Patent Description:
The present invention is directed to lens design and, more particularly, to a system and method for predictive modeling to design, evaluate and optimize ophthalmic lenses.

Visual acuity is the clarity of vision, and more specifically is the spatial resolving power of a visual system. Visual acuity is thus the spatial level of detail that can be resolved by the visual system, and may be limited by physiological factors of the patient, such as optical factors within the eye and/or neural factors. Typically, visual acuity is heuristically obtained in an ophthalmic medical practice by presentation of a letter chart to the patient. Visual acuity may be calculated in accordance with the spatial frequency at which the eye's modulation transfer function (MTF) intersects with its neural threshold function (NTF).

The optical transfer function (OTF) describes the spatial variation in a optical system as a function of spatial frequency. The OTF may account for aberration in the optical system, and has a magnitude of the MTF and a phase defined by the phase transfer function (PTF).

An ophthalmic lens may be used to correct aberrations of the eye, as defined using the OTF, for example. An ophthalmic lens may be, for example, an intraocular lens (IOL) that may be surgically implanted, such as a spheric, aspheric, diffractive, refractive, accommodating or injectable IOL, an optical inlay or overlay, or contact lenses or glasses, for example. An IOL is typically implanted to correct medical conditions, such as cataracts and/or presbyopia, for example.

On an individual basis, the modeling of the visual acuity (VA) of ophthalmic lenses using the intersection of the MTF and the NTF has not proven highly accurate when compared with clinical data. Alternative methods of preclinically testing ophthalmic lenses, such as wavefront aberration techniques, have similarly not comported well with clinical data. Further, MTF, wavefront aberration, and other modeling tests have been generally applied to only specific vision conditions, and hence offer only limited predictability of VA and other vision factors, such as contrast sensitivity.

Forty-six (<NUM>) physiological eye models for a population of eyes of particular conditions and having particular characteristics have recently been produced by Piers, et al. (See <NPL>. The Piers models provide clinically-based models of the eye, and encompass a representative model of the clinical population. The representative models include the aberrations that may be presented in the eye, which may additionally indicate the characteristics of the eye, such as the optical length of the eye, the corneal curvature, the pupil size, and variations thereof, for example. More specifically, the Piers eye models demonstrate wavefront aberrations that are characteristic for a cataract population, and which have been verified against clinical data for contrast vision. <CIT> relates to an ophthalmic lens synthesized from its specification. A prescription lens, mainly suited for ophthalmic applications, is described. When designing the lens, microscopic surfaces of the lens are defined and it is assumed that the location of an object, the lens and the required image are known. The design can be optimized by ray-tracing that will take into account height changes. <CIT>, "<NPL>), and "<NPL>) relate to the optimization of a lens design without specific improvement of an eye model based on a clinical outcome.

Although modeling techniques are available, as discussed above, and although the Piers models provide simulated eyes to which modeling techniques may be applied, modeling techniques have not been applied to model eyes in a manner that allows for the evaluation and optimization of clinical implementations of lenses designed using the modeling. More particularly, the available art fails to provide feedback from clinical implementations to evaluate and, optimize lens design, and to thereby improve the obtained characteristics of subsequent clinical implementations.

Thus, the need exists for a system and method for predictive modeling to design, evaluate and optimize ophthalmic lenses.

The present invention is and includes a system and method for predictive modeling to design, evaluate and optimize ophthalmic lenses. Ophthalmic lenses may include, for example, contacts, glasses or intraocular lenses {IOLs). In particular, the invention is defined by the independent claims. Dependent claims define embodiments of the invention.

Understanding of the disclosure will be facilitated by consideration of the following detailed description of the embodiments, taken in conjunction with the accompanying drawings, in which like numerals refer to like parts and in which:.

It is to be understood that the figures and descriptions of the present invention have been simplified to illustrate elements that are relevant for a clear understanding of the present invention, while eliminating, for the purposes of clarity, many other elements found in typical optical and optical simulation apparatuses, systems and methods. Those of ordinary skill in the art will recognize that other elements are desirable and/or required in order to implement the present invention. However, because such elements are well known in the art, and because they do not facilitate a better understanding of the present invention, a discussion of such elements is not provided herein.

