JP7412170B2 - Ophthalmological equipment, its evaluation method, program, and recording medium - Google Patents

Description

The present invention relates to an ophthalmologic apparatus, an evaluation method thereof, a program, and a recording medium.

Various types of equipment are used in ophthalmological treatment, typically imaging equipment and measuring equipment. The imaging device is an ophthalmological device for acquiring an image of the eye to be examined, and examples thereof include an optical coherence tomography (OCT) device, a fundus camera, and a scanning laser ophthalmoscope (SLO). The measurement device is an ophthalmological device for measuring the characteristics of the eye to be examined, and examples thereof include an eye refraction measurement device (refractometer, keratometer), tonometer, specular microscope, wavefront analyzer, and the like.

Such ophthalmological devices are precision instruments, and in order to fully demonstrate their performance, adjustments and calibrations based on rigorous evaluation are required. Although there are various methods for evaluating ophthalmological devices, a method using a model eye is widely used (see, for example, Patent Document 1).

In order to properly perform evaluation using a model eye, it is necessary to accurately place the model eye in relation to the optical system of the ophthalmological device to be evaluated. This required complicated work.

Japanese Patent Application Publication No. 2012-110575

An object of the present invention is to facilitate the evaluation work of an ophthalmological apparatus using a model eye.

Some exemplary aspects include an optical system for acquiring eye data, an alignment system for aligning the optical system with respect to a model eye placed in a predetermined position, and an alignment system for aligning the optical system after the alignment. and an evaluation unit that generates evaluation information based on the data of the model eye acquired by the ophthalmology apparatus.

In some exemplary embodiments, the ophthalmological device may further include a chin rest on which the subject's chin rests, and a first attachment attachable to the chin rest, and a first attachment attached to the first attachment. The model eye may be attached.

In some exemplary embodiments, the ophthalmological apparatus may further include a forehead rest to which the forehead of the subject is applied, and a second attachment attachable to the forehead rest, and the second attachment has the A model eye may be attached.

In some exemplary embodiments, the alignment system includes a moving mechanism that moves the optical system, a first imaging unit that photographs the model eye from two or more different directions, and an image captured by the first imaging unit. and a first processing section that controls the movement mechanism based on two or more images of the model eye.

In some exemplary embodiments, the model eye may include a corneal portion that corresponds to the cornea, and an iris portion that corresponds to the iris and forms an opening that corresponds to the pupil. An entrance pupil of the aperture may be located approximately 3.06 millimeters from the cornea. The diameter of the opening may be set to a value within the range of 2 to 10 mm. The infrared light reflectance of the iris portion may be set to a value within a range of 2.0 to 2.5 percent. The first imaging unit may be sensitive to infrared wavelengths. The first processing unit specifies a pupil area in each of the two or more images, calculates a three-dimensional movement amount of the optical system based on the two or more specified pupil areas, and calculates a three-dimensional movement amount of the optical system based on the three-dimensional movement amount. The moving mechanism may be configured to be controlled based on the movement mechanism.

In some exemplary embodiments, the alignment system includes a moving mechanism that moves the optical system, a projection unit that projects a light beam onto the model eye, a second imaging unit that photographs the model eye, and a second imaging unit that photographs the model eye. and a second processing section that controls the moving mechanism based on the image acquired by the second imaging section.

In some exemplary embodiments, the model eye may include a corneal portion corresponding to the cornea. The corneal portion may have a radius of curvature of approximately 7.7 millimeters. The projection section may include a first projection section that projects a light beam onto the model eye from the front. The second processing unit is configured to identify a reflected image of the light beam by the cornea in the image acquired by the second imaging unit, and to control the moving mechanism based on the identified reflected image. It's okay.

In some exemplary embodiments, the model eye may include a corneal portion corresponding to the cornea. The corneal portion may have a radius of curvature of approximately 7.7 millimeters. The projection section may include a second projection section that projects a light beam obliquely onto the model eye. The second imaging unit may include a line sensor or an area sensor arranged in a direction substantially symmetrical to the projection direction of the light beam with respect to the optical axis of the optical system. The second processing section may be configured to control the moving mechanism based on a position of a light receiving element of the line sensor or the area sensor that detects the reflected light of the luminous flux by the cornea section.

In some exemplary embodiments, the model eye may include a left model eye corresponding to the left eye and a right model eye corresponding to the right eye. The ophthalmological apparatus may further include a third attachment that sets the left model eye at a first position and sets the right model eye at a second position.

In some exemplary aspects, the evaluation unit may be configured to generate first evaluation information indicative of the quality of data acquired by the optical system.

In some exemplary aspects, the evaluation unit may be configured to generate second evaluation information indicative of the quality of alignment performed by the alignment system.

Some exemplary aspects are a method of evaluating the performance of an ophthalmological device including an optical system for acquiring ocular data, the method comprising: installing a model eye at a predetermined position; The optical system is aligned with respect to the eye, and evaluation information is generated based on data of the model eye acquired by the optical system after the alignment.

In some exemplary embodiments, the step of installing the model eye at the predetermined position includes the step of attaching a first attachment to the chin rest of the ophthalmological device, and the step of attaching the model eye to the first attachment. It may contain.

In some exemplary embodiments, the step of installing the model eye at the predetermined position includes a step of attaching a second attachment to the forehead rest of the ophthalmological device, and a step of attaching the model eye to the second attachment. It may contain.

In some exemplary embodiments, the step of performing the alignment includes the step of photographing the model eye from two or more different directions, and the step of photographing the model eye from two or more different directions. The method may include a step of moving the optical system based on the image.

In some exemplary embodiments, the model eye may include a corneal portion that corresponds to the cornea, and an iris portion that corresponds to the iris and forms an opening that corresponds to the pupil. An entrance pupil of the aperture may be located approximately 3.06 millimeters from the corneal portion. The diameter of the opening may be set to a value within the range of 2 to 10 millimeters. The infrared light reflectance of the iris portion may be set to a value within a range of 2.0 to 2.5 percent. The step of photographing the model eye from two or more different directions may include photographing that is sensitive to infrared wavelengths. The step of moving the optical system based on the two or more images includes the step of specifying a pupil area in each of the two or more images, and the step of moving the optical system based on the two or more specified pupil areas. The method may include the steps of calculating the amount of movement and moving the optical system based on the amount of three-dimensional movement.

In some exemplary embodiments, the step of performing the alignment includes a step of projecting a light beam onto the model eye, a step of photographing the model eye, and a step of performing the alignment based on an image obtained by photographing the model eye. The method may include a step of moving the optical system.

In some exemplary embodiments, the model eye may include a corneal portion corresponding to the cornea. The corneal portion may have a radius of curvature of approximately 7.7 millimeters. The step of projecting the light beam may include the step of projecting the light beam onto the model eye from the front. The step of moving the optical system includes a step of identifying a reflected image of the light beam by the cornea in the image obtained by photographing the model eye, and moving the optical system based on the identified reflected image. It may include a step of.

In some exemplary embodiments, the model eye may include a corneal portion corresponding to the cornea. The corneal portion may have a radius of curvature of approximately 7.7 millimeters. The step of projecting the light beam may include the step of projecting the light beam obliquely onto the model eye. The step of photographing the model eye includes the step of detecting the reflected light of the light beam by the cornea portion using a line sensor or an area sensor arranged in a direction substantially symmetrical to the projection direction of the light beam with respect to the optical axis of the optical system. It may be included. The step of moving the optical system may include the step of moving the optical system based on the position of a light receiving element of the line sensor or the area sensor that has detected the reflected light.

In some exemplary embodiments, the model eye may include a left model eye corresponding to the left eye and a right model eye corresponding to the right eye. The step of installing the model eye at the predetermined position includes the step of attaching a third attachment to the ophthalmological apparatus, and attaching the left model eye to the third attachment and installing the left model eye at the first position. and a step of attaching the right model eye to the third attachment and installing the right model eye at a second position.

In some exemplary aspects, generating the evaluation information may include generating first evaluation information indicative of the quality of data acquired by the optical system.

In some exemplary aspects, generating the evaluation information may include generating second evaluation information indicating the quality of alignment performed by the alignment system.

Some example aspects are programs that cause an ophthalmological apparatus to perform the evaluation method of any aspect.

Some example embodiments are computer readable non-transitory storage media having a program of any embodiment recorded thereon.

According to some exemplary aspects, it is possible to facilitate the evaluation work of an ophthalmological device using a model eye.

FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 2 is a schematic diagram illustrating an example of the configuration of a model eye for evaluating an ophthalmologic apparatus according to an exemplary aspect of the embodiment. FIG. 2 is a schematic diagram illustrating an example of a configuration for attaching a model eye to an ophthalmological apparatus according to an exemplary aspect of the embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. FIG. 1 is a schematic diagram illustrating an example of the configuration of an ophthalmologic apparatus according to an exemplary aspect of an embodiment. 3 is a flowchart illustrating an example of operations that can be performed by an ophthalmologic apparatus according to an exemplary aspect of an embodiment.

Some exemplary aspects of the ophthalmological apparatus, its evaluation method, program, and recording medium according to the embodiment will be described. In the exemplary embodiments detailed below, an ophthalmologic device that combines an optical coherence tomography (OCT) device and a fundus camera is featured, but the ophthalmologic device according to the embodiments is not limited thereto, , measurement, etc.) and an alignment function.

Although spectral domain OCT is employed in the OCT device included in the ophthalmic device of exemplary embodiments described in detail below, the type of OCT applicable to the ophthalmic device according to the embodiment is not limited to spectral domain OCT. , for example, swept source OCT.

Spectral domain OCT splits light from a low-coherence light source into measurement light and reference light, and superimposes the return light of the measurement light from the object on the reference light to generate interference light. This is a method in which the spectral distribution of spectral distribution is detected using a spectrometer, and the detected spectral distribution is subjected to Fourier transform or the like to form an image.

In contrast, swept source OCT splits the light from a wavelength tunable light source into measurement light and reference light, and superimposes the return light of the measurement light from the test object on the reference light to generate interference light. This is a method in which interference light is detected with a photodetector such as a balanced photodiode, and an image is formed by performing Fourier transform or the like on the detection data collected according to wavelength sweeps and measurement light scans.

