Optical characteristic display device and optical characteristic display method

Abstract

To provide an optical characteristic display device capable of simulating optical characteristics of a patient's eye corresponding to the patient's eye in which an intraocular lens is inserted, and optical characteristic display method.SOLUTION: An optical characteristic display device includes: an aberration acquisition part for acquiring an intraocular aberration, a corneal aberration, and an internal aberration of a patient's eye in which an intraocular lens is inserted; a display control part causing a monitor to display optical characteristics of the patient's eye based on at least the intraocular aberration and the internal aberration; a first operation part for receiving a change operation for changing only one or a plurality of parameters of the internal aberration in the patient's eye; an internal aberration prediction part for predicting an internal aberration after the change of the parameter in response to the change operation on the first operation unit; and a recalculation part for recalculating the intraocular aberration based on the internal aberration predicted by the internal aberration prediction part and the corneal aberration acquired by the aberration acquisition part. The display control part executes update processing of updating the optical characteristics to be displayed on the monitor based on the internal aberration predicted by the internal aberration prediction part and the intraocular aberration recalculated by the recalculation part.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to an optical characteristic display device and an optical characteristic display method for displaying the optical characteristics of a patient's eye on a monitor based on the aberration of the patient's eye. [Background technology]

[0002] There is known an ophthalmic apparatus that uses a wavefront sensor to capture light returning from the fundus of a patient's eye to obtain a Hartmann image of the patient's eye (see Patent Documents 1 to 3). This ophthalmic apparatus analyzes the wavefront aberration of the patient's eye based on the Hartmann image of the patient's eye, and then performs, for example, Zernike analysis on this wavefront aberration to calculate intraocular aberrations of the patient's eye expressed by Zernike polynomials (Zernike coefficients). The ophthalmic apparatus also captures light returning from the anterior segment of the patient's eye onto which a Placido ring is projected to obtain an anterior segment image of the patient's eye, and analyzes this anterior segment image to calculate corneal aberrations of the cornea of ​​the patient's eye expressed by Zernike polynomials. Furthermore, the ophthalmic apparatus calculates internal aberrations of the patient's eye based on the results of calculation of the intraocular aberrations and the corneal aberrations (see Patent Document 1).

[0003] The ophthalmologic apparatus generates an optical characteristics screen that graphically represents the optical characteristics of the patient's eye based on the calculation results of each aberration of the patient's eye, and displays this optical characteristics screen on a monitor. This optical characteristics screen includes an aberration map (spherical aberration map, high-order aberration map) of each aberration, a modulation transfer function (MTF), and how the Landolt ring appears in the patient's eye (see Patent Document 2).

[0004] Furthermore, the ophthalmic apparatus described in Patent Document 3 calculates the low-order aberrations (aberrations that can be corrected with glasses or the like) and high-order aberrations of the patient's eye based on the intraocular aberrations of the patient's eye expressed by Zernike polynomials. When the high-order aberrations are equal to or greater than a threshold, the ophthalmic apparatus described in Patent Document 3 calculates the Strehl definition while changing the low-order terms (low-order Zernike coefficients) of the Zernike polynomials to find the condition under which this Strehl ratio becomes a maximum value, and determines the amount of low-order aberration at that time as the correction value for the patient's eye. [Prior art documents] [Patent documents]

[0005] [Patent Document 1] Japanese Patent Application Laid-Open No. 2002-204784 [Patent Document 2] Japanese Patent Application Laid-Open No. 2002-209854 [Patent Document 3] Japanese Patent Application Laid-Open No. 2004-89278 Summary of the Invention [Problem to be solved by the invention]

[0006] When a patient has cataracts and corneal astigmatism, a toric IOL (intraocular lens) may be implanted into the patient's eye during cataract surgery to compensate for the corneal astigmatism. In this case, the axis angle of the toric IOL to be implanted into the patient's eye is determined before cataract surgery, and a guide light is projected onto the patient's eye during cataract surgery to ensure that the axis angle of the toric IOL does not deviate from the astigmatic axis of the patient's eye. However, there are cases in which reoperation is required due to factors such as the influence of induced astigmatism caused by the incision made during surgery or the deviation of the axis angle of the toric IOL implanted in the patient's eye after surgery.

[0007] Before performing reoperation on a patient's eye, it is preferable to simulate how the optical characteristics of the patient's eye (particularly the vision of the patient's eye) change when parameters of the internal aberration (aberration of the toric IOL), for example, the axial angle, are changed, and the results of this simulation of the optical characteristics are presented to the doctor, patient, etc. However, the ophthalmic devices described in Patent Documents 1 and 2 cannot simulate the optical characteristics of the patient's eye.

[0008] On the other hand, Patent Document 3 discloses changing the lower-order terms of Zernike polynomials that represent the aberrations of a patient's eye. Since the patient's eye described in Patent Document 3 does not have a toric IOL or the like inserted therein, the ophthalmic apparatus described in Patent Document 3 can change all of the lower-order terms of the Zernike polynomials. However, in a patient's eye having an intraocular lens such as a toric IOL inserted therein, the parameters that can be changed when simulating the optical characteristics of the patient's eye are limited to parameters corresponding to the intraocular lens, such as the axis angle, power, and position of the toric IOL. Therefore, the ophthalmic apparatus described in Patent Document 3, which is not designed for a patient's eye having an intraocular lens such as a toric IOL inserted therein, cannot simulate the optical characteristics of the patient's eye when parameters corresponding to the intraocular lens are changed, and cannot present the simulation results to a doctor or the like.

[0009] The present invention has been made in consideration of the above circumstances, and aims to provide an optical characteristic display device and an optical characteristic display method that can simulate the optical characteristics of a patient's eye corresponding to a patient's eye into which an intraocular lens has been inserted. [Means for solving the problem]

[0010] An optical property display device for achieving the object of the present invention includes an aberration acquisition unit that acquires intraocular aberrations, corneal aberrations, and internal aberrations of a patient's eye in which an intraocular lens has been inserted; a display control unit that displays the optical properties of the patient's eye on a monitor based on at least the intraocular aberrations and internal aberrations among the intraocular aberrations, corneal aberrations, and internal aberrations acquired by the aberration acquisition unit; a first operation unit that accepts a change operation that changes only one or more parameters of the internal aberrations in the patient's eye; an internal aberration prediction unit that predicts the internal aberration after the parameter change in response to the change operation on the first operation unit; and a recalculation unit that recalculates the intraocular aberrations based on the internal aberrations predicted by the internal aberration prediction unit and the corneal aberrations acquired by the aberration acquisition unit, and the display control unit performs an update process that updates the optical properties to be displayed on the monitor based on the internal aberrations predicted by the internal aberration prediction unit and the intraocular aberrations recalculated by the recalculation unit.

[0011] This optical characteristic display device can predict (simulate) the optical characteristics of a patient's eye when the parameters of the intraocular lens are changed, and display the results on a monitor.

[0012] In the optical property display device according to another aspect of the present invention, the display control unit causes the monitor to display an operation icon indicating the first operation unit in addition to the optical property.

[0013] In the optical property display device according to another aspect of the present invention, each time a parameter change operation is repeatedly performed with the first operation unit, the internal aberration prediction unit predicts the internal aberration, the recalculation unit recalculates the intraocular aberration, and the display control unit performs an update process repeatedly, thereby making it possible to determine optimal values ​​of the parameters.

