JP2006034744A - Ophthalmic equipment - Google Patents

Abstract

PROBLEM TO BE SOLVED: To obtain correction data suitable for an eye to be examined when wearing a contact lens.
A calculation unit obtains wavefront aberration including low-order and high-order aberrations of an eye to be examined based on a light reception signal obtained by receiving a reflected light beam applied to the eye to be examined (S2105). Further, the calculation unit obtains the corneal aberration and the corneal shape of the eye to be inspected based on the anterior eye image obtained by irradiating the light to the anterior eye part to be examined and reflecting the light flux (S2105). The calculation unit obtains the correction optical system aberration by removing the corneal aberration from the eyeball optical system aberration of the entire eye to be examined and adding the aberration of the correction optical system including the contact lens worn on the eye to be examined (S2106). Based on the obtained correction optical system aberration, the calculation unit obtains correction data for contact lens wearing that is suitable for the eye to be examined (S2107) and outputs it (S2109).
[Selection] Figure 6

Description

  The present invention relates to an ophthalmologic apparatus, and more particularly to an ophthalmologic apparatus for obtaining an optimal prescription value of a contact lens in consideration of correction of aberrations of the anterior cornea due to contact lens wearing.

  Conventionally, as a technique for measuring eye correction data, measurement of S (spherical power), C (astigmatic power), and A (axis) using a refractometer has been performed. Recently, an eye characteristic measuring apparatus capable of measuring even higher-order aberrations has been developed, and not only S, C, A on a line such as a φ3 mm ring such as a refractometer but also S, C on the surface. , A can be calculated from low-order aberrations. Such an eye characteristic measuring apparatus has come to calculate values close to prescription values for spectacles, contact lenses, etc. from a refractometer, particularly after refractive surgery and for sick eyes (for example, Patent Document 1). To 4).

Moreover, software for ray tracing is available (for example, CodeV (http://www.opticalres.com/), Zemax (http://www.zemax.com/), etc.).
The present inventors have applied for an apparatus or the like that limits the pupil diameter from the wavefront aberration of the eye and obtains an optimal prescription value from optical characteristics such as Strehl ratio and phase shift (PTF). Application No. 2003-25428, Japanese Patent Application No. 2003-134829, etc.).
JP 2002-204785 A JP 2002-209854 A JP 2002-306416 A JP 2002-306417 A

  However, there is a case where a difference between the objective calculation result of the conventional eye characteristic measuring device and the prescription value of the spectacles / contact lens and the like is still appropriate, and the evaluation of S, C, and A There were cases where it was insufficient. Conventionally, since the pupil diameter of the eye to be examined is measured using a fixed value, an appropriate prescription value corresponding to the pupil diameter of the eye to be examined may not be obtained.

  Furthermore, when the contact lens (CL) is worn, the aberration of the anterior cornea is corrected by the tear film between the anterior cornea and the contact lens. On the other hand, the aberration on the front surface of the contact lens is affected.

  In view of the above, an object of the present invention is to provide an ophthalmologic apparatus for obtaining an optimum contact lens prescription value when a contact lens is worn. Further, according to the present invention, the aberration of the anterior surface of the cornea is corrected by wearing the contact lens. Therefore, the optimal prescription value of the contact lens (for example, the spherical power S, the astigmatism power C, the astigmatism axis A, taking this correction amount into consideration) ). Another object of the present invention is to obtain a prescription value for a contact lens, assuming an optical system including a contact lens, a tear film, and an eye to be examined in consideration of the tear film.

  Further, the present invention is a result of measurement with an eye characteristic measuring apparatus capable of measuring up to high order aberrations, and when high order aberrations are included, low order aberrations during objective complete correction are not used as correction correction data. For example, the optical performance is evaluated by the Strehl ratio or phase shift, the low-order aberration amount is calculated such that the Strehl ratio is large and / or the phase shift is small, and correction correction data such as S, C, A, etc. at that time The purpose is to obtain correction data that is closer to the prescription value for glasses, contacts, etc., more optimally. It is another object of the present invention to obtain correction data close to a subjective value by simulating the appearance of an optometric target and obtaining an appropriate correction factor.

  Another object of the present invention is to calculate correction data close to an optical characteristic and an optimum prescription value according to the pupil diameter of the eye to be examined, and to perform more accurate measurement. In addition, the present invention obtains correction data close to the optimum prescription value in the environment using the pupil diameter under the brightness (for example, daytime or indoors) suitable for the subject's environment. With the goal.

According to the first solution of the present invention,
A wavefront aberration measuring optical system for irradiating the fundus of the eye to be examined and receiving reflected light from the fundus of the eye to be examined;
A wavefront aberration calculator that obtains wavefront aberration including low-order aberration and high-order aberration of the eye to be examined based on the signal received by the wavefront aberration measurement optical system;
A cornea / contact lens data measurement optical system for illuminating the vicinity of the subject's eye cornea with a predetermined pattern and receiving a reflected light beam from the vicinity of the subject's eye cornea,
A corneal / contact lens data calculation unit for determining a corneal shape and corneal aberration of the eye based on a signal received by the cornea / contact lens data measuring optical system;
The aberration of the correction optical system including the contact lens according to the corneal shape obtained by the cornea / contact lens data calculation unit is obtained, and the wavefront aberration, corneal aberration, and correction of the eye to be examined obtained by the wavefront aberration calculation unit are corrected. Based on the aberration of the optical system, the aberration of the correction eye optical system including the eye and the contact lens in which the contact lens is worn on the eye to be examined is obtained, and the eye to be examined is determined according to the obtained aberration of the correction eye optical system. An ophthalmologic apparatus is provided that includes a correction data calculation unit that calculates correction data for contact lens wearing that is appropriate correction.

According to the second solution of the present invention,
A wavefront aberration measurement optical system for irradiating a light beam to the fundus of the eye to be examined wearing a contact lens and receiving reflected light from the fundus of the eye to be examined;
A wavefront aberration calculator that obtains wavefront aberration including low-order aberration and high-order aberration of the eye to be examined based on the signal received by the wavefront aberration measurement optical system;
A cornea / contact lens data measurement optical system for illuminating the vicinity of the subject's eye cornea wearing a contact lens with a predetermined pattern and receiving a reflected light beam from the vicinity of the subject's eye cornea,
Based on the signal received by the cornea / contact lens data measurement optical system, the cornea / contact lens data calculation unit for obtaining the contact lens front surface shape and contact lens front aberration when the contact lens of the eye to be examined is worn,
The spherical power of the contact lens to be changed is set, and the aberration due to the deviation between the spherical power based on the wavefront aberration obtained by the wavefront aberration calculator and the spherical power of the set contact lens is obtained and obtained. A correction aberration is obtained by taking the difference between the aberration and the front aberration of the contact lens, and the corrected aberration is calculated by adding the corrected aberration to the wavefront aberration obtained by the wavefront aberration calculator. An ophthalmologic apparatus is provided that includes a correction data calculation unit that calculates aberration data and calculates correction data for contact lens wearing that is appropriate for the subject's eye according to the determined aberration of the correction eye optical system.

  ADVANTAGE OF THE INVENTION According to this invention, the ophthalmologic apparatus for obtaining the optimal contact lens prescription value at the time of contact lens wearing can be provided. Further, according to the present invention, the aberration of the anterior surface of the cornea is corrected by wearing the contact lens. Therefore, the optimum prescription value of the contact lens (for example, the spherical power S, the astigmatic power C, the astigmatic axis, taking this correction amount into consideration) A) can be obtained. Furthermore, according to the present invention, in consideration of the tear film, an optical system including a contact lens, a tear film, and an eye to be examined can be assumed to obtain a prescription value for the contact lens.

  In addition, according to the present invention, in the case where high-order aberration is included in the result of measurement with an eye characteristic measuring apparatus capable of measuring up to high-order aberration, low-order aberration corresponding to objective complete correction is not used as correction correction data. For example, optical performance is evaluated based on Strehl ratio or phase shift, and a low-order aberration amount is calculated so that Strehl ratio is large and / or phase shift is small, and correction correction of S, C, A, etc. at that time is performed. By obtaining the data, it is possible to obtain correction data that is closer to the prescription value for more optimal glasses / contacts. Furthermore, it is possible to obtain correction data close to the subjective value by simulating the appearance of the optometric target and obtaining an appropriate correction factor.

  In addition, according to the present invention, it is possible to calculate correction characteristics that are close to optical characteristics and optimum prescription values according to the pupil diameter of the subject's eye, and perform more accurate measurement. Further, according to the present invention, correction data close to the optimum prescription value under the environment is obtained using the pupil diameter under the brightness suitable for the subject's environment (for example, at daytime or indoors). be able to.

1. Ophthalmologic Apparatus FIG. 1 is a configuration diagram of an optical system 100 of an ophthalmologic apparatus (eye optical characteristic measuring apparatus).
The optical system 100 of the eye optical characteristic measuring apparatus is an apparatus that measures the optical characteristics of the eye 60 to be measured, which is an object, and includes a first illumination optical system 10, a first light receiving optical system 20, and a second light receiving optical system. A system 30, a common optical system 40, an adjustment optical system 50, a second illumination optical system 70, and a second light transmission optical system 80 are provided. Note that the retina 61 and the cornea 62 are shown in the figure for the eye to be measured (hereinafter also referred to as the eye to be examined) 60. In the present embodiment, the optical system including the first illumination optical system 10 and the first light receiving optical system 20 is a wavefront aberration measuring optical system, and the second light receiving optical system 30 and the second illumination optical system 70 are optical. The system may be called a cornea / contact lens data measurement optical system.

  The first illumination optical system 10 includes, for example, a first light source unit 11 for emitting a light beam having a first wavelength, and a condensing lens 12, and the retina of the eye 60 to be measured with the light beam from the first light source unit 11. This is for illuminating a minute region on the (fundus) 61 so that the illumination conditions can be set as appropriate. Here, as an example, the first wavelength of the illumination light beam emitted from the first light source unit 11 is an infrared wavelength (for example, 780 nm).

  The first light source unit 11 preferably has a large spatial coherence and a small temporal coherence. Here, the 1st light source part 11 is a super luminescence diode (SLD), for example, Comprising: It can obtain a point light source with high brightness | luminance. The first light source unit 11 is not limited to the SLD. For example, even a laser having a large spatial coherence or temporal coherence, a rotating diffusion plate, a declination prism (D prism), or the like is inserted to It can be used by reducing the time coherence. Furthermore, even an LED with small spatial coherence and temporal coherence can be used by inserting a pinhole or the like at the position of the light source in the optical path as long as the amount of light is sufficient.

  The first light receiving optical system 20 is, for example, a collimating lens 21 and a conversion member that converts a part of a light beam (first light beam) reflected and returned from the retina 61 of the eye 60 to be measured into at least 17 beams. And a first light receiving unit 23 for receiving a plurality of beams converted by the Hartman plate 22, and for guiding the first light flux to the first light receiving unit 23. Here, the first light receiving unit 23 is a CCD with low lead-out noise, but as the CCD, for example, a general low noise type, a cooling CCD of 1000 * 1000 elements for measurement, etc. An appropriate type can be applied.

  The second illumination optical system 70 includes a second light source 72 and a placido ring 71. Note that the second light source 72 may be omitted. A placido ring (PLACIDO'S DISC) 71 is for projecting a pattern index composed of a plurality of concentric annular zones. Note that the index of a pattern composed of a plurality of concentric annular zones is an example of an index of a predetermined pattern, and other appropriate patterns can be used. And after the alignment adjustment mentioned later is completed, the parameter | index of the pattern which consists of a some concentric ring zone can be projected.

  The second light transmission optical system 80 mainly performs, for example, alignment adjustment and measurement / adjustment of coordinate origin and coordinate axes, which will be described later, and includes a second light transmission light source unit 31, a condensing lens 32, and a beam splitter. 33.

  The second light receiving optical system 30 includes a condenser lens 34 and a second light receiving unit 35. The second light receiving optical system 30 returns a light beam (second light beam) that the pattern of the placido ring 71 illuminated from the second illumination optical system 70 is reflected and returned from the anterior eye portion or the cornea 62 of the eye 60 to be measured. And guided to the second light receiving unit 35. Further, the light beam emitted from the second light transmission light source unit 31, reflected from the cornea 62 of the eye 60 to be measured, and returned can be guided to the second light receiving unit 35. The second wavelength of the light beam emitted from the second light transmission light source unit 31 is different from the first wavelength (here, 780 nm), for example, and a long wavelength can be selected (for example, 940 nm).

The common optical system 40 is disposed on the optical axis of the light beam emitted from the first illumination optical system 10, and includes the first and second illumination optical systems 10 and 70, the first and second light receiving optical systems 20 and 30, and the second. The optical transmission system 80 can be included in common, and includes, for example, an afocal lens 42, beam splitters 43 and 45, and a condensing lens 44. Further, the beam splitter 43 transmits (reflects) the wavelength of the second light transmission light source unit 31 to the eye 60 to be measured, reflects the second light flux reflected and returned from the retina 61 of the eye 60 to be measured, On the other hand, it is formed of a mirror (for example, a dichroic mirror) that transmits the wavelength of the first light source unit 11. The beam splitter 45 transmits (reflects) the light beam of the first light source unit 11 to the eye 60 to be measured, and transmits a first light beam reflected and returned from the retina 61 of the eye 60 to be measured (a mirror ( For example, it is formed by a polarization beam splitter. The beam splitters 43 and 45 prevent the first and second light beams from entering the other optical system and causing noise.
The adjustment optical system 50 mainly performs, for example, adjustment of a working distance described later, and includes a third light source unit 51, a fourth light source unit 55, condensing lenses 52 and 53, and a third light receiving unit 54. Is provided.

