumination system” according to the embodiment. The optical system included in the OCT unit 100 is an example of the “interference optical system” according to the embodiment.

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

  FIG. 9 shows an example of the operation of the ophthalmologic apparatus 1000. FIG. 9 shows a flowchart of an operation example of the ophthalmologic apparatus 1000.

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

  Specifically, the main control unit 211 turns on the Z alignment light source 11 and the XY alignment light source 21. Further, the main control unit 211 turns on the anterior segment illumination light source 50. Thereby, the anterior segment of the eye E is illuminated by the first illumination light source 50A and the second illumination light source 50B. The processing unit 9 acquires an imaging signal of the anterior segment image on the imaging surface of the imaging element 59 and causes the display unit 270 to display the anterior segment image. Thereafter, the optical system shown in FIG. 1 is moved to the inspection position of the eye E. The inspection position is a position where the eye E can be inspected with sufficient accuracy. The eye E to be examined is arranged at the examination position through the above-described alignment (alignment by the Z alignment system 1, 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 the user or an instruction from the control unit 210. That is, the movement of the optical system to the examination position of the eye E and preparation for objective measurement are performed.

  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) along the respective optical axes.

(S2: Fixation control)
In step S2, 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 gaze at a desired fixation position.

  Note that following the fixation control in step S2, the ophthalmologic apparatus 1000 may perform kerato measurement. In this case, the main control unit 211 turns on the kerattling light source 32. When light is output from the kerato ring light source 32, a ring-shaped light beam for corneal shape measurement is projected onto the cornea Cr of the eye E to be examined. The eye refractive power calculation unit 221 calculates a corneal curvature radius by performing an arithmetic process on the image acquired by the image sensor 59, and calculates the corneal refractive power, the corneal astigmatism, and the 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 according to an instruction from the main control unit 211 or a user operation or instruction to the operation unit 280.

(S3: Objective measurement)
Next, the main control unit 211 controls the liquid crystal panel 41 to cause the fixation target to be projected onto the eye E to be subjected to the reflex measurement.

  In the reflex measurement, the main control unit 211 projects the ring-shaped measurement pattern light beam for reflex measurement onto the eye E as described above. A ring image based on the return light of the measurement pattern light beam from the eye E is formed on the imaging surface of the image sensor 59. The main control unit 211 determines whether or not a ring image based on the return light from the fundus oculi Ef detected by the image sensor 59 has been acquired. For example, the main control unit 211 detects the position (pixel) of the edge of the image based on the return light detected by the image sensor 59, and whether the width of the image (difference between the outer diameter and the inner diameter) is a predetermined value or more. Determine whether or not. Alternatively, the main control unit 211 determines whether or not a ring image has been acquired by determining whether or not a ring can be formed based on a point (image) that is equal to or greater than a predetermined height (ring diameter). Also good.

  When it is determined that the ring image has been acquired, the eye refractive power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern light beam projected onto the eye E by a known method, and calculates the provisional spherical power S and A provisional astigmatism power C is obtained. Based on the obtained temporary spherical power S and astigmatic power C, 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) (temporary distance). To the position corresponding to the point). The main control unit 211 moves the liquid crystal panel 41 further from the position to the cloud position, and then acquires the ring image again by controlling the reflex measurement projection system 6 and the reflex measurement light receiving system 7 as the main measurement. The main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, the astigmatism power, and the astigmatism axis angle from the analysis result of the ring image obtained in the same manner as described above and the moving amount of the focusing lens 74.

  Further, the eye refractive power calculation unit 221 obtains a position corresponding to the far point of the eye E (position corresponding to the far point obtained by this measurement) from the obtained spherical power and astigmatism power. The main control unit 211 moves the liquid crystal panel 41 to a position corresponding to the obtained far point. In the control unit 210, the position of the focusing lens 74, the calculated spherical power, and the like are stored in the storage unit 212. The operation of the ophthalmologic apparatus 1000 proceeds to step S4 according to an instruction from the main control unit 211 or a user operation or instruction to the operation unit 280.

  When it is determined that the ring image cannot be acquired, the main control unit 211 considers the possibility of being an intensity refraction anomalous eye, and sets the reflex measurement light source 61 and the focusing lens 74 in advance at the minus power side (for example, −10D), and move to the plus power side (for example, + 10D). The main controller 211 controls the reflex measurement light receiving system 7 to detect a ring image at each position. If it is still determined that a ring image cannot be acquired, the main control unit 211 executes predetermined measurement error processing. At this time, the operation of the ophthalmologic apparatus 1000 may move to step S4. In the control unit 210, information indicating that the ref measurement result has not been obtained is stored in the storage unit 212.

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

(S4: Tomography)
In step S4, the main control unit 211 controls the liquid crystal panel 41 to project the fixation target onto the eye E and execute OCT measurement.

