Extended focal depth intraocular lens

Abstract

To provide an extended focal depth intraocular lens.SOLUTION: An intraocular lens includes: an optic zone; and a modulation surface profile formed in the optic zone and configured to align a focus of an incident beam with a plurality of focuses. The modulation surface profile is incorporated by a base surface profile of the optic zone.SELECTED DRAWING: Figure 3

Description

[Technical Field]

[0001] The present disclosure relates to ophthalmic lenses, such as intraocular lenses (IOLs), and more particularly to extended depth of focus intraocular lenses. [Background technology]

[0002] The human eye includes a cornea and a lens that are intended to focus light that enters the eye's pupil onto the retina. However, the eye can exhibit various refractive errors that can result in light not being accurately focused onto the retina and reduced visual acuity. Ocular aberrations can range from relatively simple spherical and cylindrical errors that cause myopia, hyperopia, or regular astigmatism to more complex refractive errors that can cause, for example, halos and starbursts in a person's vision.

[0003] Many therapeutic interventions have been developed over the years to correct various ocular aberrations. These include spectacles, contact lenses, corneal refractive surgery such as laser in situ keratomileusis (LASIK) or corneal transplants, and intraocular lenses (IOLs). The specification of spherocylindrical spectacles and contact lenses for the diagnosis and treatment of myopia, hyperopia, and astigmatism is also well established.

[0004] During cataract surgery, or natural human lens replacement, an intraocular lens (IOL) is typically implanted in the patient's eye to compensate for the vision lost when the natural lens is expelled. For surgeons, the optimal outcome of cataract surgery is for the patient to experience 20 / 20 vision after the procedure and no additional intervention is required. One of the determining factors for achieving emmetropia is precise placement of the lens inside the eye. Other factors for achieving emmetropia are preoperative measurements, surgical technique, IOL design, and surgical experience. Current IOL designs require surgeons to place the IOL within a region of approximately 0.1 mm within the eye, i.e., the margin of error is ±0.05 mm. A patient's vision can be adversely affected by moderate postoperative residual refractive error in the treated eye. Summary of the Invention [Problem to be solved by the invention]

[0005] Therefore, there is a need for a system that provides an extended depth of focus IOL to reduce the impact that variations in lens placement and surgical technique have on the outcome of the procedure. [Means for solving the problem]

[0006] The present disclosure provides an intraocular lens that includes an optic zone and a modulated surface profile formed in the optic zone and configured to focus incident light rays to multiple focal points, the modulated surface profile being incorporated into a base surface profile of the optic zone.

[0007] In additional embodiments that may be combined with one another, unless clearly exclusive, there are provided intraocular lenses in which a plurality of foci produce a through-focus modulation transfer function that is symmetrical with respect to the distance focus, such that at least one of the plurality of foci is located myopically with respect to the distance focus, and at least one of the plurality of foci is located hyperopically with respect to the distance focus; an intraocular lens in which the plurality of foci include a maximum myopic focus and a maximum hyperopic focus, and the maximum myopic focus and the maximum hyperopic focus are each within 0.75 to 1.5 diopters of the distance focus; an intraocular lens in which each of the plurality of foci has one or more corresponding nearest foci, and each of the plurality of foci is separated from the one or more corresponding nearest foci by 1 diopter or less; an intraocular lens in which the modulation surface profile is a modified sinusoidal profile; an intraocular lens in which the modified sinusoidal profile is a function of radial position relative to the center of the intraocular lens, and the modified sinusoidal profile is defined by a combination of parameters including an amplitude parameter, a period parameter, and a phase constant parameter. an intraocular lens in which the amplitude parameter and the period parameter are functions of radial position; an intraocular lens in which the modulated surface profile is a triangular profile; an intraocular lens in which the triangular profile is a function of radial position relative to the center of the intraocular lens, the triangular profile comprising a plurality of triangular peaks and a plurality of intervals, each of the peaks having an amplitude and a width, and each of the intervals having a width; an intraocular lens in which the amplitude is the same for each of the plurality of peaks, the width of each of the plurality of peaks decreasing with increasing radial position, and the width of each of the plurality of intervals decreasing with increasing radial position; an intraocular lens in which the triangular profile comprises a flat portion in a central portion of the intraocular lens; an intraocular lens in which the modulated surface profile is a square of a sinusoidal profile; an intraocular lens in which the square of the sinusoidal profile is a function of radial position relative to the center of the intraocular lens, the square of the sinusoidal profile being defined by a combination of parameters including an amplitude parameter, a period parameter, and a phase constant parameter, and the square of the sinusoidal profile comprising a sign function component.

