JP7339011B2 - Ophthalmic device, ophthalmic information processing device, program, and recording medium - Google Patents

Description

The present invention relates to an ophthalmologic apparatus , an ophthalmologic information processing apparatus , a program , and a recording medium.

According to recent studies on the progression of myopia, it has been reported that the focal point of the peripheral vision is located behind the retinal surface, and that the retina tends to displace toward the back, leading to the progression of myopia ( See, for example, Non-Patent Document 1).

One of refractive correction means for increasing the refractive power in the peripheral vision (that is, making the peripheral refractive power negative or relatively decreasing the central refractive power) for the purpose of suppressing the progression of myopia. Orthokeratology (hereinafter abbreviated as “ortho-K”) is performed as one, and its effects have been clinically proven (see, for example, Non-Patent Document 2).

Ortho-K is a corneal correction therapy that treats refractive errors such as myopia by correcting the shape of the cornea by wearing contact lenses with a special curved design (ortho-K lenses). Ortho-K maintains its refractive correction effect for a certain period of time even after the contact lens is removed, so it is also suitable as a refractive correction method for contact sports and outdoor sports.

As mentioned above, the refractive state of the peripheral visual field (periphery) is thought to be important for suppressing the progression of myopia. The expected refractive correction effect can actually be obtained without being conscious of how the refractive state of the peripheral vision is (that is, whether or not the Ortho K lens was worn at the appropriate position at night). It is difficult to determine whether

Earl L. Smith III, Li-Fang Hung, Juan Huang, “Relative peripheral hyperopic defocus alters central refractive 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

SUMMARY OF THE INVENTION An object of the present invention is to make it possible to determine whether the mounting position of an ortho-K lens is appropriate.

An ophthalmologic apparatus according to some exemplary embodiments includes a storage unit that pre-stores design data of an orthokeratology lens, a corneal shape measurement unit that measures a corneal shape of an eye after the orthokeratology lens is removed, and the cornea an evaluation unit that evaluates the wearing state of the orthokeratology lens on the eye based on the corneal shape data acquired by the shape measurement unit and the design data.

In the ophthalmologic apparatus according to some exemplary aspects, the corneal topography measurement unit generates the corneal topography data by obtaining values of predetermined shape parameters for each of a plurality of positions on the cornea of the eye, and the evaluation The part includes two or more values included in the corneal shape data corresponding to two or more of the plurality of positions, and two or more design values included in the design data corresponding to the two or more positions. The evaluation is performed by comparing .

The ophthalmologic apparatus according to some exemplary aspects further includes a specific site detection unit that detects a specific site of the eye after the orthokeratology lens is removed, wherein the evaluation unit detects the two symmetrical regions with respect to the specific site. The evaluation is performed by comparing the two or more values corresponding to the locations with the two or more design values.

In the ophthalmologic apparatus according to some exemplary aspects, the evaluation unit calculates a first difference that is a difference calculated from the two or more values and the two or more design values, The evaluation is performed based on

In the ophthalmologic apparatus according to some exemplary aspects, the evaluation unit calculates a second difference that is a difference calculated from the two or more values, and performs the evaluation based on the second difference. .

In some exemplary aspects of the ophthalmic apparatus, the specific site is the corneal vertex of the eye after removal of the orthokeratology lens.

In some exemplary aspects of the ophthalmic apparatus, the specific site is the pupillary center of the eye after removal of the orthokeratology lens.

In some exemplary aspects of the ophthalmic apparatus, the specific site is the center of the iris diameter of the eye after removal of the orthokeratology lens.

In some exemplary aspects of the ophthalmic apparatus, the specific site is the center of the corneal diameter of the eye after removal of the orthokeratology lens.

In the ophthalmologic apparatus according to some exemplary aspects, the corneal topography measurement unit acquires curvature distribution data or curvature radius distribution data of the cornea of the eye after the orthokeratology lens is removed as the corneal topography data, The design data includes curvature distribution data or curvature radius distribution data of the orthokeratology lens.

In the ophthalmologic apparatus according to some exemplary aspects, the corneal topography measurement unit acquires curvature distribution data or curvature radius distribution data of the cornea of the eye after the orthokeratology lens is removed as the corneal topography data, The design data includes curvature distribution data or curvature radius distribution data set as a corneal shape correction target by the orthokeratology lens.

In the ophthalmologic apparatus according to some exemplary aspects, the corneal shape measurement unit acquires height distribution data of the cornea of the eye after removing the orthokeratology lens as the corneal shape data, and the design data is , including the shape data of said orthokeratology lens.

In the ophthalmologic apparatus according to some exemplary aspects, the corneal shape measurement unit acquires height distribution data of the cornea of the eye after removing the orthokeratology lens as the corneal shape data, and the design data is , including correction target shape data of the corneal shape by said orthokeratology lens.

A method according to some exemplary aspects is a method of controlling an ophthalmic device including an imager for imaging an eye and a processor, the ophthalmic device including an imager for imaging the eye, a memory, and a processor. comprising: controlling the processor to store orthokeratology lens design data in the storage unit; and controlling the imaging unit to obtain a captured image of the eye after the orthokeratology lens is removed. and controlling the processor to analyze the captured image to obtain corneal shape data of the eye, and determining the wearing state of the orthokeratology lens for the eye based on the corneal shape data and the design data. Control the processor to perform the evaluation.

A program according to some exemplary aspects is a program that causes an ophthalmologic apparatus including a computer to execute a control method according to any exemplary aspect.

An ophthalmologic information processing apparatus according to some exemplary aspects includes a storage unit that stores design data of an orthokeratology lens in advance, and acquires corneal shape data by analyzing a photographed image of an eye after the orthokeratology lens is removed. and an evaluation unit that evaluates the wearing state of the orthokeratology lens on the eye based on the corneal shape data and the design data.

A method according to some exemplary aspects is a method of controlling an ophthalmic information processing device including a memory and a processor, the processor being controlled to store orthokeratology lens design data in the memory. and controlling the processor to analyze captured images of the eye after removing the orthokeratology lens to obtain corneal shape data of the eye, and based on the corneal shape data and the design data. controlling the processor to perform an assessment of the fit of the orthokeratology lens on the eye;

A program according to some exemplary aspects is a program that causes a computer to execute a control method according to any exemplary aspect.

A recording medium according to some exemplary aspects is a computer-readable non-transitory recording medium on which a program according to any exemplary aspect is recorded.

According to an exemplary aspect, it is possible to perform an adequacy determination of the mounting position of the Ortho-K lens.

1 is a schematic diagram representing a configuration of an ophthalmic apparatus according to exemplary aspects; FIG. 4 is a flowchart representing the operation of an ophthalmic device in accordance with exemplary aspects; 1 is a schematic diagram representing a configuration of an ophthalmic apparatus according to exemplary aspects; FIG. 1 is a schematic diagram representing a configuration of an ophthalmic apparatus according to exemplary aspects; FIG. 1 is a schematic diagram representing a configuration of an ophthalmic apparatus according to exemplary aspects; FIG. 1 is a schematic diagram representing a configuration of an ophthalmic apparatus according to exemplary aspects; FIG. 4 is a flowchart representing the operation of an ophthalmic device in accordance with exemplary aspects; 1 is a schematic diagram showing the configuration of an ophthalmologic information processing apparatus according to an exemplary aspect; FIG.

Some exemplary aspects of embodiments are described below. It should be noted that the matters disclosed in the documents cited in this specification and the matters related to any known art can be incorporated into the exemplary embodiments.

Some exemplary aspects described below can be used to assess the fit of the Ortho-K lens, i.e., whether the Ortho-K lens was properly positioned on the eye (on the cornea). is. This is an evaluation of whether or not the cornea has been corrected to the desired shape. is located in front of the retinal plane).

In some embodiments described below, the "correction center" refers to, for example, the detected position of the vertex of the cornea deformed by the Ortho-K lens (corneal vertex) and the detected position of the center of the pupil (pupil center). It can be either. The definition of the center of correction is not limited to these, and may be other positions.

The corneal apex referred to herein is the most protruding position of the cornea after the Ortho-K lens is removed, and is generally deviated from the original corneal apex (the corneal apex without deformation effects of the Ortho-K lens). (Of course, this does not exclude the situation where the corneal apex under the influence of the Ortho-K lens coincides with the original corneal apex).

Detection of the corneal apex is performed, for example, by detecting a marker formed in the anterior segment. As a typical example, Japanese Patent Application Laid-Open No. 2015-85081 discloses that a luminous flux is projected onto the anterior eye and photographed from the front, and the resulting anterior eye image is analyzed to obtain a bright point image (Purkinje image). is detected, and the position (two-dimensional position) of this bright spot image is disclosed as the position of the corneal vertex. Further, Japanese Patent Application Laid-Open No. 2017-74115 performs imaging from two directions while projecting a light flux on the anterior segment (stereo imaging), analyzes the two anterior segment images acquired thereby, and bright point images ( Purkinje image) is detected, and the position (three-dimensional position) of this bright spot image is disclosed as the position of the corneal vertex. As another example of corneal vertex detection, the central position of the photographed image of the ring pattern light projected onto the cornea for measuring the radius of curvature of the cornea can be obtained as the position of the corneal vertex (two-dimensional position). An ophthalmic apparatus (keratometer) for measuring the radius of curvature of the cornea is disclosed, for example, in Japanese Patent Application Laid-Open No. 2-65833. As yet another example of corneal vertex detection, the position (three-dimensional position) of the corneal vertex is detected from an image of the anterior segment obtained by an optical coherence tomography (OCT) device (for example, JP-A-2015-157182). can do.