  The third illumination optical system 90 includes, for example, an optical path for projecting a target for fixation or clouding of the eye 60 to be measured, and includes a fifth light source unit (for example, a lamp) 91, a fixation target. 92 and a relay lens 93. The fixation target 92 can be irradiated to the fundus 61 with the light flux from the fifth light source unit 91, and the eye 60 to be examined is observed. The fixation target 92 and the fundus 61 are in a conjugate relationship by the third illumination optical system 90. The fifth light source unit 91 is also a light source (anterior eye illumination unit) that illuminates the anterior eye part of the eye 60 to be measured with different brightness. By adjusting the amount of light of the fifth light source unit 91, the illumination state of the eye 60 to be measured can be changed to change the size of the pupil. In addition to the fifth light source unit 91, an appropriate light source such as the second light source 72 may be used as the anterior eye illumination unit.

Next, alignment adjustment will be described. The alignment adjustment is mainly performed by the second light receiving optical system 30 and the second light transmitting optical system 80.
First, the light beam from the second light transmission light source unit 31 illuminates the eye 60 to be measured, which is an object, with a substantially parallel light beam via the condenser lens 32, the beam splitters 33 and 43, and the afocal lens 42. The reflected light beam reflected by the cornea 62 of the eye 60 to be measured is emitted as a divergent light beam as if it was emitted from a point having a radius of curvature of the cornea 62. The divergent light beam is received as a spot image by the second light receiving unit 35 through the afocal lens 42, the beam splitters 43 and 33, and the condenser lens 34.

  Here, when the spot image on the second light receiving unit 35 is off the optical axis, the eye optical characteristic measuring device main body is moved and adjusted vertically and horizontally so that the spot image coincides with the optical axis. As described above, when the spot image coincides with the optical axis, the alignment adjustment is completed. In the alignment adjustment, the cornea 62 of the eye 60 to be measured is illuminated by the third light source unit 51, and an image of the eye 60 to be measured obtained by this illumination is formed on the second light receiving unit 35. May be used so that the pupil center coincides with the optical axis.

Next, the working distance adjustment will be described. The working distance adjustment is mainly performed by the adjustment optical system 50.
First, the working distance adjustment is performed, for example, by irradiating a parallel light beam near the optical axis emitted from the fourth light source unit 55 toward the eye 60 to be measured and the light reflected from the eye 60 to be measured. This is performed by receiving light at the third light receiving unit 54 via the condenser lenses 52 and 53. Further, when the eye 60 to be measured is at an appropriate working distance, a spot image from the fourth light source unit 55 is formed on the optical axis of the third light receiving unit 54. On the other hand, when the eye 60 to be measured deviates back and forth from an appropriate working distance, the spot image from the fourth light source unit 55 is formed above or below the optical axis of the third light receiving unit 54. The third light receiving unit 54 only needs to be able to detect a change in the position of the light beam in the plane including the fourth light source unit 55, the optical axis, and the third light receiving unit 54. For example, the one-dimensionally arranged in this plane A CCD, a position sensing device (PSD), etc. can be applied.

Next, the positional relationship between the first illumination optical system 10 and the first light receiving optical system 20 will be described.
A beam splitter 45 is inserted into the first light receiving optical system 20, and the light from the first illumination optical system 10 is transmitted to the eye to be measured 60 by the beam splitter 45 and the eye to be measured 60. The reflected light from is transmitted. The first light receiving unit 23 included in the first light receiving optical system 20 receives light that has passed through the Hartmann plate 22 that is a conversion member, and generates a light reception signal.

  Further, the first light source unit 11 and the retina 61 of the eye 60 to be measured form a conjugate relationship. The retina 61 of the eye 60 to be measured and the first light receiving unit 23 are conjugate. The Hartmann plate 22 and the pupil of the eye 60 to be measured form a conjugate relationship. Further, the first light receiving optical system 20 forms a substantially conjugate relationship with the cornea 62 and the pupil, which are the anterior segment of the eye 60 to be measured, and the Hartmann plate 22. That is, the anterior focal point of the afocal lens 42 substantially coincides with the cornea 62 and the pupil, which are the anterior segment of the eye 60 to be measured.

  In addition, the first illumination optical system 10 and the first light receiving optical system 20 assume that the light flux from the first light source unit 11 is reflected at the point where the light is collected, and the signal peak due to the reflected light from the first light receiving unit 23 is generated. Move in tandem to maximize. Specifically, the first illumination optical system 10 and the first light receiving optical system 20 move in a direction in which the signal peak at the first light receiving unit 23 increases, and stop at a position where the signal peak becomes maximum. Thereby, the light beam from the first light source unit 11 is collected on the eye 60 to be measured.

  The lens 12 converts the diffused light from the light source 11 into parallel light. The diaphragm 14 is optically conjugate with the pupil of the eye or the Hartmann plate 22. The diaphragm 14 has a diameter smaller than the effective range of the Hartmann plate 22 so that so-called single-pass aberration measurement (a method in which the eye aberration affects only the light receiving side) is established. In order to satisfy the above, the lens 13 is disposed so that the fundus conjugate point of the actual light ray is at the front focal position, and further, the rear focal position is coincident with the stop 14 in order to satisfy the conjugate relationship with the eye pupil. ing.

  The light beam 15 travels in the same manner as the light beam 24 in a paraxial manner after the light beam 24 and the beam splitter 45 have a common optical path. However, in the single pass measurement, the diameters of the respective light beams are different, and the beam diameter of the light beam 15 is set to be considerably smaller than that of the light beam 24. Specifically, the beam diameter of the light beam 15 may be, for example, about 1 mm at the pupil position of the eye, and the beam diameter of the light beam 24 may be about 7 mm (in the drawing, from the beam splitter 45 of the light beam 15 to the fundus). 61 is omitted).

Next, the Hartmann plate 22 as a conversion member will be described.
The Hartmann plate 22 included in the first light receiving optical system 20 is a wavefront conversion member that converts a reflected light beam into a plurality of beams. Here, a plurality of micro Fresnel lenses arranged in a plane orthogonal to the optical axis is applied to the Hartmann plate 22. In general, in order to measure the spherical component, third-order astigmatism, and other higher-order aberrations of the measurement target portion 60 (measured eye 60), at least via the measured eye 60. It is necessary to measure with 17 beams.

  The micro Fresnel lens is an optical element, and includes, for example, an annular zone having a height pitch for each wavelength and a blaze optimized for emission parallel to the focal point. The micro Fresnel lens here is, for example, an optical path length difference of 8 levels applying a semiconductor microfabrication technique, and achieves a high light collection rate (for example, 98%).

  The reflected light from the retina 61 of the eye 60 to be measured passes through the afocal lens 42 and the collimating lens 21 and is condensed on the first light receiving unit 23 via the Hartmann plate 22. Therefore, the Hartmann plate 22 includes a wavefront conversion member that converts the reflected light beam into at least 17 beams.

  FIG. 2 is a configuration diagram of the electric system 200 of the eye optical characteristic measuring apparatus. The electrical system 200 related to the ophthalmic optical characteristic measuring apparatus includes, for example, a calculation unit 210, a control unit 220, a display unit 230, a memory 240, an input unit 270, a first driving unit 250, a second driving unit 260, and a second driving unit. 3 drive unit 280. The calculation unit 210 may include a wavefront aberration calculation unit 211, a cornea / contact lens data calculation unit 212, a correction data calculation unit 213, a simulation unit 214, and a pupil diameter measurement unit 215.

  The calculation unit 210 receives the light reception signal (4) obtained from the first light receiving unit 23, the light reception signal (7) obtained from the second light receiving unit 35, and the light reception signal (10) obtained from the third light receiving unit 54. , Coordinate origin, coordinate axis, coordinate movement, rotation, pupil diameter, total wavefront aberration, corneal wavefront aberration, Zernike coefficient, aberration coefficient, Strehl ratio (Strhl ratio), phase shift (PTF, phase shift), white light MTF, Landolt A ring pattern or the like is calculated. In addition, signals according to such calculation results are output to the control unit 220 that controls the entire electric drive system, the display unit 230, and the memory 240, respectively. Details of the operation 210 will be described later.

  The wavefront aberration calculating unit 211 obtains wavefront aberration including low-order and high-order aberrations of the eye to be examined based on the light reception signal (4) from the first light receiving unit 23. The cornea / contact lens data calculation unit 212 is based on the received light signal (7) (or the anterior segment image) from the second light receiving unit 35, or cornea data including corneal shape, corneal aberration, etc. Contact lens front surface data including contact lens front surface shape and aberration due to contact lens front surface when optometry is worn is obtained. The corneal shape and the contact lens front surface shape have coordinates of the cornea, contact lens apex, or pupil center as the origin, and have height information data or Zernike coefficient data at each position. The cornea / contact lens data calculation unit 212 may be configured to obtain data on either the cornea or the contact lens.

  Further, the correction data calculation unit 213 calculates or sets a correction element to be given to the simulation unit 214. The correction data calculation unit 213 determines whether or not an appropriate correction element is set based on the correction target image data corrected by the set correction element and formed by the simulation unit 214. The correction data calculation unit 213 is configured to set a correction element based on the determination result and repeatedly change the correction element until it is determined to be an appropriate correction element. The correction element is any one or a combination of a spherical power (S), an astigmatic power (C), and an astigmatic axis angle (A).

  In calculating correction data in template matching, which will be described later, the simulation unit 214 performs a simulation of the appearance of the optometry target in consideration of correction elements for refractive correction based on at least measurement data indicating the wavefront aberration of the eye to be examined. The target retinal image data is formed. The wavefront aberration of the eye to be examined includes higher order aberrations. The pupil diameter measuring unit 215 forms pupil diameter data from the anterior segment image. For example, the pupil diameter measurement unit 215 receives the anterior eye image from the second light receiving unit 35, calculates a point on the edge of the pupil, a focal point when the pupil is elliptical, a major axis, and a minor axis, Find the pupil diameter.

  The control unit 220 controls turning on and off of the first light source unit 11 based on a control signal from the calculation unit 210, and controls the first driving unit 250 and the second driving unit 260. Based on the signal according to the calculation result in the calculation unit 210, the signal (1) is output to the first light source unit 11, the signal (5) is output to the placido ring 71, and the second light source The signal (6) is output to the unit 31, the signal (8) is output to the third light source unit 51, the signal (9) is output to the fourth light source unit 55, and the fifth light source unit 91 is output. In response to this, a signal (11) is output, and further, a signal is output to the first drive unit 250, the second drive unit 260, and the third drive unit 280.

  The first drive unit 250 moves the entire first illumination optical system 10 in the optical axis direction based on the light reception signal (4) from the first light reception unit 23 input to the calculation unit 210, for example. A signal (2) is output to an appropriate lens moving means (not shown) and the lens moving means is driven. Thereby, the first drive unit 250 can move and adjust the first illumination optical system 10.

  For example, the second drive unit 260 moves the entire first light receiving optical system 20 in the optical axis direction based on the light reception signal (4) from the first light receiving unit 23 input to the calculation unit 210. A signal (3) is output to an appropriate lens moving means (not shown) and the lens moving means is driven. Thereby, the second drive unit 260 can move and adjust the first light receiving optical system 20.

  The third drive unit 280 moves, for example, the fixation target 92 of the third illumination optical system 90. The third drive unit 280 outputs a signal (12) to an appropriate moving unit (not shown) and drives the moving unit. To do. Thereby, the third drive unit 280 can move and adjust the fixation target 92 of the third illumination optical system 90.

  FIG. 3 is a configuration example of the front shape table stored in advance in the memory 240. The front surface shape table includes front surface shape data, a curvature, a refractive index, and the like corresponding to the contact lens ID (manufacturer ID, type, etc.), the corrected spherical power, and the rear surface shape data. Further, the thickness and the rear surface diameter of the contact lens can be further included corresponding to the contact lens ID, the corrected spherical power, and the rear surface shape data.

  FIG. 4 is a configuration example of a rear surface shape table stored in advance in the memory 240. The rear surface shape table includes rear surface shape data corresponding to the kerato value or corneal shape and the contact lens ID. The computing unit 210 acquires the rear surface shape data of CL based on the measured kerato value or corneal shape and the set contact lens ID.

2. Next, Zernike analysis will be described. A method of calculating the Zernike coefficient C _i ^2j-i from a generally known Zernike polynomial will be described. The Zernike coefficient C _i ^2j−i is an important parameter for grasping the optical characteristics of the eye 60 based on the tilt angle of the light beam obtained by the first light receiving unit 23 via the Hartmann plate 22, for example.
The wavefront aberration W (X, Y) of the eye 60 to be examined is expressed by the following equation using the Zernike coefficient C _i ^2j−i and the Zernike polynomial Z _i ^2j−i .

ただし、（Ｘ，Ｙ）はハルトマン板２２の縦横の座標である。

However, (X, Y) are the vertical and horizontal coordinates of the Hartmann plate 22.

  The wavefront aberration W (X, Y) is received by the first light receiving unit 23 with the vertical and horizontal coordinates of the first light receiving unit 23 being (x, y), the distance between the Hartmann plate 22 and the first light receiving unit 23 being f. If the moving distance of the point image is (Δx, Δy), the following relationship is established.