[0008] The present disclosure further provides an intraocular lens comprising an optic zone and a plurality of surface regions in the optic zone, each of the plurality of surface regions having a power corresponding to a focal length, the plurality of surface regions including a first surface region and a second surface region, the first surface region having a first power corresponding to the first focal length, the first power further corresponding to a through-focus modulation transfer function having peak performance, and a defocus corresponding to a percentage of the peak performance, the second surface region having a second power corresponding to a second focal length, the second focal length being offset from the first focal length by at least the defocus, and each of the plurality of surface regions having an area and configured to divide incident light rays among the plurality of surface regions.

[0009] In additional embodiments that may be combined with one another unless clearly exclusive, the intraocular lens further includes: a first surface region having a first radius and a first area, a second surface region extending from the first surface region to a second radius corresponding to the photopic aperture of the pupil, and the second surface region having a second area equal to the first area; and a third surface region, the first surface region having a first radius and a first area, the second surface region extending from the first surface region to a second radius and the second surface region having a second area equal to the first area, and the third surface region extending from the second surface region to a third radius corresponding to the mesopic aperture of the pupil, and the third surface region having a second area equal to the first area. an intraocular lens having a third area equal to the area of ​​the first focal length and a third surface area having a third power corresponding to a third focal length; an intraocular lens having a defocus corresponding to 45 to 75 percent of peak performance and the second focal length offset from the first focal length by 1.5 to 2.5 times the defocus; an intraocular lens having a defocus corresponding to 50 percent of peak performance and the second focal length offset from the first focal length by twice the defocus; an intraocular lens having a second focal length offset from the first focal length in the myopic direction; an intraocular lens having a second focal length offset from the first focal length in the myopic direction and a third focal length offset from the first focal length in the hyperopic direction by at least the defocus.

[0010] Any system described herein may be used with any method described herein, and vice versa. It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory in nature and are intended to provide an understanding of the present disclosure without limiting the scope of the disclosure. In that regard, additional aspects, features, and advantages of the present disclosure will become apparent to those skilled in the art from the following detailed description.

[0011] For a more complete understanding of the present invention, its features and advantages, reference is now made to the following descriptions taken in conjunction with the accompanying drawings, in which: [Brief explanation of the drawings]

[0012] [Figure 1] FIG. 1 shows an exemplary IOL. [Figure 2] FIG. 2 shows an example embodiment of an IOL having multiple surface regions. [Figure 3] FIG. 3 is a schematic diagram of the example IOL shown in FIG. 2 that focuses incident light rays at multiple foci. [Figure 4] FIG. 4 shows a plot of the modulation transfer function of a human eye corresponding to the example IOL shown in FIG. 2 compared with the modulation transfer function corresponding to a prior art IOL. [Figure 5] FIG. 5 is a schematic diagram of another example embodiment of an IOL that focuses incident light rays at multiple oscillating foci. [Figure 6] FIG. 6 shows a plot of an example embodiment of a modulated surface profile that may be used in the example IOL shown in FIG. [Figure 7] FIG. 7 shows a plot of the resulting oscillatory focal point position as a function of incident beam position corresponding to the example modulated surface profile shown in FIG. [Figure 8] FIG. 8 shows a plot of the resulting luminous intensity as a function of focal length corresponding to the example modulated surface profile shown in FIG. [Figure 9]FIG. 9 shows a plot of the modulation transfer function of the human eye corresponding to the example modulation surface profile shown in FIG. 6 compared to the modulation transfer function corresponding to a prior art IOL. [Figure 10] FIG. 10 shows a plot of simulated visual acuity corresponding to the example modulation surface profile shown in FIG. 6 compared to simulated visual acuity corresponding to a prior art IOL. [Figure 11] FIG. 11 shows a plot of another example embodiment of a modulated surface profile that may be used in the example IOL shown in FIG. [Figure 12] FIG. 12 shows a plot of the resulting oscillatory focal point position as a function of incident beam position corresponding to the example modulated surface profile shown in FIG. [Figure 13] FIG. 13 shows a plot of the modulation transfer function of the human eye corresponding to the example modulation surface profile shown in FIG. [Figure 14] FIG. 14 shows a plot of another example embodiment of a modulated surface profile that may be used in the example IOL shown in FIG. [Figure 15] FIG. 15 shows a plot of the resulting oscillatory focal spot position as a function of incident beam position corresponding to the example modulated surface profile shown in FIG. [Figure 16] FIG. 16 shows a plot of the modulation transfer function of the human eye corresponding to the example modulation surface profile shown in FIG. DETAILED DESCRIPTION OF THE INVENTION

