Measurement evaluation using information from multiple measuring devices

Abstract

An ophthalmic system for measuring an eye includes measurement data and a computer. The measurement device includes an optical coherence tomography (OCT) device and an aberrometer. The OCT device measures the eye by directing OCT light to the eye and detecting the OCT light reflected from the eye. The aberrometer measures the eye by directing aberrometer light to the eye and detecting the aberrometer light reflected from the eye. The computer generates an eye model of the eye according to the reflected OCT light. The eye model includes eye parameters, each parameter being assigned a value. The computer identifies an OCT-based wavefront according to the eye model, identifies an aberrometer-based wavefront according to the reflected aberrometer light, determines a deviation between the OCT-based wavefront and the aberrometer-based wavefront, and evaluates measurements from one or more of the measurement devices according to the deviation.

Description

Technical Field

[0001] The present disclosure generally relates to ophthalmic measurement devices, and more particularly to evaluating measurement values using information from multiple measurement devices.

Background Art

[0002] Ophthalmic measurement systems typically address specific applications. For example, dedicated systems provide measurement values for calculating the refractive power of an intraocular lens (IOL) in cataract surgery. Systems generally do not have multiple devices that provide measurement values for the same thing. Therefore, it can be difficult to detect measurement errors. Some physicians use measurement values from multiple systems to check for errors or calculate the average of the outputs from multiple systems to obtain a measurement value. Such techniques are time-consuming and often inefficient in obtaining accurate measurement values.

Summary of the Invention

Means for Solving the Problems

[0003] In certain embodiments, an ophthalmic system for measuring an eye includes a measurement device and a computer. The measurement device includes an optical coherence tomography (OCT) device and a aberrometer. The OCT device directs OCT light toward the eye and detects the OCT light reflected from the eye to measure the eye. The aberrometer directs aberrometer light toward the eye and detects the aberrometer light reflected from the eye to measure the eye. The computer generates an eye globe model according to the reflected OCT light. The eye globe model includes parameters of the eye, and a value is assigned to each parameter. The computer identifies an OCT-based wavefront according to the eye globe model, identifies an aberrometer-based wavefront according to the reflected aberrometer light, determines a deviation between the OCT-based wavefront and the aberrometer-based wavefront, and evaluates measurement values from one or more of the measurement devices according to the deviation.

[0004] The embodiments may not include any of the following features, or may include one, some, or all of them: The computer evaluates the measurement by identifying one or more issues related to the misalignment. One or more issues may be related to the measurement conditions or the measurement device. One or more issues may be tear film instability, inaccurate lens topography parameters, improper patient fixation, improper device alignment, and / or improper device calibration.

[0005] The computer evaluates the measurement by identifying one or more measuring devices associated with the deviation.

[0006] The measuring device includes a topograph that directs topographic light towards the eye and detects the topographic light reflected from the eye. A computer generates an eyeball model of the eye by identifying the OCT-based anterior corneal surface from the eyeball model, identifying the topographic-based anterior corneal surface from the reflected topographic light, and checking the eyeball model by comparing the OCT-based anterior corneal surface with the topographic-based anterior corneal surface. The computer may evaluate one or more measurements by identifying one or more related problems, including problems selected from a group consisting of insufficient sampling, tear film instability, improper device alignment, and improper device calibration.

[0007] The computer calculates the OCT-based spherical and cylindrical frequency parameters of the wavefront simulated through the eyeball model, and the aberration-based spherical and cylindrical frequency parameters of the wavefront, and determines the discrepancy between the OCT-based and aberration-based wavefronts by comparing the OCT-based and aberration-based spherical and cylindrical frequency parameters with those of the aberration-based wavefront. The computer may evaluate one or more measurements by identifying one or more related issues, including inaccurate axial length measurements, improper patient fixation, improper device alignment, and / or improper device calibration.

[0008] The computer identifies one or more aberration-based values ​​for the aberration-based wavefront, identifies one or more OCT-based values ​​for the eyeball model, and determines the discrepancy between the OCT-based wavefront and the aberration-based wavefront by comparing one or more aberration-based values ​​with the OCT-based values. One or more aberration-based values ​​may include the slope of one or more aberration-based values ​​for the aberration-based wavefront. One or more OCT-based values ​​may include the slope of one or more OCT-based values ​​for one or more rays emanating from the eyeball model.

[0009] The computer adjusts one or more values ​​assigned to one or more parameters by repeatedly adjusting one or more values ​​to generate a tuned eye model, identifying the OCT-based wavefront tuned according to the tuned eye model, and comparing the tuned OCT-based wavefront with the aberration-based wavefront to check whether they meet the predefined tolerances, until the tuned OCT-based wavefront and the aberration-based wavefront meet the predefined tolerances.

[0010] The OCT device checks the eyeball model by directing the next OCT light at an angle different from the angle of the previous OCT light towards the eye and detecting the next OCT light reflected from the eye. The aberration meter checks the eyeball model by directing the next aberration meter light at an angle different from the angle of the aberration meter light towards the eye and detecting the next aberration meter light reflected from the eye. The computer checks the eyeball model by generating the next eyeball model of the eye according to the reflected next OCT light, generating the next aberration meter-based wavefront according to the reflected next aberration meter light, identifying the next OCT-based wavefront according to the next eyeball model, and comparing the next OCT-based wavefront with the previous aberration meter-based wavefront.

[0011] In certain embodiments, an ophthalmic system for measuring the eye includes a measuring device and a computer. The measuring device includes an optical coherence tomography (OCT) device and a topograph. The OCT device directs OCT light towards the eye and detects the OCT light reflected from the eye. The topograph directs topograph light towards the eye and detects the topograph light reflected from the eye. The computer identifies the anterior corneal surface of the OCT base from the reflected OCT light, identifies the anterior corneal surface of the topograph base from the reflected topograph light, determines the displacement between the anterior corneal surface of the OCT base and the anterior corneal surface of the topograph base, and evaluates the anterior corneal surface of the OCT base and the anterior corneal surface of the topograph base according to the displacement.

[0012] The embodiments may not include any of the following features, or may include one, some, or all of them: A computer evaluates the OCT-based and topograph-based anterior corneal surface by identifying one or more issues related to misalignment. One or more related issues may be related to measurement conditions or measurement devices. One or more related issues may include insufficient sampling, improper device alignment, and / or improper device calibration.

[0013] The computer evaluates the anterior corneal surface using OCT-based and topography-based methods by identifying one or more measurement devices associated with the displacement.

