JP2020151099A - Ophthalmologic apparatus, its control method, ophthalmologic information processing device, its control method, program, and recording medium - Google Patents

Abstract

To enable propriety of an apparatus position of an orthokeratology lens to be determined.SOLUTION: An ophthalmologic apparatus includes a specific site detection unit, a cornea shape measurement unit, a feature point setting unit, and an evaluation unit. The specific site detection unit detects a specific site of an eye after an orthokeratology lens is removed. The cornea shape measurement unit measures a cornea shape of the eye. The feature point setting unit sets a feature point from cornea shape data acquired by the cornea shape measurement unit. The evaluation unit executes evaluation on a mounting state of the orthokeratology lens onto the eye based on the specific site detected by the specific site detection unit and the feature point set by the feature point setting unit.SELECTED DRAWING: Figure 1

Description

The present invention relates to an ophthalmic apparatus, a control method thereof, an ophthalmic information processing apparatus, a control method thereof, a program, and a recording medium.

Recent studies on the progression of myopia have reported that the focal point of the peripheral vision is located deeper than the retinal surface, and that the retina tends to displace to the back, which may lead to the progression of myopia ( For example, see Non-Patent Document 1).

One of the refraction correction means for increasing the refractive power in the peripheral visual field (that is, making the refractive power in the peripheral portion negative or relatively decreasing the refractive power in the central portion) for the purpose of suppressing the progression of myopia. Orthokeratology (hereinafter abbreviated as "Ortho K") has been performed, and its effect has been clinically demonstrated (see, for example, Non-Patent Document 2).

Ortho-K is a corneal correction therapy that treats refractive errors such as myopia by wearing contact lenses (Ortho-K lenses) with a special curve design to correct the shape of the cornea. In Ortho K, the refraction correction effect is maintained for a certain period of time even after the contact lens is removed, so that it is also applicable as a refraction correction method for contact competitions and outdoor competitions.

As mentioned above, the refraction state of the peripheral visual field (peripheral part) is considered to be important for suppressing the progression of myopia, but since the patient basically uses the central visual field (fovea centralis) during daytime activity, The expected refraction correction effect is actually obtained without being conscious of what the refraction state of the peripheral vision is (that is, whether or not the Ortho K lens was mounted in an appropriate position at night). It is difficult to judge whether it is.

Earl L. Smith III, Li-Fang Hung, Juan Huang, “Relative peripheral hyperopic defocus alters central refraction development in infant monkeys”, Vision Research, Volume 49, Issue 19, 30 September 2009, Pages 2386-2392 Jun-Kang Si, Kai Tang, Hong-Sheng Bi, Da-Dong Guo, Jun-Guo Guo, and Xing-Rong Wang, “Orthokeratology for Myopia Control: A Meta-analysis”, Optometry and Vision Science, Vol. 92, No. 3, March 2015, Pages 252-257

An object of the present invention is to make it possible to determine the suitability of the mounting position of the Ortho-K lens.

The ophthalmic apparatus according to some exemplary embodiments includes a specific site detection unit that detects a specific site of the eye after removing the orthokeratology lens, a corneal shape measuring unit that measures the corneal shape of the eye, and the corneal shape. A feature point setting unit that sets a feature point from the corneal shape data acquired by the measurement unit, and an evaluation unit that evaluates the wearing state of the orthokeratology lens on the eye based on the specific portion and the feature point. including.

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit sets feature points based on an approximate expression of the corneal shape data by a centrally symmetric expression.

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit sets feature points based on an approximate expression of the corneal shape data by a predetermined aspherical expression.

In the ophthalmic device according to some exemplary embodiments, the predetermined aspherical expression is an expression that includes at least a conic surface expression or a biconic surface expression.

In the ophthalmic apparatus according to some exemplary embodiments, the predetermined aspherical expression is an expression obtained by adding an even-order polynomial to a conic surface expression or an expression obtained by adding an even-order polynomial to a biconic surface expression. ..

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit approximates the corneal shape data in at least one direction by an aspherical expression including at least a conic surface equation.

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit approximates the corneal shape data in each of the two directions orthogonal to each other by an aspherical expression including at least the equation of the conic surface.

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit uses an aspherical type including at least the formula of the conic surface to obtain the corneal shape data in each of the astigmatic axis direction of the eye and the direction orthogonal to the astigmatic axis direction. Make an approximation.

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit approximates the corneal shape data by a three-dimensional aspherical expression including at least a biconic surface equation.

In the ophthalmic apparatus according to some exemplary embodiments, the feature point setting unit sets the center of the approximate expression as the feature point.

In the ophthalmic apparatus according to some exemplary embodiments, the specific site detection unit detects the corneal apex as the specific site, and the evaluation unit determines the deviation between the corneal apex and the center of the approximate expression. The evaluation is performed based on the above.

In the ophthalmic apparatus according to some exemplary embodiments, the specific site detection unit detects the center of the pupil as the specific site, and the evaluation unit determines the deviation between the center of the pupil and the center of the approximate expression. The evaluation is performed based on the above.

In the ophthalmic apparatus according to some exemplary embodiments, the corneal shape measuring unit acquires the curvature distribution data or the radius of curvature distribution data of the cornea as the corneal shape data.

In the ophthalmic apparatus according to some exemplary embodiments, the corneal shape measuring unit acquires the height distribution data of the cornea as the corneal shape data.

A method according to some exemplary embodiments is a method of controlling an ophthalmic apparatus including an imaging unit and a processor for imaging the eye, the first and second imaging of the eye after removing the orthokeratology lens. To control the imaging unit to acquire an image, control the processor to analyze the first captured image to detect a specific part of the eye, and acquire corneal shape data of the eye. The processor is controlled so as to analyze the second captured image, the processor is controlled so as to set a feature point from the corneal shape data, and the orthokeratology with respect to the eye is performed based on the specific portion and the feature point. -Control the processor to perform an evaluation of the attached state of the lens.

A program according to some exemplary embodiments is a program that causes an ophthalmic apparatus including a computer to execute a control method according to any of the exemplary embodiments.

The recording medium according to some exemplary embodiments is a computer-readable non-temporary recording medium on which the program according to any of the exemplary embodiments is recorded.

The ophthalmic information processing apparatus according to some exemplary embodiments includes a first analysis unit that analyzes a first captured image of the eye after removing the orthokeratology lens to detect a specific part, and a second captured image of the eye. A second analysis unit that acquires corneal shape data by analyzing the above, a feature point setting unit that sets feature points from the corneal shape data, and the orthokeratology lens for the eye based on the specific site and the feature point. Includes an evaluation unit that evaluates the wearing state of the lens.

A method according to some exemplary embodiments is a method of controlling an ophthalmic information processing apparatus including a processor, in which the first imaging of the eye after removing the orthokeratology lens in order to detect a specific part of the eye. The processor is controlled to analyze the image, the processor is controlled to analyze the second captured image of the eye in order to acquire the corneal shape data of the eye, and feature points are set from the corneal shape data. The processor is controlled so as to perform an evaluation of the wearing state of the orthokeratology lens on the eye based on the specific portion and the feature point.

A program according to some exemplary embodiments is a program that causes a computer to execute a control method according to any of the exemplary embodiments.

The recording medium according to some exemplary embodiments is a computer-readable non-temporary recording medium on which the program according to any of the exemplary embodiments is recorded.

According to an exemplary embodiment, it is possible to determine the suitability of the mounting position of the Ortho-K lens.

It is the schematic which shows the structure of the ophthalmic apparatus which concerns on an exemplary aspect. It is a flowchart which shows the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic which shows the structure of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic which shows the structure of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic which shows the structure of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic which shows the structure of the ophthalmic apparatus which concerns on an exemplary aspect. It is a flowchart which shows the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic for demonstrating the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic for demonstrating the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is a flowchart which shows the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic for demonstrating the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic for demonstrating the operation of the ophthalmic apparatus which concerns on an exemplary aspect. It is the schematic which shows the structure of the ophthalmic information processing apparatus which concerns on an exemplary aspect.

Some exemplary embodiments of the embodiments will be described below. In addition, it is possible to refer to the matters disclosed in the documents cited in this specification and the matters relating to any known technology in an exemplary manner.

Some exemplary embodiments described below can be used to evaluate the wearing state of the Ortho-K lens, i.e., whether or not the Ortho-K lens was worn in an appropriate position on the eye (on the cornea). Is. This is an evaluation of whether or not the cornea has been corrected to the desired shape, and typically whether or not the refractive state of the peripheral visual field for suppressing the progression of myopia is properly corrected (that is, the peripheral visual field). It may include an assessment of whether or not the focal point of is located in front of the retinal surface.

In some aspects described below, the "correction center" refers to the detection position of the apex of the cornea deformed by the ortho-K lens (corneal apex) and the center of the corneal shape deformed by the ortho-K lens (deformation). It may mean any of the estimated positions of the center).

The corneal apex referred to here is the most protruding position of the cornea after the ortho-K lens is removed, and is generally biased from the original corneal apex (the apex of the cornea in a state where there is no influence of deformation by the ortho-K lens). (Of course, it does not exclude the situation where the corneal apex under the influence of the Ortho-K lens matches the original corneal apex).

The detection of the corneal apex is performed, for example, by detecting an index formed in the anterior segment of the eye. As a typical example thereof, Japanese Patent Application Laid-Open No. 2015-85081 takes a picture from the front while projecting a luminous flux on the anterior segment of the eye, and analyzes the image of the anterior segment obtained thereby to obtain a bright spot image (Pulkinje image). Is disclosed, and a technique for obtaining the position (two-dimensional position) of this bright spot image as the position of the apex of the cornea is disclosed. Further, Japanese Patent Application Laid-Open No. 2017-74115 captures images from two directions (stereo imaging) while projecting a luminous flux onto the anterior segment of the eye, and analyzes the two images of the anterior segment obtained thereby to obtain a bright spot image (bright spot image). A technique for detecting a Pulkinje image) and determining the position (three-dimensional position) of this bright spot image as the position of the apex of the cornea is disclosed. As another example of detecting the apex of the cornea, the central position of the photographed image of the ring pattern light projected on the cornea for measuring the radius of curvature of the cornea can be obtained and set as the position of the apex of the cornea (two-dimensional position). An ophthalmic device (keratometer) for measuring the radius of curvature of the cornea is disclosed in, for example, Japanese Patent Application Laid-Open No. 2-65533. As yet another example of corneal apex detection, the position (three-dimensional position) of the corneal apex is detected from the image of the anterior segment obtained by an optical coherence tomography (OCT) device (for example, Japanese Patent Application Laid-Open No. 2015-157182). can do.

The deformation center is estimated, for example, by finding the center of a mathematical formula (function) that approximates the shape of the cornea (typically, the center of the fitting curved surface and the center of the fitting curve). This mathematical expression (function) may be, for example, a centrally symmetric mathematical expression (function), or may be an aspherical expression (a mathematical expression (function) representing an aspherical shape). This aspherical expression may be, for example, an expression (function) including at least a conic surface expression (function) or a biconic surface expression (function), and further, an even-order polynomial in the conic surface expression (function). It may be an expression (function) obtained by adding the above, or an expression (function) obtained by adding an even-order polynomial to the expression (function) of the biconic surface.

The Ortho-K lens has a region (transition zone, return zone) in which a curvature inflection point exists between the central portion (optical zone, treatment zone) and the peripheral portion (peripheral zone, landing zone). Therefore, since the fitting accuracy is low only on the cornic surface or the biconic surface, it is considered desirable to increase the fitting accuracy by adding a polynomial up to the fourth order, the sixth order, or the eighth order, for example.

The corneal shape to be approximated may be, for example, a corneal curvature distribution, a corneal radius of curvature distribution, or a height distribution. The corneal curvature distribution and the corneal radius of curvature distribution are determined by, for example, a keratometer and a corneal topogram (see, for example, Japanese Patent Application Laid-Open No. 8-280624). The height distribution is obtained, for example, by integrating the corneal curvature distribution twice. The estimation of the deformation center (particularly the fitting center) will be described later.

In some of the following embodiments, the "processor" is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD), and a programmable logic device (for example, a SPLD). , CPLD (Complex Programmable Logical Device), FPGA (Field Programmable Gate Array)) and the like. The processor realizes a desired function by reading and executing a program stored in a storage circuit or a storage device, for example.

