SYSTEM AND METHOD FOR INCREASING THE DEPTH OF FOCUS OF THE HUMAN EYE

Abstract: A method and apparatus for increasing the depth of focus of the human eye comprising a lens body, an optic located in the lens body, the optic configured to produce light interference, and a pinhole-like optical aperture substantially in the center of the optic. In a further embodiment of the invention, the optic is configured to produce light scattering. In a still further embodiment of the invention, the optic is composed of a light reflective material. The optic may also be configured to increase depth of focus via a combination a light interference, light scattering, light reflection and/or light absorption. In alternate embodiments of the inventions, the optic may be configured as a series of concentric circles, a weave, a pattern of particles, or a pattern of curvatures. A further method for increasing the depth of focus of the human eye includes screening a patient for an ophthalmic lens, the ophthalmic lens increasing the patient's depth of focus, using a pinhole screening device. In an alternative embodiment, the method comprises surgically implanting a mask in the patient's eye, the mask configured to increase the patient's depth of focus.

Description: SYSTEM AND METHOD FOR INCREASING THE DEPTH OF FOCUS OF THE HUMAN EYE FIELD OF THE INVENTION The invention generally relates to ophthalmic lenses and, more particularly, the invention relates to ophthalmic lenses for increasing the depth of focus of the human eye BACKGROUND OF THE INVENTION It is well-known that the depth of focus of the human eye can be increased with the use of ophthalmic lenses with pinhole-hke apertures substantially near the optical center of the lens. For example, U.S. Patent No 4,976,732 ("the '732 patent") discloses an ophthalmic lens with a pinhole-hke aperture. In the '732 patent, a mask forms the pmhole-like aperture. In one embodiment, the mask is circular in shape. When the pupil is constπcted, light enters the ret a through the pinhole-hke aperture. When the pupil is dilated, light enters the retina through the pinhole-hke aperture and the outer edges of the mask. In addition, U.S. Patent No. 3,794,414 ("the '414 patent") discloses a contact lens with a pmhole-like aperture In the '414 patent, the mask forming the pinhole-hke aperture has radial slits and/or scalloped edges. In addition, the mask forming the pinhole-hke aperture is two spaced-apart concentπc circles. However, the radial slits, scalloped edges and two spaced-apart concentπc circles promote light diffraction, which in turn reduces the contrast of the image. In U.S. Patent Nos. 4.955,904, 5,245,367, 5,757,458 and 5,786,883. vaπous modifications to an ophthalmic lens with a pmhole-hke aperture are disclosed For example, the patents disclose use of an optical power for vision coπection in the pmhole-hke aperture, or use of an optical power for vision coπection in the area outside the mask. In contrast, in U.S Patent No. 5.980,040, the mask is powered. In particular, the mask is powered to bend the light passing through the mask to impinge on the retina at a radial distance outside of the fovea. In other words, the mask is powered to "defocus" the light. In each of these patents, the mask forming the pmhole-hke aperture is made, in whole or in part, of a light absorptive mateπal. A light-absorptive mateπal is a material in which light is lost as it passes through the mateπal, generally due to conversion of the light into another form of energy, e.g., heat SUMMARY OF THE INVENTION In accordance with an embodiment of the invention, an ophthalmic lens comprises a lens body, an optic located in the lens body, the optic configured to produce light interference, and a pinhole-hke optical aperture substantially in the center of the optic. In a further embodiment of the invention, the optic is configured to positively interfere with parallel light reaching the optic and negatively interfere with diverging light reaching the optic. In addition, some diverging light may pass through the optic. In this alternate embodiment of the invention, the optic is configured to spread out the diverging light passing through the optic. In an alternate embodiment of the invention, an ophthalmic lens compπses a lens body, an optic located in the lens body, the optic configured to produce light scatteπng, and a pinhole-hke optical aperture substantially in the center of the optic. In a further embodiment of the invention, the optic is configured to forward scatter parallel light reaching the optic and back scatter diverging light reaching the optic. In another alternative embodiment of the invention, an ophthalmic lens compπses a lens body, an optic located in the lens body, the optic configured to produce light reflection, and a pinhole-hke optical aperture substantially in the center of the optic. In an alternate embodiment of the invention, the optic is composed, in whole or in part, of a light reflective mateπal. In further embodiments of the inventions, the optic may be configured as a seπes of concentπc circles, a weave, a pattern of particles, or a pattern of curvatures In addition, the pinhole-hke aperture includes an optical power for vision correction, and may have a diameter in the range of substantially .05 mm to substantially 5.0 mm Further, the optic may have an outer diameter in the range of substantially 1.0 mm to substantially 8.0 mm. The optic may also be composed of a mateπal having varying degrees of opacity, and the ophthalmic lens and the optic may be composed of a bio- compatible, non-dissolving mateπal, such as polymethyl methacrylate or a medical polymer. In accordance with another embodiment of the invention, a method for screening a patient for an ophthalmic lens, the ophthalmic lens having a pinhole-hke optical aperture, compπses fitting each of the patient's eyes with a first contact lens, placing a mask on each of the first contact lens, the mask configured to produce a pmhole-hke aperture in each of the first contact lens, fitting each of the patient's eyes with a second contact lens, the second contact lens being placed over the mask to hold the mask in a substantially constant position, and testing the patient's vision. In further embodiments of the invention, the mask may be a light interference mask, a light scatteπng mask, or a light reflective mask. The first contact lens may include an optical power for vision coπection. In addition, each of the first and second contact lenses may be soft contact lenses. Further, the mask