Detection of the center of the pupil is performed, for example, by acquiring an image (anterior segment image) obtained by photographing the anterior segment from the front, and applying luminance analysis to this anterior segment image to specify the pupil region. processing, processing to obtain the approximate ellipse of the pupil region, and processing to identify the center of the approximate ellipse and set it as the pupil center. In this example, the pupil center is obtained as a two-dimensional position. In another example, the detection of the pupil center is performed by applying stereo imaging to the anterior segment to acquire two anterior segment images, and applying luminance analysis to each of these anterior segment images to determine the pupillary region. A process of specifying, a process of obtaining approximate ellipses of each of the two pupil regions specified from the two anterior segment images, a process of specifying the center of each of the two approximate ellipses corresponding to the two pupil regions, and obtaining the pupil center as a three-dimensional position from two centers corresponding to the two pupil regions. In yet another example, a process of applying an OCT scan to the anterior segment to obtain an OCT image, a process of analyzing the OCT image to identify the pupillary region (iris region), and the peripheral edge of the pupillary region ( The inner peripheral edge of the iris region) is specified, the approximate ellipse of the pupil edge (iris edge) is obtained, and the center of the approximate ellipse is obtained as the center of the pupil. In this example, the pupil center is typically obtained as a three-dimensional position.

In some aspects, the corneal shape of an eye prescribed an Ortho-K lens is measured. The corneal shape may be, for example, a corneal curvature distribution, a corneal curvature radius distribution, or a height distribution. The corneal curvature distribution and the corneal curvature radius distribution are obtained by, for example, a keratometer and a corneal topogram (see, for example, JP-A-8-280624). The height distribution is obtained, for example, by integrating the corneal curvature distribution twice. Unlike general vision correction contact lenses, Ortho-K lenses have an inflection point of curvature between the center (optical zone, treatment zone) and the periphery (peripheral zone, landing zone). regions (transition zone, return zone) are provided.

In some aspects below, "processor" means, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (e.g., SPLD (Simple Programmable Logic D device) , CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array)), and the like. The processor, for example, reads and executes a program stored in a memory circuit or a memory device, thereby realizing a desired function.

<First Aspect>
An ophthalmologic apparatus according to a first aspect will be described. FIG. 1 shows a configuration example of an ophthalmologic apparatus according to this aspect. The ophthalmologic apparatus 1000 includes a storage unit 1010 , a corneal shape measurement unit 1020 , a specific site detection unit 1030 and an evaluation unit 1040 . The ophthalmologic apparatus 1000 further includes a control section 1050 that controls them.

The storage unit 1010 stores in advance the design data 1015 of the ortho-K lens. Storage unit 1010 includes, for example, a hard disk drive, RAM, ROM, semiconductor memory, and the like.

Exemplary design data 1015 may include any of the following data (design values): curvature distribution data for Ortho K lenses; radius of curvature distribution data for Ortho K lenses; corneal shape correction targets for Ortho K lenses. Curvature distribution data set as a corneal shape correction target by the Ortho K lens; Ortho K lens shape data; Correction target shape data of the corneal shape by the Ortho K lens.

The design values included in the exemplary design data 1015 are not limited to the examples shown above, and may include, for example, values of various parameters of the Ortho-K lens. Examples of Ortho-K lens parameters include the diameter of the entire lens, the diameter of the base curve at the center of the lens, the chord dimensions of the optical zone (treatment zone), the width and depth of the transition zone (return zone), and the peripheral Zone (landing zone) diameter, angle, width, end width, refractive power, etc.

The aspect and form of the design data 1015 are not limited to these. Also, some examples of the configuration of the storage unit 1010 and the processing related to the design data 1015 will be described below, but the present invention is not limited to these.

In some examples, the storage unit 1010 stores ortho-K lens design data 1015 for a plurality of patients, each design data 1015 including patient identification information (patient ID) and applicable eye information (left eye, right eye). eye). The control unit 1050 receives input of the patient ID and applicable eye information, selects the design data 1015 associated with them, and provides the evaluation unit 1040 and the like with the design data 1015 associated therewith.

Also, in some examples, the ortho-K lens design data 1015 for multiple patients is stored on a server located on a local area network (LAN) or a server located on a wide area network (WAN) (such as a cloud server). ). The control unit 1050 receives input of the patient ID and applicable eye information, transmits a request based on these to the server, receives the design data 1015 transmitted from the server in response to this request, and provides the evaluation unit 1040 and the like with the design data 1015 .

The corneal shape measurement unit 1020 measures the corneal shape of the eye to generate corneal shape data. For example, the corneal topography measurement component 1020 may be configured to generate corneal topography data by determining values of predetermined shape parameters for each of a plurality of locations on the cornea of the eye.

The corneal shape data is, for example, corneal curvature distribution data or corneal curvature radius distribution data obtained by a keratometer, corneal curvature distribution data or corneal curvature radius distribution data obtained by a corneal topographer, or by integrating the corneal curvature distribution data twice. , corneal curvature distribution data obtained by anterior segment OCT scanning, corneal curvature radius distribution data or height distribution data, and other measurement data.

As described above, exemplary design data 1015 includes any of the following design values: curvature distribution data for Ortho K lenses; radius of curvature distribution data for Ortho K lenses; Set curvature distribution data; Curvature radius distribution data set as a corneal shape correction target by the ortho K lens; Shape data of the ortho K lens; Correction target shape data of the corneal shape by the ortho K lens.

In some examples, if the design data 1015 includes ortho-K lens curvature distribution data or curvature radius distribution data, the corneal topography component 1020 is configured to obtain corneal curvature distribution data or curvature radius distribution data. . Further, in some examples, when the design data 1015 includes curvature distribution data or curvature radius distribution data set as a corneal shape correction target by the Ortho-K lens, the corneal topography measuring unit 1020 measures the corneal curvature distribution data or curvature radius distribution data. configured to obtain radius distribution data;

In some examples, if the design data 1015 includes ortho-K lens shape data, the corneal topography component 1020 is configured to obtain corneal height distribution data. Also, in some examples, the corneal topography component 1020 is configured to obtain corneal height distribution data when the design data 1015 includes correction target shape data for corneal topography with an Ortho-K lens.

A typical corneal topography measurement unit 1020 includes a projection system that projects light for forming a pattern image on the cornea, and an imaging unit (optical system, image pickup device, camera) that photographs the anterior segment on which the pattern image is formed. etc.) and a processor for analyzing the image obtained by the imaging unit. The processor operates, for example, according to analysis software (program) for obtaining corneal shape parameter distribution data. Another exemplary corneal topography unit 1020 includes an OCT system that applies an OCT scan to the cornea, a first processor that constructs an OCT image from data obtained by the OCT system, and a first processor that analyzes the generated OCT image. 2 processors. The first processor operates according to known OCT image construction software (program). The second processor operates, for example, according to analysis software (program) for obtaining corneal shape parameter distribution data.

A specific part detection unit 1030 detects a specific part of the eye after the ortho-K lens is removed. The specific portion of the eye is typically the corneal vertex or the pupillary center, but may be other portions.

For the detection of the corneal vertex, for example, as described above, a two-dimensional or three-dimensional position detection method based on Purkinje images, a two-dimensional position detection method based on keratling images, and a three-dimensional position using anterior segment OCT. Any of the position detection techniques and other detection techniques are applied.

For detecting the center of the pupil, for example, a two-dimensional position detection method by analyzing a frontal image of the anterior segment, a three-dimensional position detection method by analyzing two anterior segment images obtained by stereo imaging, and others is applied.

Examples of other parts of the eye detected by the specific part detection unit 1030 include the center (midpoint) of the iris diameter and the center (midpoint) of the corneal diameter.

The iris diameter is a line segment connecting two mutually opposing points on the outer periphery of the iris, typically a line segment along the horizontal direction. The iris diameter is also called the visible iris diameter. Detection of the iris diameter includes, for example, analysis of a front image of the anterior segment, analysis of two anterior segment images obtained by stereo imaging, or analysis of other anterior segment images. The specific part detection unit 1030 can specify the midpoint of the detected iris diameter using such analysis and set it as the center of the iris diameter.

The corneal diameter is a line segment connecting two points facing each other on the outer edge of the cornea (the inner edge of the conjunctiva, the boundary between the cornea and the conjunctiva), and is typically a line segment along the horizontal direction. Corneal diameter is also called white to white. Detection of the corneal diameter includes, for example, analysis of a frontal image of the anterior segment, analysis of two anterior segment images obtained by stereo imaging, or analysis of other anterior segment images. The specific site detection unit 1030 can specify the midpoint of the detected corneal diameter using such analysis and set it as the center of the corneal diameter.

The specific site detection unit 1030 may be configured to, for example, specify the corneal diameter by the above method and obtain the iris diameter from the corneal diameter. In this case, for example, a line segment located inside the corneal diameter by a predetermined distance (eg, 0.5 to 1.0 mm) is defined as the iris diameter.

A typical specific site detection unit 1030 includes an imaging unit (optical system, imaging device, camera, etc.) that images the anterior segment, and a processor that analyzes the image obtained by the imaging unit. Furthermore, the specific site detection unit 1030 may include a projection unit that projects a light beam for forming a Purkinje image or a keratling image. The processor operates, for example, according to known analysis software (program) for detecting specific sites.