The system and method of the present invention may be predictive as to the performance of ophthalmic lenses, such as IOLs, in the eye under any of a variety of circumstances, and with respect to any of a variety of ocular conditions and eye types, and may provide for improved performance of ophthalmic lenses optimized using the modified models indicated by the correspondent clinical results. For example, the present invention may include application of mathematical modeling of certain characterizations of the eye, such as visual acuity (VA) and/or contrast sensitivity, to a series of physiological eye models, such as the <NUM> physiological eye models provided by Piers, et al. , and comparison of model output to actual clinical data, wherein feedback from the actual clinical data may be employed to evaluate and/or modify one or both of the applied mathematical model and the physiological eye model to better approximate one or more indications of the clinical results.

For example, clinical results may be employed in the present invention to determine ones or groups of the <NUM> model eyes of Piers, such as <NUM>, <NUM>, or all eye models, that optimally model an eye having particular characteristics. Thus, the present invention may provide more accurate model eyes correspondent to clinical eyes having particular characteristics.

It will be appreciated by those of ordinary skill in the pertinent arts that the system and method of the present invention may be embodied in one or more computing processors, associated with one or more computing memories, within which is resident computing code to execute the mathematical models discussed herein, to provide the physiological models discussed herein, to track, such as in a relational database, the unique clinical characteristics of the clinical eyes discussed herein, preferably in conjunction with the applied physiological model, and to accumulate feedback regarding the clinical outcome of ophthalmic lenses designed using the system and method of the present invention.

Further, those skilled in the art will appreciate, in light of the disclosure herein, that the aspects of the present invention, and most particularly the feedback of the present invention, may be provided to the one or more computing processors for processing via one or more computing networks, including via one or more nodes of a computing network. Computing networks for use in the present invention may include the Internet, an intranet, an extranet, a cellular network, a satellite network, a fiber optic network, or the like. More particularly, the networking aspects of the present invention may allow for provision of the modeling techniques discussed herein to the offices of a myriad of ophthalmic practitioners of one or more selected types, throughout a selected region, throughout a country, or throughout the world, and additionally may allow for the monitoring of clinical test results and the feeding back of those test results from the offices of those practitioners to the system and method of the present invention.

<FIG> is an illustration of an eye in the natural state. Eye <NUM> includes retina <NUM> for receiving an image, produced by cornea <NUM> and natural lens <NUM>, from light incident upon eye <NUM>. Natural lens <NUM> is disposed within capsular bag <NUM>, which separates anterior and posterior chambers of eye <NUM>. Iris <NUM> may operate to change the aperture, i.e. pupil, size of eye <NUM>. More specifically, the diameter of the incoming light beam is controlled by iris <NUM>, which forms the aperture stop of eye <NUM>.

Capsular bag <NUM> is a resilient material that changes the shape and/or location of natural lens <NUM> in response to ocular forces produced when ciliary muscles <NUM> contract and stretch natural lens <NUM> via zonules <NUM> disposed about an equatorial region of capsular bag <NUM>. This shape change may flatten natural lens <NUM>, thereby producing a relatively low optical power for providing distant vision in an emmetropic eye. To produce intermediate and/or near vision, ciliary muscles <NUM> contract, thereby relieving tension on zonules <NUM>. The resiliency of capsular bag <NUM> thus provides an ocular force to reshape natural lens <NUM> to modify curvature to provide an optical power suitable for required vision. This change, or "accommodation," is achieved by changing the shape of the crystalline lens. Accommodation, as used herein, includes the making of a change in the focus of the eye for different distances.

