KR20090012370A - Static progressive surface area in optical communication with dynamic optics - Google Patents

Abstract

An ophthalmic lens is presented in which the lens includes a progressive addition region and a dynamic optic. The dynamic optic and the progressive addition region are in optical communication. The progressive addition region has an add power which Is less than a user's neat viewing distance add power. The dynamic optic, when activated, provides the additional needed optical power for the wearer to see clearly at a near distance. This combination leads to the unexpected result that not only does the wearer have the ability to see clearly at intermediate and near distances, but the level of unwanted astigmatism, distortion, and vision compromise are reduced significantly.

Description

Static progressive surface region in optical communication with a dynamic optic

Cross-References to Related Applications

This application claims the priority of the following provisional application and is incorporated by reference in its entirety:

US Patent Application No. 60 / 812,625, filed Jun. 12, 2006, entitled "Surface Area Surface in Optical Communication with Mixed Proximate Regions";

US patent application Ser. No. 60 / 812,952, filed Jun. 13, 2006 entitled "Advanced Region in Optical Communication with Mixed Proximate Light Zones";

US patent application Ser. No. 60 / 854,707, filed Oct. 26, 2006, entitled "Static progressive surface area in optical communication with dynamic optics"; And

No. 60 / 876,464, filed Dec. 22, 2006, entitled “Improvement Ophthalmic Lens, Design and Eyewear System with Progressive Power Domain”.

FIELD OF THE INVENTION The present invention relates to multifocal ophthalmic lenses, lens designs, lens systems and eyeglass products or devices used or related to or in glasses. More specifically, the present invention provides a multifocal in most cases providing light effects / final results that reduce adverse distortions, adverse astigmatism and visual impairment associated with Progressive Addition Lenses over highly acceptable areas for the wearer. Ophthalmic lenses, lens designs, lens systems and eyeglass products.

Presbyopia is a loss of control of the lens of the human eye that accompanies aging. This loss of control makes it impossible to focus on near objects. The standard tool for correcting presbyopia is a multifocal ophthalmic lens. Multifocal lenses are lenses with one or more focal lengths (ie, optical power) to correct focus problems over a range of distances. Multifocal ophthalmic lenses act by the distribution of the area of the lens into regions of different optical power. In general, a very large area at the top of the lens corrects for far vision errors. The small area located at the bottom of the lens provides additional optical power to correct near vision errors caused by presbyopia. Multifocal lenses also include small areas located close to the middle of the lens that provide additional optical power for correcting medium vision errors.

The transition between the regions of different light sources is abruptly changeable for bifocal and triplefocal lenses and smooth and continuous for progressive additional lenses. Progressive additional lenses are in the form of a multifocal lens that includes a positively refractive optical power increase that continuously increases from the start of the far field of vision of the lens to the near field of vision within the lower portion of the lens. This progression of optical power begins almost as known as the fitting cross or the fitting point of the lens and lasts until the maximum additional power is realized in the near field and then reaches a plateau. Conventional state-of-the-art progressive addition lenses utilize surface topography on top of one or both of the outer surfaces of the lenses formed to produce such progressives of optical power. Progressive additional lenses are known in the mining industry as PALs in the plural and PAL in the singular. PAL lenses can provide users with conventional bifocals and trifocals in that they can provide a wireless, cosmetically appealing multifocal lens with continuous vision correction to focus from a distant object to a near object or vice versa. It is more convenient than the lens.

PAL is now widely accepted and prevalent in the United States and around the world for presbyopia correction, but it also has severe vision impairment. These damages include but are not limited to noxious astigmatism, distortion, and perceptual disparity. These vision impairments affect the user's horizontal gaze width, which is the width of the field of view that can be clearly observed when the user observes from one side to another when focusing at a given distance. The PAL lens thus has a narrow horizontal gaze width when focusing at medium distances, which can make it difficult to stare at large sections of a computer screen. Similarly, PAL lenses have a narrow horizontal gaze width when focused at close range, which can make it difficult to stare at the complete page of a book or newspaper. Far vision is similarly affected. PAL lenses also present difficulties for wearers in sports activities due to lens distortion. Moreover, because the additional light power is located in the lower area of the PAL lens, the wearer must tilt his or her head back for use of this area when staring at an object on his or her head located at near or medium distance. In contrast, when the wearer goes down the stairs and looks down, the near focus is provided instead of the far focus needed to clearly see the wearer's feet and stairs. Thus, the wearer's foot is taken out of focus and unclear. In addition to these limitations, many PAL wearers experience an unpleasant effect known as vision shift (often referred to as "dizziness") due to the imbalance distortion present in each of the lenses. In fact, many people refuse to wear these lenses because of these effects.

The amount of near-field light power needed when considering presbyopia's near-field light power needs is directly related to the amount of control (near focusing ability) that an individual remains in his or the eye. In general, as an individual ages, the amount of control decreases. In addition, control is reduced by various health causes. Thus, as an individual ages and becomes more presbyopic, the light power required to correct the ability to focus at near and intermediate gaze distances becomes stronger in terms of the additional power of refractive light required. For example, a 45-year-old individual requires +1.00 diopter of near-field optical power to see clearly at the near point distance, while an 80-year-old individual has a +2.75 to +3.00 diopter to see clearly at the same near point distance. Close staring distance requires optical power. As the degree of visual impairment in the PAL lens increases with the addition of refractive light, the higher presbyopia suffers more visual impairment. In the above example, a 45 year old individual has a lower level of distortion relative to his or her lens than an 80 year old individual. As is evident, this is in complete opposition to the necessary quality of life problems associated with aging, such as the loss of willpower or cleverness. Multifocal lens prescriptions are in stark contrast to lenses that make life easier, safer and less complicated.

By way of example, a typical PAL with + 1.00D near optical power has a noxious astigmatism of about + 1.00D or less. However, conventional PALs with + 2.50D proximity optical power have no more than about + 2.75D noxious astigmatism, and conventional PALs with + 3.25D proximity light power have no more than about + 3.75D noxious astigmatism. Thus, as the near-field additional power of the PAL is increased (eg, + 2.50D PAL vs. + 1.00D PAL), noxious astigmatism found within the PAL increases more than the linear ratio for the near-field additional power.

More recently, double-sided PALs have been developed with progressive additional surface shapes located on each side of the lens. The two progressive additional surfaces are aligned and rotated with respect to each other to provide the proper overall additional near-field additional power required, as well as the harmful astigmatism caused by PAL on one surface of the lens, caused by PAL on the other surface of the lens. Interfere with some of the harmful astigmatism. Although this design somewhat reduces the adverse astigmatism and distortion for the near-field power provided in comparison with conventional PAL lenses, the levels of adverse astigmatism, distortion and other vision impairments described above still cause serious vision problems for the wearer.

Thus, it meets the needs of presbyopia individuals, while reducing distortion and inconsistency, widening horizontal gaze, enabling improved safety, and improving vision in sports activities, computer work, book or newspaper subscriptions. There is a need to provide spectacle lenses and / or eyewear systems to correct presbyopia.

Summary of the Invention

In an embodiment of the invention an ophthalmic lens with an adjustment point for a user comprises a progressive additional region with a channel, the progressive additional region having additional power therein. The ophthalmic lens further comprises a dynamic optic in optical communication with a progressive additional area with optical power upon activation.

In an embodiment of the invention an ophthalmic lens with an adjustment point for a user comprises a progressive additional region with a channel, the progressive additional region having additional power therein. The ophthalmic lens further comprises a dynamic optic in optical communication with a progressive additional area with optical power upon activation, the dynamic optic having a top peripheral boundary located within an adjustment point of about 15 mm.