[0014] The measuring device includes an aberration meter that directs aberration meter light towards the eye and detects the aberration meter light reflected from the eye. A computer generates an eyeball model of the eye according to the reflected OCT light. The eyeball model includes parameters of the eye, each parameter to which a value is assigned. The computer identifies an OCT-based wavefront according to the eyeball model, identifies an aberration meter-based wavefront according to the reflected aberration meter light, compares the OCT-based wavefront with the aberration meter-based wavefront, and evaluates one or more measurements from one or more of the plurality of measuring devices according to the comparison.

[0015] In certain embodiments, an ophthalmic system for measuring the eye includes measuring devices and a computer. The measuring devices include an optical coherence tomography (OCT) device, an aberration meter, and a topograph. The OCT device directs OCT light at the eye and measures the eye by detecting the OCT light reflected from the eye. The aberration meter directs aberration meter light at the eye and measures the eye by detecting the aberration meter light reflected from the eye. The topograph directs topograph light at the eye and detects the topograph light reflected from the eye. The computer generates an eyeball model of the eye according to the reflected OCT light. The eyeball model includes parameters of the eye, each parameter to which a value is assigned. The eyeball model is generated by identifying the OCT-based anterior corneal surface from the eyeball model, identifying the topograph-based anterior corneal surface from the reflected topograph light, and checking the eyeball model by comparing the OCT-based anterior corneal surface with the topograph-based anterior corneal surface. The computer identifies the OCT-based wavefront according to the eyeball model, identifies the aberration-based wavefront according to the reflected aberration-meter light, and determines the difference between the OCT-based wavefront and the aberration-meter-based wavefront. The discrepancy between the OCT-based wavefront and the aberration-based wavefront is determined by calculating the OCT-based spherical and cylindrical frequency parameters of the wavefront simulated through the eyeball model, calculating the aberration-based spherical and cylindrical frequency parameters of the aberration-based wavefront, comparing the OCT-based spherical and cylindrical frequency parameters with the aberration-based spherical and cylindrical frequency parameters, identifying one or more aberration-based values ​​for the aberration-based wavefront, identifying one or more OCT-based values ​​for the eyeball model, and comparing one or more aberration-based values ​​with the OCT-based values, where one or more aberration-based values ​​include the slope of one or more aberration-based waveforms, and one or more OCT-based values ​​include the slope of one or more OCT rays emanating from the eyeball model.The computer identifies one or more problems related to the misalignment and associated with the measurement conditions or measuring devices, the one or more associated problems being selected from a group consisting of inaccurate axial length measurement, insufficient sampling, lacrimal instability, inaccurate lens topography parameters, improper patient fixation, improper device alignment, and improper device calibration, and by identifying one or more measuring devices associated with the misalignment, it evaluates one or more measurements from one or more measuring devices according to the misalignment. The computer adjusts one or more values ​​assigned to one or more parameters by repeatedly adjusting one or more values ​​to generate an adjusted eye model, identifying the adjusted OCT-based wavefront according to the adjusted eye model, and comparing the adjusted OCT-based wavefront with the aberration-based wavefront to check whether they meet the predefined tolerances, until the adjusted OCT-based wavefront and aberration-based waveform meet the predefined tolerances. The OCT device checks the eyeball model by directing the next OCT light at a different angle than the previous OCT light and detecting the next OCT light reflected from the eye. The aberration meter checks the eyeball model by directing the next aberration meter light at a different angle than the previous aberration meter light and detecting the next aberration meter light reflected from the eye. The computer checks the eyeball model by generating the next eyeball model of the eye according to the reflected next OCT light, generating the next aberration meter-based wavefront according to the reflected next aberration meter light, identifying the next OCT-based wavefront according to the next eyeball model, and comparing the next OCT-based wavefront with the next aberration meter-based wavefront. [Brief explanation of the drawing]

[0016] [Figure 1] An example of a system for evaluating eye measurements according to a specific embodiment is shown. [Figure 2] An example of an OCT device for measuring the anterior surface of the cornea is shown. [Figure 3] An example of a topograph used to measure the anterior surface of the cornea is shown. [Figure 4]An example of OCT light and aberration meter light interacting with the eye is shown. [Figure 5A] This example demonstrates how to apply a ray tracing procedure to identify the location of the anatomical interface of the eye and generate an eyeball model. [Figure 5B] This example demonstrates how to apply a ray tracing procedure to identify the location of the anatomical interface of the eye and generate an eyeball model. [Figure 6] An example of a method for evaluating eye measurements, which can be performed by the system shown in Figure 1 according to a specific embodiment, is shown. [Modes for carrying out the invention]

[0017] Description of Embodiments Herein, examples of embodiments of the disclosed apparatus, systems, and methods are described in detail with reference to the description and drawings. The description and drawings are not intended to be exhaustive, nor are they intended to limit the claims to any particular embodiment shown in the drawings and disclosed in the description. The drawings represent possible embodiments, but they are not necessarily to scale, and certain features may be simplified, exaggerated, omitted, or partially divided to better illustrate the embodiments.

[0018] Embodiments of the disclosed systems and methods evaluate measurements from a measuring device by comparing measurements from another device with measurements from another device. In certain embodiments, measurements are compared by comparing the wavefronts derived from the measurements.

[0019] Figure 1 shows an example system 10 for evaluating measurements of an eye 12 according to a particular embodiment. In this example, system 10 includes a computer 20 (including logic 22, memory 24, and interface 26), a measuring device 28, and an optical system 36, coupled as shown. The measuring device 28 includes an optical coherence tomography (OCT) device 30, an aberration meter 32, and a topographer 34, coupled as shown.

[0020] According to an example of operation, the computer 20 generates an eye model of the eye 12 according to measurement values from the OCT device 30. The computer 20 identifies an OCT-based wavefront from the eye model and an aberrometer-based wavefront from the aberrometer 32. The computer 20 compares the OCT-based wavefront with the aberrometer-based wavefront. If there is a deviation, the computer evaluates the measurement values according to the deviation.

[0021] Looking at the parts of the system 10, the measurement device 28 includes the OCT device 30, the aberrometer 32, and the topographer 34. The OCT device 30 directs OCT light at the eye 12 and detects the OCT light reflected from a part of the eye 12 to generate an image of that part. The OCT device 30 can be any suitable device that uses OCT to acquire two-dimensional or three-dimensional images from a light-scattering medium, such as within eye tissue. The OCT device 30 can use time domain, frequency domain, or other suitable spectral encoding and can use single-point scanning, parallel scanning, or other suitable scanning. An example of the operation will be described in more detail with reference to FIG. 2.