<First aspect>
The ophthalmic apparatus according to the first aspect will be described. A configuration example of the ophthalmic apparatus according to this aspect is shown in FIG. The ophthalmic apparatus 1000 includes a specific site detection unit 1010, a corneal shape measurement unit 1020, a feature point setting unit 1030, and an evaluation unit 1040. The ophthalmic apparatus 1000 further includes a control unit 1050 that controls them.

The specific site detection unit 1010 detects a specific site of the eye after removing the ortho-K lens. The specific site of the eye is typically the apex of the cornea or the center of the pupil, but may be other sites.

For the detection of the apex of the corneum, for example, as described above, a two-dimensional position or three-dimensional position detection method based on the Pulkinje image, a two-dimensional position detection method based on the keratling image, and three-dimensional using the anterior segment OCT. Either the position detection method or any other detection method is applied.

For the detection of the center of the pupil, for example, a two-dimensional position detection method by analyzing the front image of the anterior segment, and a three-dimensional position detection method by analyzing two anterior segment images obtained by photographing from two directions. And any of the other detection methods is applied.

A typical specific site detection unit 1010 includes an imaging unit (optical system, image sensor, camera, etc.) that photographs the anterior eye portion, and a processor that analyzes an image obtained by the imaging unit. Further, the specific site detection unit 1010 may include a projection unit that projects a luminous flux for forming a Purkinje image or a keratling image. The processor operates according to, for example, known analysis software (program) for detecting a specific part.

The corneal shape measuring unit 1020 measures the corneal shape of the eye and generates corneal shape data. As described above, the corneal shape data includes, for example, corneal curvature distribution data or corneal radius of curvature distribution data obtained by a keratometer, corneal curvature distribution data or corneal radius of curvature distribution data obtained by a corneal topographer, and other measurements. One of the data.

A typical corneal shape measuring unit 1020 is a projection system that projects light for forming a pattern image on the cornea, and an imaging unit (optical system, image sensor, camera) that photographs the anterior segment on which the pattern image is formed. Etc.) and a processor that analyzes the image obtained by the photographing unit. The processor operates according to, for example, known analysis software (program) for obtaining distribution data of corneal shape parameters.

The feature point setting unit 1030 sets the feature point from the corneal shape data acquired by the corneal shape measurement unit 1020. The feature points represent characteristic positions in the shape of the cornea. The feature point is typically the aforementioned correction center. As described above, the correction center may be, for example, the apex of the cornea deformed by the ortho-K lens (corneal apex) or the center of the corneal shape deformed by the ortho-K lens (deformation center such as the fitting center). ..

A typical feature point setting unit 1030 includes a processor that analyzes corneal shape data to detect feature points. The processor operates according to analysis software (program) for setting feature points from corneal shape data. The analysis software includes, for example, software for detecting the corneal apex from the corneal shape data and software for detecting the deformation center from the corneal shape data. Software for detecting the deformation center from the corneal shape data includes, for example, a process of obtaining an approximate curved surface (fitting curved surface) or an approximate curve (fitting curve) of the corneal shape data, and a center of the approximate curved surface or the approximate curve (fitting center). It is configured to cause the processor to execute the process of requesting.

When the specific site detection unit 1010 specifies the corneal apex, the corneal shape measurement unit 1020 and the feature point setting unit 1030 set an arbitrary feature point (for example, a deformation center such as a fitting center) other than the corneal apex. Can be done. On the other hand, when the specific site detection unit 1010 specifies an eye region other than the corneal apex (for example, the center of the pupil), the corneal shape measuring unit 1020 and the feature point setting unit 1030 may use an arbitrary correction center (for example, the corneal apex or the center of the pupil). The center of deformation) can be set as the feature point.

The evaluation unit 1040 evaluates the wearing state of the orthokeratology lens on the eye based on the specific part detected by the specific part detection unit 1010 and the feature point set by the feature point setting unit 1030. The evaluation unit 1040 evaluates, for example, based on the deviation (positional deviation) between the specific portion and the feature point.

For example, when the specific site detection unit 1010 detects the corneal apex as a specific site and the feature point setting unit 1030 fits the corneal shape data, the evaluation unit 1040 performs the corneal apex detected by the specific site detection unit 1010. The evaluation is performed based on the deviation between the image and the fitting center set by the feature point setting unit 1030.

In another example, when the specific site detection unit 1010 detects the center of the pupil as a specific site and the feature point setting unit 1030 fits the corneal shape data, the evaluation unit 1040 is detected by the specific site detection unit 1010. The evaluation is performed based on the deviation between the center of the pupil and the center of fitting set by the feature point setting unit 1030.

When both the specific part and the feature point represent the three-dimensional position, the evaluation unit 1040 evaluates by comparing these two three-dimensional positions. Similarly, when both the specific part and the feature point represent a two-dimensional position, the evaluation unit 1040 evaluates by comparing these two two-dimensional positions. On the other hand, when one of the specific part and the feature point represents the two-dimensional position and the other represents the three-dimensional position, the evaluation unit 1040 typically has the latter in the two-dimensional coordinate system representing the former two-dimensional position. The two can be compared by projecting the three-dimensional position.

A typical evaluation unit 1040 includes a processor that evaluates the wearing state of the Ortho-K lens based on a specific part and a feature point. The processor operates according to the evaluation software (program) for performing the evaluation. The analysis software includes, for example, software for calculating the deviation between a specific part and a feature point, and software for performing evaluation based on the calculated deviation and a predetermined evaluation standard (evaluation protocol). ..

The control unit 1050 controls each unit of the ophthalmic apparatus 1000. The control unit 1050 includes a processor that operates according to a control program.

Although not shown, the ophthalmic apparatus 1000 may further include a display device, an operation device, a communication device, and the like.

The operation of the ophthalmic apparatus 1000 according to this aspect will be described. An example of the operation of the ophthalmic apparatus 1000 is shown in FIG. Software for realizing the operation example shown in FIG. 2 is stored in a storage device (not shown) of the ophthalmic apparatus 1000. The ophthalmic apparatus 1000 executes a series of processes shown in FIG. 2 by operating according to this software.

(S1: Remove the Ortho K lens from the eye)
First, remove the ortho-K lens to be evaluated from the eye.

(S2: Perform preparatory operations such as alignment)
Next, a predetermined preparatory operation for performing the detection and measurement described later is performed. The preparatory operation includes, for example, alignment of the ophthalmic apparatus 1000 with respect to the eye, focus adjustment, and the like. Further, when OCT is performed in any of the detection and measurement described later, the optical path length adjustment and the polarization adjustment are typically executed as preparatory operations. These preparatory operations are performed by a known method and configuration.

(S3: Detects a specific part of the eye)
The specific site detection unit 1010 detects a specific site of the eye. A particular part of the eye is typically the apex of the cornea or the center of the pupil. As a result, the position data of a specific part of the eye can be obtained.

(S4: Measure the corneal shape of the eye)
The corneal shape measuring unit 1020 measures the corneal shape of the eye. The corneal shape data is typically corneal curvature distribution data or corneal radius of curvature distribution data. As a result, the corneal shape data of the eye can be obtained.

(S5: Set feature points from corneal shape data)
The feature point setting unit 1030 sets the feature points from the corneal shape data acquired in step S4. The feature points represent characteristic positions in the shape of the cornea and are typically the correction center. The correction center is typically the corneal apex or deformation center (fitting center, etc.).

(S6: Evaluate the wearing state of the Ortho-K lens)
The evaluation unit 1040 is based on the specific site detected in step S3 and the feature point set in step S5 (for example, based on the deviation between the specific site and the feature point), and the orthokeratology K with respect to the eye. Evaluate the mounting condition of the lens.

The control unit 1050 can output, save, and record the result of the evaluation executed in step S6. For example, the control unit 1050 controls the display device to display the evaluation result, or controls the communication device to transmit the evaluation result to another device (for example, a medical information management device such as an electronic chart system). The evaluation result is stored in the storage device provided in the ophthalmic apparatus 1000, the evaluation result is printed on a paper medium by controlling the printer, and the evaluation result is written on the recording medium by controlling the drive device or the like. It is possible to make it.

The order of the steps shown in FIG. 2 can be arbitrarily changed. For example, corneal shape measurement can be performed before detection of a specific site.

<Second aspect>
The ophthalmic apparatus according to the second aspect will be described. This aspect is applied when an Ortho-K lens is prescribed with reference to the apex of the cornea of the eye. In this embodiment, when the ortho-K lens is properly attached with reference to the corneal apex of the eye, the corneal apex after removing the ortho-K lens should coincide with the deformation center (fitting center, etc.). Assuming. Further, in this aspect, it is assumed that the eye has no astigmatism and that the shape (aspherical surface) of the cornea deformed by the ortho-K lens is isotropic. Here, the absence of astigmatism in the eye means that, for example, the measured value of the degree of astigmatism in the eye is equal to or less than a predetermined threshold value, and this embodiment can be applied to such an eye.

FIG. 3 shows a configuration example of the ophthalmic apparatus according to this aspect. The ophthalmic apparatus 2000 has an eye characteristic measurement function and additionally has an OCT function.

Examples of measurable eye characteristics are refractive power and corneal shape. Examples of refractive power parameters include spherical power, astigmatic power, and astigmatic axis angle. Examples of corneal shape parameters include corneal curvature and radius of curvature of the cornea. The corneal shape is typically represented by a corneal curvature distribution or a corneal radius of curvature distribution. In general, the curvature and the radius of curvature are inversely related to each other, and the corneal curvature and the radius of curvature of the cornea are equivalent parameters.

The type of OCT applicable to this aspect is arbitrary. Swept source OCT is applied in this embodiment, but it may be spectral domain OCT or other type. Here, the swept source OCT divides the light from the variable wavelength light source into the measurement light and the reference light, and superimposes the return light of the measurement light from the test object on the reference light to generate interference light, and this interference This is a method of constructing an image by detecting light with an optical detector and performing Fourier conversion or the like on the detection data collected in response to sweeping the wavelength and scanning the measurement light. On the other hand, the spectral domain OCT divides the light from the low coherence light source (broadband light source) into the measurement light and the 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 the spectral distribution of this interference light is detected by a spectroscope, and the detected spectral distribution is subjected to Fourier transform or the like to construct an image. That is, Swept Source OCT is an OCT method for acquiring the spectral distribution of interference light by time division, and Spectral Domain OCT is an OCT method for acquiring the spectral distribution of interference light by time division.

The ophthalmic apparatus may have other objective measurement functions, and may also have a subjective examination function. The subjective test is a measurement method for acquiring information by using the response from the subject, and is typically a subjective refraction measurement such as a distance test, a near test, a contrast test, a glare test, or a visual field test. and so on. Objective measurement is a measurement method in which eye data is acquired mainly by using a physical method without referring to a response from a subject. Objective measurement includes measurement for acquiring eye characteristic data and imaging for acquiring eye image data. In addition to the above-mentioned refractive power measurement and corneal shape measurement, the objective measurement includes intraocular pressure measurement, anterior ocular segment imaging, fundus photography, OCT and the like.

In this embodiment, unless otherwise specified, the conjugate relationship between the part of the eye and the position in the optical system means the mutual positional relationship in a state where alignment is preferable. For example, the fundus conjugate position in the optical system is a position that is optically conjugate with the fundus in a state where alignment is preferable, and means a position that is optically conjugate with the fundus or its vicinity. Further, the pupil conjugate position is a position optically conjugated with the pupil in a state in which alignment is preferable, and means a position optically conjugate with the pupil or its vicinity.

Hereinafter, the direction along the optical axis of the optical system of the ophthalmic apparatus 2000 is referred to as the Z direction. Further, the first coordinate axis (for example, the coordinate axis along the horizontal direction) and the second coordinate axis (for example, the vertical direction) of the two-dimensional Cartesian coordinate system (XY coordinate system) that defines the plane (XY plane) orthogonal to the optical axis (Z coordinate axis). The direction along the first coordinate axis (X coordinate axis) is called the X direction, and the direction along the second coordinate axis (Y coordinate axis) is called the Y direction.

The ophthalmic apparatus 2000 shown in FIG. 3 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a fixation projection system 4, an anterior segment observation system 5, a reflex measurement projection system 6, and a reflex measurement light receiving system 7. , And the OCT optical system 8. In the following, for example, the anterior segment observation system 5 uses light of 940 nm to 1000 nm, and the ref measurement optical system (ref measurement projection system 6, reflex measurement light receiving system 7) uses light of 830 nm to 880 nm, and the fixation projection system. It is assumed that 4 uses light of 400 nm to 700 nm, and OCT optical system 8 uses light of 1000 nm to 1100 nm.

