Eye lens for extending depth of focus, design method thereof, and manufacturing method thereof

Abstract

The goal is to widen the depth of focus for near and / or intermediate vision, and / or improve image quality for far vision. [Solution] The lens has a region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision. In the distance region, the power is reduced so that a negative vertical spherical aberration is present that at least partially cancels out the positive vertical spherical aberration caused by the cornea. In the near region, a positive constant power is added to a predetermined aspherical reference power within a predetermined radial range of a virtual aspherical lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. The near region comprises at least three sub-regions arranged radially, sub-region 1 providing a positive power deviation to the positive constant power, sub-region 2 providing a nearly zero power deviation to the positive constant power, and sub-region 3 providing a negative power deviation to the positive constant power.

Description

Technical Field

[0001] The present invention relates to an intraocular lens, a method for designing an intraocular lens, a method for manufacturing an intraocular lens, an ophthalmic lens, an optical design method for an ophthalmic lens, and a method for manufacturing an ophthalmic lens. For example, the present invention relates to an ophthalmic lens having a base power for correcting distant vision and an additional power for correcting near vision and / or intermediate vision.

[0002] The present invention relates to a new optical design of an intraocular lens (IOL) that can be used not only for correcting distant vision but also for correcting near vision and / or intermediate vision, and a phakic intraocular lens (or an implantable contact lens (ICL), the term "implantable" will be omitted hereinafter). In the present disclosure, only the intraocular lens will be described in detail as a representative of various ophthalmic lenses. However, the present invention is also applicable to the optical design of phakic intraocular lenses and contact lenses.

Background Art

[0003] In addition to correcting distant vision, an IOL having an additional power can also be used for correcting the near vision and / or intermediate vision of aphakic patients.

[0004] In this specification, the additional power is also referred to as "addition of positive power". Just because the term "additional power" is used, it is not limited to an ophthalmic lens having an additional power (ADD) as a prescription value.

[0005] In this specification, the term "extended vision range IOL" means an IOL having a base power for correcting distant vision and an additional power for correcting near vision and / or intermediate vision. The extended vision range IOL is also referred to as "EVR IOL" in this specification.

[0006] In this specification, the case of viewing objects at infinity is used as an example, but it is also possible to consider viewing objects at a finite distance (1.5m or more (far distance)) rather than at infinity. For intermediate vision, one can consider viewing objects at an intermediate distance of 1.5m to 50cm. For near vision, we can consider the case of viewing objects at a distance of 50 cm or less (near distance). In any case, viewing distances greater than near vision is called intermediate vision, and viewing distances greater than intermediate vision is called far vision.

[0007] The lens center O refers to the geometric or optical center of the intraocular lens. In this specification, the case where the geometric center and the optical center coincide is given as an example. The refractive power at this lens center O is called the base power. This base power refers to the refractive power required for distance vision in conventional intraocular lenses.

[0008] EVR IOLs, which obtain add power by applying the principles of refractive optics, can be classified into bifocal and multifocal types. In patients with aphakia, bifocal intraocular lenses (bifocal lenses) tend to form two primary focal lengths. One focal length is set to focus light rays from a distance to correct distance vision (distance visual acuity). The other focal length is set to focus light rays from a near distance to correct near vision (near visual acuity). A multifocal intraocular lens (multifocal lens) implanted in the eye of a patient with aphakia creates three or more focal lengths. Typically, one focal length is used to correct distance vision, while two or more focal lengths are used to correct near and intermediate vision.

[0009] The first focal length of an EVR IOL used for correcting distance vision is related to the base power of the IOL. In other words, the first focal length corresponds to the spherical power (labeled refractive power) as a prescription value for the IOL, for example, 20.0 D (unit: diopter, hereafter the same). The secondary focal length used to correct near and / or intermediate vision relates to the sum of the base power (labeled refractive power) and the add power in that IOL. For example, if the add power of that IOL is 3.0D, the secondary focal length relates to a power value of 23.0D (the sum of the labeled refractive power of 20.0D and the add power of 3.0D).

[0010] Refractive EVR IOLs can be classified into three types (for example, Patent Document 1, WO2021 / 111821, by the present applicant). For information not described herein, please refer to the content of Patent Document 1. One of these three types is an enhanced monofocal IOL (commonly known as EM-IOL), for example, in which one or more added positive constant powers are 1.25D or less. Another type is a multifocal lens (for example, in which one or more added constant positive powers, i.e., an add power of 2.5D or more). There is also an intermediate lens called an extended depth-of-focus IOL (commonly known as EDOF) (for example, in which one or more added constant positive powers are greater than 1.25D and less than 2.5D (e.g., 2D)). It should be noted that the classification in this paragraph is merely an example, and for example, if two types of positive constant frequencies are provided, such as one value being 1.25D or less and the other value being greater than 1.25D but less than 2.5D, this is not excluded from the present invention.

