Patent Publication Number: US-11389329-B2

Title: Lenses, systems and methods for providing binocular customized treatments to correct presbyopia

Description:
CROSS-REFERENCES TO RELATED APPLICATIONS 
     This application claims priority to and is a divisional of U.S. patent application Ser. No. 15/665,109, filed Jul. 31, 2017, which is a divisional of U.S. patent application Ser. No. 14/096,544, filed on Dec. 4, 2013, now U.S. Pat. No. 9,717,628, which claims priority to U.S. provisional application No. 61/733,292 filed on Dec. 4, 2012, the entire contents of which are incorporated herein by reference. 
    
    
     BACKGROUND OF THE INVENTION 
     Field of the Invention 
     This invention relates generally to correction of eye defects, and more specifically, to a system, method and apparatus for providing binocular customized treatments for remedying presbyopia. 
     Description of the Related Art 
     Surgery on the human eye has become commonplace in recent years. Many patients pursue eye surgery as an elective procedure to treat an adverse eye condition, such as to avoid the use of contact lenses or glasses. One eye condition that can be treated surgically is presbyopia. A patient suffering from presbyopia lacks the capability of the eye lens to accommodate or bend and thus to see at far distance and at near distance. Presbyopia can be induced by age and/or pseudophakia (a condition in which a natural lens has been replaced with an intraocular lens). 
     Several treatment options are available for presbyopia. For example, multifocal intraocular lenses, extended depth of focus lenses, corneal inlays or other accommodating intraocular lenses can be surgically implanted in the eye of a patient suffering from presbyopia to allow the patient to focus and refocus between near and far objects. Another treatment option available to patients suffering from presbyopia is based on monovision. In this option, generally the dominant eye is targeted for distant vision and the non-dominant eye is targeted for near vision. This can be achieved by implanting the dominant eye with an intraocular lens (IOL) having a power that achieves plano refraction such that the dominant eye has no refractive error and by implanting the non-dominant eye with an IOL that has an add power between 1.0-2.0 Diopter over the dominant eye. 
     However, such an approach can result in sub-optimal intermediate vision if the non-dominant eye is targeted for near vision or sub-optimal near vision if the non-dominant eye is targeted for intermediate vision. Additionally, some patients may not tolerate the refractive differences in the dominant and non-dominant eye. 
     SUMMARY OF THE INVENTION 
     Multifocal intraocular lenses (IOLs) providing two or more optical powers, for example, one for near vision and one for distant vision, can be implanted in the eye of a patient suffering from presbyopia to overcome some of the disadvantages of monovision. Although multifocal IOLs can lead to improved quality of vision for many patients, some patients can experience undesirable visual effects (dysphotopsia), e.g. glare or halos. For example, if light from a distant point source is imaged onto the retina by the distant focus of a multifocal IOL, the near focus of the multifocal IOL will simultaneously superimpose a defocused image on top of the image formed by the distant focus. This defocused image may manifest itself in the form of a ring of light surrounding the in-focus image, and is referred to as a halo. Rotationally symmetric multifocal designs present symmetric halo shapes, while non-rotationally symmetric multifocal lenses present asymmetric halos. Additionally, intermediate vision may be compromised in multifocal IOLs that are configured to provide near and distant vision. 
     Thus, there exists a need for an ophthalmic solution that provides improved vision at all of near, far and intermediate distances while reducing dysphotopsia. One approach to provide improved vision at all of near, far and intermediate distances while reducing dysphotopsia can be a lens with an extended depth of focus. Without subscribing to any particular, a lens with an extended depth of focus can image objects with a certain distance of its focal point with acceptable sharpness on the retina. Thus, an extended depth of focus lens can produce images with acceptable sharpness for objects located at intermediate to far distances or for objects located at near to intermediate distances. Various techniques for extending the depth of focus of a lens have been proposed. For example, some approaches are based on intraocular lenses with refractive or diffractive zones with different powers. 