<FIG>, there is shown an eye having natural lens <NUM> replaced with an IOL <NUM>. Natural lens <NUM> may require removal due to a refractive lens exchange, or due to a disease such as cataracts, for example. Once removed, natural lens <NUM> may be replaced by IOL <NUM> to provide improved vision in eye <NUM>. Eye <NUM> may include IOL <NUM> with optic <NUM>, cornea <NUM>, retina <NUM>, and haptics or support structure <NUM> for centering optic <NUM>. The haptics <NUM> may center optic <NUM>, and may transfer ocular forces from ciliary muscle <NUM>, zonules <NUM>, and/or capsular bag <NUM> to optic <NUM> to change the shape, power, and/or axial location of optic <NUM> relative to retina <NUM>.

<FIG> is a flow diagram illustrating a method <NUM> of optimizing an ophthalmic lens <NUM>, such as, for example, the IOL illustrated in <FIG>, in accordance with the present invention. In the illustrated method <NUM>, an ophthalmic lens may be designed and/or provided at step <NUM> for modeling and for clinical application. Such a lens may, for example, have associated therewith a particular design parameter or parameters. The design parameter or parameters may comprise an optical shape determined by inputting a set of patient parameters into an optimizer. The design parameter or parameters may be derived by the optimizer by determining at least one coefficient of a set of Zernike polynomials. For example, calculating the design parameter or parameters often includes determining a plurality of selected Zernike coefficients, such as for power, astigmatism, or chromatic or spherical aberration, for example, at various orders. The outcome of the eye at a first viewing condition may be measured while viewing at a first viewing distance, and the outcome of the eye at a second viewing condition may be measured while viewing at a second viewing distance which is less than the first distance.

At step <NUM>, the aforementioned eye models, such as a subset of the aforementioned eye models having topologies and/or characteristics of interest, may be subjected to simulated visual acuity (sVA) modeling at step <NUM> to predict, for example, VA and/or other factors, such as contrast sensitivity. In the aforementioned example, model eyes similar in characteristics to the eye for which the design parameter or parameters are to be obtained may be subjected to step <NUM>. Characteristics of interest may include any one or more of a plurality of patient parameter inputs, such as pupil sizes, off-axis vision, and object distance vision, corneal optical power, or residual accommodation by gender, age or race, for example. Similarly, characteristics may include particular aberrations, and/or aberrations of particular severity, such as astigmatism, presbyopia, and chromatic and spherical aberration, for example.

At step <NUM>, weighted factors to optimize vision and/or performance of lens <NUM> may be applied, wherein the factors may include, for example, clinical performance of the lens <NUM> as designed at step <NUM>. Weight factors may be assigned, for example, to each of the characteristics and/or topologies discussed above. For example, the parameters of an ophthalmic lens may be determined, at least in part, by iteratively optimizing a threshold tolerance, such as by optimizing a patient's VA obtained with the corrective parameters, wherein the patients have a clinical eye characterized similarly to the characteristic eye model or models selected.

The lens <NUM> may be evaluated, adjusted and/or optimized at step <NUM>, such as a clinical adjustment to the designed lens for actual implantation, or such as a modification to the model of the designed lens for feedback to step <NUM>. For example, the parameters may be optimized for a characteristic eye by scaling a refractive shape, and/or by analytically or numerically deriving an optical shape providing the desired optical powers at an associated plurality of viewing conditions. The modification to the lens design for modeling may be made pursuant to failure of the lens design to meet a predetermined threshold tolerance in clinical implementation, and may include verification of the current lens design or recommendation of an alternative lens altogether.

<FIG> is a more detailed illustration of the method <NUM> of <FIG>. As illustrated in <FIG>, an IOL design may be provided, based on, for example, a design estimation or a design software simulation for particular input conditions, at step <NUM>. At step <NUM>, ones of a plurality of available eye models, preferably in accordance with the particular input conditions used in step <NUM>, are selected. A simulation may be provided, into which are incorporated the lens design from step <NUM> and the eye models from step <NUM>, at step 308a, which may generate a simulation outcome at step 308b. A patient group for obtaining clinical outcomes may be obtained at step <NUM>, into which are incorporated the lens design from step <NUM>, and to which patient group clinical testing may be applied at step <NUM>. The clinical testing provides clinical outcomes at step <NUM>. Optimization of or the simulation at step <NUM> may be provided at the optimization step <NUM>, which step <NUM> may be performed in accordance with a weighting of input conditions and/or simulation outcomes at step <NUM> (shown in <FIG>). For example, at step <NUM> pupil size may be weighted <NUM> to <NUM> over spherical aberration, or VA may be weighted <NUM> to <NUM> over contrast sensitivity, in obtaining a desired optimization at step <NUM>.

