Diffractive intraocular lenses for extended range of vision

Abstract

Apparatuses, systems and methods for providing improved ophthalmic lenses, particularly intraocular lenses (IOLs). Exemplary diffractive intraocular implants (IOLs) can include a diffractive profile having multiple diffractive zones. The diffractive zones can include a central zone that includes one or more echelettes and a peripheral zone beyond the central zone having one or more peripheral echelettes. The central diffractive zone can work in a higher diffractive order than a remainder of the diffractive profile. The combination of the central and peripheral zones and an optional intermediate zone provides a longer depth of focus than a diffractive profile defined just by a peripheral and/or optional intermediate zone.

Description

BACKGROUND

Embodiments of the present disclosure relate generally to ophthalmic lenses, such as intraocular lenses (IOLs), and particular embodiments provide methods, devices, and systems for mitigating or treating vision conditions such as presbyopia via ophthalmic lenses.

SUMMARY

Embodiments herein described include an ophthalmic lens with a first surface and a second surface disposed about an optical axis, the lens being characterized by a depth of focus across a range of optical powers, i.e. an extended depth of focus (EDOF) that achieves an extended range of vision (ERV). A diffractive profile is imposed on one of the surfaces and configured to cause a distribution of non-negligible amounts of light among the depth of focus. The diffractive profile includes at least a central zone with at least one central diffractive echelette having a first phase delay, and a peripheral zone comprising at least one peripheral diffractive echelette having a second phase delay less than the first phase delay. In some embodiments, a third, intermediate zone may also be provided comprising at least one intermediate diffractive echelette having a third phase delay less than the first phase delay.

The central zone operates primarily in a higher diffractive order than the peripheral zone; and may also operate in a higher diffractive order than an optional intermediate zone. The incorporation of the central diffractive zone in the lens provides the combined diffractive profile (central zone+peripheral zone) with a longer depth of focus than that achieved by a diffractive profile defined just by the peripheral zone; and provides a longer depth of focus than a diffractive profile defined by the peripheral and an optional intermediate zone. The peripheral zone and/or optional intermediate zones may operate primarily in the first and/or second diffractive orders and distribute light to the far and intermediate ranges of viewing distances; while the central zone, which operates primarily in the second or third diffractive orders, distributes light primarily to the intermediate and/or near ranges of viewing distances. In combination, the combination of the central, peripheral, and optional intermediate diffractive zones provide light to an extended range of viewing distances. Embodiments also provide for high total light efficiency, in some cases capturing more than 90% of incident light in the complete range of vision. Embodiments also correct or partially correct for chromatic aberration in the range of vision.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a graphical representation of a first example diffractive lens profile showing a central diffractive zone having one diffractive echelette, and a peripheral diffractive zone, according to some embodiments of the present invention;

FIG. 2 is a graphical representation of a second example diffractive lens profile showing a central diffractive zone having multiple diffractive echelettes, and peripheral diffractive zone, according to some embodiments of the present invention;

FIG. 3 is a graphical representation of simulated visual acuity of an example diffractive lens according to FIG. 1 compared to a diffractive lens having only a peripheral diffractive profile, according to some embodiments of the present invention;

FIG. 4 is a graphical representation of simulated visual acuity of example diffractive lenses having multiple combinations of central and peripheral diffractive zones, according to some embodiments of the present invention;

FIG. 5 is a graphical representation showing simulated defocus curves of example lenses having varied central diffractive zones, according to some embodiments of the present invention;

FIG. 6 is a graphical representation of an example diffractive lens profile, showing a central diffractive zone, peripheral diffractive zone, and intermediate diffractive zone, according to some embodiments of the present invention;

FIG. 7 is a graphical representation of simulated defocus curves of example lenses having a central diffractive zone, intermediate diffractive zone, and peripheral diffractive zone, similar to the lens of FIG. 6, with comparison to a lens having only peripheral and intermediate diffractive zones, according to some embodiments of the present invention;

FIG. 8 is a simplified block diagram illustrating a system for generating a diffractive ERV lens surface, in accordance with embodiments;

FIG. 9 illustrates an example process for generating a diffractive ERV lens surface; and

FIG. 10 illustrates an example computing environment for facilitating the systems and processes of FIGS. 8 and 9.

DETAILED DESCRIPTION

In the following description, various embodiments will be described. For purposes of explanation, specific configurations and details are set forth in order to provide a thorough understanding of the embodiments. However, it will also be apparent to one skilled in the art that the embodiments may be practiced without the specific details. Furthermore, well-known features may be omitted or simplified in order not to obscure the embodiment being described.

Embodiments herein disclosed relate to diffractive intraocular lenses for providing extended depth of focus to a patient (ERV lenses). According to some embodiments, an intraocular lens can include a diffractive profile having a central diffractive zone that works in a higher diffractive order than a remainder of the diffractive profile. Suitable diffractive lenses can have a light efficiency (i.e., total light passed to the diffractive orders as a percentage of incident light) of approximately 90%, distributed over a defocus range that covers at least three different diffractive orders within the visual range, and with at least a non-zero or non-negligible percentage of light distributed to each diffractive order. According to some embodiments, a diffractive lens can partially correct for ocular chromatic aberration. In alternative embodiments, the diffractive lens can fully correct or over-correct for ocular chromatic aberration.

Embodiments of lenses herein disclosed can be configured for placement in the eye of a patient and aligned with the cornea to augment and/or partially replace the function of the cornea. In some embodiments, corrective optics may be provided by phakic IOLs, which can be used to treat patients while leaving the natural lens in place. Phakic IOLs may be angle supported, iris supported, or sulcus supported. IOLs can be further secured with support members that attach the IOL to the eye, e.g., with physical extensions from the IOL into adjacent corneal or iris tissue. Phakic IOLs can also be placed over the natural crystalline lens or piggy-backed over another IOL. Exemplary ophthalmic lenses include contact lenses, phakic lenses, pseudophakic lenses, corneal inlays, and the like. It is also envisioned that the lens shapes disclosed herein may be applied to inlays, onlays, accommodating IOLs, spectacles, and even laser vision correction.

As used herein, non-zero may refer generally to a non-negligible or non-trivial amount of light, typically at least 10% of the total light passing through the lens for IOLs.