     The embodiments disclosed herein include various ophthalmic lens solutions (such as, for example, contact lenses, IOLs, phakic IOLs, corneal inlays, as well as corneal reshaping procedures such as, laser treatments, or combinations of thereof etc.) for treating ophthalmic conditions in both eyes to enhance visual acuity at near, intermediate and far distances, and therefore provide a full range of vision. In various embodiments disclosed herein, binocular extension of depth of focus is achieved by inducing rotationally symmetric aberrations (e.g. fourth and/or higher order spherical aberrations) in one eye and by inducing non-rotationally symmetric aberrations (e.g. astigmatism, coma and/or trefoil) in the other eye to enhance visual acuity at an intermediate distance. In another aspect, binocular extension of depth of focus is achieved by a rotationally symmetric diffractive lens solution in one eye and a rotationally asymmetric diffractive lens solution in the other eye. In another aspect, binocular extension of depth of focus is achieved by a rotationally symmetric refractive lens solution in one eye and a rotationally asymmetric refractive lens solution in the other eye. In another aspect, visual acuity at an intermediate distance can be enhanced by applying scaled version of natural aberrations that are present in the patient&#39;s eye, as referred in U.S. patent application Ser. No. 13/690,505 filed on Nov. 30, 2012 and entitled Lenses, Systems and Methods For Providing Custom Aberration Treatments And Monovision To Correct Presbyopia which is incorporated herein by reference, in addition to inducing rotationally symmetric and asymmetric aberrations. In an alternative embodiment, the aberration patterns (e.g. fourth and/or higher order spherical aberrations and astigmatism, coma and/or trefoil) may also be imposed on the top of monovision, achieved with either refractive or diffractive techniques or on the top of a mix and match of multifocal or extended depth of focus lenses, which may also combine symmetric and asymmetric concepts binocularly. 
     In various embodiments, a binocular vision simulator can be used to determine the amount and type of aberrations to be induced in each eye. The combination that provides the best through focus performance as well as the patient&#39;s comfort is chosen. An example method of implementing the concepts discussed herein includes: (i) determining with a binocular vision simulator a first amount of rotationally symmetric or non-rotationally symmetric aberration which provides visual acuity for intermediate and distant vision in a first eye; (ii) determining with the binocular vision simulator a second amount of rotationally symmetric or non-rotationally symmetric aberration which provides visual acuity for intermediate and near vision in a second eye; (iii) applying the first amount of rotationally symmetric or non-rotationally symmetric aberration in the first eye; and (iv) applying the second amount of non-rotationally symmetric or rotationally symmetric aberration in the second eye, wherein a rotationally symmetric aberration pattern is applied to the second eye if a non-rotationally symmetric aberration pattern is applied to the first eye and vice-versa. Binocular visual acuity or just visual perception at different defocus position may be tested in those conditions. The test may also be performed in the presence of rotationally symmetric and asymmetric diffractive profiles once applied using the binocular visual simulator, with a goal of determining the combination of aberrations and diffractive ophthalmic solutions which provide a continuous range of vision. 
     Various embodiments disclosed herein include lenses, methods and systems that can correct presbyopia by extending the depth of focus for lenses that are configured to provide distant or near vision such that improved intermediate vision is provided by binocular summation. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Understanding of the present invention will be facilitated by consideration of the following detailed description of the preferred embodiments of the present invention taken in conjunction with the accompanying drawings, in which like numerals refer to like parts, and in which: 
         FIG. 1  is a diagram illustrating the relevant structures and distances of the human eye. 
         FIGS. 2A and 2B  are flowcharts of an implementation of a method used to determine the combination of aberrations that can be induced to provide vision acuity at near, far and intermediate distances. 
         FIG. 3  is a diagram illustrating aspects of a system that can be used to implement the method described in  FIG. 2 . 
       FIG.  4 A 1 - 4 A 5  shows various embodiments of lenses having rotationally asymmetric diffractive features. 
     
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT 
     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 purpose of clarity, many other elements found in typical lenses, lens systems and lens design methods. Those of ordinary skill in the arts can recognize that other elements and/or steps are desirable and may be used in implementing the embodiments described herein. 
     The embodiments described herein are directed to an ophthalmic lens, such as an intraocular lens (IOL), or a corneal implant, and other vision correction methodologies, such as laser treatments, and a system and method relating to same, for providing rotationally symmetric aberration patterns in one eye and non-rotationally symmetric aberration patterns in the other eye in order to induce a binocular customized treatment that achieves visual acuity at a range of distances. 
     The terms “power” or “optical power” are used herein to indicate the ability of a lens, an optic, an optical surface, or at least a portion of an optical surface, to redirect incident light for the purpose of forming a real or virtual focal point. Optical power may result from reflection, refraction, diffraction, or some combination thereof and is generally expressed in units of Diopters. One of ordinary skill in the art will appreciate that the optical power of a surface, lens, or optic is generally equal to the reciprocal of the focal length of the surface, lens, or optic, when the focal length is expressed in units of meters. 