ここで、ゼルニケ多項式Ｚ_ｉ ^２ｊ−ｉは、以下の式（４）及び式（５）で表される（より具体的な式は、例えば特開２００２−２０９８５４号公報参照）。

Here, the Zernike polynomial Z _i ^2j-i is expressed by the following formulas (4) and (5) (for more specific formulas, see, for example, JP-A-2002-209854).

なお、ゼルニケ係数Ｃ_ｉ ^２ｊ−ｉは、以下の式（６）で表される自乗誤差を最小にすることにより具体的な値を得ることができる。

The Zernike coefficient C _i ^2j−i can be obtained as a specific value by minimizing the square error represented by the following equation (6).

ただし、Ｗ（Ｘ、Ｙ）：波面収差、（Ｘ、Ｙ）：ハルトマン板座標、（△ｘ、△ｙ）：第１受光部２３で受光される点像の移動距離、ｆ：ハルトマン板２２と第１受光部２３との距離。

However, W (X, Y): Wavefront aberration, (X, Y): Hartmann plate coordinates, (Δx, Δy): Movement distance of the point image received by the first light receiving unit 23, f: Hartmann plate 22 And the distance between the first light receiving unit 23 and the first light receiving unit 23.

The calculation unit 210 calculates the Zernike coefficient C _i ^2j-i and uses this to obtain eye optical characteristics such as spherical aberration, coma aberration, and astigmatism.

(Normalization of pupil diameter)
The Zernike polynomial always indicates a shape within a circle having a radius of 1. When performing Zernike analysis with a certain pupil diameter (pupil diameter), the Zernike polynomial is normalized with the pupil radius. For example, when the center coordinate of the pupil with the pupil radius r _p is (0, 0), the point P (X, Y) in the pupil is P (X / r _p , Y / r _p when performing Zernike analysis. ). When the center of gravity of the spot of the Hartmann image is P, the reference lattice point P _ref (X _ref , Y _ref ) corresponding to this point is represented as P _ref (X _ref / r _p , Y _ref / r _p ) The travel distance is obtained and the Zernike coefficient is calculated. The actual wavefront (wavefront whose coordinates are not normalized) W (X, Y) is expressed by the following equation.

ただし、（Ｘ、Ｙ）：規格化されていない座標、（ｘ_ｓ、ｙ_ｓ）：規格化された座標である。

However, (X, Y): non-standardized coordinates, (x _s , y _s ): standardized coordinates.

3. Landolt ring FIG. 5 is an explanatory diagram of the Landolt ring.
The creation of the data of the Landolt's luminance distribution function Land (x, y) will be described below.
The Landolt ring is represented by the reciprocal of the minimum visual angle that can be confirmed, and the ability to confirm the visual angle of 1 minute is called visual acuity 1.0. For example, if the minimum viewing angle that can be confirmed is 2 minutes, the visual acuity is defined as 0.5 by 1/2, and 0.1 by 1/10 if it is 10 minutes. In general, the Landolt ring uses, as an index, a ring with a gap of 1/5 the size of the outer ring as shown in the figure.

（Ｒ： 瞳から像点（網膜）までの距離）
で計算できる。この式とランドルト環の定義をもとにランドルト環の黒い部分を０、白い部分を１としてランドルト環の輝度分布関数Ｌａｎｄ（ｘ，ｙ）を作成する。作成された輝度分布関数Ｌａｎｄ（ｘ，ｙ）のデータはメモリ２４０に記憶され、演算部２１０により読み出され、所定の視力に対応して設定される。 The size d of the Landolt ring projected onto the fundus is

(R: Distance from pupil to image point (retina))
It can be calculated with Based on this equation and the definition of the Landolt ring, the black part of the Landolt ring is set to 0 and the white part is set to 1 to create the luminance distribution function Land (x, y) of the Landolt ring. The data of the created luminance distribution function Land (x, y) is stored in the memory 240, read by the calculation unit 210, and set corresponding to a predetermined visual acuity.

4). Correction Data Measurement Method 4-1 Main Flow FIG. 6 shows a flowchart of correction data measurement for contact lens wearing.
First, the eye optical characteristic measurement apparatus aligns the X, Y, and Z axes of the pupil position of the eye 60 to be measured (S2101). Next, the measuring apparatus moves the origin of the movable part (S2103). For example, the Hartmann plate 22 and the placido ring 71 are set to zero diopter. Based on the measured received light signals (4), (7) and / or (10), the arithmetic unit 210 calculates the pupil diameter, the corneal data such as the corneal shape and the corneal aberration W _co , the total wavefront aberration and the Zernike coefficient. The eyeball optical system data (for example, eyeball optical system aberration W _eye ) is measured (S2105). Details of step S2105 will be described later.

The calculation unit 210 performs a correction eye optical system simulation (S2106). For example, the calculation unit 210 removes corneal aberration from the aberration of the eyeball optical system measured in step S2105, adds the aberration of the correction optical system such as a contact lens to this, and corrects the corrected optical system aberration after correction by the contact lens, for example. (Corrected eye optical system simulation-1). Alternatively, for example, the calculation unit 210 may obtain the corrected optical system aberration W _correct after correction by spectacles, for example, by removing the secondary aberration from the aberration W _eye of the eyeball optical system measured in step S2105. (Correction eye optical system simulation-2).

  FIG. 32 is an explanatory diagram of the correction eye optical system and the correction optical system. In the present embodiment, FIG. 32 (a) shows an outline of the correction eye optical system. The correction eye optical system includes, for example, a contact lens, a tear film, and an eye to be measured. When the contact lens is not worn, the influence of the aberration (for example, corneal aberration) where the refractive index changes greatly like between the air and the cornea is large, but when the contact lens is worn, the aberration at the cornea Aberrations are greatly affected by the shape of the front surface of contact lenses that come into contact with air. Therefore, in the present embodiment, for example, by assuming an optical system as shown in FIG. 32A, it is possible to obtain an optimum prescription value for contact lens wearing. Note that the tear film can be omitted.

  FIG. 32B shows an outline of the correction optical system. The correction optical system includes, for example, a contact lens, a tear film, and a cornea. By subtracting the corneal aberration from the aberration of the eye to be measured and adding the aberration of the correction optical system as shown in FIG. 32B, for example, the aberration of the correction eye optical system of FIG. 32A can be obtained. .

FIG. 7 is a sub-flowchart of the correction eye optical system simulation-1 in step S2106. Hereinafter, detailed processing of the correction eye optical system simulation-1 will be described.
First, the calculation unit 210 (for example, the correction data calculation unit 213, the same applies to step 2205 below) calculates the intraocular aberration W _inter by removing the corneal aberration W _co from the eyeball optical system aberration W _eye obtained in step S2105. (S2201).
Intraocular aberration W _inter = eyeball optical system aberration W _eye −corneal aberration W _co
Next, the calculation unit 210 calculates an aberration W _CLCO including the contact lens and the cornea when the contact lens is worn (S2203). For example, in the present embodiment, an aberration corresponding to the front shape of the contact lens can be included. The contact lens front surface shape varies depending on, for example, the corrected spherical power, the contact lens rear surface shape, the manufacturer, and the type of contact lens. The calculation unit 210 considers the air layer, the contact lens layer, the tear film layer, and the cornea as lens groups, respectively, and uses these as the entire optical system (correcting optical system), and the overall aberration (hereinafter referred to as CL / corneal aberration, or referred to as a correction optical system _aberration) determine the _{W CLCO.}

  For example, the correction data calculation unit 213 responds to the provisional spherical power based on the wavefront aberration calculated by the wavefront aberration calculation unit 211 or in advance and the cornea shape calculated by the cornea / contact lens data calculation unit 212. Further, the aberration of the correction optical system including the contact lens is obtained by ray tracing based on the wear correction data including one or more of the thickness, the rear surface diameter, the shape, the curvature, and the refractive index of the contact lens.

In addition, since the change of the front shape of a lens differs between a hard contact lens and a soft contact lens, the process according to a hard lens and a soft lens can be performed as follows. For example, in the case of a hard contact lens, the shape of the contact itself is maintained, and the wavefront aberration of the cornea is canceled out, so that the spherical aberration due to the front shape of the contact lens is added to the eye to be measured, and approximately CL · Corneal aberration W _CLCO can also be calculated. On the other hand, in the case of a soft contact lens, it is assumed that the corneal shape is completely (or almost completely) compliant, or the degree along the corneal shape can be calculated and simulated based on the rigidity of each contact.

  Note that the calculation unit 210 may determine which processing is executed by inputting from the input unit 270 whether the contact lens is a hard contact lens or a soft contact lens, and based on the selected contact lens ID, It may be determined whether it is a contact lens or a soft contact lens, and which process is executed.

FIG. 33 shows a processing flow in the case of a hard contact lens.
First, processing in the case of a hard contact lens will be described. First, the calculation unit 210 selects identification information (hereinafter referred to as a contact lens ID) indicating the type of contact lens such as a manufacturer ID and a model number (S2231). In addition to the manufacturer ID, appropriate identification information can be used for the contact lens ID. The calculation unit 210 can input the contact lens ID from the input unit 270, for example. In addition, the calculation unit 210 displays a list of contact lens IDs stored in the front shape table or the rear shape table and an instruction to select a contact lens ID from the list on the display unit 230, and inputs from the input unit 270. The selected contact lens ID may be input.

  The computing unit 210 refers to the rear surface shape table based on the selected contact lens ID and the corneal shape or kerato value obtained in step S2105, and acquires corresponding rear surface shape data (S2233). Next, the calculation unit 210 refers to the front surface shape table based on the selected contact lens ID, the acquired rear surface shape data, and the provisional spherical power, and acquires the corresponding front surface shape data, curvature, refractive index, and the like. (S2235). As the provisional spherical power, for example, a reflex value or a value calculated from wavefront aberration may be used, or a value stored in advance in the memory 240 or a value input from the input unit 270 may be used. Good.

Next, the calculation unit 210 obtains CL / corneal aberration W _CLCO by a ray tracing method or the like using the measured corneal shape and given contact lens data (curvature of front and rear surfaces, refractive index, etc.). (S2237). The “ray tracing method” refers to a state of a light region that passes through an optical system, and is a method that is obtained geometrically by calculation, and a commonly used method can be used. For example, appropriate software that is commercially available can be used, but is not limited thereto. The calculation unit 210 can simulate CL and corneal aberration when the contact lens is worn, for example, as an air-contact lens-cornea (refractive index: 1.3375) as an optical system. Further, the spherical power and astigmatic power at this time can be calculated. As a simulation, the calculation unit 210 responds to infinity, or the spherical power obtained from the movement amount of the first illumination optical system 10 and the first light receiving optical system 20 or the spherical power obtained from the eyeball optical system aberration W _eye . This can be done with a light source at the focal position of the eye.

  In addition, in consideration of the tear film, the aberration caused by the optical system including the CL, the tear film, and the front surface of the cornea when the contact lens is worn can be calculated by ray tracing. Similar to the above, the analysis is performed assuming that the shape of the contact lens is maintained in the case of a hard contact lens, and that it is affected by the shape of the cornea in the case of a soft contact lens. The thickness of the tear film can be set to 2 μm, for example, but is not limited to this and may be a predetermined thickness. The contact lens material (refractive index), thickness, front shape before wearing, and rear shape are stored in the front shape table and / or the rear shape table for each type of contact lens (contact lens ID). .

  For example, the calculation unit 210 can simulate CL and corneal aberration when the contact lens is worn as an air-contact lens-tear fluid layer (refractive index 1.337) -cornea (refractive index 1.3375) as an optical system. The spherical power and astigmatic power at this time can be calculated. The tear film can be assumed to have a predetermined thickness based on the corneal shape and the rear surface shape of the contact lens.

Further, the calculation unit 210 assumes that only CL / corneal spherical aberration (C ₄ ⁰ , C ₆ ⁰ ,...) Occurs instead of ray tracing, for example, the shape for light ray tracing, the refractive index, etc. The aberration W _CLCO corresponding to the shape, refractive index, etc. may be obtained by referring to a table storing spherical aberrations calculated in advance corresponding to the predetermined data.

In addition, when using a hard contact lens with astigmatism correction, the aberration W _CLCO may be calculated by ray tracing in consideration of astigmatism and the like. Alternatively, a table storing astigmatism and the like calculated in advance may be _provided , and the aberration W _CLCO may be obtained with reference to this table. Note that the aberration W _CLCO may be obtained in consideration of a plurality of spherical aberrations, astigmatisms, and the like. Further, the above-described processing is not limited to hard contact lenses, and may be executed similarly for soft contact lenses.

FIG. 34 is a processing flow in the case of a soft contact lens.
Next, processing in the case of a soft contact lens will be described. In the case of a soft contact lens, the shape of the contact lens is considered to be deformed along the corneal shape, and the shape can be calculated taking into account that the front surface shape at each position changes by the thickness of the soft contact lens. .

  First, the calculation unit 210 selects a contact lens ID (S2251). The arithmetic unit 210 can input the contact lens ID from the input unit 270, for example, as described above. The computing unit 210 determines the rear surface shape of the contact lens according to the corneal shape, assuming that the rear surface shape of the contact lens to be worn fits (or substantially fits) with the determined corneal shape of the eye to be examined (S2253). Also, for example, if the contact lens is rigid, what percentage of the corneal shape is to be corrected is stored in advance as data, and the shape corresponding to the ratio may be corrected. .