[0022] FIG. 2 shows an example of an OCT device 30 that measures the anterior corneal surface 58 of the eye 12. Generally, the OCT device 30 detects the reflection of light from an interface between media, such as between air and the eye 12 or between parts of the eye 12, such as between the cornea and the aqueous humor. The OCT device 30 records the optical path length of the detected light and converts the optical path length into a physical distance. In certain embodiments, the raw data from the OCT device 30 is converted so that the distance to the interface of the eye 12 is represented "as in air", i.e., without considering the refractive index of the tissue.

[0023] In the illustrated example, the OCT device 30 detects the reflection of light from the anterior corneal surface 58, records the optical path length of the detected light, and represents the distance to the anterior corneal surface 58 "as in air". The surface 58 can be constructed in the eye model using the distances to different points on the surface 58. The OCT device 30 measures the distances to interfaces between other parts of the eye 12 subject to fluctuations to construct the remaining part of the eye model.

[0024] Returning to Figure 1, the aberration meter 32 directs aberration meter light towards the eye 12 and detects the aberration meter light reflected from the eye 12. The aberration meter 32 uses aberration measurement techniques (i.e., wavefront techniques) to measure how the light travels through the eye 12 to the retina that reflects the light back to the eye. Aberrations in the eye cause the light to take on different shapes, which can be used to characterize the aberrations. The aberration meter 32 generates a wavefront map (e.g., a Zernike coefficient map) from the reflected light. The Hartmann-Shack aberration meter is an example of the aberration meter 32.

[0025] The reflective topograph 34 directs topographic light towards the eye and detects the topographic light reflected from the eye to measure the shape of the anterior surface of the cornea 58. In certain embodiments, measurements from the topograph 34 and the OCT device 30 are used to construct an eyeball model of the anterior surface of the cornea 58. An example of operation is described in more detail with reference to Figure 3.

[0026] Figure 3 shows a topographer 34, an example of a reflective topographer used to measure the anterior surface of the cornea of ​​an eye 12. In this example, the topographer 34 includes an illumination system 60 and a sensor 62. The illumination system 60 directs topographer light onto the eye. The light projects a pattern (e.g., a grid of concentric rings or dots) onto the anterior surface 58 of the cornea. The sensor 62 (e.g., a camera) detects the topographer light reflected from the eye and generates an image of the reflected light. The image is analyzed to identify features of the eye, such as the shape of the surface 58. If the surface is an ideal sphere, the reflected pattern matches the projected pattern. If there are aberrations on the surface, areas where the reflective parts of the pattern (e.g., rings or dots) are close together may show a larger corneal curvature, while areas where the parts are far apart may show a flatter area. The topographer 34 can output results in the form of surface maps, such as axial, tangential, refractive power, or altitude maps.

[0027] Returning to Figure 1, multiple measuring devices 28 can acquire measurements sequentially and / or simultaneously. To compare the measurements, they should be aligned. In certain cases, the measurements can be aligned using eye features 12, such as pupil or iris markings. In other cases, the measurements can be aligned using eye tracking capabilities. In other cases, the measuring devices 28 can perform measurements along the same optical path so that the eyes 12 have the same alignment in the measurements. An example of the measuring devices 28 performing measurements along the same optical path is illustrated with reference to Figure 4.

[0028] Figure 4 shows an example of OCT light 54 and aberration meter light 56 ​​interacting with the eye 12. In this example, the eye 12 includes ocular components, such as the cornea 40, aqueous humor 42, iris 44, lens 46, vitreous humor 50, and retina 52. In certain embodiments, one or more surfaces of the eye 12 components and / or interfaces between the eye 12 components may be considered anatomical interfaces that can be used to generate an eyeball model. For example, anatomical interfaces may include the anterior surface of the cornea 40; between the cornea 40, aqueous humor 42, iris 44, lens 46, vitreous humor 50, and / or retina 52; and the retina 52.

[0029] In the example, the OCT beam 54 enters the cornea 40, and the aberration ray 56 is reflected from the retina 52. If the eye 12 has ideal normal vision (no optical aberrations), each OCT ray 54 has a reflected wavefront ray 56 that travels in the opposite direction along the exact same optical path. If the eye 12 has optical aberrations, the aberrations cause the rays 54, 56 from the measuring device 28 to travel through the eye 12 along different paths. In the illustrated example, the OCT beams 54 are parallel. However, the OCT beams 54 may have any other suitable beam geometry, such as a single-scan OCT beam. As long as the beam geometry is known, the path of the OCT beams 54 can be determined.

[0030] Returning to Figure 1, the optical system 36 includes one or more optical elements that direct light from the measuring device 28 towards the eye 12. The optical elements may act on the laser beam (e.g., by transmission, reflection, refraction, diffraction, collimation, adjustment, shaping, focusing, modulation, and / or other means). Examples of optical elements include lenses, prisms, mirrors, diffractive optical elements (DOEs), holographic optical elements (HOEs), and spatial light modulators (SLMs).

[0031] The computer 20 controls the operation of the system 10 to evaluate the measurements from the measuring device 28. In a particular embodiment, the computer 20 generates an eyeball model of the eye 12 according to the measurements from the OCT device 30. The computer 20 identifies the OCT-based wavefront from the eyeball model and the aberration-based wavefront from the aberration-meter 32. The computer 20 compares the OCT-based wavefront and the aberration-based wavefront. If there is a discrepancy, the computer evaluates the measurements according to the discrepancy. In a particular embodiment, the computer 20 may perform additional checks on the model.

[0032] Generation of the eyeball model: An eyeball model. The eyeball model may include parameters that describe the eye 12, each of which is assigned a value. The parameters may describe the characteristics (e.g., location, dimensions, shape, and / or material properties such as refractive index) of the features of the eye 12 (e.g., parts of the lens such as the cornea). The parameters may describe, for example, the following or parts of the eye 12: (1) the wavefront of the eye 12; (2) the shape of the surface of the parts of the eye 12 (e.g., the anterior or posterior surface of the cornea or lens); (3) distances (e.g., physical or optical) passing through the eye 12 or between parts of the eye 12 (e.g., the distance between the posterior cornea and the anterior lens, the distance between the posterior part of the lens and the retina, or the distance passing through the cornea, lens, vitreous humor, or aqueous humor); and the refractive index of the parts of the eye 12. The values ​​assigned to the parameters give the parameters specific values, for example, a specific thickness of the cornea.

[0033] Parameter values ​​are constrained. These constraints can be hard constraints with a high priority to satisfy or soft constraints with a low priority to satisfy. In certain examples, the following parameter values ​​may be certain and may be considered hard constraints: (1) the entire eye: wavefront; (2) cornea: anterior and posterior surface shape, physical and optical distances through the cornea, and refractive index; (3) aqueous humor: physical distances through the aqueous humor and refractive index; (4) lens: anterior surface shape, optical path through the lens, and general refractive index profile (but no specific value); (5) vitreous humor: physical distances through the vitreous humor and refractive index. In certain examples, the following parameter values ​​may be uncertain and may be considered variable or soft constraints: (1) lens: posterior surface shape, physical path through the lens, and specific values ​​of the refractive index profile; (2) vitreous humor: beam direction through the vitreous humor; (3) retina: position, surface shape.

