Human eyes see color via cone cells which are located in a 0.3 mm2 spot of the retina near the back of the eye called the fovea centralis. There are three types of cone cells commonly referred to as blue, green and red photoreceptor cells. There are six to seven million cone cells in a human eye of which, 64% are red sensitive, 33% are green sensitive and 3% are blue sensitive.
Color vision deficiency (CVD) is caused when one or more of the cone types are faulty or absent due to mutation. This causes the brain to receive incomplete or incorrect information that prevents distinguishing between different colors. The type of CVD depends on the type of faulty or missing cone cell. Protanomaly results from the sensitivity of red cone cells being shifted to a shorter wavelength. This type of CVD affects 1.08% of males and 0.03% of females. Deuteranomaly occurs when the sensitivity of green cone cells is shifted to a longer wavelength. This is the most common form of CVD and affects 4.63% of males and 0.36% of females. In tritanomaly, the blue cone is displaced. This type of CVD is uncommon and affects only 0.0002% of males. If a cone is missing, the patient is diagnosed as having dichromacy, which is classified into three types:
“Normal” color vision is trichromatic, with color being created using all three different types of cones with the activation level in all three cones allowing the brain to determine the color. When light of a specific wavelength enters the eye, it excites the cones cells to a known activation level, and the combined signal from the different types of cone cells is analyzed by the brain and the color is observed. For example, when light of a wavelength of 520 nm is observed by normal individuals, the cones are activated at different levels: 0% for blue, 90% for green, and 55% for red. However, for protanomaly, the activation of the red cone cells to stimulation by 520 nm light is increased to 75% and for deuteranomaly, the activation of green cone cells is lowered to 60%. This causes the red and green cones to be activated to similar levels in protanomaly and deuteranomaly which results in the wrong color being perceived.
Despite the fact that many individuals have adapted to live with CVD, this condition affects them in many ways. In many countries, people who have CVD are not allowed to drive as some may not distinguish between the different colors of traffic lights and road signs. Suffering from CVD also prohibits individuals from entering some professions such as pilot or firefighter due to safety concerns over their visual disadvantage.
According to one or more aspects of the present disclosure, a lens of a set of glasses includes a tinted region containing at least one selected from a list consisting of a first dye configured to absorb at least 50% of incident light in a spectral band between 480 nanometers to 500 nanometers and a second dye configured to absorb at least 50% of incident light in a spectral band between 550 nanometers to 580 nanometers. In some embodiments the region includes the whole lens. In other embodiments the region includes a layer within the lens.
According to one or more aspects of the present disclosure, a process of forming an ophthalmic contact lens using an additive manufacturing process includes the steps providing a first liquid resin solution, forming the contact lens from the first liquid resin solution using an additive manufacturing process and curing the first liquid resin solution by exposure to ultraviolet light, dipping the contact lens formed by the additive manufacturing process into a second liquid resin solution, and curing the second liquid resin solution by exposure to ultraviolet light.
A contact lens that may be used to treat color vision deficiency (CVD) is described herein. As illustrated in
The tinted region 12 includes a dye that is configured to block at least 50%, and preferably 50to 100%, of incident light in the 480-500 nanometer wavelength range to treat blue-yellow color blindness (tritanomaly and tritanopia). The tinted region 12 may also or alternatively include a dye that is configured to block at least 50%, and preferably 50 to 100%, of incident light in the 550 to 580 nanometer wavelength range to treat red-green color blindness. The percentage of light blocked by the dyes is dependent upon the particular needs of the contact lens wearer.