Embodiments disclosed herein can provide an extended depth of focus. In some embodiments, diffractive intraocular lenses herein can provide better distance, intermediate, and/or near image quality than presently available multifocal lenses while mitigating certain dysphotopsia effects, such as glare or halo.

Methods of manufacture for diffractive lenses as disclosed herein, as well as methods of treatment utilizing said diffractive lenses, may include techniques described in, e.g., U.S. Pat. No. 9,335,563, entitled “MULTI-RING LENS, SYSTEMS AND METHODS FOR EXTENDED DEPTH OF FOCUS,” which is hereby incorporated by reference.

Diffractive lenses can make use of a material having a given refractive index and a surface curvature which provide a refractive power. Diffractive lenses have a diffractive profile which confers the lens with a diffractive power or power profile that may contribute to the base power of the lens. The diffractive profile is typically characterized by a number of diffractive zones. When used for ophthalmic lenses these diffractive zones are typically annular lens zones, or echelettes, spaced about the optical axis of the lens. Each echelette may be defined by an optical zone, a transition zone between the optical zone and an optical zone of an adjacent echelette, and echelette geometry. The echelette geometry includes an inner and outer diameter and a shape or slope of the optical zone, a height or step height, and a shape of the transition zone. The surface area or diameter of the echelettes largely determines the diffractive power profile of the lens and the step height of the transition between echelettes largely determines the light distribution within the diffractive power profile. Together, these echelettes form a diffractive profile.

ERV intraocular lenses (IOLs) are intended to provide a patient with improved vision in a range of distances, covering near, intermediate and far vision. Near range of vision may generally correspond to vision provided when objects are at distances from about 33 up to 60 cm from a subject eye with the image substantially focused on the subject retina, and may correspond to a vergence of approximately −1.6 D to −3 D. Intermediate range of vision may generally correspond to vision for objects at a distance between 63 cm up to 1.3 m from a subject eye with the image substantially focused on the subject retina, and may correspond to a vergence of approximately −1.6 D to −0.75 D. Far range of vision may generally correspond to vision for objects at any distance greater than about 1.3 m from a subject eye with the image substantially focused on the subject retina, and may correspond to a vergence of less than −0.75 D. In the case of an ERV lens, or a lens having an extended depth of focus, the diffractive profile can provide a plurality of focal lengths that overlap across a range of optical powers to provide good visual acuity throughout the extended depth of focus.

A traditional multifocal diffractive profile on a lens may be used to mitigate presbyopia by providing two or more optical powers, for example, one for near vision and one for far vision. The diffractive lenses disclosed herein provide an extended depth of focus across a range of optical powers. The concepts disclosed here apply to both ERV lenses and multifocal lenses. The lenses may also take the form of an intraocular lens placed within the capsular bag of the eye, replacing the original lens, or placed in front of the natural crystalline lens. The lenses may be in the form of a contact lens, most commonly a contact lens that extends the depth of focus, or in any other form mentioned herein.

In some embodiments, a diffractive profile can include multiple diffractive zones, e.g., a central zone that includes one or more echelettes, and a peripheral zone beyond the central zone having one or more peripheral echelettes. In some specific embodiments, an intermediate diffractive zone between the central and peripheral zones may be added to the diffractive profile. Each diffractive zone may include some form of apodization. In this context, apodization means that the light distribution gradually varies between adjacent echelettes, but light remains directed to the same non-negligible diffractive orders for all echelettes within the zone. In some specific embodiments, a refractive zone may be added to a lens surface outside of the peripheral diffractive zone. In some other embodiments one or more of the diffractive zones comprise apodized diffractive surfaces. The diffractive properties of each component echelette of a diffractive zone or diffractive profile are caused by the physical parameters of the component echelettes, e.g. step height, shape, and width. A single echelette can be characterized by its phase delay, a phase delay of a zone can be characterized by the individual phase delays of its component echelettes, and a phase delay of a lens profile can be characterized by the phase delays of the echelettes and/or zones within the profile.

FIG. 1 is a graphical representation of an example lens profile 100 having a central echelette 102 that defines a central diffractive zone 101 and multiple peripheral echelettes 104 that define a peripheral diffractive zone 103 of the lens. In some embodiments, a refractive zone 114 can extend outside of the peripheral diffractive zone 103. The central diffractive zone 101 extends from a lens center 116 to the central zone boundary 105. The peripheral zone 103 extends from the central zone boundary 105 to the peripheral zone boundary 106. The specific example provides seven peripheral echelettes 104; however, lenses may have more or fewer echelettes in the peripheral zone without deviating significantly from this disclosure. The specific lens profile shown is described below in Table 1. Positions are shown in terms of the diffractive zone boundary relative to the lens center. The position of each particular echelette is determined by the position of the first echelette (e.g. 0.84 mm in the example at Table 1, below,) multiplied by the squared root of the echelette number.

TABLE 1
Diffractive lens profile 100 (FIG. 1)
	# of	Phase Delay	Step Height	Position
Zone	Echelettes	(λ)	(μM)	(mm)
Central	1	2.51	10.3 (107)	0.84 (105)
(101)
Peripheral	7	1.2	4.9 (108)	2.38 (106)
(103)
Refractive	0	0	0	>2.38 (114)
(114)

The diffractive lens profile 100 shown in FIG. 1 features a central diffractive zone 101 defined by a single central echelette 102 that has a larger phase delay than the remaining echelettes (approximately 2.51λ). The central zone 101 is joined to the peripheral zone 103 by a step height 107 that can be different, and in some cases larger, than the step heights 108 separating echelettes in the peripheral zone. Phase delay is defined in terms of the period of the design wavelength, in this case 550 nm. Phase delay is the difference in phase between the light having passed through two adjacent echelettes. By virtue of the high phase delay, this central echelette operates primarily in the 2^nd and 3^rd diffractive orders, which directs light predominantly toward the intermediate and near visual ranges. The diffractive profile outside the central zone, i.e. the peripheral echelettes 104, operate predominantly in the 1^st and 2nd diffractive orders, the 1^st diffractive order adding light to the far focal range for distance vision.

The diffractive profile partially corrects chromatic aberration induced by the ocular media and/or the lens material in the range of vision provided by the lens. The distributions of light obtained by the components of the example lens 100, and by the total lens, are shown below in Table 2. Table 2 refers the light distribution at the far visual range (i.e. by the first diffractive order) as well as to the light distribution within the complete visual range provided by the diffractive profile (i.e. distance and extended depth of focus). This complete visual range is herein defined as the combination of the first, second and third diffractive orders. In alternative embodiments, the visual range can also include the light distribution for the fourth diffractive order.

