Ophthalmic lens capable of expanding depth of field and manufacturing method

Abstract

The invention discloses an extended depth of field ophthalmic lens and a method of manufacture, the ophthalmic lens comprising a lens body comprising at least at least one optical surface, the optical power distribution of the at least one optical surface satisfying the following formula: where, is a power profile as a function of lateral coordinates, where, is a power profile as a function of lateral coordinates, and where, is a power profile as a function of lateral coordinates, a power profile as a function of lateral coordinates. On an XY-plane perpendicular to the optical axis Z of the lens; each function is a peak function with a maximum value in the center; all the coefficients are coefficients of the nth item with a peak function; all the functions are S-shaped functions with transition at a certain distance from the center; all the coefficients are coefficients of the mth item of the S-type function; wherein the sum, the sum and the sum form a series of continuous focuses by designing optical power distribution combined by a peak function and / or an S-type function and redistributing light rays, and the effect of extending the depth of field can be achieved.

Description

Technical Field

[0001] This invention relates to the technical field of ophthalmic lenses, specifically to an ophthalmic lens that extends depth of field and its manufacturing method. Background Technology

[0002] Monofocal ophthalmic lenses primarily address distance vision issues, while multifocal designs offer intermediate and near vision capabilities. However, multifocal designs present two challenges: firstly, they may generate unwanted glare; and secondly, patients typically require a period of adjustment to their use.

[0003] Extended Depth of Field (EDOF) ophthalmic lenses are designed to provide superior distance vision while improving intermediate-range visual acuity. This improved intermediate-range vision benefits patients in daily activities, often reducing reliance on corrective glasses for many tasks. A key advantage of EDOF designs is that they offer a beneficial trade-off for patients, providing enhanced functionality for everyday activities while maintaining safety comparable to monofocal products. These designs are designed to facilitate patient adaptation and achieve better visual results with minimal risk of adverse glare effects.

[0004] However, existing extended depth-of-field ophthalmic lenses are difficult to design precisely for optical power distribution, and cannot provide customized solutions for different patient needs and ocular anatomy. Summary of the Invention

[0005] The present invention aims to at least solve one of the technical problems existing in the prior art. To this end, the present invention provides an extended depth-of-field ophthalmic lens and a manufacturing method thereof, solving the problem that existing extended depth-of-field ophthalmic lenses are difficult to precisely design for optical power distribution.

[0006] According to a first aspect of an embodiment of the present invention, an ophthalmic lens for extending depth of field includes: A lens body comprising at least one optical surface, the at least one optical surface comprising an extended depth-of-field profile for providing additional refractive power contribution, the extended depth-of-field profile corresponding to an optical power distribution satisfying the following formula: (1) in, It is a power profile that functions as a horizontal coordinate. On an XY-plane perpendicular to the optical axis Z of the lens; They are all in the center Peak function with maximum value ; They all come with The coefficient of the nth term of the peak function; Functions are all located away from a certain distance from the center S-shaped function with transition at the point ; They are all sigma functions The coefficient of the m-th term; in, and , and , .

[0007] An ophthalmic lens for extending depth of field according to an embodiment of the present invention has at least the following beneficial effects: This invention designs at least one optical surface of a lens to have an optical power profile that satisfies a specific formula, which is a combination of a peak function and / or a sigmoid function. This redistributes the light passing through the optical surface to form a continuous series of focal points, thereby achieving an extended depth of field effect and effectively improving intermediate visual acuity. It provides a highly versatile and customizable optical power profile design framework. By linearly combining smooth peak functions and / or sigmoid functions, almost any desired, continuously varying power distribution can be constructed. This provides an optimized basis for optimizing depth of field extension, controlling aberrations, managing light energy distribution, and robustness to eccentricity / tilt.

[0008] According to some embodiments of the present invention, at least one of the optical surfaces and / or at least one other optical surface includes a base refractive profile, which is an optical base surface having a base curvature, and the base refractive profile is used to provide base refractive power.

[0009] According to some embodiments of the present invention, the coefficient , At least one of them is positive.

[0010] According to some embodiments of the present invention, the coefficient , All are positive values.

[0011] According to some embodiments of the present invention, the center , At least one of them is non-zero.

[0012] According to some embodiments of the present invention, each function , Around their respective centers , Rotationally symmetric.

[0013] According to some embodiments of the present invention, the sum of the terms M+N of the optical power distribution formula for the extended depth-of-field profile satisfies: .

[0014] According to some embodiments of the present invention, the optical power distribution of the ophthalmic lens provides positive average additional optical power in the range of pupil diameter not exceeding 1.5-3 mm, and provides zero additional optical power when the pupil diameter is greater than 3 mm.

[0015] According to some embodiments of the present invention, at least one of the optical surfaces and / or at least one other optical surface includes a refractive multifocal profile, the refractive multifocal profile including a telephoto vision region and a mid-range vision region with a fan-shaped optical geometry, and a smoothly connected transition region between the telephoto vision region and the mid-range vision region.

[0016] According to a second aspect of the present invention, a method for manufacturing an extended depth-of-field ophthalmic lens is applicable to the above-mentioned ophthalmic lens, the manufacturing method comprising: determining an optical power distribution; Optimize the optical power distribution parameters, and obtain the optical profile parameters based on the optimized optical power distribution. The ophthalmic lens is manufactured according to the optical profile parameters.