In one embodiment, the contact lens 10 is made of a 2-hydroxyethyl methacrylate (HEMA) material, which has a tinted region 12 shown in
In a second embodiment, the contact lens 10 is made of HEMA material and has a tinted region 12 shown in
In a third embodiment, the contact lens 20 has a tinted region 22 with two distinct layers 24, 26 as shown in
The first and second contact lenses 10 may be made using a method of mixing a solution comprising polyethylene glycol dimethacrylate (PEGDA), 2-hydroxyethyl methacrylate (HEMA), and 2,2-dimethoxy-2-phenylacetophenone (photoinitiator) with the first or second carboxytetramethylrhodamine dye. The ratio of the HEMA to PEGDA to photoinitiator is in the range of 20:1:1 to 10:10:1, by volume. The concentration of the carboxytetramethylrhodamine dye is in the range of in the range of 0.000015% to 0.00003% by weight. The mixture is then poured into a mold and the cured by exposure to an ultraviolet light source. The light source may provide energy in the range of 100 to 1200 µJ/cm2 at a wavelength of 365 nm. The mixture may be exposed to the ultraviolet light for a period of 2 to 30 minutes in order to cure the mixture.
In another embodiment, the two dyes are added in certain proportions into the mixture (comprising polyethylene glycol dimethacrylate (PEGDA), 2-hydroxyethyl methacrylate (HEMA), and 2,2-dimethoxy-2-phenylacetophenone and then formed into a lens with a single layer rather two separate layers, one for each dye.
The third contact lens 20 may be made by adding the steps of mixing another solution comprising polyethylene glycol dimethacrylate (PEGDA), 2-hydroxyethyl methacrylate (HEMA), and 2,2-dimethoxy-2-phenylacetophenone (photoinitiator) with whichever carboxytetramethylrhodamine dye was not used previously. The ratio of the HEMA to PEGDA to photoinitiator is in the range of 20:1:1 to 10:10:1, by volume. The concentration of the carboxytetramethylrhodamine dye is in the range of in the range of 0.000015% to 0.00003% by weight. The mixture is then poured into the mold over the previously formed layer and the cured by exposure to an ultraviolet light source. The light source may provide energy in the range of 100 to 1200 µJ/cm2 at a wavelength of 365 nm. The mixture may be exposed to the ultraviolet light for a period of 2 to 30 minutes in order to cure the mixture.
Alternatively, the contact lenses 10, 20, may be formed by an additive manufacturing (3D printing) process using a digital light processor printer having an ultraviolet light source and containing the solutions as described above.
The tinted area of the contact lens is stable when stored a hydroxypropyl methylcellulose (artificial tears) solution, such as TEARS NATURALE™ II manufactured by Alcon, or when stored in a phosphate buffered saline solution, such as ACUVUE™ REVITALENS® solution manufactured by Johnson & Johnson, for a period of at least one week.
Testing performed with deuteranopia subjects using the contact lenses 10 with the first dye to block 90% of light in the 480 to 500 nanometer wavelength range experienced 15% improvement in correctly identifying plates in the Ishihara test commonly used to evaluate CVD, while the contact lenses 10 with the second dye to block 90% of light in the 550 to 580 nanometer wavelength range provided about 20% improvement and the contact lens 20 provided about 23% improvement. Testing performed with deuteranomaly subjects using the contact lenses 10 with the first dye experienced a decrease of about 5% in correctly identifying plates in the Ishihara test while the contact lens 10 with the second dye provided about 11% improvement and the contact lens 20 provided about 25% improvement. Based on this testing, it is recommended that the contact lens 10, 20, used, the dye, and the dye concentration is customized to the individual person with CVD.
While the contact lenses 10, 20 described above are hydrogel contact lenses formed primarily from HEMA material, alternative contact lenses including the inventive features may be silicon hydrogel or hard contact lenses with a thin layer of HEMA material containing the tinted region described above.