[0014] An optical property display device according to another aspect of the present invention includes a second operation unit that accepts an optimization operation for optimizing parameters, a repetition control unit that, when the optimization operation is performed by the second operation unit, repeatedly executes the internal aberration prediction unit to predict internal aberrations and the recalculation unit to recalculate intraocular aberrations while changing parameters, an evaluation value calculation unit that calculates an evaluation value serving as an index for parameter optimization for each parameter based on the intraocular aberrations recalculated for each parameter by the recalculation unit, and an optimal value determination unit that determines optimal values ​​of the parameters based on the calculation results of the evaluation value for each parameter by the evaluation value calculation unit. This allows the optimal values ​​of the parameters to be determined automatically, making it possible to perform this optimization easily and in a short time.

[0015] In the optical property display device according to another aspect of the present invention, the evaluation value is a modulation transfer function or a Strehl ratio.

[0016] In the optical characteristic display device according to another aspect of the present invention, the display control unit selects the internal aberrations and intraocular aberrations corresponding to the optimal values ​​determined by the optimal value determination unit from the internal aberrations and intraocular aberrations for each parameter, and performs update processing based on the internal aberrations and intraocular aberrations corresponding to the optimal values, thereby making it possible to display on the monitor the predicted results (simulation results) of the optical characteristics of the patient's eye corresponding to the optimal values.

[0017] In the optical property display device according to another aspect of the present invention, the display control unit displays the parameter value on the monitor and changes the display mode of the parameter value displayed on the monitor before and after a change operation on the first operation unit, so that the examiner can recognize the parameter value after the change operation and can also recognize that the optical property of the patient's eye corresponding to this parameter is displayed on the monitor.

[0018] In another aspect of the optical property display device of the present invention, the aberration acquisition unit includes a first imaging system that captures a Hartmann image of the patient's eye, an intraocular aberration calculation unit that calculates intraocular aberrations based on the Hartmann image captured by the first imaging system, a second imaging system that captures an anterior segment image of the patient's eye onto which a predetermined pattern of light is projected, a corneal aberration calculation unit that calculates corneal aberrations based on the anterior segment image captured by the second imaging system, and an internal aberration calculation unit that calculates internal aberrations based on the results of the calculation of intraocular aberrations by the intraocular aberration calculation unit and the results of the calculation of corneal aberrations by the corneal aberration calculation unit.

[0019] In another aspect of the present invention, the optical property display device includes a first storage unit that stores pre-measured intraocular aberrations, corneal aberrations, and internal aberrations, and the aberration acquisition unit acquires the intraocular aberrations, corneal aberrations, and internal aberrations from the first storage unit, thereby reducing the examiner's workload and the patient's burden.

[0020] In another aspect of the present invention, the optical property display device includes a second storage unit that stores information necessary for calculating intraocular aberrations, corneal aberrations, and internal aberrations of a patient's eye, including a Hartmann image of the patient's eye and an anterior segment image of the patient's eye onto which a predetermined pattern light is projected, and the aberration acquisition unit includes an intraocular aberration calculation unit that calculates intraocular aberrations based on the information stored in the second storage unit, a corneal aberration calculation unit that calculates corneal aberrations based on the information stored in the second storage unit, and an internal aberration calculation unit that calculates internal aberrations based on the information stored in the second storage unit. This reduces the examiner's workload and the patient's burden.

[0021] In the optical property display device according to another aspect of the present invention, the parameters include at least one of an axial angle, a power, and a position of the intraocular lens.

[0022] An optical characteristic display method for achieving the object of the present invention includes an aberration acquisition step of acquiring intraocular aberrations, corneal aberrations, and internal aberrations of a patient's eye in which an intraocular lens has been inserted, the intraocular aberrations, corneal aberrations, and internal aberrations being expressed as functions; a display control step of displaying the optical characteristics of the patient's eye on a monitor based on at least the intraocular aberrations and internal aberrations among the intraocular aberrations, corneal aberrations, and internal aberrations acquired in the aberration acquisition step; an operation step of accepting a change operation that changes only parameters of the internal aberrations in the patient's eye; a prediction step of predicting the internal aberrations after the parameters have been changed in accordance with the change operation in the operation step; a recalculation step of performing a recalculation process of the intraocular aberrations based on the internal aberrations predicted in the prediction step and the corneal aberrations acquired in the aberration acquisition step; and an update step of performing an update process of updating the optical characteristics to be displayed on the monitor based on the internal aberrations predicted in the prediction step and the intraocular aberrations recalculated in the recalculation step. [Effects of the Invention]

[0023] The present invention can simulate the optical characteristics of a patient's eye corresponding to a patient's eye into which an intraocular lens has been inserted. [Brief explanation of the drawings]

[0024] [Figure 1] FIG. 1 is a block diagram of an ophthalmologic apparatus according to a first embodiment. [Figure 2] FIG. 10 is a diagram showing an example of an optical characteristics screen displayed on a monitor. [Figure 3] FIG. 10 is an explanatory diagram showing an example of an optical characteristics screen when a check box is checked. [Figure 4] FIG. 10 is an explanatory diagram showing an example of an optical characteristics screen after an operation to change the axial angle of internal aberration in response to an operation icon. [Figure 5] 5 is a flowchart showing a flow of a simulation display of optical characteristics of a patient's eye by the ophthalmologic apparatus of the first embodiment. [Figure 6] FIG. 10 is a block diagram of an ophthalmologic apparatus according to a second embodiment. [Figure 7] 10 is a flowchart showing a flow of a simulation display of optical characteristics of a patient's eye by an ophthalmologic apparatus according to a second embodiment. [Figure 8] FIG. 10 is a block diagram of an ophthalmologic apparatus according to a third embodiment. [Figure 9] 10 is a flowchart showing a flow of a simulation display of optical characteristics of a patient's eye by an ophthalmologic apparatus according to a third embodiment. [Figure 10] FIG. 10 is a block diagram showing an ophthalmologic apparatus according to a fourth embodiment. [Figure 11] FIG. 13 is a diagram showing an example of an optical characteristics screen of the fifth embodiment, which allows a change operation of the power of an IOL as a parameter of internal aberration. [Figure 12] FIG. 13 is a diagram showing an example of an optical characteristics screen of the fifth embodiment, which allows the user to change the position of the IOL as a parameter of internal aberration. DETAILED DESCRIPTION OF THE INVENTION

[0025] [First embodiment] FIG. 1 is a block diagram of an ophthalmic apparatus 10 according to a first embodiment, which corresponds to an optical property display device of the present invention.

[0026] As shown in Fig. 1, an ophthalmic apparatus 10 measures intraocular aberrations, corneal aberrations, and internal aberrations of a patient's eye in which an intraocular lens, such as a toric IOL (hereinafter abbreviated as IOL), has been inserted, generates an optical characteristics screen 40 that graphically displays the optical characteristics of the patient's eye based on the measurement results, and displays this optical characteristics screen 40 on a monitor 14. Note that the patient includes an examinee, and the patient's eye includes the eye to be examined. In this specification, intraocular aberrations refer to aberrations of the entire eye (entire eyeball), and internal aberrations refer to aberrations of the IOL excluding the cornea.