[0034] Generation of eyeball model: Ray tracing. Computer 20 can generate an eyeball model in any suitable manner according to the reflected OCT light. In certain embodiments, computer 20 generates an eyeball model by applying a ray tracing procedure. Ray tracing identifies the path of rays passing through the eye 12, including how the interfaces between parts of the eye 12 refract the rays. At tissue boundaries, refraction is calculated according to Snell's law, which states that the ratio of the sine of the angle of incidence and refraction θ is the reciprocal of the ratio of the refractive indices n: sinθ² / sinθ¹=n¹ / n². Rays passing through parts of the eye 12 with a uniform refractive index propagate in a constant direction, while rays moving through parts with a gradient of refractive indices travel along a curved path. As the rays travel through the eye 12, the process calculates the intersection points of the rays with the surface and the surface normals at those points to identify the new direction of the rays according to Snell's law. Using the points and the surface normals at those points, the shape of the surface can be identified. An example of such a process will be explained with reference to Figures 5A and 5B.

[0035] Figures 5A and 5B show an example of applying a ray tracing procedure to locate the anatomical interface 56 of the eye 12 and generate an eyeball model. Figure 5A shows the anatomical interface 56, which includes interface 56a (anterior corneal surface 58); interface 56b between aqueous humor 42 and lens 46 (anterior surface of the lens); interface 56c between lens 46 and vitreous humor 50 (posterior surface of the lens); and interface 56d (surface of the retina 52). Distance d' represents the physical distance to interface 56.

[0036] Figure 5B shows measurements from the OCT device 30, which records the distance d that the OCT ray travels to a point on the interface 56, "similar to in air". The ray travels through the air to the interface 56a, and therefore the distance d1 = d'1. However, the ray travels through the eye tissue from the interface 56b to 56d, and the distance is d' i <d i It becomes shorter as follows, and i = b, c, and d.

[0037] In one example of operation, the computer 20 defines a ray traveling through the anatomical interface of the eye 12, identifies the location of the anatomical interface from the ray, and generates an eyeball model using the location of the anatomical interface. For each anatomical interface, the computer 20 defines the ray by repeating the following: using the refractive index and angle of incidence of the tissue, it identifies the angle of refraction from the anatomical interface, and from the OCT measurement, it identifies the distance to the next anatomical interface.

[0038] In the example, the OCT device 30 provides an initial "in-air" distance d to a point on the interface 56. In certain embodiments, the topographer 34 may provide additional measurements of the shape of the interface 56a (corneal anterior surface 58). In addition, uncertain parameter values ​​can be assigned to initial values, which can be adjusted in response to additional information. For example, the corneal anterior surface 58 may first be parameterized, for example, with respect to a parameter to which an initial value has been assigned. The initial value may be, for example, the mean value of a population.

[0039] Starting from the interface 56a (anterior corneal surface 58), the OCT device 30 provides a distance d1 = d'1 to the interface 56a. The distance d'2 to a point on the interface 56b (anterior lens surface) can be calculated from the distance d2 to the point and the refractive index of the aqueous humor. The angle of refraction at a point on the interface 56b can be calculated from the shape of the anterior lens surface, the direction of the light rays, the refractive index of the aqueous humor, and the refractive index of the lens at the point. The distances d' to points on the remaining interfaces 56c and 56d can be calculated similarly.

[0040] The computer 20 constructs an eyeball model from the length and position of the light rays. The shape of the interface 56 can be determined using the points where the light rays intersect the interface 56 and the surface normals at those points. In certain embodiments, the computer 20 constructs the eyeball model by modifying an existing model. In other embodiments, the computer 20 constructs the eyeball model from raw data.

[0041] In certain cases, the computer 20 may take into account additional aspects of the eye 12 while generating the eyeball model. These additional aspects may be found, for example, in the medical history of the eye 12. Examples of such considerations include the refractive index of the IOL in patients with pseudophakic cornea, the atypical corneal refractive index of a previously cross-bridged cornea, and the atypical corneal surface of a kerataconic cornea.

[0042] Ocular Model Generation: Model Checking. In certain embodiments, the computer 20 may check the ocular model by comparing one or more parameter values ​​of the ocular model with values ​​of other measurements of the eye 12, e.g., measurements from the system 10 or an external measuring device 28. Significant deviations between values ​​may indicate a problem. Significant deviations may be, for example, deviations outside of one or two standard deviations or deviations greater than a specified percentage, such as 2% or 5%. Examples of problems include problems with measurement conditions (e.g., insufficient sampling, improper patient fixation, and / or lacrimal instability), the measuring device 28 (e.g., device alignment and / or calibration), or the parameters of the model (e.g., corneal parameters). In some cases, the deviations may have certain features that indicate a likely problem.

[0043] The computer 20 may respond to the detection of misalignment in any suitable manner. For example, the computer 20 may send a notification identifying one or more related issues, such as one or more issues that are causing or are likely to cause the misalignment. As another example, the computer 20 may provide a recommendation to repeat the measurement using one or more measuring devices 28 associated with the misalignment, for example, which may be causing the misalignment. As yet another example, the computer 20 may identify the condition of eye 12 that provides the condition of the misalignment (for example, from the medical history of eye 12) and notify the user of the condition.

[0044] Comparison of corneal surface. In certain embodiments, the computer 20 may compare a value describing the corneal surface 58 of an eyeball model with a value from another description of the corneal surface 58, such as toric refractive power measured by a topographer 34 or a measurement of the corneal surface 58. Significant discrepancies may indicate, for example, problems associated with improper sampling of the surface 58 and / or inappropriate device problems (e.g., improper device alignment or calibration). For example, the computer 20 may determine that the measurement of the surface 58 from the OCT device 30 and / or topographer 34 is insufficient or that the measurement from the OCT device 30 and / or topographer is not aligned with other measurements. The computer 20 may send a notification identifying a problem or a likely problem and / or a recommendation to repeat the measurement using one or more measuring devices 28 (e.g., OCT device 30 and / or topographer 34) that may be causing the discrepancy.

