RU2792078C2 - Ophthalmic lenses containing elementary lenses for prevention and/or slowing down of myopia progression - Google Patents

Abstract

FIELD: medicine.

SUBSTANCE: ophthalmic lens for at least one of slowing down, containment, or prevention of myopia progression contains: a front convex surface; a rear concave surface; and an optical area including main far vision correction areas of the base sphere and elementary lenses with an additional optical force, which are myopic defocusing areas distributed between main far vision correction areas of the base sphere and adjacently to them. Main correction areas of the base sphere are made with the possibility of creation of a wave front, which is focused at one point along the main optical axis of the ophthalmic lens and on the eye retina. Elementary lenses with an additional optical force are made with the possibility of creation of non-coaxial wave fronts, which are focused in front of the retina along their own optical axis, which differs from the main optical axis. A combination of elementary lenses and main far vision correction areas is located with the possibility of provision of clear vision and myopic defocusing for all retinal areas. The ophthalmic lens is selected from a group consisting of glasses lenses, intraocular lenses, and corneal implanted/applied lenses.

EFFECT: use of the invention allows for an increase in the efficiency of treatment with enhancing impact of myopic defocusing, without affecting the image quality in the fovea.

10 cl, 15 dwg, 4 tbl

Description

1. Scope of the invention

The present invention relates to ophthalmic lenses, such as monofocal and/or astigmatic lenses, and more particularly to contact lenses, intraocular lenses, corneal implantable/onlay lenses and/or spectacle lenses designed to slow, halt or prevent the progression of myopia. The ophthalmic lenses of the present invention contain non-coaxial elementary lenses with a positive optical power, which at any distance during vergent movement, stop the progression of myopia throughout the central, near and far periphery of the retina to prevent and/or slow down the progression of myopia, while maintaining clear central vision.

2. Description of the prior art

Common diseases that lead to reduced visual acuity are myopia and hypermetropia, for which corrective lenses are prescribed in the form of glasses or hard or soft contact lenses. These diseases are essentially described as an imbalance between the length of the eye and the focus of the optical elements of the eye, with myopic eyes focusing in front of the retinal plane and hyperopic eyes focusing behind the retinal plane. Myopia usually develops because the axial length of the eye increases and becomes longer than the focal length of the optical components of the eye, i.e. the eye becomes too long. Hypermetropia usually develops because the axial length of the eye becomes too short compared to the focal length of the optical components of the eye, i.e. the eye does not grow enough.

Myopia is widespread throughout the world. The greatest problem associated with this disease is its possible progression to high myopia, for example more than 5 (five) diopters, which greatly affects the ability of a person to perform activities without the help of optical devices. High myopia is also associated with an increased risk of retinal disease, cataracts, and glaucoma.

Corrective lenses are used to change the overall focus of the eye in order to create a clearer image on the retinal plane by shifting the focus from in front of the retinal plane to correct myopia or from behind the retinal plane to correct hyperopia, respectively. However, the corrective approach for these diseases does not address the cause of the pathology, but is only prosthetic or intended only to eliminate the symptoms of this disease.

In most cases, the eyes are not simply myopic or hyperopic, but may also have more complex visual anomalies such as myopic astigmatism or hyperopic astigmatism. Astigmatic focus anomalies lead to the formation of an image from a point light source of two mutually perpendicular lines at different focal lengths along the two main meridians. In the above description, the terms "myopia" and "hyperopia" include simple myopia or myopic astigmatism and hypermetropia or hyperopic astigmatism, respectively.

Emmetropia describes a state of clear vision in which an object at optical infinity is in relatively sharp focus with the lens of the eye relaxed. In adults with normal or emmetropic eyes, light from both distant and near objects, as well as passing through the central or paraxial region of the aperture or entrance pupil, is focused by the cornea and lens inside the eye near the plane of the retina, where an inverted image is perceived. However, most normal eyes have been observed to show positive longitudinal spherical aberration, essentially in the region of approximately +0.50 diopters (D) for a 5 mm aperture, which means that rays passing through the aperture or pupil in its peripheral zone are focused at +0 .50 diopters in front of the retinal plane when the eye is focused at optical infinity. In this document, the value of "dptr" is the optical power, which is defined as the reciprocal of the focal length of the lens or optical system, expressed in meters, along the optical axis. In addition, as used herein, the term "additional power" is defined as an additional positive power that allows you to achieve clearer vision at close distances.

The spherical aberration of the normal eye is not permanent. For example, accommodation, i.e., a change in the optical power of the eye, which occurs mainly when the internal lens changes, leads to a change in the positive value of spherical aberration to negative.

Myopia usually results from excessive axial growth or elongation of the eye. It is now generally accepted, primarily as a result of animal research, that axial growth of the eye can be influenced by the quality and focus of the image on the retina. Experiments performed on animals of various species, using different experimental concepts, have shown that changes in image quality on the retina can lead to permanent and predictable changes in the growth of the eye.