       FIG. 1  is a schematic drawing of a human eye  200 . Light enters the eye from the left of  FIG. 1 , and passes through the cornea  210 , the anterior chamber  220 , a pupil defined by the iris  230 , and enters lens  240 . After passing through the lens  240 , light passes through the vitreous chamber  250 , and strikes the retina  260 , which detects the light and converts it to a signal transmitted through the optic nerve to the brain (not shown). Cornea  210  has corneal thickness (CT), which is the distance between the anterior and posterior surfaces of the center of the cornea  210 . Anterior chamber  220  has an anterior chamber depth (ACD), which is the distance between the posterior surface of the cornea  210  and the anterior surface of the lens  240 . Lens  240  has lens thickness (LT) which is the distance between the anterior and posterior surfaces of the lens  240 . The eye has an axial length (AXL) which is the distance between the center of the anterior surface of the cornea  210  and the fovea of the retina  260 , where the image is focused. 
     The anterior chamber  220  is filled with aqueous humor, and optically communicates through the lens  240  with the vitreous chamber  250 . The vitreous chamber  250  is filled with vitreous humor and occupies the largest volume in the eye. The average adult eye has an ACD of about 3.15 mm, although the ACD typically shallows by about 0.01 mm per year. Further, the ACD is dependent on the accommodative state of the lens, i.e., whether the lens  240  is focusing on an object that is near or far. 
     The quality of the image that reaches the retina is related to the amount and type of optical aberrations that each patient&#39;s eye presents. The ocular surfaces that generally contribute to ocular aberrations are the anterior cornea and the lens. Although, all optical aberrations will affect the quality (e.g. blur) of the image produced on the eye, some aberrations do not necessarily affect the sharpness and the clarity of the object as seen by the patient due to neural compensation. Various embodiments described herein take into account the neural compensation that allows a patient to perceive objects sharply and clearly even in the presence of optical aberrations. 
     The term “near vision,” as used herein, refers to vision provided by at least a portion of the natural lens in a phakic eye or an intraocular lens in a pseudophakic eye, wherein objects relatively close to a patient are substantially in focus on the retina of the patient&#39;s eye. The term “near vision’ generally corresponds to the vision provided when objects are at a distance from the patient&#39;s eye of between about 25 cm to about 50 cm. The term “distant vision” or “far vision,” as used herein, refers to vision provided by at least a portion of the natural lens in a phakic eye or an intraocular lens in a pseudophakic eye, wherein objects relatively far from the patient are substantially in focus on the retina of the patient&#39;s eye. The term “distant vision” generally corresponds to the vision provided when objects are at a distance of at least about 2 m or greater. As used herein, the “dominant eye” is defined as the eye of the patient that predominates for distant vision, as defined above. The term “intermediate vision,” as used herein, refers to vision provided by at least a portion of the natural lens in a phakic eye or an intraocular lens in a pseudophakic eye, wherein objects at an intermediate distance from the patient are substantially in focus on the retina of the patient&#39;s eye. Intermediate vision generally corresponds to vision provided when objects are at a distance of about 2 m to about 50 cm from the patient&#39;s eye. 
     As used herein, an IOL refers to an optical component that is implanted into the eye of a patient. The IOL comprises an optic, or clear portion, for focusing light, and may also include one or more haptics that are attached to the optic and serve to center the optic in the eye between the pupil and the retina along an optical axis. In various implementations, the haptic can couple the optic to zonular fibers of the eye. The optic has an anterior surface and a posterior surface, each having a particular shape that contributes to the refractive properties of the lens. 
     In the embodiments disclosed herein aberrations and/or additional optical power are provided in a patient&#39;s dominant and non-dominant eye to increase depth of focus and to provide improved distant, near and intermediate vision. In some embodiments, rotationally and/or non-rotationally symmetric aberrations can be induced in the patient&#39;s dominant and/or non-dominant eye, such that the patient is able to have visual acuity for a wide range of distances. In some embodiments, an optical add power between about +0.5 Diopters and +2.0 Diopters can be provided in addition to inducing rotationally and/or non-rotationally symmetric aberrations. In various embodiments, the optical power and the aberration pattern provided in each eye is selected such that one eye (e.g. the dominant eye) has an extended depth of focus to provide visual acuity at far and intermediate distances and the other eye (e.g. the non-dominant eye) has an extended depth of focus to provide visual acuity at near and intermediate distances. Improved visual acuity at an intermediate distance is obtained due to binocular summation, which is a process by which the brain combines the information it receives from the dominant and the non-dominant eye. 