The evaluation unit 1040 evaluates the wearing state of the ortho-K lens on the eye based on the corneal shape data acquired by the corneal shape measurement unit 1020 and the design data 1015 read from the storage unit 1010 . The evaluation unit 1040 performs evaluation by comparing the corneal shape data and the design data 1015, for example. For example, the comparison includes a process of determining the difference between the value indicated by the corneal shape data and the value indicated by the design data, and the evaluation result is obtained by comparing this difference with a predetermined threshold value. Here, "difference" can be any quantity that represents the difference between two values, typically the value obtained by subtracting one value from the other, the absolute value of this subtraction, Or it may be a ratio of two values.

In some examples, the corneal topography component 1020 generates corneal topography data by determining values of predetermined shape parameters for each of a plurality of locations on the cornea of the eye, as described above. In this case, the evaluation unit 1040 calculates two or more values included in the corneal shape data corresponding to two or more of the plurality of positions and two or more values included in the design data 1050 corresponding to the two or more positions. An evaluation can be performed by comparing with the design value of . In other words, the evaluation unit 1040 calculates two or more measurement values corresponding to two or more positions among the plurality of positions of the cornea to which the shape parameter measurement is applied, and a plurality of measurement values corresponding to the plurality of positions included in the design data 1015. with two or more design values corresponding to the two or more positions, and based on the results obtained, generating an evaluation result of the wearing state of the ortho-K lens for the eye. can be done.

The two or more positions of the cornea to be compared may be arbitrary. For example, two or more positions are symmetrically arranged with respect to a specific region of the eye, and this specific region is detected by the specific region detector 1030 after removing the orthokeratology lens. In this case, the evaluation unit 1040 compares the corresponding two or more measured values with the corresponding two or more design values for two or more positions symmetrical with respect to the detected specific part, and obtains evaluation results based on the results. It is possible to

The specific part of the eye detected by the specific part detection unit 1030 may be the corneal vertex of the eye after removing the ortho-K lens. In this case, the evaluation unit 1040, for example, for a pair of positions (two positions) having a point-symmetrical relationship with respect to the corneal vertex of the eye after removing the ortho-K lens, obtains two measurement values corresponding to the pair of positions. and two design values corresponding to the pair of positions.

Since a typical ortho-K lens has a symmetrical shape with respect to the lens center, two design values corresponding to a pair of positions having a point-symmetrical positional relationship are equal to each other. Therefore, when the ortho-K lens is properly worn, the two measured values corresponding to a pair of positions having a point-symmetrical positional relationship with respect to the corneal vertex after removing the ortho-K lens are almost equal to each other. , and approximately equal to the two corresponding design values.

In view of such consideration, the evaluation unit 1040 may be configured to calculate a difference (first difference) calculated from such two measured values and two design values. The first difference may be, for example, a value obtained by subtracting one of the two design values from one of the two measured values, the absolute value of the subtracted value, or the ratio of these two values. Evaluator 1040 may perform an evaluation based on the calculated first difference. For example, this evaluation includes a process of determining whether the first difference exceeds a predetermined threshold, and if the first difference exceeds the predetermined threshold, the evaluation that the wearing state of the ortho-K lens was inappropriate. A result is obtained, and if the first difference is equal to or less than the predetermined threshold value, an evaluation result is obtained that the wearing state of the ortho-K lens is appropriate. In an ideal situation, the measured value and the set value corresponding to the same position on the cornea would be equal, so the value obtained by subtracting one of the two design values from one of the two measured values would be zero. and the ratio of these two values is 1.

Also in view of the above considerations, the evaluation unit 1040 may be configured to calculate a difference between the two measurements (a second difference) and perform an evaluation based on this second difference. The second difference may be, for example, a value obtained by subtracting one of the two measurements from the other, an absolute value of the subtracted value, or a ratio of these two measurements. Evaluator 1040 may perform an evaluation based on the calculated second difference. For example, this evaluation includes a process of determining whether or not the second difference exceeds a predetermined threshold, and if the second difference exceeds the predetermined threshold, an evaluation that the wearing state of the Ortho-K lens was inappropriate. A result is obtained, and if the second difference is equal to or less than the predetermined threshold value, an evaluation result is obtained that the wearing state of the ortho-K lens is appropriate. In an ideal situation, a pair of measured values corresponding to a pair of positions having a point-symmetrical positional relationship with respect to the corneal vertex are equal to each other. The value will be 0 and the ratio of the pair of measurements will be 1.

The specific part of the eye detected by the specific part detection unit 1030 may be the center of the pupil of the eye after the ortho-K lens is removed. In this example, it is assumed that the corneal vertex and the center of the pupil are arranged at substantially the same position in the direction orthogonal to the eye axis. In other words, this example assumes that the eccentricity between the cornea and the pupil is sufficiently small. Under this assumption, the evaluation unit 1040, for example, selects a pair of positions having a point-symmetrical relationship with respect to the center of the pupil of the eye after removal of the ortho-K lens (corresponding position on the cornea (approximate position of the corneal vertex)). For (two positions), two measured values corresponding to the pair of positions are compared with two design values corresponding to the pair of positions.

In this case, in view of the consideration described above, the evaluation unit 1040 calculates a difference (first difference) calculated from such two measured values and two design values, and the calculated first difference may be configured to perform the evaluation based on The evaluation unit 1040 may also be configured to calculate a difference (second difference) between the two measured values and perform evaluation based on the calculated second difference.

The specific part of the eye detected by the specific part detection unit 1030 may be the center of the iris diameter of the eye after the ortho-K lens is removed. In this example, it is assumed that the corneal vertex and the center of the iris diameter are arranged at substantially the same position in the direction orthogonal to the eye axis. In other words, this example assumes that the eccentricity between the cornea and the iris is sufficiently small. Under this assumption, the evaluation unit 1040 has a point-symmetrical relationship with respect to, for example, the center of the iris diameter of the eye after removal of the ortho-K lens (corresponding position on the cornea (approximate position of the corneal vertex)). (two positions), two measured values corresponding to the pair of positions are compared with two design values corresponding to the pair of positions.

In this case, in view of the consideration described above, the evaluation unit 1040 calculates a difference (first difference) calculated from such two measured values and two design values, and the calculated first difference may be configured to perform the evaluation based on The evaluation unit 1040 may also be configured to calculate a difference (second difference) between the two measured values and perform evaluation based on the calculated second difference.

The specific part of the eye detected by the specific part detection unit 1030 may be the center of the corneal diameter of the eye after removing the Ortho-K lens. In this example, it is assumed that the deviation between the corneal vertex and the corneal center is sufficiently small. Under this assumption, the evaluation unit 1040 evaluates, for example, a pair of positions (two positions) having a point-symmetrical relationship with respect to the center of the corneal diameter of the eye after removing the ortho-K lens (approximate position of the corneal vertex), Two measured values corresponding to the pair of positions are compared with two design values also corresponding to the pair of positions.

In this case, in view of the consideration described above, the evaluation unit 1040 calculates a difference (first difference) calculated from such two measured values and two design values, and the calculated first difference may be configured to perform the evaluation based on The evaluation unit 1040 may also be configured to calculate a difference (second difference) between the two measured values and perform evaluation based on the calculated second difference.

An exemplary evaluation unit 1040 includes a processor that performs an evaluation of the ortho-K lens fit based on specific sites and feature points. The processor operates according to evaluation software (program) for performing the evaluation. The analysis software includes, for example, software for calculating the deviation between the specific site and the feature point, and software for performing evaluation based on the calculated deviation and predetermined evaluation criteria (evaluation protocol). .

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

Although illustration is omitted, the ophthalmologic apparatus 1000 may further include a display device, an operation device, a communication device, and the like.

The operation of the ophthalmologic apparatus 1000 according to this aspect will be described. An example of the operation of the ophthalmologic apparatus 1000 is shown in FIG. Software for realizing the operation example shown in FIG. The ophthalmologic apparatus 1000 executes a series of processes shown in FIG. 2 by operating according to this software. It is assumed that the process of storing the design data 1015 in the storage unit 1010 has already been performed.

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

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

(S3: Detect a specific part of the eye)
Specific part detection section 1030 detects a specific part of the eye. The particular region of the eye is typically the corneal apex, the center of the pupil, the center of the iris diameter, or the center of the corneal diameter. Thereby, the position data of the specific part of the eye is obtained.

(S4: Measuring the corneal shape of the eye)
The corneal shape measurement unit 1020 measures the corneal shape of the eye. Corneal shape data is typically corneal curvature distribution data, corneal curvature radius distribution data, or height distribution data. Thereby, corneal shape data of the eye is obtained.

(S5: Compare corneal shape data and design data)
The evaluation unit 1040 obtains a position (referred to as a specific position) in the corneal shape data obtained in step S4 that corresponds to the specific site detected in step S3. This specific position is typically a position corresponding to the corneal vertex, a position corresponding to the center of the pupil, a position corresponding to the center of the iris diameter, or a position corresponding to the center of the corneal diameter.

Next, the evaluation unit 1040 selects two of the plurality of measured values included in the corneal shape data acquired in step S4 that have a symmetrical positional relationship with respect to the specific position corresponding to the specific region detected in step S3. Select two (or more) measurements corresponding to (or more) locations.

In addition, the evaluation unit 1040 selects two design values having a symmetrical positional relationship with respect to the specific position corresponding to the specific part detected in step S3 from among the plurality of design values included in the design data 1015 stored in the storage unit 1010. Select two (or more) design values corresponding to one (or more) locations.