Further, and as illustrated by way of example with respect to <FIG>, the method <NUM> of <FIG> and <FIG> may be iteratively provided in order to arrive at an improved lens design at step <NUM>. More specifically, a lens may be provided at step <NUM>, and an optimization may be iteratively provided at step <NUM>, with or without the clinical outcome input at step <NUM>, to generate an improved lens design at step <NUM>. Of course, the iteration of step <NUM> may be performed without clinical outcome input in the event of pre-clinical design, but may preferably include clinical outcome input in order to optimize the simulation for improved clinical lens design output at step <NUM>. Further, the iteration of step <NUM> may lead to a new or alternative lens design, a modification to an original lens design, or a modification to simulation at step <NUM>, for example.

The threshold tolerance of the present invention is predetermined, and may be predetermined based on literature in the art, based on experience of a patient or group of patients, or from a back-calculation from obtained clinical data, for example. For example, the threshold function may reflect optical quality throughout a particular range, and/or may represent patient tolerable parameters. The threshold function may comprise a ratio of an optical parameter of the eye with a diffraction theory parameter. Thus, exemplary tolerance thresholds may include a threshold of at least one parameter selected from the Strehl Ratio (SR), the MTF, the VA, the point spread function (PSF), the encircled energy (EE), the MTF volume or volume under MTF surface (MTFV), the compound modulation transfer function (CMTF), the contrast sensitivity (CS), and/or dysphotopsia, at any or all predefined viewing conditions. Similarly, the threshold tolerance may also be based on geometrical optics and/or ray tracing. Preferably, minimization or maximization of the threshold tolerance should yield a predictable optimized optical quality of the eye. For example, the threshold tolerance may be a function with a certain number of free parameters to be optimized, via minimization or maximization, through the optimization feedback discussed herein.

More specifically, the threshold tolerance for optimization may be a function of the MTF. As referenced above, MTF may be used to predict visual performance, in part because the MTF at one spatial frequency corresponds to one angular extent of targets. The modulation transfer function (MTF) may be calculated using the formula:<MAT>.

where u and v represent spatial frequencies, Re represents the real part of a complex number, FT represents a Fourier Transform, GPF represents a generalized pupil function, and x and y represent position or field of view.

For example, in a particular exemplary embodiment, the visual acuity in the presence of defocus of a population of cataract patients implanted with diffractive multifocal intraocular lenses may be optimized using method <NUM>. At step <NUM>, method <NUM> may use the aforementioned set of cataract patient physiological eye models, and/or may use a subset of the physiological eye models having particular eye characteristics and/or topologies, such as a subset of eye models or single eye models that include particular chromatic and higher order aberrations, for example.

The set or subset of the eye models may then be subjected to a simulation, such as a simulated VA modeling, at step <NUM>, and the results compared with clinical outcomes at step <NUM>. Optimization based on the clinical outcome comparisons may be obtained using standard optimization routines, such as the downhill simplex method or the direction set method. The downhill simplex method, for example, starts with an initialization of N+<NUM> points or vertices to construct a simplex for an N-dimensional search, and iteratively endeavors to reflect, stretch, or shrink the simplex by geometrical transformation so that a close-to-global minimum or pre-defined accuracy is found. A more detailed discussion of optimization in an optical system using the downhill simplex and direction set method may be found in <CIT> and having inventors Dai, et.