TABLE 2
Light distributions of example lens profile 100
	Order	1 (Far)	Visual Range
	Peripheral	0.85	0.94
	Central +	0.60	0.92
	Peripheral

By way of comparison, a bifocal lens typically has a light loss of less than 20% of incident light (e.g., in some cases, of about 18% of incident light). Thus, the example ERV diffractive lens profile 100, which has a light loss of only about 8%, loses less than half as much light as a standard multifocal lens. Furthermore, a typical multifocal bifocal profile with a 50:50 light distribution between distance and near provides with 40% of light for distance vision. The example at Table 2 provides a 20% more light for far, with having a total of 60% light directed to distance.

In alternative embodiments, a lens may have a central diffractive zone defined by multiple diffractive echelettes rather than a single diffractive echelette. FIG. 2, for example, illustrates a diffractive lens profile 200 that is similar to the diffractive lens profile 100, with an expanded central zone 201 having a first central echelette 202 and a second central echelette 218 separated by a central step height 207. A peripheral zone 203 is characterized by peripheral echelettes 204 separated by step heights 208, the peripheral zone ending at a peripheral zone boundary 206. Optionally, a refractive periphery 214 may extend beyond the peripheral zone boundary 206. In this example profile, the central diffractive zone 201 is connected with the peripheral zone 203 by a transition step height 220, which is similar to the transition step height 107. According to embodiments, the example lens profile 200 can also achieve an extended depth of focus as the diffractive lens profile 100, and in some cases may further increase light directed to the 2nd and 3rd diffractive order.

FIG. 3 shows a graphical representation of simulated visual acuities 300 of the example lens 100 and a sibling diffractive design in which all echelettes have the same step heights a the peripheral component as shown in Tables 1, above. The calculations of simulated visual acuity were performed according the methods described in Aixa Alarcon, Carmen Canovas, Robert Rosen, Henk Weeber, Linda Tsai, Kendra Hileman, and Patricia Piers, “Preclinical metrics to predict through-focus visual acuity for pseudophakic patients,” Biomed. Opt. Express 7, 377-1888 (2016). The example simulated visual acuities 300 illustrate that the incorporation of the central zone extends the depth of focus with respect to that provided by the echelettes with steps heights that define the peripheral zone by approximately 1 D (i.e., referring to the defocus range with a visual acuity over a threshold of about 0.2 Log MAR).

In some (general) embodiments, the phase delay in the central echelette can be larger than 2λ and smaller than 4λ. In specific embodiments, phase delay can range from about 2.3λ up to 3.5λ, or from 2.45λ to 3.2λ, or from 2.5λ to 2.95λ. The number of echelettes is determined based on the desired geometry of each echelette and the available radius. The number of echelettes may vary from as few as 8 to up to 32 in some specific embodiments within a lens diameter of 6 mm. In specific embodiments, the first echelette may be positioned with an echelette boundary between 0.5 and 0.9 mm from a center of the lens, with a remainder of the echelettes placed according the position of the first echelette multiplied by the square root of the echelette number. In some embodiments, the phase delay of the peripheral echelettes can range from 1λ and can be smaller than 2λ. In specific embodiments, phase delay can range from about 1λ up to 1.5λ, or from 1.2λ to 1.5λ, or from 1.336λ to 1.5λ.

Various peripheral diffractive zone profiles may be combined with an elevated central profile to achieve different specific lens prescriptions. For example, various alternative embodiments of peripheral diffractive lens profiles are shown below in Table 3.

TABLE 3
Alternative examples of diffractive lens
profiles with varying peripheral zones
	# of	Phase Delay	Step Height	Position
Zone	Echelettes	(λ)	(μM)	(mm)
Central 1	1	2.51	10.3	0.84
Peripheral 1	7	1	4.1	2.38
Peripheral 3	7	1.366	5.6	7.38

These peripheral zones can be combined with a central zone like described in Table 1. Therefore, the step height of the central zone is constant across the examples; and the step heights and phase delays of the diffractive echelettes in the peripheral zone are modified. In each example, the peripheral echelettes have the same step heights across the zone, which vary between 4.1 and 5.6 microns. The position of the echelettes in each peripheral diffractive profile is determined in the same way for each example combination (i.e. the position of one particular echelette is that of the central multiplied by the square root of the echelette number).

FIG. 4 shows a graphical representation of simulated visual acuities 400 of the example lenses of Table 3, above as compared to these of the sibling diffractive designs in which all echelettes have the same step heights as the peripheral component 1 and 3 respectively, as shown in Table 3. In all the cases, the combination with the higher order central echelette provides a longer depth of focus than the peripheral profile alone. The example simulated visual acuities 400 illustrate that, by varying the phase delays and step heights of the peripheral echelettes, a lens can be tuned to provide greater visual acuity at intermediate or distance, depending on the desired prescription of the lens.

In some embodiments, the step heights in the central zone can be modified as well. For example, Table 4, below, illustrates alternative embodiments having different step heights in the central zone.

TABLE 4
Alternative examples of diffractive
lens profiles with varying central zones
	# of	Phase Delay	Step Height	Position
Zone	Echelettes	(λ)	(μM)	(mm)
Central 1*	1	2.51	10.3	0.84
Central 3	1	3.2	13.13	0.84
*Note that Central 1 is the same central zone provided above in TABLE 1 and 3.

The central zone is working between the 2nd and 3rd diffractive order for the example Central 1. The central zone is working between the 3rd and 4th diffractive order for the example Central 3. The same peripheral zone 3 as described in the previous example can be combined with other central zones. Within the same peripheral zone, all echelettes have the same step height. The light distributions resulting from the above-referenced combinations of profiles are shown below in Table 5 for the far visual range (i.e. first diffractive order) as well as for two different visual ranges. Visual Range 1 contains the light distribution for the first, second and third diffractive order, while Visual Range 2 contains the light distribution for the diffractive orders at Visual Range 1 as well as the fourth diffractive order:

TABLE 5
Light distributions of diffractive lens
profiles with varying central zones
			Visual	Visual
	Order	1 (Far)	Range 1	Range 2
	Central 1 +	0.44	0.89	0.91
	Peripheral
	Central 3 +	0.43	0.86	0.91
	Peripheral

Varying the central zone parameters can adjust the amount of light distributed between the intermediate and near range. For combinations that have a central zone working between the third and fourth diffractive order (i.e. combinations with Central 3), there is an additional, non-trivial amount of light (i.e. greater than 10% of incoming light) distributed to an additional diffraction order to further extend the range of vision. The total light efficiency in distance, intermediate and near is 91%, which is greater than the typical light efficiencies of multifocal IOLs.