Here, typically the two (or more) positions corresponding to the two (or more) selected measured values are the two (or more) positions corresponding to the two (or more) selected design values. is the same as the position of Since the shape of a typical Ortho-K lens is point-symmetrical (rotationally symmetrical) with respect to the center of the lens, two For the (or more) locations, two (or more) corresponding measured values and two (or more) corresponding design values may be selected.

The evaluation unit 1040 compares the selected two (or more) measured values with the selected two (or more) design values. For example, the evaluation unit 1040 calculates one or both of the first difference and the second difference described above.

(S6: Evaluate the mounting state of the Ortho K lens)
The evaluation unit 1040 evaluates the wearing state of the ortho-K lens on the eye based on the result of the comparison performed in step S5 (eg, based on one or both of the first difference and the second difference). to run.

The control unit 1050 can output, save, or record the results of the evaluation performed in step S6. For example, the control unit 1050 controls a display device to display evaluation results, or controls a communication device to transmit evaluation results to another device (for example, a medical information management device such as an electronic medical record system). , saving the evaluation results in a storage device provided in the ophthalmologic apparatus 1000, controlling a printer to print the evaluation results on a paper medium, or controlling a drive device or the like to write the evaluation results to a recording medium. It is possible to

The order of the steps shown in FIG. 2 can be arbitrarily changed. For example, corneal topography measurements can be performed prior to site-specific detection.

<Second Aspect>
An ophthalmologic apparatus according to a second aspect will be described. In this aspect, when the prescription of the ortho-K lens is appropriate, the corneal shape is corrected according to the design of this ortho-K lens, and the corneal shape is substantially symmetrical about the lens center (for example, substantially symmetrical curvature distribution, substantially symmetrical curvature radius distribution, substantially symmetrical height distribution).

It is also assumed in this embodiment that the eye has no astigmatism and that the shape (asphericity) of the cornea deformed by the Ortho-K lens is isotropic. Here, the absence of astigmatism in the eye means, for example, that the measured value of the degree of astigmatism of the eye is equal to or less than a predetermined threshold value, and this aspect can be applied to such eyes.

For astigmatic eyes, for example, two positions (a pair of positions) described in the first embodiment are set on the meridian in the astigmatic axis direction, or set on the meridian perpendicular to the astigmatic axis direction. By doing so, it is possible to make a similar evaluation.

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

Examples of measurable eye properties are refractive power and corneal shape. Examples of refractive power parameters include spherical power, cylinder power, cylinder axis angle, and the like. Examples of corneal shape parameters include corneal curvature and corneal curvature radius. The corneal shape is typically represented by a corneal curvature distribution or a corneal curvature radius 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 are equivalent parameters.

Any type of OCT is applicable to this aspect. Although swept-source OCT is applied in this embodiment, it may be spectral-domain OCT or other types. Here, the swept source OCT splits the light from the wavelength tunable light source into measurement light and reference light, generates interference light by superimposing the return light of the measurement light from the object on the reference light, and generates interference light. In this method, light is detected by a photodetector, and an image is constructed by applying Fourier transform or the like to the detection data collected in response to wavelength sweeping and measurement light scanning. On the other hand, spectral domain OCT divides light from a low coherence light source (broadband light source) into measurement light and reference light, and generates interference light by superimposing the return light of the measurement light from the object on the reference light. , the spectrum distribution of this interference light is detected by a spectroscope, and the detected spectrum distribution is subjected to Fourier transform or the like to construct an image. That is, the swept-source OCT is an OCT technique that acquires the spectral distribution of interference light by time division, and the spectral domain OCT is an OCT technique that acquires the spectral distribution of interference light by space division.

The ophthalmic device may have other objective measurement functions and may have subjective examination functions. Subjective testing is a measurement method that acquires information using responses from the subject. and so on. Objective measurement is a measurement technique that acquires eye data mainly using physical techniques without referring to responses from the subject. Objective measurement includes measurement for acquiring eye characteristic data and photographing for acquiring eye image data. Objective measurements include intraocular pressure measurement, anterior segment imaging, fundus imaging, OCT, and the like, in addition to the above-described refractive power measurement and corneal shape measurement.

In this aspect, unless otherwise specified, the conjugate relationship between the part of the eye and the position within the optical system means the mutual positional relationship in a state of suitable alignment. For example, the fundus conjugate position in the optical system is a position that is approximately optically conjugate with the fundus when alignment is favorable, and means a position that is optically conjugate with the fundus or its vicinity. Also, the pupil conjugate position is a position that is substantially optically conjugate with the pupil in a state of good alignment, and means a position that is optically conjugate with the pupil or its vicinity.

Hereinafter, the direction along the optical axis of the optical system of the ophthalmologic apparatus 2000 will be referred to as the Z direction. In addition, a first coordinate axis (for example, a horizontal coordinate axis) and a second coordinate axis (for example, a vertical direction) of a two-dimensional orthogonal coordinate system (XY coordinate system) defining a plane (XY plane) orthogonal to this 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.

Now, the ophthalmologic apparatus 2000 shown in FIG. , and OCT optics 8 . In the following description, for example, the anterior ocular segment observation system 5 uses light of 940 nm to 1000 nm, the reflector measurement optical system (ref measurement projection system 6, reflector measurement light receiving system 7) uses light of 830 nm to 880 nm, and the fixation projection system 4 uses light of 400 nm to 700 nm, and the OCT optical system 8 uses light of 1000 nm to 1100 nm.

The anterior segment observation system 5 captures the anterior segment of the eye E as a moving image. In the optical system passing through the anterior segment observation system 5, the imaging surface of the imaging 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 a hole formed in the diaphragm (telecentric diaphragm) 53, passes through the half mirror 23, It passes through relay lenses 55 and 56 and through dichroic mirror 76 . A dichroic mirror 52 couples the optical path of the reflex measurement optical system and the optical path of the anterior eye observation system 5 . The dichroic mirror 52 is arranged such that the optical path coupling surface where 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 imaging surface of the imaging element 59 (area sensor) by the imaging lens 58 . The imaging device 59 performs imaging and signal output at a predetermined rate. The output (video signal) of the imaging device 59 is input to the computer 9, which will be described later. The computer 9 causes the display screen 10a of the display unit 10 to display the anterior segment image E' based on this video signal. The anterior segment image E' is, for example, an infrared moving image.

The Z alignment system 1 projects light (infrared light) onto the eye E for alignment in the optical axis direction (front-rear direction, Z direction) of the anterior segment observation system 5 . 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 cornea Cr (corneal vertex) 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 vertex of the eye E based on the light projection position on the sensor surface of the line sensor 13, and based on this, controls the mechanism for moving the optical system 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 any image sensor in which a plurality of photodetection elements (photodiodes, etc.) are arranged one-dimensionally or two-dimensionally.

The XY alignment system 2 directs a light beam (infrared light) to the eye E for alignment in the directions perpendicular to the optical axis of the anterior eye observation system 5 (horizontal direction (X direction) and 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 eye observation system 5 by a half mirror 23 . 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 eye observation system 5 . Reflected light from the cornea Cr of the eye E is guided to the imaging element 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 causes the display screen 10a of the display unit 10 to display the anterior segment image E' including the bright spot image Br and the alignment mark AL. When manually performing the XY alignment, the user moves the optical system so as to guide the bright spot image Br into the alignment mark AL. When performing automatic alignment, the computer 9 controls the 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 keratometry system 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea Cr of the eye E onto the cornea Cr. The keratoplate 31 is arranged between the objective lens 51 and the eye E. A kerato ring light source 32 is provided on the back side of the kerato plate 31 (on the objective lens 51 side). By illuminating the kerat plate 31 with light from the keratizing light source 32, a ring-shaped light flux (arc-shaped or circumferential measurement pattern) is projected onto the cornea Cr of the eye E. FIG. Reflected light (keratling image) from the cornea Cr of the eye E is detected by the imaging device 59 together with the anterior segment image E′. The computer 9 calculates the value of the corneal shape parameter representing the shape of the cornea Cr by performing known calculations based on this keratling image. A typical corneal shape parameter is the corneal curvature radius (corneal curvature).

Instead of or in addition to the keratometry system 3, the ophthalmologic apparatus 2000 may include a corneal topography system (corneal topographer). The corneal topography system includes a group of elements for obtaining the corneal topogram described above (see, for example, Japanese Patent Application Laid-Open No. 8-280624). The corneal topography system projects multiple concentric circular patterns called placid rings onto the cornea Cr. Reflected light (Platido ring image) from the cornea Cr is detected by the imaging element 59 together with the anterior segment image E'. The computer 9 obtains the distribution of corneal shape parameters representing the shape of the cornea Cr by performing known calculations based on this placid ring image. A pseudocolor representation of the distribution data obtained provides a corneal topogram.

The ref measurement optical system includes a ref measurement projection system 6 and a ref measurement light receiving system 7 used for refractive power measurement. The ref measurement projection system 6 projects a light flux for refractive power measurement (for example, a ring-shaped light flux) onto the fundus oculi Ef. This luminous flux is typically infrared light. The ref measurement light-receiving system 7 detects the return light from the eye E of this luminous flux. The reflector measurement projection system 6 is provided on an optical path branched by a perforated prism 65 provided in the optical path of the reflector measurement light receiving system 7 . The aperture formed in the apertured prism 65 is arranged at the pupil conjugate position. In the optical system passing through the ref measurement light-receiving system 7, the imaging surface of the imaging element 59 is arranged at the fundus conjugate position.