The anterior segment observation system 5 captures a moving image of the anterior segment of the eye E. In the optical system passing through the anterior segment observation system 5, the image pickup surface of the image pickup element 59 is arranged at the pupil conjugate position. The anterior segment illumination light source 50 irradiates the anterior segment of the eye E with illumination light (for example, infrared light). The light reflected by the anterior segment of the eye E passes through the objective lens 51, passes through the dichroic mirror 52, passes through the hole formed in the diaphragm (teresen diaphragm) 53, and passes through the half mirror 23. It passes through the relay lenses 55 and 56 and passes through the dichroic mirror 76. The dichroic mirror 52 connects the optical path of the reflex measurement optical system and the optical path of the anterior segment observation system 5. The dichroic mirror 52 is arranged so that the optical path coupling surface to which these optical paths are coupled is inclined with respect to the optical axis of the objective lens 51. The light transmitted through the dichroic mirror 76 is imaged on the image pickup surface of the image pickup element 59 (area sensor) by the image pickup lens 58. The image sensor 59 performs image pickup and signal output at a predetermined rate. The output (video signal) of the image sensor 59 is input to the computer 9 described later. The computer 9 displays the anterior segment image E'based on this video signal on the display screen 10a of the display unit 10. The anterior segment image E'is, for example, an infrared moving image.

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

When the position of the corneal Cr (corneal apex) changes in the Z direction, the light projection position on the sensor surface of the line sensor 13 changes. The computer 9 obtains the position of the corneal apex of the eye E based on the light projection position on the sensor surface of the line sensor 13, and controls the mechanism for moving the optical system based on this to perform Z alignment. This Z alignment method is an example of an alignment method using an optical lever.

Any one-dimensional or two-dimensional image sensor can be used instead of the line sensor 13. That is, the photodetector provided in the Z alignment system may be an arbitrary image sensor in which a plurality of photodetectors (photodiodes and the like) are arranged one-dimensionally or two-dimensionally.

The XY alignment system 2 provides the eye E with a luminous flux (infrared light) for aligning in a direction orthogonal to the optical axis of the anterior segment observation system 5 (horizontal direction (X direction), vertical direction (Y direction)). Irradiate. The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22 provided in an optical path branched from the optical path of the anterior segment observation system 5 by a half mirror 23. The light output from the XY alignment light source 21 passes through the collimator lens 22, is reflected by the half mirror 23, and is projected onto the eye E through the anterior segment observation system 5. The reflected light from the corneal Cr of the eye E is guided to the image sensor 59 through the anterior segment observation system 5.

The image (bright spot image) Br based on this reflected light is included in the anterior segment image E'. The computer 9 displays the anterior segment image E'including the bright spot image Br and the alignment mark AL on the display screen 10a of the display unit 10. When the XY alignment is manually performed, the user operates the optical system so as to guide the bright spot image Br in the alignment mark AL. When the alignment is performed automatically, the computer 9 controls a mechanism for moving the optical system so that the deviation of the bright spot image Br with respect to the alignment mark AL is cancelled.

The kerato measurement system 3 projects a ring-shaped luminous flux (infrared light) for measuring the shape of the corneal Cr of the eye E onto the cornea Cr. The kerato plate 31 is arranged between the objective lens 51 and the eye E. A keratling light source 32 is provided on the back side (objective lens 51 side) of the kerato plate 31. By illuminating the kerato plate 31 with the light from the kerat ring light source 32, a ring-shaped luminous flux (arc-shaped or circumferential-shaped measurement pattern) is projected onto the corneal Cr of the eye E. The reflected light (keratling image) from the corneal Cr of the eye E is detected by the image sensor 59 together with the anterior segment image E'. The computer 9 calculates the value of the corneal shape parameter representing the shape of the corneal Cr by performing a known calculation based on this keratling image. A typical corneal shape parameter is the radius of curvature of the cornea (corneal curvature).

In addition, instead of or in addition to the kerato measurement system 3, the ophthalmic apparatus 2000 may include a corneal topography system (corneal topography system). The corneal topography system includes a group of elements for obtaining the above-mentioned corneal topography (see, for example, Japanese Patent Application Laid-Open No. 8-280624). The corneal topography system projects a multiple concentric pattern called platidling onto the corneal Cr. The reflected light (platidling image) from the corneal Cr is detected by the image sensor 59 together with the anterior segment image E'. The computer 9 obtains the distribution of the corneal shape parameters representing the shape of the corneal Cr by performing a known calculation based on the platidling image. The corneal topogram is provided by expressing the obtained distribution data in pseudo color.

The reflex measurement optical system includes a reflex measurement projection system 6 and a reflex measurement light receiving system 7 used for refractive power measurement. The reflex measurement projection system 6 projects a luminous flux for measuring the refractive power (for example, a ring-shaped luminous flux) onto the fundus Ef. This luminous flux is typically infrared light. The reflex measurement light receiving system 7 detects the return light of this luminous flux from the eye E. The reflex measurement projection system 6 is provided in an optical path branched by a perforated prism 65 provided in the optical path of the reflex measurement light receiving system 7. The hole formed in the perforated prism 65 is arranged at the pupil conjugate position. In the optical system that passes through the reflex measurement light receiving system 7, the image pickup surface of the image pickup device 59 is arranged at the fundus conjugate position.

In this aspect, the ref measurement light source 61 may be, for example, a superluminescent diode (SLD) which is a high-luminance light source. The reflex measurement light source 61 is movable in the optical axis direction. The reflex measurement light source 61 is arranged at the fundus conjugate position. The light output from the reflex measurement light source 61 passes through the relay lens 62 and is incident on the conical surface of the conical prism 63. The light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63. The light emitted from the bottom surface of the conical prism 63 passes through the translucent portion formed in a ring shape on the ring diaphragm 64. The light (ring-shaped luminous flux) that has passed through the translucent portion of the ring diaphragm 64 is reflected by the reflecting surface formed around the hole portion of the perforated prism 65, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. To. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the eye E. The rotary prism 66 is used for averaging the light amount distribution of the ring-shaped luminous flux with respect to the blood vessels and diseased parts of the fundus Ef and reducing speckle noise caused by the light source.

The return light of the ring-shaped luminous flux projected on the fundus Ef passes through the objective lens 51 and is reflected by the dichroic mirror 52 and the dichroic mirror 67. The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the hole portion of the perforated prism 65, passes through the relay lens 71, is reflected by the reflection mirror 72, and is reflected by the relay lens 73 and the focusing lens. Pass through 74. The focusing lens 74 can move along the optical axis of the reflex measurement light receiving system 7. The light that has passed through the focusing lens 74 is reflected by the reflection mirror 75, reflected by the dichroic mirror 76, and imaged on the image pickup surface of the image pickup element 59 by the image pickup lens 58. The computer 9 calculates the refractive power value of the eye E by performing a known calculation based on the output from the image sensor 59. For example, the power value includes at least one of spherical power, astigmatic power and astigmatic axis angle, and equivalent spherical power.

The OCT optical system 8 is provided in an optical path whose wavelength is separated from the optical path of the ref measurement optical system by the dichroic mirror 67. The fixation projection system 4 is provided in the optical path branched from the optical path of the OCT optical system 8 by the dichroic mirror 83.

The fixation projection system 4 presents the fixation target to the eye E. The fixation unit 40 is arranged in the optical path of the fixation projection system 4. The fixation unit 40 is controlled by a computer 9 described later, and can move along the optical path of the fixation projection system 4. The fixation unit 40 includes a liquid crystal panel 41.

The liquid crystal panel 41 controlled by the computer 9 displays a pattern representing the fixation target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the eye E can be changed. The fixation position is centered on the position for acquiring an image centered on the macula, the position for acquiring an image centered on the optic nerve head, and the center of the fundus between the macula and the optic nerve head. There is a position to acquire the image to be used. It is possible to arbitrarily change the display position of the pattern representing the fixation target. Instead of the liquid crystal panel 41, a transmissive optotype chart on which an optotype or the like is printed on a film or the like and an illumination light source for illuminating the optotype chart may be provided.

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

The OCT optical system 8 is an optical system for applying OCT to the eye E. The position of the focusing lens 87 is adjusted so that the end face of the optical fiber f1 is conjugated with the imaging site (fundus Ef or anterior segment of the eye) based on the result of the reflex measurement performed before the OCT.

The OCT optical system 8 is provided in an optical path whose wavelength is separated from the optical path of the reflex measurement optical system by a dichroic mirror 67. The optical path of the fixation projection system 4 is coupled to the optical path of the OCT optical system 8 by the dichroic mirror 83. As a result, the optical axes of the OCT optical system 8 and the fixation projection system 4 can be coaxially coupled.

The OCT optical system 8 includes an OCT unit 100. As shown in FIG. 4, in the OCT unit 100, the OCT light source 101 includes a tunable light source capable of sweeping the wavelength of the emitted light, similar to a general Swept source type OCT device. The tunable light source includes a laser light source including a resonator. The OCT light source 101 changes the output wavelength with time in a near-infrared wavelength band that is invisible to the human eye. The OCT light source 101 includes, for example, a near-infrared wavelength tunable laser that changes the wavelength of emitted light (wavelength range of 1000 nm to 1100 nm) at high speed.

As illustrated in FIG. 4, the OCT unit 100 is provided with an optical system for performing Swept Source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing the light from the variable wavelength light source into the measurement light and the reference light, and superimposes the return light of the measurement light from the eye E and the reference light passing through the reference optical path to generate the interference light. It has a function to generate and a function to detect this interference light. The detection result (detection signal) of the interference light obtained by the interference optical system is a signal representing the spectrum of the interference light and is sent to the computer 9. Further, at least one of the length of the optical path (measurement arm, sample arm) of the measurement light and the length of the optical path (reference arm) of the reference light are variable.

The light L0 output from the OCT light source 101 is guided by the optical fiber 102 to the polarization controller 103, and its polarization state is adjusted. The light L0 whose polarization state is adjusted is guided by the optical fiber 104 to the fiber coupler 105 and divided into the measurement light LS and the reference light LR.

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

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

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

The optical scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. The optical scanner 88 includes, for example, a first galvano mirror and a second galvano mirror. The first galvanometer mirror deflects the measurement light LS so as to scan the imaging region (fundus Ef or anterior segment) in the horizontal direction (X direction) orthogonal to the optical axis of the OCT optical system 8. The second galvano mirror deflects the measurement light LS deflected by the first galvano mirror so as to scan the imaging portion in the vertical direction (Y direction) orthogonal to the optical axis of the OCT optical system 8. Examples of the scan pattern of the optical LS measured by the optical scanner 88 include horizontal scan, vertical scan, cross scan, radial scan, circular scan, concentric circular scan, and spiral scan.

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

The fiber coupler 122 superimposes the measurement light LS incidented through the optical fiber 128 and the reference light LR incidented through the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference light LCs by branching the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs are guided to the detector 125 through optical fibers 123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that detect each pair of interference light LCs, and outputs the difference between the pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to the data acquisition system (DAQ) 130.

A clock KC is supplied to the DAQ 130 from the OCT light source 101. The clock KC is generated in the OCT light source 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the tunable light source. The OCT light source 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then sets the clock KC based on the result of detecting the combined light. Generate. The DATA 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ130 sends the sampling result of the detection signal from the detector 125 to the computer 9. The computer 9 forms a reflection intensity profile in each A line by, for example, performing a Fourier transform or the like on the spectral distribution based on the sampling data for each series of wavelength sweeps (for each A line). Further, the computer 9 forms image data by imaging the reflection intensity profile of each A line.

In this example, an element (movable corner cube 114) for changing the reference arm length is provided in order to change the difference between the measurement arm length and the reference arm length to move the coherence gate. Elements may be adopted. For example, a movable mirror can be provided on the reference arm, or a retroreflector such as a movable corner cube can be provided on the measuring arm.

The computer 9 calculates a refractive power value from the measurement results obtained by using the reflex measurement optical system, and based on the calculated refractive power value, the fundus Ef, the reflex measurement light source 61, and the image pickup element 59 are conjugated. The reflex measurement light source 61 and the focusing lens 74 are moved to the positions in the optical axis direction. In some embodiments, the computer 9 moves the focusing lens 87 of the OCT optical system 8 in the optical axis direction in conjunction with the movement of the focusing lens 74. In some embodiments, the computer 9 moves the liquid crystal panel 41 (fixation unit 40) in the optical axis direction in conjunction with the movement of the reflex measurement light source 61 and the focusing lens 74. In addition to these, the computer 9 executes various controls, various data processes, various calculations, and the like.