[0011] EM-IOLs are designed, for example, to correct distance and intermediate vision. Typically, this type of IOL has an add power of 1.25 to 2.0 D at the IOL surface (approximately 0.9 to 1.4 D at the corneal surface). EDOF (End of Distance) lenses are designed to correct distance vision, intermediate vision, and slightly near vision. Typically, their add power is 2.0–2.75D as surface refractive power (approximately 1.4–1.9D at the corneal surface). Multifocal lenses are designed to correct distance, intermediate, and near vision. Typically, their add power is greater than 2.75D in terms of surface refractive power (greater than 1.9D in terms of corneal surface).

[0012] The disadvantage of bifocal lenses lies in the narrow range of near distances at which aphakia patients can clearly see objects, resulting in a short range of near visual acuity. This narrow range of near vision is particularly noticeable in bifocal IOLs where the add power is relatively constant in the lens area (zone) used to correct near vision. Furthermore, bifocal IOLs with a relatively large lens area for correcting near vision have the disadvantage of having a smaller lens area used for correcting far vision, resulting in a loss of image quality (image sharpness and contrast) in far vision.

[0013] Assuming implantation in the eyes of aphakia patients, a bifocal type EVR IOL with strong bifocal characteristics can provide the wearer with clear images of two objects at different distances from each other. One clear distance image (the image of a distant object reconstructed on the retina) and one clear near image (the image of a near object reconstructed on the retina) are visible to the aphakia patient. However, with respect to objects immediately in front of the cornea, they are clearly visible to the aphakia patient's eye if only the light rays from that object are focused onto the retina by the corneal optics and the EVR IOL. For the object to be focused on the retina, the distance of that nearby object in front of the cornea must be within a specific near-distance range. This specific near-distance range, in which near-distance objects are still visible, is clearly related to the add power and power profile (also called radial power or power distribution) of the EVR IOL. A power profile is, for example, a graph with radius (in mm) on the horizontal axis and power (refractive power) (in D) on the vertical axis. This type of graph shows the power value at a specific radius value, which is the radial distance from the lens center O in an IOL.

[0014] There are numerous bifocal type EVR IOLs disclosed in patent documents.

[0015] Patent document 2 (US4636211) discloses a bifocal IOL with a two-zone design. This IOL comprises a central region for correcting near vision and an annular region surrounding the central region for correcting far vision.

[0016] Patent Document 3 (US5192317) discloses a three-zone IOL comprising a central region for correcting distance vision, a first annular region surrounding the central region for correcting near vision, and a second annular region surrounding the first annular region for correcting distance vision.

[0017] Patent Document 4 (US4813955) discloses a four-zone intraocular lens having a central region, a first annular region, a second annular region, and a third annular region having functions to correct distance vision, distance vision, and near vision.

[0018] Patent document 5 (WO1997 / 26843) discloses a five-zone IOL comprising a central region, a second annular region, and a fourth annular region for correcting distance vision, and a first annular region and a third annular region for correcting near vision. The advantage of bifocal lenses is that they can form two sharp images on the retina, one of which is a sharp image of a near object within a limited range, and the other is a sharp image of a far-distance object.

[0019] Furthermore, there are patent documents disclosing IOLs that have one or more regions for correcting distance vision and one or more regions for correcting near vision, with one or more transition regions between the regions for correcting distance vision and the regions for correcting near vision. Examples of these patent documents are Patent Document 6 (US5112351), Patent Document 7 (EP0942312B1), and Patent Document 8 (US6457826). The IOLs described in these patent documents can improve the image quality of intermediate vision. On the other hand, the image quality of near vision is lower than that of bifocal IOLs. The image quality of distance vision is also inferior to that of bifocal lenses. The reason for this low image quality in distance and near vision is due to the transition regions or the power in the transition regions, which are characteristic of these patent documents. In other words, the number of rays coming from near distance is reduced by the number of rays coming from intermediate distance that can be focused on the retina, and the number of rays coming from far distance that should reconstruct the image related to distance vision on the retina is also reduced.