[0017] Other features and advantages of the invention will be set forth in the description which follows, and will be apparent in part from the description, or may be learned by practicing the invention. Attached Figure Description

[0018] The present invention will be further described below with reference to the accompanying drawings and embodiments, wherein: Figure 1 An embodiment of the contribution of the peak function in the refractive power distribution provided by the present invention. Figure 1 A is the function distribution graph under the unbiased condition. Figure 1 B is the function distribution graph under the eccentric case; Figure 2 An embodiment of the contribution of the sigmoid function to the refractive power distribution provided by the present invention. Figure 2 A is the function distribution graph under the unbiased condition. Figure 2 B is the function distribution graph under the eccentric case; Figure 3 The simulation results are for an aberration-free model eye. Figure 3 A is the EDTRS image on the retina when defocus = 0.0D. Figure 3 B is the modulation transfer function (MTF) at 0.0D defocus. Figure 3 C is the EDTRS image on the retina when defocus = 1.2D. Figure 3 D represents the MTF at 1.2D defocus. Figure 3 The pass-through MTF in image space when E is 50 cyc / mm; Figure 4 Simulation results of one embodiment of adding ophthalmic lenses to the model eye. Figure 4 A is the EDTRS image on the retina when defocus = 0.0D. Figure 4 B is the modulation transfer function (MTF) at 0.0D defocus. Figure 4 C is the EDTRS image on the retina when defocus = 1.2D. Figure 4 D represents the MTF at 1.2D defocus. Figure 4 The pass-through MTF in image space when E is 50 cyc / mm; Figure 5 for Figure 4 The embodiments in A-4B introduce eccentric simulation results. Figure 5 A is the EDTRS image on the retina when the eccentricity is 0.0 mm. Figure 5 B is the modulation transfer function (MTF) when the eccentricity is 0.0 mm. Figure 5 C is the EDTRS image on the retina when the eccentricity is 0.5 mm. Figure 5 D is the modulation transfer function (MTF) with an eccentricity of 0.5 mm. Figure 5 E represents the EDTRS image on the retina when the eccentricity is 1.0 mm. Figure 5 F is the modulation transfer function (MTF) when the eccentricity is 1.0 mm. Figure 6 Simulation results of a second embodiment in which ophthalmic lenses are added to the model eye. Figure 6 A is the EDTRS image on the retina when defocus = 0.0D. Figure 6 B is the modulation transfer function (MTF) at 0.0D defocus. Figure 6 C is the EDTRS image on the retina when defocus = 1.2D. Figure 6 D represents the MTF at 1.2D defocus. Figure 6 The pass-through MTF in image space when E is 50 cyc / mm; Figure 7 for Figure 6 The embodiments in A-6B introduce eccentric simulation results. Figure 7 A is the EDTRS image on the retina when the eccentricity is 0.0 mm. Figure 7 B is the modulation transfer function (MTF) when the eccentricity is 0.0 mm. Figure 7 C is the EDTRS image on the retina when the eccentricity is 0.5 mm. Figure 7 D is the modulation transfer function (MTF) with an eccentricity of 0.5 mm. Figure 7 E represents the EDTRS image on the retina when the eccentricity is 1.0 mm. Figure 7 F is the modulation transfer function (MTF) when the eccentricity is 1.0 mm. Figure 8 A schematic diagram of the extended depth-of-field profile of three embodiments of the ophthalmic lens provided by the present invention; Figure 9 for Figure 8 The simulation structure of the embodiments in the example, Figure 9 A is the EDTRS image on the retina when defocus = 0.0D. Figure 9 B is the modulation transfer function (MTF) at 0.0D defocus. Figure 9 C is the EDTRS image on the retina when defocus = 1.2D. Figure 9 D represents the MTF at 1.2D defocus. Figure 9 The pass-through MTF in image space when E is 50 cyc / mm; Figure 10 for Figure 9 The embodiments in A-9B introduce eccentric simulation results. Figure 10 A is the EDTRS image on the retina when the eccentricity is 0.0 mm. Figure 10 B is the modulation transfer function (MTF) when the eccentricity is 0.0 mm. Figure 10 C is the EDTRS image on the retina when the eccentricity is 0.5 mm. Figure 10 D is the modulation transfer function (MTF) with an eccentricity of 0.5 mm. Figure 10 E represents the EDTRS image on the retina when the eccentricity is 1.0 mm. Figure 10 F is the modulation transfer function (MTF) when the eccentricity is 1.0 mm. Figure 11 for Figure 8 A schematic diagram of the optical profile of one embodiment is shown.

[0019] Icon labels: 1. Ophthalmic lens; 2. Anterior surface; 3. Posterior surface; 4. Refractive power distribution of the anterior surface; 5. Refractive power distribution of the posterior surface; 6. Distance vision zone; 7. Intermediate vision zone; 8. Central optical zone for distance vision; 9. Transition zone; 10. Off-center peak-shaped refractive power contribution; 11. Off-center S-shaped refractive power contribution. Detailed Implementation

[0020] Embodiments of the present invention are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and should not be construed as limiting the present invention.

[0021] In the description of this invention, it should be understood that the orientation descriptions, such as up, down, etc., are based on the orientation or positional relationship shown in the drawings and are only for the convenience of describing this invention and simplifying the description, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this invention.

[0022] In the description of this invention, "multiple" refers to two or more. The use of "first" and "second" is for distinguishing technical features only and should not be construed as indicating or implying relative importance, or implicitly indicating the number of indicated technical features or their sequential relationship.

[0023] In the description of this invention, unless otherwise explicitly defined, terms such as "set up," "install," and "connect" should be interpreted broadly, and those skilled in the art can reasonably determine the specific meaning of the above terms in this invention in conjunction with the specific content of the technical solution.

[0024] The technical solution of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the embodiments described below are some embodiments of the present invention, not all embodiments.