for each of the patient's eyes may have a light absorption of substantially 100%. In the alternative, the mask for each of the patient's eyes may be composed of a polaπzed mateπal In still further embodiments of the invention, the process of testing compπses testing the patient's acuity for distance vision under bπght and dim lighting conditions, testing the patient's acuity for near vision under bπght and dim lighting conditions, and testing the patient's contrast sensitivity under bπght and dim lighting conditions. The process of testing may further compπse testing a patient's visual acuity using a night dπving simulation. The night dπving simulation may include a seπes of objects and road signs under bπght and dim lighting conditions, as well as having the patient face a simulated oncoming automobile headlight. In an alternate embodiment of the invention, the process of testing compπses replacing the mask in one of the patient's eyes with a mask having a light absorption of substantially 85% or less, then, if needed, replacing the mask in the patient's other eye with a mask having a light absorption of substantially 85% or less. Further, the process of testing compπses, if needed, removing the mask from one of the patient's eyes. In another alternate embodiment of the invention, the process of testing compπses placing an analyzer in the spectacle plane of one of the patient's eyes, the analyzer including a polaπzing element, rotating the polaπzing element to achieve an optimal balance of contrast and bπghtness. and determining the resultant light absorption of the mask In addition, the process of testing may include evaluating the cosmetic appearance of the mask In accordance with a still another embodiment of the invention, a method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, compπses removing the epithelial sheet, creating a depression in the Bowman's membrane, the depression being of sufficient depth and width to expose the top layer of the stroma and accommodate the mask, placing the mask in the depression, and placing the removed epithelial sheet over the mask. In a further embodiment of the invention, the depression may extend into the top layer of the stroma In an alternate embodiment of the invention, a method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye. compπses hinging open a portion of the Bowman's membrane, creating a depression in the top layer of the stroma, the depression being of sufficient depth and width to accommodate the mask, placing the mask in the depression, and placing the hinged Bowman's membrane over the mask. In another alternate embodiment of the invention, a method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, compπses creating a channel in the top layer of the stroma, the channel being in a plane parallel to the cornea's surface, and placing the mask in the channel. In this embodiment, the mask may be threaded into the channel, or the mask may be injected into the channel. In still another alternate embodiment of the invention, a method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, compπses penetrating the top layer of the stroma with an injecting device, and injecting the mask into the top layer of the stroma with the injecting device. In this embodiment. the injecting device may be a nng of needles. In addition, the mask may be a pigment, or the mask may be composed of pieces of pigmented matenal suspended in a bio- compatible medium. The pigmented mateπal may be made of a medical polymer, e g . suture mateπal. In one other alternate embodiment of the invention, a method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, compπses hinging open a corneal flap, the corneal flap compnsmg substantially the outermost 20% of the cornea, placing the mask on the cornea, and placing the hinged corneal flap over the mask. In still one other alternate embodiment of the invention, a method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, compπses creating a pocket in the stroma, the pocket being of sufficient size to accommodate the mask, and placing the mask in the created pocket In further embodiments of the inventions, the mask may be a light interference optic, a light scatteπng optic, or a light reflective optic. In addition, the mask may block visual abeπations In addition, after surgery, a contact lens may be placed over at least the affected portion of the cornea. BRIEF DESCRIPTION OF THE DRAWINGS The foregoing and other objects and advantages of the invention will be appreciated more fully from the following further descnption thereof with reference to the accompanying drawings wherein: Figures la and lb show an exemplary ophthalmic lens with an exemplary optic configured to produce light interference. Figures 2a and 2b show another exemplary ophthalmic lens with another exemplary optic configured to produce light interference. Figures 3a and 3b show an exemplary ophthalmic lens with an exemplary optic configured to produce light scatteπng. Figures 4a and 4b show an exemplary ophthalmic lens with an exemplary optic configured to produce light reflection. Figure 5 shows an exemplary process for screening a patient interested in an ophthalmic lens with a pinhole-hke aperture using an exemplary pinhole screening device. Figures 6a through 6c show a mask, configured to increase the depth of focus of the human eye, inserted underneath the cornea's epithelium sheet Figures 7a through 7c show a mask, configured to increase the depth of focus of the human eye, inserted beneath the cornea's Bowman's membrane DETAILED DESCRIPTION OF THE INVENTION In accordance with an embodiment of the invention, an ophthalmic lens (e.g , a contact lens, an intra ocular lens, a corneal inlay lens, etc.) increases the depth of focus of the human eye through the use of an optic. The optic suπounds a pinhole-hke optical aperture near the optical center of the lens. The pinhole-hke aperture in conjunction with the optic increases the depth of focus of the human eye. In particular, the optic increases the depth of focus of the human eye using light interference, light scatteπng, light reflection, light absorption and/or a combination of one or more of these properties An optic configured in accordance with the vaπous embodiments of the invention is refeπed to as a Paraxial Adaptive Optic™ Figures la and lb show an exemplary ophthalmic lens with an exemplary optic configured to produce light interference. Figure la shows a front view of the exemplary ophthalmic lens. Figure lb shows a side view of the exemplary optic