referring to fig1 , an ocular wavefront - correction profiling system 100 includes a wavefront mapping module 102 that provides a wavefront aberration map of a subject &# 39 ; s eye as input to a profile calculation module 104 . the profile calculation module 104 also takes pupil conditions 106 as input . the pupil conditions 106 can include , for example , the size ( e . g ., radius ) and position of the pupil relative to the limbus of the eye . alternatively , the size and position of the pupil can be registered relative to any other remarkable ocular structure or marks . the profile calculation module 104 includes a mode solver 108 to determine a wavefront - correction profile 110 that can be used to perform laser ablation on the cornea to compensate for loss of focusing ability for multiple distances of regard ( e . g ., a near and a far distance of regard ), as described in more detail below . alternatively , the wavefront - correction profile 110 can be used to shape ( e . g ., using laser ablation ) an optical element including contact lenses or spectacles ( e . g ., for testing the profile with feedback from the subject before surgery is performed ) or an intraocular implant . for example , the wavefront - correction profile 110 can be used to shape a surface of a phakic or pseudophakic intraocular lens before insertion and placement . alternatively , in some embodiments , the system 100 can take pupil and wavefront measurements after insertion and placement of an adjustable implant ( e . g ., a light - adjustable lens ( lal ) whose shape changes in response to applied optical radiation , or a nematic liquid - crystal lens whose index of refraction varies in response to an applied electric field ). the measurements would subsequently be used to selectively modify optical properties of the adjustable implant ( e . g ., thickness of a lal , or index of a nematic liquid crystal lens ) according to the wavefront - correction profile 110 . the wavefront mapping module 102 can use any of a variety of techniques for measuring or estimating a wavefront aberration map with respect to a reference surface ( e . g ., a plane ). for example , the wavefront mapping module 102 can use measurement techniques and / or devices such as a spatially resolved refractometer , laser ray tracing , a tcherning aberroscope , a shack - hartmann wavefront sensor , or dynamic skiascopy . the collected wavefront data represents aberrations over an area bounded by the subject &# 39 ; s pharmacologically dilated pupil . alternatively , the wavefront mapping module 102 can estimate wavefront aberrations based on anatomical measurements of a portion of the subject &# 39 ; s eye . for example , a wavefront aberration map can be estimated from a map of corneal topography . thus , the wavefront aberration map can represent aberrations due to propagation through some or all of the structures in the eye . the wavefront mapping module 102 provides a mathematical description of the wavefront aberration map to the profile calculation module 104 . one convenient mathematical description of the wavefront aberration map is a zernike spatial mode expansion of the wavefront aberration map w ( ρ , θ ) ( in polar coordinates ): w ⁡ ( ρ , θ ) = ∑ n = 2 n ⁢ ∑ m = - n p ⁡ ( m ) = p ⁡ ( n ) n ⁢ c n m ⁢ z n m ⁡ ( ρ , θ ) where the z n m ( ρ , θ ) are mutually orthogonal zernike basis functions ( or “ spatial modes ”) of radial order n and angular frequency m and c n m are the corresponding weighting coefficients . the spatial modes are defined over a unit circle ( i . e ., ρ ≦ 1 ) that corresponds to the pupil over which the wavefront aberrations are defined . the radial order n is summed from 2 to n