[0025] Monofocal lenses primarily address distance vision issues, while multifocal designs offer intermediate and near vision capabilities. However, multifocal designs present two challenges: firstly, they may generate unwanted glare; and secondly, patients typically require an adjustment period to adapt to their use.

[0026] Extended Depth of Field (EDOF) ophthalmic lenses represent an advancement designed to provide superior distance vision while enhancing intermediate-range visual acuity. This improved intermediate-range vision benefits patients in daily activities, often reducing reliance on corrective glasses for many tasks. A key advantage of EDOF designs is their ability to offer a beneficial trade-off, providing enhanced functionality for everyday activities while maintaining comparable safety to monofocal products. These designs are designed to facilitate patient adaptation and achieve better visual outcomes with minimal risk of adverse glare effects.

[0027] However, existing extended depth-of-field ophthalmic lenses are difficult to design precisely for optical power distribution, and cannot provide customized solutions for different patient needs and ocular anatomy.

[0028] To address the aforementioned problems, this invention proposes an extended depth-of-field ophthalmic lens and its manufacturing method, which effectively solves the problem of the difficulty in accurately designing the optical power distribution of existing extended depth-of-field ophthalmic lenses.

[0029] In this invention, unless the specific context otherwise requires, when referring to the X, Y and / or Z axes or coordinates, it is assumed that the coordinate system is a right-handed Cartesian coordinate system, and the Z axis is parallel to the optical axis of the ophthalmic lens.

[0030] refer to Figures 1 to 11 The present invention provides an ophthalmic lens for extending depth of field and a method for manufacturing thereof, which are illustrated in the following embodiments: The extended depth-of-field ophthalmic lens of this invention includes a lens body.

[0031] A lens body comprising at least one optical surface, the at least one optical surface comprising an extended depth-of-field profile for providing additional refractive power contribution, the extended depth-of-field profile corresponding to an optical power distribution satisfying the following formula: (1a) in, It is a power profile that functions as a horizontal coordinate. On an XY-plane perpendicular to the optical axis Z of the lens; They are all in the center Peak function with maximum value ; They all come with The coefficient of the nth term of the peak function; Functions are all located away from a certain distance from the center S-shaped function with transition at the point ; They are all sigma functions The coefficient of the m-th term; in, and , and , .

[0032] This invention designs the optical power distribution of at least one optical surface to include a combination of peak functions and / or sigmoid functions. By generating additional refractive power contributions, it redistributes light passing through the optical surface to form a continuous series of focal points, achieving an extended depth-of-field effect. Compared to traditional monofocal intraocular lenses primarily optimized for distance vision, it effectively improves intermediate vision at a given pupil size. It provides a highly versatile and customizable optical power profile design framework. By linearly combining smooth peak functions and / or sigmoid functions, almost any desired, continuously varying power distribution can be constructed. This provides an optimized basis for optimizing depth-of-field extension, controlling aberrations, managing light energy distribution, and robustness to eccentricity / tilt.

[0033] Optical surfaces in optical design can be described by analytical expressions within the optical profile, and these expressions must at least belong to C. 1 Class, but preferably belonging to C 2 The requirement of class functions ensures that the optical surface is continuous and the corresponding optical power distribution is also continuous. This means that there are no surface regions that may produce unwanted light scattering artifacts. In this context, it is accepted that the local optical power is proportional to the local surface curvature, which can be obtained from the first and / or second derivatives of the surface profile, depending on the mathematical methods and approximations used.

[0034] Regarding the number and location of optical surfaces, the optical design of ophthalmic lenses typically includes a front surface and a rear surface. However, in more complex designs, there may also be one or more internal surfaces, for example, multilayer lenses may be used. On the other hand, in simpler designs, there may actually only be one surface that dominates the optical function, while another surface plays a minor or no role in the main optical function of the lens. For example, the other surface may be flat and / or designed primarily for non-optical purposes, such as biocompatibility. Therefore, embodiments of the present invention do not limit the number and location of optical surfaces. At least one optical surface may be located on the front surface, the rear surface, or inside the lens body, etc. The number of optical surfaces may vary depending on requirements and considerations understood by those skilled in the art.

[0035] Furthermore, in the embodiments of the present invention, at least one optical surface and / or at least one other optical surface includes a base refractive profile, which is an optical base surface with a base curvature, used to provide base refractive power to correct the wearer's hyperopia or myopia, and to combine the extended depth of field effect with the base surface. While ensuring the advantages of extended depth of field, it corrects various vision conditions such as hyperopia or myopia, and integrates the functions of improving vision and extending depth of field.

[0036] Preferably, at least one of the coefficients An and Bm is positive. A positive coefficient in the optical power distribution produces an effect similar to negative spherical aberration, which is particularly beneficial in ophthalmic lens design. When An > 0, the peak function contribution creates an area of ​​increased optical power in the central region, gradually weakening towards the periphery. The resulting wavefront correction enhances focusing quality across different distances, especially improving intermediate vision, without significantly affecting the clarity of distance vision.

[0037] Preferably, all coefficients An and Bm in the embodiments of the present invention are positive. When all coefficients are positive and the refractive power contribution is located near the center of the lens surface (here, the center is defined as the position of the principal ray), a more significant extended depth of field effect can be achieved while maintaining consistent optical performance. This configuration optimizes the negative spherical aberration effect of the entire optical region, forming controllable multifocality, thereby improving vision throughout the entire focal length range.

[0038] In other embodiments, negative coefficients can be flexibly introduced, such that An < 0 or Bm < 0, to balance the distribution of optical power. These negative coefficients can create localized power reduction regions, which is beneficial for managing the light distribution between the telephoto and near-focus areas, reducing undesirable visual phenomena such as halos or glare, and optimizing performance for specific pupil sizes. By appropriately selecting the coefficients An, Bm, and their signs, it can also help reduce the sensitivity of the axial focal image contrast performance of the ophthalmic lens combined with the human eye to corneal spherical aberration.