[0013] The exemplary embodiments relate to ophthalmic devices such as IOLs and contact lenses. The following description is presented to enable one skilled in the art to make and use the invention and is provided in the context of a patent application and its requirements. Various modifications to the exemplary embodiments and the general principles and features described herein will be readily apparent. The exemplary embodiments are described primarily with reference to specific methods and systems provided in particular implementations. However, the methods and systems also work effectively in other implementations. For example, the methods and systems are described primarily with reference to IOLs. However, the methods and systems may also be used with contact lenses and eyeglasses.

[0014] In the following description, details are set forth as examples to facilitate discussion of the disclosed subject matter, however, it should be apparent to those skilled in the art that the disclosed embodiments are examples and do not encompass all possible embodiments.

[0015] As used herein, hyphenated forms of reference numerals refer to specific instances of elements, and unhyphenated forms of reference numerals refer to collective elements. Thus, for example, device "12-1" refers to an instance of a class of devices that may be collectively referred to as device "12," and any one of which may be generally referred to as device "12."

[0016] After cataract surgery, patients typically experience emmetropia or 20 / 20 vision in approximately 80% of cases. As described in more detail, it is disclosed that extended depth of focus IOLs, when used in cataract treatment, will result in a greater number of treatments with optimal emmetropia outcomes. The use of extended depth of focus IOLs may result in higher patient satisfaction, reduced likelihood of secondary surgical interventions such as implants, and a lower risk of vision changes if the lens becomes dislodged or fixed in the eye after treatment. Patients treated with extended depth of focus IOLs may not require additional corrective eyeglasses, spectacles, or contact lenses for distance vision after cataract surgery. Because less perfect surgical techniques and less sophisticated preoperative measurements may be required to achieve emmetropia, extended depth of focus IOLs may also be advantageously used in training for less experienced surgeons. Finally, extended depth of focus IOLs may allow for improved IOL design and / or improved IOL manufacturability.

[0017] Referring now to the drawings, in FIG. 1 , IOL 101 may refer to any type of IOL used for an eye. As shown, IOL 101 includes an optic zone 110 (also referred to herein simply as “optic”) and two haptics 112-1, 112-2. This is shown in an exemplary configuration for illustrative purposes. In various implementations, IOL 101 may include different types and numbers of haptics 112. In some implementations, IOL 101 may have no haptics. The materials used for optic zone 110 and haptics 112 may be different. For example, IOL 101 may be a non-foldable rigid IOL in which optic zone 110 includes a polymethylmethacrylate (PMMA) lens. In some implementations, IOL 101 can be a flexible IOL in which optic zone 110 can be composed of various materials, such as silicone, hydrophobic acrylic, hydrophilic acrylic, hydrogel, collamer, or combinations thereof. In IOL 101, haptics 112 can be composed of various materials, such as polypropylene, PMMA, hydrophobic acrylic, hydrophilic acrylic, silicone, or combinations thereof. Optic zone 110 can be designed to have a specific optical power or can be designed as a multifocal element with multiple optical powers. In particular, optic zone 110 can be implemented in an extended depth of focus IOL, for example, to provide extended vision around the distance focus. Accordingly, the present disclosure relates to surface modifications of a conventionally refractive, monofocal IOL optic.

[0018] 2, an example embodiment of an IOL having multiple surface regions is shown. IOL 200 may include an optic zone 202 divided into multiple surface regions, including first surface region 204 and second surface region 206. First surface region 204 and second surface region 206 may be concentric regions with their respective centers located at the center of optic zone 202. First surface region 204 may have a first area that may be defined as the area contained within a first radius R1. Second surface region 206 may have a first area that may be defined as the area contained between first radius R1 and second radius R2.