     In one aspect, extended depth of focus can be obtained by implanting a first IOL in the first eye and a second IOL in the second eye. The first IOL is selected to have a first optical power and a first optical aberration pattern (e.g. rotationally symmetric or non-rotationally symmetric) to provide visual acuity above a certain threshold for objects located at far to intermediate distances. The second IOL is selected to have a second optical power and a second optical aberration pattern (e.g. rotationally symmetric or non-rotationally symmetric) to provide visual acuity above a certain threshold for objects located at near to intermediate distances. The IOLs can be monofocal or multifocal. In various embodiments, the IOLs can include diffractive features, which may also be rotationally symmetric or asymmetric. The IOLs may also include refractive features, which may also be rotationally symmetric or asymmetric. 
     In another aspect, extended depth of focus can be obtained by shaping the cornea and/or the lens of the first eye to have a first optical power and a first optical aberration pattern (e.g. rotationally symmetric or non-rotationally symmetric) to provide visual acuity above a certain threshold for objects located at far to intermediate distances; and shaping the cornea and/or the lens of the second eye to have a second optical power and a second optical aberration pattern (e.g. rotationally symmetric or non-rotationally symmetric) to provide visual acuity above a certain threshold for objects located at near to intermediate distances. The shaping of the cornea or the natural lens can be performed by known methods, such as, for example using picosecond or femtosecond laser. Laser ablation procedures can remove a targeted amount stroma of a cornea to change a cornea&#39;s contour and adjust for aberrations. In known systems, a laser beam often comprises a series of discrete pulses of laser light energy, with a total shape and amount of tissue removed being determined by a shape, size, location, and/or number of laser energy pulses impinging on a cornea. In an alternative embodiment, the treatment may combine laser and cataract surgery. While during cataract surgery, IOLs implanted may be generating the desired configuration of added powers, with either refractive or diffractive concepts, the combination of rotationally symmetric and non-rotationally symmetric aberrations may be created in a posterior laser treatment that may be applied either in the corneal or in these implanted IOLs. In some embodiments, extended depth of focus can be provided by designing a first lens for use in a first eye, and a second lens for use in a second eye. The first and the second lens can be corneal implants, contact lenses or lenses for use in spectacles. The first and second lenses can be monofocal or multifocal. The first lens has an optical power and an optical aberration pattern that provides distant to intermediate vision. The second lens has an optical power and an optical aberration pattern that provides near to intermediate vision. 
     In various embodiments described herein rotationally symmetric aberrations (e.g. fourth and higher order spherical aberration terms) are induced in one eye while non-rotationally symmetric aberrations (e.g. astigmatism, coma and trefoil or combination thereof) are induced in the other eye to provide extended depth of focus. In various embodiments, the rotationally symmetric and non-rotationally symmetric aberrations can be superimposed over the naturally occurring aberrations in the eye. In some embodiments, the naturally occurring aberrations in the patient&#39;s eye may be corrected or scaled, as detailed in U.S. patent application Ser. No. 13,690,505 referenced above, in addition to inducing the rotationally symmetric or non-rotationally symmetric aberrations. 
     Rotationally symmetric aberrations, such as, for example including higher order spherical aberration terms can generate a uniform blur. In some instances, this uniform blur can translate into rotationally symmetric halos. On the other hand, non-rotationally symmetric aberrations can generate asymmetric halos which may be more tolerable as compared to rotationally symmetric halos. Providing rotationally symmetric aberrations in one eye and non-rotationally symmetric aberrations in the other eye can advantageously improve intermediate vision and extend depth of focus while reducing the impairments caused by rotationally symmetric halos. In some instances, combining spherical and/or non-rotationally symmetric with monovision can also improve stereopsis, which is related to depth perception. 