A method 100 of forming a contact lens 10 with a tinted region 12 configured to treat CVD is shown in
STEP 102, PROVIDE A SOLUTION COMPRISING PEGDA, HEMA, AND PHOTOINITIATOR, includes providing a solution that includes 2-hydroxyethyl methacrylate (HEMA), polyethylene glycol dimethacrylate (PEGDA), and a photoinitiator, e.g., 2,2-dimethoxy-2-phenylacetophenone;
STEP 104, FORM A FIRST MIXTURE OF A FIRST CARBOXYTETRAMETHYLRHODAMINE DYE AND THE SOLUTION includes forming a first mixture of a first carboxytetramethylrhodamine dye and the solution of HEMA, PEGDA, and the photoinitiator;
STEP 106, FORM THE FIRST MIXTURE INTO A DESIRED SHAPE, includes forming the first mixture into a desired shape by pouring the mixture in to a mold shaped to form the contact lens 10 or using an additive manufacturing process;
STEP 108, CURE THE FIRST MIXTURE BY EXPOSURE TO ULTRAVIOLET LIGHT, includes curing the first mixture in the mold by exposure to ultraviolet light, e.g., ultraviolet light with a wavelength of 365 nm having an intensity in the range of 100 to 1200 µJ/cm2 for a period of 2 to 30 minutes or by using a digital light processor 3D printer having an ultraviolet light source;
STEP 110, FORM A SECOND MIXTURE OF A SECOND CARBOXYTETRAMETHYLRHODAMINE DYE AND THE SOLUTION, is an optional step in forming the contact lens 20 that includes forming a second mixture of a second carboxytetramethylrhodamine dye and the solution of HEMA, PEGDA, and the photoinitiator;
STEP 112, FORM THE SECOND MIXTURE INTO A DESIRED SHAPE OVER THE FIRST CURED MIXTURE, is an optional step in forming the contact lens 20 that includes pouring the second mixture into the mold over the first cured mixture that remains in the mold to form a desired shape of the second mixture or forming the second mixture into a desired shape over the first cured mixture using an additive manufacturing process; and
STEP 114, CURE THE SECOND MIXTURE BY EXPOSURE TO ULTRAVIOLET LIGHT, is an optional step in forming the contact lens 20 that includes curing the second mixture by exposure to ultraviolet light, e.g., ultraviolet light with a wavelength of 365 nm having an intensity in the range of 100 to 1200 µJ/cm2 for a period of 2 to 30 minutes or by using a digital light processor 3D printer having an ultraviolet light source.
A process 200 of forming a contact lens 10 with a tinted region 12 configured to treat CVD using an additive manufacturing process, commonly known as a 3D printing process, is shown in
STEP 202, PROVIDE A FIRST LIQUID RESIN SOLUTION, includes providing a first liquid resin solution. Two examples of a suitable first resin solution are a first mixture of 2-hydroxyethyl methacrylate (HEMA), polyethylene glycol dimethacrylate (PEGDA), and a photoinitiator such as 2,2-dimethoxy-2-phenylacetophenone or diphenyl (2,4,6-trimethylbenzoyl) phosphine oxide (TPO). The ratio of HEMA to PEGDA may be in a range of 3:1 to 1:1 and the concentration of the photoinitiator may be in the range of 2% to 10% by weight of the solution. Preferably, the ratio of HEMA to PEGDA is 1:1 and the concentration of the photoinitiator is 2.5% by weight. The composition of the solution has been found to optimize the optical transmittance of the contact lens 10;
STEP 204, FORM THE CONTACT LENS FROM THE FIRST LIQUID RESIN SOLUTION USING AN ADDITIVE MANUFACTURING PROCESS AND CURING THE FIRST LIQUID RESIN SOLUTION BY EXPOSURE TO ULTRAVIOLET LIGHT, includes loading the first liquid resin solution into an additive manufacturing device, such as a digital light printer (DLP) or a masked stereolithography apparatus (MSLA) that is programmed to form the lens shape of the contact lens 10 and any removeable support structures 44 needed during the process of forming the contact lens as shown in
STEP 206, WASH THE CONTACT LENS WITH A FIRST SOLVENT TO REMOVE UNCURED FIRST LIQUID RESIN SOLUTION AFTER CURING THE FIRST LIQUID RESIN SOLUTION BY EXPOSURE TO ULTRAVIOLET LIGHT, is an optional step including washing the contact lens with a first solvent, e.g., isopropyl alcohol, to remove any remaining portions of the first liquid resin solution that remain uncured after exposing the first liquid resin solution to ultraviolet light;
STEP 208, DIP THE CONTACT LENS FORMED BY THE ADDITIVE MANUFACTURING PROCESS INTO A SECOND LIQUID RESIN SOLUTION, includes dip coating the contact lens that was formed by the additive manufacturing process by submerging the contact lens in a second liquid resin solution for a period of 30 seconds to one minute. The second liquid resin solution may preferably be the same as the first resin solution.
