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  • 专利说明
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    • 专利摘要:
    MULTIFOCAL CORRECTION PROVIDING IMPROVED QUALITY OF VISION. The present invention relates to strategies and devices for improving the visual experience while expanding the depth of field of presbyopic and pseudophakic patients. The invention describes strategies and devices for providing improved image quality and improved visual quality of patients using simultaneous or monovision bifocal, trifocal and multifocal corrections. The invention describes strategies and devices to reduce the visibility of the unfocused part of the retina image generated by simultaneous vision and monovision bifocal and multifocal ophthalmic corrections. The invention describes strategies and devices that use spherical aberration control or other similar asphericalities to reduce the visibility of unfocused ghost images. The invention describes strategies and devices that ensure that the lack of negative focus is always linked with negative spherical aberration (or similar asphericality) and that the lack of positive focus is always linked with positive SA (or similar asphericity) as a way to reduce the visibility of unfocused ghost images.
    公开号:BR112012004574B1
    申请号:R112012004574-1
    申请日:2010-08-30
    公开日:2020-12-01
    发明作者:Arthur Bradley；Pete S. Kollbaum；Larry N. Thibos
    申请人:Arthur Bradley；Pete S. Kollbaum；Larry N. Thibos；
    IPC主号:
    专利说明:

    Cross-reference with related orders
    [0001] This patent claims the benefits of U.S. Provisional Patent Application No. 61 / 238,774, filed on September 1, 2009, hereby incorporated by reference in its entirety. TECHNICAL FIELD
    [0002] The present invention relates, in general, to the field of ophthalmic and surgical visual visual corrections, and more particularly it provides methods, devices and systems for treating presbyopia and other visual conditions, and for developing prescriptions for the treatment of presbyopia and other visual and / or similar conditions. BACKGROUND TECHNIQUE
    [0003] As the human eye ages, its ability to change its range to generate the image of objects at different distances weakens. This decline is called "presbyopia" and it affects all humans. A similar inability to adjust the optical range of the eye lens occurs in patients who have their natural lens replaced with an artificial lens (for example, after cataract surgery). Thus the challenges of seeing in multiple distances faced by presbyopes are shared by "pseudophakes". Currently, there is no cure for presbyopia and there is no perfect optical treatment that will restore that total range of vision that those skilled in the art and practice call "accommodation". Substitute optical devices and strategies have been developed that are designed to increase the range of distances that can be seen (depth of field). Such devices produce what is known as "pseudoaccommodation". That is, they increase the depth of the field without changing the range of the eye itself. All of these devices and strategies are inferior to normal accommodation and all require adjustments by the presbyopic patient. There is an obvious need to develop improved devices and strategies to improve the quality of vision for presbyopes.
    [0004] There are several well-established strategies to increase the field of vision of presbyopes. The simplest involves implementing some form of small pupil ("black dot"), which increases the depth of the field without changing the optical characteristics of basic optics. Such a strategy fails in low light levels and can severely limit the size of the visual field. More typical are strategies that actively implement an optical lens or device that focuses light on the retina of targets located at different distances. Such a strategy uses standard monofocal lenses of different ranges in both eyes, called "monovision". Most strategies, however, use lenses that contain more than one scope, bifocal, trifocal or multifocal lenses.
    [0005] When implemented as a spectacle lens, the different ranges present in bifocal, trifocal or multifocal are distributed through the spectacle lens, and by a combination of head and eye movements, the patient can select the region of the spectacle lens. glasses that provide an image focused on the retina (and thus high quality vision) for targets that are at different distances. This approach of selecting different ranges by eye and head movements will not work for soft contact lenses (CLs) or intraocular lenses (IOLs) or correction created inside or over the cornea through refractive surgery because the corneal lenses or corrections move with the eye. Therefore, regardless of the direction of the gaze, the patient is always looking through the same lens.
    [0006] Bifocal, trifocal and multifocal optical corrections for prespieces that move with the eye (corrections inside or over the cornea (overlapping inlays or grafts of the cornea, other refractive surgeries), CLs and IOLs) therefore need contain multiple optical ranges within the same or adjacent regions of the optical device or strategy that both contribute to the retinal image. That is, unlike the correction of the presbyopic spectacle lens in which the patient sequentially selects the location of the physical lens with the most appropriate optical range, patients with presbyopic corrections in CL, IOL or refractive surgery simultaneously use different optical ranges, and so these devices and strategies are referred to as "simultaneous vision" lenses or corrections.