In addition, retinal defocusing performed in chick and primate models with positive lenses (myopic defocus) or negative lenses (hyperopic defocus) is known to result in predictable changes in both direction and magnitude of eye growth corresponding to an increase in eye size to compensate for the created defocus. Emmetropization is a process in which the growth of the eye is self-adjusted to achieve optimal matching of the optics and axial length of the eye. It has been shown that changes in the length of the eye associated with optical blurring of the image were varied by changes in the growth of the sclera. Image blur created with positive lenses, which leads to myopic blur and reduces the growth rate of the sclera, entails hyperopic refractive errors. Image blur created with negative lenses that results in hyperopic blur and increases the rate of scleral growth leads to myopic refractive errors. It has been shown that such changes in eye growth due to defocusing of the retinal image are largely triggered by local retinal mechanisms, since changes in eye length still occur even with damage to the optic nerve, and it has been shown that the superimposition of defocus on local areas of the retina leads to a change in growth. eyes precisely on that particular area.

In humans, there is both indirect and direct evidence that supports the view that retinal image quality can influence eye growth. A large number of different eye conditions, all of which lead to visual impairments such as droopy eyelids, congenital cataracts, corneal clouding, vitreous hemorrhage, and other eye diseases, have been found to be associated with abnormal eye growth in people at a young age, which suggests that relatively large changes in retinal image quality do affect the growth of the human eye. The hypothesis of the effect of less noticeable changes in the image on the retina on the growth of the human eye was also based on optical errors in the focusing system of the human eye during work requiring visual strain, which could stimulate the growth of the eye and the development of myopia.

All published approaches aimed at slowing the progression of myopia are based on the introduction of coaxial regions of positive optical power, such as bifocal and/or multifocal, which compete with the main lens distance correction region and lead to a trade-off between distance visual acuity and contrast sensitivity.

Accordingly, there is a need to achieve greater efficacy in reducing and/or slowing the progression of myopia, which enhances the effect of myopic blurring without affecting the image quality in the fovea.

SUMMARY OF THE INVENTION

The positive defocus elementary lens ophthalmic lens of the present invention overcomes the limitations of the prior art by providing better distance vision correction without compromising visual acuity and contrast sensitivity.

In accordance with one aspect, the present invention relates to an ophthalmic lens for at least one of slowing, curbing or preventing the progression of myopia. An ophthalmic lens comprising an anterior convex surface, a posterior concave surface, an optical zone including the main distance vision correction zones of the base sphere and a plurality of elementary lenses with additional optical power distributed between the main distance vision correction zones of the base sphere and adjacent to them, and the main correction zones the base spheres create a wavefront that is focused at one point along the main optical axis of the ophthalmic lens and on the retina of the eye, and a plurality of elementary lenses with additional optical power create non-coaxial wavefronts that are focused in front of the retina along their own optical axis, which differs from the main optical axis axis, and the combination of elementary lenses and the main zones of distance vision correction is located with the ability to provide clear vision and myopic defocusing for all areas of the retina, while the ophthalmic lens is selected from the group consisting of och oval lenses, intraocular lenses and corneal implanted/fixed lenses.

In this document, the optical power for coaxial optical elements or optical elements with a common axis is defined in the usual way as the reciprocal of the focal length along the optical axis of the entire lens. In this document, the optical power for non-coaxial optical elements or optical elements with a separate axis is defined as the reciprocal of the focal length along the optical axis of a single optical element and is also called "local optical power". Defocus, whether coaxial or non-coaxial, is the difference in optical power between the ideal focal length and the focal length of the optical element.

One way to improve treatment efficiency is to develop non-coaxial optical elements that enhance the effect of myopic blurring in eye growth regulation without affecting image quality in the fovea. With these designs, for each diopter of myopic defocus, image quality on the retina degrades less in the fovea, and the focus of the sagittal and tangential powers is in front of the retina. Ophthalmic lens design with zero or negative power for distance vision correction that provides optimal refractive correction, along with small islands of positive defocus, non-coaxial elementary lenses (myopic defocus zones) with local power values ranging from +1.00 to +30, 00 diopters, optimally spaced and covering twenty (20) to eighty (80) percent of the optic zone and/or central pupillary area to deliver positive foci of light in front of the retina, with low impact on image quality in the fovea when slowed down the rate of progression of myopia. The optimal pattern may comprise a circular or hexagonal design, a radial design, a uniform or irregularly spaced design, or any suitable design, including combinations of the above designs.

The ophthalmic lenses of the present invention are capable of signaling myopia arrest, ie myopic blurring, regardless of pupil diameter and with little or no visual impact. Non-coaxial plus-power elementary lenses, incorporating the contact lenses of the present invention, overcome the limitations of the prior art by providing comparable or better distance vision correction than monofocal lenses and/or astigmatic lenses with conventional power addition for controlling myopia progression.