STEP 210, CURE THE SECOND LIQUID RESIN SOLUTION BY EXPOSURE TO ULTRAVIOLET LIGHT, includes curing the second liquid resin solution by exposure to ultraviolet light for a period of one to two minutes;
STEP 214 WASH THE CONTACT LENS WITH A SECOND SOLVENT TO REMOVE UNCURED SECOND LIQUID RESIN SOLUTION AFTER CURING THE SECOND LIQUID RESIN SOLUTION BY EXPOSURE TO ULTRAVIOLET LIGHT, is an optional step including washing the contact lens with a second solvent which may be the same as the first solvent, e.g., isopropyl alcohol, to remove any remaining portions of the second liquid resin solution that remain uncured after exposing the second liquid resin solution to ultraviolet light; and
STEP 212, ADD A FIRST DYE OR A SECOND DYE TO THE FIRST OR SECOND LIQUID RESIN SOLUTION, is an optional step that includes adding a first dye configured to absorb at least 50% of incident light in a spectral band between 480 nanometers to 500 nanometers or a second dye configured to absorb at least 50% of incident light in a spectral band between 550 nanometers to 580 nanometers to the first or second liquid resin solution so that the contact lens may be used to treat CVD. The dyes may preferably be a carboxytetramethylrhodamine dye when the first or second liquid resin solution is a mixture of HEMA, PEGDA, and 2,2-dimethoxy-2-phenylacetophenone or a food grade dye when the first or second liquid resin solution is a mixture of HEMA, PEGDA, and TPO. The carboxytetramethylrhodamine dyes are added to have a concentration of 0.000015% to 0.00003% by weight while the food grade dyes are added to have a concentration of about 2% by volume.
The additive manufacturing process may also be used to form rectangular microchannels 32, as shown in
The inventors have also discovered that the surface finish and optical transmittance of the contact lens formed by the additive manufacturing process may be further improved by placing a thin film of PVC plastic on top of the print bed of the additive manufacturing apparatus thereby allowing easier removal of the contact lens from the print bed and a reduction in damage to the contact lens while removing it from the print bed.
A nanopattern 36 may be formed on the surface of the contact lens via a holographic laser ablation apparatus as shown in
The laser ablation process is carried out via direct laser interference patterning (DLIP) method in holographic Denisyuk reflection mode. To facilitate the interaction between the laser beams and the lens material, a black color dye 38 is placed on the surface of the contact lens.
The process of producing the nanopattern on the lens material may include the following steps:
Upon exposure to the laser 42, the ablative interference fringes are developed thereby forming a one-dimensional (1D) nanopattern 36 on the surface of the 3D printed contact lens 10.
Because of the high energy in the constructive interference regions, the nanogrooves are produced on the surface of the contact lens as shown in the
Accordingly, contact lenses 10, 20 configured for treating CVD and a method 100 and process 200 for manufacturing these contact lenses 10, 20 is presented herein. The use of using a dyed region to block out light with undesirable wavelengths, instead of quantum dots or nanoparticles, provides a lower cost and simplicity which make the contact lenses 10, 20 ideal for mass production. In addition, the carboxytetramethylrhodamine dye is nontoxic to the corneal tissue of the eye. Once the carboxytetramethylrhodamine dye is cross-linked with the HEMA material forming the lens, it is resistant to leaching into tears in the eye or contact lens storage solution, thereby providing a stable color in the tinted regions, 12, 22. It has also been found that crosslinking the carboxytetramethylrhodamine dye with the HEMA material does not affect the dye’s chemical structure. In addition, the carboxytetramethylrhodamine dye has high thermal stability, has high photostability, and is slightly hydrophilic.