FIG. 5 shows simulated defocus curves 500 showing visual acuity for the example lenses described above with reference to Tables 4-5. In all the cases, the incorporation of the central zone further enlarges the depth of focus with respect to that provided by the peripheral zone alone. Simulated defocus curves show that the near and intermediate visual performance for each lens is affected by the change in step height of the central zone, i.e., increasing the step height further enlarge the depth of focus. The combination with the higher step height creates a continuous range of vision longer than 3 D with at least 0.2 Log MAR visual acuity.

FIG. 6 shows graphical representation of an example lens profile 600 having a central echelette 602 in a central diffractive zone 601, multiple intermediate echelettes 606 in an intermediate diffractive zone 605, multiple peripheral echelettes 604 in a peripheral diffractive zone 603 of the lens, and a refractive zone 614 outside of the peripheral diffractive zone 603. The central diffractive zone 601 extends from a lens center 616 to the central zone boundary 610. The intermediate diffractive zone 605 is added between the central and peripheral diffractive zones 601, 603, thus extending from the central zone boundary 610 to the intermediate zone boundary 612. The peripheral zone 603 extends from the intermediate zone boundary 612 to the peripheral zone boundary 611. The intermediate diffractive zone 605 may have one or multiple intermediate echelettes 606. In this example lens profile 600, the intermediate diffractive zone 605 has two echelettes and the peripheral diffractive zone 603 has five. The step heights 609 of the intermediate echelettes 606 are lower than the step heights 608 of the peripheral echelettes 604 in the example shown, however, the step heights of the intermediate echelettes may be higher than in the peripheral diffractive zone in alternative embodiments. The specific lens profile shown is described below in Table 6. Positions are shown in terms of the diffractive zone boundary relative to the lens center. The position of each particular echelette is determined by the position of the first (i.e. 0.84 mm in the example at Table 6) multiplied by the squared root of the echelette number.

TABLE 6
Examples of diffractive lens profiles with an intermediate zone
	# of	Phase Delay	Step Height	Position
Zone	Echelettes	(λ)	(μM)	(mm)
Central	1	2.51	10.3 (607)	0.84 (610)
(601)
Intermediate	2	1.20	4.9 (609)	1.46 (612)
(605)
Peripheral	5	1.366	5.6 (608)	2.38 (611)
(603)
Refractive	0	0	0	>2.38 (614)
(614)

FIG. 7 shows simulated defocus curves 700 for the example lenses shown in FIG. 6 and described in Table 6 as compared to that of a profile without the higher order echelette (i.e. with the same intermediate, peripheral and refractive zones). In that profile, the central echelette has the same step height as the intermediate zone. FIG. 7 shows that the incorporation of the central echelette increases the depth of focus provided by the combination of the intermediate and peripheral diffractive profiles by approximately 1 D, for a cut-off visual acuity of 0.2 Log MAR.

Table 7 shows the light distribution calculated for 3 mm and 5 mm pupil for the diffractive profile at Table 6 and for a sibling diffractive profile that does not incorporate the intermediate zone. Therefore, this sibling profile has also 8 echelettes, being the central the same as in Table 6 and the remaining 7 echelettes according to the description for the peripheral zone provided in Table 6. Light distribution is shown at Table 7 for distance as well as for the range of vision provided by the lens (i.e. distance and extended depth of focus). Table 7 shows that, for a 3 mm pupil, there is a 58% of light directed to distance when the intermediate zone is included in the diffractive profile, while there is a 44% of light for far without this zone. For a 5 mm pupil the light distribution at distance are 61% and 51% for the profiles with and without the intermediate zone. Therefore, the incorporation of the intermediate zone 605 (FIG. 6) can provide an improvement in the light distribution at distance for both photopic (i.e. 3 mm pupil) and mesopic conditions (i.e. 5 mm pupil) as compared to the case when only the central and peripheral zones are included in the diffractive profile. Furthermore, the amount of light directed to distance is less affected by changes in pupil size when the intermediate zone is included in the combination. While the light directed to distance changes by 5% for the combination with the intermediate diffractive zone, there is a change of 27% in light distribution for distance when only the central and peripheral zones are combined.

TABLE 7
Light distributions of diffractive lens
profiles with varying zone configurations
		1	Visual
Order		(far focus)	Range
Central +	3 mm pupil	0.58	0.92
Intermediate +	5 mm pupil	0.61	0.90
Peripheral
Central 1 +	3 mm pupil	0.44	0.89
Peripheral (no	5 mm pupil	0.56	0.89
intermediate)

According to various embodiments, the phase delay in the central echelette can be larger than 2λ and smaller than 4λ. In specific embodiments, phase delay can range from about 2.3λ up to 3.5λ, or from 2.45λ to 3.2λ, or from 2.5λ to 2.95λ. The number of echelettes can be determined based on the desired geometry of each echelette and the available radius. In some specific embodiments, the number of echelettes may vary from as few as 8 to up to 32. The first echelette may be positioned with an echelette boundary between 0.5 and 0.9 mm from a center of the lens, with a remainder of the echelettes placed according the position of the first echelette multiplied by the square root of the echelette number. In some embodiments, the phase delay of the peripheral echelettes can range from 1λ and can be smaller than 2λ. In specific embodiments, phase delay can range from about 1λ up to 1.5λ, or from 1.2λ to 1.5λ, or from 1.336λ to 1.5λ. In some embodiments, the phase delay of the echelettes in the intermediate zone can be smaller than that of the echelettes at the peripheral zone by 0.05λ up to 0.5λ, or by 0.10λ to 0.25λ. In alternative embodiments, the phase delay of the echelettes in the intermediate zone may vary. In alternative embodiments, the phase delay of the echelettes in the intermediate zone may be greater than that of the echelettes in the peripheral zone by 0.05λ up to 0.5λ, or by 0.05λ to 0.15λ.