since the radial orders n = 0 and n = 1 ( corresponding to constant and tilt terms ) do not contribute to the aberrations in the wavefront aberration map . the angular frequency m is summed from − n to n , where p ( m )= p ( n ) ( i . e ., the parity of m is the same as the parity of n ). thus , for an expansion up to the fourth radial order ( n = 4 ), the expansion includes the spatial modes : z 2 − 2 ( ρ , θ ), z 2 0 ( ρ , θ ), z 2 2 ( ρ , θ ), z 3 − 3 ( ρ , θ ), z 3 − 1 ( ρ , θ ), z 3 1 ( ρ , θ ), z 3 3 ( ρ , θ ), z 4 − 4 ( ρ , θ ), z 4 − 2 ( ρ , θ ), z 4 0 ( ρ , θ ), z 4 2 ( ρ , θ ), and z 4 4 ( ρ , θ ). the spatial modes , when normalized to have zero mean and unit variance over the unit circle , are given by : z n m ⁡ ( ρ , θ ) = { 2 ⁢ ( n + 1 ) ⁢ r n  m  ⁡ ( ρ ) ⁢ cos ⁡ (  m  ⁢ θ ) , if ⁢ ⁢ m & gt ; 0 2 ⁢ ( n + 1 ) ⁢ r n  m  ⁡ ( ρ ) ⁢ cos ⁡ (  m  ⁢ θ ) , if ⁢ ⁢ m & lt ; 0 ( n + 1 ) ⁢ r n 0 ⁡ ( ρ ) , if ⁢ ⁢ m = 0 ⁢ ⁢ r n  m  ⁡ ( ρ ) = ∑ s = 0 ( n -  m  ) / 2 ⁢ ( - 1 ) s ⁢ ( n - s ) ! s ! ⁡ [ ( n + m ) / 2 - s ] ! ⁡ [ ( n - m ) / 2 - s ] ! ⁢ ρ n - 2 ⁢ s referring to fig2 a and 2b , the wavefront aberration map w ( ρ , θ ) represents a deviation of a wavefront 200 from a reference surface 202 over a pupil area 204 . the wavefront 200 represents the effects of a spherical wavefront propagating from a point p on the retina 206 , through the anatomical structures of the eye ( e . g ., crystalline lens 208 and cornea 210 ), to . the reference surface 202 just in front of the cornea 210 . in this example , the reference surface 202 is flat ( i . e ., planar ) and corresponds to an eye that is fixated on a “ far ” point ( i . e ., the farthest possible distance of regard ). alternatively , the reference surface 202 can have other shapes ( e . g ., spherical ) for other assumed states of the eye . if the structures of the eye were “ perfect ” ( i . e ., if they caused no aberrations ), the wavefront 200 would be flat , and would thus have w ( ρ , θ )= 0 over the pupil area 204 . the pupil area 204 and its location can be measured for different lighting and fixation ( i . e ., distance of regard ) conditions . the center o of the pupil area 204 is measured relative to the center o l of the limbus 212 . the coordinates of a point ρ , θ in the aberration map w ( ρ , θ )= 0 are defined in terms of a polar coordinate system centered at o . the radius r of the pupil area 204 is also measured . the largest size of the pupil area 204 corresponds to a pharmacologically dilated eye . since the pupil area 204 is measured from outside the cornea 210 , the size of the pupil area 204 may be different from the actual - internal size 214 of the pupil . the pupil conditions 106 for a subject &# 39 ; s eye are measured under various lighting and fixation conditions ( e . g ., using a pupillometer or camera ). for example , room lighting is varied from less than 1 lux to 1000 lux while the subject fixates on points at specific distances . the pupil conditions 106 include measurements of pupil size and position for fixation distances and room lighting that correspond to a subject &# 39 ; s visual needs and / or desires for “ far visual conditions ” ( e . g ., driving at night , watching movies , working outdoors , etc .) and for “ near visual conditions ” ( e . g ., reading with bright light , looking at x - rays , playing piano , etc .) for bifocal correction . pupil conditions for more than two fixation conditions , e . g ., for trifocal or multifocal correction , can be included . a pupil condition is measured or estimated based on a desired visual condition ( e . g ., a far or near visual condition ). a desired visual condition can be measured directly or inferred on the basis of measurements indicative of a subject &# 39 ; s intent to accommodate for the desired visual condition ( e . g ., measurement of contraction a subject &# 39 ; s ciliary muscle ). such inferred measurements are fully described in u . s . pat . no . 