The lenses 1320, 1520, 1720 used in the glasses include tinting that block a certain amount of specific wavelengths of light to treat color vision deficiency (CVD). The tinting was the result of mixing at least one dye into the photocurable resin used to form the lenses 1320, 1520, 1720. A first dye is mixed with the clear photocurable resin and is mixed in an amount configured to absorb at least 50% of incident light in a spectral band between 480 nanometers to 500 nanometers. A second dye is also mixable with the clear photo curable resin and is mixed in an amount configured to absorb at least 50% of incident light in a spectral band between 550 nanometers to 580 nanometers to the first or second liquid resin. In some embodiments, both the first dye and the second dye are mixed into the clear photo curable resin to produce lenses 1320, 1520, 1720 that absorbs at least 50% of incident light in a spectral band between 480 nanometers to 500 nanometers, and at least 50% of incident light in a spectral band between 550 nanometers to 580 nanometers. In other embodiments, just the first dye is mixed with the clear photocurable resin to produce lenses 1320, 1520, 1720 that absorb 50% of incident light in its respective spectral band. In another embodiment, just the second dye is mixed with the clear photocurable resin to produce lenses 1320, 1520, 1720 that absorb 50% of incident light in its respective spectral band. In yet another embodiment, a mixture of the first dye and the clear photo curable resin is used to form a first layer of the lenses 1320, 1520, 1720 and a mixture of the second dye with the clear photo curable resin is used to form a second layer of the lenses 1320, 1520, 1720. The resulting eyeglasses 1300 are customizable. The concentration of the first and second dyes can be varied. For example, the concentrations can be varied to be 0.5%, 1.0% or 1.5%. One or both dies can be formed into the lenses 1320, 1520, 1720.
For 3D printing of glass lenses 1320, 1520, 1720 that included both dyes in the lenses, The wavelength filtering dyes (Atto dyes) are available from Sigma-Aldrich of Burlington, Massachusetts. The Atto dyes (Atto 565 and Atto 488) were mixed individually as well as in combined form, in a clear photocurable resin. In this particular embodiment, the clear photocurable resin is DentaClear available from ASIGA of Alexandria, NSW, Australia. Dimethyl Sulfoxide (DMSO) was utilized as the solvent to prepare the liquefied dye solution. For that purpose, 1 mg powder of dyes were dissolved in 1 mL of DMSO followed by mixing with the help of vortex for 5 min to obtain the liquid form of dyes. The prepared solution (1 mL DMSO + 1 mg dye solution) was added to 100 mL of DentaClear photocurable resin. Next, more liquid resins were added to get the lower concentrations of the dyes in the resin to the desired level. As mentioned previously, the concentrations used generally could be 0.5%, 1.0% or 1.5%. It should be noted that other concentrations could be used to form the lenses 1320, 1520, 1720. Also of note, the Atto dyes have been extensively studied for life science applications and exhibit a negligible safety concern. For lenses containing both dyes, the above procedure was done for each of the dyes, Atto 565 and Atto 488, and added to the clear photocurable resin. For lenses 1320, 1520, 1720 containing just one of the wavelength filtering dyes was added to the clear photocurable resin. As will be discussed below, some of the lenses 1320, 1520, 1720 include a layer containing one of the wavelength filtering dyes, and another layer containing the other of the wavelength filtering dyes.
3D printing of the lenses 1320, 1520, 1720 was carried out utilizing a masked sterolithography 3D printing apparatus (MSLA). The MSLA 3D printer used is a Prusa SL1 available from Prusa Research of Prague, Czech Republic.[24] The 3D printing parameters play a crucial role on the resulting properties of the manufactured parts. Hence, the printing parameters (curing time and layer thickness) are optimized to achieve the desired optical and mechanical properties. The utilized printing parameters are presented in Table 1, and the 3D printing process has been discussed with respect to
The lenses 1510, were built on a support structure and pillar. Pads were added to the PVC film before printing.