The present invention is an ophthalmic lens for at least one of slowing down, curbing or preventing the progression of myopia. An ophthalmic lens within its main optical zone includes many non-coaxial zones with positive optical power. Each non-coaxial zone with a positive optical power is located adjacent to the distance vision correction zone. This design provides at least a distance correction zone and a non-coaxial positive power zone at any aperture/pupil size and viewing conditions. The non-coaxial zones have a local refractive power different from the coaxial refractive power of the base sphere and/or the refractive power of the cylinder, which perform the correction of the main refractive error. The ratio of the total area of the non-coaxial distance vision correction zones to the positive power zone is 80:20 to 20:80 and preferably 40:60 to 60:40. The size of non-coaxial zones with positive optical power varies from 0.45 to 1 mm in diameter. It is not necessary that the entire optical zone consists of non-coaxial zones with positive optical power, and it can be limited to the field of view of the pupil. For pediatric patients, typically, pupil size is in the range of 4 to 8 mm in mesopic terms. In addition, for optimal vision in the central region of the lens in the optical zone, there may be no non-coaxial zones with positive power, which will provide only basic distance vision correction.

The present invention also includes a method for at least one of slowing, curbing, or preventing the progression of myopia by providing an ophthalmic lens having a plurality of concentric, non-coaxial, positive power zones on its primary optical zone. The zones alternate between the main coaxial concentric distance correction zones and non-coaxial concentric zones with positive optical power. The local optical power of non-coaxial circular zones differs from the local optical power of coaxial concentric zones for distance vision correction. The ratio of the total area of distance vision correction to the non-coaxial positive power circular area is from about 80:20 to about 20:80. The space between non-coaxial positive power zones or elementary lenses can be used to create a zero focal plane or adjusted to provide optimal correction for the subject.

The prevalence of myopia, including high myopia, is increasing worldwide at an extraordinary rate. The contact lens design of the present invention provides a simple, economical and effective means and method for preventing and/or slowing the progression of myopia, which can help slow the rate of progression of high myopia. The lenses of the present invention are made from the same material as currently manufactured lenses using the same manufacturing processes. Only the surfaces of the mold will be changed in such a way as to introduce additional optical power for the lenses.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other features and advantages of the present invention will become apparent from the following more detailed description of the preferred embodiments of the invention shown in the accompanying drawings.

Fig. 1 is a schematic representation of a 0 diopter wavefront passing through the eye to the retina.

Fig. 2 is a schematic representation of the +10.00 diopter wavefront passing through the eye to the retina.

Fig. 3 is a schematic representation of 0 diopters with +10.00 diopters coaxial wavefront sections passing through the eye to the retina.

Fig. 4 is a schematic representation of 0 diopters with +10.00 diopters non-coaxial wavefront sections passing through the eye and focused in front of the retina and towards the fovea.

Fig. 5 is a schematic representation of 0 diopters with +10.00 diopters non-coaxial wavefront sections passing through the eye and focused in front of the retina but symmetrically away from the fovea.

Fig. 6 is a schematic representation of 0 diopters with sections of a non-coaxial +10.00 diopter wavefront passing through the eye and focused in front of the retina, but asymmetrically from the fovea.

Fig. 7 is a schematic representation of 0 diopters with sections of a non-coaxial +10.00 diopter wavefront passing through the eye and focused in front of the retina but symmetrically from the fovea without intersecting the coaxial main optical axis.

Fig. 8 is a schematic representation of 0 diopters with sections of a non-coaxial +10.00 diopter wavefront passing through the eye and focused in front of the retina but asymmetrically from the fovea without intersecting the coaxial main optical axis.

Fig. 9 is a schematic of a first set of exemplary non-coaxial lens configurations in accordance with the present invention.

Fig. 10 is a schematic diagram of a second set of exemplary non-coaxial lens configurations in accordance with the present invention.

Fig. 11 is a simulated retinal image in a diffraction-limited eye model in terms of image quality and visual performance as a function of elementary lens size and additional power.

Fig. 12A is a schematic plan view of a contact lens in accordance with the present invention.

Fig. 12B is a schematic side view of a contact lens in accordance with the present invention.

Fig. 13 is a schematic representation of glasses in accordance with the present invention.

Fig. 14 is a schematic representation of an intraocular lens in accordance with the present invention.

Fig. 15 is a schematic representation of a corneal implantable/onlay lens in accordance with the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Experiments have shown that the eyes respond to hypermetropic defocusing, which results in axial elongation, so providing higher positive gain in the central retina should slow the progression of myopia. However, simply providing higher positive gain in the central retina can have a negative impact on vision. Accordingly, an ophthalmic lens, such as a contact lens with a negative primary power that provides optimal refractive correction for distance vision, in combination with small areas or islands of positive power (elemental lenses) arranged in a specific pattern to deliver positive foci of light to the area in front of the retina , will provide myopic defocusing, which will slow down the progression of myopia without affecting visual acuity and contrast sensitivity.