  For example, in correspondence with the contact lens ID, there is a correction table storing an experience value (%) indicating what percentage of the cornea shape is corrected, and the calculation unit 210 is based on the set contact lens ID. The corresponding experience value is read with reference to the correction table, and the rear surface shape when the contact lens is worn is obtained based on the cornea shape and the read experience value. At this time, spherical aberration is not subject to correction, but is not limited thereto. As in the case of the hard contact lens described above, the calculation unit 210 responds by referring to the rear surface shape table based on the selected contact lens ID and the corneal shape or kerato value obtained in step S2105. Rear surface shape data may be acquired.

  Next, the computing unit 210 refers to the front surface shape table based on the selected contact lens ID, the obtained rear surface shape, and the provisional spherical power, and obtains the front shape of the contact lens (S2255). As the provisional spherical power, for example, a reflex value or a value calculated from wavefront aberration may be used, or a value stored in advance in the memory 240 or a value input from the input unit 270 may be used. Good. The calculation unit 210 adds, for example, the amount of change in the rear surface of the contact lens, which has changed from the front shape to the shape corresponding to the corneal shape, to the front shape, assuming that the shape of the contact lens fits the measured corneal shape. Can be. Also, for example, if the contact lens is rigid, what percentage of the corneal shape is to be corrected is stored in advance as data, and the shape corresponding to the ratio may be corrected. .

  For example, in correspondence with the contact lens ID, there is a correction table storing an experience value (%) indicating what percentage of the cornea shape is corrected, and the calculation unit 210 is based on the set contact lens ID. The corresponding experience value is read with reference to the correction table, and the front shape when the contact lens is worn is obtained based on the cornea shape and the read experience value. At this time, spherical aberration is not subject to correction, but is not limited thereto.

Next, the calculation unit 210 acquires a corresponding curvature, refractive index, and the like from the selected contact lens ID, the obtained rear surface shape, and the obtained front surface shape (S2257).
In the same manner as described above, the calculation unit 210 can simulate CL and corneal aberrations when a contact lens is worn, for example, an air-contact lens-cornea as an optical system. Further, the calculation unit 210 can simulate CL and corneal aberration when the contact lens is worn as an air-contact lens-tear film-cornea as an optical system.

Next, the calculation unit 210 obtains CL and corneal aberration W _CLCO including the contact lens and the cornea by, for example, ray tracing according to the acquired data such as the curvature and the refractive index and the obtained front surface shape (S2259). As ray tracing, the calculation unit 210 responds to infinity or the spherical power obtained from the spherical power obtained from the movement amount of the first illumination optical system 10 and the first light receiving optical system 20 or the eyeball optical system aberration W _eye. This can be done with a light source at the focal position of the eye. For ray tracing, generally available software can be used. The input data in ray tracing is, for example, the radius of curvature of each surface, the refractive index, the shape data, and the surface spacing. The shape data can be represented by, for example, Zernike coefficients. Assuming that only spherical aberrations (C ₄ ⁰ , C ₆ ⁰ ,...) Occur, a spherical aberration calculated in advance has a table stored corresponding to the curvature, refractive index, frontal shape, etc. The unit 210 may obtain the aberration by referring to this instead of tracing the ray.

Returning to FIG. 7, in step S2205, the calculation unit 210 adds the CL and corneal aberration W _CLCO to the intraocular aberration W _inter to obtain the corrected ocular optical system aberration W _correct (S2205).
Corrected eye optical system aberration W _correct = intraocular aberration W _inter + CL / corneal aberration W _CLCO
The corrected eye optical system aberration W _correct obtained here indicates the aberration of the optical system including the eye to be examined and the contact lens when the contact lens is worn.

Returning to FIG. 6, the arithmetic unit 210 performs a corrected image simulation (S2107). The calculation unit 210 executes a correction image simulation based on the obtained aberration of the correction eye optical system to obtain an optimum prescription value when the contact lens is worn. For example, the calculation unit 210 obtains appropriate correction data using any one or more of Strehl ratio, PTF, and MTF (Modulation Transfer Function) as an evaluation parameter representing the quality of appearance of the eye 60 to be measured. Further, for example, the calculation unit 210 may simulate the appearance of the optometric target and obtain appropriate correction data using the comparison result with a predetermined template as an evaluation parameter. Details of step S2107 will be described later.
The calculation unit 210 outputs the data to the display unit 230 and the memory 240 (S2109). If data has already been output in the previous process, the process in step S2109 may be omitted.

4-2 Measurement of Pupil Diameter, Corneal Data, and Ocular Optical System Data FIG. 8 is a sub-flowchart for calculation of pupil diameter, measurement of corneal data, and ocular optical system data in step S2105. FIG. 9 is an explanatory diagram of pupil diameter calculation. Note that the calculation of the pupil diameter can be omitted, and a predetermined diameter (for example, φ4 mm) or the diameter of the daytime of each eye 60 to be measured can be used.

  First, the calculation unit 210 acquires a Hartmann image and an anterior segment image from the first light receiving unit 20 and the second light receiving unit 35 (S601). The arithmetic unit 210 causes the fifth light source unit 91 to illuminate the eye 60 under illumination in a desired environmental condition, and acquires a Hartmann image and an anterior eye image from the first light receiving unit 20 and the second light receiving unit 35. . For example, the calculation unit 210 may display an instruction for selecting an environmental condition for obtaining correction data on the display unit 230 and input the selected environmental condition from the input unit 270. The environmental conditions include, for example, “daytime vision”, “dusk vision”, “indoor (under fluorescent light)”, “night vision”, “normal visual acuity measurement”, and the like. Next, for example, the calculation unit 210 refers to a table in which the environmental condition and the illumination state stored in advance in the memory 240 correspond to each other, and acquires the illumination state corresponding to the input environmental condition. Illumination conditions under each environmental condition include, for example, 50 [lx] for “normal vision measurement”, 100,000 [lx] for “daytime vision”, 2000 [lx] for “indoor (under fluorescent lamp)”, and the like. It can be. As these values, appropriate values according to the environmental conditions can be used. As an environment, it is desirable to use a fixation target larger than usual. Here, the eye to be measured 60 is illuminated by the fifth light source unit 91 in an illumination state under a desired environmental condition. However, the illumination state is created by using illumination around the eye to be examined and illumination of the background. It may be configured as described above.

  The calculation unit 210 outputs a signal (11) corresponding to the acquired illumination state to the fifth light source unit 91 via the control unit 220 to illuminate the eye 60 to be measured. In addition, the calculation unit 210 can sequentially change the illumination state from the darker to the brighter, and acquire a Hartmann image and an anterior ocular segment image in a plurality of illumination states.

  The calculation unit 210 omits step S601 and includes Hartmann image data measured in advance and stored in the memory 240, an anterior ocular segment image, a pupil shape such as a point on the pupil edge, and a pupil diameter. Pupil diameter data may be read. Further, for example, the calculation unit 210 may read the photographic data that has been taken in the past and stored in the memory 240 in the electronic medical record as pupil diameter data, and obtain an anterior ocular segment image.

Next, the calculation unit 210 (for example, the pupil diameter measurement unit 215, the same as in the following step S607) calculates the point P _i (i = 1 to n) on the edge of the pupil based on the acquired anterior segment image. For example, 36 points (n = 36) are detected (S603). The calculation unit 210 can detect a change in the amount of light (shading on the image) of the acquired anterior ocular segment image and obtain a point on the edge of the pupil by an image processing method. In FIG. 9, the detection point P _i is a point represented by a + mark.

Next, the calculation unit 210 performs ellipse fitting that best fits the detected point on the edge of the pupil (S605). First, the calculation unit 210 obtains the focal point of the ellipse (points F1 and F2 in FIG. 9). For example, the calculation unit 210 reads the coordinates of two points set in advance as the initial focus value from the memory 240. Next, the calculation unit 210 obtains the distances from the detection point P _i to the two points read out and sets the sum of the distances to L _i . The calculation unit 210 calculates the sum L _i of the distances for all the detection points P _i and calculates the average value A of L _i . Further, the arithmetic unit 210 uses a method such as least square approximation to calculate the two points at which the sum of distances L _i represented by the following equation and the square error Se of the average value A are minimum, thereby obtaining an elliptical shape. The focus can be sought.

ただし、Ｌ_ｉ：エッジ上の点Ｐ_ｉから２点Ｆ１、Ｆ２までの距離の和、Ａ：エッジ上の各点におけるＬ_ｉの平均値、ｎ：検出したエッジ上の点数である。なお、これ以外にも適宜の方法により、楕円の焦点を求めてもよい。

However, _{L i:} the sum of the distance from the point _{P i} on the edge to the two points F1, F2, A: the average value of _{L i} at each point on the edge, n: is the number of the detected edge. In addition, the focal point of the ellipse may be obtained by an appropriate method.

  Next, the calculation unit 210 calculates a sum L of distances from one point on the ellipse to the focal point (F1 and F2). Note that the arithmetic unit 210 may use the above average value A as the sum L of the distances from one point on the ellipse to the focal point. Next, the calculation unit 210 calculates the pupil diameter from the length (major axis) and the minor axis (minor axis) of the major axis of the ellipse (S607). The major axis length 2a and the minor axis length 2b can be expressed by the following equations.

ただし、Ｌ：エッジ上の点から焦点までの距離の和、（ｘ１、ｙ１）、（ｘ２、ｙ２）：楕円の焦点である。瞳径ｄ_ｐは、例えば、長軸の長さ２ａ及び短軸の長さ２ｂの平均値とすると、次式で表される。

Where L: the sum of the distance from the point on the edge to the focal point, (x1, y1), (x2, y2): the elliptical focal point. The pupil diameter d _p is expressed by the following equation, for example, when the average value of the long axis length 2a and the short axis length 2b is used.

なお、平均値を瞳径とする以外にも、短軸の長さ、長軸の長さ、短軸及び長軸の長さの中間値等、長軸の長さ２ａ、短軸の長さ２ｂに基づく適宜の値を用いてもよい。

In addition to taking the average value as the pupil diameter, the length of the major axis 2a, the length of the minor axis, such as the length of the minor axis, the length of the major axis, the intermediate value of the minor axis and the major axis length, etc. An appropriate value based on 2b may be used.

In addition to the illumination state in which the pupil diameter is in the daytime, the calculation unit 210 is in the illumination state in which the pupil diameter is set in the environment desired by the subject (for example, in an office, a classroom, or during night driving). Alternatively, the brightness of the fifth light source unit 91 may be adjusted. Thereby, the optimal prescription value in the environment which a subject desires can be analyzed. Note that the calculation unit 210 may read a pupil diameter (for example, φ4 mm) stored in advance in the memory 240 instead of the processing in steps S603 to S607.
The calculation unit 210 (for example, the cornea / contact lens data calculation unit 212) calculates corneal data (S608).

FIG. 10 is a flowchart showing corneal data calculation. With reference to FIG. 10, the process in step S608 described above will be described in detail.
First, based on the signal from the second light receiving unit 35 (acquired anterior segment image), the calculation unit 210 uses the corneal apex as a reference, and shows a corneal shape that indicates the height of the corneal shape according to the light receiving position of the placido ring. The data of the map (height map) is calculated (S301). The calculation unit 210 calculates the shape of the reference spherical surface that fits as much as possible to the corneal shape obtained in step S301 (S302). Thereby, the calculation accuracy of the Zernike coefficient can be improved. It should be noted that it is sufficient to obtain a necessary portion according to the measurement range (for example, φ3, φ7 or the obtained pupil diameter).

  Next, the calculation unit 210 subtracts the reference spherical component from the corneal shape components (height map, height data) (S303). Thereby, the residual component of only the difference from the reference spherical surface is obtained. The calculation unit 210 calculates the spherical aberration of the reference spherical surface (S304). The calculation unit 210 calculates the wavefront aberration of the residual component obtained in step S303 (S305). When calculating wavefront aberration from a corneal shape component, the converted refractive index of the cornea (1.3375) or the refractive index of the cornea calculated by some method is used. In addition, the first measurement mode for calculating the Zernike coefficient after combining the wavefront aberration of the measurement wavefront and the reference spherical surface, the Zernike coefficient is obtained for each aberration of the wavefront aberration of the measurement wavefront and the reference spherical surface, and the Zernike coefficient is calculated. Selection is made between the second measurement modes to be combined (S306). If the first measurement mode is selected (S306), the process proceeds to step S307. If the second measurement mode is selected (S306), the process proceeds to step S309.

In the first measurement mode, and the wavefront aberration of the reference spherical surface obtained in step S304, after the addition of wavefront aberration of the residual component obtained in step S305, it obtains their wavefront aberrations as corneal wavefront aberration W _CO (S307 ). Further, the Zernike coefficient of the corneal wavefront aberration obtained in step S307 is calculated (S308). This Zernike coefficient indicates corneal aberration.

  On the other hand, when the second measurement mode is selected in step S306, a Zernike coefficient is calculated from the wavefront aberration of the reference spherical surface (S309). Next, a Zernike coefficient is calculated from the wavefront aberration of the residual component obtained in step S305 (S310). A corneal aberration is obtained by synthesizing the Zernike coefficients obtained in steps S309 and S310 (S311).