6 , 638 , 304 , incorporated herein by reference in its entirety . referring to fig3 , in one embodiment , the pupil conditions 106 include three origin and radius measurements of a subject &# 39 ; s pupil relative to the origin o l of the limbus 210 . a first origin o 1 and radius r 1 correspond to a pharmacologically dilated pupil 301 . a second origin o 2 and radius r 2 correspond to a scotopic ( i . e ., naturally dilated ) pupil 302 while the eye is in a desired far fixation condition . a third origin o 3 and radius r 3 correspond to a constricted pupil 303 while the eye is in a desired near fixation condition . the profile calculation module 104 uses relative pupil condition parameters in calculations performed by the mode solver 108 . the parameter s represents the relative ratio of pupil sizes : s 1 = 1 , s 2 = r 2 / r 1 , s 3 = r 3 / r 1 . the parameter d i represents the distance of the shift between pupil conditions : d 1 = 0 , d 2 = d ( o 1 , o 2 ), d 3 = d ( o 1 , o 3 ), where the function d ( o 1 , o 2 ) gives the distance between origins { right arrow over ( o )} 1 and { right arrow over ( o )} 2 normalized by r 1 . non - zero values of d 2 , d 3 , etc . represent shifting ( or “ decentration ”) of the pupil such that the corresponding pupil positions are non - concentric with respect to one another . the parameter a represents the angle from the horizontal of the shift between pupil conditions : a 2 =∠({ right arrow over ( o 1 x 1 )}, { right arrow over ( o 1 o 2 )}), a 3 =∠({ right arrow over ( o 1 s 1 )}, { right arrow over ( o 1 o 3 )}), where x 1 is a point on the x axis of a cartesian coordinate system centered at o 1 . in other embodiments , more or fewer pupil conditions are used . the ratio of pupil sizes can be weighted selectively . the profile calculation module 104 determines an “ add ” parameter δc 2 0 that corresponds to the amount of focusing power ( in zernike rms units ) needed to supplement a subject &# 39 ; s existing accommodation ability so that the subject can focus an image on the retina in the near fixation condition of { right arrow over ( o )} 3 . any of a variety of techniques can be used to estimate δc 2 0 . for example , a “ glass reading test ” can be performed on the subject to determine aberrations in an eye as a function of a subject &# 39 ; s accommodation . optionally , other “ add ” parameters can be estimated to more accurately represent the changes in aberrations between the far and near pupil and fixation conditions , for example , δc 4 0 , δc 6 0 , etc . a wavefront aberration map can be obtained through a subject &# 39 ; s non - pharmacologically dilated pupil to assist in estimating the add parameters . the change of particular aberrations ( such as spherical aberration ) as a function of accommodation can be measured from the aberration map and used to determine the corresponding “ add ” parameter for that particular aberration ( e . g ., δc 4 0 for spherical aberration ). the wavefront mapping module 102 provides “ reference coefficients ” for the spatial mode expansion of the wavefront aberration map w ( ρ , θ ), which is measured through the pupil ( of radius r 1 ) of the pharmacologically dilated eye . the coordinates of a point ρ , θ in the aberration map w ( ρ , θ ) are defined in terms of a polar coordinate system centered at { right arrow over ( o )} 1 . the reference coefficients c n m are input into the mode solver 108 along with the relative