    [0007] Herein lies the central problem faced by CL, IOL and refractive surgery corrections that aim to provide greater depth of field for presbyopic patients. In addition to the light that is well focused on the retina by one of the optical ranges, the out-of-focus light that is being reproduced by the other range (s) in simultaneous vision correction is also present. The quality of the retinal image (and therefore the patient's vision) is therefore determined by this combination of focused and unfocused light. Most of the ophthalmic industry's efforts to provide improved optical corrections for the presbiope centered on manipulating and increasing the focused portion of that light. The invention described in that patent is designed to improve the vision of presbyopes by reducing the impact of the unfocused portion of the light.
    [0008] The central optical characteristic of all simultaneous vision corrections for presbyopia is the increased depth of the field provided. The primary determinant of the greater depth of field is the range of optical ranges within the optical device or refractive surgery. Numerous presbyopic corrections for presbyopes have been marketed and still others have been invented that distribute the range within the lens (or refractive surgery) using a wide range of strategies. Quite simply, such optical corrections can be designed to have 2 ranges (bifocal), three ranges (trifocal) or multiple ranges (multifocal). One strategy for creating a multifocal lens is to gradually change the lens range from the center towards the edge. This can be accomplished by introducing large amounts of spherical aberration (SA) into the lens, which can make the lens periphery less powerful than the center of the lens (negative SA, see US patent # 7,261,412 B2, 8/28/2007 and US patent application # 0051876 A1, 2009). This lens would have maximum range at its center and would thus be called a "center-near" project in which greater range is needed to focus on nearby targets. Alternatively, a similar strategy generates a "center-distance" design by adding positive SA on the lens (see US patent # 5,089,024, 2/18/1992). With both of these strategies, SA is manipulated in the lens design to increase the range of ranges present and thus increase the depth of field.
    [0009] There is a different general strategy that uses discrete optical ranges, for example, a bifocal with two ranges or a trifocal with three ranges, instead of a gradual change in range through the lens. In such projects, the optical quality of the retina image produced when one of the optics is in focus can be improved by including a complete correction within each zone (for example, patent # US 5,220,359.15 / 6/1993 and World Patent # WO 2005/019906 A1) or partial (for example, US patent 7,118,214, 10/10/2006) for the spherical aberration (SA) present within the human eye. Because the human eye typically has positive SA, these lenses correct this by introducing negative SA. However, there may be some eyes with negative SA, so these lenses would introduce positive SA to correct it. In many such inventions, SA is first measured using some form of aberrometer.
    [00010] When a controlled level of SA is introduced into a lens, that lens is often described as being "aspheric". In a third general design strategy for presbyopic corrections of simultaneous vision, SA and / or other radially symmetrical asphericalities are used to control the transition between zones of different ranges. That is, instead of having a spatially discrete transition, the range is gradually changed through a transition region of the lens. This gradual change in reach is sometimes referred to as asphericity or AS. Several inventions use such aspheriologies (for example, patent # US 6,457,826 B1, World Patent WO 2007/015001 A1, World Patent # WO 0221194 A2).
    [00011] Two other strategies have been implemented using SA or other radially symmetric asphericalities as part of a presbyopic or "pseudophakic" correction. First, contrary to designs that use SA correction within different optical zones to improve the quality of the focused image, a person can introduce SA within different zones in order to increase the depth of field (for example, patent # US 0176572 A1, 2006). Also, greater depth of field can be introduced in what is designed to be a monofocal correction by adding small asphericalities in the optics (patent # US 0230299 A1, 2004).