     The amount and type of rotationally symmetric and non-rotationally symmetric aberrations to be induced in each eye can be tested. A visual simulator was used to study whether the amount of aberrations that can be induced to produce a loss of one line in visual acuity is constant through the population. In order to do that, the monocular visual acuity of 5 subjects was measured under cyclopegic conditions when natural aberrations were corrected and those corresponding with an average pseudophakic eye were induced (0.15 μm RMS for a 5 mm pupil). Then, the amount of either spherical aberration or positive vertical coma that produced a loss of visual acuity of 0.1 Log MAR was determined when a physical pupil of 4 mm was imposed. The threshold value for negative SA was the smallest (−0.16±0.04 μm at 5 mm pupil induction), followed by positive SA (0.25±0.05 μm). The custom threshold for VC was consistently the highest (0.78±0.12 μm), ranging from 0.70 to 0.98 μms. Therefore, it is safe to consider a threshold of vertical coma and spherical aberration of about 0.8 μm and 0.2 μm, respectively. Those are the values that may be imposed as rotationally symmetric (spherical aberration) and asymmetric (vertical coma), while possibly correcting natural aberrations and inducing those corresponding to the average pseudophakic eye. This application is particularly advantageous for these eyes with a dense cataract which may increase the difficulty of determining potential customized thresholds. 
     In another embodiment, the vision simulator can be used to individually determine these monocular thresholds to both rotationally and non rotationally symmetric aberrations. As described previously, the visual acuity can be measured at best focus for a certain pupil size (e.g. 3 mm pupil size, 4 mm pupil size, or 5 mm pupil size). Then, the letter size may be increased until the target visual acuity is reached (ie. that corresponding to the measured VA plus n*0.1 log MAR, being n is a number between 0 and 3). Different values of rotationally symmetric aberrations (e.g. higher order spherical aberrations) or non-rotationally symmetric aberrations (e.g. astigmatism, coma or trefoil) are applied to the eye and the threshold value of rotationally symmetric aberrations and non-rotationally symmetric aberrations is determined as the maximum amount of aberration that allows for resolving that letter size, and therefore, provides with measured VA plus n*0.1 log MAR. Once the monocular thresholds are determined for each eye, the corresponding values are presented binocularly to the subject. In one implementation, the binocular threshold values are the value of the rotationally/non-rotationally symmetric aberration that provides the best through focus as well as comfort for the patient. In some instances, an optical add power (e.g. between about +0.5 Diopters and +3.0 Diopters) can be provided to the non-domination and/or the dominant eye. In an alternative embodiment, rotationally symmetric and asymmetric diffractive designs can also be induced, for the patient to compare between different options. 
     Another example method  2000  for determining the amount and type of rotationally symmetric and non-rotationally symmetric aberrations to be induced in each eye is illustrated in  FIG. 2A . The method includes: (i) determining with a binocular vision simulator a first maximum amount of rotationally symmetric or non-rotationally symmetric aberration which provides distant vision in a first eye, as shown in block  2005 ; (ii) determining with the binocular vision simulator a second maximum amount of rotationally symmetric or non-rotationally symmetric aberration which provides near vision in a second eye, as shown in block  2010 ; (iii) applying the first maximum amount of rotationally symmetric or non-rotationally symmetric aberration in the first eye, as shown in block  2015 ; and (iv) applying the second maximum amount of non-rotationally symmetric or rotationally symmetric aberration in the second eye, as shown in block  2020 . In various embodiments, a rotationally symmetric aberration pattern is applied to the second eye if a non-rotationally symmetric aberration pattern is applied in the first eye and vice-versa. 
     In one implementation of the method  2000  described above, the maximum amount of rotationally symmetric or non-rotationally symmetric aberration is that value selected from all possible values of rotationally symmetric or non-rotationally symmetric aberration which provides the highest extended depth of focus monocularly and the highest visual acuity at an intermediate distance binocularly. As previously discussed, the method  2000  can be implemented with IOLs, corneal implants, contact lenses, lenses for use in spectacles, etc. Alternately, the cornea or the lens of the patient can be shaped in accordance with the method  2000  such that rotationally/non-rotationally symmetric aberrations and an add power are induced in one eye to achieve distant vision with an extended depth of focus; and rotationally/non-rotationally symmetric aberrations and an add power are induced in the other eye to achieve near vision with an extended depth of focus. 