The present invention is an ophthalmic lens for at least one of slowing down, curbing or preventing the progression of myopia. An ophthalmic lens within its main optical zone includes a plurality of non-coaxial zones with positive optical power. Each non-coaxial zone with a positive optical power is located adjacent to the distance vision correction zone. This design provides at least a distance correction zone and a non-coaxial positive power zone in all viewing conditions. The non-coaxial zones have a local optical power that is different from the optical power of the main sphere and/or the optical power of the cylinder. The ratio of the total area of the non-coaxial distance vision correction zones to the positive power zone is 80:20 to 20:80 and preferably 40:60 to 60:40. The size of non-coaxial zones with positive optical power varies from 0.45 to 1 mm in diameter. It is not necessary that the entire optical zone consists of non-coaxial zones with positive optical power, and it can be limited to the field of view of the pupil. For pediatric patients, typically, pupil size is in the range of 4 to 8 mm in mesopic terms. In addition, for optimal vision, there may be no non-coaxial zones of myopic defocus in the central 2 mm of the optical zone of the zone lens, which will provide only basic distance vision correction.

On FIG. 1 shows a flat wavefront 101 (0 diopter defocus) that travels through the eye 100 to the retina 102 of the eye 100. As shown, assuming the eye has zero wavefront aberrations, the wavefront is focused at a single point 104 along the optical axis 106. Given, that this is a representation of the wavefront error 0, the focal point 104 is located on the fovea, which is located in the center of the macula of the retina 102. The fovea is the region of the retina responsible for clear central vision. For comparison, in Fig. 2 shows a +10.00 diopter wavefront 201 that travels through the eye 200 to the retina 202 of the eye 200. As shown, the wavefront is focused at one point 204 along the optical axis 206 in front of the retina 202, as would be expected with a defocus of +10.00 diopter. In both cases, and similarly to traditional spherical optical elements, the optical elements of the lenses are made with a main optical axis through which the light rays are directed to one point; namely, to the point of focus. The magnitude of the spherical wavefront error determines the location of the focal point at or in front of the fovea of the retina, as shown in FIG. 1 and 2, respectively. These two figures are used to establish the basic parameters/principles on which the description of the present invention is based; however, it should be understood that although only spherical refractive errors are illustrated for ease of explanation and description, the present invention is equally applicable to toric lenses that include cylindrical powers on a particular axis. In addition, as discussed in more detail subsequently, elementary lenses may include optical power and cylinder axis, and they may also contain more complex optical structures such as higher order aberrations.

On FIG. 3 shows a flat (0 diopter defocused) wavefront 301 and wavefronts 303 of +10.00 diopter defocused coaxial elementary lenses that pass through eye 300 to retina 302 of eye 300. As shown in the figure, the 0 diopter main sphere wavefront is focused into one point 304 along the main optical axis 306. Considering that this is a wavefront error representation of 0, the focus point 304 is located on the fovea 302 of the retina. as would be expected with an anomaly of +10.00 diopters. It should be noted that elementary lenses are the small +10.00 diopter wavefront section shown in FIG. 2, and thus the light rays 303 from each elementary lens are still directed in the same direction as the +10.00 diopter total wavefront. Concentric or aspherical multifocal lens designs typically also have both primary power and secondary power that share a common axis. Typically, in these applications, to maintain optimal image quality, the additional power is limited to +1.00 to +3.00 diopters. Therefore, the additional high order power required by the present invention will not work with this elementary lens design, but rather with a non-coaxial design, as detailed hereafter.

On FIG. 4 shows a flat wavefront from a flat main spherical lens 401 and a wavefront from non-coaxial elementary lenses 403 +10.00 diopters that pass through the eye 400 to the retina 402 of the eye 400. As shown in the figure, the flat wavefront 401 is focused at a single point 404 along the main optical axis 406. Considering that this is a 0 diopter wavefront error representation, the focus point 404 is located on the fovea 402 of the retina. in front of retina 402, as would be expected with a +10.00 diopter lens, but towards the fovea. Unlike Fig. 3, elementary lenses now have focal points 408 and 410 that are not aligned with the original common optical axis 406 and therefore are not coaxial. It is important to note that the wavefront of +10.00 diopter spherical elementary lenses is focused in front of the retina 402 along its own axis, with the center of each elementary lens having 0-th wavefront anomaly, and on either side of its center point having an opposite slope and therefore , still points in the same direction as the reference center of the sphere; namely, in the central fossa.