    [00012] All of the above projects using SA or similar asphericalities are designed to improve the quality of the focused image within a simultaneous vision correction or to increase the depth of field in the same type of correction. An invention sought to use the SA control on a simultaneous vision lens to reduce the visibility of the unfocused image (patent application WO 2010/014767). This strategy was simple: introducing a specific SA in bifocal correction that would correct the SA of the eye, and thus maximize the quality of the focused portion of the light. When the focused portion of the light was really well focused, this invention claimed (without supporting evidence) that the visibility of the unfocused image (often referred to as a "ghost" image) would be reduced. Of course, numerous prior patents were granted that already used the correction of SA within the bifocal (see above). We have invented a new strategy to use controlled SA (or similar asphericity) to minimize the visibility of the out-of-focus "ghost" image generated by bifocal, trifocal or multifocal presbyopic correction (see detailed description below). DESCRIPTION OF THE INVENTION
    [00013] Generally described, in one aspect, the present invention provides lenses, design strategies, devices, methods and systems to eliminate or minimize the visibility of ghost images present in presbyopic corrections through specific control of the aberration signal zone spherical or other asphericity. The prior technique corrected spherical aberration or indiscriminately induced spherical aberration without considering the relationship between the lens range and the SA signal (see above). Although such approaches may be successful in varying ways in increasing the depth of field of the presbyopic or "pseudophakic" eye, they produce highly visible and visually unacceptable ghostly unfocused images. Such ghost images reduce the overall success of these presbyopic corrections. The current technique is distinct from any previous technique in that it specifically aims to unite positive AS with the regions with the most positive (or least negative range) of the bifocal and introduce the negative AS into the individual optical zone with the least positive range ( or the most negative range), in order to maximize the depth of the field while minimizing the visibility of the phantom image. In other words, our invention aims to introduce positive SA in the near optics and negative SA in the distant optics of a bifocal, trifocal or multifocal CL, IOL or refractive surgery. It specifically requires that distance correction and close correction contain opposite opposite SA: negative distance correction and positive close correction. BRIEF DESCRIPTION OF THE DRAWINGS
    [00014] Figures 1a-c are a series of light ray diagrams representing the focusing of the light rays of a distant object through a lens with spherical zero (a), positive (b) and negative (c) aberration (C40) = 0,> 0 or <0, respectively). In each case, the vertical dotted line represents the best plane of the focus (minimum RMS, least confusing circle). The vertical dashed lines to the left represent a plane closer to the lens that requires more focusing range than the lens has and thus generates a lack of negative focus, or negative C20. The vertical dashed lines to the right represent a plane farther from the lens that requires less focusing range than the lens has and thus generates a lack of positive focus, or positive C20.
    [00015] Figures 2 a-c are a series of light ray diagrams representing the light path through a lens containing no spherical (a), positive (b) and negative (c) aberrations. In (b) the object is distant, while in (c) it is close. Thus, in 2 (b), the C40 is positive and, in the plane of the retina, then it is the lack of focus. In 2 (c), the C40 is negative, and in the plane of the retina, then it is the lack of focus.
    [00016] Figure 3 illustrates the image of the simulated retina of a high contrast letter D. The images are calculated for a range of levels of lack of focus, lack of positive focus on the right and lack of negative focus on the left. Three types of SA are modeled: SA zero, SA Deq +0.21 and SA Deq +0.50.
    [00017] Figure 4 illustrates the image of the simulated retina of an eye corrected by bifocal generated with the same lack of signal focus and spherical aberration.
    [00018] Figure 5 illustrates the image of the simulated retina of the eye corrected by bifocal generated with lack of focus of opposite sign and spherical aberration. MODES FOR CARRYING OUT THE INVENTION.
    [00019] In order to describe clearly, concisely and exactly the exemplary modalities of the invention, the manner and process of its manufacture and use, and to enable its practice, manufacture and use, reference will now be made to the exemplary modalities illustrated in the figures and specific language will be used to describe it. However, it will be understood that no limitation on the scope of the invention is created in this way and that the invention includes and protects such changes and modifications to the illustrated modalities, and such additional applications of the modalities illustrated and described here as would occur to one skilled in the art which invention refers to.
    [00020] Some exemplary modalities include lenses, design strategies, devices, systems and methods for simultaneous vision contact lenses, IOLs, corneal inlays, corneal overlays, ophthalmic surgical prescriptions, such as LASIK corrections and other corrective prescriptions and lenses and so on, which use distance and close correction in combination including all forms of monovision or variations of monovision, sometimes called a modified monovision. It will be understood that reference to simultaneous vision lenses includes the precedent and other corrective prescriptions. Simultaneous vision lenses include bifocal, trifocal, other multifocal lenses and the use of monofocal lenses used in monovision prescriptions. Certain exemplary modalities eliminate or minimize errors in these and other simultaneous vision lenses.