[0045] Wavefront Identification. Ocular wavefronts are typically measured on the corneal surface or the entrance pupil surface of the eye. However, wavefronts can be calculated at any suitable location, e.g., the anterior surface of the lens (using aberration meter and / or anatomical OCT data). Computer 20 can identify OCT-based wavefronts in any suitable manner according to the eyeball model. In certain embodiments, computer 20 identifies OCT-based wavefronts by applying a ray tracing procedure to the eyeball model. Rays originating from a spot on the retina propagate through the eye 12, similar to but in the opposite direction to those shown in Figure 5A. Computer 20 obtains the position and inorganic of the ray at a selected location and constructs OCT-based wavefronts from the position and inorganic. Computer 20 identifies aberration-based wavefronts according to the reflected aberration meter light from the aberration meter 32. In certain embodiments, the aberration meter 32 generates a wavefront map, and computer 20 identifies aberration-based wavefronts from the map.

[0046] Wavefront comparison. The computer 20 can compare the OCT-based wavefront and the principal system-based wavefront in any suitable manner. In certain embodiments, the computer compares the wavefronts to determine whether their difference exceeds a predefined tolerance. The predefined tolerance may be defined to fit the known error margin of the measuring device 28. For example, the predefined tolerance may be the maximum of the known error margins.

[0047] Wavefronts can be parameterized using the same parameters, and the computer 20 can compare wavefronts by comparing the values ​​of the parameters. In one example of operation, the computer 20 parameterizes an OCT-based wavefront using parameters, and each parameter is assigned an OCT-based value that describes the OCT-based wavefront. The computer 20 parameterizes an aberration-based wavefront using parameters, and each parameter is assigned an aberration-based value that describes the aberration-based wavefront. The computer 20 then compares the OCT-based values ​​with the aberration-based values.

[0048] Generally, the more parameter values ​​to compare, the longer the time required to perform the comparison may be. Therefore, the number of parameters to compare can be selected in light of the expected efficiency. In certain embodiments, the computer 20 may perform a faster comparison comparing fewer parameter values ​​to identify major defects in the eyeball model, and these major defects can be addressed before performing a more extensive (but slower) comparison comparing more parameter values.

[0049] In one example of rapid comparison, the computer 20 may check the eye model by generating a simulated wavefront with less detail. For example, the computer 20 may identify the toric representation of the interface 56 and then calculate the cylindrical and spherical frequency parameters of the wavefront simulated through the interface 56. The simulated wavefront parameters can be compared to the spherical and cylindrical frequency parameters of the aberration-based wavefront. Significant deviations may indicate problems, for example, inaccurate axial length measurements, improper patient fixation, and / or problems associated with improper device alignment or calibration. The computer 20 may send a notification identifying the problem or a likely problem and / or a recommendation to repeat the measurement using one or more measuring devices 28 (e.g., OCT device 30 and / or aberration-meter 32) that may be causing the deviation.

[0050] In another example of faster comparison, the computer 20 may check whether the simulated wavefront parameters match those measured from, for example, a topographer 34. For example, the computer 20 may compare the corneal anterior surface 58 of an eyeball model with the surface 58 measured by the topographer 34. In the example, the computer 20 identifies the model-based corneal anterior surface from the eyeball model and the topographer-based corneal anterior surface from the topographer 34. The computer 20 checks the eyeball model by comparing the model-based corneal anterior surface with the topographer-based corneal anterior surface. Significant discrepancies may indicate, for example, lacrimal instability and / or problems associated with improper device alignment or calibration. The computer 20 may send a notification identifying the problem or a likely problem and / or a recommendation to repeat the measurement using one or more measuring devices 28 (e.g., OCT device 30 and / or topographer 34) that may be causing the discrepancy.

[0051] In one example of a broader comparison, computer 20 utilizes a wavefront map (e.g., a Zernike coefficient map) containing wavefront parameters. In the example, computer 20 checks the OCT-based value of an OCT-based wavefront using the aberration-based value of an aberration-based wavefront. For example, the slope of an aberration-based wavefront can be compared to the slope of a ray emitted from the eye according to an OCT-based model. Any suitable number of matching values ​​for the OCT-based value and the aberration-based value (e.g., slope), e.g., values ​​between 20 and 50, 50 and 100, or greater than 100, can be checked. The number of values ​​can be adjusted according to the desired completeness and / or efficiency. Significant deviations in higher-order Zernike parameterization may indicate problems associated with, for example, lacrimal instability, inaccurate lens topography parameters, improper patient fixation, and / or improper device alignment or calibration. The computer 20 may send a notification identifying a problem or a likely problem and / or a recommendation to repeat the measurement using one or more measuring devices 28 (e.g., an OCT device 30 and / or an aberration meter 32) that may be the cause of the deviation.

[0052] Parameter value adjustment. If the OCT-based wavefront and the aberration meter-based wavefront differ by more than a predetermined tolerance, the computer 20 adjusts one or more parameter values ​​(such as lens parameter values) of the OCT-based wavefront until the comparison of the wavefronts satisfies the predetermined tolerance. The computer 20 adjusts the values ​​by repeating the following: adjusting the values ​​to generate a tuned eye model; identifying the OCT-based wavefront tuned according to the tuned eye model; and comparing the tuned OCT-based wavefront with the aberration meter-based wavefront to determine whether they satisfy the predetermined tolerance.

[0053] The computer 20 can adjust the parameter values ​​in any suitable manner. In certain embodiments, lower-accuracy values ​​are adjusted before higher-accuracy values. Lower-accuracy values ​​may include values ​​not directly measured (e.g., lens refractive index or cataract grade), values ​​from unreliable measuring devices 28, or values ​​given by softer constraints. Higher-accuracy values ​​may include values ​​supported by multiple measurements, values ​​generally known in the art, or values ​​given by harder constraints.

[0054] Performing another check. In certain embodiments, the system 10 performs another check of the eyeball model. In embodiments, the measuring device 28 measures the eye 12 from an angle different from the angle previously used to measure the eye 12, and the measurements are compared. For example, the measuring device 28 may first measure the eye "on axis," i.e., the optical axis of the measuring device 28 is aligned with the axis of the eye 12 (e.g., the visual axis or optical axis). To check the eyeball model, the measuring device 28 may measure the eye "off axis," i.e., the axis of the measuring device 28 is tilted relative to the axis of the eye. The angle may be, for example, 0 to 10 degrees and / or 10 to 20 degrees, and may be approximately 3 degrees. The computer 20 uses the measurements at different angles to generate a new wavefront to compare in order to check the eyeball model.

[0055] For example, the OCT device 30 directs OCT light towards the eye at different angles and detects the OCT light reflected from the eye. The aberration meter 32 directs aberration meter light towards the eye at different angles, detects the aberration meter light reflected from the eye, and generates an aberration meter-based wavefront. The computer 20 generates another eyeball model of the eye according to the reflected OCT light and identifies the OCT-based wavefront from that eyeball model. The computer 20 then compares the wavefronts to check the eyeball model.