The configuration of the processing system of the ophthalmic apparatus 2000 will be described. Examples of the functional configuration of the processing system of the ophthalmic apparatus 2000 are shown in FIGS. 5 and 6. FIG. 5 shows an example of a functional block diagram of the processing system of the ophthalmic apparatus 2000. FIG. 6 shows an example of a functional block diagram of the data processing unit 223.

The computer 9 controls each part of the ophthalmic apparatus 2000, performs various data processing, performs various calculations, and the like. The computer 9 includes one or more processors and one or more storage devices. The storage device includes, for example, a hard disk drive, RAM, ROM, semiconductor memory, and the like.

Various programs (software) such as one or more control programs, one or more data processing programs, and one or more arithmetic programs are stored in the storage device. When either processor operates according to any program, the computer 9 executes control, data processing, calculation, and the like. That is, the computer 9 executes control, data processing, calculation, and the like in cooperation with hardware such as a processor and software.

The computer 9 includes a control unit 210 and an arithmetic processing unit 220. Further, the ophthalmic apparatus 2000 includes a moving mechanism 200, a display unit 270, an operation unit 280, and a communication unit 290.

The moving mechanism 200 is a mechanism for moving the head portion of the ophthalmic apparatus 2000 in the front-back and left-right directions. The head includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a fixation projection system 4, an anterior segment observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an OCT optical system. 8 (at least an element group excluding the OCT unit 100) and the like are housed. For example, the moving mechanism 200 is provided with an actuator that generates a driving force for moving the head portion and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending a control signal to the actuator.

The control unit 210 includes one or more processors and controls each unit of the ophthalmic apparatus 2000. The control unit 210 includes a main control unit 211 and a storage unit 212. The storage unit 212 stores in advance a group of programs for controlling the ophthalmic apparatus 2000. The program group includes a light source control program, a detector control program, an optical scanner control program, an optical system control program, an alignment control program, an arithmetic processing program, a user interface program, and the like. The ophthalmic apparatus 2000 executes calculations and controls according to such a program.

The main control unit 211 performs various controls of the ophthalmic apparatus 2000. The control for the Z alignment system 1 includes the control of the Z alignment light source 11 and the control of the line sensor 13. The control of the Z alignment light source 11 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. The control of the line sensor 13 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. As a result, the Z alignment light source 11 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 211 captures the signal detected by the line sensor 13 and specifies the projection position of the light with respect to the line sensor 13 based on the captured signal. The main control unit 211 obtains the position of the corneal apex of the eye E based on the specified projection position, and controls the movement mechanism 200 based on this to move the head unit in the front-rear direction (Z alignment).

The control for the XY alignment system 2 includes the control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the XY alignment light source 21 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 211 captures the signal detected by the image sensor 59, and determines the position of the bright spot image based on the return light of the light from the XY alignment light source 21 based on the captured signal. The main control unit 211 controls the movement mechanism 200 so as to cancel the deviation of the bright spot image Br with respect to a predetermined target position (for example, the center position of the alignment mark AL) to move the head unit in the left-right, up-down direction. (XY alignment).

The control for the kerato measurement system 3 includes the control of the kerat ring light source 32 and the like. Control of the keratling light source 32 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the keratling light source 32 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform a known calculation on the keratling image detected by the image sensor 59. As a result, the value of the corneal shape parameter of the eye E is obtained. Even when the above-mentioned corneal topography system is provided, the main control unit 211 executes the same process.

Controls for the fixation projection system 4 include control of the liquid crystal panel 41 and movement control of the fixation unit 40. The control of the liquid crystal panel 41 includes turning on / off the display of the fixation target, switching the display position of the fixation target, and the like.

For example, the fixation projection system 4 is provided with a moving mechanism for moving the liquid crystal panel 41 (or fixation unit 40) in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and at least moves the liquid crystal panel 41 in the optical axis direction. As a result, the position of the liquid crystal panel 41 is adjusted so that the liquid crystal panel 41 and the fundus Ef are optically conjugated.

Control of the anterior segment observation system 5 includes control of the anterior segment illumination light source 50, control of the image pickup element 59, and the like. Control of the anterior segment illumination light source 50 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the lighting of the forearm illumination light source 50 can be switched between lighting and non-lighting, and the amount of light can be changed. Control of the image sensor 59 includes exposure adjustment, gain adjustment, and detection rate adjustment of the image sensor 59. The main control unit 211 captures the signal detected by the image sensor 59, and causes the arithmetic processing unit 220 to perform processing such as forming an image based on the captured signal.

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

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

The control for the OCT optical system 8 includes the control of the OCT light source 101, the control of the optical scanner 88, the control of the focusing lens 87, the control of the corner cube 114, the control of the detector 125, the control of the DAQ 130, and the like. Control of the OCT light source 101 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. The control of the optical scanner 88 includes control of the scan position, scan range, and scan speed by the first galvanometer mirror, control of the scan position, scan range, and scan speed by the second galvanometer mirror.

The control of the focusing lens 87 includes control of movement of the focusing lens 87 in the optical axis direction, control of movement of the focusing lens 87 to the focusing reference position corresponding to the imaging region, and movement range corresponding to the imaging region (focusing). There is movement control within the focal range). For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 87 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 87 in the optical axis direction. In some embodiments, the ophthalmic apparatus 2000 is provided with a holding member that holds the focusing lenses 74 and 87 and a driving unit that drives the holding member. The main control unit 211 controls the movement of the focusing lenses 74 and 87 by controlling the drive unit. For example, the main control unit 211 may move the focusing lens 87 in conjunction with the movement of the focusing lens 74, and then move only the focusing lens 87 based on the intensity of the interference signal.

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

Further, the main control unit 211 includes a measured value of the optical power calculated by the eye refractive power calculation unit 221, a tomographic image (OCT image) formed by the image forming unit 222, and a result obtained by the data processing unit 223 described later. The information corresponding to the above is displayed on the display unit 270.

The storage unit 212 stores various types of data. As an example of the data stored in the storage unit 212, the data obtained by objective measurement, the data obtained by OCT scan, the image data of the tomographic image, the image data of the anterior segment image, and the data processed unit 230 are supplied. Data, data generated by the data processing unit 230, eye test information, and the like. The eye test information includes information related to the test eye such as left eye / right eye identification information.

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

The eye refractive power calculation unit 221 is a ring image (pattern image) obtained by detecting the return light of the ring-shaped luminous flux (ring-shaped measurement pattern) projected on the fundus Ef by the reflex measurement projection system 6 by the image sensor 59. ) Is analyzed. For example, the eye refractive power calculation unit 221 obtains the position of the center of gravity of the ring image from the brightness distribution in the image in which the obtained ring image is drawn, and obtains the brightness distribution along a plurality of scanning directions extending radially from this center of gravity position. , The ring image is specified from this brightness distribution. Subsequently, the optical power calculation unit 221 obtains an approximate ellipse of the specified ring image, and substitutes the major axis and the minor axis of the approximate ellipse into a known equation to obtain a spherical power, an astigmatic power, and an astigmatic axis angle (refraction). Power value) is calculated. Alternatively, the eye refractive power calculation unit 221 can obtain the parameter of the eye refractive power based on the deformation and deviation of the ring image with respect to the reference pattern.

In addition, the optical power calculation unit 221 calculates the radius of curvature of the cornea (corneal curvature) based on the keratling image acquired by the anterior segment observation system 5. For example, the optical power calculation unit 221 calculates the radius of curvature of the strong main meridian and the radius of curvature of the weak main meridian on the anterior surface of the cornea by analyzing the keratling image, and applies statistical processing to these radii of curvature to apply statistical processing to the cornea. Calculate the radius of curvature. This statistical processing may be, for example, averaging, selection of maximum values, or selection of minimum values. The eye refractive power calculation unit 221 can calculate the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism axis angle based on the calculated radius of curvature of the cornea.

The method for determining the radius of curvature of the cornea is not limited to the method using keratling. For example, in addition to the method using the corneal topography system (platidling) described above, an arbitrary corneal shape analysis method such as a method using a slit scan, a method using a Scheimpflug camera, and a method using an anterior segment OCT is applied. It is possible. The optical power calculation unit 221 has a function as a part of the corneal shape measurement unit 1020 in the first aspect.

The image forming unit 222 forms the image data of the tomographic image of the eye E (fundus Ef, anterior eye portion, etc.) based on the output from the OCT system 8 (DAQ130). This image forming process includes filtering, a fast Fourier transform (FFT), and the like, similar to the conventional (Swept source) OCT. By such processing, the reflection intensity profile in the A line (scan path of the measurement light LS in the eye E) is acquired, and the image data (A scan data) of the A line is formed by imaging this reflection intensity profile. Will be done.

Further, the image forming unit 222 forms a plurality of A scan data according to the mode of OCT scan (deflection of the measurement light LS, movement of the A scan position), and arranges these A scan data to obtain two-dimensional image data. Three-dimensional image data can be constructed.

When a plurality of tomographic image data (stack data) are obtained by raster scanning or the like, the image forming unit 222 constructs voxel data (volume data) by applying voxelization processing such as interpolation processing to these tomographic image data. can do. Further, the image forming unit 222 can render the stack data or the volume data. The rendering method is arbitrary and may be, for example, volume rendering, multi-section reconstruction (MPR), surface rendering, or the like. Further, the image forming unit 222 can construct a plane image (for example, a front image) from the stack data or the volume data. For example, the image forming unit 222 can construct a projection image by integrating stack data or volume data along each A line.

The data processing unit 223 can execute various data processing. The data processing unit 223 can process the data (OCT data) acquired by using the OCT scan. The OCT data is, for example, a reflection intensity profile or image data. The data processing unit 223 can process the image obtained by the anterior segment observation system 5 and the signal (data) output from the line sensor 13 of the Z alignment system 1. The data processing unit 223 can also process data other than the data illustrated here.

For example, the data processing unit 223 can apply segmentation to stack data or volume data. Segmentation is a known process for identifying a partial region in image data. The data processing unit 223 performs segmentation based on the brightness value of the OCT image (two-dimensional tomographic image, three-dimensional image, etc.). For example, the plurality of layered tissues in the fundus Ef each have a characteristic reflectance, and the image region of these layered tissues also has a characteristic luminance value. The data processing unit 223 executes segmentation so as to specify a target image region based on these characteristic luminance values. The target imaging region is, for example, 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, It corresponds to any tissue of the fundus Ef, such as choroid and strong membrane.

As shown in FIG. 6, the data processing unit 223 includes a first analysis unit 2231, a feature point setting unit 2232, and an evaluation unit 2233. As described above, the optical power calculation unit 221 functions as a part (second analysis unit) of the corneal shape measurement unit 1020. In this embodiment, the anterior segment observation system 5 acquires a first captured image and a second captured image of the eye E. The first captured image and the second captured image may be different images from each other or may be the same image.

The first captured image is provided to the first analysis unit 2231 to detect a specific part of the eye E (for example, the apex of the cornea or the center of the pupil). When detecting the apex of the cornea, the anterior segment observation system 5 photographs the eye E in a state where the luminous flux from the XY alignment system 2 is projected, and the bright spot image (Pulkiner image) formed by the luminous flux is photographed. Acquires the first captured image in which is drawn. Alternatively, when detecting the corneal apex, the anterior segment observation system 5 is formed by the pattern light by photographing the eye E in a state where the pattern light from the kerato measurement system 3 or the corneal topography system is projected. The first photographed image in which the resulting Pearn image (keratling image, platidling image) is drawn is acquired. When detecting the center of the pupil, the anterior segment observation system 5 acquires the first captured image in which the pupil of the eye E is depicted. When detecting another specific part, the first captured image corresponding to the specific part is acquired. The first analysis unit 2231 is configured to execute the same data processing as the specific site detection unit 1010 of the first aspect.

Here, when detecting the apex of the cornea, the element group including the XY alignment system 2, the anterior segment imaging system 5, and the first analysis unit 2231 functions as the specific site detection unit 1010 of the first aspect. When detecting the center of the pupil, the element group including the anterior segment imaging system 5 and the first analysis unit 2231 functions as the specific site detection unit 1010 of the first aspect. When detecting another specific site, the element group including at least the anterior ocular segment imaging system 5 and the first analysis unit 2231 functions as the specific site detection unit 1010 of the first aspect.