Exemplary Light Distributions by Diffractive Order

Specific light distributions across the visual range of the extended depth of field can be calculated in part on the basis of the portion of light directed by each diffractive order in each respective diffractive zone. For example, Table 8, below, lists light distributions according to diffractive order for a specific embodiment of a diffractive ERV lens similar to the lens of FIG. 1 and Table 1, i.e. having central and peripheral diffractive zones, where the central diffractive zone operates predominantly in a higher order than the remaining echelettes. As shown, a majority of light that passes through the central diffractive zone is directed according to the second and third diffractive orders, whereas a majority of light that passes through the peripheral zone is directed according to the first and second diffractive orders. Total light distribution for the combined lens profile is also shown, with approximately 60%° of light directed to the first diffractive order that provides the distance visual range, and 19% and 14% are directed to the second and third diffractive orders that create the extended depth of focus. All, first, second and third diffractive orders have a non-negligible light distribution (i.e. greater than 10%) and create an extended range of vision that covers distance, intermediate and near as shown in FIG. 3. The combined diffractive profile directs 92% of light toward the entire range of vision. Therefore, it is more efficient than traditional bifocal diffractive lenses that lose approximately 18% of the light (82% is used for the entire range of vision).

TABLE 8
Light Distribution by Diffractive Order across Central and Peripheral
Diffractive Zones for profile described in Table 1
		1	2	3
Order	0	distance	EDF	EDF	4	Visual Range
Central	0.01	0.03	0.43	0.43	0.03	0.89
Peripheral	0.02	0.85	0.07	0.01	0.00	0.94
Combined	0.02	0.60	0.19	0.14	0.01	0.92

Table 9, below, lists light distributions according to diffractive order for a specific embodiment of a diffractive ERV lens similar to the lenses described in Table 3, i.e. having the same central zone and different peripheral diffractive zones, where the central diffractive zone operates predominantly in a higher order than the remaining echelettes. As shown, a majority of light that passes through the central diffractive zone is directed according to the second and third diffractive orders. For the peripheral1 diffractive profile, the majority of light is directed according to the first diffractive order. For the peripheral3 diffractive profile, the majority of light is directed according to the first and second diffractive orders. Total light distributions for the combined lens profiles are also shown. In both cases, there is a non-negligible amount of light directed to the first, second and third diffractive orders. The light distribution for distance is greater than for the combination with peripheral 1 than for the combination with peripheral 3. However, the light distribution at the second diffractive order is greater for the combination with the peripheral3 profile. That results in a better intermediate performance for this combination, as shown in FIG. 4. The light distribution at the third diffractive order is quite insensitive to modifications in the peripheral diffractive profile. In both cases, the combined diffractive profile directs at least 89% of light toward the extended range of vision. Therefore, it is more efficient than traditional bifocal diffractive lenses that loss approximately 18% of the light.

TABLE 9
Light Distribution by Diffractive Order across Central and
Peripheral Diffractive Zones for profile described in Table 3
		1	2	3
order	0	distance	EDF	EDF	4	Visual Range
Central	0.01	0.03	0.43	0.43	0.03	0.89
Peripheral1	0.01	0.98	0.01	0.00	0.00	0.99
Peripheral3	0.04	0.62	0.23	0.03	0.01	0.89
Central +	0.01	0.68	0.14	0.14	0.01	0.96
Peripheral1
Central +	0.03	0.44	0.29	0.16	0.02	0.89
Peripheral3

Table 10, below, lists light distributions according to diffractive order for a specific embodiment of a diffractive ERV lens similar to the lenses described in Table 4, i.e. having the same peripheral and different peripheral central zones, where the central diffractive zones operates predominantly in a higher order than the remaining echelettes. As shown for central 1, a majority of light that passes through any of the central diffractive zone is directed according to the second and third diffractive orders. However, for central 3, a majority of light that passes through any of the central diffractive zone is directed according to the third and fourth diffractive orders. For the peripheral diffractive profile, the majority of light is directed according to the first and second diffractive orders. Total light distributions for the combined lens profiles are also shown. For the combination with central 1, there is a non-negligible amount of light directed to the first, second and third diffractive orders. For the combination with central 3, there is a non-negligible amount of light directed to the first, second, third and fourth diffractive orders. That results in longer depth of focus for this combination, as shown in FIG. 5. In both cases, the combined diffractive profile directs at least 89% of light toward the extended range of vision. Therefore, it is more efficient than traditional bifocal diffractive lenses that loss approximately 18% of the light.

TABLE 10
Light Distribution by Diffractive Order across Central and Peripheral
Diffractive Zones for profile described in Table 4
		1	2	3	4
order	0	distance	EDF	EDF	EDF	Visual Range
Central 1	0.01	0.03	0.43	0.43	0.03	0.89
Central 3	0.00	0.01	0.03	0.76	0.15	0.95
Peripheral	0.04	0.62	0.23	0.03	0.01	0.89
Central1 +	0.03	0.44	0.29	0.16	0.02	0.89
Peripheral
Central3 +	0.03	0.43	0.17	0.26	0.06	0.91
Peripheral

Table 11, below, lists light distributions according to diffractive order for a specific embodiment of a diffractive ERV lens similar to the lens of FIG. 7 and Table 6, i.e. having central, intermediate, and peripheral diffractive zones, where the central diffractive zone operates predominantly in a higher order than the remaining zones. As shown, a majority of light that passes through the central diffractive zone is directed according to the second and third diffractive orders, whereas a majority of light that passes through the intermediate and peripheral zones is directed according to the first and second diffractive orders. Total light distribution for the combined lens profile is also shown, with approximately 58% of light directed to the first diffractive order, which provides the distance visual range, and 19% and 15% are directed to the second and third diffractive orders, which create the extended depth of focus. All, first, second and third diffractive orders have a non-negligible light distribution (i.e. greater than 10%) and create an extended range of vision that covers distance, intermediate and near as shown in FIG. 7. The combined diffractive profile directs 92% of light toward the extended range of vision. Therefore, it is more efficient than traditional bifocal diffractive lenses that loss approximately 18% of the light.