Simulated VA (sVA) may be determined by first calculating the MTF for each eye model at varying levels of defocus. The sVA is then calculated from the spatial frequency at which the MTF intersects with the neural threshold function (NTF). In this exemplary embodiment, the sVA produced for the eye models may be, for example, systematically <NUM> logMAR units lower (better acuity) than the clinical results, although the difference from the clinical results may be independent of defocus (p=<NUM>). If either of the simulated versus clinical or the dependence on defocus measures is outside of tolerance threshold, i.e., if the sVA in the eye models differed grossly from the clinical results outside of the predetermined tolerance, and/or if the difference between the modeled and clinical results was highly dependent on defocus, the method <NUM> may feedback, at step <NUM>, a weighting of the characteristics not within tolerance to indicate an optimization to one or both of the sVA model or the subset of eye models used at step <NUM>.

More particularly, for example, the weighting factors may, as discussed above, be made with respect to the characteristics and/or topologies employed in the selected eye models, and/or may additionally be with respect to the desired clinical outcome. As such, an improved VA may be weighted at <NUM> to <NUM> as compared to contrast sensitivity, while a VA may additionally be defined, with respect to field angles, as weighting far vision over near, forward angle over peripheral, and the like, for example.

Method <NUM> may be similarly employed for more complex lenses, such as for a population of cataract patients implanted with multifocal intraocular lenses (IOLs). Multifocal IOLs may supply two simultaneous focal points, one for distant objects and one for near objects, and may additionally provide a depth of focus that results in improved visual performance at intermediate distances. Such a multifocal IOL is the diffractive Tecnis® Multifocal IOL (model ZM900) by Abbott Medical Optics Inc. Those skilled in the pertinent arts will appreciate, in light of the discussion herein, that other multifocal lenses may be used in the instant invention.

For example, the Tecnis Multifocal IOL design has a diffractive relief pattern on the posterior surface, and splits light in equal amounts to the far and near focus. The diffractive add power for near vision, for example, is +<NUM> diopters. The Tecnis lens additionally provides an aspheric surface on the anterior side of the optic to reduce spherical aberration.

Cataract patients having certain eye characterizations may be bilaterally implanted with the Tecnis lens. For example, only patients with natural pupil diameters between <NUM> and <NUM> under photopic lighting conditions may be implanted. Such an eye characteristic may be used to select and/or weight ones of the available models eyes, and or may be weighted against other eye characteristics in the model eyes used, for example.

Several methods may be used to measure the pupil diameter using a pupilometer, such as image analysis techniques and wavefront measurements, including Wavescan RTM (VISX, Incorporated, Santa Clara, Calif. ) wavefront measurements, for example. The size of the pupil may at least partially determine the amount of light that enters the eye, and may also have an effect on the quality of the image formed by the light entering the eye. For example, when the pupil is very constricted, a relatively small percentage of the total light falling on the cornea may actually be allowed into the eye. In contrast, when the pupil is more dilated, the light allowed into the eye may correspond to a greater area of the cornea. Of note, accommodation and pupillary constriction work in unison in the healthy eyes when shifting from a far to a near viewing distance, and a fairly linear relation may thus exist between at least a portion of the pupillary constriction and accommodation ranges.

A standardized defocus test may be performed on each implanted patient, such as using a self-calibrating, self-illuminating (<NUM> cd/m<NUM>) EDTRS chart placed at <NUM> meters in front of the patient. Defocus may be introduced by placing successive minus trial lenses in <NUM> D increments over the patient's best distance correction. The relationship between defocus and viewing distance may be determined by: [viewing distance expressed in meters] = <NUM> / [defocus expressed in diopters]. Binocular visual acuity at each defocus position may then be measured, and may be from zero (best correction) to -<NUM> diopters at each defocus position, for example. The measured VA at defocus may be used to select or limit the selected eye models in the simulation, and/or may be used to enhance the modeling.