  The main control unit 211 turns on the OCT light source 101 and controls the optical scanner 88 to scan a predetermined part 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 signal. Thus, the operation of the ophthalmologic apparatus 1000 ends (END).

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

  An ophthalmic apparatus (1000) according to some embodiments includes an objective lens (51), an anterior ocular segment observation system (5), an inspection optical system (OCT optical system 8 or a reflex measurement optical system), and an optical path synthesis member. (Dichroic mirror 52) and an anterior segment illumination system (anterior segment illumination light source 50). The anterior ocular segment observation system detects first return light of illumination light from the anterior ocular segment of the eye to be examined (E) via the objective lens. The inspection optical system projects light onto the eye to be examined via the objective lens, and detects second return light from the eye to be examined. The optical path synthesis member synthesizes the optical path of the inspection optical system and the optical path of the anterior ocular segment observation system on an optical path synthesis surface arranged to be inclined with respect to the optical axis of the objective lens. The anterior ocular segment illumination system illuminates the anterior ocular segment with illumination light in a wavelength range including a wavelength corresponding to the incident angle of the first return light with respect to the optical path combining surface.

  According to such a configuration, illumination in a wavelength range including a wavelength corresponding to the incident angle of the first return light with respect to the optical path combining surface of the optical path combining member that combines the optical path of the inspection optical system and the optical path of the anterior ocular segment observation system. Since the anterior segment is illuminated with light, it compensates for a decrease in the amount of light to the anterior segment observation system due to the wavelength shift due to the incident angle dependence on the optical path synthesis surface, and improves the image quality of the anterior segment observation image It becomes possible.

  In the ophthalmologic apparatus according to some embodiments, the anterior ocular segment illumination system is shifted in wavelength by a shift corresponding to the incident angle with respect to the reference transmission center wavelength (λ0) based on the light transmission characteristics on the optical path combining surface. The anterior ocular segment is illuminated with illumination light in a wavelength range including peak wavelengths (λp1, λp2) corresponding to the transmission center wavelengths (first transmission center wavelength, second transmission center wavelength).

  According to such a configuration, the transmission center wavelength corresponding to the shift corresponding to the incident angle of the first return light is supported with respect to the reference transmission center wavelength specified from the transmission characteristic with respect to the incident angle on the optical path combining surface. Because the anterior segment is illuminated with illumination light in the wavelength range including the peak wavelength, it is possible to accurately compensate for the decrease in the amount of light to the anterior segment observation system due to the wavelength shift caused by the incident angle dependency on the optical path synthesis surface. can do.

  In the ophthalmologic apparatus according to some embodiments, an optical film is formed on the optical path combining surface so that the film thickness changes according to the position of the light incident end surface so as to compensate for the incident angle dependency of the second return light. Is formed.

  According to such a configuration, even when an inclined film is formed on the optical path synthesis surface, the illumination light in the wavelength range including the peak wavelength corresponding to the incident angle of the first return light with respect to the optical path synthesis surface is used. Since the eye part is illuminated, it compensates the light amount drop to the anterior ocular segment observation system due to the wavelength shift due to the incident angle dependence on the optical path combining surface while compensating the light amount drop to the inspection optical system. It is possible to improve the image quality of the partial observation image.

  In the ophthalmologic apparatus according to some embodiments, an optical film is formed on the optical path combining surface so that the film thickness changes according to the position of the light incident end surface so as to compensate for the incident angle dependency of the second return light. It is formed. The anterior ocular segment illumination system has a wavelength corresponding to a shift corresponding to the upper end (UP) of the incident angle of the first return light with respect to the optical path combining surface with respect to the reference transmission center wavelength (λ0) based on the light transmission characteristics on the optical path combining surface. The second transmission center whose wavelength is shifted by an amount corresponding to the first peak wavelength (λp1) corresponding to the shifted first transmission center wavelength and the shift corresponding to the lower end (LW) of the incident angle with respect to the optical path combining surface with respect to the reference transmission center wavelength. The anterior segment is illuminated with illumination light in a wavelength range including the second peak wavelength (λp2) corresponding to the wavelength.

  According to such a configuration, the incident angle of the first return light with respect to the optical path combining surface is obtained even when the inclined film is formed on the optical path combining surface to compensate the incident angle dependency of the second return light. Since the anterior ocular segment is illuminated with illumination light in a wavelength range including the peak wavelength corresponding to the upper end and lower end of the range, the incidence angle dependency on the optical path combining surface is compensated while compensating for the light amount reduction to the inspection optical system. It is possible to compensate for a decrease in the amount of light to the anterior ocular segment observation system due to the resulting wavelength shift.

  In the ophthalmologic apparatus according to some embodiments, the examination optical system divides the light from the light source (OCT light source 101) into reference light (LR) and measurement light (LS), and applies it to the eye to be examined through the objective lens. An interference optical system that projects measurement light and detects interference light (LC) between the return light of the measurement light from the eye to be examined and the reference light is included.