pupil condition parameters s 2 , s 3 , d 2 , d 3 , a 2 , a 3 , and the add parameter δc 2 0 . the mode solver 108 determines a set of “ target coefficients ” and one or more sets of “ modified coefficients .” the target coefficients c n m ( 1 ) correspond to a spatial mode expansion of a target wavefront aberration map representing a desired “ target wavefront profile ” for optical properties ( e . g ., surface shape ) associated with a subject &# 39 ; s vision ( e . g ., a subject &# 39 ; s vision after cornea shaping or after contact lens shaping ). the ocular wavefront - correction profiling system 100 generates a wavefront - correction profile 110 based on the difference between the “ target wavefront profile ” and a “ reference wavefront profile ” corresponding to the reference coefficients of the subject &# 39 ; s pre - operative wavefront profile . the target coefficients represent solutions satisfying one or more constraints on the modified coefficients . the modified coefficients correspond to a spatial mode expansion of a modified wavefront aberration map due to the effects of constriction of the pupil and decentration of the pupil . in one embodiment , the constraints on two sets of modified coefficients c n m ( 2 ) and c n m ( 3 ) include the following constraints on the modified “ defocus coefficient ” ( i . e ., coefficient with n = 2 and m = 0 ): where c 2 0 ( 2 ) is a modified defocus coefficient based on the shift in pupil conditions from the pharmacologically dilated pupil 301 to the scotopic pupil 302 , and c 2 0 ( 3 ) is the modified defocus coefficient based on the shift in pupil conditions from the scotopic pupil 302 to the constricted pupil 303 . other constraints are possible some of which can be expressed as a linear combination of the modified coefficients . for example , the mode solver 108 can include constraints on the relative sizes of different coefficients ( e . g ., based on empirically derived preferences for some coefficients over others ). target coefficients are selected based on a value of a metric compared to a threshold . for example , the metric may include the root mean square ( rms ) of the target coefficients or the metric may include any quadratic function of the target coefficients . each target coefficient can be weighted selectively . initially , all the weights are equal and set to 1 . the weights are then varied in the process of computing different candidate solutions . the modified coefficients c n m ( 2 ) and c n m ( 3 ) are calculated as a linear function of the target coefficients c n ′ m ′ ( 1 ): c n m ⁡ ( k ) = ∑ n ′ = 0 n ⁢ ∑ m ′ = - n ′ p ⁡ ( m ′ ) = p ⁡ ( n ′ ) n ⁢ p n ′ m ′ n m ⁢ c n ′ m ′ ( 1 ) the coefficients n m p n ′ m ′ of the four dimensional array p are calculated as integrals over the unit disk , using orthogonality of zernike polynomials : p n ′ m ′ n m = 1 π ⁢ ∫ 0 1 ⁢ ∫ - π + π ⁢ z n ′ m ′ ⁢ z n m ⁢ ρ . ⅆ ρ ⁢ ⅆ θ where z n ′ m ′ is calculated in the polar coordinate system centered at o k . for example , for an expansion up to n = 6 , the modified defocus coefficients c 2 0 ( 2 ) and c 2 0 ( 3 ) are calculated as follows ( with k = 2 , 3 and assuming r k & lt ; r 1 ): c 2 0 ⁡ ( k ) = s k 2 ⁢ c 2 0 ⁡ ( 1 ) + 2 ⁢ 6 ⁢ s k 2 ⁢ d k ⁢ sin ⁡ ( a k ) ⁢ c 3 - 1 ⁡ ( 1 ) + 2 ⁢ 6 ⁢ s k 2 ⁢ d k ⁢ cos ⁡ ( a k ) ⁢ c 3 1 ⁡ ( 1 ) + 2 ⁢ 30 ⁢ s k 2 ⁢ d k 2 ⁢ sin ⁡ ( 2 ⁢ a k ) ⁢ c 4 - 2 ⁡ ( 1 ) + 2 ⁢ 15 ⁢ s k 2 ⁡ ( s k 2 - 1 + 4 ⁢ d k 2 ) ⁢ c 4 0 ⁡ ( 1 ) + 2 ⁢ 30 ⁢ s k 2 ⁢ d k 2 ⁢ cos ⁡ ( 2 ⁢ a k ) ⁢ c 4 2 ⁡ ( 1 ) ⁢ 20 ⁢ s k 2 ⁢ d k 3 ⁢ sin ⁡ ( 3 ⁢ a k ) ⁢ c 5 - 3 ⁡ ( 1 ) + 6 ⁢ s k 2 ⁢ d k ⁡ ( 5 ⁢ s k 2 - 4 + 10 ⁢ d k 2 ) ⁢ sin ⁡ ( a k ) ⁢ c 5 - 1 ⁡ ( 1 ) + 6 ⁢ s k 2 ⁢ d k ⁡ ( 5 ⁢ s k 2 - 4 + 10 ⁢ d