    [00021] Exemplary modalities include the aberration control to control the visibility of the unfocused portion of the image present in the simultaneous vision lenses and monovision corrections. The unfocused portion of the image is inevitable in exemplary simultaneous and monovision lens strategies and the visibility of light without focus on the image impairs the optical quality and visual experience provided by such lens strategies. The unfocused portion of the visible light in the image is often cited by patients and doctors as a ghost image or ghost formation. The modalities described here include lenses, design strategies, devices, methods and systems to eliminate or minimize the visibility of such ghosts. Optical principles related to such ghosts and the reduction or elimination of such ghosts will now be described together with figures 1a, 1b, 1c, 2a, 2b and 2c.
    [00022] Figure 1a above represents the focusing of the light rays of a distant object through a lens with positive range and zero spherical aberration (ie, Zernike coefficient C40 = 0). In figure 1a, the rays are evenly spaced in planes of lack of hyperopic focus (C20 <0) and lack of myopic focus (C20> 0), which means that dark circles formed in these planes are uniformly illuminated discs of light. Figure 1b above represents the effect of positive spherical aberration, for which the marginal rays are refracted more and the central rays are refracted less than in the upper diagram. The result is a compression of the light in a pair of small, high-intensity dark circles in a plane of the hyperopic lack of focus, but an expansion of the light in a larger, more uniform, low-intensity dark circle with indistinct edges in the plane of the lack of focus myopic. Figure 1c above represents the effect of negative spherical aberration, for which the marginal rays are refracted less and the central rays are refracted more than in the upper diagram. The result is a compression of light in a pair of small dark circles of high intensity in a plane of lack of myopic focus, but an expansion of light in a larger, uniform, low intensity circle in the plane of lack of hyperopic focus. The advantage of a larger uniformly obscure circle of lesser intensity is a greater attenuation of the contrast of the unwanted unfocused image produced by a bifocal contact lens. The disadvantage of a pair of small, high-intensity dark circles is diplopia or annular halo, for which disturbing ghost images or high-contrast halos are formed on the retina.
    [00023] Figures 2a, 2b and 2c above illustrate the optical mechanism that is the basis for exemplary modalities disclosed here. Bifocal contact lenses form two retinal images of each object. One of these images will be more out of focus than the other and the intention of the present invention is to reduce the evidence of the image with a greater lack of focus by reducing its contrast and overall visibility. Ray diagrams represent only the unfocused portion of the image from a point source (for example, rays for the near-addition optics with greater range when objects are far away and rays for the distance optics with less range when objects are close) . Figure 2a above represents an unfocused image of a distant object formed by this part of the bifocal, implementing the prescription closely for the case of zero spherical aberration. The eye has super range in this case, so the lack of focus coefficient C20> 0. The dark circle on the retina is illuminated evenly. The diagram in figure 2b above represents the same conditions, but for a lens with positive spherical aberration (C40> 0). The result is an enlarged obscure circle, of less intensity, illuminated more evenly that mischaracterizes the image obscured by the reduction of its contrast. Figure 2c above represents the formation of the image of light from a nearby target by the distance component of the prescription. Since the lack of focus coefficient C20 is negative in this example, the sign of the spherical aberration coefficient C40 needs to be negative in order to obtain the desired result from a large, dimly illuminated, low-intensity circle. Note that the reason is the same regardless of whether the central part of the bifocal contact lens provides the distance prescription and the peripheral part of the lens provides the prescription at close range or vice versa. The lack of positive focus must be combined with positive SA and vice versa.
    [00024] Certain exemplary modalities that apply to all bifocal, multifocal and monovision corrections can be easily understood using an example of a patient using a simultaneous bifocal vision lens. Distance correction within such a lens focuses on a distant object, but will produce a lack of focus when viewing a nearby object. Conversely, the range of the addition close to the lens will focus on a nearby object, but will produce an unfocused image when viewing a distant target. Certain exemplary modalities revealed here eliminate or minimize the visibility of these unfocused images (ghosts).