[0039] Preferably, for extended depth of field, there is at least one center. , The peak function and the sigmoid function can be non-zero. The non-zero centers of the peak function and the sigmoid function can form an asymmetric optical power distribution. By designing the peak function and the sigmoid function to have non-zero centers, it is beneficial to adapt to the natural asymmetry of the human visual system.

[0040] The human visual system typically exhibits natural asymmetry, including variations in the kappa angle (the angle between the pupillary midline and the visual axis) and the position of the pupil center. By implementing eccentricity in the optical power distribution, as long as this eccentricity follows the natural eccentricity of the line of sight, image quality can be improved and neural adaptation of the patient's visual system can be facilitated without significantly affecting optical performance.

[0041] This invention, through the design of an optical power distribution formula that extends the depth-of-field profile with a non-zero center, generates an optical power contribution that is not centered relative to the optical axis of the ophthalmic lens. This can mitigate the impact of optical eccentricity on vision in some patients' eyes while maintaining the function of improving intermediate vision. By rotating the ophthalmic lens in the optical plane, these additional power contributions can be realigned to align with the pupil opening and / or axis of the human eye, thereby adapting to the natural eccentricity and tilt of the human eye and ensuring good optical performance.

[0042] Preferably, in the optical power distribution formula for the extended depth-of-field profile, each function , Around their respective centers , It exhibits rotational symmetry to ensure that rotationally symmetric functions can provide more consistent optical effects from different viewing angles, thereby improving overall visual performance and enhancing the user experience.

[0043] Preferably, in this embodiment of the invention, the sum of M and N is limited to less than or equal to 10 for the number of terms in the optical power distribution formula. Further, in some embodiments, the sum of M and N is preferably less than or equal to 8, more preferably less than or equal to 6, and most preferably less than or equal to 4. This embodiment of the invention simplifies the design and manufacturing process of the lens by limiting the number of terms in the optical power distribution formula. At the same time, the simplified optical power distribution formula can still provide an effective extended depth of field effect. By limiting the number of terms, manufacturing feasibility and visual performance requirements are balanced.

[0044] Furthermore, the optical power distribution can provide positive average additional optical power within a pupil diameter of 1.5 to 3 mm, and zero additional power at larger apertures. A pupil diameter of 1.5 to 3 mm is typical under photopic lighting conditions. Under photopic lighting conditions, the ophthalmic lens provided by this invention can achieve optimal visual performance, improving near and intermediate vision under bright and moderately dim light conditions when the pupil constricts. At the same time, under mesopic conditions, the pupil dilates, and good distance vision is maintained when the pupil diameter is greater than 3 mm, thereby enhancing intermediate vision while maintaining effective distance vision.

[0045] Furthermore, in some embodiments, at least one optical surface and / or at least one other optical surface are provided with additional surface profiles, which can reduce various aberrations and improve the image quality on the retina after light passes through the ophthalmic lens.

[0046] In some embodiments, at least one optical surface and / or at least one other optical surface includes a surface profile for correcting corneal asphericity, which can reduce optical aberrations and improve retinal image quality, especially in low light conditions or when the pupil is large.

[0047] Specifically, since the human eye is not typically perfectly symmetrical, the introduction of controlled aberrations enables the visual system to neurally adaptively process the resulting retinal image, potentially shortening the adaptation period after lens implantation. Notably, even with refractive power distribution eccentricity of up to 1.0 mm or more (e.g., when an ophthalmic lens with an eccentric refractive power distribution acts on a pupil with a small kappa angle), image quality remains acceptable. This indicates that the asymmetrical refractive power distribution does not significantly affect the optical performance of the ophthalmic lens. This characteristic is particularly beneficial in cases of eccentric lens distribution, as the human brain's neural adaptation capabilities more readily accommodate these intentionally eccentric distributions, leading to greater visual comfort, a shorter adaptation period, and improved functional vision across various viewing distances and lighting conditions.

[0048] In some of these implementations, at least one optical surface and / or at least one other optical surface contains a refractive multifocal profile. Combining the extended depth-of-field effect with the refractive multifocal profile can expand the range of clear vision and improve visual performance at different distances. Specifically, this design can address the transition area of ​​the defocus curve between different focal points (e.g., mid-range and near-range focal points) in basic multifocal optics by extending the depth of field, thereby reducing glare and alleviating discomfort when switching between different focal points.

[0049] In this embodiment of the invention, the refractive multifocal profile includes a fan-shaped optical geometry, wherein the refractive multifocal profile includes a distance vision zone and a mid-range vision zone with a fan-shaped optical geometry, and there is a smooth transition zone between the distance vision zone and the mid-range vision zone. By configuring the fan-shaped optical geometry, different areas can be created for distance vision and intermediate vision, and light energy can be redistributed. High visual quality can be maintained even when the pupil diameter is relatively small, and visual performance can be maintained even in the case of decentering. At the same time, the transition zone ensures a smooth transition between these areas, thereby minimizing visual interference for the wearer.

[0050] Multifocal contour ophthalmic lenses typically consist of two optical surfaces that work together to provide the required visual correction. The combined effect of the two surfaces optimizes the lens's optical performance at various distances, enhancing overall depth of field and maintaining good visual quality at multiple focal points, both near and far. This configuration provides flexibility in lens design to meet a variety of visual needs and ocular anatomy considerations.