     An example of the procedure is shown at  FIG. 2B , in which spherical aberration represents rotationally symmetric aberration term and vertical coma the non-rotationally symmetric aberration term. In order to select the treatment, the thresholds may be customized, while using a visual simulator as previously described or can be taken from those measured in the average population. Once the thresholds have been determined monocularly, the binocular test starts. Different options are shown in  FIG. 2B . For a determined letter size, corresponding to a VA between 0 and 0.1 Log MAR, different viewing distances (0 D of defocus, corresponding to far, −1.5 D of defocus corresponding to intermediate and −2.5 D of defocus corresponding to far) may be shown to a subject for him/her to subjectively judge the option that is more suitable or comfortable. This test can be performed before cataract surgery, in order to make a customized selection of the lens to implant for the patient and only if the degree of cataract allows for visual simulation. The test can be also performed after the surgery, when the resulting aberration patterns or added powers may be induced as a laser treatment either in the cornea or the IOL itself.  FIG. 2B  lists potential binocular combinations with the first combinations utilizing a purely refractive (mixed monovision) platform. Symmetric diffractive platforms in combination with asymmetric diffractive platforms as seen, for example, in FIGS.  4 A 1 - 4 A 5  may also be used. Symmetric refractive platforms along with asymmetric refractive platforms, such as seen in U.S. patent application Ser. No. 13/309,314, entitled filed on Dec. 1, 2011, and incorporated herein by reference in its entirety, may also be used. 
     The IOLs or other ophthalmic devices discussed for use herein may be constructed of any commonly employed material or materials used for rigid optics, such as polymethylmethacrylate (PMMA), or of any commonly used materials for resiliently deformable or foldable optics, such as silicone polymeric materials, acrylic polymeric materials, hydrogel-forming polymeric materials, such as polyhydroxyethylmethacrylate, polyphosphazenes, polyurethanes, and mixtures thereof and the like. The material used preferably forms an optically clear optic and exhibits biocompatibility in the environment of the eye. Additionally, foldable/deformable materials are particularly advantageous for formation of implantable ones of ophthalmic lenses for use in the present invention, in part because lenses made from such deformable materials may be rolled, folded or otherwise deformed and inserted into the eye through a small incision. 
     In addition to providing visual acuity at near, intermediate and far distances, the ophthalmic solutions (e.g. IOLs, contact lenses, corneal implants, etc.) used herein can correct for other conditions of the eye. For example, the ophthalmic solution can be a toric lens for correcting astigmatism and include rotationally/non-rotationally symmetric aberrations to provide enhanced visual acuity. As another example, the ophthalmic solution can be an aspheric lens including rotationally/non-rotationally symmetric aberrations to provide enhanced visual acuity. As yet another example, the ophthalmic solution can be a combination of refractive and diffractive features that are rotationally/non-rotationally symmetric to provide enhanced visual acuity. 
     The methods described herein can be performed by using instruments that are known to a person having ordinary skill in the art. An instrument to implement the methods described herein can comprise a set of apparatuses, including a set of apparatuses from different manufacturers that are configured to perform the necessary measurements and calculations. Any instrument comprising all needed measurements (ocular and corneal wavefront aberration measurements) as well as the needed calculations to implement the methods described herein, including but not limited to the method  2000  can be considered as an inventive embodiment.  FIG. 3  is a block diagram illustrating an embodiment of a clinical system  3000  that can be used to implement the methods described herein, including but not limited to the method  2000 . The system  3000  includes one or more apparatuses capable of performing the calculations, assessments and comparisons set forth in determining the rotationally/non-rotationally symmetric aberration patterns and the add power that provide enhanced visual acuity at near, intermediate and far distances. The system  3000  may include a biometric reader  3001  (e.g. a binocular vision simulator), a processor  3002 , and a computer readable memory or medium  3004  coupled to the processor  3002 . The computer readable memory  3004  includes therein an array of ordered values  3008  and sequences of instructions  3010  which, when executed by the processor  3002 , cause the processor  3002  to select the rotationally/non-rotationally symmetric aberration pattern that provides distant vision with an extended depth of focus in one eye and near vision with an extended depth of focus in the other eye such that an enhanced visual acuity at an intermediate distance is obtained by binocular summation. 
     The array of ordered values  3008  can include one or more desired refractive outcomes, data obtained from measurements of the patient&#39;s eye, data related to one or more types of available ophthalmic solutions, a set of all possible rotationally/non-rotationally symmetric aberration patterns, parameters of refractive and diffractive features, etc. In some embodiments, the sequence of instructions  3010  can include algorithms to perform calculations, customization, simulation, comparison, etc. 
     The processor  3002  may be embodied in a general purpose desktop, laptop, tablet or mobile computer, and/or may comprise hardware and/or software associated with inputs  3001 . In certain embodiments, the system  3000  may be configured to be electronically coupled to another device, such as one or more instruments for obtaining measurements of an eye or a plurality of eyes. Alternatively, the system  3000  may be adapted to be electronically and/or wirelessly coupled to one or more other devices. 