[0027] Furthermore, the ophthalmic apparatus 10 has a function of performing a simulation to predict the optical characteristics of the patient's eye after a second surgery to change the parameters of the internal aberration of the patient's eye in which an IOL has been inserted, before the second surgery is performed, and updating the display on the optical characteristics screen 40 based on the results of the simulation. Examples of the parameters of the internal aberration include the axial angle, power, and position of the IOL. In the following, this embodiment will be described taking as an example a case where a simulation of the optical characteristics of the patient's eye is performed before a second surgery to change the axial angle as a parameter of the internal aberration.

[0028] The ophthalmologic apparatus 10 has a known corneal topography function and can measure the corneal shape of the patient's eye. Examples of this corneal shape include a corneal axial power map 50 that represents the corneal curvature of the patient's eye in diopters, and K-value information 52 (corneal refractive power), as shown in Fig. 2 (described later).

[0029] The ophthalmic apparatus 10 includes a wavefront sensor 12, a monitor 14, and a control device 16. The wavefront sensor 12, together with an aberration calculation unit 32 of the control device 16 (described later), constitutes an aberration acquisition unit of the present invention. The wavefront sensor 12 includes an illumination system 20, a first imaging system 22, a projection system 24, and a second imaging system 26.

[0030] The illumination system 20 and the first imaging system 22 are used to measure (acquire) the intraocular aberration of the patient's eye. The illumination system 20 irradiates the fundus of the patient's eye with illumination light (e.g., infrared light). The first imaging system 22 captures an image of the light returning from the fundus irradiated with the illumination light by the illumination system 20 through a Hartmann plate (not shown), and outputs a Hartmann image 23 of the patient's eye to the control device 16. Note that the configurations of the illumination system 20 and the first imaging system 22 used to capture the Hartmann image 23 are publicly known technologies (see Patent Documents 1 to 3 above), and therefore a detailed description thereof will be omitted here.

[0031] The projection system 24 and the second imaging system 26 are used to measure (acquire) the corneal aberration of the patient's eye. The projection system 24 projects Placido ring light (or Kerat ring light), which corresponds to the predetermined pattern light of the present invention, onto the cornea of ​​the patient's eye. The second imaging system 26 captures the return light from the cornea onto which the Placido ring light is projected by the projection system 24, and outputs a corneal Meyer image 27, which is an image of the anterior segment of the patient's eye, to the control device 16. Note that the configurations of the projection system 24 and the second imaging system 26 used to capture the corneal Meyer image 27 are also publicly known techniques (see Patent Documents 1 and 2 above), so a detailed description thereof will be omitted here. Furthermore, the projection system 24 and the second imaging system 26 may be provided separately from the wavefront sensor 12.

[0032] The monitor 14 displays the optical characteristics screen 40 under the control of the control device 16. The monitor 14 is a so-called touch panel type and also functions as an operation unit that accepts various input operations by the examiner. Examples of these input operations include an operation to start measuring the intraocular aberration, corneal aberration, and internal aberration of the patient's eye, an operation to start simulating the optical characteristics of the patient's eye, and an operation to change parameters of the internal aberration (such as the axial angle). Note that the operation unit that performs these operations may be provided separately from the monitor 14.

[0033] The control device 16 includes an arithmetic circuit configured with various processors, memories, etc. The various processors include a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), and a programmable logic device (e.g., simple programmable logic devices (SPLD), complex programmable logic devices (CPLD), and field programmable gate arrays (FPGA)). The various functions of the control device 16 may be realized by a single processor or by multiple processors of the same or different types.

[0034] The control device 16 controls the overall operation of the wavefront sensor 12 and the monitor 14 based on input operations input by touching the monitor 14. Specifically, the control device 16 controls the capture of the Hartmann image 23 and the corneal Meyer image 27 by the wavefront sensor 12 and the display of the optical characteristics screen 40 by the monitor 14. The control device 16 executes a control program (not shown) to function as a measurement control unit 30, an aberration calculation unit 32, a display control unit 34, an internal aberration prediction unit 35, and a recalculation unit 36.

[0035] The measurement control unit 30 causes the wavefront sensor 12 to capture the Hartmann image 23 and the corneal Meyer image 27 based on a measurement start operation input to the monitor 14. As a result, the Hartmann image 23 and the corneal Meyer image 27 are input to the aberration calculation unit 32.

[0036] The aberration calculation unit 32 includes an intraocular aberration calculation unit 32a that calculates the intraocular aberration of the patient's eye, a corneal aberration calculation unit 32b that calculates the corneal aberration of the patient's eye, and an internal aberration calculation unit 32c that calculates the internal aberration of the patient's eye.

[0037] The intraocular aberration calculation unit 32a analyzes the Hartmann image 23 input from the first imaging system 22 to calculate the intraocular aberration of the patient's eye. Specifically, the intraocular aberration calculation unit 32a analyzes the Hartmann image 23 to calculate the wavefront aberration of the patient's eye (eyeball), and further represents this wavefront aberration using a mathematical descriptor. For example, the intraocular aberration calculation unit 32a performs Zernike analysis, which expands the wavefront aberration of the patient's eye into Zernike polynomials. As a result, the intraocular aberration calculation unit 32a calculates the intraocular aberration of the patient's eye expressed in Zernike polynomials (Zernike coefficients).

[0038] The corneal aberration calculation unit 32b analyzes the corneal Meyer image 27 input from the second imaging system 26 and calculates the corneal aberration expressed by Zernike polynomials (Zernike coefficients) based on the distortion of the Placido ring image caused by the aberration of the cornea of ​​the patient's eye.

[0039] The internal aberration calculation unit 32c calculates the internal aberration of the patient's eye, which is expressed by Zernike polynomials (Zernike coefficients), based on the calculation result of the intraocular aberration by the intraocular aberration calculation unit 32a and the calculation result of the corneal aberration by the corneal aberration calculation unit 32b.

[0040] Note that the specific calculation methods for intraocular aberrations, corneal aberrations, and internal aberrations are publicly known technologies [see Patent Documents 1 to 3 (especially Patent Document 1) and JP 2020-81450 A], so detailed explanations will be omitted here.

[0041] The display control unit 34 controls the display on the monitor 14. The display control unit 34 generates an optical characteristics screen 40 based on the calculation results of each aberration by the aberration calculation unit 32, the Hartmann image 23, the corneal Meyer image 27, and the corneal axial power map 50 and K value information 52 acquired in advance, and causes the monitor 14 to display the optical characteristics screen 40.

[0042] 2 is a diagram showing an example of an optical characteristics screen 40 displayed on the monitor 14. The optical characteristics screen 40 includes a left / right eye switching button 42, a layout switching button 44, and a display field 46.

[0043] The left / right eye switching button 42 is used to switch between the left and right eyes of the patient's eye whose optical characteristics are to be displayed. The display control unit 34 switches the display of the optical characteristics of the left and right eyes displayed on the optical characteristics screen 40 in response to the left / right eye switching operation of the left / right eye switching button 42 by the examiner.

[0044] The layout switching button 44 is used to switch the layout of the optical characteristics of the patient's eye displayed on the optical characteristics screen 40. Examples of layout types include an "ocular aberration map" that displays an ocular aberration map, a "corneal aberration map" that displays a corneal aberration map, and an "IOL selection map" that is used to display a simulation of the optical characteristics of the patient's eye before reoperation. In response to a selection operation on the layout switching button 44, the display control unit 34 displays in a display field 46 the optical characteristics of the patient's eye that correspond to this selection operation.