For each individual eye model, the power of the multifocal IOL may be determined, such as based on the eye length and corneal power. A lens may be modeled at a range of <NUM>-<NUM>, and preferably <NUM>, in front of the cornea of the modeled eye, and the imaging of the eye models may be traced and refracted for both spherical and cylindrical power. Defocus testing may then be simulated by: placing a point source target at <NUM> meters in front of the anterior cornea, i.e., at a distance correspondent to that used in the clinical setting; fixing the eye model to a fixed physical pupil diameter of <NUM>, corresponding to an average apparent pupil size of approximately <NUM> in the clinical setting; varying the power of the spectacle lens in <NUM> diopter increments to obtain defocus; and, at each defocus position, calculating the sVA.

Pursuant to the sVA modeling, differences between the clinical outcomes, on average, and the aforementioned eye models may indicate a need for modification of one or both of the sVA model or the eye models used. Needless to say, the larger the sample size that is fed back through the system to the sVA model and the eye models, the more likely any correction to the modeling will be properly indicative of clinical optimization. As such, the present invention is advantageous in that it may provide a networking among large numbers of practitioners, and thus may accept a large volume of feedback. Further, the feedback provided may be corresponded to the sVA modeling of the eye models used, thus enabling a correspondence, over a large sample size, between sVA modeling of the eye models and clinical outcomes.

<FIG> is a block diagram illustrating system <NUM> in accordance with the present invention. The illustrated system <NUM> may include at least one processor <NUM>, having associated therewith a plurality of eye models <NUM>, such as the Piers models or subsets thereof, the Liou and Brennan model, the Seidel aberration model, or the Le Grandoye, for patients having particular aberrations, characterizations and/or topologies, and simulator <NUM>. Simulator <NUM> may be any type of modeling software capable of modeling an ophthalmic lens <NUM> of a given design in at least one of the eye models <NUM> provided. Simulator <NUM> may be embodied as Code V, OSLO, Zemax, ASAP, and similar software modeling programs, for example. The at least one processor <NUM> applies simulator <NUM> to at least one eye model <NUM> to output a simulation <NUM> of eye characteristics, such as VA and/or contrast sensitivity.

System <NUM> further includes at least one remote, and may include at least one local, clinical input <NUM>. Clinical input <NUM> may be provided over at least one network <NUM>, and is input to at least one processor <NUM> for comparison to the characteristics of simulation output <NUM>. In the event that simulation output <NUM> is deficient, such as showing suboptimal variance from clinical input <NUM>, processor <NUM> may act as an optimizer <NUM> to modify at least one of selected eye models <NUM>, the weights associated with the selected eye models <NUM> and/or the characteristics of the eye, and the actions of simulator <NUM>, in order to obtain a more suitable simulation output <NUM> in light of clinical input <NUM>.

As will be understood by those skilled in the pertinent arts, clinical input <NUM> may, in certain exemplary embodiments, be an average over a predetermined number, or over all, clinical outcomes having one or more predetermined, or all, common topologies and/or characteristics of the patient eye. Correspondingly, eye models <NUM> used may be a simulated or clinically obtained average over a population having particular characteristics, a simulated or clinically obtained average over a population generally, a simulation matched to a particular patient, a patient type (i.e., cataract patient or LASIK patient), a group of patients, or the like.

For example, the optimizer <NUM> may optimize the parameters of lenses designed at simulator <NUM>, wherein the simulator initially designed the lens based on patients of a particular pupil diameter and/or having a desired optical power, and wherein optimizer <NUM> determines variations to the simulation <NUM> at simulator <NUM> based on failure of clinical results to meet the desired optical power tolerance threshold for that parameter(s) in patients having the designed-for pupil diameter.

Moreover, and as referenced above, the method of <FIG> and the system of <FIG>, and the exemplary embodiments set forth herein, may be implemented using computer hardware and software on a computer readable medium, and the computing hardware and software may preferably be connected to at least one computing network. The software may, for example, be implemented by system <NUM> to perform method <NUM>, such as via a graphical user interface (GUI) provided in a clinical setting. The GUI may provide any number of graphical panels for convenient use by a clinician, such as three primary panels. The primary panels may include, for example, an optical parameter panel, a clinical outcome input <NUM> panel, and a recommended action panel that may be based on simulation <NUM>. Needless to say, one or more of the graphical panels may be divided into sub-panels, such as sub-panels for optimizations, verifications, graphs, images, historical data, and the like. The software GUI may also provide menu bars, tool bars, status bars, drop down menus, and the like.