In this way, spectral domain OCT is an OCT technique that acquires a spectral distribution by spatial division, and swept source OCT is an OCT technique that acquires a spectral distribution by time division.

In this specification, unless otherwise specified, "image data" and "image" which is visualization information based on the image data are not distinguished. Further, unless otherwise specified, no distinction is made between the site or tissue of the eye to be examined and the corresponding portion of the model eye. Similarly, the part or tissue of the eye to be examined and the image that visualizes it are not distinguished, and the part of the model eye and the image that is visualized are not distinguished.

<composition>
An exemplary embodiment of an ophthalmic device is shown in FIG. The ophthalmological apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system and mechanism for acquiring a front image of the eye E to be examined, and an optical system and mechanism for performing OCT. The OCT unit 100 is provided with an optical system and mechanism for performing OCT. Arithmetic control unit 200 includes one or more processors configured to perform various types of processing (arithmetic operations, control, etc.). Further, the ophthalmological apparatus 1 includes two anterior eye cameras 300 for photographing the anterior eye from two different directions.

The fundus camera unit 2 is provided with a chin rest and a forehead rest for holding the subject's face. The chin rest and forehead rest correspond to the face holding part 450 shown in FIGS. 4A and 4B. The base 310 houses a drive mechanism and an arithmetic control circuit. An optical system is housed in a housing 320 provided on the base 310. The objective lens 22 is accommodated in a lens accommodating portion 330 provided protruding from the front surface of the housing 320 .

Furthermore, the ophthalmologic apparatus 1 includes a lens unit for switching the region to which OCT is applied. Specifically, the ophthalmologic apparatus 1 includes an anterior segment OCT attachment 400 for applying OCT to the anterior segment of the eye. The anterior segment OCT attachment 400 may be configured in the same manner as the optical unit disclosed in JP-A-2015-160103, for example.

As shown in FIG. 1, the anterior segment OCT attachment 400 can be placed between the objective lens 22 and the eye E to be examined. When the anterior segment OCT attachment 400 is placed in the optical path, the ophthalmologic apparatus 1 can apply OCT scanning to the anterior segment. On the other hand, when the anterior segment OCT attachment 400 is retracted from the optical path, the ophthalmologic apparatus 1 can apply OCT scanning to the posterior segment. The anterior segment OCT attachment 400 is moved manually or automatically.

In some embodiments, an OCT scan can be applied to the posterior segment when the attachment is placed in the optical path, and an OCT scan can be applied to the anterior segment when the attachment is retracted from the optical path. It's good. Furthermore, the measurement site that can be switched by the attachment is not limited to the posterior segment and the anterior segment, but may be any location on the eye. Note that the configuration for switching the region to which OCT scanning is applied is not limited to such an attachment, and for example, a configuration that includes a lens that is movable along the optical path, or a lens that can be inserted and removed from the optical path. It is also possible to adopt a configuration with the following.

At least some of the functionality of the elements disclosed herein is implemented using circuitry or processing circuitry. The circuitry or processing circuitry may include a general purpose processor, special purpose processor, integrated circuit, central processing unit (CPU), graphics processing unit (GPU) configured and/or programmed to perform at least a portion of the disclosed functions. ), ASIC (Application Specific Integrated Circuit), programmable logic devices (for example, SPLD (Simple Programmable Logic Device), CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array), conventional circuit configurations, and any of these A processor is considered to be a processing circuitry or circuitry that includes transistors and/or other circuitry. In this disclosure, the term circuitry, unit, means, or similar terminology refers to the disclosure Hardware that performs at least some of the functions disclosed herein, or hardware that is programmed to perform at least some of the functions disclosed. or may be known hardware programmed and/or configured to perform at least some of the functions described.A processor where the hardware may be considered a type of circuitry. , the term circuitry, unit, means, or similar terms is a combination of hardware and software, the software being used to configure the hardware and/or the processor.

<Funus camera unit 2>
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef (and anterior segment) of the eye E to be examined. The acquired digital image of the fundus Ef (referred to as a fundus image, fundus photograph, etc.) is generally a frontal image such as an observation image or a photographed image. Observation images are obtained by video shooting using near-infrared light. The photographed image is a still image using flash light in the visible range.

The fundus camera unit 2 includes an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the eye E to be examined with illumination light. The photographing optical system 30 detects the return light of the illumination light irradiated onto the eye E to be examined. The measurement light from the OCT unit 100 is guided to the eye E through the optical path within the fundus camera unit 2. The return light of the measurement light projected onto the eye E to be examined (for example, the fundus Ef) is guided to the OCT unit 100 through the same optical path within the fundus camera unit 2.

Light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by the concave mirror 12, passes through the condensing lens 13, and passes through the visible cut filter 14 to become near-infrared light. Further, the observation illumination light is once focused in the vicinity of the photographing light source 15, is reflected by a mirror 16, and passes through a relay lens system 17, a relay lens 18, an aperture 19, and a relay lens system 20 to an apertured mirror 21. be guided. The observation illumination light is reflected at the periphery of the apertured mirror 21 (the area around the aperture), passes through the dichroic mirror 46, and is refracted by the objective lens 22 to illuminate the eye E (fundus Ef). do. The return light of the observation illumination light from the subject's eye E is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the center area of the perforated mirror 21, and passes through the dichroic mirror 55. , passes through the photographic focusing lens 31 and is reflected by the mirror 32. Further, this returned light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is imaged by the imaging lens 34 on the light receiving surface of the image sensor 35. The image sensor 35 detects the returned light at a predetermined frame rate. The focus of the imaging optical system 30 can be adjusted to match the fundus Ef or its vicinity, and can also be adjusted to match the anterior segment of the eye or its vicinity.

The light output from the photographing light source 15 (photographing illumination light) passes through the same path as the observation illumination light and is irradiated onto the fundus Ef. The return light of the imaging illumination light from the eye E is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the imaging lens 37. An image is formed on the light receiving surface of the image sensor 38.

A liquid crystal display (LCD) 39 displays a fixation target (fixation target image). A portion of the light beam output from the LCD 39 is reflected by the half mirror 33A, then reflected by the mirror 32, passes through the photographic focusing lens 31 and the dichroic mirror 55, and then passes through the hole of the perforated mirror 21. The light beam that has passed through the hole of the perforated mirror 21 is transmitted through the dichroic mirror 46, refracted by the objective lens 22, and projected onto the fundus Ef. Fixation targets are typically used to guide and fix the line of sight. The direction in which the line of sight of the eye E to be examined is guided (and fixed), that is, the direction in which fixation of the eye E to be examined is encouraged is called a fixation position.

The fixation position can be changed by changing the display position of the fixation target image on the screen of the LCD 39. Examples of fixation positions include a fixation position for acquiring an image centered on the macula, a fixation position for acquiring an image centered on the optic disc, and a position between the macula and the optic disc ( These include a fixation position for acquiring an image centered on the fundus (center of the fundus) and a fixation position for acquiring an image of a region far away from the macula (periphery of the fundus).

A graphical user interface (GUI) or the like may be provided for specifying at least one of such typical fixation positions. Further, a GUI or the like for manually moving the fixation position (the display position of the fixation target) can be provided. Furthermore, it is also possible to apply a configuration in which the fixation position is automatically set.

The configuration for presenting the eye E with a fixation target whose fixation position can be changed is not limited to a display device such as an LCD. For example, a device (fixation matrix) in which a plurality of light emitting parts (such as light emitting diodes) are arranged in a matrix can be used instead of the display device. In this case, by selectively lighting up the plurality of light emitting units, the fixation position of the eye E to be examined based on the fixation target can be changed. As another example, a fixation target whose fixation position can be changed can be generated by a device including one or more movable light emitting parts.

The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E to be examined. The alignment light output from the light emitting diode (LED) 51 passes through the aperture 52 , the aperture 53 , and the relay lens 54 , is reflected by the dichroic mirror 55 , passes through the hole of the perforated mirror 21 , and passes through the dichroic mirror 46 . The light is transmitted through the objective lens 22 and projected onto the eye E to be examined. The return light of the alignment light from the eye E is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment or auto alignment can be performed based on the received light image (alignment index image).

Note that the alignment method that can be applied to the embodiment is not limited to using such an alignment index, but also a method that uses the anterior segment camera 300 or a method that is formed by projecting a light beam onto the cornea from the front. Any known method may be used, such as a method using a corneal reflection image (Purkinje image) or a method using an optical lever that projects a light beam onto the cornea obliquely and detects the corneal reflection light in the opposite direction. .

The focus optical system 60 generates a split index used for focus adjustment for the eye E to be examined. In conjunction with the movement of the photographing focusing lens 31 along the optical path of the photographing optical system 30 (photographing optical path), the focusing optical system 60 is moved along the optical path of the illumination optical system 10 (illumination optical path). The reflection rod 67 is inserted into and removed from the illumination optical path. When performing focus adjustment, the reflective surface of the reflective rod 67 is arranged at an angle to the illumination optical path. The focus light output from the LED 61 passes through a relay lens 62 , is separated into two beams by a split indicator plate 63 , passes through a two-hole diaphragm 64 , is reflected by a mirror 65 , and is reflected by a condensing lens 66 into a reflecting rod 67 . Once the image is formed on the reflective surface of the image, it is reflected. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, passes through the dichroic mirror 46, and is projected onto the eye E via the objective lens 22. The return light of the focus light from the eye E to be examined (fundus reflected light, etc.) is guided to the image sensor 35 through the same path as the return light of the alignment light. Manual focusing or autofocusing can be performed based on the received light image (split index image).

Diopter correction lenses 70 and 71 can be selectively inserted into the photographing optical path between the perforated mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus lens (convex lens) for correcting severe hyperopia. The diopter correction lens 71 is a minus lens (concave lens) for correcting severe myopia.

The dichroic mirror 46 combines the fundus photographing optical path and the OCT optical path (measuring arm). The dichroic mirror 46 reflects light in a wavelength band used for OCT and transmits light for fundus photography. The measurement arm is provided with a collimator lens unit 40, a retroreflector 41, a dispersion compensation member 42, an OCT focusing lens 43, an optical scanner 44, and a relay lens 45 in this order from the OCT unit 100 side.