[0056] The computer 20 stores the generated eyeball model in memory 24 and can output the model via interface 26. In certain embodiments, the computer 20 uses the generated eyeball model to plan ophthalmic surgery, such as cataract surgery or refractive surgery. For example, the model can be used to determine the size of an accommodative intraocular lens (IOL) or to predict the postoperative position of the IOL.

[0057] Figure 6 shows an example of a method for evaluating eye measurements that may be performed by the system 10 of Figure 1, according to a particular embodiment. In a particular embodiment, a computer 20 may perform the steps of the method by sending instructions to the components of the system 10.

[0058] The procedure begins in step 110, when the OCT device 30 directs OCT light towards the eye, and the eye reflects the light. In step 112, the OCT device 30 detects the reflected OCT light to measure the eye. In step 116, the aberration meter 32 directs aberration meter light towards the eye, and in step 118, the aberration meter light reflected from the eye is detected to measure the eye. In step 120, the topographer 34 directs topographer light towards the eye, and in step 122, the topographer light reflected from the eye is detected to measure the eye.

[0059] In step 126, the computer 20 constructs an eyeball model of the eye according to the reflected OCT light. In certain embodiments, the computer 20 generates the eyeball model by applying a ray tracing procedure. Certain embodiments may include variations in the generation of the eyeball model. For example, the computer 20 may construct the corneal anterior surface of the eyeball model according to measurements from the OCT device 30 and the topographer 34. The computer 20 may check the eyeball model by identifying the OCT-based corneal anterior surface from the eyeball model, identifying the topograph-based corneal anterior surface from the reflected topographer light, and comparing the OCT-based corneal anterior surface with the topograph-based corneal anterior surface. Misalignments between surfaces may indicate problems, such as insufficient sampling, tear film instability, improper device alignment, and / or improper device calibration. If there are misalignments in this step, the computer 20 may report the misalignments in step 138, etc.

[0060] In step 128, the computer 20 identifies the OCT-based wavefront according to the eyeball model. The computer 20 may apply a ray tracing process to calculate the OCT-based wavefront. In step 130, the computer 20 identifies the aberration-based wavefront according to the reflected aberration-meter light. In certain embodiments, the aberration-meter 32 generates a wavefront map and provides the map to the computer 20.

[0061] In step 132, the computer 20 compares the OCT-based wavefront and the aberration-based wavefront to determine the misalignment. The computer 20 may compare the wavefronts by parameterizing them using parameter values ​​and comparing the wavefront values. In step 136, the computer 20 evaluates one or more measurements from one or more measuring devices according to the misalignment. The computer 20 may evaluate the measurements by identifying one or more problems associated with the misalignment. The associated problems may be related to the measurement conditions or the measuring device. Examples of associated problems related to the measurement conditions include tear film instability and / or improper patient fixation. Examples of associated problems related to the measuring device include inaccurate lens topography parameters, improper device alignment, and / or improper device calibration. The computer 20 may identify one or more measuring devices that are potentially causing the misalignment.

[0062] In certain embodiments, the comparison in step 132 may notify the computer 20 of any issues related to misalignment. For example, the computer 20 may compare wavefronts by checking the eye model by identifying the OCT-based corneal anterior surface from the eyeball model, identifying the topograph-based corneal anterior surface from the reflected topograph light, and comparing the OCT-based corneal anterior surface with the topograph-based corneal anterior surface. Surface misalignment may indicate problems such as insufficient sampling, tear film instability, improper device alignment, and / or improper device calibration.

[0063] As another example, the computer 20 can compare wavefronts by calculating OCT-based spherical and cylindrical frequency parameters of wavefronts simulated through an eyeball model; calculating aberration-based spherical and cylindrical frequency parameters of aberration-based wavefronts; and comparing the OCT-based spherical and cylindrical frequency parameters with the aberration-based spherical and cylindrical frequency parameters. Parameter deviations may indicate problems such as inaccurate axial length measurements, improper patient fixation, improper device alignment, and / or improper device calibration.

[0064] As another example, the computer 20 may compare wavefronts by identifying one or more aberration-based values ​​for an aberration-based wavefront; identifying one or more OCT-based values ​​for an eyeball model; and comparing the aberration-based values ​​with the OCT-based values. In some cases, the aberration-based value is the aberration-based slope of the wavefront of the aberration-based wavefront, and the OCT-based value is the OCT-based slope of the rays emanating from the eyeball model. Discrepancies in values ​​may indicate problems such as lacrimal instability, inaccurate lens topography parameters, improper patient fixation, improper device alignment, and / or improper device calibration.

[0065] In step 138, the computer 20 provides the results. The computer 20 may display and / or use the results in any suitable format. For example, the results may be used to plan an ophthalmic surgery (e.g., cataract or refractive surgery). The method then terminates.

[0066] In certain embodiments, the computer 20 may check the eyeball model to improve its accuracy, thereby improving detection and evaluating the eye measurements. For example, the computer 20 may adjust one or more values ​​assigned to the parameters of the eyeball model by repeating the following until the adjusted OCT-based wavefront and the aberration meter-based wavefront meet predefined tolerances: adjust the values ​​to generate an adjusted eyeball model; identify the OCT-based wavefront adjusted according to the adjusted eyeball model; and compare the adjusted OCT-based wavefront and the aberration meter-based wavefront to determine whether they meet predefined tolerances.

[0067] As another example, system 10 may measure the eye at different angles, and computer 20 may use the measurements to adjust the eyeball model. In the example, the OCT device directs the next OCT light at the eye at a different angle than the angle of the previous OCT light and detects the next OCT light reflected from the eye. The aberration meter directs the next aberration meter light at the eye at a different angle than the angle of the aberration meter light and detects the next aberration meter light reflected from the eye. The computer generates the next eyeball model of the eye according to the reflected next OCT light; generates the next aberration meter-based wavefront according to the reflected next aberration meter light; identifies the next OCT-based wavefront according to the next eyeball model; and checks the eyeball model by comparing the next OCT-based wavefront with the next aberration meter-based wavefront.

[0068] The components of the systems and apparatus disclosed herein (such as control computers) may include interfaces, logic, and / or memory, any of which may include computer hardware and / or software. Interfaces can receive inputs to and / or transmit outputs from components and are typically used to exchange information between, for example, software, hardware, peripherals, users, and combinations thereof. User interfaces (e.g., graphical user interfaces (GUIs)) are a type of interface that a user can use to interact with a computer. Examples of user interfaces include displays, touchscreens, keyboards, mice, gesture sensors, microphones, and speakers.