The second captured image is provided to the eye refractive power calculation unit 221 (second analysis unit) for measuring the corneal shape of the eye E. As described above, the optical power calculation unit 221 generates corneal shape data (typically, corneal curvature distribution data or corneal radius of curvature distribution data) which is measurement data by kerato measurement or corneal topography. The optical power calculation unit 221 (second analysis unit) is configured to execute the same data processing as the corneal shape measurement unit 1020 of the first aspect. The anterior segmental observation system 5 and the optical power calculation unit 221 (second analysis unit) of the present embodiment function as the corneal shape measurement unit 1020 of the first aspect.

The corneal shape data obtained by the eye refractive power calculation unit 221 is provided to the feature point setting unit 2232. The feature point setting unit 2232 functions as the feature point setting unit 1030 of the first aspect, and is configured to execute data processing similar to this.

The evaluation unit 2233 evaluates the wearing state of the orthokeratology lens with respect to the eye E based on the specific portion detected by the first analysis unit 2231 and the feature points set by the feature point setting unit 2232. The evaluation unit 2233 functions as the evaluation unit 1040 of the first aspect, and is configured to execute data processing similar to this.

The operation of the ophthalmic apparatus 2000 according to this aspect will be described. An example of the operation of the ophthalmic apparatus 2000 is shown in FIG. A storage device (not shown) of the ophthalmic apparatus 2000 stores software for realizing an operation example shown in FIG. 7. The ophthalmic apparatus 2000 executes a series of processes shown in FIG. 7 by operating according to this software.

(S11: Remove the Ortho K lens from the eye)
First, the ortho-K lens to be evaluated is removed from the eye E.

(S12: Performs preparatory operations such as alignment)
Next, a predetermined preparatory operation is performed in the same manner as in step S2 of the first aspect.

(S13: Start projecting pattern light onto the cornea)
Next, the ophthalmic apparatus 2000 projects the pattern light onto the cornea of the eye E by the kerato measurement system 3 or the corneal topography system. The projection of the pattern light is continued at least until the anterior segment image is acquired.

(S14: Capture the anterior segment image)
Next, the ophthalmic apparatus 2000 acquires an anterior segment image of the eye E in a state where the pattern light is projected on the cornea. Typically, the ophthalmologic apparatus 2000 starts moving the anterior segment of the eye by the anterior segment observation system 5 in step S12 and captures the frame obtained after step S13.

The acquired anterior segment image may be not only a pattern image formed by the pattern light but also an image of a luminous flux (bright spot image, Purkinje image) from the XY alignment system 2. Alternatively, the ophthalmic apparatus 2000 may separately acquire the anterior segment image in which the pattern image is depicted and the anterior segment image in which the bright spot image is depicted.

(S15: Detect the corneal apex)
The first analysis unit 2231 analyzes the anterior segment image acquired in step S14 to detect the corneal apex. As a result, the position data of the corneal apex of the eye E after removing the Ortho-K lens can be obtained. That is, the position data of the corneal apex of the eye E in which the cornea is deformed by the ortho-K lens can be obtained.

When the image of the luminous flux (bright spot image, Pulkinje image) from the XY alignment system 2 is drawn on the anterior segment image, the first analysis unit 2231 sets the X and Y coordinates of the bright spot image to the corneal apex. It can be obtained as two-dimensional position data. Further, when the image of the luminous flux from the XY alignment system 2 is depicted in the anterior segment image and the stereo imaging described in the first aspect is possible, the first analysis unit 2231 is different from each other. The three-dimensional position data of the corneal apex can be obtained from the two bright spot images drawn on the two anterior segment images taken from the directions. On the other hand, when the image of the luminous flux from the XY alignment system 2 is not drawn on the anterior segment image, the first analysis unit 2231 may use, for example, the keratling image (concentric pattern image) projected by the kerato measurement system 3. The center of the ring image having the smallest diameter can be obtained as the two-dimensional position data of the corneal apex.

(S16: Generates eye corneal shape data)
The optical power calculation unit 221 (second analysis unit) analyzes the anterior segment image acquired in step S14 to generate corneal shape data (for example, corneal curvature distribution data or corneal curvature radius distribution data). Further, the eye refractive power calculation unit 221 (second analysis unit) may generate height distribution data obtained by integrating the corneal curvature distribution data twice as corneal shape data. The height distribution data is, for example, data expressing a relative height with respect to a predetermined position (for example, the position of the apex of the cornea).

(S17: Determine the fitting center from the corneal shape data)
The feature point setting unit 2232 sets the feature point from the corneal shape data acquired in step S16. In this operation example, the fitting center is required as a feature point.

As described above, the fitting center is the center of the mathematical formula that approximates the corneal shape data (typically, the center of the fitting curved surface, the center of the fitting curve). This formula may be a centrally symmetric formula and may be an aspherical formula. This aspherical expression may be, for example, an expression including at least the expression of the conic surface, and may be an expression obtained by adding an even-order polynomial to the expression of the conic surface.

An equation obtained by adding an even-order polynomial to the equation of the conic plane is typically expressed as: z = (ch ² / (1 + √ (1- (1 + k) c ² h ² ) )) + Ah ⁴ + Bh ⁶ + Ch ^8. Where z is the sag amount of the plane parallel to the Z axis, h is the coordinates in any direction on the XY plane, c is the curvature, k is the conic coefficient, A, B and C is the coefficient of the fourth-order, sixth-order, and eighth-order terms of the polynomial, respectively. Here, if h is (hh ₀ ), an aspherical expression regarding an arbitrary center position h ₀ can be expressed.

The feature point setting unit 2232 applies the aspherical fitting by such a mathematical formula to the corneal shape data. The aspherical fitting may be, for example, an aspherical fitting centered on the apex of the cornea or an aspherical fitting having an arbitrary center.

Since the eye E is assumed to be an astigmatic eye in this embodiment, the feature point setting unit 2232 applies, for example, a two-dimensional center-symmetrical aspherical fitting to a certain meridian of the cornea, and the center (fitting center) thereof. ) To find the coordinates. Alternatively, when the corneal shape data is three-dimensional data, the feature point setting unit 2232 can apply a point-symmetrical aspherical fitting to the corneal shape data and obtain the coordinates of the center (fitting center). ..

(S18: Calculate the deviation of the corneal apex and the fitting center)
The evaluation unit 2233 compares the position data of the corneal apex detected in step S15 with the position data of the fitting center determined in step S17, and calculates the deviation Δ between them.

The offset delta, for example, deviation [Delta] X in the X direction, the Y-direction deflection [Delta] Y, deviation [Delta] xy = √ in the XY plane (ΔX ² + ΔY ^2), and, excursion ΔXYZ in XYZ space = √ (ΔX ² + ΔY It may be any of ² + ΔZ ² ). The deviation Δ may be a deviation ΔYZ in the YZ plane, a deviation ΔZX in the ZX plane, or a deviation according to another definition.

(S19: deviation> threshold?)
The evaluation unit 2233 compares the deviation Δ calculated in step S18 with a predetermined threshold value. This threshold is set to, for example, 0.5 mm, but may be set to another value. The ophthalmic apparatus 2000 displays the comparison result on the display unit 270.

When it is determined that the deviation Δ exceeds the threshold value (S19: Yes), the process proceeds to step S20. On the other hand, when it is determined that the deviation Δ is equal to or less than the threshold value (S19: No), the processing of this operation example ends (end).

(S20: Review the prescription of Ortho K lens)
When it is determined that the deviation Δ exceeds the threshold value (S19: Yes), the user (doctor or the like) reviews the prescription of the Ortho-K lens for the eye E. For example, the user determines and prescribes the type of Ortho-K lens that is more suitable for the eye E.

Similar to the first aspect, the ophthalmologic apparatus 2000 can output, store, and record the result of the evaluation performed in step S19 and the result of the review of the prescription made in step S20. Further, the order of the steps shown in FIG. 7 can be arbitrarily changed.

The evaluation of the mounted state of the orthokeratology lens in this embodiment will be described with reference to FIGS. 8A and 8B. Here, FIG. 8A corresponds to a case where the mounting state is good, and FIG. 8B corresponds to a case where the mounting state is poor.

Reference numeral 2100 in FIG. 8A indicates a map (corneal topomap) created based on the corneal curvature distribution data obtained by corneal topography. The distribution represented by the corneal topomap 2100 is, for example, a corneal curvature distribution, a corneal radius of curvature distribution, a corneal curvature distribution or a refractive power distribution based on the corneal radius of curvature distribution, a height distribution based on the corneal curvature distribution, or another distribution. You can. Hereinafter, the corneal topomap 2100 will be described as a map expressing the corneal curvature distribution, but the same matter holds true even when other distributions are applied.

Reference numeral 2110 indicates a predetermined meridian of the cornea. Reference numeral 2120 is a graph showing the curvature distribution on the meridian 2110. Reference numeral 2130 indicates a correction center (fitting center) determined by applying an aspherical fitting to the curvature distribution graph 2120. Reference numeral 2200 indicates the position of the corneal apex detected by analyzing the anterior segment image.

Here, the corneal apex position 2200 is an example of the data acquired in step S15 of FIG. 7, and the fitting center 2120 is an example of the data acquired in step S17. In this case, step S18 calculates the deviation Δ1 (deviation in the direction along the meridian 2110) between the corneal apex position 2200 and the fitting center 2130.

In step S19, it is determined whether or not the deviation Δ1 exceeds the threshold value. In this example, the deviation Δ1 is determined to be below the threshold value, and the evaluation result that the currently used Ortho-K lens (its wearing state) is appropriate is obtained, and the prescription of the Ortho-K lens in step S20 is reviewed. Not done. However, it does not prevent the user from reviewing the formulation of the Orthokeratology lens by referring to the deviation Δ1, the corneal topomap 2100, the curvature distribution graph 2120, other examination data, the interview data, and the like.

On the other hand, reference numeral 2300 in FIG. 8B indicates another corneal topomap. Reference numeral 2310 indicates a predetermined meridian of the cornea. Reference numeral 2320 is a graph showing the curvature distribution on the meridian 2310. Reference numeral 2330 indicates a correction center (fitting center) determined by applying an aspherical fitting to the curvature distribution graph 2320. Reference numeral 2400 indicates the position of the corneal apex detected by analyzing the anterior segment image.

Similar to the example shown in FIG. 8A, the corneal apex position 2400 is an example of the data acquired in step S15 of FIG. 7, and the fitting center 2320 is an example of the data acquired in step S17. In this case, step S18 calculates the deviation Δ2 (deviation in the direction along the meridian 2310) between the corneal apex position 2400 and the fitting center 2330.

In step S19, it is determined whether or not the deviation Δ2 exceeds the threshold value. In this example, it was determined that the deviation Δ2 exceeded the threshold value, and an evaluation result was obtained that the currently used Ortho-K lens (its wearing state) was not appropriate. Therefore, the formulation of the Ortho-K lens in step S20 was reviewed. Is done. However, the user may review the prescription of the orthokeratology lens by referring to the deviation Δ2, the corneal topomap 2300, the curvature distribution graph 2320, other examination data, the interview data, and the like.

Comparing the two curvature distribution graphs 2120 and 2320, in the curvature distribution graph 2120, the inclination of the left end portion and the inclination of the right end portion are substantially equal, and the graph shape is relatively symmetrical, while the curvature distribution graph. In 2320, the inclination of the left end portion is gentler than the inclination of the right end portion, and the graph shape is relatively asymmetrical. This is because in the example shown in FIG. 8A, the deviation between the center position of the ortho-K lens and the apex position of the cornea is relatively small, and the effect of the ortho-K lens is generally exhibited as expected, whereas the example shown in FIG. 8B. However, the deviation is relatively large, and the effect of the Ortho-K lens is not sufficiently obtained.

As described above, according to the example shown in FIG. 8A, the degree of coincidence between the corneal apex and the correction center is high, the fitting of the ortho-K lens is good, and the aspherical shape (the shape of the ortho-K lens or its approximate shape). Is symmetrical about the apex of the cornea, and it can be seen that the Orthokeratology lens matches the cornea well. Furthermore, it can be seen that various lens parameters such as the base curve of the central region of the Orthokeratology lens are appropriate, and the corneal curvature distribution as intended (close to the target) is achieved.

On the other hand, according to the example shown in FIG. 8B, the degree of coincidence between the corneal apex and the correction center is low, the fitting of the ortho-K lens is poor, the aspherical shape is asymmetric with respect to the corneal apex, and the ortho-K lens. It turns out that does not match the cornea. Furthermore, it can be seen that various lens parameters such as the base curve of the central region of the Orthokeratology lens are not appropriate, and the intended corneal curvature distribution is not achieved. These suggest that the Ortho-K lens may have shifted at night. If this deviation is large, it may adversely affect eyesight.