Method <NUM> and system <NUM> may be applied to a given population of modeled eyes having predetermined characteristics and/or topologies, such as in order to gain a sufficient sample size to enable optimization of the lens design, the selected eye models, and/or the simulation methodology based on clinical findings. Figures Sa-Sd are histograms illustrating eye characteristics for a population of model eyes. As illustrated, Figure Sa shows the corneal power of the eye across a population of model eyes. Figure Sb shows the description of the topography of a population of model eyes by a <NUM>th order Zernike polynomial. As will be understood to those skilled in the art, Zernike polynomials describe aberrations of the lens from an ideal spherical shape, which aberrations may result in refraction errors.

The histogram of Figure Sc illustrates the axial length of the eye across a population of model eyes. Finally, Figure Sd is a histogram of the magnitude of the total refractive errors of the eye across a population of model eyes using root-mean squares (RMS). For example, a minimum root-mean- squares (RMS) error may be used to determine the accommodation during different conditions. For instance, if no aberrations are present, and there is <NUM> D of residual accommodation, such a patient uses <NUM> D of residual accommodation when visualizing a target at <NUM> meters. Moreover, the patient uses all <NUM> D of residual accommodation to view a target at <NUM> meters. However, the patient would have difficulty viewing targets closer than <NUM> meters, as the residual accommodation is exhausted and no longer available.

While <FIG> illustrates characteristics of populations of eyes within the Piers physiological models, <FIG> is a plot illustrating the sVA across the <NUM> Piers eye models. As shown, the sVA is plotted against defocus, wherein the defocus is varied to simulate performance of the eye. Upon simulation, ones of the eye models having similar characteristics and/or topologies to the clinical eye(s) of interest may be plotted against the clinical eye(s) of interest, such as to obtain a comparative plot of the sVA and clinical performance. Such comparative plots are illustrated in <FIG>, and may be used in the method <NUM>, for example, in order to assess optimizing modifications to be made to at step <NUM> of <FIG>.

<FIG> are plots illustrating sVA (light plot) and clinical VA (dark plot) versus defocus, for a population of eyes having varying pupil characteristics. Defocus has is mathematically expressed above. For example, <FIG> illustrates a comparison of average clinical VA and sVA for a set of eyes having a small pupil, <FIG> illustrates the same comparison for a set of eyes having a medium pupil, and <FIG> illustrates the comparison for a set of eyes having a large pupil.

As indicated by the plots of <FIG>, clinical VA and sVA for a set of modeled eyes may vary over a range of defocus for different eye characteristics. This variation over the range of defocus may also provide secondary characteristics via the comparison, such as the plot of <FIG> showing the correlation between clinical VA and sVA. As discussed above, particularly with respect to <FIG> and <FIG>, the difference between the clinical VA and sVA, and/or the secondary characteristics of the difference, may have an accepted tolerance threshold within which the simulation is deemed to acceptably define the clinical implementation of the lens. If the clinical VA is not within tolerance of the sVA, the difference in the plots of <FIG>, and/or the secondary characteristics of the difference as shown in <FIG>, may be used in the method of <FIG> and the system of <FIG> as feedback to modify the simulation. Modification of the simulation may include, for example and as discussed hereinabove, variation in the simulation and/or calculations, changes in the weighting factors, or the weighting of the factors and/or changes to the selected model eye(s). A designed lens may then be modified until the lens is optimized using the modified simulation, and that lens, once clinically implemented, may be deemed clinically optimal if the clinical VA is within the predetermined tolerance of the sVA.

