Patent ID: 12259596

It will be understood by those skilled in the art that the following accompanying drawings are for illustrative purposes only. These accompanying drawings are not intended to limit the scope of the present disclosure in any way.

DETAILED DESCRIPTION

It shall be understood that the present disclosure simplifies the accompanying drawings and description to illustrate the components of the present disclosure in a manner that is helpful for a clear understanding, and other components visible in a typical ophthalmic lens are not shown for the sake of clarity and brevity. Accordingly, one of ordinary skill in the art shall understand that there exist certain other components desirable and/or needed in implementing the present disclosure. Because such components are well known in the art and may not be conducive to a better understanding of the present disclosure, no description of such components is provided in the present disclosure. The present disclosure is intended to cover all changes and modifications based on components known to those skilled in the art.

An existing extended depth of field technology (such as the aforementioned EDOF IOLs) creates a single-elongated focal point corresponding to the range of vision covering both far and intermediate vision without a significant discretion of foci as in multifocal IOLs, and thereby can provide the patients with a continuous range of vision correction from far to intermediate distances. The known EDOF technology can be classified into two types. One type is to adopt diffraction technology as in multifocal technology, the principles and shortcomings of which are thus similar to those of multifocal correction technology. The other is to use phase shift technology and also have following two shortcomings. 1) Although this technology adopts the phase shift technology, there are at least two partitions with two completely different base profiles (e.g., sag (i.e., sagittal height) profiles). In addition, the energy distribution, although continuous, still needs to be optimized, and the corrected vision of the patient is still unsatisfactory when looking into the distance via a small aperture, thus there is still a certain gap compared with the effect of monofocal IOL far vision correction. 2) Since the phase shift zone is close to the optical center, the IOL based on this technology is more like a monofocal IOL in the case of a large aperture, which cause the reduced ability to correct intermediate vision and thereby fail to achieve the effect of extending the depth of field.

Compared to existing EDOF designs (e.g., EDOF IOL), the improved ophthalmic lens with an extended depth of field according to the present disclosure creates a single-elongated focal point corresponding to the range of vision covering both far and intermediate vision by a unique freeform surface combined with a phase transition technology. Specifically, parameters of the freeform surface are reasonably configured to overcome the problem in the prior art that two partitions have different base profiles, and relative positions and amplitudes for the phase transition with a higher degree of freedom compared with the existing phase shift technology are configured to not only ensure the correction of the far and intermediate vision of the patient under different apertures while optimizing the light energy distribution for the far vision of the patient. Thus, the ophthalmic lens according to the present disclosure enables patients to acquire correction over a continuous range of vision from intermediate to far distances and also optimizes their far vision without visual disturbances, such that the resulting far vision correction is equivalent to that of existing monofocal ophthalmic lenses (such as, IOL). According to embodiments of the present disclosure, the light energy is more effectively distributed for the range of vision from intermediate to far distances under different optical apertures, whereby the energy distribution for key frequency bands corresponding to far distances is optimized and enhanced under a premise of maintaining the continuity of energy distribution.

Embodiments of the present disclosure may advantageously provide an ophthalmic lens for vision correction (including, but not limited to, myopia, hyperopia, astigmatism, cataracts, and/or presbyopia) with an extended depth of field and enhanced vision. In some embodiments, the ophthalmic lens may include contact lenses, corneal inlays or covers, or artificial lenses (IOLs), which may for example include phakic IOLs and piggyback IOLs (i.e., IOLs implanted in eyes with existing IOLs). The ophthalmic lens according to the present disclosure is particularly useful for the treatment of presbyopia and cataracts in the middle-aged population.

FIG.1Aschematically shows a cross-sectional view of an ophthalmic lens100according to some embodiments of the present disclosure; andFIG.1Bschematically shows a plan view of an ophthalmic lens100according to some embodiments of the present disclosure. The ophthalmic lens100may include an optical unit102. The optical unit102transmits (e.g., refracts) and focuses light received by the ophthalmic lens100. As will be described in more detail below, the optical unit102may include a surface profile of one or more surfaces designed to refract and focus incident light to increase the depth of field and improve the visual acuity. For example, in some embodiments, the surface profile of the optical unit102may be designed such that the optical unit102can continuously focus incident light to increase the depth of field, thereby achieving a higher visual acuity (e.g., 20/25 vision) for the object vergence within a wide object distance range (e.g., the vergence within a range of at least about 0 to about 1.35 Diopters). In addition, in some embodiments, the surface profile of the optical unit102may be designed such that the images are substantially coaxial and have a substantially similar magnitude to reduce the presence of ghost images.