In addition to calculating corneal data by executing steps S301 to S311 described above, the calculation unit 210 generates a corneal shape map (Height Map) indicating the height of the corneal shape according to the light receiving position of the placido ring. Suppose that the light source is located at the focal position of the eye according to the spherical power obtained from the calculated spherical power obtained from the amount of movement of the first illumination optical system 10 and the first light receiving optical system 20 or from the eyeball optical system aberration W _eye. The corneal aberration _Wco can also be calculated by making a light beam incident on a cornea having a map of the cornea shape and tracing the light. For ray tracing, generally available software can be used. The input data in ray tracing is, for example, the radius of curvature of each surface, the refractive index, the shape data, and the surface spacing. The shape data can be represented by, for example, Zernike coefficients. In the present embodiment, as an example, data obtained by calculating the shape of the front surface of the cornea with a Zernike coefficient is used. It is also possible to analyze the Height Map into a Zernike polynomial and use the analyzed data for ray tracing. Note that the arithmetic unit 210 may obtain the kerato value at an appropriate timing.

Returning to FIG. 8, the calculation unit 210 (for example, the wavefront aberration calculation unit 211) calculates eyeball optical system data based on the pupil diameter and the Hartmann image (S609). Here, the eyeball optical system indicates an optical system of the entire eye to be measured. First, the calculating part 210 detects the gravity center point of each spot from the Hartmann image acquired at step S601. Next, the arithmetic unit 210, normalized with the pupil radius r _p of the detected center of gravity coordinates. Here, pupil radius r _p = pupil diameter d _p / 2. That is, the arithmetic unit 210, when the center coordinates of the pupil of the pupil radius _{r p} (0, 0), the center of gravity _P s (X, Y) within the range of the pupil diameter of _P s (X / r _p , Y / r _p ), and when the center of gravity of the spot of the Hartmann image is P _s , the reference grid point P _ref (X _ref , Y _ref ) corresponding to this point is _designated as P _ref (x _ref / r _p , y _ref / r _p ). The actual wavefront (wavefront whose coordinates are not normalized) W (X, Y) is expressed by the following equation.

ここで、（Ｘ、Ｙ）：規格化されていない座標、（ｘ_ｓ、ｙ_ｓ）：規格化された座標である。
演算部２１０は、規格化した座標を用いて、ゼルニケ係数、全波面収差等の眼球光学系データを算出する。また、演算部２１０は、適宜のタイミングでデータをメモリ２４０に記憶する。

Here, (X, Y): non-standardized coordinates, (x _s , y _s ): standardized coordinates.
The calculation unit 210 calculates eyeball optical system data such as Zernike coefficients and total wavefront aberration using the standardized coordinates. The arithmetic unit 210 stores data in the memory 240 at an appropriate timing.

4-3 First Flowchart of Corrected Image Simulation FIG. 11 shows a flowchart of the corrected image simulation in step S2107.
The calculation unit 210 (for example, the correction data calculation unit 213) calculates the best image condition (S201). As will be described later in detail, the calculation unit 210 obtains low-order Zernike coefficients and obtains correction correction data so that the Strehl ratio is maximized or the phase shift is minimized. The correction correction data includes, for example, appropriate data among coefficients corresponding to defocus, astigmatism components, S, C, A, higher order spherical aberration, higher order astigmatism, higher order coma aberration, Strehl ratio, and the like. Can be mentioned.

  Based on the wavefront aberration W (x, y) at the time of the best image condition obtained in S201, the calculation unit 210 (for example, the simulation unit 214, and so on until step S215) calculates the pupil function f from the W (x, y). (X, y) is calculated by the following equation (S203).

The calculation unit 210 calculates the luminance distribution function Land (x, y) of the Landolt ring (or any image) with reference to the memory 240 (S205). The calculation unit 210 obtains a spatial frequency distribution FR (u, v) by performing two-dimensional Fourier transform on Land (x, y) (S207). The computing unit 210 multiplies the spatial frequency distribution FR (u, v) of the Landolt ring (or any image) and the spatial frequency distribution OTF (u, v) of the eyeball as shown in the following equation, so that the optical system of the eye The frequency distribution OR (u, v) after passing is obtained (S209).
FR (u, v) × OTF (u, v) → OR (u, v)

  Next, the calculation unit 210 obtains a luminance distribution image LandImage (X, Y) of the Landolt ring (or any image) by performing two-dimensional inverse Fourier transform on OR (u, v) (S211). The calculation unit 210 displays LandImage (X, Y) and PSF (X, Y) on the display unit 230 by an appropriate display method such as a figure, graphic data, a graph, and / or a numerical value, and appropriately stores the data in the memory 240. (S213). The calculation unit 210 reads the correction correction data from the memory 240 as necessary and outputs it to the display unit 230 (S215).

(Correction data calculation based on Strehl ratio)
FIG. 12 shows a flowchart for the first example of the best image condition calculation. FIG. 12 is a detailed flowchart (1) regarding step S201 described above.
First, the calculation unit 210 sets a threshold value for each aberration amount RMS _i ^2j-i as a branching condition (S401). For example, this threshold value can be a sufficiently small value (eg, 0.1) of aberration. The calculation unit 210 calculates the Zernike coefficient C _i ^2j-i from the obtained corrected eye optical system aberration W _correct and converts it to the aberration amount RMS _i ^2j-i by the following equation (S403).

The computing unit 210 determines whether at least one of the values of RMS _i ^2j-i (i> 2) is equal to or greater than a threshold value (S405). If NO is determined here, the process proceeds to step S419. On the other hand, when the determination is Yes, the calculation unit 210 executes the next process.

That is, the calculation unit 210 determines whether at least one of the higher-order spherical aberration amounts R ₄ ⁰ , R ₆ ⁰ ... Of the aberration amount RMS (R _i ^2j−i ) is equal to or greater than a threshold value (S407). Here, in the case of Yes, the calculation unit 210 changes the coefficient (C ₂ ⁰ ) corresponding to aberration defocusing so that the Strehl ratio is maximized (S409). On the other hand, in the case of No, the calculation unit 210 proceeds to step S411. In order to vary varying the contact lens shape for changing the coefficients C ₂ ⁰ corresponding to spherical power also other aberrations, approximately coefficients C _{4 ^0,} the change amount of the C ₆ ⁰ in this case added Can respond. On the other hand, the optimum in order to obtain the correction value _to calculate the CL · corneal aberration _{W CLCO} each time changing the _C ^{2 0,} and by re-calculating a corrective eye optical system aberration _{W correct,} corrective value with high precision Can also be requested. For example, each step shown in FIG. 7 described above can be performed to calculate the corrected eye optical system aberration W _correct .

Next, the calculation unit 210 determines whether at least one of the asymmetric high-order coma-like aberration components RMS _i ^2j-i (i: odd number) is equal to or greater than a threshold value (S411). Here, in the case of Yes, the arithmetic part 210 changes the coefficient (C ₂ ⁰ ) corresponding to aberration defocusing so that the Strehl ratio is maximized (S 413), while in the case of No, the operation proceeds to Step S 414. Note, again as in step S409 described above, it is possible to deal with addition of C _{4 ^0,} the change amount of the C ₆ ⁰ of approximately this time, also, in order to obtain the optimum correction value, C ₂ It is also possible to obtain a correction value with high accuracy by calculating CL / corneal aberration W _CLCO each time ⁰ is changed and recalculating the correction eye optical system aberration W _correct .

  Next, the calculation unit 210 determines whether to correct astigmatism (S414). For example, whether or not to perform astigmatism correction may be set in advance, or an instruction as to whether or not to perform astigmatism correction may be input from the input unit. When it is determined that the astigmatism correction is performed (S414), the calculation unit 210 proceeds to step S415, and when it is determined that the astigmatism correction is not performed (S414), the process proceeds to step S419.

In step S415, the calculation unit 210 determines whether at least one of the high-order astigmatism amounts RMS _i ^2j-i (i: even number and 2j−i ≠ 0) is equal to or greater than a threshold value (S415). Here, in the case of Yes, the arithmetic part 210 adds astigmatism components (C ₂ ⁻² , C ₂ ² ) to the aberration so that the Strehl ratio is maximized (S 417), while in the case of No, the operation proceeds to step S 419.

  Thus, the calculation unit 210 calculates OTF (u, v) and PSF (X, Y) from the aberration, and further corrects correction correction data (coefficient corresponding to defocus, astigmatism component, S, C, A, higher order from the Zernike coefficient. Appropriate data such as spherical aberration, higher-order astigmatism, higher-order coma aberration, Strehl ratio, etc.) are calculated and stored in the memory 240 (S419).

  It should be noted that any one of the sets of steps S407 and S409, S411 and S413, S415 and S417 may be omitted so that only a desired component of the defocus and astigmatism components is corrected. Steps may be added to correct for appropriate higher order aberrations or Zernike coefficients. For example, when fourth-order spherical aberration is mainly included in high-order aberration, correction correction data can be obtained by correcting in a direction to increase the defocus amount corresponding to low-order aberration.

Next, detailed processing in steps S409, S413, and S417 will be described. In each step, the arithmetic unit 210 executes processing as follows.
The calculation unit 210 has an aberration equivalent to the high-order aberration amount from the threshold value of the high-order aberration amount (RMS ₄ ⁰ , RMS ₆ ⁰ ...) That was noticed one time before in the flow in order to obtain a more optimal image plane. A low-order Zernike coefficient C _i ^2j−i (1 ≦ i ≦ 2) at each step of interest is added to the wavefront aberration W (x, y). For example, _C ² ₀ In step _{S409, C} ^{2 0} In step S413, _C ² -2 At step _S417, a _C ^{2 2.}
Further, the pupil function f (x, y) is obtained from the wavefront aberration W (x, y) as follows.
f (x, y) = e ^{ikW (x, y)}
(I: imaginary number, k: wave vector (2π / λ), λ: wavelength)
Here, W (x, y) is a corrected eye optical system aberration W _correct or a wavefront aberration obtained by changing the aberration so that the Strehl ratio is maximized. Further, the arithmetic unit 210 obtains the point image amplitude distribution U (u, v) by the Fourier transform of the pupil function f (x, y) as the following equation.

（λ：波長
Ｒ：瞳から像点（網膜）までの距離
（ｕ，ｖ）：像点Ｏを原点とし，光軸に直行する面内での座標値
（ｘ，ｙ）：瞳面内の座標値）
演算部２１０は、Ｕ（ｕ，ｖ）とその複素共役を掛けて、次式により点像強度分布（ＰＳＦ）であるＩ（ｕ，ｖ）を求める。
Ｉ（ｕ，ｖ）＝Ｕ（ｕ，ｖ）Ｕ^＊（ｕ，ｖ）

(Λ: wavelength R: distance from pupil to image point (retina) (u, v): coordinate value (x, y) in plane perpendicular to optical axis with image point O as origin Coordinate value)
The arithmetic unit 210 multiplies U (u, v) and its complex conjugate to obtain I (u, v) which is a point image intensity distribution (PSF) by the following equation.
I (u, v) = U (u, v) U ^* (u, v)

The Strehl ratio is calculated by assuming that the center intensity of the PSF when there is no aberration (W (X, Y) = 0) is I ₀ (0,0).
Strehl ratio = I (0,0) / I ₀ (0,0)
Defined in
In the first example, the calculation unit 210 recursively or analytically obtains a value of a low-order Zernike coefficient C _i ^2j−i (1 ≦ i ≦ 2) that maximizes the Strehl ratio value.

(Calculation of correction data based on phase shift)
FIG. 13 shows a flowchart for the second example of the best image condition calculation.
First, the calculation unit 210 sets a threshold value of each aberration amount RMS _i ^2j-i as a branching condition (S501). For example, this threshold value is set to a sufficiently small value of aberration (eg, 0.1).

The calculation unit 210 calculates the Zernike coefficient C _i ^2j-i from the obtained corrected eye optical system aberration W _correct and converts it to the aberration amount RMS _i ^2j-i using the formula shown in the first example (S503). The computing unit 210 determines whether at least one of the values of RMS _i ^2j-i (i> 2) is equal to or greater than a threshold value (S505). Here, if it is determined No, the process proceeds to step S519. On the other hand, when the determination is Yes, the calculation unit 210 executes the next process.

That is, the calculation unit 210 determines whether at least one of the higher-order spherical aberration amounts R ₄ ⁰ , R ₆ ⁰ ... Is equal to or greater than a threshold value (S507). Here, in the case of Yes, the calculation unit 210 changes the coefficient (C ₂ ⁰ ) corresponding to aberration defocusing so as to eliminate the phase shift as much as possible (S509). On the other hand, in the case of No, the processing unit 210 proceeds to step S511.

In order to vary varying the contact lens shape for changing the coefficients C ₂ ⁰ corresponding to spherical power also other aberrations, approximately coefficients C _{4 ^0,} the change amount of the C ₆ ⁰ in this case added Can respond. On the other hand, the optimum in order to obtain the correction value _to calculate the CL · corneal aberration _{W CLCO} each time changing the _C ^{2 0,} and by re-calculating a corrective eye optical system aberration _{W correct,} corrective value with high precision Can also be requested. For example, each step shown in FIG. 7 described above can be performed to calculate the corrected eye optical system aberration W _correct .

Next, the calculation unit 210 determines whether at least one of the higher-order coma-like aberration components R _i ^2j-i (i: odd number) is greater than or equal to a threshold value (S511). Here, in the case of Yes, the arithmetic part 210 changes the coefficient (C ₂ ⁰ ) corresponding to the defocus to the aberration so as to eliminate the phase shift as much as possible (S513). On the other hand, in the case of No, the operation proceeds to step S515. Note, again as in step S509 described above, can be made to correspond by adding C _{4 ^0,} the change amount of the C ₆ ⁰ of approximately this time. Further, the optimum in order to obtain the correction value _to calculate the CL · corneal aberration _{W CLCO} each time changing the _C ^{2 0,} and by re-calculating a corrective eye optical system aberration _{W correct,} corrective value with high precision Can also be requested.