[0051] Reference Figure 11 For example, an ophthalmic lens includes two optical surfaces, front and back. The rear optical surface uses an extended depth-of-field profile composed of an eccentric peak function and an S-shaped function, while the front optical surface uses a fan-shaped design with different optical regions. In other embodiments, these two extended depth-of-field and refractive multifocal characteristics can be integrated simultaneously on the same optical surface, while an optical profile for astigmatism correction is designed on another optical surface. This design facilitates the production of ophthalmic lenses and can effectively reduce manufacturing difficulty.

[0052] Furthermore, regarding the materials used in the ophthalmic lenses provided by this invention, the ophthalmic lenses can be made of biocompatible acrylic polymer materials. Biocompatible acrylic polymer materials can ensure the safety of the lenses when used in the human eye and provide long-term stability and optical clarity. As an alternative to acrylic polymer materials, ophthalmic lenses can also be made of silicone or other biocompatible materials suitable for ophthalmic applications.

[0053] The ophthalmic lens provided in this embodiment of the invention is an artificial intraocular lens, which achieves an extended depth-of-field effect within the artificial lens, making it suitable for cataract surgery or refractive lens replacement surgery, providing better vision for patients undergoing these treatments. Since the surface of the ophthalmic lens in this embodiment is a smooth refractive surface, it is suitable for intraocular implantation scenarios. However, this invention does not limit the structure of the ophthalmic lens. In other embodiments, the ophthalmic lens may be a contact lens, an inlay lens, a phakic intraocular lens, or an external implantable lens for vision correction.

[0054] The present invention also provides a method for manufacturing an ophthalmic lens, applicable to the above-mentioned extended depth-of-field ophthalmic lens, the method comprising: S100: Determine the optical power distribution; S200: Optimize optical power distribution parameters and obtain optical profile parameters based on the optimized optical power distribution; S300: Manufacturing ophthalmic lenses according to optical profile parameters.

[0055] The manufacturing method is described in detail below with reference to the preferred embodiments given by formulas (12) and (15): In step S100, an optical power distribution including an eccentric peak function and / or an S-shaped function is designed. In this embodiment, the optical power distribution is obtained by referring to formula (12) and formula (15).

[0056] In step S200, by optimizing the coefficients , , , , , , To optimize the optical power distribution, ray tracing can be used to optimize the lens material's physical parameters to obtain the optimal full-focal-length modulation transfer function (MTF). It should be noted that for diffractive lenses, this type of optimization cannot be performed via ray tracing and requires more complex computational methods based on physical optics principles.

[0057] Optical surfaces in optical design can be described by analytical expressions within the optical profile, and these expressions must at least belong to C. 1 Class, but preferably belonging to C 2The requirement of class-specific functions ensures that the optical surface is continuous, and the corresponding optical power distribution is also continuous. This means that there are no surface regions that may produce unwanted light scattering artifacts. In this context, it is acknowledged that the local optical power is proportional to the local surface curvature, which can be obtained from the first and / or second derivatives of the surface profile, depending on the mathematical methods and approximations used. Therefore, the optical profile parameters of ophthalmic lenses can be calculated from the optimized optical power distribution, ensuring that the complex optical power distribution is accurately translated into physical lens design and maintaining the expected extended depth of field effect.

[0058] In step S300, the actual implementation methods for manufacturing ophthalmic lenses include techniques such as lathe cutting, casting, and injection molding. Each technique has unique advantages in terms of precision, scalability, and material compatibility. Taking lathe cutting as an example, it can precisely shape the lens surface, thereby accurately replicating the complex optical power distribution required to achieve the extended depth of field effect.

[0059] The specific lathe cutting steps include: preparing the turning manufacturing CNC code based on the optical profile parameters obtained in S200. This CNC code includes additional customized machine tool parameters and manufacturing parameters, such as spindle speed, feed rate, tool radius, etc.; turning at least one optical surface of the ophthalmic lens using the turning manufacturing CNC code; reclamping; milling the lens profile using the pre-generated CNC code; cleaning the lens; removing the lens; hydrating; quality inspection; sterilization; and packaging. These steps are applicable to most hydrophilic acrylic lenses and some hydrophobic acrylic lenses.

[0060] The following are specific embodiments of an ophthalmic lens for extending depth of field and its manufacturing method provided by the present invention.

[0061] Based on formula (1a), the optical power distribution of the extended depth-of-field contour contribution is specifically given by the following formula: (1b) In the first item, It is the Euclidean norm; It is a normalized function. The maximum value of this smooth peak function is located at the center. Location, and relative to Symmetrical decrease, making ; With width parameter Steepness parameters The slope is defined to limit x when it is not zero. The dependence of the peak function on the exponent n is achieved through the dependence of the parameters on the exponent.

[0062] It is the width parameter of the nth item; It is the steepness parameter of the nth term; It is a peak function The coefficients of the nth term; these coefficients have physical dimensions, preferably expressed in diopter, in the design In the embodiments, by setting a positive coefficient, an effect similar to negative spherical aberration can be achieved, which is beneficial to enhance the focusing quality of vision at different distances; It is a peak function The center position of the nth term; It is the total number of terms that contribute to the peak function. and .

[0063] In the second item, It is a normalized function. and This smooth sigmoid function can map real values ​​to a range between 0 and 1 and... Transitional period; With steepness parameter This parameter specifies The slope in the vicinity. The dependence of the peak function on the exponent n is achieved through the dependence of the parameters on the exponent.

[0064] It uses the S-shaped function. Calculate the width or shift parameter of the nth term; It has an S-shaped function The steepness parameter of the m-th term; It has an S-shaped function The coefficient of the m-th term; coefficient It has physical dimensions, and is preferably expressed in diopter, in the design In some embodiments, setting a positive coefficient can achieve an effect similar to negative spherical aberration; however, in more complex examples... ; It is an S-shaped function The center position of the m-th item; It is the total number of terms that contribute to the sigmoid function. and .