     The system illustrated in  FIG. 3  can be used for selecting the rotationally/non-rotationally symmetric optical aberration patterns in blocks  2005  and  2010  of the method  2000 . For example, the clinical measurements provided by the reader  3001 , can be used to determine which rotationally/non-rotationally symmetric optical treatments stored in the processor  3002  provides distant vision with an extended depth of focus in one eye and near vision with an extended depth of focus in the other eye such that an enhanced visual acuity at an intermediate distance is obtained by binocular summation. 
     As discussed above, the methods described herein can be implemented in lenses (e.g. IOLs, contact lenses, lenses for use with spectacles, etc.). For example, in some embodiments, the lenses can be monofocal lenses that provide distant or near vision that include rotationally/non-rotationally symmetric aberration pattern for providing visual acuity for object located at intermediate distance. As another example, in some embodiments, the lenses can be multifocal lenses providing distant and near vision and further including rotationally/non-rotationally symmetric aberration pattern for providing visual acuity for object located at intermediate distance. As yet another example, in some embodiments, the lenses can have refractive or diffractive features that are symmetric or asymmetric such that improved visual acuity at near, intermediate and far distances is obtained. Some examples of lenses including rotationally asymmetric features that provide improved visual acuity at near, intermediate and far distances are discussed below with reference to FIGS.  4 A 1 - 4 A 5 . As discussed above, rotationally symmetric aberrations can include higher order (e.g. 4 th  and 6 th  order) spherical aberrations. As discussed above, non-rotationally symmetric aberrations can include astigmatism, coma or trefoil. 
     By way of example, FIGS.  4 A 1 - 4 A 5  shows various embodiments of lenses including rotationally asymmetric diffractive features. The lenses illustrated in FIGS.  4 A 1 - 4 A 5  include a plurality of partially annular structures. The partially annular structures can be distributed around a central optical zone disposed about an optical axis. In some embodiments, the optical zone between two consecutive partially annular structures can have an optical power that is equal to the optical power of the central zone. In some other embodiments, the optical zone between two consecutive partially annular structures can have an optical power that is different from the optical power of the central zone. Each of the partially annular structure can include microstructures that are diffractive or refractive. Each of the partially annular structure can have a vertical and horizontal profile that determines the overall optical power of the lens and the distribution of light between the various optical zones. 
     In FIG.  4 A 1 , region A 1  includes a plurality of semi-annular structures that cover about 50% of the surface area of the ophthalmic lens. The upper part of the lens has 50% light distribution between 1 D and 2D add power, while the rest has an asymmetric light distribution between the same add powers. In various embodiments, the portion of the ophthalmic lens below the region A 1  can be devoid of microstructures or include microstructures similar to the microstructures in the region A 1 , such that the ophthalmic lens illustrated in FIG.  4 A 1  is rotationally symmetric. In an alternative embodiment, the lower part may be composed by a different diffractive designs which provides different add powers and light distributions. 
     FIG.  4 A 2  illustrates an ophthalmic lens including a first region A 2  having partially annular structures with an add power of 1 D, being essentially monofocal, and a second region B 2  having partially annular structures with an add power of 2D, also monofocal. The regions A 2  and B 2  can each occupy about 25% of the surface area of the ophthalmic lens, while the remaining approximately 50% of the lens has a 0 D add power and its basically refractive monofocal. 
     FIG.  4 A 3  illustrates an ophthalmic lens including a first region A 3  having partially annular structures with an add power of 2D, being essentially monofocal, a second region B 3  having partially annular structures with an add power of 3D, being essentially monofocal, and a third region C 3  having partially annular structures with an add power of 1 D, being essentially monofocal. The regions A 3  and B 3  can each occupy about 25% of the surface area of the ophthalmic lens and the region C 3  can occupy about 50% of the surface area of the ophthalmic lens. The area occupied by every different sector can be modified as shown in FIG.  4 A 4 , where each region subtends the same area. In an alternative embodiment, at FIG.  4 A 5 , the area occupied by the region with an add power of 1 D is greater than for the rest. 
     Although the invention has been described and pictured in an exemplary form with a certain degree of particularity, it should be understood that the present disclosure of the exemplary form has been made by way of example, and that numerous changes in the details of construction and combination and arrangement of parts and steps may be made without departing from the spirit and scope of the invention as set forth in the claims hereinafter.