    [00025] Patients wearing a lens or bifocal lenses may experience positive or negative spherical aberration ("SA") (patients often experience positive SA, but some eyes and some patients with long-range negative lenses may have negative SA). Certain exemplary modalities ensure that the unfocused image of a nearby object (created by the distance range of the lens), or the unfocused image of a distant target (created by the addition range of the lens) will occur together with the same signal as that of the SA . Certain modalities provide independent control of spherical aberration in the optics of the distance and at close range to minimize the unwanted effects of unfocused images from both the distant and the next target. Some modalities include simultaneous vision lenses that minimize the visibility of out-of-focus ghosts. These and other modalities have been shown to offer improved vision correction that patients experience.
    [00026] Certain exemplary modalities include bifocal or monovision lenses or refractive surgeries that use the opposite signal SA from a distance and near optics. Specifically, the close addition will include the positive SA, while the distance optics will include the negative SA, because the lack of focus caused by the close addition occurs due to the lack of positive focus (excessive range) when looking at the distant target. Conversely, distance correction will include negative SA because the lack of focus caused by distance correction will be negative (insufficient range) when the target is close. This is contrary to the current technique that produces lenses and optics that have positive or negative SA for the entire correction, or asfericities in the transition zones, certain exemplary modalities guarantee the opposite signal SA for the near and distance correction.
    [00027] Some exemplary lens designs use knowledge of the patient's spherical aberration to create bifocal / multifocal contact lenses, intraocular lens (IOL) and other lens designs in which the visibility of the out-of-focus ghost image is minimized. The image quality in an eye corrected with a simultaneous vision bifocal can be modeled by the quality of the focused image and the characteristics of the unfocused image that are simultaneously present. Eye SA can be included in the design or implementation of that opposite-sign SA invention.
    [00028] Some modalities improve simultaneous vision by improving the unfocused image as a function of the levels and types of HOAs. In figure 3, it can be seen that eyes with positive AS, the image of the retina of an eye with a lack of positive focus (over-range) is very different from the image generated with a lack of negative focus (under-range). The former has little contrast and dark edges, and thus poor visibility, while the latter may have high contrast and may be spatially distorted due to changes in phase in the image. An exemplary design goal for a simultaneous view bifocal is to make the unfocused image have low visibility. Thus, for an eye with typical positive SA levels, the new lens design would ensure that the optical zone at close range (the unfocused because of an excess in range when viewing targets from a distance) would have positive SA when in the eye. Also, when the distance portion of the lens is unfocused (due to insufficient range when viewing a nearby target) it will have negative SA when in the eye. The SA level in the eye + lens combination is the sum of that contributed by the eye and the lens.
    [00029] Using computational optical tools, the inventors generated simulated retinal images of the eyes with exemplary bifocal optics. A comparison of the two examples shown in figure 4 and figure 5 shows a difference in the quality of the bifocal image when the sign of the lack of focus and the SA are the same (figure 4) and when they are opposite (figure 5).
    [00030] Figure 4 illustrates the simulated retina image of the bifocal eye generated with the lack of focus of the same signal and spherical aberration. Unfocused ghosts have been minimized and are almost invisible. Figure 5 illustrates the simulated retinal image of the bifocal eye generated with the lack of opposite signal focus and spherical aberration. Note that unfocused ghosts are clearly visible. The visibility of the ghosts shown in figure 5 will be further increased when the CL, IOL or refractive surgery or implant is decentralized in relation to the pupil.
    [00031] Certain exemplary modalities for the control of the SA in the optical zones of distance and near will guarantee that the lack of focus and the SA (or another similar radially symmetrical asphericity) always have the same signal and thus the ghost will be invisible (or at least significantly less visible) than would be obtained with the lack of focus and opposite sign SA. This is accomplished by introducing sufficient negative SA in the distance correction and ensuring that there is sufficient positive SA in the close correction. The respective negative and positive SA in distance and close correction is obtained when in the eye and thus can incorporate the inherent SA of the eye in the design as needed. Levels resulting from positive and negative SA can vary from small (for example, 0.1 microns) to large (for example, 0.4 microns) through a 6 mm diameter pupil, but can be graduated to any size pupil and adjusted in level to achieve the required visibility of ghost images. In this document, we use the terms SA to describe radially symmetrical changes in optical range through the lens or pupil. Examples of SA could be Seidel SA, Zernike SA or any other gradual change in range as a function of the distance from the lens or center of the pupil. Such changes can be produced by the modeling of the optical surface, manipulation of the refractive index and manipulation of the zone separations and profiles in the diffractive bifocals. In one embodiment, the sign of this SA is defined as positive if the range becomes more positive with the distance from the center and negative if the range becomes more negative with the distance from the center.