[0019] In some examples, R2 may be defined to correspond to the photopic aperture of the human eye. The photopic aperture corresponds to daylight conditions or approximately 3 candelas per square meter (cd / m 2 ) or greater. A typical photopic aperture of the human eye is about 3 mm in diameter (or 1.5 mm in radius). In another example, R2 may be defined to correspond to the mesopic aperture of the human eye. The mesopic aperture is larger than the photopic aperture and is typically less than 3 cd / m under moonlight or about 3 cd / m. 2 ~Approx. 0.01cd / m 2 1 illustrates the pupil aperture in dimly lit conditions, such as an ambient light intensity of 1000 Hz. A typical mesopic aperture of the human eye is approximately 5 mm in diameter (or 2.5 mm in radius). In still other examples, R2 may be defined to correspond to some other size aperture diameter, e.g., 3.5 mm, 4 mm, 4.5 mm, or may be arbitrarily sized.

[0020] In some examples, R1 may be defined such that a first area of ​​the first surface region 204 is equal to a second area of ​​the second surface region 206. Defining R1 in this manner results in approximately half of the incident light rays passing through the first surface region 204 and approximately half of the incident light rays passing through the second surface region 206. When the first surface region 204 and the second surface region 206 have equal areas, the following equation defines the relationship between R1 and R2:

number

[0021] In other examples, R1 may be defined such that the area of ​​first surface region 204 is greater than or less than the area of ​​second surface region 206. Thus, selection of R1 may allow for different designs of IOLs that split light between first surface region 204 and second surface region 206 in different proportions as needed for a given design.

[0022] While FIG. 2 illustrates an optic zone 202 having only two surface regions, other embodiments of IOLs having optic zones with more surface regions may also be designed. For example, an optic zone may be designed with three surface regions, where the third surface region may have a third area defined as the area contained between a third radius R3 and a second radius R2. When the optic zone has three regions, R3 may be defined to correspond to a photopic aperture, a mesopic aperture, an aperture of some other size, or may be arbitrarily sized. In some instances, R1 and R2 may be defined such that the areas of the first, second, and third surface regions are equal to one another. Defining R1 and R2 in this manner results in approximately one-third of the incident light passing through each of the surface regions. R1 and R2 can be calculated based on the set value of R3 using principles similar to those illustrated above. In other examples, R1 and R2 may be defined to have different areas from one or more of the surface regions, where the surface region has a smaller or larger area than one or more of the other surface regions.

[0023] Referring now to Figure 3, a schematic diagram of the example IOL shown in Figure 2 is shown, which focuses incident light rays at multiple focal points. As described above, IOL 200 may include a first surface region 204 and a second surface region 206. First surface region 204 may be characterized by a first power such that incident light rays passing through first surface region 204 are focused at focal point 302. Second surface region 206 may be characterized by a second power such that incident light rays passing through second surface region 206 are focused at focal point 304. Focus point 302 is located at a first focal distance 306 from IOL 200, and focal point 304 is located at a second focal distance 308 from IOL 200. In general, powers may be related to corresponding focal lengths by the following equation:

number

[0024] Focal point 302 is separated from focal point 304 by distance 310. The locations of focal points 302 and 304 may be selected to achieve a through-focus modulation transfer function (MTF) with an approximately plateau shape throughout the focus range. For example, the desired value for distance 310 may be determined by identifying the defocus plane or defocus at which the MTF of the monofocal lens reaches 50% of its maximum or peak performance. In other designs, the desired value for distance 310 may be determined by identifying the defocus plane or defocus corresponding to a different percentage of MTF peak performance, e.g., 45-75% of MTF peak performance. In one example, the MTF of an SN60WF monofocal lens with a power of 21.0 D may be simulated in a human eye model with a 3 mm pupil at 35°C with a resolution of 100 lp / mm. In this example simulation, the lens achieves 50% of its MTF peak performance in the human eye model at a defocus of 0.065 mm. In this example, a plateau through-focus MTF can be achieved by defining distance 310 as twice this defocus, or 0.13 mm. In other designs, distance 310 can be defined differently, for example, as at least the defocus, or 1.5 to 2.5 times the defocus. If focal points 302 and 304 are closely spaced, for each focal length and power, the MTF will achieve 50% of its peak at approximately the same defocus. Thus, positioning focal points 302 and 304 in this manner results in overlapping MTF performance within the focus range associated with distance 310.

[0025] In this example, the first power of first surface region 204 is set to 21.0D, and first focal length 306 is calculated based on the above equation for 21.0D power. The first posterior focal length 306 of the human eye model may be 18.3 mm. Second focal length 308 may then be offset by distance 310, which in this example is twice the defocus, or 0.13 mm. As shown in FIG. 3 , focal point 304 is located myopically relative to focal point 302 such that the magnitude of second focal length 308 is smaller than first focal length 306. However, in some designs of IOL 200, the magnitude of second focal length 308 may be greater than first focal length 306, and focal point 304 may be located hyperopically relative to focal point 302. Second focal length 308 may then be used to calculate the second power of second surface region 206. If focal point 304 is myopic relative to focal point 302 by twice the defocus, then the second power of second surface region 206 is set to 21.5 D. IOL 200 designed according to this embodiment may include first surface region 204 having a power of 21.0 D and second surface region 206 having a power of 21.5 D.