implanted in the cornea of a human eye. Light interference is the additive process in which the amplitude of two or more overlapping light waves is either attenuated or reinforced. For example, when two overlapping light waves are m-phase (the crest and trough of one wave coincides with the crest and trough of the other wave), then the amplitude of the resultant light wave is reinforced. This type of interference is refeπed to as positive interference. In contrast, when two overlapping light waves are out-of-phase (the crest of one wave coincides with the trough of the other wave), then the amplitude of the resultant light wave is attenuated. This type of interference is refeπed to as negative interference. Of course, light interference also occurs between the two extremes of m-phase and out-of-phase. As shown in Figure la and lb, optic 100 is located substantially in the center of lens body 110. Optic 100 suπounds optical aperture 120 located near the optical center of lens body 110. The specific location of optical aperture 120 in lens body 110 varies in accordance with the patient's eye. Specifically, optical aperture 120 is positioned in lens body 110 to be concentπc with the patient's pupil. In operation, optical aperture 120 increases the depth of focus of the human eye via a "pinhole effect." In particular, optical aperture 120 increases depth of focus by limiting the light reaching the retina to plane wavefront light. In photonics, a wavefront is a surface connecting all points equidistant from a source. Plane wavefront light is relatively parallel light, e.g.. light from a distant source. It is "relatively" parallel light because, in reality, even light from a distant star is diverging light. In contrast, convex wavefront light is relatively diverging light, e.g., light from a near source. It is easier for the human eye to focus plane wavefront light because the crystalline lens of the human eye can focus parallel light on the retina with little or no accommodation. In accommodation, the crystalline lens, through the action of the ciliary muscles, thickens and, thereby, changes its degree of curvature. In order to achieve a useful "pinhole effect," optical aperture 120 should have a diameter in the range of substantially .05 millimeters ("mm") to substantially 5 0 mm In addition, in order to aid examination of the retina and increase brightness when the pupil is dilated, the outer diameter of optic 100 should be in the range of substantially 1.0 mm to substantially 8.0 mm. Moreover, to further improve vision, optical aperture 120 may include an optical power for vision coπection, e.g.. coπection for near vision, coπection for distance vision, coπection for intermediate vision, etc Also, the area outside optic 100 may include an optical power for vision coπection In operation, optic 100 increases the depth of focus of the human eye via its configuration. In particular, optic 100 is configured to produce light interference via a seπes of concentπc circles. Specifically, optic 100 is configured to reinforce relatively parallel light and attenuate relatively diverging light When optic 100 attenuates less than all of the relatively diverging light, then optic 100 is further configured to spread out the diverging light that passes through optic 100, Le., weakening the diverging light passing through optic 100. Thus, because diverging light is attenuated and or weakened, the "pinhole effect" of optical aperture 120 is increased for relatively near objects, producing a higher contrast depth of focus image of relatively near objects. Moreover, because parallel light is reinforced, the "pinhole effect" of optical aperture 120 is reduced, producing a bπghter image of relatively distant objects. Optic 100 is also configured to effect the chromatic abeπation of the human eye. The human eye's chromatic abeπation, in which the size of an image appears to change when the color of the image is changed, results from the normal increase in refractive index toward the blue end of the color spectrum. In optic 100, the increase in refractive index is toward the red end of the color spectrum Thus, optic 100 may reduce or cancel the chromatic aberration of the human eye. Further, optic 100 is configured to meet the specific needs of the patient. For example, a person of skill in the art understands that, among other things, the addition of concentric circles, the removal of concentπc circles, the change in spacing between concentπc circles, the varying of spacing between concentπc circles, and the shape of the concentπc circles (e.g.. oval, round, elliptical, etc.) would influence the light interference properties of optic 100. Figures 2a and 2b show another exemplary ophthalmic lens with another exemplary optic configured to produce light interference. In this exemplary embodiment, optic 200 is configured to produce light interference via a weave As discussed in regard to optic 100, the weave reinforces relatively parallel light and attenuates relatively diverging light Depending on the weave ' s mateπal, the weave may also absorb light coming into contact with the weave's mateπal Figure 2a shows a front view of the exemplary ophthalmic lens Figure 2b shows a side view of the exemplary optic implanted in the cornea of a human eye. As discussed in regard to optic 100, optic 200 is configured to meet the specific needs of the patient. For example, a person of skill in the art understands that, among other things, the density of the weave would influence the light interference properties of optic 200. Figures 3a and 3b show an exemplary ophthalmic lens with an exemplary optic configured to produce light scatteπng Figure 3a shows a front view of the exemplary ophthalmic lens. Figure 3b shows a side view of the exemplary optic implanted in the cornea of a human eye. In general, light scattenng is the deflection of light upon interaction with a medium. Light is forward scattered when, upon interaction with a medium, it is deflected through angles of 90° or less with respect to the oπginal direction of motion Light is back scattered when, upon interaction with a medium, it is deflected through angles in excess of 90° with respect to the ongmal direction of motion. As shown in Figures 3a and 3b, optic 300 is located substantially in the center of lens body 310. Optic 300 suπounds optical aperture 320 located near the optical center of lens body 310. The specific location of optical aperture 320 in lens body 310 vanes in accordance with the patient's eye. Specifically, optical