On FIG. 5 shows a flat wavefront from a flat main spherical lens 501 and a wavefront from non-coaxial elementary lenses 503 +10.00 diopters that pass through the eye 500 to the retina 502 of the eye 500. As shown in the figure, the flat wavefront is focused at a single point 504 along main optical axis 506. Considering that this is a 0 diopter wavefront error representation, the focal point 504 is located on the fovea 502. Each of the +10.00 diopter defocused wavefronts 503 from the non-coaxial elementary lenses is focused at one point 508 and 510 in front of retina 502, as expected with a +10.00 diopter lens, but symmetrical from the fovea. As in the previous case, elementary lenses now have focal points 508 and 510 that do not coincide with the original common optical axis 506 and are therefore not coaxial. It is important to note that the wavefront of elementary spherical lenses is focused along its own axis and its slopes are different from those of the elementary lenses of FIG. 4, allowing the centers to be directed symmetrically away from the fovea, yet its local focus point of +10.00 diopters is located in front of the retina 502. In addition, the axes of the elementary lenses converge symmetrically to the central axis 506 of the main sphere wavefront. In other words, elementary lenses 512 direct light rays through the original common optical axis 506 to the peripheral sections of the retina 502 equidistant from the fovea, which is a symmetrical design.

On FIG. 6 shows a flat wavefront from a flat main spherical lens 601 and a wavefront from +10.00 diopter non-coaxial elementary lenses 603 that pass through the eye 600 to the retina 602 of the eye 600. As shown in the figure, the flat wavefront is focused at a single point 604 along main optical axis 606. Given that this is a 0 diopter wavefront error representation, the focus point 604 is located on the fovea 602 of the retina. retina 602, as expected with a +10.00 diopter lens, but asymmetrically from the fovea. As in the previous case, elementary lenses now have focal points 608 and 610 that do not coincide with the original common axis 606 and are therefore not coaxial. It is important to note that the wavefront of the elementary spherical lenses is focused along its own axis and its slopes are different from those of the elementary lenses in FIG. 4, allowing the centers to be directed asymmetrically away from the fovea, but with its local focus point of +10.00 diopters located in front of the retina 602. In addition, the axes of the elementary lenses converge asymmetrically in front of the wavefront focal point of the central main sphere. In other words, elementary lenses direct light rays through the original common optical axis to the peripheral sections of the retina 602, at different distances from the fovea, which is a non-symmetrical design.

On FIG. 7 shows a flat wavefront from a flat main spherical lens 701 and a wavefront from +10.00 diopter non-coaxial elementary lenses 703 that pass through the eye 700 to the retina 702 of the eye 700. As shown in the figure, the flat wavefront is focused at a single point 704 along the main optical axis 706. Considering that this is a 0 diopter wavefront error representation, the focus point 704 is located on the fovea 702 of the retina. retina 702, as expected with a +10.00 diopter lens, but symmetrical from the fovea without crossing the main optical axis 706. As in the previous case, elementary lenses now have focal points 708 and 710 that do not coincide with the original common axis 706 and therefore are not coaxial. It is important to note that the wavefront of the elementary spherical lenses is focused along its own axis and its slopes are different from those of the elementary lenses in FIG. 4, allowing the centers to be directed symmetrically away from the fovea, yet its local focus point of +10.00 diopters is located in front of the retina 702. In addition, the elementary lens axes converge symmetrically behind the main sphere wavefront focal point 704. In other words, elementary lenses direct light rays that do not cross the original common optical axis 706, but are still directed towards peripheral sections of the retina 702 that are equidistant from the fovea, which is a symmetrical design.

On FIG. 8 shows a flat wavefront from a flat main spherical lens 801 and a wavefront from a non-coaxial elementary lens 803 +10.00 diopters that pass through the eye 800 to the retina 802 of the eye 800. As shown in the figure, the flat wavefront is focused at one point 804 along main optical axis 806. Given that this is a 0 diopter wavefront error representation, the focus point 804 is located on the fovea 802. Each of the +10.00 diopter defocused wavefronts 803 from the non-coaxial elementary lenses is focused at one point 808 and 810 in front of retina 802, as expected with a +10.00 diopter lens, but asymmetrically from the fovea, not crossing the main optical axis 806. As in the previous case, elementary lenses now have focal points 808 and 810 that do not coincide with the original common axis 806 and therefore are not coaxial. It is important to note that the wavefront of the elementary spherical lenses is focused along its own axis and its slopes are different from those of the elementary lenses in FIG. 4, allowing the centers to be directed asymmetrically away from the fovea, yet its local focus point of +10.00 diopters is located in front of the retina 802. In addition, the axes of the elementary lenses converge asymmetrically behind the main sphere wavefront central axis 806. In other words, elementary lenses direct light rays that do not cross the original common optical axis 806 within the eye, but are still directed towards peripheral sections of the retina 802 that are at different distances from the fovea, which is a non-symmetrical design.

It is important to note that combinations of the configurations described above are also possible, such as an optical configuration that includes a main sphere with zero wavefront error, elementary lenses that direct beams through the main optical axis, and elementary lenses that direct beams to the same side. main optical axis. In addition, elementary lenses can be easily created in a non-spherical shape. This would make it possible to fine-tune and control the distribution of rays emerging from elementary lenses and incident on the retina. One example would be the creation of elementary lenses with local astigmatism corresponding to their angular position. The degree of astigmatism can be adjusted to change the width of the retinal blur in the form of a "ring" around the fovea.