[0065] function and All are dimensionless, and the sum of the number of terms M+N is at least two. For example, there are at least two peak function contributions, i.e., N≥2; or at least two sigmoid function contributions, i.e., M≥2; or there are at least one peak function contribution and at least one sigmoid function contribution, i.e., N≥1 and M≥1. Those skilled in the art will understand that "at least two contributions" means that at least two contributions are mutually different. In the embodiment of equation (1b), this means that at least one pair of parameters of at least two terms in the optical power distribution formula are mutually different, such that the optical power is mainly changed by one of the terms in different ranges.

[0066] The selection of parameters or coefficients in the optical power distribution formula can be adapted to the visual performance requirements of different ophthalmic lenses. For example, for patients with small pupils, the width parameter can be reduced to concentrate the optical effect within the smaller pupil diameter, while for patients with large pupils, the width parameter can be increased to distribute the optical effect over a larger optical area.

[0067] The selection of parameters or coefficients in the optical power distribution formula can also be adjusted according to the type of ophthalmic lens. For example, contact lenses move freely on the surface of the eye, while artificial lenses are implanted inside the eye and need to be kept fixed near the pupil. In this case, it is necessary to select a non-zero value based on the type of ophthalmic lens, the center position, and the type of non-zero value.

[0068] Peak functions in formulas (1a) and (1b) The choice can be an exponential function, a sigmoid function, a polynomial expression, and / or any analytical expression with the desired peak profile. Two possible implementations are given below: (2a) (2b) Reference Figure 1 As shown, Figure 1 A and Figure 1 B corresponds to the peak function of formula (2b), where, and , Figure 1 A shows that The example peak function centered on the center, Figure 1 B shows the position where the example peak function moved. The situation of eccentricity.

[0069] S-shaped functions in formulas (1a) and (1b) The choice can be an exponential function, a sigmoid function, a polynomial expression, and / or any analytical expression with the desired peak profile. Two possible implementations are given below: (3a) (3b) Alternatively, equation (2b) can also be used for s-shaped functions, i.e. ,in The width of the sigmoid function makes equation (2b) satisfy the condition: It varies between 1 and 0. It should also be noted that this is due to the width parameter in formulas (1a) and (1b). , variables in It can take both positive and negative values.

[0070] Reference Figure 1 As shown, Figure 2 A and Figure 2 B corresponds to the peak function of formula (2b), where, and , Figure 2 A shows that The example peak function centered on the center, Figure 2 B shows the position where the example peak function moved. The situation of eccentricity.

[0071] It should be noted that formulas (1b), (2a), (2b), (3a) and (3b) are only one possible implementation of formula (1a). The specific expression of formula (1a) is not limited to the above formula and other formulas can be used instead.

[0072] To implement ophthalmic lenses conforming to formulas (1a) and (1b), the corresponding optical profile parameters need to be obtained by transforming the optical power distribution according to formulas (1a) and / or (1b). This transformation can be achieved through various methods known to those skilled in the art, including analytical transformation, ray tracing, etc. The wavefront path is established below. with local convergence Contact: (7) Among them, wavefront path The following formula can be used to address surface depressions. Related: (8) in, and These are the refractive indices of the lens material and the surrounding medium, respectively; when the surface depression is defined in mm, a factor of 1000 is introduced to obtain local convergence in the commonly accepted unit of diopter (reciprocal meter).

[0073] It should be noted that formula (7) represents local convergence. Or local optical power and the light transmitted through the surface The light wavefront behind the formed optical interface One possible relationship between them is that alternative mathematical expressions can be used to relate the wavefront to the local optical power, without being limited to formula (7).

[0074] In formula (8), the surface depression is given in cylindrical coordinates and can be used... The formula converts it to a Cartesian coordinate system; here Assuming the coordinate transformation described above, the surface depression is represented below as... Or equivalently represented as Starting with equation (1a), the above expressions related to surface or power can also be represented in an alternative coordinate system, depending on the chosen notation and the practical applicability of the surface geometry. This transformation is known to those skilled in the art.

[0075] According to formulas (7) and (8), surface depression (Unit: mm) Convergence functions can be used. (Unit: diopters) An assessment will be conducted: (9) Select the integration limit here to ensure From equation (9), it can be seen that when When, the surface profile value is The expression corresponds to a focal length of . The parabolic lens is concave, in which Units are millimeters.

[0076] When applying equation (9) to ophthalmic lenses, the refractive power referred to is... (10) in This refers to the base refractive power of the ophthalmic lens surface, for example, ranging from -10.0D to +50.0D. The additional refractive power required to extend the depth of field is given by equations (1a) and / or (1b) above. Applying equation (9), the surface concavity becomes: (11) To ensure compatibility with conventional ophthalmic lens designs, the constant base refractive power of the term in formula (10) that causes the concavity of the parabolic surface is used. The surface depression can be replaced by a traditional conical cross-section profile, thus yielding the expression for the surface depression using formula (11): (12) In this figure, the first item in brackets represents a standard conic section. In this context, This represents the radial distance to the vertex of the lens surface. Indicates curvature. ,in It is the radius of curvature of the basic optical surface. This represents the conic constant. Preferably negative, corresponding to the shape of a long ellipsoid or parabola. In a preferred embodiment, the radius of curvature... Typically within the range of -100.0 mm to -100.0 mm, where Corresponds to a flat surface.