[0045] In the present embodiment, the description will be given assuming that "IOL selection map" is selected. The display control unit 34 generates a graphic showing the optical characteristics of the patient's eye based on the calculation results of the intraocular aberration (wavefront aberration), corneal aberration, and internal aberration of the patient's eye by the aberration calculation unit 32, and displays this graphic in a display field 46 for "IOL selection map." The display control unit 34 also displays the Hartmann image 23 and the corneal Meyer image 27 used in the calculation (analysis) by the aberration calculation unit 32, as well as a corneal axial power map 50 and K-value information 52 acquired in advance by a corneal topography function of the ophthalmic apparatus 10, in the display field 46 for "IOL selection map."

[0046] In the "IOL Selection Map" display field 46, there are displayed, as graphics showing the optical characteristics of the patient's eye, an "ocular total aberration map 54," an "astigmatism map 56," a "spherical aberration map 58," a "higher-order aberration map 60," "corneal higher-order aberration information 62," "corneal spherical aberration information 64," "corneal astigmatism information 66," and a "Landolt ring simulation image 68." In addition, a "check box 70" is displayed in the display field 46.

[0047] The total ocular aberration map 54 displays the total refractive state of the patient's eye. The astigmatism map 56 is a map of astigmatism of the patient's eye, showing, from top to bottom, corneal astigmatism, ocular astigmatism, and internal astigmatism. The spherical aberration map 58 is a map of spherical aberration of the patient's eye, showing, from top to bottom, corneal spherical aberration, ocular spherical aberration, and internal spherical aberration. The high-order aberration map 60 is a map of high-order aberration of the patient's eye, showing, from top to bottom, corneal high-order aberration, ocular high-order aberration, and internal high-order aberration. The display control unit 34 generates the total ocular aberration map 54, the astigmatism map 56, the spherical aberration map 58, and the high-order aberration map 60 using a known method (see, for example, Patent Document 1) based on the calculation results of the intraocular aberration, corneal aberration, and internal aberration of the patient's eye, and displays them in the display field 46.

[0048] The corneal high-order aberration information 62 displays the value of the high-order aberration of the cornea of ​​the patient's eye. The corneal spherical aberration information 64 displays the value of the spherical aberration of the cornea of ​​the patient's eye. The corneal astigmatism information 66 displays the value of the astigmatism of the cornea of ​​the patient's eye. The display control unit 34 calculates the corneal high-order aberration, corneal spherical aberration, and corneal astigmatism using a known method based on the calculation results of the corneal aberration of the patient's eye, and displays the calculation results, the corneal high-order aberration information 62, the corneal spherical aberration information 64, and the corneal astigmatism information 66, in the display field 46.

[0049] The Landolt ring simulation image 68 is an image that represents how the Landolt ring appears through the patient's eye. The display control unit 34 generates the Landolt ring simulation image 68 by a known method (see, for example, Patent Documents 1 and 2) based on the wavefront aberration of the patient's eye calculated by the intraocular aberration calculation unit 32a from the Hartmann image 23, and displays the image in the display field 46.

[0050] The check box 70 accepts a start operation, specifically a check operation, for starting a simulation display of the optical characteristics of the patient's eye when the axial angle of the internal aberration corresponding to the axial angle of the IOL in the patient's eye is changed.

[0051] Fig. 3 is an explanatory diagram showing an example of the optical property screen 40 when a check operation is performed on the check box 70. As shown in Fig. 3, when the examiner performs a check operation on the check box 70, the display control unit 34 displays an operation icon 72 and axial angle information 74 on the optical property screen 40, for example, in the display field 46 (or outside the display field 46).

[0052] The operation icon 72 corresponds to the first operation unit of the present invention, and accepts a change operation for changing the parameter of the internal aberration corresponding to the aberration of the IOL, in this case, a change operation for the axial angle of the internal aberration. This change operation for the axial angle includes a rotation operation for rotating the axial angle clockwise and a rotation operation for rotating the axial angle counterclockwise.

[0053] The number, shape, and display mode of the operation icons 72 are not particularly limited as long as they allow for the operation of changing the axial angle of the internal aberration, and for example, the operation icons 72 may be displayed as a pop-up on the optical characteristics screen 40 (display field 46). Furthermore, the method of inputting the axial angle to the operation icons 72 is not particularly limited and may include touch operation, motion operation, drag operation, direct input using a keyboard, etc.

[0054] The axial angle information 74 displays the value of the axial angle of the internal aberration (corresponding to the parameter value of the present invention). Here, the axial angle of the current (before re-operation) internal aberration (IOL in the patient's eye) is set to 0 degrees, and when the axial angle is rotated clockwise by α degrees from 0 degrees by the axial angle change operation using the operation icon 72, it becomes +α degrees, and conversely, when the axial angle is rotated counterclockwise by α degrees from 0 degrees, it becomes -α degrees.

[0055] Returning to FIG. 1 , when an operation to change the axial angle of the internal aberration for the operation icon 72 is performed, the internal aberration prediction unit 35 performs a simulation to predict the internal aberration after this change operation. Specifically, the internal aberration prediction unit 35 refers to the Zernike polynomial representing the internal aberration calculated by the internal aberration calculation unit 32c. Next, the internal aberration prediction unit 35 changes the second-order term corresponding to the axial angle of the internal aberration in the Zernike polynomial representing the internal aberration. This allows the internal aberration prediction unit 35 to simulate (predict) the internal aberration after the axial angle of the internal aberration is changed. Thereafter, the internal aberration prediction unit 35 repeatedly performs the internal aberration simulation every time an operation to change the axial angle of the internal aberration for the operation icon 72 is performed.

[0056] When the internal aberration prediction unit 35 performs a simulation of the internal aberration, the recalculation unit 36 ​​performs a recalculation process of the intraocular aberration of the patient's eye based on the internal aberration of the patient's eye simulated by the internal aberration prediction unit 35 and the corneal aberration calculated by the corneal aberration calculation unit 32b. This simulates the intraocular aberration after the axial angle of the internal aberration is changed. Thereafter, the recalculation unit 36 ​​performs a recalculation process of the intraocular aberration, i.e., a simulation of the intraocular aberration, every time the internal aberration prediction unit 35 performs a new simulation of the internal aberration.

[0057] FIG. 4 is an explanatory diagram showing an example of the optical characteristics screen 40 after the operation of changing the axial angle of the internal aberration with respect to the operation icon 72 is performed. As shown in FIG. 4 , when the internal aberration prediction unit 35 performs a simulation of the internal aberration and the recalculation unit 36 ​​performs a recalculation process of the intraocular aberration, the display control unit 34 performs an update process to update the display of the optical characteristics of the patient's eye corresponding to the internal aberrations and the intraocular aberrations in the display field 46 based on the results of these processes, thereby displaying a simulation of the internal aberrations and the intraocular aberrations. Here, the optical characteristics of the patient's eye corresponding to the internal aberrations and the intraocular aberrations include various maps, images, and measurements generated or calculated based on at least one of the internal aberrations and the intraocular aberrations. For example, in this embodiment, the total ocular aberration map 54, the astigmatism map 56 excluding corneal aberrations, the spherical aberration map 58, the high-order aberration map 60, and the Landolt ring simulation image 68 are updated (simulation displayed).