Contact lenses are lenses that are placed directly on the eye. Contact lenses are medical devices and may be used for vision correction and/or for cosmetic or other therapeutic reasons. Contact lenses have been used commercially to improve vision since the 1950s. The first contact lenses were made or made from hard materials, such lenses were relatively expensive and fragile. In addition, these early contact lenses were made from materials that did not allow sufficient oxygen to pass through the contact lens to the conjunctiva and cornea, potentially resulting in a number of adverse clinical effects. Although such contact lenses are still in use today, they are not suitable for all patients due to the low level of initial comfort. Further developments in this field have led to the creation of hydrogel-based soft contact lenses, which are extremely popular and widely used today. Currently available silicone hydrogel contact lenses combine the advantages of silicone, which has exceptionally high oxygen permeability, with the proven comfort and clinical performance of hydrogels. As such, such silicone hydrogel contact lenses have higher oxygen permeability values and are substantially more comfortable to wear than contact lenses made from prior hard materials. On the other hand, rigid gas permeable contact lenses are made from polymers containing siloxane, but are more rigid than soft contact lenses, allowing them to retain their shape and make them more durable.

Currently available contact lenses remain an economically effective means of correcting vision. Thin plastic lenses are worn on the cornea of the eye to correct visual defects, including myopia (or nearsightedness), hypermetropia (or farsightedness), astigmatism, i.e., the toricity of the cornea, and senile farsightedness, i.e., loss of the ability of the lens to accommodate. There are different shapes of contact lenses available that are made from different materials and provide different functionalities. Soft contact lenses for daily wear are typically made from soft polymeric materials bonded to water for oxygen permeability. Daily wear soft contact lenses can be daily disposable lenses or extended wear disposable lenses. One-day disposable contact lenses are usually worn for one day and then discarded, while long-wear disposable contact lenses are usually worn continuously for up to thirty days. Colored soft contact lenses use different materials to provide different functionality. For example, tinted contact lenses use a slight tint to make it easier for the wearer to find a dropped contact lens; tinted contact lenses have a clear or translucent tint that can enhance the wearer's natural eye color; colored tinted contact lenses have an opaque tint that can change the color of the wearer's eyes, and light-filtering tinted contact lenses can enhance certain colors while muting others. Bifocal and multifocal contact lenses are specially designed for patients suffering from presbyopia and are available in both soft and hard contact lenses. Toric contact lenses are specially designed for patients with astigmatism and are also available in both soft and hard versions. Combination lenses are also available that combine various aspects of the above, such as hybrid contact lenses.

In accordance with the present invention, elemental lens configurations are designed for ophthalmic lenses that provide foveal vision correction and have myopic blur in the near and far periphery of the retina to reduce or stop the eye's growth signal with little or no impact on primary vision. The contact lenses of the present invention may be spherical lenses or toric lenses. On FIG. 12A and 12B show an example of a contact lens 1200 that may be used in accordance with the present invention. On FIG. 12A is a plan view of the lens 1200, and FIG. 12B is a side view of the lens 1200. The contact lens 1200 includes an anterior convex surface 1202 and a posterior concave surface 1204. The optic zone 1206 includes optics 1208 for basic distance vision correction and a plurality of non-coaxial elementary lenses 1210 with high power addition to create myopic defocus for treatment of myopia progression. The ratio of the total area of optical elements 1208 for basic distance vision correction to the area of non-coaxial elementary lenses 1210 can vary from 20:80 to 80:20. Elementary lenses 1210 may be formed on the front convex surface 1202 or rear concave surface 1204. Preferably elementary lenses 1210 are formed on the front convex surface 1202. Contact lens 1200 also includes a peripheral zone 1212.

On FIG. 9 shows six exemplary embodiments of non-coaxial elementary lens configurations for a pupil aperture of 5.5 mm, in which the ratio of distance correction area to plus gain area or fill factor varies from twenty (20) to sixty (60) percent, and the value of plus gain varies. +2.50 diopters to +20.0 diopters. In these examples, elementary lens sizes 900 are 0.45 mm, 0.62 mm, and 0.77 mm for 20, 40, and 60 percent fill factors, respectively. The distance between the centers of elementary lenses remained constant at 0.88 mm. The transparent center diameter also remained constant at 2.00 mm. It is important to note that any suitable design of elementary lenses 900 may be used. In addition, any suitable shape and size may be used for elementary lenses 900, such as circular, hexagonal, concentric rings, or even radial zones ranging in size from 0.5 to 1.1 mm. Table 1 below lists the configuration options for the above examples.