The retroreflector 41 is movable along the optical path of the measurement light LS incident thereon, thereby changing the length of the measurement arm. Changing the measurement arm length is used, for example, to correct the optical path length according to the axial length or to adjust the interference state.

The dispersion compensation member 42 acts together with a dispersion compensation member 113 (described later) disposed on the reference arm to match the dispersion characteristics of the measurement light LS and the dispersion characteristics of the reference light LR.

The OCT focusing lens 43 is moved along the measurement arm to perform focus adjustment of the measurement arm. Note that the movement of the imaging focusing lens 31, the movement of the focusing optical system 60, and the movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

The optical scanner 44 is arranged at a position that is substantially optically conjugate with the pupil of the eye E to be examined. The optical scanner 44 deflects the measurement light LS guided by the measurement arm. The optical scanner 44 is, for example, a galvano scanner capable of two-dimensional scanning. Typically, the optical scanner 44 includes a one-dimensional scanner (x-scanner) for deflecting measurement light in the ±x direction and a one-dimensional scanner (y-scanner) for deflecting the measurement light in the ±y direction. including. In this case, for example, either one of these one-dimensional scanners is placed at a position optically conjugate to the pupil, or a position optically conjugate to the pupil is placed between these one-dimensional scanners.

<OCT unit 100>
The exemplary OCT unit 100 shown in FIG. 2 is equipped with an optical system for performing spectral domain OCT. This optical system includes an interference optical system. This interference optical system splits light from a low-coherence light source (broadband light source) into measurement light and reference light, and overlaps the return light of the measurement light projected onto the eye E with the reference light that has passed through the reference optical path. Together, they generate interference light. The spectral distribution of the interference light generated by the interference optical system is detected by a spectrometer. Data (detection signal) obtained by detecting the spectral distribution of the interference light is sent to the arithmetic and control unit 200.

The light source unit 101 outputs broadband low coherence light L0. The low coherence light L0 includes, for example, a wavelength band in the near-infrared region (about 800 nm to 900 nm), and has a temporal coherence length of about several tens of micrometers. Note that the low coherence light L0 may be near-infrared light having a wavelength band that is invisible to the human eye, for example, a center wavelength of about 1040 to 1060 nm. The light source unit 101 includes light output devices such as a superluminescent diode (SLD), an LED, and a semiconductor optical amplifier (SOA).

Note that when swept source OCT is employed, the light source unit includes, for example, a near-infrared variable wavelength laser that changes the wavelength of emitted light at high speed.

The low coherence light L0 output from the light source unit 101 is guided to the polarization controller 103 through the optical fiber 102, and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided to a fiber coupler 105 by an optical fiber 104 and is split into a measurement light LS and a reference light LR. The optical path that guides the measurement light LS is called a measurement arm (sample arm), and the optical path that guides the reference light LR is called a reference arm.

The reference light LR generated by the fiber coupler 105 is guided to a collimator 111 by an optical fiber 110, converted into a parallel light beam, and guided to a retroreflector 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 compensation member 113 acts together with the dispersion compensation member 42 disposed on the measurement arm to match the dispersion characteristics between the reference light LR and the measurement light LS. The retroreflector 114 is movable along the optical path of the reference light LR incident thereon, thereby changing the length of the reference arm. Changing the reference arm length is used, for example, to correct the optical path length according to the axial length or to adjust the interference state.

The reference light LR that has passed through the retroreflector 114 passes through the dispersion compensating member 113 and the optical path length correcting member 112, is converted from a parallel beam into a convergent beam by the collimator 116, and enters the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided to a polarization controller 118 to have its polarization state adjusted, guided to an attenuator 120 through an optical fiber 119 to have its light amount adjusted, and then sent to a fiber coupler 122 through an optical fiber 121. be guided.

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided to the collimator lens unit 40 through the optical fiber 127 and converted into a parallel light beam, which is then converted into a parallel light beam. , and the relay lens 45, is reflected by the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the eye E to be examined. The measurement light LS is scattered and reflected at various depth positions of the eye E to be examined. The return light of the measurement light LS from the eye E to be examined travels through the measurement arm in the opposite direction, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

The fiber coupler 122 generates interference light LC by superimposing the measurement light LS input through the optical fiber 128 and the reference light LR input through the optical fiber 121.

The interference light LC generated by the fiber coupler 122 is guided to the spectrometer 130 through the optical fiber 129. For example, the spectrometer 130 converts the incident interference light LC into a parallel light beam using a collimator lens, decomposes the converted interference light LC into parallel light beams into spectral components using a diffraction grating, and spectral components decomposed by the diffraction grating. is projected onto the image sensor by the lens 114. This image sensor is, for example, a line sensor, and detects a plurality of spectral components of the interference light LC to generate an electric signal (detection signal). The generated detection signal is sent to the arithmetic and control unit 200.

Note that when swept source OCT is adopted, the interference light generated by superimposing the measurement light and the reference light is split at a predetermined branching ratio (for example, 1:1) to generate a pair of interference lights. A pair of interference lights are guided to a photodetector. The photodetector includes, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights, and outputs a difference between a pair of detection signals obtained by these photodetectors. The photodetector sends this output (a detection signal such as a differential signal) to a data acquisition system (DAQ). The data acquisition system is supplied with a clock from the light source unit. The clock is generated in the light source unit in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the variable wavelength light source. For example, the light source unit splits light of each output wavelength to generate two branched lights, optically delays one of these branched lights, combines these branched lights, and detects the resulting combined light. , generates a clock based on the detection signal. The data acquisition system performs sampling of the detection signal (difference signal) input from the photodetector based on a clock. The data obtained through this sampling is used for processing such as image construction.

The ophthalmological apparatus 1 shown in FIGS. 1 and 2 includes an element for changing the measurement arm length (for example, a retroreflector 41) and an element for changing the reference arm length (for example, a retroreflector 114 or a reference mirror). ), although in some exemplary embodiments only one of these elements is provided. By changing the measurement arm length and the reference arm length relative to each other (ie, by changing the optical path length difference between the measurement arm and the reference arm), the coherence gate position is changed. The element for changing the optical path length difference is not limited to the elements disclosed in this embodiment, and may be any element (optical member, mechanism, etc.).

<Arithmetic control unit 200>
Arithmetic control unit 200 executes control of each part of ophthalmologic apparatus 1 . Further, the calculation control unit 200 executes various calculations. For example, the arithmetic and control unit 200 forms a reflection intensity profile for each A line by subjecting the spectral distribution acquired by the spectrometer 130 to signal processing such as Fourier transformation. Furthermore, the arithmetic and control unit 200 forms image data by imaging the reflection intensity profile of each A-line. The calculation processing for this purpose is similar to that of conventional spectral domain OCT.

The arithmetic control unit 200 includes, for example, a processor, a RAM (Random Access Memory), a ROM (Read Only Memory), a hard disk drive, a communication interface, and the like. Various computer programs are stored in storage devices such as hard disk drives. Arithmetic control unit 200 may include an operation device, an input device, a display device, and the like.

As shown in FIG. 3A, user interface 240 includes a display section 241 and an operation section 242. The display unit 241 includes, for example, the display device 3. The operation unit 242 includes various operation devices and input devices. The user interface 240 may include a device such as a touch panel that has a display function and an operation function integrated. An ophthalmic device according to some example embodiments may not include at least a portion of a user interface. For example, the display device and/or the operating device may be a peripheral of an ophthalmological apparatus.

<Anterior segment camera 300>
The anterior segment camera 300 photographs the anterior segment of the eye E to be examined from two or more different directions. Anterior segment camera 300 includes an imaging device such as a CCD image sensor or a CMOS image sensor. In this aspect, two anterior segment cameras 300 are provided on the front surface (the surface facing the subject) of the fundus camera unit 2 (see anterior segment cameras 300A and 300B shown in FIG. 4A). As shown in FIGS. 1 and 4A, the anterior segment cameras 300A and 300B are provided at positions away from the optical path passing through the objective lens 22. In the present disclosure, one of the anterior segment cameras 300A and 300B may be designated by the reference numeral 300, and both may be designated by the reference numeral 300 together. Further, an anterior eye camera that can be used instead of the anterior eye cameras 300A and 300B may be indicated by the reference numeral 300.

In this aspect, two anterior eye cameras 300A and 300B are provided, but the number of anterior eye cameras 300 may be any number greater than or equal to one. Considering the arithmetic processing described below, it is sufficient to have a configuration that can photograph the anterior eye segment from two different directions (however, it is not limited to this). Alternatively, a movable anterior eye camera 300 may be provided to sequentially photograph the anterior eye from two or more different positions.

In this embodiment, two anterior eye cameras 300 are provided separately from the illumination optical system 10 and the photographing optical system 30, but the photographing optical system 30 can be used to photograph the anterior eye, for example. That is, one of the two or more anterior segment cameras 300 may be the photographing optical system 30. The anterior segment camera 300 according to this aspect only needs to be capable of photographing the anterior segment from two (or more) different directions.

Arrangements may be provided for illuminating the anterior segment. The anterior segment illumination means includes, for example, one or more light sources. Typically, at least one light source (eg, an infrared light source) can be provided near each of the two or more anterior segment cameras 300.

Typically, anterior segment imaging from two or more different directions is performed substantially simultaneously. "Substantially simultaneous" refers to cases in which the timing of anterior eye segment imaging from two or more different directions is simultaneous, but also cases in which there is a difference in timing to the extent that eye movement can be ignored, for example, is also acceptable. Show that. Through such substantially simultaneous imaging, it is possible to image the anterior segment of the eye from two or more different directions when the subject's eye E is in substantially the same position and orientation.

Anterior segment photography from two or more different directions may be video photography or still image photography. In the case of video shooting, for example, by controlling the shooting start timings of two or more anterior segment cameras 300 to match, or by controlling the frame rate and the acquisition timing of each frame, the above-mentioned substantially simultaneous shooting can be performed. It is possible to achieve imaging of the anterior segment of the eye. On the other hand, in the case of still image photography, for example, substantially simultaneous anterior eye segment photography can be realized by controlling the timing of photography by two or more anterior eye cameras 300 to match.

Note that when photographing a model eye as described later, it is not necessary to carry out such substantially simultaneous photographing.