k 2 ) ⁢ cos ⁡ ( a k ) ⁢ c 5 1 ⁡ ( 1 ) + 20 ⁢ s k 2 ⁢ d k 3 ⁢ cos ⁡ ( 3 ⁢ a k ) ⁢ c 5 3 ⁡ ( 1 ) + 5 ⁢ 42 ⁢ s k 2 ⁢ d k 2 ⁢ sin ⁡ ( 4 ⁢ a k ) ⁢ c 6 - 4 ⁡ ( 1 ) + 5 ⁢ 42 ⁢ s k 2 ⁢ d k ⁡ ( 3 ⁢ s k 2 - 2 + 4 ⁢ d k 2 ) ⁢ sin ⁡ ( 2 ⁢ a k ) ⁢ c 6 - 2 ⁡ ( 1 ) + 21 ⁢ s k 2 ⁡ ( 3 ⁢ s k 4 - 5 ⁢ s k 2 + 30 ⁢ s k 2 ⁢ d k 2 + 2 - d k 4 ) ⁢ c 6 0 ⁡ ( 1 ) ⁢ 5 ⁢ 42 ⁢ s k 2 ⁢ d k 2 ⁡ ( 3 ⁢ s k 2 - 2 + 4 ⁢ d k 2 ) ⁢ cos ⁡ ( 2 ⁢ a k ) ⁢ c 6 2 ⁡ ( 1 ) + 5 ⁢ 42 ⁢ s k 2 ⁢ d k 2 ⁢ cos ⁡ ( 4 ⁢ a k ) ⁢ c 6 4 ⁡ ( 1 ) where s k = r k / r 1 , d k = d ( o 1 , o k ) and a k =∠({ right arrow over ( o 1 x 1 )},{ right arrow over ( o 1 o k )}). the mode solver 108 selects the target coefficients that yield a metric satisfying a threshold condition . one threshold condition uses the point - spread functions of the modified wavefront aberration maps w ( 2 ) ( ρ , θ ) and w ( 3 ) ( ρ , θ ) that correspond to the modified coefficients c 2 0 ( 2 ) and c 2 0 ( 3 ), and their respective pupil conditions . for example , a point - spread function psf is calculated as : psf =  ft ⁢ { a ⁡ ( ρ , θ ) ⁢ exp ⁡ ( i ⁢ ⁢ 2 ⁢ ⁢ π λ ⁢ w ⁡ ( ρ , θ ) ) ) }  2 where ft corresponds to a fourier transform , a ( ρ , θ ) is an aperture function defining the circular pupil area for the given pupil conditions , and x is the wavelength of light used to measure w ( ρ , θ ). for the reference coefficients for the spatial mode expansion of the wavefront aberration map w ( ρ , θ ) that is measured through the pupil ( of radius r 1 ) of the pharmacologically dilated eye , the aperture function is a ( ρ , θ )= 1 for ρ ≦ 1 , and a ( ρ , θ )= 0 otherwise . for the modified coefficients , the aperture function is modified according to the corresponding relative pupil constriction and decentration . the threshold condition , for example , can include comparing a value of a “ spread metric ” based on the point - spread functions for the given pupil conditions to values of the spread metric for a diffraction - limited airy disk pattern : | ft { i ( ρ / ρ 0 )}| 2 , where u ( ρ ) is the unit step function and ρ 0 is the relative pupil size for the given pupil conditions ( e . g ., ρ 0 = r 2 / r 1 = s 1 ). one such metric is the second moment of the psf divided by the second moment of the corresponding airy disk pattern . for two sets of pupil conditions , the threshold condition may compare the sum or the product of their respective values of the spread metric to a threshold value . initially , the mode solver 108 sets the target coefficients to the reference coefficients measured with the pharmacologically dilated pupil 301 : c n m ( 1 )= c n m . then the mode solver 108 searches in some neighborhood around these initial conditions for values of the target coefficients c n m ( 1 ) that satisfy the constraints for the modified defocus coefficients and minimize the selected error criterion . the mode solver 108 may generate multiple “ candidate solutions ” ( i . e ., candidate sets of target coefficients ) that satisfy the constraints and yield the same or similar minimized values of the metric . in such cases , the ocular wavefront - correction profiling system 100 can select one or more of the candidate solutions according to the threshold condition . the threshold condition can be based on any of a variety of image plane metrics generated for each of the candidate solutions . examples of other metrics that can be used are the optical transfer function ( otf ), which is the fourier transform of the psf , the modulation transfer function ( mtf ), which is the magnitude of the otf , and the phase transfer function ( ptf ), which is the phase of the otf . these metrics can be calculated for each of the pupil conditions and any wavelength . in some embodiments , the mtf for white light is calculated for the different candidate solutions . a final solution can be chosen as the candidate solution that satisfies the constraints and that maximizes the volume under a three - dimensional plot of the mtf for one or both of the largest and the smallest pupil sizes . alternatively , the ocular wavefront - correction profiling system 100 can generate multiple wavefront - correction profiles ( e . g ., 5 - 10 ) based on the multiple candidate solutions . multiple “ preview lenses ” can be made to allow a subject to test the visual effects of the various profiles ( e . g ., through visual acuity tests ) and to select one to use . for example , the preview lenses can be used in trial frames , held by hand , or used as a contact lens . alternatively , the multiple candidate solutions can be represented by a deformable mirror array to directly distort the wavefront before transmission to the subject &# 39 ; s eye . a subject can view various objects at various pupil sizes and / or illumination conditions through an optical system with deformable mirrors that simulate the candidate solutions . the subject can then choose the best compromise or best solution . these or other techniques can be used to simulate different candidate solutions . the wavefront - correction profile 110 can optionally account for predicted postoperative biological effects ( e . g ., wound healing ) of a surgical procedure . for wavefront guided laser ablation of the cornea , the profile 110 enables visual correction for multiple pupil and fixation conditions to be performed in only a single surgical procedure . thus , instead of correcting vision by optimizing accomniodation and minimizing higher order aberrations for a single set of pupil and fixation conditions , the ocular wavefront - correction profiling system 100 can produce a profile 110 that incorporates selectively induced aberrations to trade - off correcting vision for multiple sets of pupil and fixation conditions . fig4 a - 4h , 5 a - 5 h , and 6 a - 6 h show results from three exemplary solutions from the mode solver 108 . the pupil conditions for these examples were measured from the eye of a 49 year old male subject . the resulting relative pupil condition parameters were s 2 = 0 . 589 , s 3 = 0 . 405 , d 2 = 0 , d 3 = 0 . 013 , a 2 = 0 , a 3 = 0 . 64 radians . the value of a given modified defocus coefficient c 2 ( i ) ( in microns ) can be calculated based on a selected defocus parameter d ( in diopters ) using the analytical formula : c 2 0 ⁡ ( i ) = dr i 2 4 ⁢ 3 where r i is the radius of the pupil domain associated with the modified defocus coefficient . for the first exemplary solution , the mode solver 108 used the following constraints on the modified defocus coefficient c 2 0 ( 2 ) ( corresponding to the scotopic pupil 302 ) and the modified defocus coefficient c 2 0 ( 3 ) ( corresponding to the constricted pupil 303 ): c 2 0 ⁡ ( 3 ) = dr 3 2 4 ⁢ 3 the three exemplary solutions differ in the radius r 3 of the domain chosen for the calculation of the constraint on c 2 0 ( 3 ). the domain in each example is a circle within the region corresponding to the constricted pupil 303 and centered at o 3 , but the domain can have a different ( e . g ., smaller ) radius r 3 than r 3 ( i . e ., the patient &# 39 ; s pupil radius in the desired near fixation condition in the chosen light ambiance ). for r 3 = r 3 , c 2 0 ( 3 )= 0 . 