TABLE 11
Light Distribution by Diffractive Order across Central, Intermediate,
and Peripheral Diffractive Zones for profile described in Table 6
		1	2	3		Visual
Order	0	distance	EDF	EDF	4	range
Central	0.01	0.03	0.43	0.43	0.03	0.89
Intermediate	0.02	0.85	0.07	0.01	0.00	0.94
Peripheral	0.04	0.62	0.23	0.03	0.01	0.89
Combined	0.02	0.58	0.19	0.15	0.01	0.92

According to various embodiments, between 43% and 68% of light may be directed to the 1^st diffractive order, which provides the distance visual range, between 14% and 29%, may be directed to the second diffractive order and between 14% and 26% may be directed to the third diffractive order, which creates the extended depth of focus. It is further envisioned that for creating useful vision in the intermediate and/or near distances, a non-negligible amount of light of at least 10% should be directed to the second and third diffractive order. Considering the total light loss being at least 4%, the maximum amount of light in the 1st order in this case would be 75%. In order to create maximum visual quality in the intermediate and/or near range without detrimental effect on distance vision, a maximum amount of light of 30% may be directed to the second and/or third diffractive order. As a result, the minimum amount for the first diffractive order would be 40%. Thus, the range for the first diffractive order may be between 40% and 75%, and the ranges for the second and third diffractive orders may be between 10% and 30%.

Systems and Methods for Determining the Diffractive Power Profile:

FIG. 8 is a simplified block diagram illustrating a system 800 for generating a diffractive profile having at least a central higher order echelette and a peripheral zone, in accordance with embodiments. The system 800 may, in some cases, be used to include an intermediate zone. The system 800 may also be used to produce IOLs conforming to the embodiments.

The system 800 includes a user input module 802 configured to receive user input defining aspects of an intraocular lens. Inputs to design an intraocular lens may include a patient's visual needs, corneal aberrations (or corneal topography, from which corneal aberrations can be retrieved), a pupil size performance, and lens dimensions, among other attributes. A simulated optical or visual performance can be calculated from patient's visual needs that represent the desired visual performance of the patient after the surgery. In some cases, a desired optical performance may relate to a patient's lifestyle, e.g., whether the patient prefers to participate in activities requiring predominantly distance vision, intermediate vision, or near vision without additional visual correction. The power profile prescription can be calculated from the simulated performance including, for example, a preferred optical power or optical power profile for correcting far vision and expected depth of focus. The corneal aberrations (or corneal wave front aberrations) can include the higher order rotationally symmetrical aberrations of the cornea as a function of the pupil size. A pupil size performance can include a pupil diameter of a patient under different lighting conditions. These parameters can also be related to patient's life style or profession, so that the design incorporates patient's visual needs as a function of the pupil size. In some cases, parameters such as lens asphericity can be determined based on a function of the wave front aberrations and visual needs of the patient. Lens dimensions can include a preferred radius of the total lens, and may further include preferred thickness, or a preferred curvature of one or the other of the anterior surface and posterior surface of the lens, as well as the optional incorporation of toricity in any of the IOL surfaces.

A diffractive profile modeling module 804 can receive information about the desired lens from the user input module 802, and can determine aspects of the diffractive profile. For example, the diffractive profile modeling module 804 can determine the position and heights of the echelette of the central zone. It can also determine the position, number and height of the echelettes in peripheral zones required to fulfill the performance determined from patient's visual needs. The module can determine the need of including an intermediate zone, as well as the structural characteristics of the zone (number and heights of the echelettes). The base curvature of the profile can be related to the biometry of the patient. The asphericity can also be related to that of the patient's cornea, so that it either compensates patient's corneal spherical aberration or induces a certain amount of spherical aberration to help improving intermediate and near performance in mesopic conditions.

The diffractive profile modeling module 804 can be configured to generate performance criteria 812, e.g. via modeling optical properties in a virtual environment. Performance criteria can include the match of the expected performance derived from patient's visual needs to that of the actual diffractive profile that results from 804. In some cases, the diffractive profile modeling module 804 can provide an intraocular lens surface to an intraocular lens fabrication module 808 for facilitating the production of a physical lens, which can be tested via an intraocular lens testing module 810 for empirically determining the performance criteria 812, so as to identify optical aberrations and imperfections not readily discerned via virtual modeling, and to permit iteration.

FIG. 9 is an example process 900 for generating a refractive ERV lens surface, in accordance with embodiments. The process 900 may be implemented in conjunction with, for example, the system 800 shown in FIG. 8. Some or all of the process 900 (or any other processes described herein, or variations, and/or combinations thereof) may be performed under the control of one or more computer systems configured with executable instructions and may be implemented as code (e.g., executable instructions, one or more computer programs, or one or more applications) executing collectively on one or more processors, by hardware or combinations thereof. The code may be stored on a computer-readable storage medium, for example, in the form of a computer program comprising a plurality of instructions executable by one or more processors. The computer-readable storage medium may be non-transitory.

The process 900 includes receiving an input indicative of a patient's visual needs (act 902). The input can include, e.g., a desired optical power profile for correcting impaired distance vision, a desired optical power profile for correcting impaired intermediate vision, a desired optical power profile for accommodating near vision, and any suitable combination of the above. Next, a diffractive ERV lens profile can be defined according to the visual needs determined above (act 904). In some cases, the diffractive profile may be defined for providing an extended depth of focus by, e.g., defining a central diffractive zone including one more echelettes configured to operate primarily in the second and/or third and/or fourth diffractive orders, where the central diffractive zone is operable to direct incident light to a range of distances to further enlarge the depth of focus of the diffractive profile. The diffractive profile may be further defined to include a peripheral diffractive zone configured to operate primarily in a first and/or second diffractive order, or a lower diffractive order than the central diffractive zone, that is operable to direct light to a range of distances corresponding to the intermediate and/or far visual range. A diffractive lens surface can then be generated based on the diffractive profile (act 906). The system can then generate instructions to fabricate an intraocular lens based on the generated diffractive lens surface (act 908).

FIG. 10 is a simplified block diagram of an exemplary computing environment 1000 that may be used by systems for generating the continuous progressive lens surfaces of the present disclosure. Computer system 1000 typically includes at least one processor 1052 which may communicate with a number of peripheral devices via a bus subsystem 1054. These peripheral devices may include a storage subsystem 1056 comprising a memory subsystem 1058 and a file storage subsystem 1060, user interface input devices 1062, user interface output devices 1064, and a network interface subsystem 1066. Network interface subsystem 1066 provides an interface to outside networks 1068 and/or other devices, such as the lens fabrication module 808 or lens testing module 810 of FIG. 8. In some cases, some portion of the above-referenced subsystems may be available in a diagnostics device capable of measuring the biometric inputs required for calculating attributes such as base power.