aperture 320 is positioned in lens body 310 to be concentπc with the patient's pupil As discussed in regard to optical apertures 120 and 220, optical aperture 320 increases the depth of focus of the human eye via a "pinhole effect." Similarly, as discussed in regard to optics 100 and 200, optic 300 increases the depth of focus of the human eye via its configuration. In particular, optic 300 is configured to produce light scatteπng via a pattern of particles. Specifically, optic 300 is configured to forward scatter relatively parallel light and back scatter relatively diverging light. Thus, because diverging light is back scattered, the "pinhole effect" of optical aperture 320 is increased for relatively near objects, producing a higher contrast depth of focus image of relatively near objects. Moreover, because parallel light is forward scattered, the "pinhole effect" of optical aperture 320 is reduced, producing a bπghter image of relatively distant objects. Further, optic 300 is configured to meet the specific needs of the patient. For example, a person of skill in the art understands that, among other things, the light absorption of the particles, the index of refraction of the particles, the index of refraction of the media suπounding the particles, the size of the particles, and the space between the particles would influence the light scatteπng properties of optic 300. In addition. optic 300 may be configured to produce light interference, as discussed in regard to optics 100 and 200. Figures 4a and 4b show an exemplary ophthalmic lens with an exemplary optic configured to produce light reflection. Figure 4a shows a front view of the exemplary ophthalmic lens. Figure 4b shows a side view of the exemplary optic implanted in the cornea of a human eye. Optic 400 is located substantially in the center of lens body 410. Optic 400 surrounds optical aperture 420 located near the optical center of lens body 410 The specific location of optical aperture 420 in lens body 410 vanes in accordance with the patient's eye. Specifically, optical aperture 420 is positioned in lens body 410 to be concentπc with the patient's pupil. As discussed in regard to optical apertures 120, 220 and 320, optical aperture 420 increases the depth of focus of the human eye via a "pinhole effect." Similarly, as discussed in regard to optics 100, 200 and 300, optic 400 increases the depth of focus of the human eye via its configuration. In particular, optic 400 is configured to reflect light, in whole or in part, via a pattern of curvatures. Specifically, optic 400 is configured to favor transmission of the light to which the retinal rods are more sensitive, ι_e., dim light and/or blue light, and to block the light to which retinal cones are more sensitive, i.e., bπght light. Thus, because bπght light is blocked, the "pinhole effect" of optical aperture 420 is increased for relatively near objects, producing a higher contrast depth of focus image of relatively near objects. Moreover, because dim light and/or blue light is transmitted, the "pinhole effect" of optical aperture 420 is reduced, producing a bπghter image of relatively distant objects. In an alternate embodiment, optic 400 may be composed, in whole or in part, of a light reflective mateπal. A light reflective mateπal is a mateπal that, in whole or in part, reflects back light coming into contact with the mateπal. Further, optic 400 may be configured to meet the specific needs of the patient For example, a person of skill in the art understands that, among other things, the type of matenal, the thickness of mateπal, and the curvature of mateπal would influence the light reflective properties of optic 400 In addition, optic 400 may be configured to produce light interference and/or light scatteπng, as discussed in regard to optics 100. 200 and 300, respectively. In a particular embodiment of the ophthalmic lens descπbed in Figure 4, optic 400 is composed of a light reflective mateπal with a peak transmission of substantially 550 nanometers ("nm"). A light-adapted retina has a peak transmission at 550 nm. In contrast, a dark-adapted retina has a peak transmission at 500 nm. Thus, an optic with a peak transmission of substantially 550 nm filters out more light with a peak transmission of 500 nm, I ., bπght light, than light with a peak transmission of 550 nm, LC., dim light Thus, as discussed above, because bπght light is blocked, the "pinhole effect" of optical aperture 420 is increased for relatively near objects, producing a higher contrast depth of focus image of relatively near objects. Moreover, because dim light is transmitted, the "pinhole effect" of optical aperture 420 is reduced, producing a bπghter image of relatively distant objects. Further, this particular embodiment of optic 400 may be configured to meet the specific needs of the patient. For example, a person of skill in the art understands that, among other things, the peak transmission of the mask may be changed, e ^ g., to a peak transmission of 500 nm. In addition, the mask may be composed of mateπal, other than light reflective mateπal, which also allows the desired peak transmissions. In alternate embodiments, the optic is composed of bio-compatible, non- dissolving mateπal, e g . polymethyl methacrylate or medical polymers. In addition, the optic may be composed, in whole or in part, of a light reflective mateπal or, in whole or in part, of a light absorptive mateπal. Further, the optic may be composed, in whole or in part, of a mateπal having varying degrees of opacity The optic may also be configured to produce light interference, light scatteπng and light reflection, or some combination of one or more of these properties. Moreover, the optic may be colored to match the color of a patient's ins In accordance with a further embodiment of the invention, a patient interested in an ophthalmic lens with a pinhole-hke aperture is screened using soft contact lenses and a mask, refeπed to as a pinhole screening device. The mask may be an optic as described in the pnor art, an optic as descπbed herein, or an optic combining one or more of these properties. After insertion of the pinhole screening device, the patient ' s vision is tested. Figure 5 shows an exemplary process for screening a patient interested in an ophthalmic lens with a pinhole-hke aperture using an exemplary pinhole screening device. The process begins at step 500, in which the patient is fitted with soft contact lenses, Le., a soft contact lens in placed in each of the patient's eyes. If needed, the