Table 1

configuration example no. Transparent center diameter (mm) Pupil aperture (mm) Filling ratio (%) Distance between elementary lenses (mm) Refraction for distance vision correction (dptr) Additional optical power (dptr) (myopic power) 1 2.0 5.5 20 0.88 0.00 +10 2 2.0 5.5 40 0.88 0.00 +2.5 3 2.0 5.5 40 0.88 0.00 +5 4 2.0 5.5 40 0.88 0.00 +10 5 2.0 5.5 40 0.88 0.00 +20 6 2.0 5.5 60 0.88 0.00 +10

Information on visual performance and Weber contrast sensitivity for the above non-coaxial elementary lens configurations relative to better spherical correction and compared to conventional +3.00 diopter spherical lens, +3.00 diopter dual zone bifocal lens, or concentric ring bifocal lens with an additional optical power of +2.00 diopters is given in Table 2 below. In all cases, the configuration of elementary lenses with non-coaxial optical elementary lenses resulted in less loss of visual acuity and loss of Weber contrast sensitivity compared to conventional coaxial optical approaches such as dual-zone and concentric bifocal lenses. Contrast is essentially the difference in illuminance/brightness that makes an object or objects in the field of view distinguishable, and Weber's contrast sensitivity is essentially the eye's detection threshold between object illuminance and background illuminance.

table 2

Configuration type Pupil fill factor 5.5 mm Additional optical power / hyperopic power (dptr) VSOTF Elementary lens size Visual acuity loss logMAR Mean/SD (N=5) Loss of contrast sensitivity according to Weber
Average/SD
(N=5) +3.00 diopters regular sphere 100% N/A 0.001 N/A 0.81±0.06 N/A Concentric bifocal 50% 2.0 N/A N/A 0.07 ± 0.02 0.04±0.02 Dual zone 85% 3.0 N/A N/A 0.08±0.01 0.05±0.01 Example 1 20% 10.0 0.6332 0.02±0.01 0.02 ± 0.02 Example 2 40% 2.5 0.5375 0.02±0.04 0.01 ± 0.01 Example 3 40% 5.0 0.5277 0.03±0.04 0.03±0.02 Example 4 40% 10.0 0.5083 0.04±0.04 0.03±0.01 Example 5 40% 20.0 0.4952 0.05±0.05 0.03±0.01 Example 6 60% 10.0 0.3720 0.04±0.02 0.02 ± 0.02

In accordance with another embodiment of the present invention in FIG. 10 shows a variant of the optical configuration with and without a transparent central zone while maintaining a constant percentage fill factor, additional optical power and elementary lens size. As shown in the figure, in the optical design with a transparent central zone 1000, the location of the elementary lenses 1002 in such a zone is not provided. The configuration parameters and the calculated visual performance (VSOTF) for each of the configuration examples are given in Table 3 below.

The Strehl number based on optical transfer function (VSOTF) is a widely used measure of visual performance that can be directly derived from wavefront aberrations. It indicates how the image quality on the retina is affected by the optical elements of the eye and other aberrations caused by various types of additional visual aids (eg glasses or contact lenses, etc.). The extended value of VSOTF is given by the following equation:

,

,

обозначает дифракционно-ограниченную оптическую передаточную функцию,

- функция нейронной контрастной чувствительности, а

-координаты пространственной частоты.Where

denotes the diffraction-limited optical transfer function,

is the function of neural contrast sensitivity, and

- spatial frequency coordinates.

Table 3

configuration example no. Transparent center diameter (mm) Pupil aperture (mm) Filling ratio (%) Distance between elementary lenses (mm) Refraction for distance vision correction (dptr) Additional optical power (dptr) (myopic power) VSOTF 1 N/A 5.5 60 0.88 0.00 +10 0.1683 2 2 5.5 60 0.88 0.00 +10 0.3720 3 N/A 5.5 40 0.88 0.00 +20 0.3940 4 2 5.5 40 0.88 0.00 +20 0.4952

In accordance with another embodiment of the present invention in FIG. 11 shows simulated retinal images in a diffraction-limited eye model in terms of image quality and visual performance as a function of elementary lens size 1100 and additional power. Table 4 below lists the configuration parameters and calculated visual performance for each of the configurations. It can be seen from the data in Table 4 that the additional optical power has a smaller effect on VSOTF than the size of elementary lenses. Accordingly, optimal design parameters may include a high degree of additional power to improve treatment efficiency, a small elemental lens size, and a clear center.

Table 4

configuration example no. Pupil aperture (mm) Filling ratio (%) Elemental lens diameter (mm) Additional optical power (dptr) VSOTF Additional optical power (dptr) VSOTF Additional optical power (dptr) VSOTF 1 5.5 40 0.9 +5 0.3037 +10 0.3036 +20 0.3023 2 5.5 40 0.8 +5 0.3715 +10 0.3526 +20 0.3499 3 5.5 40 0.7 +5 0.3921 +10 0.3795 +20 0.3720

It is important to note that while the exemplary embodiments described herein refer to contact lenses that comprise elemental lenses having the same local power, whether +1.00 D or +30.00 D, it is possible to implement contact lenses containing elemental lenses of different optical powers. . For example, a contact lens may comprise elemental lenses with a local power of +2.00 diopters in one area and +10.00 diopters or +20.00 diopters in another area. In still other embodiments, the local optical powers may be changed alternately with neighboring elementary lenses. As such, any suitable combination of local optical powers can be used.