[0020] Typical EVR IOLs in the refractive bifocal type have 2-zone and 3-zone optical designs. IOLs with a two-zone optical design have two regions. The inner region (the first region, including the lens center) has a higher power than the outer region, which is used to correct near vision. The outer region has a base power for correcting distance vision. IOLs with a 3-zone optical design have three zones. The first zone, including the center of the lens, is used to correct distance vision. The second zone is an annular region surrounding the first zone, has a power value greater than the base power value, and is used to correct near vision. The third zone is an annular region surrounding the second zone and is used to correct distance vision. The optical properties and performance of bifocal 2-zone and bifocal 3-zone IOLs for correcting distance and near vision in aphakia patients depend on the add power value and power profile of those IOLs. [Prior art documents] [Patent Documents]

[0021] [Patent Document 1] WO2021 / 111821 Publication [Patent Document 2] US4636211 Specification [Patent Document 3] US5192317 Specification [Patent Document 4] US4813955 Specification [Patent Document 5] WO97 / 026843 Publication [Patent Document 6] US5112351 Specification [Patent Document 7] EP0942312B1 Specification [Patent Document 8] US6457826 Specification [Summary of the Invention] [Problems to be Solved by the Invention]

[0022] In this specification, for example, a new diopter profile of a bifocal type EVR IOL is disclosed. Further, the new bifocal type EVR IOL can have an optical design of two zones and three zones.

[0023] The diopter profile disclosed in this specification can improve, for example, the optical characteristics and performance of a bifocal type EVR IOL for correcting the far vision and near vision of the eyes of aphakic patients.

[0024] An object according to one aspect of the present invention is to widen the depth of focus of near vision and / or intermediate vision and / or improve the image quality of far vision as compared with those (described as "Flat") to which the present invention is not applied among the specific examples described below. [Means for Solving the Problems]

[0025] According to a first aspect of the present invention, the lens comprises at least one distance region for correcting distance vision and at least one near region for correcting near vision, wherein the distance region and the near region are concentric with respect to the lens center O. In the aforementioned far region, as the radial distance to the lens center O increases, the optical power of the lens decreases. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 introduces a positive frequency deviation to the virtual optical frequency profile in the near region, and the virtual optical frequency profile is an aspherical frequency profile with a constant positive frequency added. Sub-region 2 results in a zero frequency deviation with respect to the virtual optical frequency profile. Subregion 3 provides an intraocular lens that results in a negative power deviation with respect to the virtual optical power profile. In other words, sub-region 1 results in a positive frequency deviation for a constant positive frequency, sub-region 2 results in a zero frequency deviation for a constant positive frequency, and sub-region 3 results in a negative frequency deviation for a constant positive frequency. IOLs with these three sub-regions in the near field of view have been found to lead to an extension of the depth of focus for near vision. Preferably, in sub-region 2, a frequency deviation is considered to be zero if the mean of the frequency deviations in sub-region 2 is in the range of -0.2 to 0.2D. For this reason, a zero frequency deviation can also be considered to be approximately zero. The far-field region, where the optical power of the lens decreases as the radial distance to the lens center O increases, can also be considered a far-field region where the power decreases. Preferably, in the far-field region, the optical power of the lens decreases as the radial distance to the lens center O increases; that is, the far-field region reduces the power in order to at least partially offset the positive longitudinal spherical aberration of the human cornea with negative longitudinal spherical aberration. Therefore, preferably, in the far-field region, the decrease in optical power with increasing radial distance to the lens center, i.e., the corresponding power profile, is such that the positive longitudinal spherical aberration of the human cornea is at least partially offset. This enables improved distance vision. In one example, the human cornea is an average human cornea. Therefore, in one example, the power decreases in the distance region; that is, in the distance region, the optical power decreases as the radial distance to the center of the lens increases, because the positive longitudinal spherical aberration of the average human cornea is at least partially offset by the negative longitudinal spherical aberration. The average human cornea is the average of several human corneas. The average human cornea can be any average of human corneas. For example, the average can correspond to the cornea of ​​a human eye model in optical design software such as Zemax®, particularly Zemax® 13. The average cornea may correspond to the corneas listed in Table 1 of this specification. Preferably, the aspheric power profile of the virtual optical power profile (which can also be considered as an aspheric reference power) can be expressed as having a base power at the lens center O, and in the near region, a positive constant power is added to the aspheric reference power to form a virtual optical power profile which can also be considered as the power profile of a virtual aspheric lens. In other words, in the near region, a positive constant power is added to the aspheric reference power within a predetermined radial range in the virtual aspheric lens, which has a base power at the lens center O. The virtual optical power profile in the near region is preferably such that the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea, is canceled out. This cancellation may be partial or complete. In one embodiment, the near region has a predetermined base power at the lens center O, and a constant positive power is added to the aspheric base power within a predetermined radial range of the virtual aspheric lens to completely cancel out the positive longitudinal spherical aberration of the average human cornea. Thus, the first embodiment is, A region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision, In the aforementioned distant region, the power is reduced so that a negative longitudinal spherical aberration is present that at least partially cancels out the positive longitudinal spherical aberration caused by the cornea. In the aforementioned near region, a positive constant power is added to the aspherical reference power within a predetermined radial range of a virtual aspherical lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a zero frequency deviation, particularly a nearly zero frequency deviation, for the aforementioned positive constant frequency. Subregion 3 is an intraocular lens that produces a negative power deviation relative to the aforementioned positive constant power. The power reduction of the aspherical power profile in the near region is preferably equal to the power reduction in the far region. In other words, for example, in the far region, the optical power decreases as the radial distance to the lens center increases, in line with the power reduction of the aspherical power profile of the virtual optical power profile in the near region.