[0026] Referring now to Figure 4, a plot of the modulation transfer function corresponding to the example IOL shown in Figure 2 is shown compared to a modulation transfer function corresponding to a prior art IOL. Plot 402 shows the MTF performance of IOL 200 designed according to the example described above with respect to Figure 3. Plot 404 shows the MTF performance of the SN60WF monofocal lens for a 3mm photopic aperture condition, and plot 406 shows the MTF performance of the SN60WF monofocal lens for a 5mm mesopic aperture condition. As shown in Figure 4, IOL 200 provides plateau-like MTF performance over a wider range of focal lengths than either monofocal lens.

[0027] While the above description with respect to Figures 3 and 4 describes the performance of a particular embodiment of IOL 200, the scope of the disclosure is not so limited. For example, the first power of the first surface region may be based on a different monofocal lens having a different power. Furthermore, the simulation of the monofocal lens resulting in the MTF performance may be based on different inputs, including, but not limited to, a different eye model, different temperatures, resolution, aperture conditions, etc. Finally, as described above with respect to Figure 2, IOL 200 may have more than two surface regions. The principles described with respect to Figures 3 and 4 may be applied to IOLs with a greater number of surface regions. For example, an IOL may be designed with three surface regions, where the second and third surface regions are designed to have second and third powers for focusing incident light rays to myopic and hyperopic foci, respectively, relative to the focus associated with the first surface region. The focal lengths of the myopic and hyperopic foci may be offset from the first focus by the same distance or by different distances. The offset distance may be at least the defocus.

[0028] Referring now to FIG. 5, a schematic diagram of another example embodiment of an IOL that focuses incident light rays at multiple oscillating foci is shown. The IOL 500 may include an optic zone (not explicitly shown) that includes a modulating surface profile 502. The modulating surface profile 502 may be incorporated on one surface of a typically refractive monofocal IOL optic. The modulating surface profile 502 may also be formed as a pattern within the same material as the base IOL optic itself. The modulating surface profile 502 may introduce phase perturbations into the optical path of the incident light rays, resulting in, for example, a two-plane extended depth of focus around a distance focus. The incident light rays are focused at multiple alternating or oscillating foci around a base focus (not explicitly shown), e.g., foci 504, 506, and 508.

[0029] As shown in FIG. 5, light is focused at different foci depending on the incident ray height or position with respect to the optical axis 510. For example, incident rays close to the optical axis 510 may be focused at focus 506, incident rays near the periphery of the IOL 500 may be focused at focus 504, and incident rays at intermediate ray heights may be focused at focus 508. While FIG. 5 illustrates only three foci, the scope of the disclosure is not so limited. As described in more detail below, the modulated surface profile 502 may be designed to focus light at multiple foci or may be designed to focus light at continuous foci. For example, the foci may be considered continuous if each of the multiple foci is less than or equal to 1 diopter from each of its nearest foci.

[0030] Incident light rays at different heights or positions relative to the optical axis 510 can be focused onto different focal points due to local visual acuity variations of the modulated surface profile 502, for example, based on curvature and slope variations. Thus, the IOL 500 can produce an extended depth of focus in a range 512. The range 512 can encompass the foci 504, 506, and 508, and can also include, for example, a distance focus. At least one of the foci can be hyperopic relative to the distance focus, while at least one of the foci can be myopic relative to the distance focus. The range 512 can be defined by a maximum myopic focus and a maximum hyperopic focus. The range 512 can encompass, for example, approximately ±0.75 diopters to ±1.5 diopters relative to the distance focus. By alternating or oscillating the focal points at which incident light rays are focused, a symmetrical extension of the depth of focus can be achieved, and the effects of both myopic and hyperopic refractive errors can be reduced. Alternating focus may also reduce pupil size dependence, such that a similar range of depth of focus extension occurs for photopic and mesopic pupil conditions.