<Control system>
An example of the configuration of the control system (processing system) of the ophthalmologic apparatus 1 is shown in FIGS. 3A and 3B. The control section 210, the image forming section 220, and the data processing section 230 are provided in the arithmetic control unit 200, for example.

<Control unit 210>
The control section 210 includes a processor and controls each section of the ophthalmologic apparatus 1 . Control section 210 includes a main control section 211 and a storage section 212.

<Main control unit 211>
The main control unit 211 includes a processor and controls each element of the ophthalmologic apparatus 1 (including the elements shown in FIGS. 1 to 3B). The main control unit 211 is realized, for example, by cooperation between hardware including a circuit and control software.

The photographic focusing lens 31 disposed in the photographing optical path and the focusing optical system 60 disposed in the illumination optical path are controlled integrally or cooperatively by a photographic focusing drive section (not shown) under the control of the main control section 211. will be moved to The retroreflector 41 provided on the measurement arm is moved by a retroreflector (RR) driving section 41A under the control of the main control section 211. The OCT focusing lens 43 arranged on the measurement arm is moved by the OCT focusing drive section 43A under the control of the main control section 211. Note that the movement of the OCT focusing lens 43 can be performed in conjunction with the movement of the imaging focusing lens 31 and the focusing optical system 60. The retroreflector 114 disposed on the reference arm is moved by a retroreflector (RR) drive unit 114A under the control of the main control unit 211. Each of the mechanisms illustrated here typically includes an actuator such as a pulse motor that operates under the control of main controller 211. The optical scanner 44 provided on the measurement arm operates under the control of the main controller 211. Furthermore, the main control unit 211 can control arbitrary elements included in the ophthalmological apparatus 1, such as the polarization controller 103, the polarization controller 118, the attenuator 120, various light sources, various optical elements, various devices, and various mechanisms. . The main control unit 211 also controls any peripheral equipment (apparatus, apparatus, device, etc.) connected to the ophthalmological apparatus 1 and controls any apparatus, apparatus, device, etc. that can be accessed by the ophthalmological apparatus 1. It may be possible.

The moving mechanism 150 moves at least the fundus camera unit 2 three-dimensionally, for example. In a typical example, the moving mechanism 150 includes an x stage that is movable in the ±x direction (horizontal direction), an x moving mechanism that moves the x stage, and a y stage that is movable in the ±y direction (vertical direction). , a y-moving mechanism that moves the y-stage, a z-stage that can move in the ±z direction (depth direction), and a z-moving mechanism that moves the z-stage. Each of these moving mechanisms includes an actuator such as a pulse motor that operates under the control of the main control section 211.

<Storage unit 212>
The storage unit 212 stores various data. Examples of the data stored in the storage unit 212 include image data of an OCT image, image data of a fundus image, and eye information to be examined. The eye information to be examined includes patient information such as patient ID and name, left eye/right eye identification information, electronic medical record information, and the like.

<Image forming section 220>
The image forming unit 220 forms OCT image data based on the data acquired by the spectrometer 130. Image forming section 220 includes a processor. The image forming unit 220 is realized, for example, by cooperation between hardware including a circuit and image forming software.

The image forming unit 220 forms cross-sectional image data based on the data acquired by the spectroscope 130. Similar to conventional spectral domain OCT, this image formation processing includes signal processing such as sampling (A/D conversion), noise removal (noise reduction), filter processing, and fast Fourier transform (FFT).

The image data formed by the image forming unit 220 is a group of image data formed by imaging reflection intensity profiles in a plurality of A-lines (scan lines along the z direction) arranged in the area to which the OCT scan was applied. This is a data set that includes image data (a group of A-scan image data).

The image data formed by the image forming unit 220 is, for example, one or more B-scan image data or stack data formed by embedding a plurality of B-scan image data into a single three-dimensional coordinate system. The image forming unit 220 can also perform voxelization processing on stack data to construct volume data (voxel data). Stack data and volume data are typical examples of three-dimensional image data expressed using a three-dimensional coordinate system.

The image forming unit 220 can process three-dimensional image data. For example, the image forming unit 220 can construct new image data by applying rendering to three-dimensional image data. Rendering techniques include volume rendering, maximum intensity projection (MIP), minimum intensity projection (MinIP), surface rendering, and multiplanar reconstruction (MPR). Further, the image forming unit 220 can construct projection data by projecting three-dimensional image data in the z direction (A-line direction, depth direction). Further, the image forming unit 220 can construct a shadowgram by projecting a part of the three-dimensional image data (three-dimensional partial image data) in the z direction. Note that the three-dimensional partial image data is set, for example, by applying segmentation to the three-dimensional image data.

<Data processing unit 230>
The data processing unit 230 performs various data processing. For example, the data processing unit 230 can apply image processing or analysis processing to OCT image data, or apply image processing or analysis processing to observed image data or photographed image data. Data processing section 230 includes a processor. The data processing unit 230 is realized, for example, by cooperation between hardware including a circuit and data processing software.

Next, the functional configuration of the ophthalmologic apparatus 1 realized by the elements (hardware elements, software elements) shown in FIGS. 1 to 3A will be described. An example of the functional configuration of the ophthalmologic apparatus 1 is shown in FIG. 3B. This example provides a configuration for evaluating the ophthalmologic apparatus 1 using a model eye 500.

<Model eyes 500>
The model eye 500 is attached to the face holder 450 via the attachment 460 for performance evaluation of the ophthalmologic apparatus 1 . In this aspect, the model eye 500 is placed at the same position as the eye E to be examined. Thereby, the alignment function of the ophthalmological apparatus 1 can be used to align the data acquisition optical system 410 with respect to the model eye 500, thereby facilitating the evaluation work. It becomes possible to evaluate not only the quality of the acquired data but also the quality of the alignment performed by the alignment system 420.

An exemplary configuration of the model eye 500 is shown in FIG. The model eye 500 of this example includes a corneal part 510 (corneal equivalent lens) corresponding to the cornea, an iris part 520 corresponding to the iris, a crystalline lens part 550 (crystalline lens equivalent lens) corresponding to the crystalline lens, and a vitreous body. It includes a vitreous body part 560 and a fundus part 570 corresponding to the fundus of the eye. The number of elements (for example, the number of lenses) included in the model eye 500 is arbitrary.

Iris section 520 forms an aperture 540 corresponding to a pupil. Further, the iris section 520 may be provided with a variable section 530 for changing the size (aperture diameter) of the aperture 540. The variable part 530 is, for example, removable from the iris part 520, and a plurality of members corresponding to different aperture diameters are selectively applied. Alternatively, the variable section 530 is configured to be movable relative to the iris section 520. Note that the size of the opening 540 may be fixed. The vitreous body portion 560 is filled with a liquid such as oil. Note that the substance filled in the vitreous body portion 560 is arbitrary, and may be, for example, any gas, any liquid, or any solid. Gas (air) typically exists in the space between the cornea section 510 and the crystalline lens section 550. Note that the material provided in the space between the cornea section 510 and the crystalline lens section 550 is arbitrary, and may be, for example, any gas, any liquid, or any solid.

The fundus portion 570 has a laminated structure that corresponds to the fundus of the human eye. For example, fundus portion 570 includes one or more layers corresponding to arbitrary tissues of the fundus of the human eye. The tissues of the fundus include the inner limiting membrane, nerve fiber layer, ganglion cell layer, inner plexiform layer, inner nuclear layer, outer plexiform layer, outer nuclear layer, outer limiting membrane, photoreceptor layer, retinal pigment epithelial layer, and Bruch's membrane. , choroid, and sclera. The thickness and refractive index of each layer of the fundus 570 may be equivalent to the thickness and refractive index of one or more corresponding tissues. The shape of the fundus 570 is not limited to a flat plate shape as shown in FIG. 5, but may be a curved shape such as a spherical shape or an elliptical shape. Further, the fundus portion 570 may have a structure corresponding to any part or tissue of the human eye. For example, the fundus portion 570 may include a structure corresponding to a macular region, a structure corresponding to an optic disc, a structure corresponding to a blood vessel, and the like. Furthermore, the fundus 570 may have a structure corresponding to any disease, any pathological condition, or any lesion. For example, it may include a structure corresponding to age-related macular degeneration (AMD) (such as drusen), a structure corresponding to retinal detachment, a structure corresponding to hemorrhage, a structure corresponding to a tumor, a structure corresponding to atrophy, etc.

The parameter values of the model eye 500 may be designed to be equivalent or similar to those of the human eye. The values of the parameters of the eye model 500 are obtained, for example, from a standard eye model or from clinical data. Standard model eyes include Gullstrand model eye, Navarro model eye, Liou-Brennan model eye, Badal model eye, Arizona model eye, Indiana model eye, any standardized model eye, and models equivalent to any of these. There are eyes, etc. Furthermore, the model eye 500 may be designed based on an eye having a disease such as severe myopia. Furthermore, the model eye 500 may have a structure corresponding to any disease, any pathological condition, or any lesion. For example, the model eye 500 may have a structure corresponding to any corneal disease, any crystalline lens disease, or the like. Furthermore, the model eye 500 may include a structure corresponding to an artificial object. For example, the model eye 500 may include an intraocular lens (IOL) or an equivalent structure.

The distance between the center position of the front surface of the corneal section 510 (position corresponding to the corneal apex) and the front surface of the fundus section 570 may be designed based on the axial length of the human eye. Further, the overall focal length of the cornea section 510, crystalline lens section 550, and vitreous body section 560 may be designed to have a value equivalent to the focal length of the human eye. For example, it may include means (for example, a spacer) for changing the optical distance between the crystalline lens section 550 and the fundus section 570. Thereby, it is possible to change the refractive power of the model eye 500, and for example, it is possible to perform imaging and measurement evaluation for an eye with a long axial length.

The reflectance of the front surface (the surface on the cornea section 510 side) of the iris section 520 (variable section 530) may be designed to be equivalent to that of the human eye. This reflectance may be, for example, a reflectance at infrared wavelengths. Similarly, the front surface of the corneal portion 510 can also be designed to have a reflectance equivalent to that of the human eye. Furthermore, the model eye 500 may be designed such that the entrance pupil of the iris section 520 (variable section 530, aperture 540) is arranged at the same position as the entrance pupil of the iris of a human eye.