[0069] Logic can perform the actions of components. Logic may include one or more electronic devices that process data, for example, by executing instructions to produce an output from an input. Examples of such electronic devices include computers, processors, microprocessors (e.g., central processing units (CPUs)), and computer chips. Logic may also include computer software that encodes instructions that can be executed by the electronic devices to perform actions. Examples of computer software include computer programs, applications, and operating systems.

[0070] Memory may include tangible, computer-readable and / or computer-executable storage media capable of storing information. Examples of memory include computer memory (e.g., random-access memory (RAM) or read-only memory (ROM)), mass storage media (e.g., hard disks), removable storage media (e.g., compact discs (CDs) or digital video or multi-purpose discs (DVDs)), databases, network storage (e.g., servers), and / or other computer-readable media. Certain embodiments may involve memory encoded using computer software.

[0071] While this disclosure has described specific embodiments, modifications to the embodiments (e.g., altered, replaced, added, omitted, and / or other modifications) will be apparent to those skilled in the art. Thus, modifications to the embodiments can be made without departing from the scope of the invention. For example, modifications can be made to the systems and apparatus disclosed herein. As will be apparent to those skilled in the art, the components of the systems and apparatus can be integrated or separated, or the operation of the systems and apparatus can be performed by more, fewer, or other components. As another example, modifications can be made to the methods disclosed herein. As will be apparent to those skilled in the art, the methods may include more, fewer, or other steps, and the steps may be performed in any suitable order.

[0072] To assist the Patent Office and readers in interpreting the claims, the applicant notes that, unless the words “means for” or “step for” are expressly used in any particular claim, neither the claim nor any claim element is intended to evoke Section 112(f) of the U.S. Patent Act. Any other term used in the claims (e.g., “mechanism,” “module,” “device,” “unit,” “component,” “element,” “member,” “apparatus,” “machine,” “system,” “processor,” or “controller”) is understood by the applicant to refer to a structure known to those skilled in the art in the relevant field and is not intended to be subject to Section 112(f) of the U.S. Patent Act.

Claims

1. An ophthalmic system for measuring the eye, Multiple measuring devices The plurality of measuring devices include, Optical coherence tomography (OCT) device, Direct the OCT light towards the eye, The OCT light reflected from the eye is detected, and the eye is measured. An OCT device configured as follows, It is an aberration meter, Direct the aberration meter light towards the eye, The aberration meter light reflected from the eye is detected, and the eye is measured. an aberration meter configured as follows, Equipped with, The aforementioned ophthalmic system is equipped with a computer, The aforementioned computer, The process involves generating an eyeball model of the eye according to the reflected OCT light, wherein the eyeball model includes a plurality of parameters of the eye, each parameter to which a value is assigned. Identifying the OCT-based wavefront according to the aforementioned eyeball model, Identifying the wavefront of the aberration meter base according to the reflected aberration meter light, To determine the difference between the wavefront of the OCT base and the wavefront of the aberration meter base, Evaluating one or more measurements from one or more of the multiple measuring devices according to the aforementioned deviation, An ophthalmic system configured to perform the following actions.

2. The aforementioned computer, Identifying one or more issues related to the aforementioned misalignment. The ophthalmic system according to claim 1, configured to evaluate one or more measurements.

3. The ophthalmic system according to claim 2, wherein the one or more of the aforementioned related problems are associated with measurement conditions or a measurement device.

4. The ophthalmic system according to claim 2, wherein the one or more related problems include problems selected from the group consisting of lacrimal film instability, inaccurate lens topography parameters, improper patient fixation, improper device alignment, and improper device calibration.

5. The aforementioned computer, Identifying one or more measuring devices associated with the aforementioned misalignment. The ophthalmic system according to claim 1, configured to evaluate one or more measurements.

6. The topographer further comprises, Directing the topograph light towards the eye, It is configured to detect the topograph light reflected from the eye, The aforementioned computer, From the aforementioned eyeball model, the anterior surface of the cornea based on OCT was identified, The corneal surface of the topograph base is identified from the reflected topograph light, The eyeball model is checked by comparing the anterior corneal surface based on the OCT with the anterior corneal surface based on the topograph. The ophthalmic system according to claim 1, configured to generate the eyeball model of the eye by means of the eye.

7. The aforementioned computer, Identifying one or more related problems, including a problem selected from the group consisting of insufficient sampling, tear film instability, improper device alignment, and improper device calibration. The ophthalmic system according to claim 6, configured to evaluate one or more measurements.

8. The aforementioned computer, The OCT-based spherical frequency parameters and cylindrical frequency parameters of the wavefront simulated through the aforementioned eyeball model are calculated. The calculation of the spherical frequency parameter and cylindrical frequency parameter of the aberration meter base wavefront, To compare the OCT base and cylindrical frequency parameters with the aberration meter base's spherical frequency parameters and cylindrical frequency parameters. This is configured to determine the discrepancy between the wavefront of the OCT base and the wavefront of the aberration meter base. The ophthalmic system according to claim 1.

9. The aforementioned computer, Identifying one or more related problems, including problems selected from the group consisting of inaccurate axial length measurement, improper patient fixation, improper device alignment, and improper device calibration. The ophthalmic system according to claim 8, configured to evaluate one or more measurements.

10. The aforementioned computer, Identifying one or more aberration meter base values ​​of the wavefront of the aberration meter base, Identifying one or more OCT base values ​​of the aforementioned eyeball model, Comparing the one or more aberration meter base values ​​with the OCT base values. The ophthalmic system according to claim 1, configured to determine the discrepancy between the wavefront of the OCT base and the wavefront of the aberration meter base.

11. The one or more aberration meter base values ​​include the slope of one or more aberration meter bases of the wavefront of the aberration meter base, The ophthalmic system according to claim 10, wherein the one or more OCT base values ​​include the inclination of one or more OCT bases of one or more rays emanating from the eyeball model.

12. The computer continues until the adjusted OCT-based wavefront and the aberration meter-based wavefront satisfy a predetermined tolerance. The process involves adjusting one or more of the aforementioned values ​​to generate an adjusted eyeball model, Identifying the adjusted OCT-based wavefront according to the adjusted eyeball model, The adjusted OCT-based wavefront and the aberration meter-based wavefront are compared to check whether they satisfy the predefined tolerance. The ophthalmic system according to claim 1, further configured to adjust one or more values ​​assigned to one or more of the parameters by repeating the process.