User interface input devices 1062 may include a keyboard, pointing devices such as a mouse, trackball, touch pad, or graphics tablet, a scanner, foot pedals, a joystick, a touchscreen incorporated into the display, audio input devices such as voice recognition systems, microphones, and other types of input devices. The input devices 1062 may also include one or more biometric input devices capable of measuring a patient's biometric inputs required to generate the diffractive lens surface. For example, input devices 1062 can include a biometer capable of measuring axial length, corneal power, corneal aberrations, preoperative anterior chamber depth, lens thickness, and/or pupil size for a patient under different lighting conditions. These variables are nonlimiting and are mentioned herein by way of example. User input devices 1062 will often be used to download a computer executable code from a tangible storage media embodying any of the methods of the present invention. In general, use of the term “input device” is intended to include a variety of conventional and proprietary devices and ways to input information into computer system 1022.

User interface output devices 1064 may include a display subsystem, a printer, a fax machine, or non-visual displays such as audio output devices. The display subsystem may be a cathode ray tube (CRT), a flat-panel device such as a liquid crystal display (LCD), a projection device, or the like. The display subsystem may also provide a non-visual display such as via audio output devices. In general, use of the term “output device” is intended to include a variety of conventional and proprietary devices and ways to output information from computer system 1022 to a user.

Storage subsystem 1056 can store the basic programming and data constructs that provide the functionality of the various embodiments of the present invention. For example, a database and modules implementing the functionality of the methods of the present invention, as described herein, may be stored in storage subsystem 1056. These software modules are generally executed by processor 1052. In a distributed environment, the software modules may be stored on a plurality of computer systems and executed by processors of the plurality of computer systems. Storage subsystem 1056 typically comprises memory subsystem 1058 and file storage subsystem 1060. Memory subsystem 1058 typically includes a number of memories including a main random access memory (RAM) 1070 for storage of instructions and data during program execution.

Various computational methods discussed above, e.g. with respect to generating a diffractive lens surface, may be performed in conjunction with or using a computer or other processor having hardware, software, and/or firmware. The various method steps may be performed by modules, and the modules may comprise any of a wide variety of digital and/or analog data processing hardware and/or software arranged to perform the method steps described herein. The modules optionally comprising data processing hardware adapted to perform one or more of these steps by having appropriate machine programming code associated therewith, the modules for two or more steps (or portions of two or more steps) being integrated into a single processor board or separated into different processor boards in any of a wide variety of integrated and/or distributed processing architectures. These methods and systems will often employ a tangible media embodying machine-readable code with instructions for performing the method steps described above. Suitable tangible media may comprise a memory (including a volatile memory and/or a non-volatile memory), a storage media (such as a magnetic recording on a floppy disk, a hard disk, a tape, or the like; on an optical memory such as a CD, a CD-R/W, a CD-ROM, a DVD, or the like; or any other digital or analog storage media), or the like.

The particulars shown herein are by way of example and for purposes of illustrative discussion of the preferred embodiments of the present invention only and are presented in the cause of providing what is believed to be the most useful and readily understood description of the principles and conceptual aspects of various embodiments of the invention. In this regard, no attempt is made to show structural details of the invention in more detail than is necessary for the fundamental understanding of the invention, the description taken with the drawings and/or examples making apparent to those skilled in the art how the several forms of the invention may be embodied in practice.

The following definitions and explanations are meant and intended to be controlling in any future construction unless clearly and unambiguously modified in the following examples or when application of the meaning renders any construction meaningless or essentially meaningless. In cases where the construction of the term would render it meaningless or essentially meaningless, the definition should be taken from Webster's Dictionary, 3rd Edition or a dictionary known to those of skill in the art, such as the Oxford Dictionary of Biochemistry and Molecular Biology (Ed. Anthony Smith, Oxford University Press, Oxford, 2004).

As used herein and unless otherwise indicated, the terms “a” and “an” are taken to mean “one”, “at least one” or “one or more”. Unless otherwise required by context, singular terms used herein shall include pluralities and plural terms shall include the singular.

Unless the context clearly requires otherwise, throughout the description and the claims, the words ‘comprise’, ‘comprising’, and the like are to be construed in an inclusive sense as opposed to an exclusive or exhaustive sense, that is to say, in the sense of “including, but not limited to”. Words using the singular or plural number also include the plural and singular number, respectively. Additionally, the words “herein,” “above,” and “below” and words of similar import, when used in this application, shall refer to this application as a whole and not to any particular portions of the application.

The description of embodiments of the disclosure is not intended to be exhaustive or to limit the disclosure to the precise form disclosed. While the specific embodiments of, and examples for, the disclosure are described herein for illustrative purposes, various equivalent modifications are possible within the scope of the disclosure, as those skilled in the relevant art will recognize.

All references, including patent filings (including patents, patent applications, and patent publications), scientific journals, books, treatises, technical references, and other publications and materials discussed in this application, are incorporated herein by reference in their entirety for all purposes.

Aspects of the disclosure can be modified, if necessary, to employ the systems, functions, and concepts of the above references and application to provide yet further embodiments of the disclosure. These and other changes can be made to the disclosure in light of the detailed description.

Specific elements of any foregoing embodiments can be combined or substituted for elements in other embodiments. Furthermore, while advantages associated with certain embodiments of the disclosure have been described in the context of these embodiments, other embodiments may also exhibit such advantages, and not all embodiments need necessarily exhibit such advantages to fall within the scope of the disclosure.

While the above provides a full and complete disclosure of exemplary embodiments of the present invention, various modifications, alternate constructions and equivalents may be employed as desired. Consequently, although the embodiments have been described in some detail, by way of example and for clarity of understanding, a variety of modifications, changes, and adaptations will be obvious to those of skill in the art. Accordingly, the above description and illustrations should not be construed as limiting the invention, which can be defined by the appended claims.