As shown inFIG.1AandFIG.1B, the exemplary ophthalmic lens100may further include a haptic component110. In some embodiments, one or more haptic components110may be included to stabilize the ophthalmic lens100in and attach the ophthalmic lens100to the eye. For example, a plurality of haptic components110are provided to surround the optical unit102to affix the optical unit102in place when implanted in the eye. In some embodiments, the haptic component110is provided to stabilize the optical unit102in the eye, such that an optical axis of the optical unit102is disposed along a central optical axis of the eye. In such embodiments, the stability of the wavefront of the optical unit102in the eye may be provided by the haptic component110. In some embodiments, the ophthalmic lens100and, in particular, the haptic member110are provided to be implanted outside a capsular bag, and may, for example, be designed to be implanted in front of a natural lens for a phakic IOL. For example, the phakic IOL may be provided to be implanted between the iris and the natural lens. Although two haptic components110as shown are in a form of wings, there is no particular limitation on the shape, size, and number of the haptic components110. In some embodiments, the ophthalmic lens is provided for implantation into the capsular bag after removing the natural lens. Such an ophthalmic lens may have a haptic components110which is in a shape, size, and/or number suitable for providing secure placement and orientation within the capsular bag after implantation.

As shown inFIG.1B, the optical unit102includes a first surface106and a second surface108that are opposite to each other. For example, the first surface106and the second surface108are both centered by the optical axis104, and one of the first surface106and the second surface108is an anterior surface, with the other being a posterior surface.

In some embodiments, the first surface106includes: a first zone112extending from the optical axis104to the first radial boundary; a second zone114extending from the first radial boundary to the second radial boundary; and a third zone116extending from the second radial boundary to a circumference of the optical unit102. The first zone112is designed as a freeform surface zone, the second zone114is designed as a phase transition zone, and the third zone116is designed as a peripheral optical zone. The surface profile of the first surface106is defined by the superposition of the base sag profile and the feature sag profile. For example, the base sag profile may be spherical or aspheric.

Although the first zone112, the second zone114, and the third zone116described above are illustrated and described as being disposed on the first surface106of the optical unit102, the present disclosure contemplates that the first zone112, the second zone114, and the third zone116may additionally or alternatively be disposed on a second surface108of the optical unit102, such that a similar light wave phase modulation effect is produced. In addition, the optical unit102determines a reference focal length of the ophthalmic lens, which typically needs to correspond to the patient's distance vision correction. However, the additional focal length of the ophthalmic lens may be defined relative to the reference focal length depending on the situation, e.g., depending on the dominant and non-dominant eyes to thereby improve the overall vision of both eyes.

As a particular embodiment, the surface profile of the first surface106may be described as a following equation (1):
Z(r)=Zbase(r)+Zfeature(r)  (1)

where Z(r) represents a sag profile of the first surface106, Zbase(r) represents the base sag profile, Zfeature(r) represents the feature sag profile, and r represents a radial distance from the optical axis104.

Zbase(r) and Zfeature(r) may be described as following equations (2) and (3), respectively:

Zbase(r)=cr21+1-(1+k)⁢c2⁢r2+a4⁢r4+a6⁢r6(2)Zfeature(r)={Z1⁢1⁢2⁢(r),0<r≤r⁢112Z1⁢1⁢4⁢(r),r⁢1⁢12<r≤r⁢114Z1⁢1⁢6⁢(r),r⁢114<r≤ro⁢z(3)

where c represents a base curvature of the first surface106; k represents a conic constant; a4and a6represent a fourth order coefficient and a sixth order coefficient, respectively; Z112(r), Z114(r) and Z116(r) represent the feature sag profiles corresponding to the first zone112, the second zone114and the third zone116, respectively; and r112, r114and rozrepresent radial distances from the optical axis104to the first radial boundary, the second radial boundary, and the circumference of the optical unit102, respectively.

Although the equation (2) describes the base sag profile of the aspheric surface in general, the equation (2) may be configured to describe the spherical surface by choosing k, a4and a6to be all zero.

In some embodiments, the first zone112as a freeform surface zone may include an inner region120, a middle region122, and an outer region124along a radial direction away from the optical axis104. In the feature sag profile of the first zone112(i.e., without the contribution of the base sag profile), the sag of the inner region120is constant, sag of the middle region122increases as per a power series along a radial direction away from the inner region120, and the sag of the outer region124increases linearly.