Description of the Preferred Embodiments

Many ophthalmological, ophthalmic, and optical terms are used in this application. These definitions are described below for clarity:

Add power : Optical power added to the far-field staring optical power required for clear near field vision within a multifocal lens. For example, if an individual has a -3.00D long range prescription with + 2.00D extra power for near vision, the actual optical power of the near field of the multifocal lens is -1.00D. The additional power is distinguished by representing "medium look distance extra power" representing additional power in the near gaze distance portion of the lens and "medium look distance extra power" representing additional power in the middle gaze distance portion of the lens. In general, the intermediate staring distance additional power is about 50% of the proximity staring distance additional power. Thus in this example the individual has + 1.00D additional power for the medium range gaze and the actual total optical power in the middle gaze distance portion of the multifocal lens is -2.00D.

About : Includes 10 percent plus or minus. The phrase “about 10 mm” is therefore understood to mean including 9 mm to 11 mm.

Blend zone : Continuous optical power conversion from the first correction power by the optical power conversion along the peripheral boundary of the lens to the second correction power or vice versa. In general, the mixing zone is designed to be as small as possible. The peripheral boundary of the dynamic optic includes a mixing zone to reduce the visibility of the dynamic optic. Mixing zones are used for cosmetic enhancement causes and also to increase vision functionality. The mixing zone is generally not considered an usable part of the lens due to its high noxious astigmatism. The mixing zone is also known as the conversion zone.

Channel : A region of progressive additional lenses defined by an increase in the addition of optical power extending from a far optical power region or region to a near optical power region or region. This optical power progression begins within the PAL region known as the control point and ends at the near field. Channels are sometimes referred to as corridors.

Channel Length : The channel length is the distance measured from the control point to the position in the channel if the additional power is within about 85% of the specified near field power.

Channel width : The narrowest channel portion combined by noxious astigmatism of about + 1.00D or more. This definition is useful when comparing PAL lenses due to the fact that wider channel widths are generally correlated with less distortion, good visual performance, increased visual comfort and easy wearer adaptation.

Contour Map: A plot generated by measuring and plotting the harmful astigmatism optical power of a progressive additional lens. Contour plots can be generated with varying sensitivity of astigmatism light power and thus provide a visual representation of where and to what extent harmful astigmatism possesses progressive progressive lenses as part of its optical design. Analysis of these maps is generally used to quantify channel length and sampling width in relation to the PAL width and far-field width. Contour maps are also designated as hazardous astigmatism power maps. These maps can be used to measure and describe the optical power of various parts of the lens.

Conventional channel length : It is desirable to have the lens shortened vertically due to aesthetic concerns or eyewear fashion trends. In these lenses, the channel also shrinks naturally. Typical channel lengths are referred to as channel lengths in non-short PAL lenses. These channel lengths are not always, but are generally about 15 mm or more. Longer channel lengths generally mean wider channel widths and less adverse astigmatism. Long channel designs are often combined with "soft" progressives because the transition between far and near calibration becomes smoother due to a more gradual increase in optical power.

Dynamic lens : A lens with variable optical power with the application of electrical energy, mechanical energy or force. The entire lens has a variable optical power or only a portion, region or region of the lens has a variable optical power. The optical power of such lenses is dynamic or tunable such that the optical power is switched between two or more optical powers. One of the optical powers is substantially no optical power. Examples of dynamic lenses include electro-active lenses, uneven lenses, fluid lenses, movable dynamic optics with one or more components, gas lenses and membrane lenses with deformable membranes. Dynamic lenses are also referred to as dynamic optics, dynamic light elements, dynamic light zones or dynamic light regions.

Far reference point : A reference point located about 3 to 4 mm from the calibration intersection where the far prescription or far optical power of the lens can be easily measured.

Far field of view : A portion of a lens containing optical power that allows the user to see accurately at a far distance.

Far-field width : The narrowest horizontal width within the far-field portion of the lens that provides clear, mostly distortion-free correction with light power within the 0.25D wearer's far-field optical power calibration.

Distant Staring Distance : For example, the distance you observe when looking beyond the bounds of your desk, driving a car, observing mountains in the distance, or watching a movie. This distance is not always but is generally considered to be about 32 inches or more from the eye. The far gaze is also denoted as far and far points.

Adjustment Cross / Adjustment Point : A reference point on the PAL that represents the approximate location of the wearer's pupil when looking directly through the lens when the lens is mounted on the eyeglass frame and positioned on the face of the wearer. The adjustment crossover / adjustment point is not always, but is usually located 2 to 5 mm above the start of the channel. The adjustment crossover typically has a very small amount of positive optical power ranging from +0.00 diopters to about +0.12 diopters. These points or intersections can be marked on the lens surface to provide an easy reference point for measuring or double-checking the adjustment of the lens relative to the wearer's pupil. The marking can be easily removed when selling the lens to the patient / wearer.

Hard progressive additional lenses : Progressive additional lenses with a gradual sharp transition between long range correction and near field correction. In the case of hard PAL, noxious distortions exist below the control points and do not extend around the lens. Hard PAL also has a short channel length and narrow channel width. "Modified hard progressive additional lenses" feature a limited number of soft PAL characteristics, such as more progressive optical power conversion, longer channels, wider channels, more harmful astigmatism extended into the lens's periphery, and less noxious astigmatism below the control point. Hard PAL modified to have.

Medium field of view: A portion of a lens containing optical power that allows the user to see accurately at a medium field of view.

Intermediate gaze distance : For example, the distance an individual observes when reading a newspaper, working on a computer, washing dishes in the sink, or ironing clothes. This distance is not always, but is generally considered to be between about 16 inches and about 32 inches from the eye. Intermediate gaze distances are also referred to as mid-range and mid-range points.

Lens : A device or part of a device that concentrates or diverges light. The device is either static or dynamic. The lens is refracted or diffracted. The lens is concave, convex or flat on one or both sides. The lens is spherical, cylindrical, prism or a combination thereof. The lens is made of optical glass, plastic or resin. Lenses are also referred to as light elements, light zones, light regions, optical power regions or optics. In the mining industry, a lens may be referred to as a lens even when it has zero optical power.

Lens blank : A device made of an optical material formed in a lens. The lens blank is completed, which means that it is formed to have optical power on both outer surfaces. The lens blank is semi-finished, which means that the lens blank is formed to have optical power only on one outer surface. The lens blank is incomplete, which means that the lens blank is not formed to have optical power on any exterior surface. The surface of an unfinished or semi-finished lens blank is completed by a manufacturing process known as free-forming or by conventional surfacing and polishing.

Low additional power PAL : Progressive additional lenses with less than the proximity extra power needed for the wearer to see clearly at close range.

Multifocal lens : A lens with one or more focus or optical powers. Such lenses are static or dynamic. Examples of static multifocal lenses include bifocal lenses, trifocal lenses or progressive additional lenses. An example of a dynamic multifocal lens is produced in a lens, including an electro-active lens, in which various optical powers are used differently depending on the form of the electrode, the voltage applied to the electrode, and the refractive index changing within the thin liquid crystal. Multifocal lenses are also capable of both static and dynamic combinations. For example, electro-active elements are used for optical communication with static multifocal lenses such as static spherical lenses, static single vision lenses, for example progressive additional lenses. Most, but not all, multifocal lenses are refractive lenses.

Near field of view : A portion of a lens containing optical power that allows a user to see accurately at a close gaze distance.

Melee Staring Distance : For example, the distance an individual observes when reading, sewing, or reading a vial. This distance is not always, but is generally considered to be between about 12 inches and about 16 inches from the eye. Proximity gaze distances are also expressed as near and near points.