  Next, the calculation unit 210 determines whether to correct astigmatism (S514). For example, whether or not to perform astigmatism correction may be set in advance, or an instruction as to whether or not to perform astigmatism correction may be input from the input unit. When it is determined that the astigmatism correction is to be performed (S514), the calculation unit 210 proceeds to step S515, and when it is determined that the astigmatism correction is not to be performed (S514), the process proceeds to step S519.

In step S515, the calculation unit 210 determines whether at least one of the high-order astigmatism amounts R _i ^2j−i (i: even number and 2j−i ≠ 0) is equal to or greater than a threshold value (S515). Here, in the case of Yes, the arithmetic part 210 adds astigmatism components (C ₂ ⁻² , C ₂ ² ) to the aberration so as to eliminate the phase shift as much as possible (S517), while in the case of No, the operation proceeds to step S519.

  In this way, the calculation unit 210 calculates OTF (u, v), PSF (X, Y) from the aberration, and further corrects correction data (coefficient corresponding to defocus, astigmatism component, S, C, A, higher order from the Zernike coefficient. Appropriate data such as spherical aberration, higher-order astigmatism, higher-order coma aberration, and PTF) are calculated and stored in the memory 240 (S519).

  It should be noted that any of the combinations of steps S507 and S509, S511 and S513, S515 and S517 may be omitted so that only a desired component of the defocus and astigmatism components is corrected. Steps may be added to correct for appropriate higher order aberrations or Zernike coefficients.

Next, detailed processing in steps S509, S513, and S517 will be described. The calculation unit 210 performs processing as follows.
First, as described in the detailed processing in steps S409, S413, and S417, the calculation unit 210 obtains a point image intensity distribution (PSF) from an objective wavefront expression calculated from Zernike coefficients. Next, the arithmetic part 210 calculates | requires OTF by Fourier-transforming (or autocorrelation) and normalizing PSF like following Formula.

一般に空間周波数領域の振幅と位相の分布Ｒ（ｒ，ｓ）は複素数になり、実数部Ａ（ｒ，ｓ）、虚数部Ｂ（ｒ，ｓ）とすれば、
Ｒ（ｒ，ｓ）＝Ａ（ｒ，ｓ）＋ｉＢ（ｒ，ｓ）
となり、位相のずれ（位相シフト、ＰＴＦ）は、

In general, the amplitude and phase distribution R (r, s) in the spatial frequency domain is a complex number. If the real part A (r, s) and the imaginary part B (r, s) are given,
R (r, s) = A (r, s) + iB (r, s)
The phase shift (phase shift, PTF) is

で計算できる。第２の例では、演算部２１０は、このＲ（ｒ，ｓ）が極値を持つ値をできる限り高周波に持っていくような即ち、位相シフトができる限りなくなるような低次ゼルニケ係数Ｃ_ｉ ^２ｊ−ｉの値を再帰的、或いは解析的に求める。

It can be calculated with In the second example, the arithmetic unit 210 takes a value having an extreme value of R (r, s) as high as possible, that is, a low-order Zernike coefficient C _i that eliminates the phase shift as much as possible. The value of ^2j-i is obtained recursively or analytically.

  In the first and second examples of the best image condition calculation described above, a condition in which the Strehl ratio is large and the phase shift is small may be obtained by performing both processes.

5). Modified example of measurement flow (correction eye optical system simulation-2)
FIG. 14 is a sub-flowchart of the correction eye optical system simulation-2 in step S2106. The process shown in FIG. 14 can be used, for example, in the case of correction using glasses. For example, the calculation unit 210 obtains the corrected optical system aberration W _correct after correction by removing the secondary aberration from the aberration W _eye of the eyeball optical system measured in step S2105. The obtained correction optical system aberration W _correct represents, for example, an aberration after correction by glasses. At this time, if the higher-order aberration W _{glass of the} glasses is known, it may be added, and W _correct obtained by accurately calculating the aberration when actually wearing the glasses may be calculated.

(Modification of main flow (1))
FIG. 15 shows a modification (1) of the flowchart of the correction data measurement for contact lens wear. The flow shown in FIG. 15 executes the above-mentioned correction eye optical system simulation-1 for contact lenses and the above-mentioned correction eye optical system simulation-2 for eyeglasses as correction eye optical system simulations. A correction image simulation is executed for each of the glasses. Thereby, for example, both correction using contact lenses and correction using glasses can be displayed, and both corrections can be compared. In addition, about the process similar to the process shown in FIG. 6, the same code | symbol as FIG. 6 is attached | subjected and the detailed description is abbreviate | omitted.

First, the calculating part 210 performs the process of step S2101-S2105. Next, the arithmetic part 210 executes correction eye optical system simulation-1 and correction eye optical system simulation-2, respectively (S2406). Here, for example, the calculation unit 210 performs the correction eye optical system aberration W _correct (first correction eye optical system aberration) obtained by executing the correction eye optical system simulation-1 shown in FIG. The correction eye optical system aberration W _correct (second correction eye optical system aberration) obtained by executing the correction eye optical system simulation-2 shown in FIG.

Next, the calculation unit 210 performs a correction image simulation (S2407). For example, the calculation unit 210 executes correction image simulation based on the first correction eye optical system aberration stored in the storage unit in the same manner as in step S2107 described above to perform correction data and / or appearance condition by contact lens correction. Further, based on the second correction eye optical system aberration stored in the storage unit, correction image simulation is executed in the same manner as in the above-described step S2107, and correction data and / or appearance degree by eyeglass correction is calculated.
The calculation unit 210 displays the contact lens correction and eyeglass correction data and / or appearance obtained in step S2407 on the display unit or outputs them to the output unit (S2409).

(Modification of main flow (2))
FIG. 16 shows a modification (2) of the flowchart of the correction data measurement for contact lens wear. Wear the type of CL you want to examine, measure the eyeball optical system, corneal aberration (contact lens front aberration) _WCL , and add aberrations (for example, spherical aberration) generated by shifting the spherical power from there. Then, W _correct is calculated again, and the same processing as described above is performed. In addition, about the process similar to the process shown in FIG. 6, the same code | symbol as FIG. 6 is attached | subjected and the detailed description is abbreviate | omitted.

  First, the calculating part 210 performs the process of step S2101-S2105. In step S2105, the corneal aberration (contact lens front aberration) is calculated using the refractive index of the worn contact lens without using the refractive index of the cornea. The corneal shape in step S2105 corresponds to the contact lens front surface shape in the present modification, and the corneal aberration in step S2105 corresponds to the aberration (for example, front aberration) of the contact lens in the present modification. Next, the calculation unit 210 executes the correction eye optical system simulation-3 or the correction eye optical system simulation-4 (S2106). Details of the processing will be described later. Next, the calculating part 210 performs the process of step S2107 and S2109.

(Correction eye optical system simulation-3)
FIG. 17 is a sub-flowchart of the correction eye optical system simulation-3. FIG. 17 is a flowchart in a case where higher-order aberrations also change when the CL power is changed.
First, the calculation unit 210 (for example, the correction data calculation unit 213, the same applies to step S2507 below) sets the spherical power of the contact lens after the change (S2502). For example, the calculation unit 210 may input the spherical power from the input unit, or input an instruction to increase or decrease the spherical power based on the measured aberration or the like from the input unit, and according to the input instruction A spherical power may be set.

The calculation unit 210 obtains an aberration W _{CL NEW} generated by shifting the spherical power of the front surface of the contact lens after the change (S2503). The contact lens front surface shape after the change is known by referring to the front surface shape table based on the contact lens ID, the set spherical power, and the rear surface shape data. Therefore, the contact indicating the height of the contact lens front surface shape Data of the lens front surface shape map (height map) is calculated, and can be calculated in the same manner as when the contact lens front surface aberration is calculated in step S2105. Alternatively, it can be calculated by the ray tracing method because the shape and refractive index are known. The calculation unit 210 may obtain a difference between the set spherical power and the spherical power of the contact lens worn, and may obtain an aberration corresponding to the difference. Next, the calculation unit 210 calculates the corrected W _{CL correct} by taking the difference between the calculated W _{CL NEW} and the aberration W _CL of the wearing _CL (S2505).
W _{CL correct} = W _{CL New} -W _CL

The calculation unit 210 adds the obtained W _{CL correct} to the eyeball optical system aberration W _eye obtained in S2105 to obtain a corrected eye optical system aberration W _correct (S2507).
Corrected eye optical system aberration W _correct = W _eye + W _{CL correct}

(Correction eye optical system simulation-4)
FIG. 18 is a sub-flowchart of the correction eye optical system simulation-4. FIG. 18 is a flowchart when it is assumed that the high-order aberration does not change when the power of CL is changed.
The calculation unit 210 (for example, the correction data calculation unit 213, the same applies to step S2517 below) sets the spherical power of the contact lens to be worn (S2512). The computing unit 210 obtains a deviation amount between the spherical power based on the wavefront aberration obtained by the wavefront aberration computing unit 211 and the spherical power of the set contact lens, and based on the obtained deviation amount of the spherical power, An aberration W _{CL NEW} generated by the deviation is obtained (S2513).

The calculation unit 210 obtains a corrected aberration W _{CL correct} by taking a difference between the obtained aberration W _{CL NEW} and the obtained aberration W _CL of the correction optical system (S2515).
The calculation unit 210 adds the secondary aberration of the eyeball optical system aberration W _eye obtained in S2105 and the obtained W _{CL correct} to obtain a corrected eye optical system aberration Wcorrect (S2517).
Correction eye optical system aberration W _correct = W _eye + W _{CL correct} (secondary aberration)
Note that a secondary aberration may be obtained for one or more of the aberration W _CL of the correction optical system, the aberration W _{CL NEW} generated due to the shift, and the corrected aberration W _{CL correct} .

6). Modification Example of Correction Image Simulation 6-1. Second flowchart of correction image simulation (spherical power calculation in template matching)
FIG. 19 shows a second flowchart of the corrected image simulation. FIG. 19 is a flowchart for calculating a corrected spherical power so that a Landolt ring can be identified by performing a retinal image simulation. In the following flowcharts, the same processing is executed for steps having the same reference numerals.

  First, the calculation unit 210 calculates a provisional spherical power Sr (S1401). As the provisional spherical power Sr, for example, a reflex value, a value calculated from wavefront aberration (for example, wavefront aberration of a correction eye optical system), or the like may be used, or a value stored in the memory 240 in advance or an input unit The value input from 270 may be used.

  Next, the calculation unit 210 sets the simulation spherical power Ss (S1451). Ss is normally set to weak correction (for example, Ss = Sr + 5D) with respect to Sr. The calculation unit 210 sets a Landolt ring with a predetermined visual acuity Vs (for example, Vs = 0.1) (S1453).

The simulation unit 214 of the calculation unit 210 performs Landolt's ring retinal image simulation and obtains target image data (S1405). Here, the simulation unit 214 first performs with respect to a Landolt ring in a predetermined direction (for example, a ring with a gap between the upper, lower, right, and left directions). That is, the simulation unit 214 obtains target image data indicating how the Landolt ring looks by simulation according to the obtained corrected eye optical system aberration W _correct . Specific processing of this simulation will be described later.

  Next, the correction data calculation unit 213 of the calculation unit 210 performs Landolt ring template matching (S1407). The correction data calculation unit 213 performs template matching between the target image data obtained by the simulation and the Landolt ring in a certain direction, and stores a score n indicating the direction and the degree of coincidence in the memory 240. This specific process will be described later.

  The correction data calculation unit 213 determines whether template matching has been performed in all directions (S1409). Here, in the case of No, the process proceeds to step S1407, and the process is repeated until template matching is performed in all directions. On the other hand, if Yes in step S1409, the correction data calculation unit 213 determines whether the score nh having the largest score n matches the direction of the Landolt ring of the target image data simulated in step S1405 (S1411). Here, in the case of Yes, the correction data calculation unit 213 determines whether the score nh is higher than a threshold value predetermined in the memory 240 or the like (S1413).

In the case of No in step S1411 or S1413, the correction data calculation unit 213 determines whether Ss exceeds a predetermined allowable value (for example, Sr-5D) (S1415). In the case of No here, the correction data calculation unit 213 sets the correction element of Ss slightly stronger (for example, Ss−0.25D) (S1417), and the simulation unit 214 performs Landolt's ring retinal image simulation based on this correction element. . The correction data calculation unit 213 calculates the CL / corneal aberration W _CLCO every time Ss is changed and recalculates the correction eye optical system aberration W _correct every time Ss is obtained in order to obtain an optimal correction value. It is also possible to obtain a correction value with accuracy.

  The calculation unit 210 performs the processing from step S1407 on the target image data obtained by this simulation. On the other hand, if Yes in step S1415, the correction data calculation unit 213 determines that the Landolt ring cannot be discriminated (S1419), and stores the direction at this time and the fact that this direction was impossible in the memory 240. .

  After step S1419 or in the case of Yes in step S1413, the correction data calculation unit 213 determines whether simulation is performed in all directions of the Landolt ring (S1421). Here, in the case of No, the process returns to step S1405, and the calculation unit 210 repeats the above-described process in all directions. On the other hand, in the case of Yes in step S1421, the correction data calculation unit 213 determines whether more than half of the number of set directions has been determined (S1455).