    [00032] Certain exemplary modalities include a multifocal lens design including reduced or minimized ghosting. Some modalities include a contact lens. Some modalities include an IOL. Some modalities include an ophthalmic surgical prescription rather than a separate corrective lens. Some modalities include a refractive surgical correction, such as a LASIK correction. Some modalities include monovision corrections and variations of this form of prescription, often referred to as modified monovision.
    [00033] Certain exemplary modalities include a method of determining a multifocal prescription including reduced or minimized ghosting. Some modalities include a spectacle lens. Some modalities include a contact lens. Some modalities include an IOL. Some modalities include an ophthalmic surgical prescription rather than a separate corrective lens. Some modalities include a LASIK prescription.
    [00034] The modalities of the invention illustrated and described in detail in the figures and preceding description are illustrative and not limiting or restrictive. Some
    [00035] n the currently preferred modalities have been shown and described and all changes and modifications that fall within the scope of the invention must be protected. It should be understood that several characteristics and aspects of the modalities described above may not be necessary and modalities that lack them are also protected. When reading the claims, it is planned that when words such as "one", "one", "at least one" or "at least a portion" are used, there is no intention to limit the claim to only one item unless specifically otherwise stated in the claim. When the language "at least a portion" and / or "a portion" is used, the item may include a portion and / or the entire item unless specifically stated to the contrary.
    [00036] This invention is distinct from all previous inventions that increase SA or decrease SA by introducing positive or negative SA through the entire pupil or an individual optical zone. It specifically requires that distance correction and close correction contain an opposite sign SA: negative SA in distance correction and positive SA in close correction.
    权利要求:
    Claims (19)
    [0001]
    1. Corrective optical lens adapted to move with and change the range of a user's eye, characterized by the fact that it comprises: a first optical zone that extends radially extending from a center of the corrective optical lens having a first range that, when combined with the user's eye range, is adapted to result in a first liquid range that increases as the radius of the first radially extending optical zone increases; and a second optical distance zone that extends radially having a second range that, when combined with the user's eye range, is adapted to result in a second liquid range that decreases as the radius of the second optical zone that extends radially increases; wherein the first net range is greater than the second net range; and where the sizes and ranges of the first and second radially extending optical zones are adapted to limit the visibility of blurred portions of an image simultaneously viewed through the radically extending first optical zone and the second optical distance zone that extends radially.
    [0002]
    2. Corrective optical lens, according to claim 1, characterized by the fact that the first radially extending optical zone is separated in a radial direction from the second radially extending optical zone.
    [0003]
    3. Corrective optical lens, according to claim 1, characterized by the fact that the first radially extending optical zone is separated in an axial direction from the second radially extending optical zone.
    [0004]
    4. Corrective optical lens, according to claim 1, characterized by the fact that the first range is achieved at least partially with at least one of the refractive or diffractive optics.
    [0005]
    5. Corrective optical lens, according to claim 1, characterized by the fact that the second range is achieved at least partially with at least one of the refractive or diffractive optics.
    [0006]
    6. Corrective optical lens according to claim 1, characterized by the fact that the corrective optical lens comprises a bifocal lens.
    [0007]
    7. Corrective optical lens according to claim 1, characterized by the fact that the corrective optical lens comprises a trifocal lens.
    [0008]
    8. Corrective optical lens according to claim 1, characterized by the fact that the corrective optical lens comprises a multifocal lens.
    [0009]
    9. Corrective optical lens, according to claim 1, characterized by the fact that the corrective optical lens comprises a contact lens (CL).
    [0010]
    10. Corrective optical lens, according to claim 1, characterized by the fact that the corrective optical lens comprises an intraocular lens (IOL).
    [0011]
    11. Corrective optical lens, according to claim 1, characterized by the fact that the corrective optical lens comprises a cornea.
    [0012]
    12. Corrective optical lens, according to claim 1, characterized by the fact that the corrective optical lens comprises an inlay on the cornea.