When a two layer type lens is made, the process is essentially the same as above. An additional step in the process happens after the first layer or portion of the lens 1510, 1710 is formed from multiple rows of formed plastic. The vat is emptied of the first mixture of clear photocurable resin mixed with the first wavelength filtering dye. The lens and vat are cleaned with IPA to remove uncured dye. The vat is then filled with a second mixture of clear photocurable resin with a second wavelength filtering dye. Once the vat is filled with the second mixture, the additive manufacturing process is used to add the second layer including multiple rows of formed plastic atop the first layer. According to one embodiment, the layer thickness used in the additive manufacturing process, the curing time, the print speed and other printing parameters are set forth in the following Table 1.
After 3D printing, the parts were washed in Isopropyl Alcohol (IPA) and sonicated to ensure all uncured resin was removed from the printed parts. Finally, the support structures were removed. Other post processing includes polishing the lenses 1510, 1710 with a fine grit polish.
Another post processing procedure includes testing the lens 1520, 1720 for hardness.
Where, d is the Arithmetic mean of the two diagonals, d1 and d2 in mm.
It is also contemplated that other hardness tests could be used to determine the hamdess of the lenses. For example, a Brinnell hardness test could be used to characterize the hardness and scratch resistance of the lenses.
Additionally, if the hardness test yields a hardness out of a selected range, the manufacturing process, namely the thickness of each row of material added in the additive process, and the curing time can be varied to produce a lens 1320, 1520, 1720 within the selected range.
3D printing of the frames 1340 and bows or temples 1342, 1342 was carried out utilizing a printing apparatus (masked sterolithography 3D printing apparatus (MSLA). The MSLA 3D printer used is a Prusa SL1 available from Prusa Research of Prague, Czech Republic.) To print the frames and bows, a gray resin, such as Wanhao 3D Printing High Tenacity Resin available from Wanhao Factory Co., LTD of Hangzhou, Zhejiang, China was utilized. The 3D printing parameters play a crucial role on the resulting properties of the manufactured parts. Hence, the printing parameters (curing time and layer thickness) are selected to achieve the desired mechanical properties of the frames and bows. The utilized printing parameters are also presented in Table 1, and the 3D printing process includes 1) CAD model preparation, 2) slicing, and 3) 3D printing, and 4) post processing (washing) of the frames. The printed frame 2640 and the bows 2642, 2643 are shown in
The mechanical properties of the glasses and frame materials (DentaClear and Gray resins) were characterized by tensile and three-point bending tests. Mechanical properties were determined and are presented in Table 2 below. The mechanical properties from both materials demonstrated their durability as glass lenses and frame materials, which is apparent when comparing them with materials employed in similar applications. The flexural properties (from three-point bending test) indicated that the frame manufactured via 3D printing will not break easily even if it was subjected to folding or bending. Overall, the spectacles (including both the lenses and frame) exhibited excellent durability.
It should be noted that in some embodiments, the lenses are formed of a first layer of a resin dyed with a first wavelength filtering dye, and the formed of a second layer of a resin dyed with a second wavelength filtering dye. The second layer is formed on top of the first layer. This adds the further elements of emptying the vat of the unused portion of the resin dyed with the first wavelength filtering dye and cleaning the partially formed lenses and the vat. The resin dyed with a second wavelength filtering dye is then placed in the vat and printing is continued using the resin with the second wavelength filtering dye.