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

The return light of the ring-shaped luminous flux projected onto the fundus oculi Ef passes through the objective lens 51 and is reflected by the dichroic mirrors 52 and 67 . The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the aperture of the perforated prism 65, passes through the relay lens 71, is reflected by the reflecting mirror 72, and passes through the relay lens 73 and the focusing lens. Pass 74. The focusing lens 74 is movable along the optical axis of the ref measurement light receiving system 7 . The light that has passed through the focusing lens 74 is reflected by the reflecting mirror 75 , reflected by the dichroic mirror 76 , and imaged on the imaging surface of the imaging element 59 by the imaging lens 58 . The computer 9 calculates the refractive power value of the eye E by performing known calculations based on the output from the imaging element 59 . For example, the power value includes at least one of spherical power, cylinder power and cylinder axis angle, and equivalent spherical power.

The OCT optical system 8 is provided in an optical path separated by a dichroic mirror 67 from the optical path of the reflex measurement optical system. A fixation projection system 4 is provided on an optical path branched from the optical path of the OCT optical system 8 by a dichroic mirror 83 .

A fixation projection system 4 presents the eye E with a fixation target. A fixation unit 40 is arranged in the optical path of the fixation projection system 4 . The fixation unit 40 can move along the optical path of the fixation projection system 4 under the control of the computer 9 which will be described later. 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 positions include the position for acquiring an image centered on the macula, the position for acquiring an image centered on the optic disc, and the center of the fundus between the macula and the optic disc. There is a position for acquiring 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 in which optotypes or the like are printed on a film or the like and an illumination light source for illuminating the optotype chart may be provided.

Light from the liquid crystal panel 41 passes through the relay lens 42 , dichroic mirror 83 , relay lens 82 , reflection mirror 81 , dichroic mirror 67 , and dichroic mirror 52 . . The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus oculi Ef. In some aspects, each of the liquid crystal panel 41 and the relay lens 42 is independently movable 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 surface of the optical fiber f1 is conjugated with the imaging site (fundus oculi Ef or anterior segment) based on the results of reflex measurement performed prior to OCT.

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

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 wavelength tunable light source capable of sweeping the wavelength of emitted light, like a general swept source type OCT apparatus. A tunable light source includes a laser light source including a resonator. The OCT light source 101 temporally changes the output wavelength in the near-infrared wavelength band invisible to the human eye. The OCT light source 101 includes, for example, a near-infrared 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 wavelength tunable light source into measurement light and reference light, and superimposing the return light of the measurement light from the eye E and the reference light that has passed through the reference light path to generate interference light. It has a function of generating and a function of detecting this interference light. A 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 . At least one of the length of the optical path of the measurement light (measurement arm, sample arm) and the length of the optical path of the reference light (reference arm) is variable.

The light L0 output from the OCT light source 101 is guided to the polarization controller 103 by the optical fiber 102, and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided by the optical fiber 104 to the fiber coupler 105 and split 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 and converted into a parallel beam, 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 and the optical path length of the measurement light LS. The dispersion compensation member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The corner cube 114 is movable in the incident direction of the reference light LR, thereby changing the optical path length of the reference light LR.

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

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

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

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

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

Detector 125 is, for example, a balanced photodiode. A balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between a pair of detection results obtained by these photodetectors. Detector 125 sends this output (detection signal) to data acquisition system (DAQ) 130 .

A clock KC is supplied from the OCT light source 101 to the DAQ 130 . 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 wavelength tunable light source. For example, the OCT light source 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then outputs the clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the computer 9 . The computer 9 forms a reflection intensity profile for each A-line, for example, by applying Fourier transform or the like to the spectral distribution based on the sampling data for each series of wavelength sweeps (for each A-line). Furthermore, the computer 9 forms image data by imaging the reflection intensity profile of each A-line.

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

The computer 9 calculates the refractive power value from the measurement results obtained using the reflector measurement optical system, and based on the calculated refractive power value, the fundus oculi Ef, the reflector measurement light source 61, and the imaging element 59 are conjugated. , the ref measurement light source 61 and the focusing lens 74 are moved in the optical axis direction. In some aspects, the computer 9 moves the focusing lens 87 of the OCT optical system 8 along its optical axis in conjunction with the movement of the focusing lens 74 . In some aspects, the computer 9 moves the liquid crystal panel 41 (fixation unit 40) along its optical axis in conjunction with the movement of the ref measurement light source 61 and the focusing lens 74. FIG. In addition to these, the computer 9 executes various controls, various data processing, various calculations, and the like.

The configuration of the processing system of the ophthalmologic apparatus 2000 will be described. An example of the functional configuration of the processing system of the ophthalmologic apparatus 2000 is shown in FIGS. 5 and 6. FIG. FIG. 5 shows an example of a functional block diagram of the processing system of the ophthalmologic apparatus 2000. As shown in FIG. FIG. 6 represents an example of a functional block diagram of the main elements for performing an assessment of the fit of the Ortho-K lens on the eye.

The computer 9 executes control of each part of the ophthalmologic apparatus 2000, various data processing, various calculations, and the like. Computer 9 includes one or more processors and one or more storage devices. Storage devices include, for example, hard disk drives, RAMs, ROMs, semiconductor memories, and the like.

The storage device stores various programs (software) such as one or more control programs, one or more data processing programs, and one or more arithmetic programs. The computer 9 executes control, data processing, calculation, etc. by any processor operating according to any program. That is, the computer 9 executes control, data processing, calculation, and the like through cooperation between hardware such as a processor and software.

The computer 9 includes a control section 210 and an arithmetic processing section 220 . The ophthalmologic apparatus 2000 also includes a moving mechanism 200 , a display section 270 , an operation section 280 and a communication section 290 .

The moving mechanism 200 is a mechanism for moving the head portion of the ophthalmologic apparatus 2000 in the front-rear and left-right directions. The head unit includes a Z alignment system 1, an XY alignment system 2, a keratometry system 3, a fixation projection system 4, an anterior eye observation system 5, a reflector measurement projection system 6, a reflector measurement light receiving system 7, and an OCT optical system. 8 (at least a group of elements excluding the OCT unit 100), etc. are accommodated. For example, the moving mechanism 200 is provided with an actuator that generates driving force for moving the head section and a transmission mechanism that transmits this driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is configured by, for example, a combination of gears, a rack and pinion, or the like. The control unit 210 (main control unit 211) controls the movement mechanism 200 by sending control signals to the actuators.

The control unit 210 includes one or more processors and controls each unit of the ophthalmologic apparatus 2000 . Control unit 210 includes a main control unit 211 and a storage unit 212 . A program group for controlling the ophthalmologic apparatus 2000 is stored in advance in the storage unit 212 . 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 ophthalmologic apparatus 2000 performs calculations and controls according to such programs.

A main control unit 211 performs various controls of the ophthalmologic apparatus 2000 . Control of the Z alignment system 1 includes control of the Z alignment light source 11, control of the line sensor 13, and the like. The control of the Z alignment light source 11 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. 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, or the amount of light is changed. The main control unit 211 captures the signal detected by the line sensor 13 and identifies the projection position of the light on the line sensor 13 based on the captured signal. The main control unit 211 obtains the position of the corneal vertex of the eye E based on the specified projection position, and based on this, controls the movement mechanism 200 to move the head unit in the front-rear direction (Z alignment).

Control of the XY alignment system 2 includes control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the XY alignment light source 21 are switched, or the amount of light is changed. The main control unit 211 captures the signal detected by the imaging element 59 and identifies the position of the bright spot image based on the return 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), and moves the head unit in the left, right, up and down directions. (XY alignment).

Control of the keratometry system 3 includes control of the keratometry light source 32 and the like. The control of the keratling light source 32 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the keratling light source 32 are switched, or the amount of light is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform known arithmetic operations on the keratling image detected by the imaging device 59 . Thereby, the value of the corneal shape parameter of the eye E is obtained. The main controller 211 performs similar processing when the corneal topography system described above is provided.

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

The control of the anterior segment observation system 5 includes control of the anterior segment illumination light source 50, control of the imaging element 59, and the like. The control of the anterior ocular segment illumination light source 50 includes turning on/off the light source, light amount adjustment, aperture adjustment, and the like. As a result, the lighting and non-lighting of the anterior segment illumination light source 50 is switched, or the amount of light is changed. Control of the imaging element 59 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the imaging element 59 . The main control unit 211 captures the signals detected by the imaging device 59 and causes the arithmetic processing unit 220 to execute processing such as formation of an image based on the captured signals.

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

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

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

The control of the focusing lens 87 includes movement control of the focusing lens 87 in the optical axis direction, movement control of the focusing lens 87 to the focus reference position corresponding to the imaging part, movement range (focusing) corresponding to the imaging part. 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, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator to move the focusing lens 87 in the optical axis direction. In some aspects, the ophthalmic device 2000 is provided with a retaining member that retains the focusing lenses 74 and 87 and a drive that drives the retaining member. The main control section 211 performs movement control of the focusing lenses 74 and 87 by controlling the driving section. 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 of the corner cube 114 along the optical path. For example, the OCT optical system 8 includes a movement mechanism that moves the corner cube 114 along the optical path. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the corner cube 114 and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending control signals to the actuators to move the corner cube 114 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 perform processing such as image construction based on the sampled signal.