Office lens / office PAL : A specially designed progressive addition lens that provides medium-range vision, wide channel width, and wide read width on adjustable crossovers. This is achieved by an optical design that extends noxious astigmatism over the control crossover and replaces the far vision zone with the predominantly dry vision zone. Due to this shape, this type of PAL is very suitable for office work, but because the lens does not include a remote gaze area, an individual cannot drive his or her car or use it to walk around the office or home.

Ophthalmic Lenses : Lenses suitable for vision correction, including spectacle lenses, contact lenses, intraocular lenses, corneal in-lays and corneal on-lays.

Optical communication : A condition in which two or more optics of a given optical power are aligned in such a way that the light passing through the aligned optics experiences a combined optical power equal to the total of the optical powers of the individual elements.

Patterned electrode : An electrode used in an electro-active lens such that the optical power produced by the liquid crystal upon application of an appropriate voltage to the electrode is produced diffractively regardless of the size, shape and alignment of the electrode. For example, diffractive light effects can be generated dynamically in liquid crystals by using concentric electrode.

Pixelated Electrode : An electrode used in an electro-active lens that can be processed individually, regardless of the size, shape and alignment of the electrode. Moreover, any electrode pattern is applied to the electrodes because the electrodes can be processed individually. For example, the pixelated electrode may be a hexagon arranged in a rectangular or square or hexagonal arrangement arranged in a Cartesian arrangement. For example, pixelated electrodes are concentric if all the circles can be processed individually. The concentric pixelated electrodes can be individually processed to produce a diffractive light effect.

Progressive additional region : A lens region having a first optical power in the first part of the region where there is a continuous change in optical power therebetween and a second optical power in the second part of the region. For example, the lens region has a staring distance optical power at one end of the region. The optical power is increased in addition to the power over the region up to the intermediate staring distance optical power and the proximity staring distance optical power at opposite ends of the region. After the optical power reaches the near staring distance optical power, the optical power is reduced in such a way that the optical power of this progressive additional area conversion returns to the distant staring distance optical power. The progressive additional area is present on the lens surface or embedded in the lens. If a progressive additional area is present on the surface and comprises a surface morphology it is known as a progressive additional surface.

Read Width : The narrowest horizontal width within the near-field portion of the lens that provides a clear, mainly distortion-free correction with optical power within the wearer's near-field optical power correction of 0.25D.

Short channel length : It is desirable to have a lens that is vertically shortened due to aesthetic concerns or spectacle fashion trends. In such lenses, the channel is also shortened naturally. Short channel length is referred to as the channel length in the shortened PAL lens. These channel lengths are not always, but are generally between about 11 mm and about 15 mm. Shorter channel lengths generally mean narrower channel widths and more harmful astigmatism. The short channel design is combined with "hard" progressive because the transition between far and near calibration is more robust due to a sharp increase in optical power.

Short progressive lenses : Progressive additional lenses with a more gradual transition between distant and near correction. In soft PAL, the harmful distortion is above the control point and extends into the periphery of the lens. Soft PAL also has a long channel length and wide channel width. "Modified soft progressive additional lenses" are modified to have a limited number of hard PAL characteristics, such as rapid optical power conversion, short channels, narrow channels, more harmful astigmatism pushing into the gaze portion of the lens, and more harmful astigmatism below the control point. Soft PAL.

Static lens : A lens with optical power that can change when an electrical energy, mechanical energy or force is applied. Examples of static lenses include spherical lenses, cylindrical lenses, progressive additional lenses, bifocals, and trifocals. Static lenses are also referred to as fixed lenses.

Hazard Astigmatism: Hazardous aberrations, distortions, or astigmatism found in progressive additional lenses are not part of the patient's prescribed vision correction but are derived from the PAL's optical design due to the flat increase and decrease of optical power between gaze zones. Although a lens has noxious astigmatism over different areas of the lens of varying refractive power, the noxious astigmatism in the lens is generally referred to as the largest noxious astigmatism found in the lens. The noxious astigmatism is also referred to as the noxious astigmatism, which is located in a specific part of the lens when facing the lens as a whole. In this case the definitive language is used to indicate only noxious astigmatism within the particular part of the lens under consideration.

When describing dynamic lenses, the present invention considers, by way of example, electro-active lenses, fluid lenses, gas lenses, membrane lenses and mechanically movable lenses. Examples of such lenses are Blum et al. US Pat. Nos. 6,517,203, 6,491,394, 6,619,799, Epstein and Kuitin, US Pat. Nos. 7,008,054, 6,040,947, 5,668,620, 5,999,328, 5,956,183, 6,893,124 US Pat. Nos. 4,890,903, 6,069,742, 7,085,065, 6,188,525, 6,618,208 to Silver, US Pat. No. 5,182,585 to Stoner, and US Pat. No. 5,229,885 to Quaglia.

As long as lens astigmatism and distortion of the lens is about 1.00D or less, the lens user is hardly aware of it in most cases and is well known and accepted in the light industry. The present invention disclosed herein relates to embodiments of optical designs, lenses and eyewear systems that solve many of the problems associated with PAL. Moreover, the present invention disclosed herein significantly eliminates most of the visual impairment associated with PAL. The present invention provides a means for the wearer to achieve adequate long, medium and near light power and to provide continuous focusing capability for various distances similar to PAL. At the same time, however, the present invention maintains noxious astigmatism with a maximum of about 1.50D for certain high additional power regimens such as + 3.00D, + 3.25D and + 3.50D. In most cases, however, the present invention maintains noxious astigmatism to a maximum of about 1.00 D or less.

The present invention is based on aligning the low additional power PAL with the dynamic lens such that the dynamic lens and the low additional power PAL are in optical communication, the dynamic lens provides the additional optical power necessary for the wearer to see clearly at close range. This combination not only has the ability for the wearer to see clearly at medium and near distances, but also results in unexpected consequences in which the levels of noxious astigmatism, distortion and vision damage are significantly reduced.

Dynamic lenses are electro-active elements. In an electro-active lens the electro-active optic is embedded in or attached to the surface of the optical substrate. The optical substrate is a finished, semi-finished or incomplete lens blank. If a semi-finished or incomplete lens blank is used, the lens blank is completed during manufacture of the lens to have one or more optical powers. Electro-active optics are also embedded in or attached to the surface of conventional optical lenses. Conventional optical lenses are multifocal lenses such as monofocal lenses or progressive addition lenses or bifocal or trifocal lenses. The electro-active optics are located in the entire gaze area or only a portion of the electro-active lenses. The electro-active optics are spaced from the peripheral boundaries of the optical substrate for edging the electro-active lenses for the spectacles. The electro-active element is located proximate to the top, center or bottom part of the lens. If substantially no voltage is applied, the electro-active optics are inactive, providing virtually no optical power. In other words, the electro-active optic has substantially the same refractive index as the buried or attached optical substrate or conventional lens when substantially no voltage is applied. When a voltage is applied, the electro-active optics are activated to provide additional light power. That is, when voltage is applied, the electro-active optics have a refractive index that is different from the buried or attached optical substrate or conventional lenses.

Electro-active lenses are used to correct typical or non-traditional errors in the eye. Calibration is produced by electro-active elements, optical substrates or conventional optical lenses or by a combination of the two. Common errors in the eye include low-level aberrations such as myopia, hyperopia, presbyopia and astigmatism. Non-normal errors of the eye include high-level aberrations that can be caused by eye layer irregularities.