13. The OCT device is Directing the next OCT light towards the eye at an angle different from the angle of the previous OCT light, To detect the next OCT light reflected from the eye. The eyeball model is further configured to check the eyeball model, The aberration meter is, Directing the next aberration meter beam towards the eye at an angle different from the angle of the aforementioned aberration meter beam, To detect the aberration meter light reflected from the eye. The eyeball model is further configured to check the eyeball model, The aforementioned computer, To generate the next eyeball model of the eye according to the reflected next OCT light, To generate the next aberration-based wavefront according to the reflected next aberration-meter light, Identifying the following OCT-based wavefront according to the following eyeball model, To compare the wavefront of the OCT-based wavefront with the wavefront of the aberration meter-based wavefront. The ophthalmic system according to claim 1, further configured to check the eyeball model.

14. An ophthalmic system for measuring the eye, Multiple measuring devices The plurality of measuring devices include, Optical coherence tomography (OCT) device, Direct the OCT light towards the eye, The OCT light reflected from the eye is detected. An OCT device configured as follows, Topographer, Directing the topograph light towards the eye, The topograph light reflected from the eye is detected. A topograph configured in such a way, Includes, The aforementioned ophthalmic system is a computer, Identifying the corneal surface of the OCT base from the reflected OCT light, Identifying the corneal surface of the topograph base from the reflected topograph light, To determine the displacement between the corneal surface of the OCT base and the corneal surface of the topograph base, Evaluate the anterior surface of the cornea based on the OCT and the anterior surface of the cornea based on the aforementioned misalignment. A computer configured to perform the following actions: An ophthalmic system including

15. The aforementioned computer, Identifying one or more issues related to the aforementioned misalignment. The ophthalmic system according to claim 14, configured to evaluate the OCT-based corneal surface and the topograph-based corneal surface.

16. The ophthalmic system according to claim 15, wherein the one or more of the aforementioned related problems are associated with measurement conditions or a measurement device.

17. The ophthalmic system according to claim 15, wherein the one or more related problems include problems selected from the group consisting of insufficient sampling, improper device alignment, and improper device calibration.

18. The aforementioned computer, Identifying one or more measuring devices associated with the aforementioned misalignment. The ophthalmic system according to claim 14, configured to evaluate the OCT-based corneal surface and the topograph-based corneal surface.

19. The plurality of measuring devices further include aberration meters, and the aberration meters are Direct the aberration meter light towards the eye, The aberration meter light reflected from the eye is detected. It is configured in such a way, The aforementioned computer, The process involves generating an eyeball model of the eye according to the reflected OCT light, wherein the eyeball model includes a plurality of parameters of the eye, each parameter to which a value is assigned. Identifying the OCT-based wavefront according to the aforementioned eyeball model, Identifying the wavefront of the aberration meter base according to the reflected aberration meter light, Comparing the wavefront of the OCT base with the wavefront of the aberration meter base, Evaluating one or more measurement values ​​from one or more of the multiple measuring devices in accordance with the above comparison, The ophthalmic system according to claim 14, further configured to perform the following:

20. An ophthalmic system for measuring the eye, Multiple measuring devices, wherein the multiple measuring devices are Optical coherence tomography (OCT) device, Direct the OCT light towards the eye, The OCT light reflected from the eye is detected, and the eye is measured. An OCT device configured as follows, It is an aberration meter, Direct the aberration meter light towards the eye, The aberration meter light reflected from the eye is detected, and the eye is measured. an aberration meter configured as follows, Topographer, Directing the topograph light towards the eye, The topograph light reflected from the eye is detected. A topographer configured in such a way Multiple measuring devices, including, It is a computer, The process involves generating an eyeball model of the eye according to the reflected OCT light, wherein the eyeball model includes a plurality of parameters of the eye, each parameter being assigned a value, and the eyeball model is generated by identifying the OCT-based corneal anterior surface from the eyeball model, identifying the topography-based corneal anterior surface from the reflected topography light, and checking the eyeball model by comparing the OCT-based corneal anterior surface with the topography-based corneal anterior surface. Identifying the OCT-based wavefront according to the aforementioned eyeball model, Identifying the wavefront of the aberration meter base according to the reflected aberration meter light, The purpose is to determine the difference between the wavefront of the OCT base and the wavefront of the aberration meter base, and the difference between the wavefront of the OCT base and the wavefront of the aberration meter base is The OCT-based spherical frequency parameters and cylindrical frequency parameters of the wavefront simulated through the eyeball model are calculated, the aberration-based spherical frequency parameters and cylindrical frequency parameters of the wavefront based on the aberration meter are calculated, and the OCT-based spherical frequency parameters and cylindrical frequency parameters are compared with the aberration-based spherical frequency parameters and cylindrical frequency parameters. Identify one or more aberration meter base values ​​of the wavefront of the aberration meter base, identify one or more OCT base values ​​of the eyeball model, and compare the one or more aberration meter base values ​​with the OCT base values. This is determined by determining that the one or more aberration meter base values ​​include the tilt of one or more aberration meter bases of the wavefront of the aberration meter base, and the one or more OCT base values ​​include the tilt of one or more OCT bases of one or more rays emanating from the eyeball model, Evaluating one or more measurements from one or more of the plurality of measuring devices according to the aforementioned deviation, Identifying one or more problems related to the aforementioned misalignment and related to the measurement conditions or measurement device, wherein the one or more related problems include, among others, problems selected from the group consisting of inaccurate axial length measurement, insufficient sampling, tear film instability, inaccurate lens topography parameters, improper patient fixation, improper device alignment, and improper device calibration, and Identifying one or more measuring devices associated with the aforementioned misalignment. To evaluate, to evaluate, The adjustment involves adjusting one or more values ​​assigned to one or more of the parameters, which are adjusted to generate an adjusted eyeball model by adjusting the one or more values ​​until the adjusted OCT-based wavefront and the aberration meter-based wavefront satisfy a predetermined tolerance, identifying the adjusted OCT-based wavefront according to the adjusted eyeball model, and comparing the adjusted OCT-based wavefront and the aberration meter-based wavefront to check whether they satisfy the predetermined tolerance. A computer configured to perform the following actions: Includes, The OCT device is further configured to check the eyeball model by directing the next OCT light at an angle different from the angle of the previous OCT light towards the eye and detecting the next OCT light reflected from the eye. The aberration meter is further configured to check the eyeball model by directing the aberration meter light towards the eye at an angle different from the angle of the aberration meter light, and detecting the next aberration meter light reflected from the eye. An ophthalmic system further configured such that the computer generates a next eyeball model of the eye according to the reflected next OCT light, generates a next aberration-based wavefront according to the reflected next aberration-meter light, identifies a next OCT-based wavefront according to the next eyeball model, and checks the eyeball model by comparing the next OCT-based wavefront with the next aberration-meter-based wavefront.

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