[0031] Referring now to FIG. 6, there is shown a plot of an example embodiment of a modulated surface profile that may be used with the example IOL shown in FIG. 5. A first example sag profile 600 may be used as the modulated surface profile 502 shown in FIG. 5 above. The sag profile 600 may be a modified sinusoidal profile. In general, the surface profile of a lens, for example, IOL 500, may be a surface profile of a base surface Z base and modulated surface profile Z MS The sum of (Z=Z base +Z MS ) can be shown as the base surface Z base may be defined by the following equation:

number

[0032] The sag profile 600 may be defined by the following equation:

number

number

number

[0033] For sag profile 600, the sinusoidal component may enable IOL 500 to produce continuous focus shifts. The phase constant Phi may enable IOL 500 to achieve symmetric through-focus MTF performance. In some examples, amplitude A may include position dependence, which may enable IOL 500 to have an extended range of focus variation or pupil size dependence or apodization. In other examples, amplitude A may be constant so that sag profile 600 is the same for all pupil sizes. As shown in FIG. 6, sag profile 600 illustrates one example design of a sag profile where a = 0.48 μm, b = 0.458, Phi = 4.8, and all other coefficients are set to zero. However, the scope of the present disclosure is not so limited. For example, each coefficient and parameter in the above equation may be selected and adjusted to produce a sag profile that provides a desired extended depth of focus for IOL 500.

[0034] Referring now to FIG. 7, a plot of the resulting oscillatory focus position as a function of incident ray position corresponding to the example modulated surface profile shown in FIG. 6 is shown. Plot 700 illustrates how IOL 500 can focus incident rays having various incident ray positions when sag profile 600 is included in the optic zone. For example, as shown in FIG. 7, an incident ray passing through IOL 500 at a position approximately 1 mm from the center of the lens can be focused at a point approximately 0.4 mm near relative to the base focal length, e.g., distance focus. As shown in FIG. 7, sag profile 600 can result in a depth of focus extension of approximately ±0.4 mm relative to the base focus. As noted above with respect to FIG. 6, the parameters of sag profile 600 can be adjusted to increase or decrease the depth of focus extension.

[0035] Referring now to FIG. 8, a plot of the resulting luminous intensity as a function of focal length corresponding to the example modulated surface profile shown in FIG. 6 is shown. Plot 800 illustrates the axial ray intensity at various focal lengths, which was generated using geometric ray tracing techniques. As shown in FIG. 8, plot 800 shows a continuous distribution of ray intensity near zero, which indicates the base focus, e.g., distance focus. The ray intensity remains relatively high within ±0.4 mm, similar to the depth of focus extension shown in FIG. 7.

[0036] Referring now to FIG. 9, a plot of the modulation transfer function corresponding to the example modulation surface profile shown in FIG. 6 is shown, compared to a modulation transfer function corresponding to a prior art IOL. Plot 900 shows the through-focus MTF performance of IOL 500 when sag profile 600 is included in the optic zone. The spatial frequency of plot 900 is equal to 20 / 40 resolution. For comparison, plot 902 shows the through-focus MTF performance of a monofocal IOL. Plots 900 and 902 were generated by simulating the IOL in a model of the human eye. Plot 900 shows a depth-of-focus extension similar to that shown in FIGS. 7 and 8. Plot 900 includes peaks at approximately 0.4 mm (or 1.0 diopter) on both the near and far sides of the base focal length, e.g., distance focus. Plot 902 shows that the monofocal IOL has MTF performance that approaches zero at these same locations.

[0037] Referring now to FIG. 10 , a plot of simulated visual quality corresponding to the example modulation surface profile shown in FIG. 6 is shown compared to simulated visual acuity corresponding to a prior art IOL. Plot 1000 shows the visual acuity of a model eye including IOL 500 when sag profile 600 is included in the optic zone. For comparison, plot 1002 shows the visual acuity of a model eye including a monofocal IOL. Plots 1000 and 1002 were generated by simulating the model eye including the IOL via a Monte Carlo method using 200 virtual eyes incorporating clinical variation in biometric data. Plot 1000 shows that the visual acuity of IOL 500 with sag profile 600 can maintain 0.1 LogMar performance, equivalent to 20 / 25 vision, from +0.75 diopters to −1.0 diopters with moderate postoperative refractive error. Plot 1002 shows that visual acuity for a monofocal IOL can degrade by up to 0.2 LogMar, which is equivalent to 20 / 32 visual acuity, in these same locations.