[0077] The additional refractive power contribution that provides extended depth-of-field performance can include contributions from two eccentric peak functions; for example, the optical power distribution can be expressed by the following equation: (13) Wherein, the width parameter is Steepness parameter is and , making Represented as a rational form, in some other embodiments, Other expressions are possible, such as choosing different values ​​for the steepness parameter.

[0078] and It is the amplitude of the peak function term in the optical power distribution, with units of diopter, and is the reciprocal of the length unit, 1D = 1m. -1 ; It is a scaling factor that defines the width of the peak function, in length (mm). It is the eccentric vector that defines the position of the eccentric peak in the Cartesian coordinate system, given by a value in two length units (mm).

[0079] Reference Figures 3 to 5 The imaging performance of an ophthalmic lens design employing the optical power contribution of Equation (13) is demonstrated, including the relationship between modulation transfer function (MTF) and spatial frequency, simulated images from the Early Treatment of Diabetic Retinopathy in Retina Study (ETDRS), and MTF response within the focal range. These results are compared with an aberration-free design.

[0080] Figure 3 To compare the imaging performance of the imageless model eye, the simulation parameters are as follows: (λ = 546 nm, pupil size 3.0 mm, exit pupil distance to retina 14 mm). Figure 3 A is the EDTRS image on the retina when defocus = 0.0D. Figure 3 B is the modulation transfer function (MTF) at 0.0D defocus. Figure 3 C is the EDTRS image on the retina when defocus = 1.2D. Figure 3 D represents the MTF at 1.2D defocus. Figure 3 E represents the focus MTF in image space at 50 cycles / mm. Figure 3 On the E-axis, the MTF value is a dimensionless value, while the defocus is measured in D. It can be seen that as the defocus increases, the image quality decreases very quickly.

[0081] Figure 4 Showing with Figure 3 The same simulation was performed, but an ophthalmic lens with extended depth of field was added to the eye of the aberration-free model, using formula (13), where, , , , ,contrast Figure 3 As you can see, the contrast is not as good as Figure 3 The aberration-free design in the A-3E. However, the focal length MTF response curve shows that this design produces a wider profile, which is beneficial for intermediate vision performance, and has a secondary contrast peak at approximately 1.2D. Simulated EDTRS images at 1.2D defocus still show acceptable image quality, while the image quality of the aberration-free design suffers a significant decrease in sharpness. Figure 4 In the simulated state, although the focusing performance is slightly worse, it is still within an acceptable range, while the defocusing performance is greatly improved.

[0082] Figure 5 A-5F demonstrated with Figure 4 The simulation was the same as for A-4B, only simulating a different degree of optical deflection. Model parameters are as follows: Figure 4 As shown in A-4B, eccentricity passes through Introduced, among which This refers to the tangential eccentricity. Figure 5 In the A-5F, the out-of-focus value is 0.0D, while... Figure 5 In A-5B, the eccentricity is 0.0 mm. Figure 5 The thickness is 0.5mm in the C-5D. Figure 5 The value is 1.0 mm in E-5F.

[0083] Figure 5A-5F demonstrates the imaging performance of a phakic eye model using Equation (13), with an implanted intraocular lens as an example. Modulation transfer function (MTF) performance gradually decreases with optical power contribution eccentricity of 0.5 mm and further 1.0 mm. However, even with high eccentricity, the quality of the retinal image remains acceptable. These results indicate that optical power distribution eccentricity does not significantly degrade image quality performance in eyes implanted with this extended depth-of-field ophthalmic lens, demonstrating strong robustness to additional power distribution eccentricity. Since some degree of eccentricity often occurs in practical applications, and eccentricity contributes to wearer neural adaptation, this robustness of simulated optical performance helps improve the performance of ophthalmic lenses in real-world applications.

[0084] The additional refractive power contribution that provides extended depth-of-field performance can include two eccentric sigmoid function contributions; for example, the optical power distribution can be expressed by the following equation: (14) Wherein, the steepness parameter is The amplitude coefficient is Assuming The distribution in equation (15) will result in an eccentric "donut" shaped optical power distribution map. The corresponding surface profile... It can be derived from equation (11) or equation (12).

[0085] Figure 6 Showing with Figure 3 The same simulation was performed, but an ophthalmic lens with extended depth of field was added to the eye of the aberration-free model, using formula (14), where, , , , ,contrast Figure 3 As you can see, the contrast is not as good as Figure 3 The aberration-free design in the A-3E. However, the focal length MTF response curve shows that this design produces a wider profile, which is beneficial for intermediate vision performance, and has a secondary contrast peak at approximately 1.2D. Simulated EDTRS images at 1.2D defocus still show acceptable image quality, while the image quality of the aberration-free design suffers a significant decrease in sharpness. Figure 6 In the simulated state, although the focusing performance is slightly worse, it is still within an acceptable range, while the defocusing performance is greatly improved.

[0086] Figure 7 The A-7F demonstrated with Figure 6 The simulation results for A-6B were the same, only simulating different degrees of optical deviance. The model parameters are as follows: Figure 6 As shown in A-6B, via Introducing eccentricity, where This refers to the tangential eccentricity. Figure 7 In the A-7F, the out-of-focus value is 0.0D, while... Figure 7 The eccentricity in A-7B is 0.0 mm. Figure 7 The thickness is 0.5mm in C-7D. Figure 7 The value is 1.0 mm in E-7F.

[0087] Figure 7 A-7F demonstrates the imaging performance of a phakic eye model using Equation (14), with an implanted intraocular lens as an example. Modulation transfer function (MTF) performance gradually decreases with optical power contribution eccentricity of 0.5 mm and further 1.0 mm. However, even with high eccentricity, the quality of the retinal image remains acceptable. These results indicate that optical power distribution eccentricity does not significantly degrade image quality performance in eyes implanted with this extended depth-of-field ophthalmic lens; that is, the optical performance of this ophthalmic lens is robust to additional power distribution eccentricity, and the sensitivity of the optical power distribution to extreme eccentricity is reduced.