The evaluation unit 2233 may be configured to quantify and / or qualitate these evaluation indexes. For example, the evaluation unit 2233 quantitatively and / or qualitatively expresses the degree of coincidence between the corneal apex and the correction center based on the magnitude of the deviation Δ, and quantitatively and / or expresses the symmetry number of the curvature distribution graph. It can be expressed qualitatively. Here, the symmetry quantification is, for example, a calculation for obtaining the difference or ratio between the area of the left side portion and the area of the right side portion of the curvature distribution graph, or a calculation for obtaining the laterality of the difference between the curvature distribution graph and the symmetry curve. Etc. may be included.

In step S20 (review of the prescription of the ortho-K lens), for example, review of various parameters of the ortho-K lens, search for the optimum value, simulation, and the like are performed. The parameters of the Ortho-K lens are the diameter of the entire lens, the diameter of the base curve in the center of the lens, the dimensions of the chord of the optical zone (treatment zone), the width / depth of the transition zone (return zone), and the peripheral zone. (Landing zone) diameter, angle, width, end width, refractive power, etc.

<Third aspect>
The ophthalmic apparatus according to the third aspect will be described. Hereinafter, unless otherwise specified, the terms, symbols, etc. in the second aspect shall apply mutatis mutandis.

Similar to the second aspect, this aspect applies when the ortho-K lens is prescribed relative to the apex of the cornea of the eye. Further, as in the second aspect, in this aspect, when the ortho-K lens is properly attached with reference to the corneal apex of the eye, the corneal apex after removing the ortho-K lens is the deformation center (fitting center). Etc.), and it is assumed that they should match.

On the other hand, unlike the second aspect, in this aspect, it is assumed that the eye has astigmatism and that the shape (aspherical surface) of the cornea deformed by the orthokeratology lens is isotropic. Here, the presence of astigmatism in the eye means, for example, that the measured value of the degree of astigmatism of the eye exceeds a predetermined threshold value, and this embodiment can be applied to such an eye.

This aspect can be realized by an ophthalmic apparatus having the same configuration and function as the second aspect. However, while the second aspect targets the astigmatic eye, this aspect targets the astigmatic eye. Therefore, instead of step S17 in FIG. 7 in the second aspect, for example, the approximate expression shown below is used. (Biconic surface equation) is applied to the fitting of corneal shape data.

The approximate expression applied in this embodiment is typically expressed as: z = ((c _x x ² + c _y y ² ) / (1 + √ (1- (1 + k _x )) ) c _x ² x ^2- (1 + k _y ) c _y ² y ² ))) + A _R ((1-A _P ) x ² + (1 + A _P ) y ² ) ² + B _R ((1) -B _P ) x ² + (1 + B _P ) y ² ) ³ + C _R ((1-C _P ) x ² + (1 + C _P ) y ² ) ⁴ . Here, z is the sag amount of the plane parallel to the Z axis, x is the X coordinate, y is the Y coordinate, c _x is the curvature in the X direction, c _y is the curvature in the Y direction, and k _x is the cornic coefficient in the X direction. k _y is the Y-direction of the conic coefficient, a _R, B _R and C _R are fourth order, respectively conic, sixth and eighth order coefficient of rotational symmetry portion, a _P, fourth order, respectively B _P and C _P conic , 6th and 8th order non-rotational symmetry parts. Here, if x is (xx ₀ ) and y is (yy ₀ ), an aspherical expression regarding an arbitrary center position (x ₀ , y ₀ ) can be expressed. As a special case, if k _x = k _y and c _x = c _y , the same point-symmetrical cornic surface equation as in the second aspect can be obtained.

The feature point setting unit 2232 applies the aspherical fitting by such a mathematical formula to the corneal shape data. The aspherical fitting may be, for example, an aspherical fitting centered on the apex of the cornea or an aspherical fitting having an arbitrary center.

Since the eye E is assumed to be an astigmatic eye in this embodiment, fitting is performed on two (or more) meridians that are different from each other. Fitting is typically performed on two meridians that are orthogonal to each other. The two meridians are typically a meridian along the astigmatic axis of the eye E and a meridian orthogonal to it. That is, the feature point setting unit 2232 first applies a two-dimensional center-symmetrical aspherical fitting to the first meridian of the cornea, and obtains the coordinates of the center (fitting center). Next, the feature point setting unit 2232 performs the same fitting on the second meridian different from the first meridian, and obtains the coordinates of the center (fitting center). Alternatively, when the corneal shape data is three-dimensional data, the feature point setting unit 2232 may apply the fitting by the mathematical formula of the biconic surface to the corneal shape data and obtain the coordinates of the center (fitting center). it can.

With respect to matters other than those described above, the second aspect can be applied to this aspect.

<Fourth aspect>
The ophthalmic apparatus according to the fourth aspect will be described. Hereinafter, unless otherwise specified, the terms, symbols, etc. in the second aspect shall apply mutatis mutandis.

Unlike the second and third aspects, this aspect applies when an ortho-K lens is prescribed relative to the pupil of the eye. In this aspect, it is assumed that the center of the pupil after removing the Ortho-K lens should coincide with the center of correction. Further, as in the second aspect, it is assumed that the eye E is an astigmatic eye and that the shape (aspherical shape) of the cornea deformed by the ortho-K lens is isotropic. This aspect can be realized by an ophthalmic apparatus having the same configuration and function as the second aspect.

Similar to the second aspect, the data processing unit 223 includes a first analysis unit 2231, a feature point setting unit 2232, and an evaluation unit 2233 (see FIG. 6). Further, the eye refractive power calculation unit 221 functions as a part (second analysis unit) of the corneal shape measurement unit 1020 (see FIG. 6). Further, the anterior segment observation system 5 acquires the first captured image and the second captured image of the eye E.

The first captured image is provided to the first analysis unit 2231 to detect a specific part of the eye E (center of the pupil in this embodiment). The anterior segment observation system 5 acquires a first captured image in which the pupil of the eye E is depicted. For example, the first analysis unit 2231 analyzes the first captured image obtained by photographing the eye E from the front by the anterior segment observation system 5, detects the pupil edge, and applies an elliptical fitting to the pupil edge. To find an ellipse that approximates the pupil edge, and find the center of this ellipse. This elliptical center is adopted as two-dimensional position data of the pupil center. In another example, the first analysis unit 2231 analyzes the first captured image obtained by photographing the eye E from the front by the anterior segment observation system 5, detects the pupil edge or the pupil region, and determines the center of gravity thereof. You may ask. This ellipse center of gravity is adopted as two-dimensional position data of the ellipse center. In still another example, when stereo imaging described in the first aspect is possible, the first analysis unit 2231 may display two first captured images (two anterior segment images) captured from different directions. By applying the same processing to the pupil, the three-dimensional position data of the center of the pupil can be obtained. In this aspect, the element group including the anterior ocular segment imaging system 5 and the first analysis unit 2231 functions as the specific site detection unit 1010 of the first aspect.

The second captured image is provided to the eye refractive power calculation unit 221 (second analysis unit) for measuring the corneal shape of the eye E. The optical power calculation unit 221 generates corneal shape data (typically, corneal curvature distribution data or corneal radius of curvature distribution data) which is measurement data by kerato measurement or corneal topography. The optical power calculation unit 221 (second analysis unit) is configured to execute the same data processing as the corneal shape measurement unit 1020 of the first aspect. The anterior segmental observation system 5 and the optical power calculation unit 221 (second analysis unit) of the present embodiment function as the corneal shape measurement unit 1020 of the first aspect.

The corneal shape data obtained by the eye refractive power calculation unit 221 is provided to the feature point setting unit 2232. The feature point setting unit 2232 functions as the feature point setting unit 1030 of the first aspect, and is configured to execute data processing similar to this. The feature point in this embodiment may be an arbitrary correction center, and is typically a detection position of the corneal apex or an estimated position of the deformation center. The deformation center is typically the fitting center.

The evaluation unit 2233 evaluates the wearing state of the ortho-K lens with respect to the eye E based on the pupil center detected by the first analysis unit 2231 and the feature point (correction center) set by the feature point setting unit 2232. Execute. The evaluation unit 2233 functions as the evaluation unit 1040 of the first aspect, and is configured to execute data processing similar to this.

The operation of the ophthalmic apparatus 2000 according to this aspect will be described. An example of the operation of the ophthalmic apparatus 2000 is shown in FIG. A storage device (not shown) of the ophthalmic apparatus 2000 stores software for realizing an operation example shown in FIG. The ophthalmic apparatus 2000 executes a series of processes shown in FIG. 9 by operating according to this software.

(S31: Remove the Ortho K lens from the eye)
First, the ortho-K lens to be evaluated is removed from the eye E.

(S32: Performs preparatory operations such as alignment)
Next, a predetermined preparatory operation is performed in the same manner as in step S2 of the first aspect.

(S33: Start projecting pattern light onto the cornea)
Next, the ophthalmic apparatus 2000 projects the pattern light onto the cornea of the eye E by the kerato measurement system 3 or the corneal topography system. The projection of the pattern light is continued at least until the anterior segment image is acquired.

(S34: Capture the anterior segment image)
Next, the ophthalmic apparatus 2000 acquires an anterior segment image of the eye E in a state where the pattern light is projected on the cornea. Typically, the ophthalmologic apparatus 2000 starts moving the anterior segment of the eye by the anterior segment observation system 5 in step S12 and captures the frame obtained after step S33.

(S35: Detects the center of the pupil)
The first analysis unit 2231 analyzes the anterior segment image acquired in step S34 to detect the center of the pupil.

(S36: Generates eye corneal shape data)
The optical power calculation unit 221 (second analysis unit) analyzes the anterior segment image acquired in step S34 to generate corneal shape data (for example, corneal curvature distribution data or corneal curvature radius distribution data). Further, the eye refractive power calculation unit 221 (second analysis unit) may generate height distribution data obtained by integrating the corneal curvature distribution data twice as corneal shape data.

(S37: Determine the correction center from the corneal shape data)
The feature point setting unit 2232 sets the feature point from the corneal shape data acquired in step S36. In this operation example, an arbitrary correction center is required as a feature point. The correction center is typically the corneal center or fitting center.

When determining the corneal center as the correction center, the feature point setting unit 2232 executes, for example, the same corneal center detection process as in step S15 of FIG. 7 in the second aspect. When obtaining the fitting center as the correction center, the feature point setting unit 2232 executes, for example, the same aspherical fitting as step S15 of FIG. 7 in the second aspect.

(S38: Calculate the deviation of the center of the pupil and the center of correction)
The evaluation unit 2233 compares the position data of the pupil center detected in step S35 with the position data of the correction center determined in step S37, and calculates the deviation Δ between them.

(S39: deviation> threshold?)
The evaluation unit 2233 compares the deviation Δ calculated in step S38 with a predetermined threshold value. The ophthalmic apparatus 2000 displays the comparison result on the display unit 270.

When it is determined that the deviation Δ exceeds the threshold value (S39: Yes), the process proceeds to step S40. On the other hand, when it is determined that the deviation Δ is equal to or less than the threshold value (S39: No), the processing of this operation example ends (end).

(S40: Review the prescription of Ortho K lens)
When it is determined that the deviation Δ exceeds the threshold value (S39: Yes), the user (doctor or the like) reviews the prescription of the Ortho-K lens for the eye E.

The ophthalmologic apparatus 2000 can output, store, and record the result of the evaluation performed in step S39 and the result of the review of the prescription made in step S40. Further, the order of the steps shown in FIG. 9 can be arbitrarily changed.

The evaluation of the mounted state of the orthokeratology lens in this embodiment will be described with reference to FIGS. 10A and 10B. Here, FIG. 10A corresponds to a case where the mounting state is good, and FIG. 10B corresponds to a case where the mounting state is poor.

The corneal topomap 2500 shown in FIG. 10A will be described as a map expressing the corneal curvature distribution, but the same matter holds true even when other distributions are applied. Reference numeral 2510 indicates a predetermined meridian of the cornea. Reference numeral 2520 is a graph showing the curvature distribution on the meridian 2510. Reference numeral 2530 indicates a correction center (fitting center) determined by applying an aspherical fitting to the curvature distribution graph 2520. Reference numeral 2600 indicates the position of the center of the pupil detected by analyzing the anterior segment image.