The main control unit 211 also controls the refractive power measurement value calculated by the eye refractive power calculation unit 221, the tomographic image (OCT image) formed by the image forming unit 222, and the results obtained by the data processing unit 223, which will be described later. is displayed on the display unit 270.

The storage unit 212 stores various data. Examples of data stored in the storage unit 212 include data obtained by objective measurement, data obtained by OCT scanning, image data of a tomographic image, image data of an anterior segment image, and data supplied to the data processing unit 230. data, data generated by the data processing unit 230, eye information to be examined, and the like. The eye information to be inspected includes information related to the eye to be inspected, such as left eye/right eye identification information. Further, the storage unit 212 stores in advance the design data 2121 of the ortho-K lens. Design data 2121 is an example of design data 1015 of the first aspect.

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 calculator 221 calculates a ring image (pattern image ). For example, the eye refractive power calculation unit 221 obtains the barycentric position of the ring image from the luminance distribution in the obtained image in which the ring image is drawn, and obtains the luminance distribution along a plurality of scanning directions radially extending from this barycentric position. , the ring image is specified from this luminance distribution. Subsequently, the eye refractive power calculation unit 221 obtains an approximate ellipse of the specified ring image, and substitutes the major axis and minor axis of the approximate ellipse into a known formula to obtain the spherical power, the cylinder power, and the cylinder axis angle (refraction strength value). Alternatively, the eye refractive power calculator 221 can obtain parameters of the eye refractive power based on the deformation and displacement of the ring image with respect to the reference pattern.

The eye refractive power calculator 221 also calculates the corneal curvature radius (corneal curvature) based on the keratling image acquired by the anterior eye observation system 5 . For example, the eye refractive power calculator 221 calculates the radius of curvature of the strong principal meridian and the radius of curvature of the weak principal meridian of the corneal anterior surface by analyzing the keratling image, and applies statistical processing to these curvature radii to Calculate the radius of curvature. This statistical treatment may be, for example, averaging, selecting the maximum value, or selecting the minimum value. The eye refractive power calculator 221 can calculate the corneal refractive power, the corneal astigmatic degree, and the corneal astigmatic axis angle based on the calculated corneal curvature radius.

The method for obtaining the corneal curvature radius is not limited to the method using keratling. For example, in addition to the method using the corneal topography system (platyd ring) described above, any corneal shape analysis method such as a method using a slit scan, a method using a Scheimpflug camera, a method using an anterior segment OCT, etc. is applied. Is possible. The eye refractive 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 image data of a tomographic image of the eye E (fundus Ef, anterior segment, etc.) based on the output from the OCT optical system 8 (DAQ 130). This imaging process includes filtering, fast Fourier transform (FFT), etc., as well as conventional (swept-source) OCT. Through such processing, a reflection intensity profile in the A-line (scanning path of the measurement light LS in the eye E) is acquired, and by imaging this reflection intensity profile, image data of the A-line (A-scan data) is formed. be done.

Furthermore, the image forming unit 222 forms a plurality of A-scan data according to the OCT scan (deflection of the measurement light LS, movement of the A-scan position) mode, and arranges the A-scan data to form two-dimensional image data or 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 the tomographic image data. can do. Further, the imager 222 can render stack data or volume data. Any rendering method may be used, and may be, for example, volume rendering, multiplanar reconstruction (MPR), surface rendering, or the like. Also, the image forming unit 222 can construct a planar image (for example, a front image) from stack data or volume data. For example, the image forming section 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 data (OCT data) acquired using an OCT scan. OCT data are, for example, reflection intensity profiles 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 processor 223 can apply segmentation to stack data or volume data. Segmentation is a known process for identifying subregions in image data. The data processing unit 223 performs segmentation based on the luminance values of OCT images (two-dimensional tomograms, three-dimensional images, etc.). For example, multiple layers of tissue in the fundus oculi Ef each have a characteristic reflectance, and the image regions of these layers also have characteristic luminance values. The data processing unit 223 performs segmentation so as to identify a target image region based on these characteristic luminance values. The image area of interest is, for example, the inner limiting membrane, the nerve fiber layer, the ganglion cell layer, the inner reticular layer, the inner nuclear layer, the outer reticular layer, the outer nuclear layer, the outer limiting membrane, the photoreceptor layer, the retinal pigment epithelial layer, It corresponds to any tissue of the fundus oculi Ef such as choroid and sclera.

As shown in FIG. 6, the data processing section 223 includes an evaluation section 2231 . As described above, the eye refractive power calculation unit 221 functions as a part (analysis unit) of the corneal shape measurement unit 1020 .

In this aspect, the anterior segment observation system 5 acquires an image (captured image) by photographing the eye E after the ortho-K lens is removed. The captured image is provided to the eye refractive power calculator 221 (analyzer) in order to measure the corneal shape of the eye E. FIG. As described above, the eye refractive power calculator 221 calculates corneal shape data (typically, corneal curvature distribution data, corneal curvature radius distribution data, or height distribution data) that is data measured by keratometry or corneal topography. Generate. The eye refractive power calculation unit 221 (analysis unit) is configured to execute data processing similar to that of the corneal topography measurement unit 1020 of the first aspect. The anterior segment observation system 5 and the eye refractive power calculation unit 221 (analysis unit) of this aspect function as the corneal shape measurement unit 1020 of the first aspect. When generating corneal shape data from an anterior segment OCT image, the OCT optical system 8, the image forming unit 222, and the eye refractive power calculating unit 221 (analyzing unit) are the corneal shape measuring unit of the first aspect. 1020 functions.

The evaluation unit 2231 evaluates the wearing state of the ortho-K lens for the eye E based on the corneal shape data acquired by the eye refractive power calculation unit 221 and the design data 2121 stored in the storage unit 212. do. The evaluation unit 2231 functions as the evaluation unit 1040 of the first aspect and is configured to perform data processing similar to this.

The operation of the ophthalmologic apparatus 2000 according to this aspect will be described. An example of the operation of the ophthalmologic apparatus 2000 is shown in FIG. Software for realizing the operation example shown in FIG. The ophthalmologic apparatus 2000 executes a series of processes shown in FIG. 7 by operating according to this software. It is assumed that the process of storing the design data 2121 in the storage unit 212 has already been performed.

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

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

(S13: Start projecting pattern light onto the cornea)
Next, the ophthalmologic apparatus 2000 projects pattern light onto the cornea of the eye E using the keratometry system 3 or the corneal topography system. Projection of pattern light continues at least until an anterior segment image is acquired.

(S14: Capture the anterior segment image)
Next, the ophthalmologic apparatus 2000 acquires an anterior segment image of the eye E in which pattern light is projected onto the cornea. Typically, the ophthalmologic apparatus 2000 starts capturing moving images of the anterior segment by the anterior segment observation system 5 in step S12, and captures frames obtained after step S13.

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

(S15: Detect corneal vertex)
The data processing unit 223 analyzes the anterior segment image acquired in step S14 to detect the corneal vertex. Thereby, the position data of the corneal vertex of the eye E after removing the ortho-K lens is obtained. That is, position data of the corneal vertex of the eye E whose cornea has been deformed by the ortho-K lens is obtained.

When the image of the luminous flux from the XY alignment system 2 (bright point image, Purkinje image) is rendered in the anterior segment image, the data processing unit 223 converts the X coordinate and Y coordinate of this bright point image to the corneal vertex. It can be obtained as dimensional position data. Further, when the image of the light flux from the XY alignment system 2 is drawn in the anterior segment image, and the stereo imaging described in the first aspect is possible, the data processing unit 223 performs The three-dimensional position data of the corneal vertex can be obtained from the two bright spot images respectively drawn on the two anterior segment images photographed from the . On the other hand, when the image of the light flux from the XY alignment system 2 is not rendered in the anterior segment image, the data processing unit 223, for example, calculates The center of the ring image with the smallest diameter can be obtained as two-dimensional position data of the corneal vertex.

(S16: Generate eye corneal shape data)
The eye refractive power calculator 221 (analyzer) analyzes the anterior segment image acquired in step S14 to generate corneal shape data (eg, corneal curvature distribution data or corneal curvature radius distribution data). Further, the eye refractive power calculator 221 (analyzer) may generate height distribution data obtained by integrating the corneal curvature distribution data twice as the corneal shape data. The height distribution data is, for example, data representing relative heights with reference to a predetermined position (for example, corneal vertex position).

(S17: Compare corneal shape data and design data)
The evaluation unit 2231 compares the corneal shape data generated in step S<b>16 with the design data 2121 read from the storage unit 212 . This comparison is performed, for example, in the same manner as step S5 of the first aspect.

(S18: Calculate the first difference and the second difference)
The evaluation unit 2231 calculates a first difference based on the two (or more) measured values and the two (or more) design values by comparing the corneal shape data and the design data 2121 in step S17, and A second difference based on one (or more) measurements is calculated.

Note that either one of the first difference and the second difference may be calculated, or another calculated value may be obtained.

(S19: First difference>threshold?, Second difference>threshold?)
The evaluation unit 2231 compares the first difference calculated in step S18 with a default threshold, and compares the second difference with a default threshold. For example, if it is determined that one or both of the first difference and the second difference exceed the threshold (S19: Yes), the process proceeds to step S20. On the other hand, if it is determined that both the first difference and the second difference are equal to or less than the threshold (S19: No), the processing of this operation example ends (end).