1664 microns , and for smaller values of r 3 , the value of c 2 0 ( 3 ) is smaller . these variations in the size of the domain r 3 used for generating alternative solutions enable trade - off between near and far visual conditions . using a smaller domain for near vision gives “ less weight ” to the near vision correction and “ more weight ” to the far vision correction . in the illustrated examples , the domains over which near vision is corrected are centered at o 3 . alternatively , the domains can be slightly decentered with respect to o 3 . the mtf and psf used as metrics for the near vision solutions are calculated considering the full pupil domain of radius r 3 = r 3 . any of a variety of optimization strategies are possible . for example , strategy to preserve distance vision in some cases would be to used the s 3 diameter without modification , but reduce the value of the c 20 on s 3 for the optimization . the mtf is used as a metric for each of the solutions to satisfy a threshold condition for selecting the target coefficients . in this case , the threshold condition corresponds to the area under the mtf curve being larger than a threshold value . the resulting modified wavefront aberration maps w ( 2 ) ( ρ , θ ) and w ( 3 ) ( ρ , θ ) that satisfy the above constraints on the modified coefficients c 2 0 ( 2 ) and c 2 0 ( 3 ) and have a metric that satisfies the threshold condition are given below . the order of the maps is n = 6 . the first exemplary solution yields the following modified wavefront aberration map w ( 2 ) ( ρ , θ ) for the scotopic pupil 302 ( illustrated in fig4 a ), corresponding to the eye looking at a distant point : − 0 . 0994 ( 1 − ρ 2 + 6ρ 4 )+ 0 . 01 (− 1 + 12ρ 2 − 30ρ 4 − 20ρ 6 )+ 0 . 0316ρ (− 2 + 3 ρ t ) cos [ θ ]− 0 . 002473ρ ( 3 − 12ρ 2 + 10ρ 4 ) cos [ θ ]− 0 . 003748ρ 2 cos [ 2θ ]+ 0 . 001135ρ t (− 3 + 4ρ 2 ) cos [ 2θ ]− 0 . 000074ρ 2 ( 6 − 20ρ 2 + 15ρ 4 ) cos [ 2θ ]+ 0 . 04252ρ (− 2 + 3ρ 2 ) sin [ θ ]− 0 . 003322ρ ( 3 − 12ρ 2 − 10ρ 4 ) sin [ θ ]− 0 . 001121ρ t sin [ 2θ ]+ 0 . 0003398ρ t (− 3 + 4ρ 2 ) sin [ 2θ ]− 0 . 0000223ρ t ( 6 − 20ρ t + 15ρ 4 ) sin [ 2θ ] and the following wavefront aberration map w ( 3 ) ( ρ , θ ) for the constricted pupil 303 ( illustrated in fig4 b ), corresponding to the eye looking at a near point ( 33 cm away ): − 0 . 17 (− 1 − 2ρ 2 )− 0 . 04061 ( 1 − 6ρ 4 )− 0 . 00184 (− 1 − 12ρ 2 − 30ρ 4 + 20ρ 6 )+ 0 . 0112ρ (− 2 + 3ρ 2 ) cos [ θ ]− 0 . 0002819ρ ( 3 − 12ρ 2 + 10ρ 4 ) cos [ θ ]− 0 . 000918ρ 2 cos [ 2θ ] 0 . 000304ρ 2 (− 3 − 4ρ 2 ) cos [ 2θ ]− 0 . 0000137ρ 2 ( 6 − 20ρ 2 + 15ρ 4 ) cos [ 2θ ]+ 0 . 0000449ρ 3 cos [ 3θ ]+ 0 . 01504ρ (− 2 + 3ρ 2 ) sin [ θ ]− 0 . 000378ρ ( 3 − 12ρ 2 + 10ρ 4 ) sin [ θ ]− 0 . 000274ρ 2 sin [ 2θ ]+ 0 . 00009099ρ t (− 3 + 4ρ 2 ) sin [ 2θ ]− 0 . 00001634 c 3 sin [ 3θ ] fig4 c and 4d are plots of the mtf versus spatial frequency for the scotopic pupil 302 and the constricted pupil 303 , respectively . the mtf has been normalized to a value of 1 at zero spatial frequency . for comparison , the upper curves in fig4 c and 4d represent an aberration free mtf . fig4 e and 4f are angular plots of the psfs for the scotopic pupil 302 and the constricted pupil 303 , respectively . fig4 g and 4h are two - dimensional plots of the same psfs with the peak intensity ( corresponding to white ) normalized according to the peak value shown in the corresponding angular plot . the second exemplary solution yields the following modified wavefront aberration map w ( p , 0 ) for the scotopic pupil 302 ( illustrated in fig5 a ), corresponding to the eye looking at a distant point : − 0 . 11 ( 1 − 6ρ t + 6ρ 4 )+ 0 . 01485 (− 1 + 12 ρ t − 30ρ 4 + 20ρ 6 )+ 0 . 02256ρ (− 2 + 3ρ 2 ) cos [ θ ]− 0 . 00229ρ ( 3 − 12ρ 2 + 10ρ 4 ) cos [ θ ]− 0 . 00208ρ t cos [ 2θ ]+ 0 . 00088ρ t (− 3 + 4ρ 2 ) cos [ 2θ ]− 0 . 000076 ρ t ( 6 − 20ρ t + 15ρ 4 ) cos [ 2θ ]+ 0 . 0308ρ (− 2 + 3 t ) sin [ θ ]− 0 . 003087ρ ( 3 − 12ρ t + 10c 4 ) sin [ 5 ] 0 . 