The light used by the data acquisition optical system 410 (measurement light LS in this embodiment) and the light used by the alignment system 420 (in this embodiment, the wavelength band detected by the anterior segment camera 300 (for example, infrared wavelength)) In order to prevent multiple reflections within the model eye 500, it is possible to provide an antireflection film on the lens or the like, or to apply an antireflection paint to internal members.

When alignment is performed using two or more anterior segment cameras 300 (cameras sensitive to infrared wavelengths) as in the ophthalmic apparatus 1 of this embodiment, the following parameter values can be set, for example. First, the entrance pupil of the aperture 540 may be located approximately 3.06 mm away from the corneal portion 510. Further, the diameter of the opening 540 may be set to a value within the range of 2 to 10 mm. Furthermore, the infrared light reflectance of the iris section 520 (variable section 530) may be set to a value within the range of 2.0 to 2.5 percent. Such a design makes it possible to perform alignment for the model eye 500 using the aperture 540 as a reference, similar to when alignment is performed using the pupil of the human eye as a reference.

Even when another alignment method is used, the parameter values of the model eye 500 are set according to that method. For example, when alignment is performed using a corneal reflection image (Purkinje image), the radius of curvature of the corneal portion 510 (the radius of curvature of the front surface of the cornea equivalent lens) may be set to approximately 7.7 mm. Furthermore, when alignment is performed using an optical lever, the radius of curvature of the corneal portion 510 (the radius of curvature of the front surface of the lens equivalent to the cornea) can be set to approximately 7.7 mm.

<Face holding part 450, attachment 460>
The face holding unit 450 is a member that holds the face of the subject in order to fix the position of the eye E to be examined. A typical ophthalmological apparatus is provided with a chin rest and a forehead rest (for example, see Japanese Patent Application Laid-Open Nos. 2010-200905 and 2015-139527). The subject's chin is placed on the chin rest. The forehead of the subject is applied (contacted) to the forehead rest.

Attachment 460 is a member for attaching model eye 500 to ophthalmological apparatus 1 . Typically, attachment 460 is interposed between model eye 500 and ophthalmological apparatus 1 . In some exemplary embodiments, the model eye 500 and the attachment 460 may be integrally configured, but in this embodiment, the model eye 500 is detachably attached to the attachment 460. For example, the model eye 500 is attached to the attachment 460, and the attachment 460 is attached to the face holding section 450. In other words, the model eye 500 is indirectly attached to the ophthalmological apparatus 1 via the attachment 460.

Note that the location of the ophthalmological apparatus 1 to which the model eye 500 (attachment 460) is attached is not limited to the face holding section 450. For example, it is possible to adopt a configuration in which the model eye 500 is attached to the outer surface of the casing that houses the data acquisition optical system 410, or a configuration in which the model eye 500 is built into the casing. When the model eye 500 is built into the housing, the model eye 500 may be configured to be insertable into the optical path of the data acquisition optical system 410, or may be arranged in an optical path branching from the optical path of the data acquisition optical system 410. Good too. In the latter case, for example, when performing performance evaluation using the model eye 500, a total reflection mirror or a beam splitter is inserted into the optical path of the data acquisition optical system 410, and the light from the data acquisition optical system 410 is transmitted through the branched optical path. Light (for example, measurement light LS) is guided to the model eye 500.

An example of the model eye 500 and attachment 460 is shown in FIG. In this example, an attachment 460 is attached to the chin rest 451 of the face holding section 450. More specifically, the mounting portion 461 at the lower end of the attachment 460 is mounted on the upper surface of the table 451 on which the subject's chin is placed. The manner in which the base 451 and the mounting portion 461 are mounted is arbitrary, for example, by screwing or fitting. Further, a left model eye 500L corresponding to the left eye and a right model eye 500R corresponding to the right eye are attached to the model eye stand 462 at the upper end of the attachment 460. The model eye stand 462 and the model eyes 500L and 500R may be attached in any manner, for example, by screwing or fitting. According to this aspect, the model eye 500 can be placed at the same position as the actual eye to be examined, so the alignment function of the ophthalmological apparatus 1 is used to align the data acquisition optical system 410 with respect to the model eye 500. Is possible.

In another exemplary embodiment, the model eye 500 may be attached to the forehead rest 452 via an attachment 460. For example, the attachment 460 of this example is attached to the forehead rest 452 at its upper end, and the model eye 500 is attached to its lower end. The manner of attachment is arbitrary.

In the example shown in FIG. 6, two model eyes 500L and 500R are (indirectly) attached to the ophthalmologic apparatus 1, but the number of model eyes attached to the ophthalmologic apparatus 1 is arbitrary. Typically, one or two model eyes are attached to the ophthalmological device 1.

<Data acquisition optical system 410>
The data acquisition optical system 410 is an optical system for acquiring data on the eye E to be examined. When evaluating the ophthalmologic apparatus 1, the data acquisition optical system 410 acquires data on the model eye 500 in the same manner as when acquiring data on the eye E to be examined. For example, the ophthalmological apparatus 1 of this embodiment can apply an OCT scan to the model eye 500. Further, the ophthalmological apparatus 1 of this embodiment can photograph the fundus 570 of the model eye 500 using the fundus camera unit 2.

<Alignment system 420>
The alignment system 420 is configured to align the data acquisition optical system 410 with respect to the model eye 500 installed at a predetermined position. The predetermined position where the model eye 500 is installed is, for example, the position of the model eye 500L (and/or 500R) shown in FIG.

In this embodiment, alignment system 420 includes two anterior segment cameras 300, a processing section 430, and movement mechanism 150. As described above, the two anterior segment cameras 300 include image sensors sensitive to infrared wavelengths, and are configured to photograph the model eye 500 installed at a predetermined position from two different directions. Further, the moving mechanism 150 is configured to move the data acquisition optical system 410.

<Processing unit 430>
The processing unit 430 controls the movement mechanism 150 based on two or more images of the model eye 500 acquired by the two anterior segment cameras 300.

The processing unit 430 is configured to execute, for example, the process described in Japanese Patent Application Publication No. 2013-248376 by the present applicant. More specifically, the processing unit 430 first identifies the pupil region in each image by analyzing each of the two images of the model eye 500 acquired by the two anterior segment cameras 300.

Next, the processing unit 430 calculates the three-dimensional movement amount of the data acquisition optical system 410 based on the two pupil regions specified from the two images. Trigonometry is used for this calculation.

Further, the processing unit 430 controls the movement mechanism 150 based on the calculated three-dimensional movement amount. More specifically, the processing unit 430 uses a movement mechanism to move the data acquisition optical system 410 by the calculated three-dimensional movement amount (the amount of movement in the x direction, the amount of movement in the y direction, and the amount of movement in the z direction). 150 controls.

For details of the processing executed by the processing unit 430, please refer to a series of documents by the applicant regarding inventions using two or more anterior segment cameras, such as Japanese Patent Laid-Open No. 2013-248376 and Japanese Patent Laid-Open No. 2014-113385. Please refer. The processing unit 430 is realized by, for example, the main control unit 211 and the data processing unit 230.

Note that the ophthalmological apparatus 1 of this embodiment may perform alignment of the data acquisition optical system 410 with respect to the model eye 500 using the alignment optical system 50. In this case, auto-alignment using the alignment index (described above) is applied to the model eye 500.

Some exemplary embodiments of the ophthalmic apparatus may be capable of performing the XY alignment and/or Z alignment described in Japanese Patent Application Publication No. 2018-164616 by the present applicant. XY alignment is an alignment method that uses a corneal reflection image (Purkinje image), and Z alignment is an alignment method that uses an optical lever.

When applying a method using a corneal reflection image (Purkinje image) to alignment of the data acquisition optical system 410 with respect to the model eye 500, the configuration shown in FIG. 7A, for example, can be adopted instead of the configuration shown in FIG. 3B. In the configuration example shown in FIG. 7A, alignment system 420 shown in FIG. 3B is replaced with alignment system 420A. Elements shown in FIG. 7A that are similar to those in FIG. 3B are designated by the same reference numerals, and the description of those elements will not be repeated unless otherwise noted.

The model eye 500 of this example includes at least a corneal portion (510) corresponding to the cornea, and the radius of curvature of this corneal portion is set to approximately 7.7 mm.

The alignment system 420A includes a projection section 421A, an imaging section 422A, a processing section 430A, and a moving mechanism 150.

The projection unit 421A projects a light beam onto the model eye 500. In particular, the projection unit 421A projects a light beam onto the model eye 500 from the front. Typically, the projection unit 421A is configured to project a parallel light beam onto the model eye 500 through a part of the optical path of the data acquisition optical system 410. As a result, a bright spot image (corneal reflection image, Purkinje image) is formed in the corneal portion of the model eye 500.

The photographing section 422A photographs the model eye 500 on which the light beam is projected by the projection section 421A. A corneal reflection image is depicted in the image of the model eye 500 obtained by the imaging unit 422A. The image of the model eye 500 obtained by the photographing section 422A is input to the processing section 430A. The photographing unit 422A is an area sensor in which a plurality of light receiving elements (photoelectric conversion elements) are two-dimensionally arranged.

The processing unit 430A analyzes the image of the model eye 500 acquired by the imaging unit 422A to identify a corneal reflection image. This analysis includes, for example, image processing (eg, edge detection) based on changes in brightness values.

Further, the processing unit 430A controls the movement mechanism 150 based on the corneal reflection image identified from the image of the model eye 500. For example, the processing unit 430A calculates the deviation of the corneal reflection image with respect to a predetermined reference position (for example, a position corresponding to the optical axis of the data acquisition optical system 410), and calculates the deviation of the corneal reflection image so as to cancel this deviation (the corneal reflection image control the moving mechanism 150 so that the moving mechanism 150 is placed at the reference position. Thereby, the optical axis of the data acquisition optical system 410 can be guided to the vertex position of the corneal portion of the model eye 500.

For details of the processing executed by the processing unit 430A, please refer to, for example, Japanese Patent Application Publication No. 2018-164616, Japanese Patent Application Publication No. 10-024019, and the like. The processing unit 430A is realized by, for example, the main control unit 211 and the data processing unit 230.