soft contact lenses may include vision coπection. Next, at step 510, a mask is placed on the soft contact lenses. The mask should be placed concentric with the patient's pupil. In addition, the curvature of the mask should parallel the curvature of the patient's cornea. The process continues at step 520, in which the patient is fitted with a second set of soft contact lenses, Le., a second soft contact lens is placed over the mask in each of the patient's eyes The second contact lens holds the mask in a substantially constant position Last, at step 530, the patient's vison is tested. Duπng testing, it is advisable to check the positioning of the mask to ensure it remains concentnc with the patient's pupil. A test of the patient's vision may include testing the patient's acuity for distance vision under bnght and dim lighting conditions, testing the patient's acuity for near vision under bπght and dim lighting conditions, and testing the patient's contrast sensitivity under bπght and dim lighting conditions. In addition, the test may include testing the patient's visual acuity using a night dπving simulation. A night dπving simulation may include a seπes of objects and road signs under bπght and dim lighting conditions, as well as a simulated oncoming automobile headlight. The test of the patient's vision may further include changing the mask For example, the test might first be conducted using, in each of the patient's eyes, a mask having a light absorption of substantially 100%. If, for example, the patient expeπences a sense of dimness, the mask in one of the patient's eyes may be replaced with a mask having a light absorption of substantially 85% If, for example, the sense of dimness continues, the mask in the patient's other eye may be replaced with a mask having a light absorption of substantially 85% Then, for example, if the sense of dimness continues, the mask may be removed from one of the patient's eyes. In the alternate, the mask in one of the patient's eyes may be replaced with a mask having a light absorption less than substantially 85%. If, for example, the patient experiences a sense of dimness with a mask having a light absorption of substantially 100%, then the mask in one of the patient's eyes may be replaced with a mask having a light absorption of substantially 75% If. for example, the sense of dimness continues, the mask in the patient's other eye may be replaced with a mask having a light absorption of substantially 75%. Then, for example, if the sense of dimness continues, the 75% mask may be replaced with a mask having a light absorption of substantially 50% As can be seen, there are numerous permutations for thoroughly screening the patient to find the optimal balance of contrast and bnghtness. In effect, the mask in each of the patient's eyes is replaced, every other time, with a mask having a different light absorption than the replaced mask. This process continues until the optimal balance of contrast and bnghtness is found. The process for changing the mask while testing the patient's vision also includes changing from an optic as descπbed in the pπor art to an optic as descnbed herein. In addition, vaπous mask configurations may be used. For example, an optic having both light interference and light scattenng may be used, or an optic having both light reflective and light absorptive properties may be used. Once again, the numerous permutations allow for thoroughly screening the patient to find the optimal balance of contrast and bnghtness pπor to, for example, the doctor placing a customized order or the patient undergoing invasive surgery The test of the patient's vision may also include evaluating the cosmetic appearance of the mask. For example, if the patient is dissatisfied with the appearance of the mask, the mask can be replaced with a mask of appropπate configuration colored to match the patient's ins In an alternate testing process, the mask placed on the soft contact lens in each of the patient's eyes is composed of a polaπzed mateπal A polaπzed mateπal has a light absorption of substantially 50%. Then, an analyzer, which contains a polaπzed element, is used to help calculate the patient's optimal light absorption properties for the mask. In the process, the analyzer is placed in the spectacle plane of one of the patient's eyes and the polaπzed element in the analyzer is rotated until the patient expeπences an optimal balance of contrast and bnghtness. The process may be repeated for the patient's other eye. Using the analyzer, the doctor may now calculate the resultant light absorption of the mask. If desired, a mask of similar light absorption, whether it be an optic as descπbed in the pπor art. an optic as described herein, or an optic combining one or more of these properties, can now be placed between the contact lenses in each of the patient's eyes and the patient's vision tested, as descπbed above In accordance with a still further embodiment of the invention, a mask is surgically implanted into the eye of a patient interested in increasing his or her depth of focus. For example, the patient may suffer from presbyopia, a condition in which the crystalline lens can no longer accommodate near vision because of a loss of elasticity the lens or a weakness in the ciliary muscle. The mask may be an optic as descnbed in the pnor art, an optic as descnbed herein, or an optic combining one or more of these properties. Further, the mask may be configured to coπect visual abeπations. To aid the surgeon surgically implanting a mask into a patient's eye, the mask may be pre-rolled or folded for ease of implantation. The mask may be implanted in several locations. For example, the mask may be implanted underneath the cornea's epithelium sheet, beneath the cornea's Bowman membrane, in the top layer of the cornea's stroma, or in the cornea's stroma. When the mask is placed underneath the cornea's epithelium sheet, removal of the mask requires little more than removal of the cornea's epithelium sheet. Figures 6a through 6c show mask 600 inserted underneath epithelium sheet 610. In this embodiment, the surgeon first removes epithelium sheet 610. For example, as shown in Figure 6a, epithelium sheet 610 may be rolled back. Then, as shown in Figure 6b, the surgeon creates depression 615 in Bowman's member 620. Depression 615 should be of sufficient depth and width to both expose top layer 630 of stroma 640 and to accommodate mask 600 Mask 600 is then placed in depression 615. Last, epithelium sheet 610 is placed over mask 600. Over