Claims

1. An ophthalmic lens, comprising: a first surface and a second surface disposed about an optical axis, the lens being characterized by an extended depth of focus across a range of optical powers; anda diffractive profile imposed on one of the first and second surfaces and configured to cause a distribution of non-negligible amounts of light to the extended depth of focus, the diffractive profile comprising:a central zone comprising at least one central diffractive echelette having a first phase delay;an intermediate zone comprising at least one intermediate echelette having a second phase delay; anda peripheral zone comprising one or more peripheral diffractive echelettes having a third phase delay;wherein the central zone is configured to operate in a higher diffractive order than the peripheral zone;wherein the first, second and third phase delay are different and the third phase delay is less than the first phase delay; andwherein the combination of the central, intermediate and peripheral zones provides a longer depth of focus than a diffractive profile defined just by the peripheral zone, andwherein a step height of a central diffractive echelette of the at least one central diffractive echelette adjacent to the intermediate zone is larger than a step height of an intermediate echelette of the at least one intermediate echelette adjacent to the central zone.

2. The ophthalmic lens of claim 1, wherein the peripheral zone is configured to operate in a first diffractive order by directing light toward a far focal length for distance vision.

3. The ophthalmic lens of claim 1, wherein the peripheral zone is configured to operate in a first diffractive order and a second diffractive order by directing light toward a far focal length for distance vision and to an intermediate focal length for intermediate vision.

4. The ophthalmic lens of claim 1, wherein the central zone is configured to operate in a second diffractive order and a third diffractive order by directing light toward an intermediate focal length for intermediate vision and to a short focal length for near vision.

5. The ophthalmic lens of claim 4, wherein at least the second and third diffractive orders create an extended range of vision.

6. The ophthalmic lens of claim 1, wherein the peripheral zone directs light toward a far focal length.

7. The lens of claim 1, wherein the at least one central diffractive echelette in the central zone has a phase delay of more than 2.0λ, and wherein the one or more peripheral diffractive echelettes have a phase delay of less than 2.0λ.

8. The lens of claim 1, wherein a total number of echelettes defining the central, intermediate and peripheral optical zones is from 8 to 32 echelettes.

9. The lens of claim 1, wherein the central optical zone has a phase shift from 2λ to 4λ and wherein the peripheral optical zone has a phase shift from 1λ to 2λ.

10. The lens of claim 1, wherein the central optical zone comprises 1 to 2 central echelettes, and wherein the peripheral optical zone comprises 5 to 7 peripheral echelettes.

11. The ophthalmic lens of claim 1, wherein the intermediate zone is configured to operate in a first diffractive order by directing light toward a far focal length for distance vision.

12. The ophthalmic lens of claim 1, wherein the phase delay of the at least one echelette in the intermediate zone is smaller than that of the one or more peripheral diffractive echelettes by 0.05λ, up to 0.5λ.

13. The ophthalmic lens of claim 1, wherein there is a non-negligible light distribution in a first diffractive order, a second diffractive order and a third diffractive order of the diffractive profile, wherein the first diffractive order directs light toward a far focal length for distance vision, the second diffractive order directs light toward an intermediate focal length for intermediate vision, and the third diffractive order directs light to a short focal length for near vision.

14. The lens of claim 1, wherein the lens is an intraocular implant.

15. The lens of claim 1, further comprising two principal meridians with different base powers.

16. The lens of claim 1, wherein the central zone comprises 1 echelette.

17. An ophthalmic lens, comprising: a first surface and a second surface disposed about an optical axis, the lens being characterized by an extended depth of focus across a range of optical powers; anda diffractive profile imposed on one of the first and second surfaces and configured to cause a distribution of non-negligible amounts of light to the extended depth of focus, the diffractive profile comprising:a central zone comprising at least one central diffractive echelette having a first phase delay;an intermediate zone comprising at least one intermediate echelette having a second phase delay; anda peripheral zone comprising one or more peripheral diffractive echelettes having a third phase delay;wherein the central zone is configured to operate in a higher diffractive order than the peripheral zone;wherein the first, second and third phase delay are different and the third phase delay is less than the first phase delay;wherein the combination of the central, intermediate and peripheral zones provides a longer depth of focus than a diffractive profile defined just by the peripheral zone; andwherein a light distribution for a distance focus ranges between 75% and 40% of light incident on the lens.

18. The ophthalmic lens of claim 17, wherein a light directed to a distance focus of the extended depth of focus ranges from between 58% and 61% of incident light on the diffractive profile.

19. The ophthalmic lens of claim 17, wherein light directed to a full range of vision provided by the lens ranges from 90% to 92% of light incident on the lens.

20. The ophthalmic lens of claim 17, wherein at least 90% of incident light on the lens is directed to a full range of vision provided by diffractive profile.

21. An ophthalmic lens, comprising: a first surface and a second surface disposed about an optical axis, the lens being characterized by an extended depth of focus across a range of optical powers; anda diffractive profile imposed on one of the first and second surfaces and configured to cause a distribution of non-negligible amounts of light to the extended depth of focus provided by the lens wherein the diffractive profile comprises a central diffractive zone that works in a higher diffractive order than a remainder of the diffractive profile, wherein the central diffractive zone has a phase delay from 2.3λ to 3.5λ.

22. The lens of claim 21, wherein the central diffractive zone has a phase delay from 2.45λ to 3.2λ.

23. The lens of claim 21, wherein the central diffractive zone has a phase delay from 2.5λ to 2.95λ.

24. The lens of claim 21, wherein the remainder of the diffractive profile has a phase delay of between 1λ and 1.5λ.

25. The lens of claim 21, wherein the remainder of the diffractive profile has a phase delay of between 1.2λ and 1.5λ.

26. The lens of claim 21, wherein the remainder of the diffractive profile has a phase delay of between 1.2 and 1.336λ.

27. The lens of claim 21, wherein the diffractive profile is operable to mitigate ocular chromatic aberration imparted by the lens.

28. The lens of claim 21, wherein: the first surface is a posterior surface of the lens and the second surface is an anterior surface of the lens; and the diffractive profile is disposed on the first surface.

29. The lens of claim 21, further comprising a refractive profile disposed on one of the first surface and the second surface, the refractive profile being configured to correct for corneal spherical aberration.

30. The lens of claim 21, further comprising a refractive profile disposed on one of the first surface and the second surface, the refractive profile being configured to correct for corneal astigmatism.

31. The lens of claim 21, wherein the lens is an intraocular implant.

32. The lens of claim 21, wherein the remainder of the diffractive profile comprises echelettes configured to operate in a first diffractive order by directing light toward a far focal length for distance vision and that have phase delays less than 2λ.

33. The lens of claim 21, wherein the central zone comprises 1 echelette.