[0058] Furthermore, the display control unit 34 changes the display mode of the axial angle information 74 before and after the operation to change the axial angle of the internal aberration. For example, the display mode is not particularly limited as long as the difference between the axial angle information 74 before and after the change operation and the axial angle information 74 before the change operation is clear, such as by changing the display color, font, or size of the axial angle information 74.

[0059] [Operation of the first embodiment] FIG. 5 is a flowchart showing the flow of a simulation display of the optical characteristics of a patient's eye by the ophthalmologic apparatus 10 of the first embodiment configured as described above, according to the optical characteristics display method of the present invention.

[0060] 5, when the examiner operates the monitor 14 to start measurement while the face of a patient who has undergone IOL insertion surgery is supported on a face support unit (not shown), known alignment is performed and then the measurement control unit 30 is activated. The measurement control unit 30 then controls each unit of the wavefront sensor 12 to capture a Hartmann image 23 of the patient's eye (step S1) and a corneal Meyer image 27 (step S2). As a result, the Hartmann image 23 and the corneal Meyer image 27 are input from the wavefront sensor 12 to the aberration calculation unit 32.

[0061] Next, the intraocular aberration calculation unit 32a analyzes the Hartmann image 23 and calculates the intraocular aberration of the patient's eye expressed by Zernike polynomials (step S3), and the corneal aberration calculation unit 32b analyzes the corneal Meyer image 27 and calculates the corneal aberration of the patient's eye expressed by Zernike polynomials (step S4). Then, the internal aberration calculation unit 32c calculates the internal aberration of the patient's eye expressed by Zernike polynomials based on the calculation results of the intraocular aberration by the intraocular aberration calculation unit 32a and the calculation results of the corneal aberration by the corneal aberration calculation unit 32b (step S5). Note that steps S1 to S5 correspond to the aberration acquisition step of the present invention.

[0062] When the calculation of the various aberrations of the patient's eye is completed, the display control unit 34 generates the optical characteristics screen 40 as shown in FIG. 2 based on the calculation results of each aberration, the Hartmann image 23, the corneal Meyer image 27, and the corneal axial power map 50 and K value information 52 acquired in advance, and displays it on the monitor 14 (step S6, which corresponds to the display control step of the present invention).

[0063] When performing a simulation display of the optical characteristics of the patient's eye when the axial angle is changed as a parameter of the internal aberration in the patient's eye, the examiner checks the check box 70 in the display field 46 of the optical characteristics screen 40, as shown in Fig. 3. This causes the display control unit 34 to display an operation icon 72 and axial angle information 74 in the display field 46.

[0064] Next, when the examiner starts an operation to change the axial angle of the internal aberration using the operation icon 72 (step S7, which corresponds to the operation step of the present invention), the internal aberration prediction unit 35 is activated. The internal aberration prediction unit 35 changes the second-order term corresponding to the axial angle of the internal aberration in the Zernike polynomial representing the internal aberration calculated by the internal aberration calculation unit 32c, thereby performing a simulation to predict the internal aberration of the patient's eye when this axial angle is changed (step S8, which corresponds to the prediction step of the present invention).

[0065] Then, the recalculation unit 36 ​​performs recalculation processing of the intraocular aberration of the patient's eye based on the simulation result (prediction result) of the internal aberration by the internal aberration prediction unit 35 and the corneal aberration calculated by the corneal aberration calculation unit 32b, thereby simulating the intraocular aberration of the patient's eye when the axial angle of the internal aberration is changed (step S9, corresponding to the recalculation step of the present invention).

[0066] When the recalculation process of the intraocular aberration by the recalculation unit 36 ​​is completed, the display control unit 34 performs a simulation display that updates the display of the corresponding optical characteristics in the display field 46 based on the simulation result of the internal aberration by the internal aberration prediction unit 35 and the recalculation result of the intraocular aberration by the recalculation unit 36, as shown in Fig. 4 (step S10). Note that step S10 corresponds to the update step of the present invention. This allows the examiner (doctor) and the patient to confirm how the vision in the patient's eye changes when the axial angle of the internal aberration is changed.

[0067] At the same time, the display control unit 34 changes the display mode of the axial angle information 74 in response to the operation for changing the axial angle of the internal aberration performed using the operation icon 72. This allows the examiner to recognize the axial angle of the internal aberration after the change operation, and also to recognize that a simulation display of the optical characteristics of the patient's eye corresponding to this axial angle is being performed.

[0068] Thereafter, the processes from step S8 to step S10 described above are repeatedly executed (step S11) each time an operation to change the axial angle of the internal aberration is performed using the operation icon 72. This allows the doctor to determine the optimal value of the axial angle of the internal aberration by referring to the simulation display of the optical characteristics of the patient's eye that is updated on the display field 46 with each change operation.

[0069] As described above, the ophthalmologic apparatus 10 of the first embodiment can simulate the internal aberrations and intraocular aberrations of a patient's eye when the axial angle of the internal aberration is changed, and can display a simulation of the optical characteristics of the patient's eye based on the simulation results. This makes it possible to simulate the optical characteristics of a patient's eye corresponding to changes in internal aberration parameters, such as the axial angle of the internal aberration. As a result, it is possible to provide information for doctors and patients to decide whether or not to perform reoperation, or, if reoperation is to be performed, for doctors to decide how much the axial angle of the internal aberration (IOL) should be rotated.

[0070] [Second embodiment] 6 is a block diagram of an ophthalmic apparatus 10 according to a second embodiment of the present invention. In the first embodiment, a doctor determines the optimal value of the axial angle of the internal aberration while changing the axial angle of the internal aberration. In contrast, the ophthalmic apparatus 10 according to the second embodiment has a function for optimizing the axial angle of the internal aberration, and can automatically determine this optimal value.

[0071] 6, the ophthalmologic apparatus 10 of the second embodiment has basically the same configuration as the ophthalmologic apparatus 10 of the first embodiment, except that the display control unit 34 displays an optimization icon 71 on the optical property screen 40, and the control device 16 further functions as a repetition control unit 37, an evaluation value calculation unit 38, and an optimum value determination unit 39. Therefore, components that are the same in function or configuration as those of the first embodiment are denoted by the same reference numerals, and their description will be omitted.

[0072] The optimization icon 71 corresponds to the second operation unit of the present invention and accepts an optimization operation for optimizing the axial angle of the internal aberration, which activates the repetition control unit 37, evaluation value calculation unit 38, and optimal value determination unit 39 of the control device 16.

[0073] The repetition control unit 37 performs repetition control to repeatedly execute the internal aberration simulation by the internal aberration prediction unit 35 and the intraocular aberration recalculation process by the recalculation unit 36 ​​while changing the setting of the internal aberration axial angle. As a result, the internal aberration and intraocular aberration are simulated for each internal aberration axial angle.

[0074] The evaluation value calculation unit 38 calculates an evaluation value serving as an index for optimizing the axial angle of the internal aberration for each axial angle of the internal aberration based on the intraocular aberration recalculated for each axial angle of the internal aberration by the recalculation unit 36 ​​in the above-mentioned repetitive control. Examples of this evaluation value include the modulation transfer function (MTF), which is an index of resolution, or the Strehl ratio, which is known as a method for evaluating point images. Note that methods for calculating the MTF or Strehl ratio from the intraocular aberration (wavefront aberration) of a patient's eye are well-known techniques (see Patent Documents 1 to 3 above), and therefore detailed explanations thereof will be omitted here.