[0038] Referring now to FIG. 11 , a plot of another example embodiment of a modulation surface profile that may be used with the example IOL shown in FIG. 5 is shown. Another example sag profile 1100 may be used as the modulation surface profile 502 shown in FIG. 5 above. The sag profile 1100 may be a triangular profile including multiple triangular peaks and multiple intervals between the peaks. Each peak may have an amplitude and a width, and each interval may have a width. The sag profile 1100 may be a function of radial position relative to the center of the IOL 500. Furthermore, each peak may have the same amplitude, or the amplitudes may vary. The widths of the peaks and intervals may remain constant or may vary. For example, the width of the peaks may decrease with increasing radial position. The width of the intervals may also decrease with increasing radial position. The sag profile 1100 may also include a flat portion 1102 at the center of the IOL 500. The flat portion 1102 may direct incident light rays to a distance focus, thereby improving distance MTF performance. 11, sag profile 1100 illustrates one example design of a sag profile. However, the scope of the present disclosure is not so limited. For example, various parameters, including but not limited to the presence or absence of a flat portion of the sag profile, the width of the flat portion, the amplitude of the peaks, the width of the peaks, the width of the gaps, and the number of peaks and gaps, may be selected and adjusted to produce a sag profile that provides a desired extended depth of focus for IOL 500.

[0039] Referring now to FIG. 12, a plot of the resulting oscillatory focus position as a function of incident ray position corresponding to the example modulated surface profile shown in FIG. 11 is shown. Plot 1200 illustrates how IOL 500 can focus incident rays having various incident ray positions when sag profile 1100 is included in the optic zone. For example, as shown in FIG. 12, an incident ray passing through IOL 500 at a position approximately 1 mm from the center of the lens can be focused at a point approximately 0.3 mm near relative to the base focal length, e.g., distance focus. As shown in FIG. 12, sag profile 1100 can result in a depth of focus extension of approximately ±0.3 mm relative to the base focus. As noted above with respect to FIG. 11, the parameters of sag profile 1100 can be adjusted to increase or decrease the depth of focus extension.

[0040] Referring now to FIG. 13, a plot of the modulation transfer function corresponding to the example modulation surface profile shown in FIG. 11 is shown. Plot 1300 shows the through-focus MTF performance of IOL 500 when sag profile 1100 is included in the optic zone. Plot 1300 is generated by simulating IOL 500 with sag profile 1100 in a model of the human eye. Plot 1300 shows a depth of focus extension similar to that shown in FIG. 12. Plot 1300 shows that the MTF performance remains relatively high within ±0.3 mm, similar to the depth of focus extension shown in FIG. 12.

[0041] Referring now to Figure 14, there is shown a plot of another example embodiment of a modulated surface profile that may be used with the example IOL shown in Figure 5. Another example sag profile 1400 may be used as the modulated surface profile 502 shown in Figure 5 above. The sag profile 1400 may be a squared sinusoidal profile. The sag profile 1400 may be defined by the following equation:

number

number

[0042] Referring now to FIG. 15, a plot of the resulting oscillatory focus position as a function of incident ray position corresponding to the example modulated surface profile shown in FIG. 14 is shown. Plot 1500 illustrates how IOL 500 can focus incident rays having various incident ray positions when sag profile 1400 is included in the optic zone. For example, as shown in FIG. 15, an incident ray passing through IOL 500 at a position approximately 1 mm from the center of the lens can be focused at a point approximately 0.3 mm near relative to the base focal length, e.g., distance focus. As shown in FIG. 15, sag profile 1400 can result in a depth of focus extension of approximately ±0.3 mm relative to the base focus. As noted above with respect to FIG. 14, the parameters of sag profile 1400 can be adjusted to increase or decrease the depth of focus extension.

[0043] Referring now to FIG. 16, a plot of the modulation transfer function corresponding to the example modulation surface profile shown in FIG. 14 is shown. Plot 1600 shows the through-focus MTF performance of IOL 500 when sag profile 1400 is included in the optic zone. Plot 1600 is generated by simulating IOL 500 with sag profile 1400 in a model of the human eye. Plot 1600 shows a depth of focus extension similar to that shown in FIG. 12. Plot 1600 shows that the MTF performance remains relatively high within ±0.3 mm, similar to the depth of focus extension shown in FIG. 12. Plot 1600 includes peaks at approximately 0.4 mm (or 1.0 diopters) on both the near and far sides of the base focal length, e.g., distance focus.