Liquid crystals are used as part of the electro-active optics because the refractive index of the liquid crystal can be changed by crossing the liquid crystal to produce an electric field. This electric field is created by applying one or more voltages to electrodes located on both sides of the liquid crystal. The electrode is made of a substantially transparent conductive material such as indium tin oxide (ITO) or a material well known in the art. Liquid crystal based electro-active optics are particularly well suited for use as part of electro-active optics because the liquid crystals can provide a range of refractive index changes necessary to provide light addition power of plane to + 3.00D. This additional range of light power makes it possible to correct presbyopia in most patients.

A thin layer of liquid crystal (10 μm or less) is used to construct the electro-active optics. The thin liquid crystal is sandwiched between two transparent substrates in a sandwich form. The two substrates are also sealed along their peripheral boundaries such that the liquid crystal is sealed in the substrate in a substantially closed manner. The transparent conductive material layer is deposited on the inner surface of the two substantially planar transparent substrates. The conductive material is then used as an electrode. When thin layers are used, the shape and size of the electrode (s) is used to induce specific light effects in the lens. The required operating voltage applied to these electrode electrodes for such thin liquid crystals is generally very low, below 5 volts. The electrode is patterned. For example, diffractive light effects can be generated dynamically in the liquid crystal by using electrodes in the form of concentric circles deposited on at least one or more substrates. This light effect can generate additional light power based on the radius of the circle, the width of the circle, and the voltage range applied separately to the other circle. For example, the pixelated electrode is a hexagon arranged in a rectangular or square or hexagonal arrangement arranged in a Cartesian arrangement. This arrangement of pixelated electrodes is used to generate additional light power by competing with the diffractive concentric electrode substrate. Pixelated electrodes are also used to correct high-level aberrations of the eye in a manner similar to that used to correct atmospheric turbulence effects in ground-based astronomy.

Current manufacturing processes limit the maximum pixel size, which limits the maximum dynamic electro-active optic diameter. As an example the maximum dynamic electro-active optic diameter is estimated to be 20 mm for + 1.50D, 24 mm for + 1.25D and 30 mm for + 1.50D when using a concentric pixelation method that produces a diffractive pattern. Current manufacturing processes limit the maximum dynamic electro-active optic diameter when using the pixelated diffractive method. As such, embodiments of the present invention may include dynamic electro-active optics with smaller optical power at larger diameters.

Alternatively the electro-active optic consists of two transparent substrates and a layer of liquid crystal, the first substrate is coated with a substantially planar and transparent conductive layer, and the second substrate is a surface relief diffractive pattern and coated with a transparent conductive layer. Has a patterned surface. Surface relief diffractive optics are physical substrates having a diffractive grating etched or produced thereon. The surface relief diffractive pattern can be produced by diamond turing, injection molding, casting, thermoforming and stamping. Such optics are designed to have a fixed optical power and / or aberration correction. By applying a voltage to the liquid crystal through the electrode, optical power / aberration correction can be switched on or off by refractive index mismatching and matching, respectively. The liquid crystal has substantially the same refractive index as the surface relief diffractive optics when substantially no voltage is applied. This negates the optical power typically provided by the surface relief diffractive elements. When voltage is applied, the liquid crystal will have a different refractive index than the surface relief diffractive element such that the surface relief diffractive element provides additional light power. Dynamic electro-active optics with large diameters or horizontal widths can be made by using the surface relief diffractive pattern method. The width of these optics can be made up to 40 mm or more.

Also, a later layer of liquid crystal (typically> 50 μm) is also used to construct the electro-active multifocal lens. For example, a form lens is used to generate refractive optics. As is known in the art, aquaculture lenses include a single continuous low conductivity circular electrode surrounded by and in electrical contact with a single high conductivity annular electrode. When a single voltage is applied to the highly conductive annular electrode, the low conductivity electrode, which is essentially a radially symmetrical and electrically resistive network, crosses the liquid crystal layer, creating a voltage gradient, which substantially induces a refractive index gradient in the liquid crystal. The liquid crystal layer with refractive index gradient will function as an electro-active lens and focus on the light projected on it.

In an embodiment of the present invention dynamic optics are used in combination with progressive further lenses to form a combined lens. The progressive addition lens is a low additional power progressive addition lens. The progressive addition lens includes a progressive addition region. Dynamic optics are positioned to optically communicate with the progressive additional areas. Dynamic optics maintain a constant distance from progressive additional areas, but communicate optically with him.

In an embodiment of the present invention, the progressive additional region has an additional power of one of + 0.50D, + 0.75D, + 1.OOD, + 1.12D, + 1.25D, + 1.37D and + 1.50D. In an embodiment of the invention the dynamic optics are + 0.50D, + 0.75D, + 1.00D, + 1.12D, + 1.25D, + 1.37D, + 1.50D, + 1.62D, + 1.75D, +2.00 in the activated state. Has an optical power of one of D and + 2.25D. The additional power of the progressive additional area and the optical power of the dynamic optics are prepared or prescribed to the patient in + 0.125D (around + .12D or + .13D) steps or + 0.25D steps.

It should be appreciated that the present invention includes all possible power combinations, static and dynamic, that are necessary to properly correct the wearer's vision at distant, intermediate and close gaze distances. The examples and embodiments of the invention provided in this disclosure are illustrative only and not intended to be limiting. This is to show additional optical power correlation when the low additional power progressive additional region is in optical communication with the dynamic optics.

Dynamic optics have mixing zones so that the optical power along the perimeter of the element is mixed to reduce the visibility of the perimeter when the element is activated. In most but not all cases, the optical power of the dynamic optics is converted in the mixing zone from the maximum optical power provided by the dynamic optics when activated with the optical power found in the progressive additional lens. In embodiments of the invention the mixing zone is 1 mm to 4 mm wide along the perimeter of the dynamic optics. In another embodiment of the present invention the mixing zone is 1 mm to 2 mm wide along the perimeter of the dynamic optics.

The dynamic optics will not provide virtually any additional optical power when the dynamic optics are disabled. Thus, when the dynamic optics are deactivated, the progressive additional lenses provide all additional power to the combined lens (ie the total added power of the combined optics is equal to the additional power of the PAL). If the dynamic optic comprises a mixing zone, the mixing zone in the deactivated state provides substantially no optical power and substantially no harmful astigmatism due to refractive index matching in the deactivated state. In embodiments of the invention the total noxious astigmatism in the combined lens when the dynamic optics are inactive is substantially the same as that provided by the progressive additional lens. In embodiments of the invention the total added power of the coupling optics when the dynamic optics are inactive is about + 1.00D, and the total noxious astigmatism in the coupling lens is about 1.00D or less. In another embodiment of the present invention, when the dynamic optics are inactive, the total added power of the combined optics is about + 1.25D, and the total noxious astigmatism in the combined lens is about 1.25D or less. In another embodiment of the present invention, when the dynamic optics are inactive, the total additional power of the coupling optics is about + 1.50D and the total noxious astigmatism in the coupling lens is about 1.50D or less.

The dynamic optic will provide additional optical power when the dynamic optic is activated. Since the dynamic optics are in optical communication with the progressive additional lenses, the combined extra power of the combined optics is equal to the extra power of the PAL and the extra optical power of the dynamic optics. If the dynamic optic comprises a mixing zone, the mixing zone in the activated state provides optical power and noxious astigmatism due to refractive index mismatching in the activated state and is not very useful for visual focus. Thus, if the dynamic optic includes a mixing zone, the harmful astigmatism of the coupling optic is measured only within the usable portion of the dynamic optic that does not include the mixing zone. In embodiments of the invention the total noxious astigmatism in the combined lens measured through the usable portion of the lens when the dynamic optic is activated is substantially the same as the noxious astigmatism in the progressive additional lens. In embodiments of the invention the total additional power of the coupling optics when the dynamic optics are activated is between about + 0.75D and about + 2.25D, and the total noxious astigmatism in the usable portion of the coupling lens is less than or equal to 1.00D. In another embodiment of the present invention, when the dynamic optic is activated, the total additional power of the coupling optic is between about + 2.50D and about + 2.75D, and the total noxious astigmatism in the usable portion of the coupling lens is less than 1.25D. In another embodiment of the present invention, when the dynamic optic is activated, the total additional power of the coupling optic is between about + 3.00D and about + 3.50D, and the total noxious astigmatism in the usable portion of the coupling lens is less than 1.50D. The present invention thus enables the creation of a lens with a significantly higher total additional power than the noxious astigmatism of the lens when measured through the usable portion of the lens. That is, the degree of noxious astigmatism is substantially reduced in the provided total additional power of the combined lens of the present invention. This is a significant degree of improvement over that described or circulated in the literature. This improvement translates to higher adaptation speed, lower distortion, lower tripping or disorientation of the wearer, and a much wider clear field of view at medium distance and near vision by the wearer.