[0075] Based on the evaluation value calculation results for each axial angle of the internal aberration calculated by the evaluation value calculation unit 38, the optimal value determination unit 39 determines the axial angle of the internal aberration at which the evaluation value is maximized as the optimal value, and outputs the result of determining this optimal value to the display control unit 34.

[0076] The display control unit 34 of the second embodiment selects the internal aberrations and intraocular aberrations corresponding to the optimal values ​​from the internal aberrations and intraocular aberrations for each axial angle of the internal aberrations calculated in the above-described repetitive control, based on the optimal value of the axial angle of the internal aberration determined by the optimal value determination unit 39. Then, the display control unit 34 performs a simulation display that updates the display of the corresponding optical characteristics in the display field 46, based on the internal aberrations and intraocular aberrations corresponding to the optimal values.

[0077] In addition, when the optimal value determination unit 39 determines the optimal value of the axial angle of the internal aberration, the internal aberration prediction unit 35 may perform a simulation of the internal aberration corresponding to the optimal value, and the recalculation unit 36 ​​may perform a recalculation process of the intraocular aberration.

[0078] 7 is a flowchart showing the flow of the simulation display of the optical characteristics of a patient's eye by the ophthalmologic apparatus 10 of the second embodiment. Note that the processes from step S1 to step S6 are the same as those in the first embodiment described with reference to FIG. 5, and therefore will not be described here.

[0079] When optimizing the axial angle of the internal aberration, the examiner performs an optimization operation by touching the optimization icon 71 in the optical property screen 40 (step S7A). When this optimization operation is performed, the repetition control unit 37, evaluation value calculation unit 38, and optimal value determination unit 39 of the control device 16 are activated.

[0080] Next, the repetitive control unit 37 starts repetitive control to repeatedly execute (step S7E) the change of the axial angle of the internal aberration (step S7B), the simulation of the internal aberration by the internal aberration prediction unit 35 (step S7C), and the recalculation process of the intraocular aberration by the recalculation unit 36 ​​(step S7D). As a result, the internal aberration and intraocular aberration of the patient's eye are simulated for each axial angle of the internal aberration.

[0081] Furthermore, the evaluation value calculation unit 38 calculates an evaluation value for each axial angle of the internal aberration based on the intraocular aberrations recalculated for each axial angle of the internal aberration by the recalculation unit 36. The calculation of the evaluation value by the evaluation value calculation unit 38 may be performed after the completion of the above-mentioned repetitive control as shown in Fig. 7, or may be performed each time the recalculation unit 36 ​​recalculates the intraocular aberration while the repetitive control is being performed.

[0082] When the evaluation value calculation unit 38 has completed the calculation of all evaluation values ​​for each axial angle of the internal aberration, the optimal value determination unit 39 determines the optimal value of the axial angle of the internal aberration based on the calculation results of each evaluation value, and outputs the determined optimal value to the display control unit 34 (step S7G).

[0083] Then, the display control unit 34 performs a simulation display that updates the display of the corresponding optical characteristics in the display field 46, similar to the first embodiment, based on the internal aberrations and intraocular aberrations corresponding to the optimal value of the axial angle of the internal aberration determined by the optimal value determination unit 39 (step S10).

[0084] As described above, the ophthalmologic apparatus 10 of the second embodiment can automatically optimize the axial angle of the internal aberration, and therefore, this optimization can be performed easily and in a short time.

[0085] [Third embodiment] Fig. 8 is a block diagram of the ophthalmologic apparatus 10 of the third embodiment. Fig. 9 is a flowchart showing the flow of a simulation display of the optical characteristics of a patient's eye by the ophthalmologic apparatus 10 of the third embodiment.

[0086] In the ophthalmic apparatus 10 of each of the above embodiments, the wavefront sensor 12 captures a Hartmann image 23 and a corneal Meyer image 27 of the patient's eye, and the intraocular aberration, corneal aberration, and internal aberration of the patient's eye are acquired by analyzing the Hartmann image 23 and the corneal Meyer image 27 in the aberration calculation unit 32. In contrast, the ophthalmic apparatus 10 of the third embodiment acquires measurement results of the intraocular aberration, corneal aberration, and internal aberration of the patient that have been measured in the past.

[0087] 8, the ophthalmic apparatus 10 of the third embodiment has basically the same configuration as the ophthalmic apparatus 10 of each of the above-described embodiments, except that the control device 16 is provided with a storage unit 80 and a search unit 82. Therefore, components that are the same in function or configuration as those of the above-described embodiments are given the same reference numerals and their description will be omitted. Note that in the third embodiment (the same applies to the fourth embodiment described below), the control device 16 alone functions as the optical property display device of the present invention.

[0088] The storage unit 80 corresponds to the first storage unit of the present invention, and stores past data 81 including measurement results of intraocular aberrations, corneal aberrations, and internal aberrations for each patient that have been measured in the past. This past data 81 associates, for example, patient IDs (identification), which are unique identification information for multiple patients, with the intraocular aberrations, corneal aberrations, and internal aberrations for each patient. The storage unit 80 may be provided outside the control device 16 (for example, an external server).

[0089] The search unit 82 corresponds to the aberration acquisition unit of the present invention, and acquires the intraocular aberration, corneal aberration, and internal aberration corresponding to the patient ID from the past data 81 in the storage unit 80.

[0090] For example, the optical characteristics screen 40 has an ID input field (not shown) for inputting a patient ID. As shown in FIG. 9, when the examiner inputs the patient ID into this ID input field (step S1A), the search unit 82 refers to the past data 81 in the memory unit 80 and obtains the intraocular aberration, corneal aberration, and internal aberration corresponding to the patient ID (steps S1B and S1C).

[0091] In this way, the search unit 82 acquires the intraocular aberration, corneal aberration, and internal aberration, thereby making it possible to execute the processing from step S6 onwards shown in Figure 5 of the first embodiment, or to execute the processing from step S6 onwards shown in Figure 7 of the second embodiment.

[0092] As described above, in the third embodiment, by acquiring the intraocular aberrations, corneal aberrations, and internal aberrations from the past data 81 in the storage unit 80, it is possible to perform a simulation of the internal aberrations and intraocular aberrations of the patient's eye and to display a simulation of the optical characteristics of the patient's eye without capturing the Hartmann image 23 and the corneal Meyer image 27 with the wavefront sensor 12. As a result, it is possible to reduce the work of the examiner and the burden on the patient. Furthermore, the above-mentioned simulation and simulation display can be performed at a location different from the location where the aberrations of the patient's eye are measured.

[0093] [Fourth embodiment] 10 is a block diagram showing an ophthalmic apparatus 10 according to a fourth embodiment. In the ophthalmic apparatus 10 according to the third embodiment, past data 81 indicating the measurement results of the patient's intraocular aberration, corneal aberration, and internal aberration is stored in the storage unit 80. However, in the ophthalmic apparatus 10 according to the fourth embodiment, past data 81A different from the past data 81 is stored in the storage unit 80 as shown in FIG.

[0094] The ophthalmologic apparatus 10 of the fourth embodiment has basically the same configuration as the ophthalmologic apparatus 10 of the third embodiment, except that past data 81A is stored in the storage unit 80. Therefore, components that are the same in function or configuration as those of the above embodiments are denoted by the same reference numerals and their description will be omitted. The storage unit 80 of the fourth embodiment corresponds to the second storage unit of the present invention.