Here, the pupil center position 2600 is an example of the data acquired in step S35 of FIG. 9, and the fitting center 2520 is an example of the data acquired in step S37. In this case, step S38 calculates the deviation Δ3 (deviation in the direction along the meridian 2510) between the pupil center position 2600 and the fitting center 2530.

In step S39, it is determined whether or not the deviation Δ3 exceeds the threshold value. In this example, the deviation Δ3 is determined to be below the threshold value, and the evaluation result that the currently used Ortho-K lens (its wearing state) is appropriate is obtained, and the prescription of the Ortho-K lens in step S40 is reviewed. Not done. However, it does not prevent the user from reviewing the prescription of the Orthokeratology lens by referring to the deviation Δ3, the corneal topomap 2500, the curvature distribution graph 2520, other test data, the interview data, and the like.

On the other hand, reference numeral 2700 in FIG. 10B indicates another corneal topomap. Reference numeral 2710 indicates a predetermined meridian of the cornea. Reference numeral 2720 is a graph showing the curvature distribution on the meridian line 2710. Reference numeral 2730 indicates a correction center (fitting center) determined by applying an aspherical fitting to the curvature distribution graph 2720. Reference numeral 2800 indicates the position of the center of the pupil detected by analyzing the anterior segment image.

Similar to the example shown in FIG. 10A, the pupil center position 2800 is an example of the data acquired in step S35 of FIG. 9, and the fitting center 2720 is an example of the data acquired in step S37. In this case, step S38 calculates the deviation Δ4 (deviation in the direction along the meridian 2710) between the pupil center position 2800 and the fitting center 2730.

In step S39, it is determined whether or not the deviation Δ4 exceeds the threshold value. In this example, it was determined that the deviation Δ4 exceeded the threshold value, and an evaluation result was obtained that the currently used Ortho-K lens (its wearing state) was not appropriate, and the prescription of the Ortho-K lens in step S40 was reviewed. Is done. However, the user may review the formulation of the Orthokeratology lens by referring to the deviation Δ4, the corneal topomap 2700, the curvature distribution graph 2720, other examination data, the interview data, and the like.

The inclination of the curvature distribution graph, the symmetry of the curvature distribution graph, the quantification and qualitativeization of the evaluation index, the review of the formulation of the ortho-K lens, and the like may be the same as those of the second aspect.

<Fifth aspect>
The ophthalmic apparatus according to the fifth aspect will be described. Hereinafter, unless otherwise specified, the terms, symbols, etc. in the above aspects shall apply mutatis mutandis.

Similar to the fourth aspect, this aspect is applied when the ortho-K lens is prescribed with reference to the pupil of the eye. Further, as in the fourth aspect, in this aspect, when the ortho-K lens is properly attached with reference to the center of the pupil of the eye, the center of the pupil after removing the ortho-K lens is the center of correction (corneal center). , Fitting center, etc.).

On the other hand, unlike the fourth aspect, in this aspect, it is assumed that the eye has astigmatism and that the shape (aspherical surface) of the cornea deformed by the orthokeratology lens is isotropic. Here, the presence of astigmatism in the eye means, for example, that the measured value of the degree of astigmatism of the eye exceeds a predetermined threshold value, and this embodiment can be applied to such an eye.

This aspect can be realized by an ophthalmic apparatus having the same configuration and function as the fourth aspect. However, while the fourth aspect is intended for astigmatic eyes, this aspect is intended for astigmatic eyes, so instead of step S37 in FIG. 9 in the fourth aspect, for example, in the third aspect. The described biconic surface approximation formula is applied to the fitting of corneal shape data. That is, the feature point setting unit 2232 of this embodiment applies the aspherical fitting based on the approximation formula of the biconic surface to the corneal shape data. The aspherical fitting may be, for example, an aspherical fitting centered on the apex of the cornea or an aspherical fitting having an arbitrary center.

Since the eye E is assumed to be an astigmatic eye in this embodiment, fitting is performed on two (or more) meridians that are different from each other. Fitting is typically performed on two meridians that are orthogonal to each other. The two meridians are typically a meridian along the astigmatic axis of the eye E and a meridian orthogonal to it. That is, the feature point setting unit 2232 first applies a two-dimensional center-symmetrical aspherical fitting to the first meridian of the cornea, and obtains the coordinates of the center (fitting center). Next, the feature point setting unit 2232 performs the same fitting on the second meridian different from the first meridian, and obtains the coordinates of the center (fitting center). Alternatively, when the corneal shape data is three-dimensional data, the feature point setting unit 2232 may apply the fitting by the mathematical formula of the biconic surface to the corneal shape data and obtain the coordinates of the center (fitting center). it can.

With respect to matters other than those described above, the fourth aspect can be applied to this aspect.

<Effect>
Some effects of the ophthalmic apparatus according to the exemplary embodiments described above will be described.

The ophthalmic apparatus according to the exemplary embodiment includes a specific site detection unit, a corneal shape measurement unit, a feature point setting unit, and an evaluation unit. For example, the ophthalmic apparatus 1000 includes a specific site detection unit 1010, a corneal shape measurement unit 1020, a feature point setting unit 1030, and an evaluation unit 1040. Further, the ophthalmic apparatus 2000 has a corneal shape including a specific site detection unit including an anterior ocular region observation system 5 and a first analysis unit 2231, and an anterior ocular region observation system 5 and an ocular refractive force calculation unit 221 (second analysis unit). It includes a measuring unit, a feature point setting unit 2232, and an evaluation unit 2233.

The specific site detection unit is configured to detect a specific site of the eye after the ortho-K lens is removed. The specific site is, for example, the apex of the cornea or the center of the pupil. The corneal shape measuring unit is configured to measure the corneal shape of the eye. The feature point setting unit is configured to set feature points from the corneal shape data acquired by the corneal shape measurement unit. The evaluation unit is configured to evaluate the wearing state of the orthokeratology lens on the eye based on the specific part detected by the specific part detection unit and the feature point set by the feature point setting unit. ing.

According to such an exemplary embodiment, it is possible to automatically determine the suitability of the mounting position of the Ortho-K lens. Therefore, it is possible to actually obtain the expected refraction correction effect and the material for judging what the refraction state of the peripheral vision is (that is, whether or not the Ortho K lens was mounted at an appropriate position at night). It is possible to provide the user (doctor, etc.) with the material for determining whether or not the lens is present.

In the ophthalmic apparatus according to the exemplary embodiment, the feature point setting unit may be configured to set feature points based on an approximate expression of corneal shape data by a centrally symmetric expression. This approximate expression is, for example, a centrally symmetric curved surface expression or a curve expression. According to such a configuration, it is possible to perform approximation (fitting) according to the shape of the cornea deformed by the ortho-K lens having a centrally symmetrical shape.

In an exemplary embodiment, the centrally symmetric equation used as the approximate equation may be an aspherical equation. That is, the feature point setting unit may be configured to set feature points based on an approximate expression of corneal shape data by a predetermined aspherical expression. According to such a configuration, it is possible to perform fitting according to the shape of the cornea deformed by the ortho-K lens having the aspherical shape portion.

In an exemplary embodiment, the predetermined aspherical expression may be an expression that includes at least a conic surface expression or a biconic surface expression. According to such a configuration, it is possible to perform fitting according to the shape of the cornea deformed by the ortho-K lens having a conic-shaped or bi-conic-shaped portion.

In an exemplary embodiment, the predetermined aspherical expression may be an expression obtained by adding an even-order polynomial to a conic surface expression or an expression obtained by adding an even-order polynomial to a biconic surface expression. By using such an aspherical type, it becomes possible to perform aspherical fitting to the shape of the cornea deformed by the ortho-K lens having a shape having an inflection point with high accuracy.

In an exemplary embodiment, fitting may be performed in at least one direction (meridian) of the cornea if the given aspherical formula includes at least the formula for the conic plane. That is, the feature point setting unit may be configured to approximate the corneal shape data in at least one direction by an aspherical expression including at least a conic surface equation. According to such a configuration, when the aspherical property of the corneal shape is isotropic as in an astigmatic eye, for example, one (or more) meridian lines are preferably fitted by the equation of the cornic surface. It is also possible, and in the case where the aspherical property of the corneal shape is isotropic, for example, astigmatic eyes, it is possible to preferably perform fitting by the equation of the conic surface for two (or more) meridian lines. It is possible.

In an exemplary embodiment, if a given aspherical formula includes at least a conic plane formula, fitting may be performed in each of two directions (two meridians) orthogonal to each other in the cornea. That is, the feature point setting unit may be configured to approximate the corneal shape data in each of the two directions orthogonal to each other by an aspherical expression including at least the equation of the conic surface. According to such a configuration, when the aspherical surface of the corneal shape is isotropic as in an astigmatic eye, it is possible to suitably fit two meridians orthogonal to each other by the equation of the cornic surface. Is.

In an exemplary embodiment, if the given aspherical formula includes at least the conic plane formula, fitting may be performed for the astigmatic axis direction of the cornea and the direction orthogonal thereto. That is, the feature point setting unit may be configured to approximate the corneal shape data in each of the astigmatic axis direction of the eye and the direction orthogonal to the astigmatic axis direction of the eye by an aspherical type including at least the formula of the conic surface. According to such a configuration, it is possible to preferably perform fitting by the formula of the cornic surface for astigmatic eyes.

In an exemplary embodiment, three-dimensional fitting may be performed if the given aspherical formula includes at least the formula for the biconic surface. That is, the feature point setting unit may be configured to approximate the corneal shape data by a three-dimensional aspherical expression including at least the equation of the biconic surface. According to such a configuration, it is possible to suitably perform fitting according to the three-dimensional shape of the cornea.

In an exemplary embodiment, the feature point setting unit may be configured to set the center of the approximate expression of the corneal shape data by the centrally symmetric expression as the feature point based on the corneal shape data. According to such a configuration, it is possible to suitably set the feature points of the cornea deformed by the ortho-K lens having a centrally symmetric shape based on the fitting by the centrally symmetric equation.

In an exemplary embodiment, the specific site detection unit may be configured to detect the corneal apex as a specific site, and the evaluation unit is located between the corneal apex and the center of the approximate expression by a centrally symmetric expression. It may be configured to perform an evaluation of the wearing state of the Ortho-K lens with respect to the eye based on the deviation of. According to such a configuration, it is possible to preferably evaluate, for example, an ortho-K lens formulated based on the apex of the cornea.

In an exemplary embodiment, the specific site detection unit may be configured to detect the center of the pupil as a specific site, and the evaluation unit is located between the center of the pupil and the center of the approximate expression by a centrally symmetric expression. It may be configured to perform an evaluation of the wearing state of the Ortho-K lens with respect to the eye based on the deviation of. According to such a configuration, it is possible to preferably evaluate, for example, an ortho-K lens prescribed based on the pupil.

In an exemplary embodiment, the corneal shape measuring unit may be configured to acquire the curvature distribution data or the radius of curvature distribution data of the cornea as the corneal shape data. According to such a configuration, the corneal shape data obtained by a general corneal shape measuring device such as a keratometer, a corneal topographer, or an OCT device can be used for evaluation of an orthokeratology lens.

In an exemplary embodiment, the corneal shape measuring unit may be configured to acquire corneal height distribution data as corneal shape data. According to such a configuration, the height distribution data obtained by integrating the corneal shape data obtained by a general corneal shape measuring device twice can be used for the evaluation of the ortho-K lens.

An exemplary embodiment can provide a method of controlling an ophthalmic apparatus including an imaging unit and a processor that images the eye. For example, the ophthalmic apparatus 1000 includes an imaging unit (optical system, image sensor, camera, etc.) for photographing the anterior segment of the eye, and a processor (one or more). Further, the ophthalmic apparatus 2000 includes an anterior ocular segment observation system 5 that functions as an imaging system and a computer provided with a processor.

In the control method according to the exemplary embodiment, in the first control step, the photographing unit is controlled in order to acquire the first photographed image and the second photographed image of the eye after removing the ortho-K lens. Further, in the second control step, the processor is controlled to analyze the first captured image in order to detect the specific part of the eye. Further, in the third control step, the processor is controlled to analyze the second captured image in order to acquire the corneal shape data of the eye. Further, in the fourth control step, the processor is controlled so as to set a feature point from the corneal shape data acquired based on the third control step. In addition, in the fifth control step, the evaluation of the wearing state of the orthokeratology lens with respect to the eye is based on the specific portion detected in the second control step and the feature points set in the fourth control step. Control the processor to run.

It is possible to combine any of the matters described with respect to the ophthalmic device according to the exemplary embodiment with such a control method of the ophthalmic device.