[0088] In another embodiment of the ophthalmic lens based on formula (1a) or (1b), the additional refractive power contribution includes two eccentric peak function contributions and two eccentric sigmoid function contributions, which together form a complex optical power distribution based on formulas (13) and (14). By applying equation (11) or equation (12), the combined optical power profile can be converted into a surface profile. Examples of extended depth-of-field surfaces with this power profile include... Figure 8 As shown.

[0089] Figure 9 Showing with Figure 3 The same simulation, but with the addition of elements corresponding to the model's eye. Figure 8 The optical power distribution, in comparison Figure 3 As you can see, the contrast is not as good as Figure 3 The aberration-free design in the A-3E. However, the focal length MTF response curve shows that this design produces a wider profile, which is beneficial for intermediate vision performance, and has a secondary contrast peak at approximately 1.2D. Simulated EDTRS images at 1.2D defocus still show acceptable image quality, while the image quality of the aberration-free design suffers a significant decrease in sharpness. Figure 9 In the simulated state, although the focusing performance is slightly worse, it is still within an acceptable range, while the defocusing performance is greatly improved. Furthermore, it can be seen that... Figure 9 The image quality in it is better than Figure 4 ,but Figure 4 and Figure 9 All images are of acceptable quality.

[0090] Figure 10 A-10F demonstrated with Figure 9 The simulation results for A-9B are the same, only simulating different degrees of optical deviance. Model parameters are as follows: Figure 9 As shown in A-9B, via Introducing eccentricity, where This refers to the tangential eccentricity. Figure 10 In the A-10F, the defocus is 0.0D, while... Figure 10 The eccentricity in A-10B is 0.0 mm. Figure 10 The thickness is 0.5mm in the C-10D. Figure 10 The value is 1.0 mm in E-10F.

[0091] Reference Figure 11 The diagram shown is a structural schematic of an embodiment of the present invention. The lens body 1 includes a front surface 2 with a fan-shaped optical structure and a rear surface 3 with an off-center peak and an S-shaped contribution. In the refractive power distribution 4 of the front surface, the horizontal and vertical scales are relative values, corresponding to the entire lens aperture. It shows a distance vision zone 6 and a mid-distance vision zone 7 with a fan-shaped optical geometry. The mid-distance vision zone 7 has a central optical zone 8 for distance vision to promote distance vision. There is a smooth transition zone 9 between the distance vision zone 6 and the mid-distance vision zone 7. In the refractive power distribution 5 of the rear surface, the horizontal and vertical scales are relative values, corresponding to the entire lens aperture. The refractive power distribution 5 of the rear surface includes an off-center peak 10 and an S-shaped contribution 11.

[0092] Figure 11 Only one of the many preferred embodiments is shown. In other embodiments, the ophthalmic lens may be in other forms, such as: the posterior surface 3 having fan-shaped optical properties, and / or the anterior surface 2 having peak-shaped and / or S-shaped contributions; the lens body 1 having one, three or more surfaces, etc.

[0093] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0094] The embodiments of the present invention have been described in detail above with reference to the accompanying drawings. However, the present invention is not limited to the above embodiments. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of the present invention.

Claims

1. An extended depth of focus ophthalmic lens characterized by, Comprising: a lens body comprising at least one optical surface, at least one of said optical surface comprising an extended depth of focus profile for providing an additional refractive power contribution, said extended depth of focus profile corresponding to an optical power distribution satisfying the following equation: ， wherein is a power profile as a function of the transverse coordinate, in an XY-plane perpendicular to the optical axis Z of the lens; are a center peak function with maximum ; are a band coefficient of the nth term of the peak function Functions are all S-shaped functions with a transition at a distance from the center ; ; are all S-shaped functions of the m-th term; wherein and , and , .

2. The ophthalmic lens of claim 1, wherein, Comprising: at least one of said optical surface and / or at least one other of said optical surface comprising a base refractive profile, said base refractive profile being an optical base curve having a base curvature, said base refractive profile being for providing a base refractive power.

3. The ophthalmic lens of claim 1, wherein: at least one of the coefficients , is positive.

4. The ophthalmic lens of claim 3, wherein: The coefficients , are positive values.

5. The ophthalmic lens of claim 1, wherein: The center , At least one of the center 6. The ophthalmic lens of claim 1, wherein: where each function , is rotationally symmetric around its respective center , .

7. The ophthalmic lens of claim 1, wherein: The total number of terms M+N of the optical power distribution formula of the extended depth of field profile satisfies: .

8. The ophthalmic lens of any one of claims 1 to 7, wherein: the optical power distribution of said ophthalmic lens provides a positive mean additional optical power for pupil apertures of up to 1.5-3 mm and zero additional optical power for pupil apertures greater than 3 mm.

9. The ophthalmic lens of any one of claims 1 to 8, wherein: at least one of said optical surface and / or at least one other of said optical surface comprises a refractive multifocal profile comprising a distance vision zone and an intermediate distance vision zone in a sectorial optical geometry, said distance vision zone and said intermediate distance vision zone having a transition zone with a smooth connection therebetween.

10. A method of manufacturing an ophthalmic lens with extended depth of field, characterized in that, A method of manufacturing an ophthalmic lens according to any one of claims 1 to 9, said method comprising: determining an optical power distribution; optimizing parameters of the optical power distribution, the optical profile parameters being derived from the optimized optical power distribution; manufacturing said ophthalmic lens according to said optical profile parameters.

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