In an embodiment of the present invention, the dynamic optic provides between about 30% and about 70% of the total additional power required for the user's near vision prescription. The progressive additional area of low additional power PAL provides the remainder of the additional power required for the user's near vision prescription, ie between about 70% and about 30%, respectively. In another embodiment of the present invention, the dynamic optics and progressive additional regions each provide about 50% of the total additional power required for the near vision prescription of the user. If the dynamic optics provide too much total additional power, the user will not be able to see clearly at mid-range when the dynamic lenses are deactivated. Moreover, when dynamic optics are activated, the user will have too much optical power in the mid-range gaze zone and therefore cannot see clearly at mid-range. If the dynamic optics provide too little total additional power, the combined lens will have too much harmful astigmatism.

If the dynamic optic comprises a mixing zone it is required that the dynamic optic is wide enough to ensure at least a portion of the mixing zone located around the coupling optic. In an embodiment of the invention the horizontal width of the dynamic optics is at least about 26 mm. In another embodiment of the present invention, the horizontal width of the dynamic optic is between about 24 mm and about 40 mm. In another embodiment of the present invention, the horizontal width of the dynamic optic is between about 30 mm and about 34 mm. If the dynamic optic is about 24 mm wide or less, it is possible that when the dynamic optic is activated, the mixing zone interferes with the user's vision and causes too much distortion and dizziness for the user. If the dynamic optics are about 40 mm wide or more, it is difficult to edge the combined lens into the shape of the eyeglass frame. In most, but not all cases, dynamic optics have an elliptical shape with horizontal width dimensions greater than their vertical height dimensions when the dynamic optics are located at or below the control point of the combined lens. This is not always the case when the dynamic optic is located with the mixing zone above the adjustment point, but in general the dynamic optic is positioned so that the upper peripheral boundary of the dynamic optic is at least 8 mm above the adjustment point. It should be noted that dynamic optics that are not electro-active are located at the peripheral boundary of the coupling lens. Moreover, these non-electro-active dynamic optics are up to 24 mm wide.

In an embodiment of the invention the dynamic optic is located at or above the control point. The upper peripheral boundary of the dynamic optic is between about 0 mm and 15 mm above the adjustment point. Dynamic optics can provide the optical power needed when activated when the wearer gazes between medium, near or near and near (near-medium) distances. It comes from dynamic optics located at or above the control point. This will allow the user to have an accurate mid-range prescription when staring straight ahead. Moreover, due to the progressive additional area, the optical power is continuously increased at the adjustment point facing down through the channel. The user will have accurate near-medium distance and near-prescription correction when staring through the channel. Thus, in many situations, the user does not have to stare farther down or raise his chin far to see through the lens's medium distance gaze zone. If the dynamic optics are spaced vertically from the top of the combined lens, the user can see from a distance by using a portion of the combined lens on top of the activated dynamic optics. When dynamic optics are deactivated, the lens area at or near the control point will return to the far optical power of the lens.

In embodiments where the dynamic optic has a mixing zone, it is desirable to place the dynamic optic above the control point. In this embodiment, when dynamic optics are activated, the user does not stare through the mixing zone but directly through the control point and down through the channel. As described above, the mixing zone introduces a high degree of harmful astigmatism that is inconvenient to stare. Thus, the user does not have to pass through the boundary of the dynamic optics or the mixing zone, so the user uses the combined optics in the active state without experiencing a high degree of noxious astigmatism.

In an embodiment of the invention the dynamic optic is located below the control point. The upper peripheral boundary of the dynamic optic is between about 0 mm and 15 mm below the adjustment point. If the user stares directly through the adjustment point, the distance prescription correction is provided by the coupling optics when the dynamic optics are not in optical communication with a portion of the coupling lens. However, if the user moves his or her gaze down through the channel at the control point, the user experiences a high degree of noxious astigmatism when the user's eye passes over the mixing zone of the dynamic optics. This is adjusted in various ways as described below.

The combined ophthalmic lens of the present invention includes an optical design taking into account:

1) the total near field additional power of the ophthalmic lens of the present invention necessary to satisfy the wearer's near vision correction;

2) noxious astigmatism or distortion levels within the usable portion of the combined lens;

3) the amount of light additional power provided in part by the progressive additional region;

4) the amount of optical power provided by the dynamic optics upon activation;

5) channel length of the progressive additional region;

6) design of progressive additional areas such as whether it is a soft PAL design, a hard PAL design, a modified soft PAL design or a modified hard PAL design;

7) width and height of dynamic optics; And

8) Position of the dynamic optics relative to the progressive addition region.

1A shows an embodiment of a progressive additional lens 100 with an adjustment point 110 and a progressive additional region 120. The progressive additional lens of FIG. 1A is a low additional power progressive additional lens designed to provide the wearer with a desired optical power that is less than the wearer's required near optical power correction. For example, the additional optical power of the PAL is 50% of the near optical power calibration. The length along the line AA axis of the lens from the adjustment point to the point on the lens where optical power is within 85% of the desired additional optical power is known as the channel length. The channel length is designated by distance D in FIG. 1A. The value of distance D depends on many factors, such as the frame shape that the lens is edged to fit, how much optical power is needed, and how wide channel width is required. In an embodiment of the present invention, the distance D is between about 11 mm and about 20 mm. In another embodiment of the present invention, the distance D is between about 14 mm and about 18 mm.

FIG. 1B shows a graph of optical power 130 taken along the cross section of the lens of FIG. 1A along the line AA axis. The x-axis of the graph represents the distance along the line AA axis in the lens. The y-axis of the graph represents the amount of optical power in the lens. The optical power shown in the graph starts at the adjustment point. The optical power at or before the control point is about + 0.00D to about + 0.12D (ie, almost no optical power) or has a different positive or negative refractive power depending on the user's remote prescription needs. 1B shows a lens without any optical power at or before the adjustment point. After the adjustment point, the optical power is continuously increased to the maximum power. The maximum power lasts for some length of the lens along the line AA axis. 1B shows the maximum power duration that appears as the peak of optical power. 1B also shows that the distance D occurs before the maximum power. After the maximum power peak, the optical power continues to decrease until the desired optical power. The preferred optical power can be any power up to the maximum power and may be the same as the optical power at the control point. 1B shows the optical power continuously decreasing after the maximum power.

In an embodiment of the invention the progressive addition area is a progressive addition surface located on the front surface of the lens and the dynamic optics are embedded inside the lens. In another embodiment of the present invention, the progressive addition region is a progressive addition surface located on the back surface of the lens and the dynamic optics are buried inside the lens. In another embodiment of the present invention, the progressive additional region is two progressive additional surfaces having one surface located on the front surface of the lens and the second surface located on the rear surface of the lens (such as the dual surface of the progressive additional lens). Dynamic optics are embedded inside the lens. In another embodiment of the invention the progressive additional regions are not created by the geometric surface but instead by the refractive index gradient. This embodiment allows both surfaces of the lens to be similar to the surface used on a single focus lens. This refractive index gradient, which provides a progressive additional area, is located within or on the surface of the lens.