(S20: Review the prescription of the Ortho K lens)
If it is determined that one or both of the first difference and the second difference exceed the threshold (S19: Yes), the user (doctor, etc.) 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 fits the eye E better.

In step S20 (review of the prescription of the ortho K lens), for example, various parameters of the ortho K lens are reviewed, optimum values are searched, and simulations are performed. The parameters of the Ortho-K lens include the diameter of the entire lens, the diameter of the base curve at the center of the lens, the chord dimensions of the optical zone (treatment zone), the width and depth of the transition zone (return zone), and the peripheral zone. (Landing zone) diameter, angle, width, end width, refractive power, etc.

As in the first aspect, the ophthalmologic apparatus 2000 can output, save, and record the results of the evaluation performed in step S19 and the results of prescription review performed in step S20. Also, the order of the steps shown in FIG. 7 can be arbitrarily changed.

In addition, in this operation example, the corneal vertex is detected in step S15, but as described in the first aspect, the specific part of the eye is not limited to the corneal vertex, and the pupil center, iris diameter center, corneal It may be the center of the diameter or the like. Even when a specific part other than the corneal vertex is adopted, it is possible to perform the same processing as in this operation example.

<effect>
Some advantages of the ophthalmic apparatus according to the exemplary aspects described above will now be described.

An ophthalmic device according to an exemplary embodiment includes a storage unit, a corneal topography measurement unit, and an evaluation unit. For example, the ophthalmologic apparatus 1000 includes a storage unit 1010 , a corneal shape measurement unit 1020 and an evaluation unit 1040 . The ophthalmologic apparatus 2000 also includes a storage unit 212 , a corneal shape measurement unit including the anterior eye observation system 5 and an eye refractive power calculation unit 221 (analysis unit), and an evaluation unit 2231 .

The storage unit stores in advance the design data of the ortho-K lens. The corneal shape measuring unit measures the corneal shape of the eye after removing the ortho-K lens. The evaluation unit evaluates the wearing state of the ortho-K lens for the eye based on the corneal shape data and the design data acquired by the corneal shape measurement unit.

According to such an exemplary aspect, it is possible to automatically determine whether or not the mounting position of the ortho-K lens is appropriate. Therefore, it is not possible to determine the refraction state of the peripheral vision (that is, whether or not the Ortho-K lens was worn at the appropriate position at night) and to actually obtain the expected refractive correction effect. It is possible to provide users (doctors, etc.) with information for determining whether or not they are

In the ophthalmic apparatus according to exemplary aspects, the corneal topography measurement unit may be configured to generate corneal topography data by determining values of predetermined shape parameters for each of a plurality of locations on the cornea of the eye. Furthermore, the evaluation unit determines two or more values (two or more measured values) included in the corneal shape data corresponding to two or more of the plurality of positions and the design data corresponding to the two or more positions. It may be configured to perform an assessment of the fit of the Ortho-K lens on the eye by comparing two or more included design values. According to such a configuration, it is possible to appropriately determine the appropriateness of the mounting position of the ortho-K lens based on the shape measurement values at a plurality of positions of the cornea.

An ophthalmic device according to an exemplary embodiment may further include a specific site detector that detects a specific site of the eye after removal of the Ortho-K lens. For example, in the ophthalmologic apparatus 1000, the specific site detection unit 1030 detects the specific site, and in the ophthalmologic apparatus 2000, the data processing unit 223 detects the specific site. The specific site may be, for example, any one of the corneal vertex, the center of the pupil, the center of the iris diameter, and the center of the corneal diameter. Furthermore, the evaluation unit compares two or more measured values corresponding to two or more positions symmetrical with respect to the detected specific region and two or more design values, thereby determining the wearing state of the ortho-K lens for the eye. It may be configured to perform an evaluation. According to such a configuration, it is possible to determine the appropriateness of the mounting position of the ortho-K lens by utilizing the symmetry of the shape of a typical ortho-K lens.

In the ophthalmologic apparatus according to the exemplary aspect, the evaluation unit calculates a first difference that is a difference calculated from the two or more measured values and the two or more design values, and based on the first difference It may be configured to perform an assessment of the fit of the ortho-K lens on the eye. With such a configuration, it is possible to determine whether or not the ortho-K lens mounting position is appropriate based on the difference between the measured value of the corneal shape after removing the ortho-K lens and the design value of the ortho-K lens. is.

In the ophthalmologic apparatus according to the exemplary aspect, the evaluation unit calculates a second difference that is a difference calculated from the two or more measured values, and estimates the ortho-K lens for the eye based on the second difference. It may be configured to perform a wearing state assessment. According to such a configuration, it is possible to determine the appropriateness of the mounting position of the ortho-K lens based on the difference between the measured values of the corneal shape after the ortho-K lens is removed.

Example aspects can provide a method of controlling an ophthalmic device that includes an imager for imaging an eye, a memory, and a processor. For example, the ophthalmologic apparatus 1000 includes an imaging unit (optical system, imaging device, camera, etc.) for imaging the anterior segment, a storage unit 1010, and (one or more) processors. The ophthalmologic apparatus 2000 also includes an anterior segment observation system 5 functioning as an imaging system, a storage unit 212, and a computer having a processor.

A control method according to an exemplary aspect controls a processor to store design data of an ortho-K lens in a storage unit in a first control step. In a second control step, the imaging unit is controlled to acquire a captured image of the eye after removing the ortho-K lens. In a third control step, controlling the processor to analyze the captured image to obtain corneal shape data for the eye. A fourth control step controls the processor to perform an assessment of the fit of the orthokeratology lens on the eye based on the corneal shape data and the design data.

Any of the matters described with respect to the ophthalmic device according to the exemplary embodiment can be combined with such a method of controlling the ophthalmic device.

A program can be provided that causes an ophthalmologic apparatus including a computer to execute the control method according to the exemplary embodiment. Any of the items described with respect to the ophthalmic apparatus according to the exemplary embodiment can be combined with this program.

It is possible to create a computer-readable non-transitory recording medium recording such a program. Any of the items described with respect to the ophthalmic device according to the exemplary embodiment can be combined with this recording medium. This non-transitory recording medium may be in any form, examples of which include magnetic disks, optical disks, magneto-optical disks, and semiconductor memories.

According to the control method, program, or recording medium according to the exemplary aspects, it is possible to cause the ophthalmologic apparatus to determine whether the mounting position of the ortho-K lens is appropriate. As a result, we can actually obtain information for determining how the refraction state of the peripheral vision is (that is, whether or not the Ortho-K lens was worn at the appropriate position at night) and the expected refractive correction effect. It is possible to directly or indirectly provide the user (doctor, etc.) with information for determining whether or not the ophthalmologic apparatus is being used.

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

The ophthalmologic information processing apparatus according to the exemplary embodiment may be, for example, a personal computer, a server provided on a local area network (LAN), a server (such as a cloud server) provided on a wide area network (WAN), or other may include a computer in the form of

FIG. 8 shows the configuration of an ophthalmologic information processing apparatus according to an exemplary embodiment. The ophthalmologic information processing apparatus 3000 includes a storage unit 3010 , an image reception unit 3020 , an analysis unit 3030 , an evaluation unit 3040 and a control unit 3050 .

The storage unit 3010 stores design data 3015 of the ortho-K lens in advance. The design data 3015 may be data similar to the design data 1015 in the first aspect. Storage unit 3010 includes, for example, a hard disk drive, RAM, ROM, semiconductor memory, and the like.

The image reception unit 3020 receives an image obtained by photographing the eye with another ophthalmologic apparatus. Image reception unit 3020 includes, for example, either a communication device or a drive device.

The communication device of the image reception unit 3020 receives, for example, captured images from other ophthalmologic apparatuses via the network. Alternatively, the communication device of the image reception unit 3020 receives captured images stored in an image archiving system or the like from another ophthalmologic apparatus via a network.

The drive device of the image reception unit 3020 reads out from the recording medium the photographed image acquired by another ophthalmologic apparatus and recorded on the recording medium.

The image reception unit 3020 receives a photographed image of the eye after removing the ortho-K lens. Also, the image receiving unit 3020 may receive design data 3015 and the like.

The analysis unit 3030 is configured to execute data processing similar to that of the processor of the corneal shape measurement unit 1020 of the ophthalmologic apparatus 1000 (data processing similar to that of the eye refractive power calculation unit 221 of the ophthalmologic apparatus 2000). It functions to analyze the photographed image received by the unit 3020 and acquire corneal shape data.

The evaluation unit 3040 is configured to execute data processing similar to that of the evaluation unit 1040 of the ophthalmologic apparatus 1000 (data processing similar to that of the evaluation unit 2231 of the ophthalmologic apparatus 2000). Based on the data and the design data 3015 stored in the storage unit 3010, it functions to evaluate the wearing state of the ortho-K lens on the eye.

The control unit 3050 controls each unit of the ophthalmologic information processing apparatus 3000 . Control unit 3050 includes a processor that operates according to a control program.

According to the ophthalmologic information processing apparatus 3000 configured in this way, it is possible to automatically determine whether or not the mounting position of the ortho-K lens is appropriate based on the photographed image of the eye acquired by another ophthalmologic apparatus. Therefore, it is not possible to determine the refraction state of the peripheral vision (that is, whether or not the Ortho-K lens was worn at the appropriate position at night) and to actually obtain the expected refractive correction effect. It is possible to provide users (doctors, etc.) with information for determining whether or not they are

In an exemplary embodiment, the ophthalmologic information processing apparatus 3000 can be installed on a network and configured to process captured images from multiple ophthalmologic apparatuses. As a result, the ophthalmologic information processing apparatus 3000 can centrally (integrally) perform the evaluation processing without providing each ophthalmologic apparatus with an ortho-K lens evaluation function. According to this configuration, it is possible to widely provide a service for evaluating the mounting state of the ortho-K lens.