By way of specific example, the optimization method <NUM> and system <NUM> may be applied to a particular IOL design, such as design model 911A by Abbott Medical Optics Inc. , and may subsequently dictate the use of an alternative design, such as a multifocal IOL. In this illustration, the model 911A is clinically tested in three groups of normal cataract patients, having small, medium, and large pupils. The clinical outcome of VA as a function of defocus is illustrated in <FIG>, wherein each line shown depicts an average outcome for the respective group of patients.

For the sVA, three sets of the <NUM> Piers eye models, representing a normal cataract population and having essentially the same or similar characteristics (small, medium and large pupil sizes) to the eyes in the clinical groups, are selected. The design of model 911A is modeled for the sVA as a function of defocus, and the results are illustrated in <FIG>, wherein each line depicts the average outcome for the respective set of eye models.

The differences between the simulation outcome, namely the sVA in this example, and the clinical outcome, namely the VA in this example, are assessed. Figure 1O illustrates the correlation between the sVA and the clinical VA, wherefrom the differences between the sVA and the clinical VA may be assessed.

<FIG> illustrates the optimization of the modeled lens based on the assessed differences, and compares the optimized simulated outcome to the clinical outcome. The optimized simulation may be used to generate a new IOL design to be optimally provided for the same groups of cataract patients. In this exemplary embodiment, a multifocal IOL design may be employed to provide the desired visual acuity shown in <FIG>.

An IOL design that matches the desired outcome, according to the simulation outcome, is the aforementioned Tecnis Multifocal IOL model ZM900. The IOL model ZM900 may thus be implanted in the three groups of normal cataract patients having small, medium, and large pupils. The clinical outcome, expressed as VA as a function of defocus, is illustrated in <FIG>, wherein each line depicts the average outcome for each group of patients. The differences between the sVA and the clinical VA may again be assessed, and used to iteratively optimize the simulator, or the recommended lens, as desired, for example. In accordance with <FIG>, those skilled in the art will appreciate that the use of simulation in the present invention resulted in a lens design, namely model ZM900 in this example, that closely matched clinical performance, although the simulation was based on a different lens design, namely model <NUM> in this example.

Needless to say the illustration immediately hereinabove is provided by way of example only, and may be applicable to lens design, modification of physical lens design, modification to simulation, modification to selections of eye models, and the like. Similarly, the illustration is applicable to not only groups of patients, or with regard to current lens designs, but is equally applicable to custom and quasi-custom lens design, for individual patients and limited or unique subsets of patients, respectively.

Claim 1:
A system for optimizing a clinical implementation of an ophthalmic lens, wherein the ophthalmic lens is indicated for treating at least one condition of a set of eyes, comprising:
a simulator (<NUM>) provided by at least one processor (<NUM>) that is adapted to model the ophthalmic lens in at least one of a plurality of eye models (<NUM>) having at least first characteristics, wherein said simulator is adapted to output a first outcome of the ophthalmic lens in the at least one of said plurality of eye models, and wherein said at least one eye model is indicative of the at least one condition of the set of eyes;
wherein the at least one processor (<NUM>) is adapted to receive at least one clinical input (<NUM>) comprising at least second characteristics of a clinical eye associated with the clinical implementation, wherein the second characteristics are at least substantially equivalent to the first characteristics, and a second outcome indicative of the clinical implementation of the ophthalmic lens; and the system further comprising:
a comparator instantiated by the at least one processor (<NUM>) that is adapted to compare the first outcome and the second outcome, wherein comparing the first outcome and the second outcome comprises comparing differences between the first outcome and the second outcome to a predetermined tolerance threshold; wherein
if the differences between the first outcome and the second outcome are not within the predetermined tolerance threshold the processor (<NUM>) is adapted to optimize the at least one of a plurality of eye models (<NUM>) to bring the differences within the predetermined tolerance threshold and then use the optimized at least one of a plurality of eye models (<NUM>) to optimize the ophthalmic lens to a second ophthalmic lens using the optimized at least one of a plurality of eye models.