One of the important advantages of the present invention is that the wearer will always have the correct medium and far vision optical power even when the dynamic optics are inactive as described above. Therefore, the only required control mechanism is a means of selectively activating the dynamic optics when a suitable near-field power is needed for the wearer. This effect is provided by a low additional power PAL with additional power at the near field which provides less optical power than the user's prescription near field requirement, and this low additional power is also close to the exact prescription optical power for the wearer's medium range gaze demand. . When dynamic optics are activated, the wearer's near optical power focusing needs will be met.

This greatly simplifies the set of sensors needed to control the lens. All that is really needed is a sensing device that can detect whether the user is focused over longer distances. Dynamic optics are activated when the user focuses closer than far. Dynamic optics are disabled if the user does not focus closer than far. Such devices are simple tilt switches, manual switches or range switches.

In embodiments of the present invention a small amount of temporary delay is located in the control system such that the patient's eye is passed past a point at the peripheral boundary of the dynamic optic before the dynamic optic is activated. This prevents the unpleasant harmful distortion effect caused by the wearer staring through the peripheral boundary of the dynamic optics. This embodiment is beneficial if the dynamic optics include mixing zones. For example, if the wearer's gaze is shifted to gaze at a near object at a far object, the wearer's eye will move past the perimeter of the dynamic optic and into the near field. In this case, the dynamic optics will not be activated until the wearer's line of sight is transformed into the near field of vision beyond the perimeter of the dynamic optics. This is caused by delaying the time to activate the dynamic optics in order for the wearer's gaze to pass through the perimeter boundary. If the activation of the dynamic optics is not temporarily delayed but instead activated before the wearer's gaze is transformed past the perimeter, the wearer will experience a high degree of adverse astigmatism when gazing through the perimeter. This embodiment of the present invention is mainly used when the peripheral boundary of the dynamic optic is located at or below the adjustment point of the coupling lens. In another embodiment of the present invention, the peripheral boundary of the dynamic optic is located above the adjustment point of the combined lens, so in most cases the delay is because the gaze of the wearer never passes through the peripheral boundary of the dynamic optic when gazing between the medium distance and the near field. Do not need.

In another embodiment of the present invention the mixing zone of the progressive additional lens and the dynamic optic is designed such that in the region where the two overlap, the harmful astigmatism in the mixing zone at least partially invalidates some of the harmful astigmatism in the PAL. This effect is similar to the double-sided PAL, in which the harmful astigmatism of one hyomyeon is designed to negate some of the harmful astigmatism of another surface.

In embodiments of the present invention, it is desirable to increase the size of the dynamic optics and to position the dynamic optics so that the upper peripheral boundary of the dynamic optics is above the adjustment point of the lens. FIG. 2A shows an embodiment of a low additional power progressive additional lens 200 combined with a larger dynamic optic 220 positioned such that the upper peripheral boundary 250 of the dynamic optic is located above the adjustment point 210 of the lens. In embodiments of the invention the diameter of the larger dynamic optics is between about 24 mm and about 40 mm. The vertical displacement of the dynamic optics relative to the adjustment point of the lens is specified by the distance d. In an embodiment of the present invention, the distance d ranges from about 0 mm to about half the diameter of the dynamic optic diameter. In another embodiment of the present invention, the distance d is between about 1/8 of the dynamic optic diameter and 3/8 of the dynamic optic diameter. 2B illustrates an embodiment with combined optical power 230 generated because the dynamic optics are in optical communication with the progressive additional region 240. Lens 200 has a reduced channel length. In embodiments of the invention the channel length is between about 11 mm and about 20 mm. In another embodiment of the present invention the channel length is between about 14 mm and about 18 mm.

In the embodiment of the present invention shown in FIGS. 2A and 2B, when the dynamic optic is activated, the wearer has an accurate mid-range vision when staring directly because the lens is a low additional power PAL and the dynamic optic is located above the control point. In addition, if the wearer's eye moves down the channel, the wearer has the correct near-medium distance. Finally, the power of the dynamic optics and the progressive additional areas are missing, forming the required near staring distance correction, and the wearer has the correct near vision within the combined lens area. This is an advantageous way to combine dynamic optics with progressive additional areas, because computer use is primarily a medium gaze distance task and many people stare at the computer in front of or with very little staring down. The lens area above and near the adjustment point in the inactive state allows for far vision correction with weak progressive power below the adjustment point. The maximum optical power of the progressive additional zone provides about half of the near optical power required by the wearer and the dynamic optics provide the rest of the optical power required for clear near vision.

3A-3C show an embodiment of the invention wherein the dynamic optic 320 is located within the lens 300 and the progressive additional area 310 is located on the back surface of the lens. This back progressive additional surface may be located on the lens during processing of the semi-finished lens blank with the dynamic optics integrated by a manufacturing method known as preforming. In another embodiment of the present invention, the progressive additional region is located on the front surface of the semi-finished lens blank. The semi-finished lens blank incorporates dynamic optics so that the dynamic optics are properly aligned with the progressive additional surface curvature. The semi-finished lens blank is then processed by conventional surface finishing, polishing, boundary treatment and mounted into the spectacle frame.

The optical power taken along the line of sight from the wearer's eye 340 through the control point when the dynamic optics are deactivated as shown in FIG. 3A provides the wearer with accurate far vision 330. As shown in FIG. 3B, the optical power taken along the line of sight from the wearer's eye through the adjustment point when the dynamic optic is activated provides the wearer with accurate mid-range focusing power 331. As shown in FIGS. 3B-3C, when the wearer moves his or her gaze down the channel, the combined optics of the dynamic and progressive additional surfaces provide primarily continuous power conversion from medium to near focus. Thus, as shown in FIG. 3C, when dynamic optics are activated, optical power taken along the line of sight from the wearer's eye through the near-field gaze zone provides the wearer with accurate near focusing power 332. One of the major advantages of this embodiment of the present invention is that the control system is only needed to determine if the wearer is staring at a distance. In this case, the dynamic optics remain inactive. In embodiments where a ranging device is used, a ranging system is only needed to determine whether an object is closer to the eye than the individual's medium distance. In this case, the dynamic optics are activated to provide combined optical power that enables simultaneous calibration of medium and near optical power. Another major advantage of this embodiment of the present invention is that the eye passes over or crosses the upper boundary of the dynamic optics when the direction changes, such as when the user stares from the distant portion of the lens to the near portion of the lens or vice versa. There is no need to do it. If the dynamic optic has its highest boundary located below the control point, the eye must pass over or cross this upper boundary when gazing from far to near or from far to far. However, embodiments of the present invention allow for positioning below the dynamic optic's control point so that the eyeball does not pass over the top boundary of the dynamic optic. This embodiment enables another advantage in visual performance and ergonomics.