It is possible to provide a program for causing an ophthalmic apparatus including a computer to execute a control method according to an exemplary embodiment. It is possible to combine this program with any of the items described with respect to the ophthalmic device according to the exemplary embodiment.

It is possible to create a computer-readable non-temporary recording medium on which such a program is recorded. It is possible to combine this recording medium with any of the items described with respect to the ophthalmic apparatus according to the exemplary embodiment. The non-temporary recording medium may be in any form, and examples thereof include a magnetic disk, an optical disk, a magneto-optical disk, and a semiconductor memory.

According to the control method, the program, or the recording medium according to the exemplary embodiment, it is possible to make the ophthalmic apparatus perform the suitability determination of the mounting position of the Ortho-K lens. As a result, it is possible to actually obtain the expected refraction correction effect and the material for judging what the refraction state of the peripheral vision is (that is, whether or not the Ortho-K lens was mounted in an appropriate position at night). It becomes possible to directly or indirectly provide the user (doctor, etc.) with the material for determining whether or not the lens is used.

<Other aspects>
In the above exemplary embodiment, the ophthalmic apparatus including the function of photographing the eye (imaging unit) has been described, but the embodiment is not limited thereto. For example, the ophthalmic information processing apparatus described below is a computer that receives an image of an eye acquired by another ophthalmic apparatus having an imaging function and executes a series of processes.

The ophthalmic information processing device according to the exemplary embodiment is, for example, a personal computer, a server provided on a local area network (LAN), a server (cloud server, etc.) provided on a wide area network (WAN), or another. It may include a computer in the form of.

The configuration of the ophthalmic information processing apparatus according to the exemplary embodiment is shown in FIG. The ophthalmic information processing apparatus 3000 includes an image receiving unit 3010, a first analysis unit 3020, a second analysis unit 3030, a feature point setting unit 3040, an evaluation unit 3050, and a control unit 3060.

The image receiving unit 3010 receives an image obtained by photographing the eye with another ophthalmic apparatus. The image receiving unit 3010 includes, for example, either a communication device or a drive device.

The communication device of the image receiving unit 3010 receives, for example, a captured image from another ophthalmic apparatus via a network. Alternatively, the communication device of the image receiving unit 3010 receives the captured image stored in the image archiving system or the like from another ophthalmic device via the network.

The drive device of the image receiving unit 3010 reads out the captured image acquired by another ophthalmic device and recorded on the recording medium from the recording medium.

The image receiving unit 3010 receives the first captured image and the second captured image of the eye after removing the ortho-K lens. The first captured image and the second captured image are the same as those in the second aspect. Typically, the first captured image and the second captured image received by the image receiving unit 3010 are stored in a storage device (not shown), and the first captured image is provided to the first analysis unit 3020 by the control unit 3060. The second captured image is provided to the second analysis unit 3030 by the control unit 3060.

The first analysis unit 3020 is configured to execute the same data processing as the processor of the specific site detection unit 1010 of the ophthalmic apparatus 1000 (the same data processing as the first analysis unit 2231 of the ophthalmic apparatus 2000). 1 It functions to analyze the captured image and detect a specific part.

The second analysis unit 3030 is configured to execute the same data processing as the processor of the corneal shape measuring unit 1020 of the ophthalmic apparatus 1000 (the same data processing as the ophthalmic refractive force calculation unit 221 of the ophthalmic apparatus 2000). It functions to analyze the second captured image and acquire corneal shape data.

The feature point setting unit 3040 is configured to execute the same data processing as the feature point setting unit 1030 of the ophthalmic apparatus 1000 (the same data processing as the feature point setting unit 2232 of the ophthalmic apparatus 2000), and is configured to perform the second analysis. It functions to set a feature point from the corneal shape data acquired by the unit 3030.

The evaluation unit 3050 is configured to execute the same data processing as the evaluation unit 1040 of the ophthalmic apparatus 1000 (the same data processing as the evaluation unit 2233 of the ophthalmic apparatus 2000), and was detected by the first analysis unit 3020. It functions to evaluate the wearing state of the ortho-K lens on the eye based on the specific portion and the feature point set by the feature point setting unit 3040.

The control unit 3060 controls each unit of the ophthalmic information processing apparatus 3000. The control unit 3060 includes a processor that operates according to the control program.

According to the ophthalmic information processing device 3000 configured in this way, it is possible to automatically determine the suitability of the mounting position of the ortho-K lens based on the captured image of the eye acquired by another ophthalmic device. Therefore, it is possible to actually obtain the expected refraction correction effect and the material for judging what the refraction state of the peripheral vision is (that is, whether or not the Ortho K lens was mounted at an appropriate position at night). It is possible to provide the user (doctor, etc.) with the material for determining whether or not the lens is present.

In an exemplary embodiment, the ophthalmic information processing apparatus 3000 can be installed on a network to be capable of processing images taken from a plurality of ophthalmic apparatus. As a result, the ophthalmic information processing apparatus 3000 can perform the evaluation process intensively (unifiedly) without providing the ortho-K lens evaluation function in each ophthalmic apparatus. According to this configuration, it is possible to widely provide an evaluation service of the wearing state of the Ortho-K lens.

It is possible to combine such an ophthalmic information processing apparatus 3000 with any of the items described with respect to the ophthalmic apparatus (1000, 2000) according to the exemplary embodiment.

An exemplary embodiment can provide a method of controlling an ophthalmic information processing device including a processor. For example, the ophthalmic information processing device 3000 includes (one or more) processors. The same applies to the computer 9 of the ophthalmic apparatus 2000.

In the control method according to the exemplary embodiment, in the first control step, the processor is controlled to analyze the first captured image of the eye after removing the ortho-K lens in order to detect a specific part of the eye. .. In the second control step, the processor is controlled to analyze the second captured image of the eye in order to acquire the corneal shape data of the eye. In the third control step, the processor is controlled so as to set a feature point from the corneal shape data acquired in the second control step. In the fourth control step, the evaluation of the wearing state of the orthokeratology lens on the eye is executed based on the specific portion detected in the first control step and the feature points set in the third control step. Control the processor to do so.

It is possible to combine any of the matters described with respect to the ophthalmic apparatus according to the exemplary embodiment with the control method of such an ophthalmic information processing apparatus. Further, it is possible to combine any of the items described with respect to the ophthalmic information processing device according to the exemplary embodiment with the control method of such an ophthalmic information processing device.

A program can be provided that causes a computer to execute a control method according to an exemplary embodiment. It is possible to combine this program with any of the items described with respect to the ophthalmic device according to the exemplary embodiment. It is also possible to combine this program with any of the items described for the ophthalmic information processing apparatus according to the exemplary embodiment.

It is possible to create a computer-readable non-temporary recording medium on which such a program is recorded. It is possible to combine this recording medium with any of the items described with respect to the ophthalmic apparatus according to the exemplary embodiment. In addition, it is possible to combine this recording medium with any of the items described with respect to the ophthalmic information processing apparatus according to the exemplary embodiment. The non-temporary recording medium may be in any form, and examples thereof include a magnetic disk, an optical disk, a magneto-optical disk, and a semiconductor memory.

According to the control method, the program, or the recording medium according to the exemplary embodiment, it is possible to make the computer execute the suitability determination of the mounting position of the Ortho-K lens. As a result, it is possible to actually obtain the expected refraction correction effect and the material for judging what the refraction state of the peripheral vision is (that is, whether or not the Ortho K lens was mounted in an appropriate position at night). It becomes possible to directly or indirectly provide the user (doctor, etc.) with the material for determining whether or not the lens is used.

Some of the embodiments described above are merely examples of embodiments of the present invention. Therefore, it is possible to make arbitrary modifications (omission, substitution, addition, etc.) within the scope of the gist of the present invention.

1000 Ophthalmology device 1010 Specific site detection unit 1020 Corneal shape measurement unit 1030 Feature point setting unit 1040 Evaluation unit 2000 Ophthalmology device 5 Front eye observation system 221 Eye refractive force calculation unit 2231 First analysis unit 2232 Feature point setting unit 2233 Evaluation unit 3000 Ophthalmology information processing device 3010 Image reception unit 3020 First analysis unit 3030 Second analysis unit 3040 Feature point setting unit 3050 Evaluation unit

Claims (20)

A specific part detection unit that detects a specific part of the eye after removing the orthokeratology lens,
The corneal shape measuring unit that measures the corneal shape of the eye,
A feature point setting unit that sets a feature point from the corneal shape data acquired by the cornea shape measurement unit, and a feature point setting unit.
An ophthalmic apparatus including an evaluation unit that evaluates the wearing state of the orthokeratology lens on the eye based on the specific portion and the feature point. The feature point setting unit sets the feature point based on the approximate expression of the corneal shape data by the centrally symmetric expression.
The ophthalmic apparatus of claim 1. The feature point setting unit sets feature points based on an approximate expression of the corneal shape data by a predetermined aspherical expression.
The ophthalmic apparatus of claim 2. The predetermined aspherical expression is an expression including at least a conic surface expression or a biconic surface expression.
The ophthalmic apparatus of claim 3. The predetermined aspherical expression is an expression obtained by adding an even-order polynomial to a conic surface expression or an expression obtained by adding an even-order polynomial to a biconic surface expression.
The ophthalmic apparatus of claim 4. The feature point setting unit approximates the corneal shape data in at least one direction by an aspherical expression including at least a conic surface equation.
The ophthalmic apparatus according to claim 4 or 5. The feature point setting unit approximates the corneal shape data in each of the two directions orthogonal to each other by an aspherical expression including at least the equation of the conic surface.
The ophthalmic apparatus according to claim 4 or 5. The feature point setting unit approximates the corneal shape data in each of the astigmatic axis direction of the eye and the direction orthogonal to the astigmatic axis direction of the eye by an aspherical type including at least the formula of the conic surface.
The ophthalmic apparatus of claim 7. The feature point setting unit approximates the corneal shape data by a three-dimensional aspherical expression including at least the equation of the biconic surface.
The ophthalmic apparatus according to claim 4 or 5. The feature point setting unit sets the center of the approximate expression as the feature point.
The ophthalmic device according to any one of claims 2 to 9. The specific site detection unit detects the corneal apex as the specific site,
The evaluation unit performs the evaluation based on the deviation between the apex of the cornea and the center of the approximate expression.
The ophthalmic apparatus of claim 10. The specific site detection unit detects the center of the pupil as the specific site,
The evaluation unit performs the evaluation based on the deviation between the center of the pupil and the center of the approximate expression.
The ophthalmic apparatus of claim 10. The corneal shape measuring unit acquires the curvature distribution data or the radius of curvature distribution data of the cornea as the corneal shape data.
The ophthalmic apparatus according to any one of claims 1 to 12. The corneal shape measuring unit acquires the height distribution data of the cornea as the corneal shape data.
The ophthalmic apparatus according to any one of claims 1 to 12. A method of controlling an ophthalmic apparatus including an imaging unit that photographs the eye and a processor.
Control the imaging unit to acquire the first and second captured images of the eye after removing the orthokeratology lens.
The processor is controlled to analyze the first captured image in order to detect a specific part of the eye.
The processor is controlled to analyze the second captured image in order to acquire the corneal shape data of the eye.
The processor is controlled so as to set a feature point from the corneal shape data,
The processor is controlled to perform an evaluation of the wearing state of the orthokeratology lens on the eye based on the specific portion and the feature point.
How to control an ophthalmic device. A program that causes an ophthalmic apparatus including a computer to execute the control method of claim 15. The first analysis unit that analyzes the first captured image of the eye after removing the orthokeratology lens to detect a specific part, and
A second analysis unit that analyzes the second captured image of the eye and acquires corneal shape data,
A feature point setting unit that sets feature points from the corneal shape data,
An ophthalmic information processing apparatus including an evaluation unit that evaluates the wearing state of the orthokeratology lens on the eye based on the specific portion and the feature point. A method of controlling an ophthalmic information processing device including a processor.
In order to detect a specific part of the eye, the processor is controlled to analyze the first captured image of the eye after removing the orthokeratology lens.
The processor is controlled to analyze the second captured image of the eye in order to acquire the corneal shape data of the eye.
The processor is controlled so as to set a feature point from the corneal shape data,
The processor is controlled to perform an evaluation of the wearing state of the orthokeratology lens on the eye based on the specific portion and the feature point.
Control method of ophthalmic information processing device. A program that causes a computer to execute the control method of claim 18. A computer-readable non-temporary recording medium on which the program of claim 16 or 19 is recorded.

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