[0095] The past data 81A associates, for example, a patient ID for each patient with information (hereinafter referred to as calculation information) required for calculating each aberration (intraocular aberration, corneal aberration, and internal aberration) for each patient. The calculation information includes, for example, the Hartmann image 23 of the patient's eye, the corneal Meyer image 27, the center of gravity positions of the Hartmann image 23 and the Placido ring, and the analytical center for aberration calculation.

[0096] The search unit 82 of the fourth embodiment, together with the aberration calculation unit 32, constitutes the aberration acquisition unit of the present invention. When the examiner inputs a patient ID in the ID input field on the optical property screen 40, the search unit 82 references the past data 81A in the storage unit 80 to acquire calculation information corresponding to the patient ID. Then, the search unit 82 outputs the acquired calculation information to the aberration calculation unit 32.

[0097] The aberration calculation unit 32 (intraocular aberration calculation unit 32a, corneal aberration calculation unit 32b, and internal aberration calculation unit 32c) of the fourth embodiment calculates the intraocular aberration, corneal aberration, and internal aberration of the patient's eye, similarly to the first and second embodiments, based on the calculation information input from the search unit 82. This makes it possible to execute the processes from step S6 onwards shown in Fig. 5 of the first embodiment, or to execute the processes from step S6 onwards shown in Fig. 7 of the second embodiment, similarly to the third embodiment.

[0098] As described above, in the fourth embodiment as well, by acquiring calculation information from the storage unit 80 (past data 81A), it is possible to perform a simulation of the internal aberrations and intraocular aberrations of the patient's eye and to display a simulation of the optical characteristics of the patient's eye without capturing the Hartmann image 23 and the corneal Meyer image 27 with the wavefront sensor 12. As a result, the same effects as in the third embodiment can be obtained.

[0099] [Fifth embodiment] Fig. 11 is a diagram showing an example of the optical characteristics screen 40 of the fifth embodiment, which allows the user to change the power of the IOL as a parameter of the internal aberration. Fig. 12 is a diagram showing an example of the optical characteristics screen 40 of the fifth embodiment, which allows the user to change the position of the IOL as a parameter of the internal aberration.

[0100] In each of the above embodiments, a simulation display of the optical characteristics of a patient's eye is performed when the axial angle of the internal aberration is changed as a parameter of the internal aberration, but the ophthalmic apparatus 10 of the fifth embodiment displays a simulation display of the optical characteristics of a patient's eye when parameters other than the axial angle are changed, such as the power and position of the IOL, etc. Note that the ophthalmic apparatus 10 of the fifth embodiment has basically the same configuration as the ophthalmic apparatus 10 of each of the above embodiments, and therefore, components that are the same in function or configuration as those of each of the above embodiments are assigned the same reference numerals and their description will be omitted.

[0101] As shown in FIG. 11, in a mode for simulating and displaying the optical characteristics of a patient's eye when the power of the IOL in the patient's eye is changed (i.e., the IOL is replaced), the display control unit 34 of the fifth embodiment displays a check box 70A on the optical characteristics screen 40.

[0102] The check box 70A accepts a start operation (check operation) for starting a simulation display of the optical characteristics of the patient's eye when the power of the IOL in the patient's eye is changed. When the examiner checks the check box 70A, the display control unit 34 displays an operation icon 72A and power information 74A in the optical characteristics screen 40.

[0103] The operation icon 72A (corresponding to the first operation unit) accepts a change operation for changing the power of the IOL. This change operation for the power of the IOL includes an operation for increasing the power of the IOL and an operation for decreasing the power.

[0104] The power information 74A displays the value of the IOL power (corresponding to the parameter value of the present invention). As in the above embodiments, the display control unit 34 changes the display mode of the power information 74A before and after the operation to change the IOL power.

[0105] Furthermore, as shown in FIG. 12, the display control unit 34 of the fifth embodiment displays an optical characteristics screen 40 in a mode for performing a simulation display of the optical characteristics of the patient's eye when the position of the IOL in the patient's eye is changed.

[0106] The check box 70B accepts a start operation (check operation) for starting a simulation display of the optical characteristics of the patient's eye when the position of the IOL in the patient's eye is changed. When the examiner checks the check box 70B, the display control unit 34 displays an operation icon 72B and position information 74B in the optical characteristics screen 40.

[0107] The operation icon 72B (corresponding to the first operation unit) accepts an operation to change (decenter) the position of the IOL. The operation to change the position of the IOL includes an operation to individually change the X and Y positions of the IOL in the patient's eye.

[0108] The position information 74B displays the XY position (XY coordinates) of the IOL in the patient's eye. As in the above embodiments, the display controller 34 changes the display mode of the position information 74B before and after the operation to change the position of the IOL.

[0109] When an operation to change the power of the IOL is performed using the operation icon 72A, or when an operation to change the position of the IOL is performed using the operation icon 72B, the internal aberration prediction unit 35 of the fifth embodiment performs a simulation to predict the internal aberration after this change operation.

[0110] For example, when an operation to change the power of the IOL is performed, the internal aberration prediction unit 35 simulates the internal aberration after the change in the power of the IOL by changing the second-order term corresponding to the power of the IOL in the Zernike polynomial that represents the internal aberration.Furthermore, when an operation to change the position of the IOL is performed, the internal aberration prediction unit 35 recalculates the internal aberration to simulate the internal aberration after the position of the IOL is changed.

[0111] Thereafter, similarly to the above-described embodiments, the recalculation unit 36 ​​recalculates the intraocular aberration, and the display control unit 34 displays a simulation of the optical characteristics of the patient's eye.

[0112] It is also possible to change parameters of internal aberrations other than the axial angle, power, and position. In this case, the internal aberration prediction unit 35 simulates the internal aberrations, the recalculation unit 36 ​​recalculates the intraocular aberrations, and the display control unit 34 displays a simulation of the optical characteristics of the patient's eye.

[0113] Furthermore, for example, by simultaneously displaying each operation icon 72, 72A, and 72B on the optical characteristics screen 40, it is possible to perform changes to multiple parameters of internal aberrations in parallel, thereby simulating the internal aberrations after changing multiple parameters, recalculating the intraocular aberrations, and displaying a simulation of the optical characteristics of the patient's eye.

[0114] As described above, the fifth embodiment can also provide information for doctors and patients to decide whether or not to perform reoperation on the patient's eye, or, if reoperation is to be performed, whether or not to change the power and position of the IOL.

[0115] [others] In each of the above embodiments, the operation icons 72, 72A, and 72B displayed on the optical characteristics screen 40 are used to change various internal aberration parameters, or the optimization icon 71 displayed on the optical characteristics screen 40 is used to perform optimization operations for various parameters. However, the input method for the change operations and optimization operations is not particularly limited, and various known operation units may be used.

[0116] In each of the above embodiments, the wavefront sensor 12 (first imaging system 22, second imaging system 26) is used to acquire the intraocular aberration, corneal aberration, and internal aberration of the patient's eye, but the method for acquiring the various aberrations of the patient's eye is not particularly limited, and other known methods may be used.