  In the case of Yes in step S1455, the correction data calculation unit 213 sets S = Ss, V = Vs, and sets the Landolt ring with visual acuity Vs = Vs + 0.1 (S1457). Thereafter, the process proceeds to step S1405, where the simulation unit 214 performs retinal image simulation based on the set correction element and the Landolt's ring, obtains target image data, and executes the processes after step S1407. On the other hand, in the case of No in step S1455, the calculation unit 210 performs data output (S1423). That is, for example, the calculation unit 210 displays the spherical power S = Ss at this time, the direction of the Landolt ring that can be determined, and the simulation result on the display unit 230 and stores them in the memory 240.

FIG. 20 shows a flowchart of the retinal image simulation in step S1405. First, the calculation unit 210 calculates a pupil function f (x, y) based on the correction eye optical system aberration W _correct obtained in step S106 of FIG. 6 and the set correction element (S204). The details of the processes in steps S205 to S211 are the same as the steps with the same symbols in FIG.

FIG. 21 is an explanatory diagram of template matching in step S1407.
As shown in the figure, a template image (lower diagram) is set corresponding to the Landolt ring original image (upper diagram), and such a template image is stored in the memory 240 corresponding to the identifier indicating the size of the Landolt ring. In this example, the template image has b = 1.5a, the number of pixels in the Landolt ring is N1, the pixel value is 1, the number of pixels in the blurred point image around the Landolt ring is N2, and the pixel value is −N1. However, the present invention is not limited to this and can be set as appropriate.

FIG. 22 shows a flowchart of Landolt ring template matching in step S1407.
The calculation unit 210 reads the template image from the memory 240 according to the set size of the Landolt ring, and obtains the spatial frequency distribution Temp (x, y) (S1301). Next, the calculation unit 210 obtains a two-dimensional Fourier transform FT (u, v) of Temp (x, y) (S1303). The calculation unit 210 obtains a two-dimensional Fourier transform OR (u, v) of the spatial frequency distribution of the target image data by simulation of the retinal image, and OR (u, v) and the spatial frequency distribution FT (u, v) of the template. And OTmp (u, v) is obtained (S1305).
OR (u, v) × FT (u, v) → OTmp (u, v)
The calculation unit 210 performs two-dimensional inverse Fourier transform on OTmp (u, v) to obtain TmpIm (X, Y) (4a × 4a complex number matrix) (S1307). The calculation unit 210 acquires the maximum absolute value of TmpIm (X, Y) and sets it as a score n (S1309).
By taking such a correlation, if the simulation target image is close to the original image, the score is high, and if it is blurred, the score is lowered accordingly.

6-2. Third flowchart of correction image simulation (astigmatism-1)
23 and 24 show third flowcharts (1) and (2) of the corrected image simulation. FIG. 23 and FIG. 24 are flowcharts for performing astigmatism axis A and astigmatism power C so that the Landolt ring can be discriminated by performing retinal image simulation.

  The calculation unit 210 (for example, the correction data calculation unit 213) calculates the provisional spherical power Sr as in step S1401 described above (S1401). Next, the calculation unit 210 sets a simulation astigmatism power Cs (S1501). For example, Cs is used as an astigmatism degree C calculated from a ref value or wavefront aberration (for example, wavefront aberration of a correction eye optical system), or Cs is stored in advance corresponding to a correction element such as S or C or a Zernike coefficient. The correspondence table may be stored in the memory 240 and obtained by referring to it. Next, the arithmetic part 210 performs Landolt's ring setting of visual acuity Vs (for example, Vs = 0.1) (S1453).

  In steps S1405 to S1413, the calculation unit 210 performs processing such as Landolt's ring retinal image simulation and Landolt's ring template matching, as described above. If the answer is No in step S1411 or S413, the correction data calculation unit 213 determines that the Landolt ring cannot be determined, and stores the direction at this time and the fact that this direction was impossible in the memory 240 (S1419). . After step S1419 or in the case of Yes in step S1413, the arithmetic part 210 executes the processes of steps S1421 and S1455 as described above.

  If it is determined in step S1455 that more than half of the set direction number has been determined, the calculation unit 210 stores the set correction element in the memory 240 (S1503). Next, the correction data calculation unit 213 sets V = Vs, and sets a Landolt ring with visual acuity Vs = Vs + 0.1 (S1505). Thereafter, the process proceeds to S1405, where the simulation unit 214 performs retinal image simulation based on the set correction element and Landolt's ring to obtain index image data, and executes the processing from step S1407.

  On the other hand, in the case of No in step S1455, the correction data calculation unit 213 determines whether simulation has been performed in all astigmatic axis angle directions (0 to 180) (S1507). In the case of No here, the correction data calculation unit 213 rotates the astigmatic axis angle As (for example, As = As + 5) (S1509). Then, it progresses to step S1453 and repeats the process after step S1453.

  Next, with reference to FIG. 24, when the correction data calculation unit 213 determines Yes in step S1507, the correction data calculation unit 213 of the calculation unit 210 sets As when the visual acuity V is the largest as the astigmatic axis angle A. Substitute (S1511). The astigmatic axis angle A is set to the largest number of Landolt rings that can be determined by the visual acuity V when there are a plurality of As at the largest, and further determined by the visual acuity V when there are a plurality of As. The one with the maximum sum of nh in the generated direction is set. Thereby, the astigmatic axis angle A was determined.

  In steps S1453 and S1405 to S1413, as described in the above embodiment, based on the set Sr, Cs, and A, the calculation unit 210 performs each process such as Landolt ring retinal image simulation and Landolt ring template matching. Execute.

  In the case of No in step S1411 or S1413, the correction data calculation unit 213 determines whether Cs exceeds a predetermined allowable value (for example, Cs-10D) (S1515). In the case of No here, the correction data calculation unit 213 sets the correction element of Cs slightly stronger (for example, Cs−0.25D) (S1517), and the simulation unit 214 performs Landolt's ring retinal image simulation based on this correction element. This is performed (S1405). The calculation unit 210 repeatedly executes the processing from step S1407 on the target image data obtained by this simulation. On the other hand, in the case of Yes in step S1415, the correction data calculation unit 213 determines that the Landolt ring cannot be determined (S1419), and stores the direction at this time and the fact that this direction was impossible in the memory 240. .

  After step S1419 or in the case of Yes in step S1413, the arithmetic unit 210 executes the processes of steps S1421 and S1455 as described above. In the case of Yes in step S1455, the calculation unit 210 executes the processes of steps S1503 and S1505. The processing of each step is the same as described above. Thereafter, the process proceeds to step S1405, and the simulation unit 214 performs retinal image simulation based on the set correction element and the Landolt's ring to obtain index image data, and executes the processing from step S1407.

  On the other hand, in the case of No in step S1455, the calculation unit 210 outputs data (S1423). That is, the calculation unit 210 displays the spherical power S = Ss at this time, the direction that can be determined, the simulation result, and the like on the display unit 230 and stores them in the memory 240.

6-3. Fourth flowchart of correction image simulation (astigmatism-2)
FIG. 25 shows a fourth flowchart of the corrected image simulation.
In step S1401, the calculation unit 210 (for example, the correction data measurement unit 213) calculates the provisional spherical power Sr as described above. Next, the calculation unit 210 initially sets the astigmatism power Cs, the astigmatism axis angle As, and the comparison numerical value Mh, which are astigmatism components (S1571). For these values, data stored in advance in the memory 240 may be used, or may be input by the input unit 270. For example, the calculation unit 210 initially sets Cs = 0, As = 0, and Mh = 0.

  The computing unit 210 calculates the MTF based on the wavefront aberration that has already been obtained (for example, the wavefront aberration of the correction eye optical system) (S1573). A specific method for calculating the MTF will be described later. The computing unit 210 calculates a comparative numerical value M from the MTF cross section at the set astigmatism axis angle As (S1575). As the comparison numerical value M, the MTF cross-sectional area or the like can be used. The calculation unit 210 stores the currently set As and, for example, the sum of MTFs, the MTF cross-sectional area, or the sum of 3, 6, 12, and 18 cpd in the memory 240.

  The calculation unit 210 determines whether M ≧ Mh (S1577). In the case of No here, the process proceeds to step S1581, while in the case of Yes, the correction data calculation unit 213 of the calculation unit 210 sets Mh = M and A = As (S1579). Next, the correction data calculation unit 213 determines whether As is 180 or more (S1581). In the case of No here, the correction data calculation unit 213 rotates the astigmatic axis angle As (for example, As = As + 5) (S1509). Thereafter, the calculation unit 210 returns to step S1575 and repeats the process, so that the direction in which M is the maximum at an axis angle of 0 to 180 degrees is the astigmatic axis angle (weak main meridian or strong main meridian), The value of M and the value of As are obtained.

  In the case of Yes in step S1581, that is, when the astigmatic axis angle A is obtained, the calculation unit 210 calculates the MTF based on the astigmatic component Cs, As = A (S1585). The arithmetic part 210 further calculates a numerical value for comparison M from each MTF cross section at 0 to 180 degrees (for example, at intervals of 5 degrees) (S1587).

The correction data calculation unit 213 determines whether the calculated Ms are substantially the same at each angle (S1589). For example, this can be determined based on whether or not all the differences of M are smaller than a predetermined threshold value t. In the case of No in step S1589, the arithmetic unit 210 changes the astigmatism power Cs slightly (for example, Cs = Cs−0.25) (S1591), and repeats the processing after step S1585. On the other hand, in the case of Yes in step S1589, the calculation unit 210 sets C = Cs (S1593).
The calculation unit 210 stores the obtained astigmatism power C and astigmatism axis angle A in the memory 240 and displays them on the display unit 230 as necessary (S1595).

(MTF calculation)
Next, calculation of MTF will be described.
First, MTF is an index indicating the transfer characteristic of the spatial frequency, and is widely used to express the performance of the optical system. For example, the MTF can be predicted in appearance by obtaining transfer characteristics for 0 to 100 sinusoidal gray gratings per degree. In the present embodiment, as described below, a monochromatic MTF or a white MTF may be used.

First, the monochromatic MTF is calculated from the wavefront aberration W (x, y). Note that W (x, y) is an input value (measured value), and corneal wavefront aberration obtained from the corneal shape can be used as the corneal aberration. The pupil function, the point image amplitude distribution, and the point image intensity distribution (PSF) are obtained from the wavefront aberration as in the case of the detailed processing in step S409 in FIG. Next, OTF is calculated | required using Formula (16) in description of detailed processes, such as step S509 of FIG. Also, since the size of OTF is MTF,
MTF (r, s) = | OTF (u, v) |
Holds.

Next, the white light MTF is calculated based on the monochromatic MTF obtained as described above. In order to obtain the white light MTF, first, the MTF at each wavelength is weighted and added. Here, since the MTF described above has a different value for each wavelength, the MTF at the wavelength _λ is expressed as MTF _λ .

Here, the visible light is heavily weighted for calculation.
Specifically, assuming that the three primary colors (RGB) of red, green, and blue are, for example, 656.27 nm: 1, 587.56 nm: 2, and 486.13 nm: 1,
MTF (r, s) = (1 × MTF _656.27 + 2 × MTF _587.56 + 1
× MTF _486.13 ) / (1 + 2 + 1)
It becomes.

Further, since the white light MTF is measured with only one wavelength (840 nm), other wavelengths may be calibrated based on the measurement result and corrected to white. Specifically, when the MTF at each wavelength is an aberration of the eye, when the wavelength measured by the eye optical characteristic measurement apparatus is, for example, 840 nm, the wavefront aberration W ₈₄₀ (x , Y) is measured for chromatic aberration W _Δ (x, y) corresponding to the amount of deviation from this, and W ₈₄₀ (x, y) is added to this chromatic aberration W _Δ (x, y), and MTF is calculated from this wavefront aberration. Is required. That is,
W _λ (x, y) = W ₈₄₀ (x, y) + W _Δ (x, y)
It becomes.
Note that the first, second, third, and fourth flowcharts described above may be used in combination to determine the spherical power, the astigmatism power, and the astigmatic axis correction value.

7). Display Example FIG. 26 is a diagram illustrating a display example of comparison before and after correction. In this figure, the corrected visual acuity before and after correction, the wavefront aberration, the appearance of the Landolt ring, and the pupil diameter are displayed. As shown in the figure, it is shown that the wavefront aberration is made relatively uniform after correction correction, and the Landolt ring is also seen relatively well. In addition, the corrected visual acuity in the environment of the subject after correction correction is shown.

  FIG. 27 shows an explanatory diagram of prescription data examples for glasses and contacts. Each of these data is stored in the memory 240 by the arithmetic unit 210 and / or displayed on the display unit 230. In this example, in the case of performing refractive surgery using only SCA as correction correction data, correction is performed by increasing the value of S in the correction correction data, weakening the value of C, and slightly changing the axial direction of A. Indicates that the corrected visual acuity is improved.

  FIG. 28 is an explanatory diagram of an example of optimum prescription data for each contact. Each of these data is stored in the memory 240 by the arithmetic unit 210 and / or displayed on the display unit 230. For example, the SCA value, the corrected visual acuity, and the appearance of the Landolt ring (for example, 0.5) are shown for a plurality of types of contact lenses and / or glasses. Moreover, the pupil diameter used for the measurement is shown.

  The optimum one can be selected automatically or manually from the optical characteristics (PSF, MTF, Landolt ring simulation, etc.) in the correction with glasses (simply correction of S, C, A) and the optical characteristics at the time of wearing the contact. .