[0044] The above disclosed subject matter should be considered illustrative and not limiting, and the appended claims are intended to encompass all such modifications, enhancements, and other embodiments that fall within the true spirit and scope of the present disclosure. Accordingly, to the maximum extent permitted by law, the scope of the present disclosure shall be determined by the broadest permissible interpretation of the following claims and their equivalents, and shall not be limited or constrained by the above detailed description.

Claims

1. The optic zone and a modulated surface profile formed in the optic zone and configured to focus incident light rays to a plurality of focal points; An intraocular lens comprising: An intraocular lens wherein the modulated surface profile is incorporated into the base surface profile of the optic zone.

2. 2. The intraocular lens of claim 1, wherein the plurality of foci produce a through-focus modulation transfer function that is symmetrical about the distance focus, such that at least one of the plurality of foci is located myopically relative to the distance focus and at least one of the plurality of foci is located hyperopically relative to the distance focus.

3. the plurality of foci includes a maximum near vision focus and a maximum far vision focus; and 3. The intraocular lens of claim 2, wherein the maximum near vision focus and the maximum far vision focus are each within 0.75 to 1.5 diopters from the distance focus.

4. each of the plurality of focal points has one or more corresponding nearest focal points; and An intraocular lens according to any one of claims 1 to 3, wherein each of the plurality of foci is separated from the one or more corresponding nearest foci by no more than 1 diopter.

5. the modulated surface profile is a modified sinusoidal profile; and the modified sinusoidal profile is a function of radial position relative to the center of the intraocular lens; the modified sinusoidal profile is defined by a combination of parameters including an amplitude parameter, a period parameter, and a phase constant parameter; and The intraocular lens according to any one of claims 1 to 4, wherein the amplitude parameter and the period parameter are functions of the radial position.

6. the modulated surface profile is a triangular profile; and the triangular profile is a function of radial position relative to the center of the intraocular lens; the triangular profile includes a plurality of triangular peaks and a plurality of intervals; each of the peaks has an amplitude and a width; each of the intervals has a width; the amplitude is the same for each of the plurality of peaks; the width of each of the plurality of peaks decreases as the radial position increases; and The intraocular lens according to any one of claims 1 to 4, wherein the width of each of the plurality of intervals decreases as the radial position increases.

7. The intraocular lens of claim 6 , wherein the triangular profile includes a flat portion in a central portion of the intraocular lens.

8. the modulated surface profile is a square of a sinusoidal profile; and the square of the sinusoidal profile is a function of radial position relative to the center of the intraocular lens; the square of the sinusoidal profile is defined by a combination of parameters including an amplitude parameter, a period parameter, and a phase constant parameter; and The intraocular lens according to any one of claims 1 to 4, wherein the square of the sinusoidal profile includes a sign function component.

9. The optic zone and a plurality of surface regions of the optic zone; an intraocular lens comprising: each of the plurality of surface regions having a power corresponding to a focal length; the plurality of surface regions includes a first surface region and a second surface region; the first surface area has a first power corresponding to a first focal length; the first power further corresponds to a through-focus modulation transfer function having peak performance, and the defocus corresponds to a percentage of the peak performance; the second surface area has a second power corresponding to a second focal length; the second focal length is offset from the first focal length by at least the defocus; and An intraocular lens, wherein each of the plurality of surface regions has an area and is configured to divide incident light rays among the plurality of surface regions.

10. the first surface region further having a first radius and a first area; the second surface area extends from the first surface area to a second radius corresponding to the photopic aperture of the pupil; and The intraocular lens of claim 9 , wherein the second surface region has a second area equal to the first area.

11. the plurality of surface regions further includes a third surface region; the first surface region has a first radius and a first area; the second surface region extends from the first surface region to a second radius; the second surface region has a second area equal to the first area; the third surface area extends from the second surface area to a third radius corresponding to the mesopic opening of the pupil; the third surface region has a third area equal to the second area; and 11. The intraocular lens of claim 9 or 10, wherein the third surface region has a third power corresponding to a third focal length.

12. the defocus corresponds to 45 to 75 percent of the peak performance; and An intraocular lens according to any one of claims 9 to 11, wherein the second focal length is offset from the first focal length by 1.5 to 2.5 times the defocus.

13. The intraocular lens according to any one of claims 9 to 12, wherein the second focal length is offset from the first focal length in the myopic direction.

14. the second focal length is offset from the first focal length in a near vision direction; and 13. The intraocular lens of claim 11 or 12, wherein the third focal length is offset from the first focal length by at least the defocus in the far vision direction.

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