[0117] In each of the above embodiments, the optical characteristics corresponding to the corneal aberration of the patient's eye (corneal axial power map 50, K value information 52, corneal high-order aberration information 62, corneal spherical aberration information 64, corneal astigmatism information 66, etc.) are displayed on the optical characteristics screen 40, but the display of the optical characteristics corresponding to the corneal aberration may be omitted.

[0118] In the above embodiments, the cases where each aberration of the patient's eye (intraocular aberration, corneal aberration, and internal aberration) is expressed by Zernike polynomials have been described as examples, but each aberration may be expressed by other functions such as Taylor expansion polynomials or spherical harmonic functions.

[0119] In each of the above embodiments, the case where a simulation display of the optical characteristics of a patient's eye into which a toric IOL has been inserted has been described as an example, but the present invention can also be applied to the case where a simulation display of the optical characteristics of a patient's eye into which a known intraocular lens other than a toric IOL has been inserted. [Explanation of symbols]

[0120] 10 Ophthalmological equipment 12 Wavefront sensor 14 monitors 16 Control device 20 Lighting System 22 First Imaging System 23 Hartmann Statue 24 Projection system 26 Second Imaging System 27 Corneal Meyer image 30 Measurement control section 32 Aberration calculation unit 32a Intraocular aberration calculation unit 32b Corneal aberration calculation unit 32c Internal aberration calculation unit 34 Display control unit 35 Internal aberration prediction unit 36 Recalculation section 37 Repeat control section 38 Evaluation value calculation unit 39 Optimum value determination section 40 Optical properties screen 42 Left / Right Eye Switch Button 44 Layout switch button 46 Display field 50 Corneal Axial Power Map 52 K value information 54 Total eye aberration map 56 Astigmatism Map 58 Spherical Aberration Map 60 High-order aberration maps 62 Corneal higher-order aberration information 64 Corneal spherical aberration information 66 Corneal Astigmatism Information 68 Landolt ring simulation image 70, 70A, 70B check boxes 71 Optimization Icon 72, 72A, 72B operation icons 74 Axis angle information 74A Frequency information 74B Location information 80 Storage section 81,81A Historical Data 82 Search Section

Claims

1. an aberration acquisition unit that acquires intraocular aberration, corneal aberration, and internal aberration of a patient's eye into which an intraocular lens has been inserted; a display control unit that displays optical characteristics of the patient's eye on a monitor based on at least the intraocular aberration and the internal aberration among the intraocular aberration, the corneal aberration, and the internal aberration acquired by the aberration acquisition unit; and a first operation unit that accepts a change operation to change only one or more parameters of the internal aberration in the patient's eye; an internal aberration prediction unit that predicts the internal aberration after the parameter is changed in response to the change operation on the first operation unit; a recalculation unit that recalculates the intraocular aberration based on the internal aberration predicted by the internal aberration prediction unit and the corneal aberration acquired by the aberration acquisition unit; Equipped with an optical characteristic display device, wherein the display control unit performs an update process to update the optical characteristics displayed on the monitor based on the internal aberration predicted by the internal aberration prediction unit and the intraocular aberration recalculated by the recalculation unit.

2. The optical characteristic display device according to claim 1 , wherein the display control unit causes the monitor to display an operation icon indicating the first operation unit in addition to the optical characteristic.

3. 3. The optical property display device according to claim 1, wherein each time the parameter change operation is repeatedly executed by the first operation unit, the prediction of the internal aberration by the internal aberration prediction unit, the recalculation of the intraocular aberration by the recalculation unit, and the update processing by the display control unit are repeatedly executed.

4. a second operation unit that accepts an optimization operation for optimizing the parameters; a repetition control unit that, when the optimization operation is performed by the second operation unit, repeatedly executes the prediction of the internal aberration by the internal aberration prediction unit and the recalculation of the intraocular aberration by the recalculation unit while changing the parameters; an evaluation value calculation unit that calculates, for each parameter, an evaluation value that serves as an index for optimizing the parameter based on the intraocular aberration recalculated for each parameter by the recalculation unit; an optimal value determination unit that determines optimal values ​​of the parameters based on the calculation results of the evaluation values ​​for the parameters by the evaluation value calculation unit; The optical property display device according to claim 1 , comprising:

5. 5. The optical characteristic display device according to claim 4, wherein the evaluation value is a modulation transfer function or a Strehl ratio.

6. The optical property display device according to claim 4 or 5, wherein the display control unit selects the internal aberrations and intraocular aberrations corresponding to the optimal value determined by the optimal value determination unit from the internal aberrations and intraocular aberrations for each parameter, and performs the update process based on the internal aberrations and intraocular aberrations corresponding to the optimal value.

7. An optical property display device described in any one of claims 1 to 6, wherein the display control unit displays the value of the parameter on the monitor and changes the display mode of the value of the parameter displayed on the monitor before and after the change operation on the first operation unit.

8. The aberration acquisition unit a first imaging system that captures a Hartmann image of the patient's eye; an intraocular aberration calculation unit that calculates the intraocular aberration based on the Hartmann image captured by the first imaging system; a second imaging system that captures an image of an anterior segment of the patient's eye onto which a predetermined pattern of light is projected; a corneal aberration calculation unit that calculates the corneal aberration based on the anterior eye image captured by the second imaging system; an internal aberration calculation unit that calculates the internal aberration based on a calculation result of the intraocular aberration by the intraocular aberration calculation unit and a calculation result of the corneal aberration by the corneal aberration calculation unit; The optical property display device according to claim 1 , comprising:

9. a first storage unit that stores the intraocular aberration, the corneal aberration, and the internal aberration that have been measured in advance; The optical property display device according to claim 1 , wherein the aberration acquisition unit acquires the intraocular aberration, the corneal aberration, and the internal aberration from the first storage unit.

10. a second storage unit that stores information necessary for calculating the intraocular aberration, the corneal aberration, and the internal aberration of the patient's eye, including a Hartmann image of the patient's eye and an anterior segment image of the patient's eye onto which a predetermined pattern light is projected; The aberration acquisition unit an intraocular aberration calculation unit that calculates the intraocular aberration based on the information stored in the second storage unit; a corneal aberration calculation unit that calculates the corneal aberration based on the information stored in the second storage unit; an internal aberration calculation unit that calculates the internal aberration based on the information stored in the second storage unit; The optical property display device according to claim 1 , comprising:

11. The optical property display device according to claim 1 , wherein the parameters include at least one of an axial angle, a power, and a position of the intraocular lens.

12. an aberration acquisition step of acquiring intraocular aberrations, corneal aberrations, and internal aberrations of a patient's eye into which an intraocular lens has been inserted, the intraocular aberrations, corneal aberrations, and internal aberrations being expressed by functions; a display control step of displaying optical characteristics of the patient's eye on a monitor based on at least the intraocular aberration and the internal aberration among the intraocular aberration, the corneal aberration, and the internal aberration acquired in the aberration acquisition step; an operation step of accepting a change operation for changing only the parameters of the internal aberration in the patient's eye; a prediction step of predicting the internal aberration after the parameter is changed in accordance with the change operation in the operation step; a recalculation step of performing a recalculation process of the intraocular aberration based on the internal aberration predicted in the prediction step and the corneal aberration acquired in the aberration acquisition step; an updating step of performing an updating process to update the optical characteristics to be displayed on the monitor based on the internal aberration predicted in the prediction step and the intraocular aberration recalculated in the recalculation step; An optical characteristic display method comprising:

Images