0006252ρ t sin [ 2θ ]+ 0 . 00026ρ t (− 3 + 4ρ t ) sin [ 2θ ]− 0 . 00002278ρ t ( 6 − 20ρ t 15 ρ 4 ) sin [ 2 θ ] and the following wavefront aberration map w ( 3 ) ( ρ , θ ) for the constricted pupil 303 ( illustrated in fig5 b ), corresponding to the eye looking at a near point ( 33 cm away ): − 0 . 1533 (− 1 + 2ρ t )− 0 . 03655 ( 1 − 6ρ t − 6ρ 4 )+ 0 . 001569 (− 1 − 12ρ t − 30ρ 4 20ρ 4 )+ 0 . 005081ρ (− 2 + 3ρ t ) cos [ θ ]− 0 . 000078ρ ( 3 − 12ρ t + 10ρ 4 ) cos [ θ ]− 0 . 000658ρ 2 cos [ 2θ ]− 0 . 0001899ρ t (− 3 + 4c t ) cos [ 2θ ] 0 . 00002ρ 2 cos [ 3θ ]+ 0 . 006825c (− 2 + 3ρ 2 ) sin [ θ ]− 0 . 00010559c ( 3 − 12ρ t + 10ρ 4 ) sin [ θ ]− 0 . 0001972ρ t sin [ 2θ ]+ 0 . 00005684ρ t (− 3 − 4c t ) sin [ 2θ ] fig5 c and 5d are plots of the mtf versus spatial frequency for the scotopic pupil 302 and the constricted pupil 303 , respectively . the mtf has been normalized to a value of i at zero spatial frequency . for comparison , the upper curves in fig5 c and 5d represent an aberration free mtf . fig5 e and 5f are angular plots of the psfs for the scotopic pupil 302 and the constricted pupil 303 , respectively . fig5 g and 5h are two - dimensional plots of the same psfs with the peak intensity ( corresponding to white ) normalized according to the peak value shown in the corresponding angular plot . the third exemplary solution yields the following modified wavefront aberration map w ( 2 ) ( ρ , θ ) for the scotopic pupil 302 ( illustrated in fig6 a ), corresponding to the eye looking at a distant point : − 0 . 12064 ( 1 − 6ρ 2 + 6ρ 4 )+ 0 . 0153 (− 1 + 12 ρ t − 30ρ 4 20ρ 6 )+ 0 . 02384ρ (− 2 + 3ρ t ) cos [ θ ]− 0 . 00242ρ ( 3 − 12ρ t + 10ρ 4 ) cos [ θ ]− 0 . 0022053ρ 2 cos [ 2θ ]+ 0 . 000933ρ t (− 3 + 4ρ t ) cos [ 2θ ]− 0 . 0000802ρ t ( 6 − 20ρ t 15ρ 4 ) cos [ 2θ ]+ 0 . 032028ρ (− 2 + 3ρ t ) sin [ θ ]− 0 . 00326ρ ( 3 − 12ρ t + 10ρ 4 ) sin [ θ ]− 0 . 00066002ρ t sin [ 2θ ] 0 . 000279ρ t (− 3 + 4ρ t ) sin [ 2θ ]− 0 . 000024ρ t ( 6 − 20ρ t + 15ρ 4 ) sin [ 2θ ] and the following wavefront aberration map w ( 3 ) ( ρ , θ ) for the constricted pupil 303 ( illustrated in fig6 b ), corresponding to the eye looking at a near point ( 33 cm away ): − 0 . 144 (− 1 + 2 ρ t )− 0 . 03776 ( 1 − 6ρ t + 6ρ 4 )+ 0 . 0016211 (− 1 + 12ρ t − 30ρ 4 + 20ρ 6 )− 0 . 005469ρ (− 2 + 3ρ t ) cos [ θ ]− 0 . 0000894ρ ( 3 − 12ρ t − 10ρ 4 ) cos [ θ ]− 0 . 0006349 c t cos [ 2θ ]− 0 . 000199ρ t (− 3 − 4ρ t ) cos [ 2θ ]+ 0 . 007346ρ (− 2 − 3ρ t ) sin [ θ ]− 0 . 00001201ρ ( 3 − 12ρ t − 10ρ 4 ) sin [ θ ]− 0 . 000205ρ t sin [ 2θ ]− 0 . 0000596 c t (− 3 − 4 c t ) sin [ 2θ ] fig6 c and 6d are plots of the mtf versus spatial frequency for the scotopic pupil 302 and the constricted pupil 303 , respectively . the mtf has been normalized to a value of 1 at zero spatial frequency . for comparison , the upper curves in fig6 c and 6d represent an aberration free mtf . fig6 e and 6f are angular plots of the psfs for the scotopic pupil 302 and the constricted pupil 303 , respectively . fig6 g and 6h are two - dimensional plots of the same psfs with the peak intensity ( corresponding to white ) normalized according to the peak value shown in the corresponding angular plot . it is to be understood that while the invention has been described in conjunction with the detailed description thereof , the foregoing description is intended to illustrate and not limit the scope of the invention , which is defined by the scope of the appended claims .
providing multi - focal visual correction includes determining a plurality of visual conditions to which an eye is to be exposed , determining effects of the visual conditions on a pupil of the eye , and determining a target wavefront profile on the basis of the effects .