When applying a method using an optical lever to the alignment of the data acquisition optical system 410 with respect to the model eye 500, the configuration shown in FIG. 7B, for example, can be adopted instead of the configuration shown in FIG. 3B. In the configuration example shown in FIG. 7B, alignment system 420 shown in FIG. 3B is replaced with alignment system 420B. Elements shown in FIG. 7B that are similar to those in FIG. 3B are designated by the same reference numerals, and the description of those elements will not be repeated unless otherwise noted.

The model eye 500 of this example includes at least a corneal portion (510) corresponding to the cornea, and the radius of curvature of this corneal portion is set to approximately 7.7 mm.

Alignment system 420B includes a projection section 421B, an imaging section 422B, a processing section 430B, and a movement mechanism 150.

The projection unit 421B projects a light beam onto the model eye 500. In particular, the projection unit 421B projects a light beam onto the model eye 500 obliquely. Typically, the projection unit 421B is configured to project a parallel light beam onto the model eye 500 from a position away from the optical path of the data acquisition optical system 410. Thereby, the light beam projected onto the cornea of the model eye 500 is reflected on the surface of the cornea.

The photographing section 422B is arranged in a direction substantially symmetrical to the direction in which the light beam is projected by the projection section 421B with respect to the optical axis of the data acquisition optical system 410. Typically, the projection section 421B and the photographing section 422B are arranged at substantially symmetrical positions with respect to the optical axis of the data acquisition optical system 410. The photographing unit 422B is typically a line sensor in which a plurality of light receiving elements are arranged one-dimensionally. Note that the imaging unit 422B may be an area sensor in which a plurality of light receiving elements are two-dimensionally arranged. When the distance between the model eye 500 and the data acquisition optical system 410 is within a predetermined range, the light reflected by the cornea of the light beam emitted from the projection section 421B (corneal reflected light) is detected by the imaging section 422B. . When the corneal reflected light is not detected by the imaging unit 422B, the image obtained by the imaging unit 422B is an entirely black image. On the other hand, when the corneal reflected light is detected by the imaging unit 422B, the image obtained by the imaging unit 422B includes a bright spot image. The image obtained by the photographing section 422B is input to the processing section 430B.

The processing unit 430B analyzes the image acquired by the photographing unit 422B to determine the presence or absence of a bright spot image, and sends a predetermined control signal to the moving mechanism 150 if there is no bright spot image. On the other hand, if there is a bright spot image, the processing unit 430B identifies the position of the bright spot image and determines the deviation of the position of the bright spot image with respect to a predetermined reference position. In other words, the processing unit 430B identifies the address of the light receiving element that detected the corneal reflected light among the plurality of light receiving elements of the imaging unit 422B, and calculates the deviation between the address of this light receiving element and a predetermined reference address. demand.

Furthermore, the processing unit 430B controls the moving mechanism 150 based on the deviation identified in this manner. For example, the processing unit 430B controls the moving mechanism 150 so as to cancel this deviation (so that the corneal reflected light is detected by the light receiving element at the reference address). Thereby, the distance between the model eye 500 and the data acquisition optical system 410 can be guided to a predetermined working distance.

For details of the processing executed by the processing unit 430B, please refer to, for example, Japanese Patent Application Publication No. 2018-164616, Japanese Patent Application Publication No. 2015-146859, and the like. The processing section 430B is realized by, for example, the main control section 211 and the data processing section 230.

<Evaluation section 440>
After alignment is performed by alignment system 420 (420A, 420B), data acquisition optical system 410 acquires data of model eye 500. For example, the ophthalmological apparatus 1 aligns the data acquisition optical system 410 with respect to the model eye 500 using the alignment system 420, and then applies an OCT scan to the model eye 500 using the data acquisition optical system 410.

The evaluation unit 440 generates evaluation information based on the data of the model eye 500 acquired after alignment. For example, the evaluation unit 440 may be configured to generate data quality evaluation information indicating the quality of data acquired by the data acquisition optical system 410. Furthermore, the evaluation unit 440 may be configured to generate alignment quality evaluation information indicating the quality of alignment performed by the alignment system.

When generating data quality evaluation information, the evaluation unit 440 executes a predetermined data quality evaluation process. For example, as described above, when the fundus 570 of the model eye 500 has a laminated structure corresponding to the fundus of a human eye, the ophthalmological apparatus 1 applies an OCT scan to the fundus 570 using the data acquisition optical system 410. do. The image forming unit 220 forms an image of the fundus 570 from the OCT data acquired by the data acquisition optical system 410. For example, the evaluation unit 440 compares the formed image of the fundus 570 with a predetermined evaluation image. This evaluation image is, for example, an image of the fundus 570 with high data quality. The evaluation unit 440 can generate data quality evaluation information based on the comparison result between the image of the fundus 570 and the evaluation image.

As another example of generating data quality evaluation information, the evaluation unit 440 can determine the value of a predetermined evaluation parameter representing data quality by analyzing the data acquired by the data acquisition optical system 410. This evaluation parameter may be, for example, an image quality evaluation parameter such as contrast or signal-to-noise ratio. Further, the evaluation parameter may be, for example, a measurement quality evaluation parameter such as a measurement accuracy parameter or a measurement accuracy parameter.

When generating alignment quality evaluation information, the evaluation unit 440 executes a predetermined alignment quality evaluation process. For example, the evaluation unit 440 can evaluate the alignment quality based on the time taken for alignment, processing details, and results.

In some exemplary aspects, the evaluation unit 440 evaluates the evaluation unit 440 based on the length of time (alignment time) from the start of alignment until reaching a suitable alignment state (e.g., a state in which the alignment error is within a predetermined range). alignment quality evaluation information can be generated. For example, the evaluation unit 440 compares the alignment time with a predetermined threshold, and evaluates the alignment time as "low quality" if it exceeds the threshold, and evaluates it as "high quality" if the alignment time is less than or equal to the threshold. be able to. Alternatively, the evaluation unit 440 determines to which range the alignment time belongs among a plurality of predetermined ranges (high quality range, acceptable range, poor range), and evaluates the alignment quality based on the range to which the alignment time belongs. The information may be configured to generate information.

In some exemplary aspects, the evaluation unit 440 can generate alignment quality evaluation information based on the content of the processing performed by the alignment system 420 (420A, 420B). For example, the evaluation unit 440 can generate alignment quality evaluation information based on the number of repetitions of the alignment operation performed from the start of alignment until reaching a suitable alignment state. The alignment operation is, for example, the number of times the processing unit 430 (430A, 430B) processes the image from the anterior segment camera 300. For example, the evaluation unit 440 compares the number of repetitions of the alignment operation with a predetermined threshold, and evaluates it as "low quality" if the number of repetitions exceeds the threshold, and evaluates it as "high quality" if the number of repetitions is less than or equal to the threshold. It can be evaluated as follows. Alternatively, the evaluation unit 440 determines to which range the number of repetitions belongs among a plurality of predetermined ranges (high quality range, acceptable range, poor range), and evaluates the alignment quality based on the range to which the number of repetitions belongs. The information may be configured to generate information.

In some exemplary aspects, the evaluation unit 440 can generate alignment quality evaluation information based on the results of the processing performed by the alignment system 420 (420A, 420B). For example, the evaluation unit 440 can determine the alignment state (for example, alignment error) reached by the alignment system 420 performing an alignment operation for a predetermined period of time, and generate alignment quality evaluation information based on this alignment error. For example, the evaluation unit 440 compares the alignment error with a predetermined threshold, and evaluates it as "low quality" if the alignment error exceeds the threshold, and evaluates it as "high quality" if the alignment error is less than or equal to the threshold. be able to. Alternatively, the evaluation unit 440 determines to which range the alignment error belongs among a plurality of predetermined ranges (high quality range, acceptable range, poor range), and evaluates the alignment quality based on the range to which the alignment error belongs. The information may be configured to generate information.

<motion>
An example of the operation of the ophthalmologic apparatus 1 according to this aspect will be described. An example of the operation of the ophthalmologic apparatus 1 is shown in FIG.

First, a model eye 500 is installed (S1). In this aspect, for example, the two model eyes 500L and 500R are attached to the chin rest 451 using the attachment 460. Note that the model eye 500 may be directly attached to the chin rest 451, the model eye 500 may be attached directly or indirectly to the forehead rest 452, or the model eye 500 may be directly attached to other parts of the ophthalmological apparatus 1. It may be possible to attach it directly or indirectly.

After the eye model 500 is attached to the ophthalmological apparatus 1, the ophthalmological apparatus 1 starts alignment with respect to the eye model 500 (S2). This alignment is performed using, for example, one of alignment system 420 in FIG. 3B, alignment system 420A in FIG. 7A, and alignment system 420B in FIG. 7B.

Alignment is performed, for example, until a suitable alignment condition is achieved. Alternatively, alignment is performed over a predetermined period of time. Alternatively, alignment is performed until the number of repetitions of the alignment operation reaches a predetermined number.

When the alignment is completed (S3), the ophthalmological apparatus 1 applies an OCT scan to the model eye 500 (S4). This OCT scan may be, for example, an OCT scan of the fundus 570 or a portion corresponding to the anterior segment (any one of the cornea 510, iris 520, variable portion 530, aperture 540, and crystalline lens 550). above) may be an OCT scan.

The ophthalmological apparatus 1 generates evaluation information by the evaluation unit 440 (S5). For example, the ophthalmological apparatus 1 can generate data quality evaluation information by the evaluation unit 440 based on the OCT data acquired by the OCT scan in step S4. Further, the ophthalmological apparatus 1 can generate alignment quality evaluation information by the evaluation unit 440 based on the data obtained regarding the alignment in step S3.

The evaluation information generated in step S5 is displayed on the display unit 241, for example. Furthermore, the evaluation information generated in step S5 is transmitted from the ophthalmological apparatus 1 to an external device. Furthermore, the evaluation information generated in step S5 is recorded on a recording medium. This is the end of this operation example.

<effect>
Some features, some actions, and some effects of the ophthalmological device 1 according to this embodiment will be explained.

The ophthalmological apparatus 1 includes a data acquisition optical system 410, an alignment system 420 (420A, 420B), and an evaluation section 440. Data acquisition optical system 410 includes an optical system for acquiring ocular data. The alignment system 420 is configured to align the data acquisition optical system 410 with respect to the model eye 500 installed at a predetermined position. The evaluation unit 440 is configured to generate evaluation information based on data of the model eye 500 acquired by the data acquisition optical system 410 after alignment by the alignment system 420 (420A, 420B).