time, as shown in Figure 6c, epithelium sheet 610 will grow and adhere to top layer 630 of stroma 640, as well as mask 600 depending, of course, on the composition of mask 600. As needed, a contact lens may be placed over the incised cornea to protect the mask. Figures 7a through 7c show mask 700 inserted beneath Bowman's membrane 720. In this embodiment, as shown in Figure 7a, the surgeon first hinges open Bowman's member 720 Then, as shown in Figure 7b, the surgeon creates depression 715 in top layer 730 of stroma 740. Depression 715 should be of sufficient depth and width to accommodate mask 700. Then, mask 700 is placed in depression 715. Last, Bowman's member 720 is placed over mask 700. Over time, as shown in Figure 7c, epithelium sheet 710 will grow over the incised area of Bowman's member 720 As needed, a contact lens may be placed over the incised cornea to protect the mask In an alternate embodiment, a mask of sufficient thinness, Le_, less than substantially 20 microns, may be placed underneath epithelium sheet 610, or beneath Bowman's member 720, without creating a depression in the top layer of the stroma. In an alternate method for surgically implanting a mask in the eye of a patient, the mask may be threaded into a channel created in the top layer of the stroma. In this method, a curved channeling tool creates a channel in the top layer of the stroma, the channel being in a plane parallel to the surface of the cornea The channeling tool either pierces the surface of the cornea or, in the alternative, is inserted via a small superficial radial incision. In the alternative, a laser focusing an ablative beam may create the channel in the top layer of the stroma. In this embodiment, the mask may be a single segment with a break, or it may be two or more segments In another alternate method for surgically implanting a mask in the eye of a patient, the mask may be injected into the top layer of the stroma. In this embodiment, an injection tool with a stop penetrates the surface of the cornea to the specified depth For example, the injection tool may be a nng of needles capable of producing a mask with a single injection. In the alternative, a channel may first be created in the top layer of the stroma. Then, the injector tool may inject the mask into the tunnel. In this embodiment, the mask may be a pigment, or it may be pieces of pigmented matenal suspended in a bio-compatible medium. The pigment matenal may be made of a polymer or, in the alternative, made of a suture mateπal. In still another alternate method for surgically implanting a mask in the eye of a patient, the mask may be placed beneath the corneal flap created duπng keratectomy, when the outermost 20% of the cornea is hinged open. In one still other alternate method for surgically implanting a mask in the eye of a patient, the mask may be placed in a pocket created in the cornea's stroma. Although vaπous exemplary embodiments of the invention have been disclosed, it should be apparent to those skilled in the art that vaπous changes and modifications can be made which will achieve some of the advantages of the invention without departing from the true scope of the invention. These and other obvious modifications are intended to be covered by the appended claims

Claims: We claim 1 An ophthalmic lens compπsing a lens body; an optic located in the lens body, the optic configured to produce light interference, and a pinhole-hke optical aperture substantially in the center of the optic 2. The ophthalmic lens according to claim 1 wherein the optic is configured to positively interfere with parallel light reaching the optic and negatively interfere with diverging light reaching the optic. 3. The ophthalmic lens according to claim 2 wherein some of the diverging light passes through the optic. 4 The ophthalmic lens according to claim 3 wherein the optic is configured to spread out the diverging light passing through the optic. 5. The ophthalmic lens according to claim 1 wherein the optic is configured as a senes of concentπc circles. 6. The ophthalmic lens according to claim 1 wherein the optic is configured as a weave. 7. The ophthalmic lens according to claim 1 wherein the optic is configured as a pattern of particles. 8. The ophthalmic lens according to claim 1 wherein the pmhole-hke aperture includes an optical power for vision coπection. 9. The ophthalmic lens according to claim 1 wherein the pmhole-hke aperture has a diameter in the range of substantially .05 mm to substantially 5 0 mm. 10 The ophthalmic lens according to claim 1 wherein the optic has an outer diameter in the range of substantially 1.0 mm to substantially 8 0 mm 11. The ophthalmic lens according to claim 1 wherein the optic is composed of a matenal having varying degrees of opacity 12. The ophthalmic lens according to claim 1 wherein the ophthalmic lens is composed of a bio-compatible, non-dissolving matenal. 13. The ophthalmic lens according to claim 1 wherein the optic is composed of a bio- compatible, non-dissolving mateπal. 14 The ophthalmic lens according to claim 12 or claim 13 wherein the bio- compatible, non-dissolving mateπal is polymethyl methacrylate. 15. The ophthalmic lens according to claim 12 or claim 13 wherein the bio- compatible, non-dissolving mateπal is a medical polymer. 16. An ophthalmic lens compπsing: a lens body; an optic located in the lens body, the optic configured to produce light scatteπng, and a pinhole-hke optical aperture substantially in the center of the optic. 17 The ophthalmic lens according to claim 16 wherein the optic is configured to forward scatter parallel light reaching the optic and back scatter diverging light reaching the optic 18. The ophthalmic lens according to claim 16 wherein the optic is configured as a pattern of particles. 19. The ophthalmic lens according to claim 16 wherein the pmhole-hke aperture includes an optical power for vision coπection 20. The ophthalmic lens according to claim 16 wherein the pinhole-hke aperture has a diameter in the range of substantially .05 mm to substantially 5.0 mm. 21. The ophthalmic lens according to claim 16 where the optic has an outer diameter in the range of substantially 1.0 mm to substantially 8.0 mm. 22. The ophthalmic lens according to claim 16 wherein the optic is composed of a mateπal having varying degrees of opacity. 23. The ophthalmic lens according to claim 16 wherein the ophthalmic lens is composed of a bio-compatible, non-dissolving mateπal. 24. The ophthalmic lens according to claim 16 wherein the optic is composed of a bio-compatible, non-dissolving mateπal. 