3A-3C show progressive additional surface areas on the back surface but where dynamic optics are located within the lens, they are located on the front surface of the lens or on both the front or back surface of the lens. Moreover, when dynamic optics appear to be located within the lens, they are also located on the surface of the lens if they are made of a convex substrate and covered with an ophthalmic covering material. It is possible to substantially reduce the number of dynamic optic semi-finished blank SKUs by using one dynamic optic with a known optical power combined with another PAL lens, each with a different additional power. For example, + 0.75D dynamic optics can be combined with + 0.50D, + 0.75D, or + 1.0OD progressive additional regions or surfaces to generate 1.25D, + 1.50D, or + 1.75D, respectively. Alternatively, + 1.00D dynamic optics can be combined with + 0.75D or + 1.0OD progressive additional areas or surfaces to generate additional power of + 1.75D or + 2.00D. Furthermore, progressive addition areas can be optimized in view of the wearer's characteristics such as the patient's far power and eye path through the lens, as well as the fact that progressive addition areas are added to the dynamic electro-active optics, which provide about half of the required reading correction. have. Similarly the reverse works well. For example, + 1.00D progressive additional areas or surfaces are combined with + 0.75D, + 1.00D, + l.25D or + 1.50D dynamic optics to combine +1 75D, + 2.00D, + 2.25D or + 2.5OD Generate additional power.

4A illustrates another embodiment of the present invention in which a low additional power progressive additional lens 400 is combined with a dynamic optic 420 that is larger than a progressive additional region and / or channel 430. In this embodiment the harmful distortion 450 from the mixing zone of the dynamic optics will be outside of the control point 410 and both the progressive additional channel 430 and the reading zone 440. 4B-4D show optical power graphs taken along the cross section of the lens of FIG. 4A along the line AA axis. The x-axis of each graph represents the distance along the line AA axis of the lens. The y-axis of each graph represents the amount of optical power in the lens. The optical power at or before the control point is about + 0.00D to about + 0.12D (ie, there is little optical power present) or has other positive or negative refractive power depending on the user's remote prescription needs. 4B shows a lens without any optical power at or before the adjustment point. 4B shows the optical power 460 provided by the fixed progressive additional surface or area taken along the line AA axis of FIG. 4A. 4C shows the optical power 470 provided by the dynamic optics taken along the line AA axis of FIG. 4A upon activation. Finally, FIG. 4D shows the combined power of the dynamic electro-active optics and the fixed progressive additional region taken along the line AA axis of FIG. 4A. It is evident from the figure that the top and bottom distortion mixing regions 450 of the dynamic electro-active optics are outside of both the adjustment point 410 and the progressive further reading regions 440 and channel 430.

5A and 5B show an embodiment where the dynamic optic 520 is located below the adjustment point 510 of the low additional power progressive additional lens 500. The position of the mixing zone of the dynamic electro-active optics results in significant overall distortion 550 when the wearer's eye tracks down the progressive corridor 530 in FIG. 5A. In certain embodiments of the present invention this is solved by delaying the activation of the dynamic optics when the wearer's eye passes over the upper boundary of the mixing zone of the dynamic optics. 5B shows the optical power along the line AA axis of FIG. 5A. The region of distortion 550 appears to overlap the additional power of the lens just below the adjustment point and also indicates that it is necessary to delay activation of the dynamic optics until the eye passes over this region. As the eye passes over this area and enters, for example, into the reading zone 540, there is no further significant light distortion. In an embodiment of the present invention a very narrow mixing zone of 1 mm to 2 mm is provided to allow the eye to pass quickly over this area. In an embodiment of the invention the horizontal width of the dynamic optic is between about 24 mm and about 40 mm. In another embodiment of the invention, the horizontal width of the dynamic optic is between about 30 mm and about 34 mm. In another embodiment of the invention, the horizontal width of the dynamic optics is about 32 mm. Thus, in certain embodiments of the present invention, the dynamic optic is shaped like an ellipse with a horizontal dimension wider than the vertical dimension.

6A-6C illustrate embodiments of dynamic optics. In the embodiment shown, the dynamic optic is elliptical and is between about 26 mm and about 32 mm wide. Various heights of dynamic optics are shown. 6A shows dynamic optics with a height of about 14 mm. 6B shows dynamic optics with a height of about 19 mm. 6C shows dynamic optics with a height of about 24 mm.

7A-7K illustrate a noxious astigmatism contour map comparing an embodiment of the present invention with existing state-of-the-art progressive addition lenses and low additional power progressive addition lenses and dynamic optics. Hazardous Astigmatism Power Map is a Visionix State of the Ait Power MapVM 2000 ^TM "High, the same equipment used by lens manufacturers in PAL manufacturing or design to measure and inspect their own PAL for both quality control and marketing specification purposes. Precision Lens Analyzer ". Embodiments of the present invention were simulated using low additional power PAL and spherical lenses. Spherical lenses have the same optical power as the activating dynamic optics of the provided optical power extending around the lens.

FIG. 7A compares an embodiment of the present invention comprising an Essilor Varilux Physio ^™ + 1.25D PAL and an Essilor Varilux Physio ^™ + 1.0OD PAL and + 0.25D dynamic optics producing a total additional power of + 1.25D. Figure 7B compares the Essilor Varilux Physio ^TM + 1.50D PAL and Essilor Varilux Physio ^TM PAL + 0.75D and 0.75D + embodiment of the present invention including a dynamic optics for generating a total add power of + 0.75D. FIG. 7C compares an embodiment of the present invention comprising an Essilor Varilux Physio ^™ + 1.75D PAL and an Essilor Varilux Physio ^™ + 1.00D PAL and + 0.75D dynamic optics producing a total additional power of + 1.75D. FIG. 7D compares an embodiment of the present invention comprising an Essilor Varilux Physio ^™ + 2.00D PAL and an Essilor Varilux Physio ^™ + 1.00D PAL and + 1.00D dynamic optics producing a total additional power of + 2.00D. FIG. 7E compares an embodiment of the present invention comprising an Essilor Varilux Physio ^™ + 2.00D PAL and an Essilor Varilux Physio ^™ + 0.75D PAL and + 1.25D dynamic optics producing a total additional power of + 2.00D. FIG. 7F compares an embodiment of the invention comprising an Essilor Varilux Physio ^™ + 2.25D PAL and an Essilor Varilux Physio ^™ + 1.00D PAL and + 1.25D dynamic optics producing a total additional power of + 2.25D. FIG. 7H compares an embodiment of the invention comprising an Essilor Varilux Physio ^™ + 2.50D PAL and an Essilor Varilux Physio ^™ + 1.25D PAL and + 1.25D dynamic optics producing a total additional power of + 2.50D. FIG. 7I compares an embodiment of the invention comprising an Essilor Varilux Physio ^™ + 2.50D PAL and an Essilor Varilux Physio ^™ + 1.00D PAL and + 1.50D dynamic optics producing a total additional power of + 2.50D. FIG. 7J compares an embodiment of the present invention comprising an Essilor Varilux Physio ^™ + 2.75D PAL and an Essilor Varilux Physio ^™ + 1.25D PAL and + 1.50D dynamic optics producing a total additional power of + 2.75D. FIG. 7K compares an embodiment of the invention comprising an Essilor Varilux Physio ^™ + 3.00D PAL and an Essilor Varilux Physio ^™ + 1.50D PAL and + 1.50D dynamic optics producing a total additional power of + 3.00D.

7A-7K clearly show a significant improvement of the method of the present invention over current state-of-the-art progressive addition lenses. The embodiments of the present invention shown in FIGS. 7A-7K present significantly less distortion, significantly less noxious astigmatism, even wider channel width and somewhat shorter for both low and high additional power compared to current state of the art PAL. Has a channel length. The method of the present invention can provide these remarkable improvements while allowing the user to see clearly at long, medium and near distances like a conventional PAL lens.

In the present invention, the dynamic optics need to deviate from the center vertically and in some cases horizontally with respect to the progressive additional area, depending on the wearer's pupil distance, the adjustment point and the dimensions of the cut frame eye-wire. It is considered more. In all cases, however, if the dynamic optics are off center for the progressive additional regions, the optical optics continue to communicate with the regions when the dynamic optics are activated. It should be noted that the vertical dimensions of the eye-wires or rims of the frame determine the amount of off center but in most cases.