  According to such a configuration, it is possible to compensate for the light amount decrease to the anterior ocular segment observation system due to the wavelength shift caused by the incident angle dependency on the optical path combining surface while compensating for the light amount decrease to the interference optical system.

  In the ophthalmologic apparatus according to some embodiments, the interference optical system divides the light from the wavelength swept light source into reference light and measurement light, projects the measurement light to the eye to be examined, and returns the measurement light from the eye to be examined. Interference light between light and reference light is detected.

  According to such a configuration, the anterior ocular segment observation system due to the wavelength shift due to the incident angle dependence on the optical path combining surface is compensated for while compensating for the light amount reduction to the interference optical system capable of the swept source type optical coherence tomography. Can be compensated for.

  In the ophthalmologic apparatus according to some embodiments, the anterior ocular segment illumination system includes a first illumination light source (50A) that emits illumination light in a wavelength range including a first peak wavelength, and a wavelength range that includes a second peak wavelength. And a second illumination light source (50B) that emits illumination light.

  According to such a configuration, the first illumination light source and the second illumination light source compensate for a decrease in the amount of light to the anterior ocular segment observation system due to the wavelength shift corresponding to the upper end and the lower end of the incident angle range with a simple configuration. be able to.

  According to such a configuration, it is possible to reliably compensate for the light amount reduction to the anterior ocular segment observation system due to the wavelength shift corresponding to the upper end and the lower end of the incident angle range.

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

DESCRIPTION OF SYMBOLS 1 Z alignment system 2 XY alignment system 3 Kerat measurement system 4 Fixation projection system 5 Anterior eye part observation system 6 Ref measurement projection system 7 Ref measurement light reception system 8 OCT optical system 9 Processing part 51 Objective lens 52 Dichroic mirror 210 Control part 211 Main control unit 1000 Ophthalmic device

Claims (7)

An objective lens;
An anterior ocular segment observation system for detecting first return light of illumination light from the anterior ocular segment of the eye to be examined via the objective lens;
An inspection optical system that projects light onto the eye to be examined through the objective lens and detects second return light from the eye to be examined;
An optical path combining member that combines the optical path of the inspection optical system and the optical path of the anterior ocular segment observation system on an optical path combining surface arranged to be inclined with respect to the optical axis of the objective lens;
An anterior segment illumination system that illuminates the anterior segment with illumination light in a wavelength range including a transmission center wavelength corresponding to an incident angle of the first return light with respect to the optical path combining surface;
Ophthalmic device. The anterior ocular segment illumination system has a wavelength including a peak wavelength corresponding to a transmission center wavelength in which a wavelength is shifted by a shift corresponding to the incident angle with respect to a reference transmission center wavelength based on light transmission characteristics on the optical path combining surface. The ophthalmologic apparatus according to claim 1, wherein the anterior segment is illuminated with a range of illumination light. An optical film is formed on the optical path combining surface so that the film thickness changes according to the position of the light incident end face so as to compensate for the incident angle dependency of the second return light. The ophthalmologic apparatus according to claim 1 or 2. An optical film is formed on the optical path combining surface so that the film thickness changes according to the position of the incident end surface of the light so as to compensate for the incident angle dependency of the second return light,
In the anterior segment illumination system, the wavelength is shifted by a shift corresponding to the upper end of the incident angle of the first return light with respect to the optical path combining surface with respect to the reference transmission center wavelength based on the light transmission characteristics in the optical path combining surface. The first peak wavelength corresponding to the first transmission center wavelength and the second transmission center wavelength corresponding to the second transmission center wavelength shifted by the shift corresponding to the lower end of the incident angle with respect to the optical path combining surface with respect to the reference transmission center wavelength. The ophthalmologic apparatus according to claim 1, wherein the anterior segment is illuminated with illumination light in a wavelength range including two peak wavelengths. The inspection optical system divides light from a light source into reference light and measurement light, projects the measurement light onto the eye to be examined through the objective lens, and returns light of the measurement light from the eye to be examined and the The ophthalmologic apparatus according to claim 4, further comprising an interference optical system that detects interference light with reference light. The interference optical system divides light from a wavelength swept light source into reference light and measurement light, projects the measurement light onto the eye to be examined, and returns the measurement light from the eye to be examined and the reference light. The ophthalmic apparatus according to claim 5, wherein interference light is detected. The anterior ocular segment illumination system is
A first illumination light source that emits illumination light in a wavelength range including the first peak wavelength;
A second illumination light source for irradiating illumination light in a wavelength range including the second peak wavelength;
The ophthalmologic apparatus according to any one of claims 4 to 6, wherein the ophthalmologic apparatus is included.

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