For such an ophthalmic information processing device 3000, it is possible to combine any of the matters described with respect to ophthalmic devices (1000, 2000) according to exemplary aspects.

Exemplary aspects can provide a method of controlling an ophthalmic information processing device that includes a memory unit and a processor. For example, ophthalmic information processing apparatus 3000 includes (one or more) processors. The computer 9 of the ophthalmologic apparatus 2000 is similar.

A control method according to an exemplary aspect controls a processor to store design data of an ortho-K lens in a storage unit in a first control step. In a second control step, the processor is controlled to analyze captured images of the eye after removal of the Ortho-K lens to obtain corneal shape data of the eye. In the third control step, the wearing state of the ortho-K lens for the eye is evaluated based on the corneal shape data acquired in the second control step and the design data stored in the storage unit. to control the processor.

Any of the items described with respect to the ophthalmologic apparatus according to the exemplary embodiment can be combined with such a control method for the ophthalmologic information processing apparatus. Also, any of the items described with respect to the ophthalmologic information processing apparatus according to the exemplary embodiment can be combined with such a control method for the ophthalmologic information processing apparatus.

A program that causes a computer to execute the control method according to the exemplary aspect can be provided. Any of the items described with respect to the ophthalmic apparatus according to the exemplary embodiment can be combined with this program. Moreover, it is possible to combine any of the items described regarding the ophthalmologic information processing apparatus according to the exemplary embodiment with this program.

It is possible to create a computer-readable non-transitory recording medium recording such a program. Any of the items described with respect to the ophthalmic device according to the exemplary embodiment can be combined with this recording medium. Also, any of the items described with respect to the ophthalmologic information processing apparatus according to the exemplary embodiment can be combined with this recording medium. This non-transitory recording medium may be in any form, examples of which include magnetic disks, optical disks, magneto-optical disks, and semiconductor memories.

According to the control method, program, or recording medium according to the exemplary aspects, it is possible to cause a computer to determine whether the mounting position of the ortho-K lens is appropriate. As a result, we can actually obtain information for determining how the refraction state of the peripheral vision is (that is, whether or not the Ortho-K lens was worn at the appropriate position at night) and the expected refractive correction effect. It is possible to directly or indirectly provide the user (doctor, etc.) with information for determining whether or not the patient is being treated.

The several aspects described above are merely exemplary of implementations of the invention. Therefore, any modification (omission, substitution, addition, etc.) within the scope of the present invention is possible.

1000 ophthalmologic apparatus 1010 storage unit 1015 design data 1020 corneal topography measurement unit 1030 specific site detection unit 1040 evaluation unit 2000 ophthalmologic apparatus 5 anterior eye observation system 212 storage unit 2121 design data 221 eye refractive power calculation unit 2231 evaluation unit 3000 ophthalmic information processing Device 3010 Storage unit 3015 Design data 3020 Image reception unit 3030 Analysis unit 3040 Evaluation unit

Claims (14)

a storage unit for pre-storing design data of the orthokeratology lens;
a corneal shape measuring unit for measuring the corneal shape of the eye after removing the orthokeratology lens;
an evaluation unit that evaluates the wearing state of the orthokeratology lens on the eye based on the corneal shape data acquired by the corneal shape measurement unit and the design data;
The corneal shape measurement unit generates the corneal shape data by obtaining values of predetermined shape parameters for each of a plurality of positions on the cornea of the eye,
The evaluation unit comprises two or more values included in the corneal shape data corresponding to two or more of the plurality of positions and two or more designs included in the design data corresponding to the two or more positions. performing said evaluation by comparing a value with
Further comprising a specific site detection unit that detects a specific site of the eye after removing the orthokeratology lens,
The evaluation unit performs the evaluation by comparing the two or more values corresponding to the two or more positions symmetrical with respect to the specific part and the two or more design values, calculating a second difference that is the difference calculated from the value of and performing the evaluation based on the second difference;
ophthalmic equipment. The evaluation unit calculates a first difference that is a difference calculated from the two or more values and the two or more design values, and performs the evaluation based on the first difference.
The ophthalmic device of claim 1. The specific site is the corneal vertex of the eye after removing the orthokeratology lens,
3. The ophthalmic device according to claim 1 or 2. The specific site is the center of the pupil of the eye after removing the orthokeratology lens,
3. The ophthalmic device according to claim 1 or 2. The specific site is the center of the iris diameter of the eye after removing the orthokeratology lens,
3. The ophthalmic device according to claim 1 or 2. The specific site is the center of the corneal diameter of the eye after removal of the orthokeratology lens.
3. The ophthalmic device according to claim 1 or 2. The corneal shape measurement unit acquires curvature distribution data or curvature radius distribution data of the cornea of the eye after the orthokeratology lens is removed as the corneal shape data,
The design data includes curvature distribution data or curvature radius distribution data of the orthokeratology lens,
The ophthalmic device according to any one of claims 1-6. The corneal shape measurement unit acquires curvature distribution data or curvature radius distribution data of the cornea of the eye after the orthokeratology lens is removed as the corneal shape data,
The design data includes curvature distribution data or curvature radius distribution data set as a corneal shape correction target by the orthokeratology lens,
The ophthalmic device according to any one of claims 1-6. The corneal shape measurement unit acquires height distribution data of the cornea of the eye after removing the orthokeratology lens as the corneal shape data,
The design data includes shape data of the orthokeratology lens,
The ophthalmic device according to any one of claims 1-6. The corneal shape measurement unit acquires height distribution data of the cornea of the eye after the orthokeratology lens is removed as the corneal shape data,
The design data includes corneal shape correction target shape data by the orthokeratology lens,
The ophthalmic device according to any one of claims 1-6. A program to be executed by an ophthalmologic apparatus including an imaging unit for imaging an eye, a storage unit, and a processor,
In the ophthalmic device,
controlling the processor to store orthokeratology lens design data in the storage;
controlling the imaging unit to obtain a captured image of the eye after removing the orthokeratology lens;
controlling the processor to analyze the captured image to obtain corneal shape data of the eye;
controlling the processor to perform an assessment of fit of the orthokeratology lens on the eye based on the corneal shape data and the design data;
The step of controlling the processor to obtain the corneal shape data includes the processor to generate the corneal shape data by determining values of predetermined shape parameters for each of a plurality of locations on the cornea of the eye. comprising a step of controlling
The step of controlling the processor to perform the evaluation comprises: two or more values included in the corneal shape data corresponding to two or more of the plurality of positions; and corresponding to the two or more positions. controlling the processor to perform the evaluation by comparing two or more design values contained in the design data to
Furthermore,
causing the ophthalmic device to perform the step of controlling the processor to detect a specific portion of the eye after removal of the orthokeratology lens;
The step of controlling the processor to perform the evaluation includes comparing the two or more design values with the two or more values corresponding to the two or more locations symmetrical about the specific site. comprising calculating a second difference that is a difference calculated from the two or more values, and performing the evaluation based on the second difference.
program. a storage unit for pre-storing design data of the orthokeratology lens;
an analysis unit that acquires corneal shape data by analyzing a photographed image of the eye after the orthokeratology lens is removed;
an evaluation unit that evaluates the wearing state of the orthokeratology lens for the eye based on the corneal shape data and the design data;
The analysis unit generates the corneal shape data by obtaining values of predetermined shape parameters for each of a plurality of positions on the cornea of the eye,
The evaluation unit comprises two or more values included in the corneal shape data corresponding to two or more of the plurality of positions and two or more designs included in the design data corresponding to the two or more positions. performing said evaluation by comparing a value with
The analysis unit further detects a specific part of the eye after removing the orthokeratology lens,
The evaluation unit performs the evaluation by comparing the two or more values corresponding to the two or more positions symmetrical with respect to the specific part and the two or more design values, calculating a second difference that is the difference calculated from the value of and performing the evaluation based on the second difference;
Ophthalmic information processing device. A program to be executed by a computer including a storage unit and a processor,
to the computer;
controlling the processor to store orthokeratology lens design data in the storage;
controlling the processor to analyze captured images of the eye after removal of the orthokeratology lens to obtain corneal shape data of the eye;
controlling the processor to perform an assessment of fit of the orthokeratology lens on the eye based on the corneal shape data and the design data;
The step of controlling the processor to obtain the corneal shape data includes the processor to generate the corneal shape data by determining values of predetermined shape parameters for each of a plurality of locations on the cornea of the eye. comprising a step of controlling
The step of controlling the processor to perform the evaluation comprises: two or more values included in the corneal shape data corresponding to two or more of the plurality of positions; and corresponding to the two or more positions. controlling the processor to perform the evaluation by comparing two or more design values contained in the design data to
Furthermore,
causing the computer to perform the step of controlling the processor to detect a specific portion of the eye after removal of the orthokeratology lens;
The step of controlling the processor to perform the evaluation includes comparing the two or more design values with the two or more values corresponding to the two or more locations symmetrical with respect to the specific site. comprising calculating a second difference that is a difference calculated from the two or more values, and performing the evaluation based on the second difference.
program. A computer-readable non-transitory recording medium on which the program according to claim 11 or 13 is recorded.

Images