The ophthalmic lens of the present invention enables light transmission of 88% or more. If the antireflective coating is used on both surfaces of the ophthalmic lens the light transmission will exceed 90%. The light efficiency of the ophthalmic lens of the present invention is 90% or more. Ophthalmic lenses of the invention can be coated with a variety of well known lens treatments such as, for example, antireflective coatings, anti-scratch coatings, cushion coatings, hydrophobic coatings and ultraviolet coatings. Ultraviolet coatings are applied to ophthalmic lenses or dynamic optics. In embodiments where the dynamic optics are liquid crystal based electro-active optics, the ultraviolet coating protects the liquid crystals from ultraviolet radiation which can damage the liquid crystals over time. It is also possible for the ophthalmic lens of the invention to be perforated to be bordered in the form required for the spectacle frame or for example to be mounted in the frameless frame.

The invention also provides an ophthalmic lens for all; It should be noted that contact lenses, intraocular lenses, corneal onlays, corneal inlays and spectacle lenses are considered.

Specific embodiments of the present invention will be described with reference to the following drawings:

1A shows an embodiment of a low additional power progressive addition lens with control points and progressive addition regions.

FIG. 1B shows a graph of optical power 130 taken along the cross section of the lens of FIG. 1A along the line AA axis.

2A illustrates an embodiment of the present invention with a low additional power progressive additional lens combined with a larger dynamic optic positioned such that the dynamic optic portion lies above the adjustment point of the lens.

FIG. 2B shows the combined lens of FIG. 2A with the combined optical power generated because the dynamic optics are in optical communication with the progressive additional region.

3A illustrates an embodiment of the present invention with a low additional power progressive additional lens combined with a larger dynamic optic positioned such that the dynamic optic portion lies above the adjustment point of the lens. 3A shows that optical power taken along the line of sight from the wearer's eye through the control point when the dynamic optics are inactive provides the wearer with accurate far vision.

3B shows the lens of FIG. 3A. 3B shows that optical power taken along the line of sight from the wearer's eye through the control point when the dynamic optic is activated provides the wearer with accurate mid-range focusing power.

3C shows the lens of FIG. 3A. 3B shows that optical power taken along the line of sight from the wearer's eye through the near-field area upon activation of dynamic optics provides the wearer with accurate near focusing power.

4A shows an embodiment of the invention with a low additional power progressive additional lens combined with a progressive optic larger than the channel and / or progressive optic located above the adjustment point of the lens.

4B shows the optical power provided by a fixed progressive additional surface or area taken along the line AA axis of FIG. 4A.

4C shows the optical power provided by the dynamic optics taken along the line AA axis of FIG. 4A upon activation.

4D shows the combined power of the dynamic electro-active optics and the fixed progressive additional region taken along the line AA axis of FIG. 4A. 4D shows that the top and bottom distortion blend regions of the dynamic electro-active optics are outside of both the control point and the progressive additional read region and channel.

5A illustrates an embodiment of the invention located below the adjustment point of an additional power progressive addition lens with low dynamic optics.

FIG. 5B shows the optical power taken along the line AA axis of FIG. 5A.

6A-6C illustrate various embodiments of dynamic optics size.

7A-7K illustrate a noxious astigmatism contour map comparing an embodiment of the present invention with existing state-of-the-art progressive addition lenses and low additional power progressive addition lenses and dynamic optics.

Claims (38)

A progressive additional region having a channel and having additional power therein; And Includes dynamic optics in optical communication with those having optical power upon activation, The dynamic optic has a top perimeter boundary located within about 15 mm of the fitting point. Ophthalmic lens with adjustment points for the user The ophthalmic lens of claim 1, wherein the additional power is less than a user's proximity staring distance additional power. The ophthalmic lens of claim 1, wherein the additional power is about 50% of the proximity staring distance additional power. The ophthalmic lens of claim 1, wherein the additional power is between about 30% and about 70% of the proximity staring distance additional power. The ophthalmic lens of claim 1, wherein the optical power is substantially equal to the user's proximity staring distance additional power when added to the additional power. The ophthalmic lens of claim 1, wherein the progressive additional region is located on a front surface of the lens. The ophthalmic lens of claim 1, wherein the progressive additional region is located on a back surface of the lens. The ophthalmic lens of claim 1, wherein the progressive additional region is embedded in the lens. The ophthalmic lens of claim 1, wherein the dynamic optic is located on a front surface of the lens. The ophthalmic lens according to claim 1, wherein the dynamic optic is located on the front and rear of the lens. The ophthalmic lens of claim 1, wherein the dynamic optic is embedded in the lens. The ophthalmic lens of claim 1 wherein the dynamic optic is an electro-active optic. The ophthalmic lens of claim 1, wherein the dynamic optic is an uneven lens. 2. The ophthalmic lens of claim 1, wherein the dynamic optic is a fluid lens. The ophthalmic lens of claim 1 wherein the dynamic optic is a movable dynamic optic having one or more moving components. The ophthalmic lens according to claim 1, wherein the dynamic optic is a gas lens. The ophthalmic lens according to claim 1, wherein the dynamic optic is a membrane lens having a deformable membrane. The ophthalmic lens of claim 1 wherein said additional power is between about +0.50 diopters and about +1.50 diopters. The ophthalmic lens of claim 1, wherein the optical power is between about +0.50 diopters and about +2.25 diopters. The ophthalmic lens of claim 1, wherein the dynamic optic has a width between about 24 mm and about 40 mm. The ophthalmic lens of claim 1, wherein the channel of the progressive additional region has a length between about 11 mm and about 20 mm. 2. An ophthalmic lens according to claim 1, wherein at least a portion of the upper peripheral boundary of the dynamic optic is located above the adjustment point of the lens. The ophthalmic lens of claim 1, wherein the upper peripheral boundary of the dynamic optic is located between about 0 mm and about half of the vertical length of the dynamic optic above the adjustment point of the lens. The method of claim 1, wherein the upper peripheral boundary of the dynamic optic is located between about 1/8 of the vertical length of the dynamic optic and about 3/8 of the vertical length of the dynamic optic above the adjustment point of the lens. Ophthalmic lens The ophthalmic lens of claim 1, wherein the dynamic lens is not activated until a user's eye passes over a top peripheral boundary of the dynamic optic. The ophthalmic lens of claim 1 further comprising a mixing zone coupled with the dynamic optics. The ophthalmic lens of claim 1, wherein the optical power comprises at least two optical powers. The ophthalmic lens of claim 1 wherein the optical power comprises a positive power and substantially no optical power. The ophthalmic lens according to claim 1, wherein the optical power is changeable. 2. An ophthalmic lens according to claim 1, wherein the dynamic optics can be activated and deactivated. The ophthalmic lens of claim 1, wherein the dynamic optic maintains a constant distance in the progressive additional region. 2. An ophthalmic lens according to claim 1, further comprising a sensor for controlling said optical power. 33. The ophthalmic lens of claim 32, wherein the sensor deactivates the dynamic optic when the user gazes over the medium distance. 33. The ophthalmic lens of claim 32, wherein the sensor activates the dynamic optics when the user gazes closer than the distance. The ophthalmic lens of claim 1, wherein the intermediate vision correction is provided to the user when the dynamic optic is activated when the user gazes through the control point. 2. An ophthalmic lens according to claim 1, wherein the distance vision correction is provided to the user when the user gazes through the control point when the dynamic optic is inactive. The ophthalmic lens according to claim 1, wherein the dynamic optic is off-centered with respect to the progressive additional region. The ophthalmic lens of claim 1 wherein the lens is formed from a semi-finished blank.

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