It is also important to note that the exemplary embodiments described here relate to contact lenses that can slow the progression of myopia. Such elementary lenses contain a base sphere of zero or negative optical power for distance vision correction and non-coaxial elementary lenses with positive additional optical power for the formation of myopic blur. It is also possible to implement contact lenses for hyperopic subjects with reversed polarity. In such lenses, the basic spherical correction is a positive-magnification refractive correction, and non-coaxial elementary lenses have a negative optical power, which allows the formation of hyperopic blur, leading to emmetropia.

It is important to note that the term "ophthalmic lens" is a broader concept than just contact lenses. Ophthalmic lenses include corrective lenses. Corrective lenses are commonly referred to as glasses. Corrective lenses or spectacles typically include two lenses secured by a frame configured to secure the lenses at an appropriate distance from the wearer's eyes. On FIG. 13 shows an exemplary pair of eyeglasses 1300. As noted above, exemplary eyeglasses 1300 comprise two lenses 1302 that are secured in a frame 1304. Ophthalmic lenses also include intraocular lenses or IOLs. Intraocular lenses are medical devices that are implanted into the eye to replace the lens of the eye as part of cataract treatment. After reaching a certain level of opacity, the lens of the eye is removed and the IOL is replaced. In rare cases, subjects can be born without a lens and the IOL is implanted without the need to remove the existing opaque lens. After removal of the lens of the eye, the pseudophakic IOL provides the same light focusing function as the lens. A phakic IOL can be used as part of refractive surgery to change the power of the eye as a treatment for myopia. This type of IOL is placed over the natural lens of the eye. On FIG. 14 shows an example of an IOL 1400. An exemplary IOL 1400 includes a lens 1402 and two support members 1404 that hold the lens 1402 in the correct position within the eye's capsular sac or eye capsule. Ophthalmic lenses also include corneal implant/fixed lenses. A corneal implantable/onlay lens is a medical device that is surgically implanted into the corneal intrinsic layer, usually to treat presbyopia. On FIG. 15 shows an exemplary corneal implantable/applied lens 1500 in the cornea of an eye 1502. The optics of the present invention may be incorporated into any of the ophthalmic lenses described herein.

Although the embodiments shown and described are considered to be the most practical and preferred, those skilled in the art will recognize the possibility of deviating from the described and shown established method configurations that may be used without departing from the spirit and scope of the present invention. The present invention is not limited to the specific structures described and illustrated, but should be considered in conjunction with all modifications within the scope defined by the appended claims.

Claims (13)

1. An ophthalmic lens for performing at least one of slowing down, curbing or preventing the progression of myopia, comprising: front convex surface; back concave surface; And an optical zone, including the main zones of correction of distant vision of the base sphere and elementary lenses with additional optical power, which are zones of myopic defocusing and distributed between the main zones of correction of far vision of the base sphere and adjacent to them, moreover, the main zones of correction of the base sphere are made with the possibility of creating a wave front, which is focused at one point along the main optical axis of the ophthalmic lens and on the retina, and these elementary lenses with additional optical power are made with the ability to create non-coaxial wave fronts that are focused in front of the retina along their own optical axis, which differs from the main optical axis , moreover, the combination of elementary lenses and main distance vision correction zones is located with the ability to provide clear vision and myopic defocusing for all areas of the retina, while the ophthalmic lens is selected from the group consisting of from spectacle lenses, intraocular lenses and corneal implantable/fixed lenses. 2. An ophthalmic lens according to claim 1, wherein the elemental lenses provide additional optical power in the range of +1.00 to +30.00 diopters. 3. Ophthalmic lens according to claim 1, in which elementary lenses with additional optical power occupy from 20 to 80 percent of the optical zone. 4. An ophthalmic lens according to claim 1, in which elementary lenses with additional optical power are configured to direct light through the main optical axis of the lens. 5. An ophthalmic lens according to claim 1, in which elementary lenses with additional optical power are configured to direct light to one side of the main optical axis of the lens. 6. An ophthalmic lens according to claim 1, in which elementary lenses with additional optical power are configured to direct light symmetrically from the fovea of the patient's retina. 7. An ophthalmic lens according to claim 1, in which elementary lenses with additional optical power are configured to direct light asymmetrically from the fovea of the patient's retina. 8. The ophthalmic lens of claim. 1, in which elementary lenses with additional optical power are configured to create myopic blur around the fovea of the patient's retina. 9. An ophthalmic lens according to claim 1, wherein elementary lenses with additional optical power are formed on the anterior convex surface. 10. An ophthalmic lens according to claim 1, wherein elementary lenses with additional optical power are formed on a posterior concave surface.

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