In summary, a set of eyeglasses includes a printed frame having a first opening and a second opening, a first ophthalmic printed lens for the first opening in the printed frame, and a second ophthalmic printed lens for the second opening in the printed frame. In one embodiment, both of the first ophthalmic printed lens and the second ophthalmic printed lens formed with a first dye therein configured to absorb at least 50% of incident light in a spectral band between 550 nanometers and 580 nanometers. In another embodiment, both of the first ophthalmic printed lens and the second ophthalmic printed lens are formed with a first dye therein configured to absorb at least 50% of incident light in a spectral band between 550 nanometers and 580 nanometers and the first dye therein in a first portion of both of the first ophthalmic printed lens and the second ophthalmic printed lens. In one embodiment, the portion is inside both of the first ophthalmic printed lens and the second ophthalmic printed lens. For example, the first portion could be a sandwiched layer or other inner layer within the first and second ophthalmic printed lens. In another embodiment, the first ophthalmic printed lens and the second ophthalmic printed lens are formed with a second dye therein. The second dye is configured to absorb at least 50% of incident light in a spectral band between 480 nanometers and 500 nanometers. The second dye therein in a second portion of both of the first ophthalmic printed lens and the second ophthalmic printed lens inside both of the first ophthalmic printed lens and the second ophthalmic printed lens. In one embodiment, the second portion is an inner layer or a layer sandwiched within both the first ophthalmic printed lens and the second ophthalmic printed lens.
In one embodiment, both of the first ophthalmic printed lens and the second ophthalmic printed lens are formed with a first dye therein configured to absorb at least 50% of incident light in a spectral band between 550 nanometers and 580 nanometers, and a second dye therein configured to absorb at least 50% of incident light in a spectral band between 480 nanometers and 500 nanometers. In other words, the first dye and second dye are inside both of the first ophthalmic printed lens and the second ophthalmic printed lens. In other words, these are not coatings on the outside of an otherwise clear lens.
In another embodiment, the first dye is in a first portion of both the first ophthalmic printed lens and the second ophthalmic printed lens, and the second dye is in a second portion of both the first ophthalmic printed lens and the second ophthalmic printed lens. The first portion and the second portion being different portions within both of the first ophthalmic printed lens and the second ophthalmic printed lens. In one embodiment, the first portion is a first layer and the second portion is a second layer of both the first ophthalmic printed lens and the second ophthalmic printed lens.
A printed ophthalmic lens for eyeglasses includes a first major exterior surface and a second major exterior surface. The printed ophthalmic lens also includes a first interior portion between the first major exterior surface and the second major exterior surface. The first interior portion includes a first dye configured to absorb at least 50% of incident light in a spectral band between 550 nanometers and 580 nanometers. In another embodiment, the interior portion also includes second dye therein configured to absorb at least 50% of incident light in a spectral band between 480 nanometers and 500 nanometers. In still another embodiment, the printed ophthalmic lens for eyeglasses of claim 10 further includes a second interior portion that includes second dye therein configured to absorb at least 50% of incident light in a spectral band between 480 nanometers and 500 nanometers. The second portion different than the first interior portion. In one embodiment, the first interior portion is a first layer and the second interior portion is a second layer. In some embodiments, the first layer and the second layer extend to all the edges of the printed ophthalmic lens.
A process of forming an ophthalmic lens includes providing a first liquid resin solution with at least one of a first dye therein configured to absorb at least 50% of incident light in a spectral band between 550 nanometers and 580 nanometers, and a second dye therein configured to absorb at least 50% of incident light in a spectral band between 480 nanometers and 500 nanometers. The ophthalmic lens from the first liquid resin solution is formed using an additive manufacturing process and is cured by exposing the first liquid resin solution to ultraviolet light.
While the invention has been described with reference to an exemplary embodiment(s), it will be understood by those skilled in the art that various changes may be made, and equivalents may be substituted for elements thereof without departing from the scope of the invention. In addition, many modifications may be made to adapt a particular situation or material to the teachings of the invention without departing from the essential scope thereof. Therefore, it is intended that the invention is not limited to the disclosed embodiment(s), but that the invention will include all embodiments falling within the scope of the appended claims.
This application is a continuation-in-part application and claims the benefit of U.S. Pat. Application No. 17/499,251, filed Oct. 12, 2021, the entire disclosure of which is hereby incorporated by reference, which is a continuation-in-part application and claims the benefit of U.S. Pat. Application No. 17/307,316, filed May 4, 2021, the entire disclosure of which is hereby incorporated by reference.
Number | Date | Country | |
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Parent | 17499251 | Oct 2021 | US |
Child | 18087397 | US | |
Parent | 17307316 | May 2021 | US |
Child | 17499251 | US |