    [0013]
    13. Corrective optical lens, according to claim 1, characterized by the fact that the first radially extending optical zone extends radially outward to a first diameter and the second radially extending optical zone extends radially outward to from a second diameter that is at least as large as the first diameter.
    [0014]
    14. Corrective optical lens according to claim 1, characterized by the fact that the second radially extending optical zone extends radially outward to a first diameter and the first radially extending optical zone extends radially outward to from a second diameter that is at least as large as the first diameter.
    [0015]
    15. Corrective optical lens, according to claim 1, characterized by the fact that at least one of the first radially extending optical zone or the second radially extending optical zone defines an annular shape.
    [0016]
    16. Corrective optical lens, according to claim 1, characterized by the fact that the amount of the change in range through the first radially extending optical zone or through the second radially extending optical zone can be defined by a front of wave proportional to a wavefront having an RMS magnitude of 0.1 to 0.4 microns for a 6 mm diameter pupil.
    [0017]
    17.Pair of corrective optical lenses adapted to move with and change the range of a user's first and second eyes, characterized by the fact that it comprises: a first corrective optical lens up close for use with the user's first eye, the first corrective optical lens including a first radially extending optical zone that extends from a center of the corrective optical lens and having a first range that, when combined with the user's first eye range, is adapted to result in a first range liquid that increases as the radius of the first radially extending optical zone increases; and a second distance corrective optical lens for use with the second eye of the user, the second optical corrective lens including a second optical zone that extends radially having a second range that, when combined with the range of the second eye of the user, is adapted to result in a second net range that decreases as the radius of the second radially extending optical zone increases, where the first net range is larger than the second net range and the sizes and ranges of the first and second zones Radially extending optics are adapted to limit the visibility of unfocused portions of an image simultaneously viewed through the first radially extending optical zone and the second radially extending optical zone.
    [0018]
    18. Method of adapting an optical lens to have more than one range, characterized by the fact that it comprises the steps of: forming a first optical zone from close up that extends radially that extends from a center of the corrective optical lens and having a first range that, when combined with a user's eye range, is adapted to result in a first liquid range that increases as the radius of the first radially extending optical zone increases; form a second optical distance zone that extends radially from the lens to have a second range that, when combined with a user's eye range, is adapted to result in a second liquid range that decreases as the radius of the second zone radially extending optics increases; adapting the first optical zone that extends radially and the second optical zone that extends radially to make the first net range greater than the second net range; and adapting the sizes and ranges of the first and second radially extending optical zones to limit the visibility of blurred portions of an image simultaneously viewed through the first radially extending optical zone and the second extending optical zone radially.
    [0019]
    19. Method according to claim 18, characterized by the fact that the step of adapting the sizes and ranges of the first and second optical zones that extend radially to attenuate the visibility of the unfocused light to the user still comprises at least at least one of the following steps: model an optical profile of the lens; manipulate a separation zone on the lens; manipulate a refractive index of the lens.
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    法律状态:
    2016-09-20| B08F| Application fees: application dismissed [chapter 8.6 patent gazette]|Free format text: REFERENTE AS 3A E 4A ANUIDADES. |
    2016-11-08| B08G| Application fees: restoration [chapter 8.7 patent gazette]|
    2019-01-08| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2019-07-09| B06T| Formal requirements before examination [chapter 6.20 patent gazette]|
    2020-01-28| B07A| Technical examination (opinion): publication of technical examination (opinion) [chapter 7.1 patent gazette]|
    2020-08-18| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2020-12-01| B16A| Patent or certificate of addition of invention granted|Free format text: PRAZO DE VALIDADE: 10 (DEZ) ANOS CONTADOS A PARTIR DE 01/12/2020, OBSERVADAS AS CONDICOES LEGAIS. |
    2021-07-27| B16C| Correction of notification of the grant|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 30/08/2010, OBSERVADAS AS CONDICOES LEGAIS. PATENTE CONCEDIDA CONFORME ADI 5.529/DF, QUE DETERMINA A ALTERACAO DO PRAZO DE CONCESSAO |
    优先权:
    申请号 | 申请日 | 专利标题
    US23877409P| true| 2009-09-01|2009-09-01|
    US61/238,774|2009-09-01|
    PCT/US2010/047138|WO2011028659A1|2009-09-01|2010-08-30|Multifocal correction providing improved quality of vision|
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