As a particular embodiment, Z112(r) corresponding to the feature sag profile of the first zone112may be a continuous curve and may be expressed as the following equation (4a):

Z112(r)={0,0<r≤r120k122⁢_⁢4⁢r4+k122⁢_⁢3⁢r3+k122⁢_⁢2⁢r2+k122⁢_⁢1⁢r1+k122⁢_⁢0,r120<r≤r122k124⁢_⁢1⁢r1+k124⁢_⁢0,r122<r≤r⁢112(4⁢a)

where r120and r122represent radial distances from the optical axis104to outer peripheral boundaries of the inner region120and the middle region122, respectively; k122_4, k122_3, k122_2, k122_1, and k122_0represent polynomial coefficients of the feature sag profile corresponding to the middle region122; and k124_1and k124_0represent linear coefficients of the feature sag profile corresponding to the outer region124, with the k122_0and k124_0enabling the function continuity of Z112(r).

FIG.2shows a graph of a feature sag profile of a first zone112in an optical unit of an ophthalmic lens according to some embodiments of the present disclosure. The horizontal axis represents a radial distance from the optical axis104, and the vertical axis represents a feature sag at the radial distance (i.e., without the contribution of the base sag profile).

Preferably, the radial distance r120(e.g., a boundary radius) of the peripheral boundary of the inner region120from the optical axis104is in a range of 0.15 mm to 0.35 mm. Preferably, the power increase in the feature sag of the middle region122produces an optical power greater than 0 D (Diopter) and less than 1 D, and the radial distance r122of the peripheral boundary of the middle region122from the optical axis104is in the range of 0.85 mm to 1.15 mm. Preferably, the linear increase in the feature sag of the outer region124produces an optical power greater than −0.5 D and less than +0.5 D, and the radial distance r112of the outer peripheral boundary of the outer region124from the optical axis104is in the range of 1.2 mm to 1.5 mm.

As an alternative or optional embodiment, the feature sag profile of the first zone112is not configured by partition (e.g., inner, middle, and outer regions as described above), but is defined by polynomial fitting as a whole or in the form of a spline curve by fixing key nodes, provided that the aforesaid features are substantially satisfied.

As a particular embodiment, Z112(r) corresponding to the feature sag profile of the first zone112may be overall expressed as the following equation (4b):
Z112(r)=Σn=0Nk112_nrn, 0<r≤r112(4b)

where k112_nrepresents a polynomial coefficient of the feature sag profile defining the first zone112, and N represents a polynomial coefficient required to achieve the feature sag profile of the first zone112.

In some embodiments, the second zone114as a phase transition zone may include at least one stepped portion. In the feature sag profile of the second zone114(i.e., without the contribution of the base sag profile), the sag of each stepped portion increases in a radial direction away from the optical axis104.

As a particular embodiment, Z114(r) corresponding to the feature sag profile of the second zone114may be expressed as the following equation (5):

Z1⁢1⁢4-⁢i(r)=hi(r-ri)(ri+1-ri)+zi,i=1,2,3⁢…(5)

where Z114_i(r) represents a feature sag profile defining an ithstepped portion from the at least one stepped portion; hi represents a feature sag difference between an outer peripheral boundary and an inner peripheral boundary of the ithstepped portion; rirepresents a radial distance from the inner peripheral boundary of the ithstepped portion to the optical axis104; and zirepresents a feature sag of the inner peripheral boundary of the ithstepped portion. It shall be noted that riis equal to r112, and r(i+1)is equal to r114for the last stepped portion (i.e., the outermost stepped portion with the largest i). Preferably, in order to ensure continuity between the inner peripheral boundary of the first stepped portion of the second zone114(i.e., the innermost stepped portion with i being 1) and the first zone112, the feature sag z1of the inner peripheral boundary of the of the first stepped portion may be substantially the same as the feature sag of the first zone112at the first radial boundary (i.e., at a distance r112from the optical axis104).

FIG.3shows a graph of a feature sag profile of a second zone114in an optical unit of an ophthalmic lens according to some embodiments of the present disclosure. The horizontal axis represents a radial distance from the optical axis104, and the vertical axis represents a feature sag at the radial distance (i.e., without the contribution of the base sag profile).

Preferably, the number of stepped portions of the second zone114is in the range of 1 to 4. Preferably, the radial width of the stepped portion (i.e., ri+1−ri) is in the range of 0.1 mm to 0.3 mm, and the optical path difference of the step height (i.e., hi) is in the range of 0.1 wave to 0.5 wave at the designed wavelength. Preferably, the radial distance r114of the second radial boundary from the optical axis104is in the range of 1.5 mm to 2.0 mm.

In some embodiments, the feature sag profile of the third zone116, which is the peripheral optical zone, is substantially constant.

As a particular embodiment, Z116(r) corresponding to the feature sag profile of the third zone116may be expressed as the following equation (6):
Z116(r)=C, r114<r≤roz(6)

where C represents a constant.

As an example, C may be 0. As another example, in order to ensure continuity between the third zone116and the second zone114, C may be substantially the same as the feature sag of the second zone114at the second radial boundary (i.e., at a distance r114from the optical axis104).