According to this aspect configured in this way, it is possible to facilitate the evaluation work of an ophthalmological apparatus using a model eye. That is, in order to appropriately perform evaluation using a model eye, it is necessary to accurately place the model eye with respect to the optical system of the ophthalmological device to be evaluated. This eliminates the need for complicated work such as manually adjusting the position of the

Further, according to this aspect, it is possible to evaluate the ophthalmological apparatus with the model eye installed in a suitable alignment state. Therefore, it is possible to appropriately evaluate the ophthalmological device. For example, according to this aspect, it is possible to improve accuracy, precision, and reproducibility in evaluating an ophthalmological device.

Furthermore, according to this aspect, it is possible to evaluate not only the imaging performance and measurement performance of the ophthalmological apparatus, but also the alignment performance.

The ophthalmologic apparatus 1 may further include a chin rest 451 on which the subject's chin is placed, and an attachment 460 that can be attached to the chin rest 451. Furthermore, the model eye 500 is attached to an attachment 460.

According to this aspect configured in this manner, the model eye 500 can be placed at the same position as the eye to be examined, which is the actual target of imaging and measurement by the ophthalmological apparatus, so that the alignment function of the ophthalmological apparatus can be applied to the model eye. 500 can be suitably applied as is.

The ophthalmological apparatus 1 may further include a forehead rest 452 to which the forehead of the subject is applied, and an attachment (not shown) that can be attached to the forehead rest 452. Furthermore, the model eye 500 is attached to this attachment.

According to this aspect configured in this manner, the model eye 500 can be placed at the same position as the eye to be examined, which is the actual target of imaging and measurement by the ophthalmological apparatus, so that the alignment function of the ophthalmological apparatus can be applied to the model eye. 500 can be suitably applied as is.

The alignment system of the ophthalmological device 1 may be the alignment system 420. Alignment system 420 includes a movement mechanism 150, two (or more) anterior segment cameras 300, and a processing section 430. The moving mechanism 150 is configured to move the data acquisition optical system 410. The two (or more) anterior segment cameras 300 are configured to photograph the model eye 500 from two (or more) different directions. The processing unit 430 is configured to control the movement mechanism 150 based on two (or more) images of the model eye 500 acquired by the two (or more) anterior segment cameras 300.

According to this aspect configured in this way, it is possible to align the data acquisition optical system 410 with respect to the model eye 500 using an alignment method using two (or more) anterior segment cameras 300. . That is, it is possible to apply this aspect to an ophthalmological apparatus having an alignment function using two (or more) anterior ocular segments.

In this aspect configured in this manner, the model eye 500 includes a corneal portion 510 that corresponds to the cornea, and an iris portion 520 (and variable portion 530) that corresponds to the iris and forms an opening 540 that corresponds to the pupil. It's okay to be there. Further, the entrance pupil of the aperture 540 may be located approximately 3.06 mm away from the corneal portion 510, and the diameter of the aperture 540 may be set to a value within a range of 2 to 10 mm. Further, the infrared light reflectance of the iris section 520 (and the variable section 530) may be set to a value within the range of 2.0 to 2.5 percent. Additionally, the two (or more) anterior segment cameras 300 may be sensitive to infrared wavelengths. Further, the processing unit 430 identifies the pupil area in each of the two (or more) images acquired by the two (or more) anterior segment cameras 300, and generates data based on the identified two or more pupil areas. It may be configured to calculate the three-dimensional movement amount of the acquisition optical system 410 and control the movement mechanism 150 based on this three-dimensional movement amount.

According to this aspect configured in this way, it is possible to perform an alignment operation in the same manner as alignment for the human eye using a model eye having parameter values equivalent to those of the human eye.

The alignment system of the ophthalmological device 1 may be alignment system 420A or 420B. The alignment system 420A or 420B includes a moving mechanism 150, a projection section 421A or 421B, an imaging section 422A or 422B, and a processing section 430A or 430B. The moving mechanism 150 is configured to move the data acquisition optical system 410. The projection unit 421A (421B) is configured to project a light beam onto the model eye 500. The photographing unit 422A (422B) is configured to photograph the model eye 500. The processing unit 430A (430B) is configured to control the moving mechanism 150 based on the image acquired by the imaging unit 422A (or 422B).

According to this aspect configured in this way, it is possible to align the data acquisition optical system 410 with respect to the model eye 500 using a type of alignment method that projects a light beam onto the target object (eye to be examined, model eye). It is. In other words, this embodiment can be applied to an ophthalmological apparatus having a type of alignment function that projects a light beam onto a target object (eye to be examined, model eye).

The alignment system of the ophthalmological apparatus 1 may be the alignment system 420A. In this case, the model eye 500 includes a corneal portion 510 corresponding to the cornea. The radius of curvature of the corneal portion 510 is designed to be approximately 7.7 mm. The alignment system 420A includes a moving mechanism 150, a projection section 421A, a photographing section 422A, and a processing section 430A. The moving mechanism 150 is configured to move the data acquisition optical system 410. The projection unit 421A is configured to project a light beam onto the model eye 500 from the front. The photographing unit 422A is configured to photograph the model eye 500. Typically, the photographing section 422A is configured to photograph the model eye 500 from the front, and the projection section 421A and the photographing section 422A are arranged coaxially. The processing unit 430A is configured to identify the reflected image of the light flux by the corneal unit 510 in the image acquired by the imaging unit 422A, and to control the moving mechanism 150 based on the identified reflected image.

According to this aspect configured in this way, it is possible to align the data acquisition optical system 410 with respect to the model eye 500 using an alignment method using a corneal reflection image (Purkinje image). That is, the present embodiment can be applied to an ophthalmological apparatus having an alignment function using a corneal reflection image (Purkinje image).

The alignment system of the ophthalmological device 1 may be the alignment system 420B. In this case, the model eye 500 includes a corneal portion 510 corresponding to the cornea. The radius of curvature of the corneal portion 510 is designed to be approximately 7.7 mm. Alignment system 420B includes moving mechanism 150, projection section 421B, photographing section 422B, and processing section 430B. The moving mechanism 150 is configured to move the data acquisition optical system 410. The projection unit 421B is configured to project a light beam onto the model eye 500 obliquely. The photographing unit 422B includes a line sensor or an area sensor arranged in a direction substantially symmetrical to the projection direction of the luminous flux with respect to the optical axis of the data acquisition optical system 410. Typically, the projection unit 421B and the line sensor (area sensor) are arranged at substantially symmetrical positions with respect to the optical axis of the data acquisition optical system 410. The processing unit 430B is configured to control the moving mechanism 150 based on the position of the light receiving element of the line sensor (area sensor) that detects the reflected light of the light beam by the corneal unit 510.

According to this aspect configured in this way, it is possible to align the data acquisition optical system 410 with respect to the model eye 500 using an alignment method using an optical lever. In other words, the present embodiment can be applied to an ophthalmological apparatus having an alignment function using an optical lever.

Note that by applying an alignment method using two (or more) anterior segment cameras 300, three-dimensional alignment of the data acquisition optical system 410 with respect to the model eye 500 is possible. Furthermore, three-dimensional alignment of the data acquisition optical system 410 with respect to the model eye 500 is possible by combining an alignment method using a corneal reflection image (Purkinje image) and an alignment method using an optical lever.

The model eye 500 may include a left model eye 500L corresponding to the left eye, and a right model eye 500R corresponding to the right eye. Furthermore, the ophthalmological apparatus 1 may further include an attachment 460 for installing the left model eye 500L in the first position and the right model eye in the second position (see FIG. 6).

According to this aspect configured in this way, it is possible to apply the alignment of the data acquisition optical system 410 to both the left model eye 500L and the right eye to be examined 500R. Furthermore, the evaluation based on the left model eye 500L and the evaluation based on the right eye to be examined 500R can be performed individually or collectively. It is also possible to evaluate the performance of the function of switching the object of the data acquisition optical system 410 between the left eye and the right eye.

The evaluation unit 440 may be configured to generate data quality evaluation information indicating the quality of data acquired by the data acquisition optical system 410. Furthermore, the evaluation unit 440 may be configured to generate alignment quality evaluation information indicating the quality of alignment performed by the alignment system 420 (420A, 420B). The types of evaluation information are not limited to these.

The ophthalmological apparatus 1 of this embodiment can provide the following exemplary evaluation method. This evaluation method is a method for evaluating the performance of an ophthalmological apparatus including an optical system for acquiring eye data.

In an ophthalmological device evaluation method according to some exemplary embodiments, first, a model eye is installed at a predetermined position. Next, the optical system is aligned with respect to the model eye installed at a predetermined position. Furthermore, evaluation information is generated based on the data of the model eye acquired by the optical system after this alignment.

In some exemplary embodiments, placing the eye model in place includes attaching a first attachment to a chinrest of an ophthalmological device and attaching the eye model to the first attachment. good.

In some exemplary embodiments, placing the eye model in place includes attaching a second attachment to the forehead rest of the ophthalmological device and attaching the eye model to the second attachment. good.

In some exemplary embodiments, the step of performing the alignment includes the step of photographing the model eye from two or more different directions, and the step of performing the alignment based on the two or more images of the model eye obtained by photographing from the two or more directions. The method may include a step of moving the optical system.

In some exemplary embodiments, the model eye may include a corneal portion that corresponds to the cornea, and an iris portion that corresponds to the iris and forms an aperture that corresponds to the pupil. The entrance pupil of the aperture may be located approximately 3.06 millimeters from the cornea. The diameter of the aperture may be set to a value within the range of 2 to 10 millimeters. The infrared light reflectance of the iris may be set to a value within the range of 2.0 to 2.5 percent. Further, the step of photographing the model eye from two or more different directions may include photographing sensitive to infrared wavelengths. The step of moving the optical system based on two or more images includes the step of specifying the pupil area in each of the two or more images, and calculating the three-dimensional movement amount of the optical system based on the specified two or more pupil areas. and a step of moving the optical system based on this three-dimensional movement amount.

In some exemplary embodiments, performing the alignment includes projecting a light beam onto the model eye, photographing the model eye, and moving the optical system based on the image obtained by photographing the model eye. It may include a process.