25. The ophthalmic lens according to claim 23 or claim 24 wherein the bio- compatible, non-dissolving matenal is polymethyl methacrylate. 26. The ophthalmic lens according to claim 23 or claim 24 wherein the bio- compatible, non-dissolving matenal is a medical polymer. 27. An ophthalmic lens compπsing: a lens body; an optic located in the lens body, the optic configured to produce light reflection; and a pinhole-like optical aperture substantially in the center of the optic. 28. The ophthalmic lens according to claim 27 wherein the optic is composed of a light reflective matenal. 29. The ophthalmic lens according to claim 27 wherein the optic is partially composed of a light reflective mateπal. 30 The ophthalmic lens according to claim 27 wherein the optic is composed of a pattern of curvatures 31 The ophthalmic lens according to claim 27 wherein the optic is configured as a senes of concentπc circles. 32. The ophthalmic lens according to claim 27 wherein the optic is configured as a weave. 33 The ophthalmic lens according to claim 27 wherein the optic is configured as a pattern of particles. 34. The ophthalmic lens according to claim 27 wherein the pinhole-hke aperture includes an optical power for vision coπection. 35. The ophthalmic lens according to claim 27 wherein the pinhole-hke aperture has a diameter in the range of substantially 05 mm to substantially 5.0 mm. 36. The ophthalmic lens according to claim 27 wherein the optic has an outer diameter in the range of substantially 1 0 mm to substantially 8.0 mm. 37 A method for increasing the depth of focus of the human eye, the method compnsing. providing an ophthalmic lens, the ophthalmic lens compπsing a lens body, an optic located in the lens body, the optic configured to produce light interference, and a pmhole-hke optical aperture substantially in the center of the optic; and fitting the ophthalmic lens 38 The method according to claim 37 wherein the optic is configured to positively interfere with parallel light reaching the optic and negatively interfere with diverging light reaching the optic. 39. The ophthalmic lens according to claim 38 wherein some of the diverging light passes through the optic. 40 The ophthalmic lens according to claim 39 wherein the optic is configured to spread out the diverging light passing through the optic. 41. A method for increasing the depth of focus of the human eye, the method compnsing' providing an ophthalmic lens, the ophthalmic lens compπsing a lens body, an optic located in the lens body, the optic configured to produce light scatteπng, and a pinhole-hke optical aperture substantially in the center of the optic; and fitting the ophthalmic lens. 42. The method according to claim 41 wherein the optic is configured to forward scatter parallel light reaching the optic and to back scatter diverging light reaching the optic 43. A method for increasing the depth of focus of the human eye, the method compnsing: providing an ophthalmic lens, the ophthalmic lens compπsing a lens body, an optic located in the lens body, the optic configured to produce light reflection, and a pmhole- ke optical aperture substantially in the center of the optic; and fitting the ophthalmic lens. 44 The ophthalmic lens according to claim 43 wherein the optic is composed of a light reflective matenal. 45 The method according to claim 43 wherein the optic is partially composed of a light reflective matenal. 46. A method for screening a patient for an ophthalmic lens, the ophthalmic lens having a p hole- ke optical aperture, the method compnsing fitting each of the patient's eyes with a first contact lens; placing a mask on each of the first contact lens, the mask configured to produce a pinhole-like aperture in each of the first contact lens; fitting each of the patient's eyes with a second contact lens, the second contact lens being placed over the mask to hold the mask in a substantially constant position, and testing the patient's vision. 47. The method of claim 46 wherein the mask is a light interference optic. 48. The method of claim 46 wherein the mask is a light scatteπng optic. 49. The method of claim 46 wherein the mask is a light reflective optic. 50. The method of claim 46 wherein each of the first contact lenses includes an optical power for vision coπection. 51. The method of claim 46 wherein each of the first and second contact lenses are soft contact lenses. 52. The method of claim 46 wherein the mask for each of the patient's eyes has a light absorption of substantially 100%. 53. The method of claim 46 wherein the mask for each of the patient's eyes is composed of a polaπzed mateπal. 54. The method of claim 46 wherein the process of testing further compπses: testing the patient's acuity for distance vision under bright lighting conditions; testing the patient's acuity for near vision under bπght lighting conditions; and testing the patient's contrast sensitivity under bπght lighting conditions. 55. The method of claim 46 wherein the process of testing further compπses- testing the patient's acuity for distance vision under dim lighting conditions; testing the patient's acuity for near vision under dim lighting conditions; and testing the patient's contrast sensitivity under dim lighting conditions. 56. The method of claim 46 wherein the process of testing further compπses: testing a patient's visual acuity using a night dnving simulation 57 The method of claim 56 wherein the night dnving simulation includes a senes of objects and road signs under bnght lighting conditions 58. The method of claim 56 wherein the night dπving simulation includes a senes of objects and road signs under dim lighting conditions. 59. The method of claim 56 wherein the night dnving simulation includes the patient facing a simulated oncoming automobile headlight. 60. The method of claim 52 wherein the process of testing further compnses' replacing the mask in one of the patient's eyes with a mask having a light absorption of substantially 85%. 61. The method of claim 60 wherein the process of testing further compnses: replacing the mask in the patient's other eye with a mask having a light absorption of substantially 85%. 62. The method of claim 61 wherein the process of testing further compπses. removing the mask from one of the patient's eyes. 63. The method of claim 52 wherein the process of testing further compπses: replacing the mask in one of the patient's eyes with a mask having a light absorption less than substantially 85%. 