  FIG. 29 shows an explanatory diagram of prescription data examples for eyeglasses and contacts when environmental conditions change. For example, the pupil diameter of the eye 60 to be measured is measured in an illumination state corresponding to each environmental condition, and correction data and corrected visual acuity at each pupil diameter are displayed. It is shown that the correction correction data is slightly different depending on the pupil diameter. That is, it is shown that the optimum prescription value varies depending on the environment of the subject. In addition, for example, a doctor or the like can select a prescription value in consideration of the environment of the subject. The environmental conditions to be displayed can be changed as appropriate.

  In the example shown in FIG. 29, correction data corresponding to each environmental condition is obtained and visual acuity under the environmental condition is displayed. However, visual acuity under other environmental conditions can be estimated and displayed. For example, when correction is performed using correction correction data during daylight hours, the visual acuity can be estimated and displayed during daylight hours, under fluorescent lights, and in daytime rooms.

  FIG. 30 shows an explanatory diagram of an example of pupil data when the environmental conditions change. For example, the pupil diameter of the eye 60 to be measured is measured in an illumination state corresponding to each environmental condition, and the shift amount (x direction, y direction) from the center of the pupil at each pupil diameter and the corrected visual acuity are indicated. It is shown that the center of the pupil is shifted due to a change in environmental conditions, and the center (origin) at the time of analysis is shifted.

FIG. 31 shows a comparison diagram with the measurement based on the fixed pupil diameter of the prescription data for glasses and contacts. For example, as in the conventional measurement, correction data and corrected visual acuity are displayed when the pupil diameter is 4 mm and 6 mm and when the pupil diameter is measured (for example, illumination at 50 lx). When the pupil diameter is fixed and when the measurement is performed, the correction data and the corrected visual acuity are slightly different. FIG. 30 shows data using the pupil diameter when illuminated at 50 lx as an example. By appropriately changing the conditions, it is possible to estimate the visual acuity of the subject in an appropriate environment.
In the above-described figure, the visual acuity is expressed by a small number of visual acuities, but may be displayed by log MAR visual acuity. The display conditions can be changed as appropriate.

8). APPENDIX An apparatus / system according to the ophthalmic apparatus of the present invention includes a correction data measurement program for causing a computer to execute each procedure, a computer-readable recording medium storing the correction data measurement program, and a correction data measurement program. It can be provided by a program product that can be loaded into the internal memory, a computer such as a server including the program, and the like.

  The measurement data indicating the refractive power distribution of the eye to be measured is obtained by the optical system 100 shown in FIG. 1, but is not limited to this, and can be constituted by another avelometer or the like. For example, regardless of the measurement result of the wavefront sensor, the result can be used as long as eye aberration (averometer, etc.) and corneal shape (topography, etc.) are obtained.

  The present invention can be applied to an ophthalmologic apparatus, an application apparatus thereof, an ophthalmic surgery apparatus, and the like. It can also be applied to devices for contact lens prescription and inspection.

The block diagram of the optical system of an ophthalmologic apparatus (eye optical characteristic measuring apparatus). The block diagram of the electric system 200 of an eye optical characteristic measuring apparatus. 4 is a configuration example of a front shape table stored in advance in a memory 240. 4 is a configuration example of a rear surface shape table stored in advance in a memory 240. Illustration of Landolt ring. The flowchart of the correction data measurement for contact lens wearing. The sub-flowchart of correction | amendment eye optical system simulation-1 of step S2106. The sub flowchart about calculation of the pupil diameter of step S2105, measurement of cornea data, and eyeball optical system data. Explanatory drawing of pupil diameter calculation. The flowchart which shows corneal data calculation. The flowchart of the correction image simulation of step S2107. The flowchart about the 1st example of best image condition calculation. The flowchart about the 2nd example of best image condition calculation. The sub-flowchart of correction | amendment eye optical system simulation-2 in step S2106. The modification (1) of the flowchart of the correction data measurement for contact lens wearing. The modification (2) of the flowchart of the correction data measurement for contact lens wearing. The sub-flowchart of correction | amendment eye optical system simulation-3. The sub-flowchart of correction | amendment eye optical system simulation-4. The 2nd flowchart of correction image simulation. The flowchart of the retinal image simulation of step S1405. Explanatory drawing of the template matching of step S1407. The flowchart of Landolt ring template matching of step S1407. The 3rd flowchart (1) of correction image simulation. The 3rd flowchart (2) of correction image simulation. The 4th flowchart of correction image simulation. The figure which shows the example of a display about the comparison before correction | amendment and after correction | amendment. Explanatory drawing of the example of prescription data for glasses and contacts. Explanatory drawing of the optimal prescription data example for every contact. Explanatory drawing of the prescription data example for spectacles and a contact when environmental conditions change. Explanatory drawing of the pupil data example when environmental conditions change. The comparison figure with the measurement by the fixed pupil diameter of prescription data for glasses and contacts. Explanatory drawing of a correction | amendment eye optical system and a correction optical system. Processing flow for hard contact lenses. Processing flow for soft contact lenses.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 1st illumination optical system 11 1st light source part 12,32,34,44,52,53 Condensing lens 20 1st light reception optical system 21 Collimating lens 22 Hartmann plate 23,35,54 1st-3rd light-receiving part 30 1st 2 light receiving optical systems 33, 43, 45 beam splitter 40 common optical system 42 afocal lens 50 adjusting optical system 60 eye 70 to be measured second illumination optical system 71 platide ring 72 second light source 80 second light transmitting optical system 90 first 3 illumination optical system 91 fifth light source unit 92 fixation target 100 optical system 200 of correction data measuring device electric system 210 calculation unit 211 wavefront aberration calculation unit 212 cornea / contact lens data calculation unit 213 correction data calculation unit 214 simulation unit 215 pupil Diameter measurement unit 220 Control unit 230 Display unit 240 Memory 250 First drive unit 260 Second drive unit 280 Third drive Part 270 input part

Claims (13)

A wavefront aberration measuring optical system for irradiating the fundus of the eye to be examined and receiving reflected light from the fundus of the eye to be examined;
A wavefront aberration calculator that obtains wavefront aberration including low-order aberration and high-order aberration of the eye to be examined based on the signal received by the wavefront aberration measurement optical system;
A cornea / contact lens data measurement optical system for illuminating the vicinity of the subject's eye cornea with a predetermined pattern and receiving reflected light from the vicinity of the subject's eye cornea,
A corneal / contact lens data calculation unit for determining a corneal shape and corneal aberration of the eye based on a signal received by the cornea / contact lens data measuring optical system;
The aberration of the correction optical system including the contact lens corresponding to the corneal shape obtained by the cornea / contact lens data calculation unit is obtained, and the wavefront aberration of the eye to be examined, the corneal aberration, and the correction obtained by the wavefront aberration calculation unit are corrected. Based on the aberration of the optical system, the aberration of the corrected eye optical system including the eye to be examined and the contact lens in which the contact lens is worn on the eye to be examined is obtained. An ophthalmologic apparatus provided with a correction data calculation unit for obtaining correction data for contact lens wearing that is appropriate correction. The correction data calculation unit
Contact lens thickness, rear surface according to the provisional spherical power based on the wavefront aberration obtained by the wavefront aberration calculator and the cornea shape obtained by the cornea / contact lens data calculator The ophthalmologic apparatus according to claim 1, wherein an aberration of a correction optical system including a contact lens is obtained by ray tracing based on wear correction data including any one or more of a diameter, a shape, a curvature, and a refractive index. The correction data calculation unit
The intraocular aberration is obtained by subtracting the corneal aberration obtained by the cornea / contact lens data computing unit from the wavefront aberration obtained by the wavefront aberration computing unit,
Obtain the aberration of the correction optical system including the contact lens and / or tear film according to the cornea shape obtained by the cornea / contact lens data calculation unit,
The ophthalmic apparatus according to claim 1, wherein the aberration of the corrected eye optical system is obtained by adding the calculated intraocular aberration and the aberration of the correction optical system. The ophthalmologic apparatus according to claim 1, further comprising a simulation unit that simulates the appearance of a predetermined optometry target by the eye to be examined based on the obtained correction data, and displays or outputs the appearance. In correspondence with the contact lens identifier and the corneal shape, it further comprises a rear surface shape table storing the rear surface shape data of the contact lens,
The correction data calculation unit
Enter the contact lens identifier,
Refer to the rear surface shape table based on the input contact lens identifier and the determined corneal shape, to obtain the corresponding rear surface shape data,
The ophthalmologic apparatus according to claim 1, wherein aberrations of a correction eye optical system including a contact film and a tear film having a shape corresponding to a corneal shape of the eye to be examined and a rear surface shape of the acquired contact lens are obtained. Corresponding to the contact lens identifier, the corrected spherical power and the rear surface shape data, further comprising a front surface shape table storing front surface shape data, curvature and refractive index,
The correction data calculation unit
Based on the input contact lens identifier, the corrected spherical power corresponding to the wavefront aberration obtained by the wavefront aberration calculating unit or predetermined, and the acquired rear surface shape data, refer to the front surface shape table. , Get the corresponding front shape data, curvature and refractive index,
The ophthalmologic apparatus according to claim 5, wherein the aberration of the correction optical system is obtained by ray tracing based on the acquired front surface shape data, curvature, and refractive index. The correction data calculation unit
As the shape of the contact lens fits or almost fits with the cornea shape of the eye to be examined determined by the cornea / contact lens data calculation unit, the rear surface shape and the front surface shape of the contact lens are determined according to the cornea shape,
The ophthalmologic apparatus according to claim 1, wherein aberrations of a correction optical system including a contact lens and / or a tear film having the obtained rear surface shape and front surface shape are obtained. Based on the signal received by the cornea / contact lens data measurement optical system, further comprising a pupil diameter measurement unit for obtaining the pupil diameter of the eye to be examined,
The wavefront aberration calculating unit obtains low-order aberration and / or high-order aberration of the eye to be examined based on the pupil diameter obtained by the pupil diameter measuring unit and the signal received by the wavefront aberration measuring optical system. The ophthalmic apparatus according to claim 1, which is configured as follows. The correction data calculation unit is
Based on the obtained aberration of the correction eye optical system, one of Strehl ratio, phase shift, and MTF (Modulation Transfer Function) indicating the transfer characteristic of the eye after correction is obtained,
Aberration amount, spherical power, astigmatism power, astigmatism axis or astigmatism axis is included so that Strehl ratio becomes large, phase shift becomes small, or MTF becomes large and uniform The ophthalmologic apparatus according to claim 1, wherein correction data for contact lens wear is obtained by changing the correction value so as to correct the eye appropriately. Based on the obtained aberration of the corrected ophthalmic optical system, further comprising a simulation unit for simulating the appearance of a predetermined optometry target in the eye to be corrected and obtaining the target image data,
The correction data calculation unit
For the target image data obtained by the simulation unit and the pattern data of the optometric target, the degree of matching by pattern matching is obtained,
Requesting correction data for contact lens wearing that corrects for the subject's eye by changing the correction value including one or more of spherical power, astigmatism power, astigmatism axis, or aberration amount so that the matching degree is high The ophthalmic apparatus according to Item 1. The correction data calculation unit is
The intraocular aberration is obtained by subtracting the corneal aberration obtained by the cornea / contact lens data computing unit from the wavefront aberration obtained by the wavefront aberration computing unit,
Obtain the aberration of the correction optical system including the contact lens and / or tear film according to the cornea shape obtained by the cornea / contact lens data calculation unit,
Adding the calculated intraocular aberration and the aberration of the correction optical system to determine the aberration of the first correction eye optical system;
According to the obtained aberration of the first correction eye optical system, the first correction data for the contact lens wearing that corrects the eye to be examined is obtained,
From the wavefront aberration obtained by the wavefront aberration calculator, subtract the secondary aberration to obtain the aberration of the second correction eye optical system,
According to the obtained aberration of the second correction eye optical system, second correction data for spectacle wearing that is correction appropriate for the eye to be examined is obtained,
The ophthalmologic apparatus according to claim 1, wherein the obtained first and second correction data and / or the appearance of the correction is displayed or output. A wavefront aberration measurement optical system for irradiating a light beam to the fundus of the eye to be examined wearing a contact lens and receiving reflected light from the fundus of the eye to be examined;
A wavefront aberration calculator that obtains wavefront aberration including low-order aberration and high-order aberration of the eye to be examined based on the signal received by the wavefront aberration measurement optical system;
A cornea / contact lens data measurement optical system for illuminating the vicinity of the subject's eye cornea wearing a contact lens with a predetermined pattern and receiving a reflected light beam from the vicinity of the subject's eye cornea,
Based on the signal received by the cornea / contact lens data measurement optical system, the cornea / contact lens data calculation unit for obtaining the contact lens front surface shape and contact lens front aberration when the contact lens of the eye to be examined is worn,
The spherical power of the contact lens to be changed is set, and the aberration due to the deviation between the spherical power based on the wavefront aberration obtained by the wavefront aberration calculator and the spherical power of the set contact lens is obtained and obtained. The corrected aberration is obtained by calculating the difference between the aberration and the front aberration of the contact lens, and adding the corrected aberration to the wavefront aberration obtained by the wavefront aberration calculator. An ophthalmologic apparatus comprising: a correction data calculation unit that calculates aberration data and calculates correction data for contact lens wearing that is appropriate for the subject's eye according to the calculated aberration of the correction eye optical system. The correction data calculation unit
The ophthalmologic apparatus according to claim 12, wherein an aberration of the corrected eye optical system is obtained by adding a secondary aberration of the corrected aberration to the wavefront aberration obtained by the wavefront aberration calculating unit.

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