In some exemplary embodiments, the model eye may include a corneal portion that corresponds to the cornea. The radius of curvature of the corneal portion may be approximately 7.7 millimeters. Furthermore, the step of projecting the light beam may include the step of projecting the light beam onto the model eye from the front. The step of moving the optical system includes a step of identifying a reflected image of the light beam by the cornea in an image obtained by photographing the model eye, and a step of moving the optical system based on the identified reflected image. It's okay to stay.

In some exemplary embodiments, the model eye may include a corneal portion that corresponds to the cornea. The radius of curvature of the corneal portion may be approximately 7.7 millimeters. Furthermore, the step of projecting the light beam may include the step of projecting the light beam onto the model eye obliquely. The step of photographing the model eye includes the step of detecting the light reflected from the cornea by a line sensor or an area sensor arranged in a direction substantially symmetrical to the projection direction of the light beam with respect to the optical axis of the optical system. good. The step of moving the optical system may include the step of moving the optical system based on the position of the light receiving element of the line sensor or area sensor that detected the reflected light.

In some exemplary embodiments, the model eye may include a left model eye corresponding to the left eye and a right model eye corresponding to the right eye. Further, the step of installing the model eye in a predetermined position includes a step of attaching a third attachment to the ophthalmological apparatus, a step of attaching the left model eye to the third attachment and installing the left model eye in the first position, and a step of attaching the left model eye to the third attachment. The method may include a step of attaching the model eye to a third attachment and setting the right model eye at the second position.

In some example aspects, generating evaluation information may include generating first evaluation information indicative of the quality of data acquired by the optical system.

In some example aspects, generating evaluation information may include generating second evaluation information indicative of the quality of alignment performed by the alignment system.

Note that it is possible to combine any matter (configuration, element, process, operation, action, function, etc.) or any publicly known matter explained in the above-mentioned exemplary embodiments with any of the above-described evaluation methods.

It is possible to configure a program that causes an ophthalmological apparatus (including a computer) to execute such an evaluation method. This program may include, for example, any of the aforementioned programs for operating the ophthalmological device 1 of the exemplary embodiments.

Furthermore, it is possible to create a computer-readable non-temporary recording medium that records such a program. This non-transitory recording medium may be in any form, examples of which include magnetic disks, optical disks, magneto-optical disks, and semiconductor memory.

The embodiments described above are merely illustrative of the implementation of this invention. Those who wish to carry out this invention can make any modifications (omissions, substitutions, additions, etc.) within the scope of the gist of this invention.

1 Ophthalmic apparatus 150 Moving mechanism 300, 300A, 300B Anterior segment camera 410 Data acquisition optical system 420, 420A, 420B Alignment system 421A, 421B Projection section 422A, 422B Photographing section 430, 430A, 430B Processing section 440 Evaluation section 450 Face holding Part 451 Chin rest 452 Forehead rest 460 Attachments 500, 500L, 500R Model eye 510 Cornea part 520 Iris part 570 Fundus part

Claims (22)

an optical system for acquiring eye data;
an alignment system that aligns the optical system with respect to a model eye installed at a predetermined position;
an evaluation unit that generates evaluation information based on data of the model eye acquired by the optical system after the alignment ;
The model eye is
A left model eye corresponding to the left eye,
The right model eye corresponds to the right eye.
including;
further comprising a third attachment for installing the left model eye in a first position and installing the right model eye in a second position;
Ophthalmology equipment. an optical system for acquiring eye data;
an alignment system that aligns the optical system with respect to a model eye installed at a predetermined position;
an evaluation unit that generates evaluation information based on data of the model eye acquired by the optical system after the alignment ;
The evaluation unit generates second evaluation information indicating the quality of alignment performed by the alignment system.
Ophthalmology equipment. a chin rest on which the subject's chin is placed;
and a first attachment attachable to the chin rest,
the model eye is attached to the first attachment;
The ophthalmological device according to claim 1 or 2 . A forehead pad to which the forehead of the subject is applied;
and a second attachment attachable to the forehead rest,
the model eye is attached to the second attachment;
The ophthalmological device according to claim 1 or 2 . The alignment system is
a moving mechanism that moves the optical system;
a first imaging unit that photographs the model eye from two or more different directions;
a first processing unit that controls the movement mechanism based on two or more images of the model eye acquired by the first imaging unit;
The ophthalmological device according to any one of claims 1 to 4 . The model eye is
A corneal part corresponding to the cornea,
an iris portion corresponding to an iris and forming an aperture corresponding to a pupil;
an entrance pupil of the aperture is located approximately 3.06 mm away from the cornea;
The diameter of the opening is set to a value within a range of 2 to 10 mm,
The infrared light reflectance of the iris is set to a value within a range of 2.0 to 2.5%,
The first imaging unit has sensitivity to infrared wavelengths,
The first processing unit specifies a pupil area in each of the two or more images, calculates a three-dimensional movement amount of the optical system based on the two or more specified pupil areas, and calculates a three-dimensional movement amount of the optical system based on the three-dimensional movement amount. controlling the moving mechanism based on
The ophthalmological device according to claim 5 . The alignment system is
a moving mechanism that moves the optical system;
a projection unit that projects a light beam onto the model eye;
a second imaging unit that photographs the model eye;
a second processing unit that controls the movement mechanism based on the image acquired by the second imaging unit;
The ophthalmological device according to any one of claims 1 to 4 . The model eye includes a corneal part corresponding to the cornea,
The radius of curvature of the corneal portion is approximately 7.7 mm,
The projection unit includes a first projection unit that projects a light beam onto the model eye from the front,
The second processing unit specifies a reflected image of the light flux by the corneal portion in the image acquired by the second imaging unit, and controls the moving mechanism based on the specified reflected image.
The ophthalmological device according to claim 7 . The model eye includes a corneal part corresponding to the cornea,
The radius of curvature of the corneal portion is approximately 7.7 mm,
The projection unit includes a second projection unit that projects a light beam obliquely onto the model eye,
The second imaging unit includes a line sensor or an area sensor arranged in a direction substantially symmetrical to the projection direction of the luminous flux with respect to the optical axis of the optical system,
The second processing unit controls the moving mechanism based on the position of a light receiving element of the line sensor or the area sensor that detects the reflected light of the luminous flux by the cornea part.
The ophthalmological device according to claim 7 or 8 . The evaluation unit generates first evaluation information indicating the quality of data acquired by the optical system.
The ophthalmological device according to any one of claims 1 to 9. A method for evaluating the performance of an ophthalmological device including an optical system for acquiring ocular data, the method comprising:
Place the model eye in the specified position,
aligning the optical system with respect to the model eye installed at the predetermined position;
generating evaluation information based on data of the model eye acquired by the optical system after the alignment;
The model eye includes a left model eye corresponding to the left eye and a right model eye corresponding to the right eye,
The step of installing the model eye at the predetermined position includes:
attaching a third attachment to the ophthalmological device;
attaching the left model eye to the third attachment and placing the left model eye in a first position;
attaching the right model eye to the third attachment and placing the right model eye in a second position;
including,
Method. A method for evaluating the performance of an ophthalmological device including an optical system for acquiring ocular data, the method comprising:
Place the model eye in the specified position,
aligning the optical system with respect to the model eye installed at the predetermined position;
generating evaluation information based on data of the model eye acquired by the optical system after the alignment;
The step of generating the evaluation information includes the step of generating second evaluation information indicating the quality of the alignment.
Method. The step of installing the model eye at the predetermined position includes:
attaching a first attachment to the chin rest of the ophthalmological device;
and a step of attaching the model eye to the first attachment.
The method according to claim 11 or 12. The step of installing the model eye at the predetermined position includes:
attaching a second attachment to the forehead rest of the ophthalmological device;
and a step of attaching the model eye to the second attachment.
The method according to claim 11 or 12. The step of performing the alignment includes:
photographing the model eye from two or more different directions;
moving the optical system based on two or more images of the model eye obtained by photographing from the two or more directions;
The method according to any one of claims 11 to 14. The model eye is
A corneal part corresponding to the cornea,
an iris portion corresponding to an iris and forming an aperture corresponding to a pupil;
an entrance pupil of the aperture is located approximately 3.06 mm away from the cornea;
The diameter of the opening is set to a value within a range of 2 to 10 mm,
The infrared light reflectance of the iris is set to a value within a range of 2.0 to 2.5%,
The step of photographing the model eye from two or more different directions includes photographing with sensitivity to infrared wavelengths;
The step of moving the optical system based on the two or more images,
identifying a pupil area in each of the two or more images;
calculating a three-dimensional movement amount of the optical system based on the two or more identified pupil regions;
moving the optical system based on the three-dimensional movement amount;
16. The method of claim 15. The step of performing the alignment includes:
Projecting a light beam onto the model eye;
a step of photographing the model eye;
moving the optical system based on the image obtained by photographing the model eye;
The method according to any one of claims 11 to 14. The model eye includes a corneal part corresponding to the cornea,
The radius of curvature of the corneal portion is approximately 7.7 mm,
The step of projecting the light beam includes the step of projecting the light beam onto the model eye from the front,
The step of moving the optical system includes:
identifying a reflected image of the light beam by the cornea in the image obtained by photographing the model eye;
moving the optical system based on the identified reflected image;
18. The method of claim 17. The model eye includes a corneal part corresponding to the cornea,
The radius of curvature of the corneal portion is approximately 7.7 mm,
The step of projecting the light beam includes the step of projecting the light beam obliquely onto the model eye,
The step of photographing the model eye includes the step of detecting the reflected light of the light beam by the cornea portion using a line sensor or an area sensor arranged in a direction substantially symmetrical to the projection direction of the light beam with respect to the optical axis of the optical system. including,
The step of moving the optical system includes the step of moving the optical system based on the position of the light receiving element of the line sensor or the area sensor that detected the reflected light.
The method according to claim 17 or 18. The step of generating the evaluation information includes the step of generating first evaluation information indicating the quality of data acquired by the optical system.
The method according to any one of claims 11 to 19 . A program that causes an ophthalmological apparatus to execute the method according to any one of claims 11 to 20 . A computer-readable non-transitory recording medium on which the program according to claim 21 is recorded.

Images