FIG.4shows a graph of a feature sag profile of a third zone116in an optical unit of an ophthalmic lens according to some embodiments of the present disclosure. The horizontal axis represents a radial distance from the optical axis104, and the vertical axis represents a feature sag at the radial distance (i.e., without the contribution of the base sag profile).

Preferably, the radial distance rozto the peripheral boundary of the third zone116, i.e., the circumference of the optical unit102, from the optical axis104is in a range of 2.5 mm to 4.0 mm.

The improved ophthalmic lens with an extended depth of field according to the present disclosure may produce a delay in the phase distribution of light waves in space by an optical unit having at least some of the aforementioned features, such that each subwave of different phases in the light waves distributed in space generates interference, thereby achieving the effect of extending the depth of field by rational distribution of light energy for the range of vision from far to intermediate distances.

The experimental examples will be described in detail below in conjunction with specific examples of the present disclosure and comparative examples for performance comparison.

An example of an improved ophthalmic lens with an extended depth of field according to the present disclosure is designed and prepared based on the parameters illustrated in Table 1 below, where only one surface employs a superposition of the base sag profile and the feature sag profile based on the parameters in Table 1 below.

TABLE 1ParametersValuesLens material1.55refractive indexr1121.22mmr1141.90mmroz3.00mmr1200.19mmr1221.05mmk122_40.00086632mm−3k122_3−0.00369424mm−2k122_20.00492636mm−1k122_1−0.00129371k122_00.00009217mmk124_10k124_00.00094157mmr11.22mmz10.37waveh10.09waver21.505mmz20.26waveh20.23waver31.71mmz30.24waveh30.15waver41.90mmc1/15mm−1k0.21a40.0016a60.000078

FIG.5shows a schematic diagram of wavefront aberration vector diameter of an ophthalmic lens according to the aforesaid example in a pupillary plane of the eyeball.

The existing monofocal ophthalmic lens prepared as a comparative example is essentially the same as the ophthalmic lens according to the aforesaid example, except for that a corresponding surface employs only the same base sag profile (that is, parameters, such as the lens material refractive index, roz, c, k, a4, a6, etc., are the same) as in the example without the feature sag profile.

In order to confirm the performance improvement of the ophthalmic lens with an extended depth of field according to the example of the present disclosure over the existing monofocal ophthalmic lens taken as a comparative example, modulation transfer function (MTF) are obtained for different object vergences to acquire images, the results of which are shown inFIG.6AandFIG.6B.

The horizontal axis ofFIG.6Arepresents the object vergence in Diopter, which is an inverse of the object distance. For example, 0 Diopter corresponds to an object distance at infinity, 1 Diopter corresponds to an object distance of 1 meter, and 1.5 Diopter corresponds to an object distance of approximately 0.67 meters. The vertical axis ofFIG.6Aindicates the MTF value measured for the corresponding object vergence, and the higher the value, the higher the imaging quality. As seen inFIG.6A, for a given MTF threshold, a depth of field of up to 1.35 D is acquired with the ophthalmic lens according to the example of the present disclosure, whereas the existing ophthalmic lens of the comparative example merely acquires a depth of field of only about 0.85 D. Thus, the depth of field of the ophthalmic lens according to the example of the present disclosure is increased by about 58% compared to the existing ophthalmic lens of the comparative example.FIG.6Bemploys a letter E (opening leftward) with a size corresponding to 20/32 (−0.6) in the vision table. As seen inFIG.6B, in the images acquired with the ophthalmic lens according to the example of the present disclosure, the opening direction of the letter E can be distinguished and identified even at an object vergence of 1.35 D. In the images acquired with the existing ophthalmic lens of the comparative example, the opening direction of the letter E cannot be distinguished and identified at an object vergence of 0.75 D or more. Thus, compared with the ophthalmic lens of the comparative example, the ophthalmic lens according to the example of the present disclosure not only can significantly extend the depth of field of the patient, but also has no significant difference in the imaging quality, especially clarity and contrast, when looking into the distance (e.g., 0 D).

The terms “approximately” and “substantially” herein denote an amount that is equal to or close to the stated amount (e.g., an amount that still performs the desired function or achieves the desired result). For example, unless otherwise stated, the terms “about” and “substantially” may refer to the amount within (e.g., above or below) 10%, within (e.g., above or below) 5%, within (e.g., above or below) 1%, within (e.g., above or below) 0.1%, or within (e.g., above or below) 0.01% of the stated amount.

Various embodiments of the present disclosure have been described herein. Although the present disclosure has been described with reference to specific embodiments, this specification is only intended to illustrate rather than limit the present disclosure. Those of ordinary skill in the art may envisage various modifications and applications without departing from the basic concept and scope of the present disclosure.