64 The method of claim 63 wherein the process of testing further compπses' replacing the mask in the patient's other eye with a mask having a light absorption less than substantially 85%. 65. The method of claim 64 wherein the process of testing further compπses removing the mask from one of the patient's eyes. 66. The method of claim 53 wherein the process of testing further compnses placing an analyzer in the spectacle plane of one of the patient's eyes, the analyzer including a polaπzing element, rotating the polaπzing element to achieve an optimal balance of contrast and bnghtness; and determining the resultant light absorption of the mask 67. The method of claim 46 wherein the process of testing further compnses evaluating the cosmetic appearance of the mask 68 A method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, the cornea compnsing an epithelial sheet, a Bowman's member, and a stroma, the stroma having a top layer, the method compπsing: removing the epithelial sheet; creating a depression in the Bowman's membrane, the depression being of sufficient depth and width to expose the top layer of the stroma and accommodate the mask; placing the mask in the depression; and placing the removed epithelial sheet over the mask. 69. The method according to claim 68 wherein the mask is a light interference optic. 70. The method according to claim 68 wherein the mask is a light scatteπng optic. 71. The method according to claim 68 wherein the mask is a light reflective optic 72. The method according to claim 68 wherein the mask blocks visual abeπations. 73. The method according to claim 68, further compπsing: placing a contact lens over at least the affected portion of the cornea until the epithelial sheet has adhered to the mask and the top layer of the stroma. 74 The method according to claim 68 wherein the depression extends into the top 9? layer of the stroma. 75. A method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, the cornea comprising an epithelial sheet, a Bowman's member, and a stroma, the stroma having a top layer, the method comprising: hinging open a portion of the Bowman's membrane; creating a depression in the top layer of the stroma, the depression being of sufficient depth and width to accommodate the mask; placing the mask in the depression; and placing the hinged Bowman's membrane over the mask. 76. The method according to claim 75 wherein the mask is a light interference optic. 77. The method according to claim 75 wherein the mask is a light scattering optic. 78. The method according to claim 75 wherein the mask is a light reflective optic. 79. The method according to claim 75 wherein the mask blocks visual abeπations. 80. The method according to claim 75, further comprising: placing a contact lens over at least the affected portion of the cornea until the epithelial sheet has grown over the hinged Bowman's membrane. 81. A method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, the cornea comprising an epithelial sheet, a Bowman's member, and a stroma, the stroma having a top layer, the method comprising: creating a channel in the top layer of the stroma, the channel being in a plane parallel to the cornea's surface; and placing the mask in the channel. 82. The method according to claim 81 wherein the mask is a light interference optic. 83. The method according to claim 81 wherein the mask is a light scattering optic. 84. The method according to claim 81 wherein the mask is a light reflective optic. 85 The method according to claim 81 wherein the mask blocks visual abeπations 86. The method according to claim 81 wherein the mask is threaded into the channel 87. The method according to claim 81 wherein the mask is injected into the channel. 88. A method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, the cornea compπsing an epithelial sheet, a Bowman's member, and a stroma, the stroma having a top layer, the method compπsing: penetrating the top layer of the stroma with an injecting device; and injecting the mask into the top layer of the stroma with the injecting device. 89. The method according to claim 88 wherein the mask is a light interference optic. 90. The method according to claim 88 wherein the mask is a light scatteπng optic. 91. The method according to claim 88 wherein the mask is a light reflective optic. 92. The method according to claim 88 wherein the mask blocks visual abeπations. 93. The method according to claim 88 herein the injecting device is a nng of needles. 94. The method according to claim 87 or claim 88 wherein the mask is a pigment. 95. The method according to claim 87 or claim 88 wherein the mask is composed of pieces of pigmented matenal suspended in a bio-compatible medium. 96. The method according to claim 95 wherein the pigmented matenal is a medical polymer. 97. The method according to claim 95 wherein the medical polymer is suture material. 98. A method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, the cornea compnsing an epithelium sheet, the method compπsing: hinging open a corneal flap, the corneal flap compπsing substantially the outermost 20% of the cornea; placing the mask on the cornea; and placing the hinged corneal flap over the mask. 99. The method according to claim 98 wherein the mask is a light interference optic. 100. The method according to claim 98 wherein the mask is a light scatteπng optic. 101. The method according to claim 98 wherein the mask is a light reflective optic. 102. The method according to claim 98 wherein the mask blocks visual abeπations. 103. The method according to claim 98, further compnsing: placing a contact lens over at least the affected portion of the cornea until the epithelial sheet has grown over the hinged corneal flap. 104 A method for implanting a mask in a cornea, the mask configured to increase the depth of focus of the human eye, the cornea compπsing a stroma, the method compπsing: creating a pocket in the stroma, the pocket being of sufficient size to accommodate the mask; and placing the mask in the created pocket. 105. The method according to claim 104 wherein the mask is a light interference optic. 106. The method according to claim 104 wherein the mask is a light scattenng optic. 107. The method according to claim 104 wherein the mask is a light reflective optic. 108. The method according to claim 104 wherein the mask blocks visual abeπations. 110591

Inventors: BLANCO ERNESTO, MILLER DAVID, BLANCO, ERNESTO, MILLER, DAVID
Applicants: BOSTON INNOVATIVE OPTICS INC, BOSTON INNOVATIVE OPTICS, INC.
Application year: 2000
Main classification: G02C7
IPC codes: G02C7