[0026] The near-field region includes the lens center O, and the far-field region may be located outside the near-field region. Therefore, the second embodiment is, A region concentric with the lens center O, comprising a near region that includes the lens center O and corrects near vision, and a far region that is located outside the near region when the radial direction from the lens center O is taken outward and corrects far vision, In the aforementioned distant region, the power is reduced so that a negative longitudinal spherical aberration is present that at least partially cancels out the positive longitudinal spherical aberration caused by the cornea. In the aforementioned near region, a positive constant power is added to the aspherical reference power within a predetermined radial range of a virtual aspherical lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a zero frequency deviation, particularly a nearly zero frequency deviation, for the aforementioned positive constant frequency. Subregion 3 is an intraocular lens that produces a negative power deviation relative to the aforementioned positive constant power.

[0027] According to a third aspect of the present invention, the lens comprises a distance region including the lens center O and correcting distance vision, and an outer region positioned outside the near region that corrects near vision when the radial direction is taken outward from the lens center O, and correcting distance vision, wherein the distance region, the near region, and the outer region are concentric with respect to the lens center O, that is, they start from the lens center O and are oriented radially away from the lens center O, and the order of the regions is the distance region, the near region, and the outer region. In the aforementioned outer region, the optical power of the lens decreases as the radial distance to the lens center O increases. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 results in a positive frequency deviation to the virtual optical frequency profile in the near region, which is the sum of the aspherical frequency profile and a positive constant frequency; that is, the virtual optical frequency profile is the aspherical frequency profile with a positive constant frequency added to it. Sub-region 2 results in a zero frequency deviation with respect to the virtual optical frequency profile. Subregion 3 provides an intraocular lens that results in a negative power deviation with respect to the virtual optical power profile. In other words, sub-region 1 results in a positive frequency deviation for a constant positive frequency, sub-region 2 results in a zero frequency deviation for a constant positive frequency, and sub-region 3 results in a negative frequency deviation for a constant positive frequency. IOLs with these three sub-regions in the near region can extend the depth of focus for near vision, and the inner far region, in conjunction with the outer region, can improve image quality for far vision. Preferably, in sub-region 2, a frequency deviation is considered to be zero if the mean of the frequency deviations in sub-region 2 is in the range of -0.2 to 0.2D. For this reason, a zero frequency deviation can also be considered to be approximately zero. The far region in which the optical power of the lens decreases as the radial distance to the lens center O increases can also be considered a far region where the power decreases. Preferably, in the outer region, the optical power of the lens decreases as the radial distance to the lens center O increases; that is, the outer region reduces the power in order to at least partially offset the positive longitudinal spherical aberration of the human cornea with negative longitudinal spherical aberration. Therefore, preferably, in the outer region, the decrease in optical power with increasing radial distance to the lens center, i.e., the corresponding power profile, is such that the positive longitudinal spherical aberration of the human cornea is at least partially offset. This enables further improved distance vision. As explained above, in one example, the human cornea is an average human cornea. Therefore, in one example, the power decreases in the outer region, that is, in the outer region, the optical power decreases as the radial distance to the center of the lens increases, in order to at least partially offset the positive longitudinal spherical aberration of the average human cornea with the negative longitudinal spherical aberration. The average human cornea is the average of several human corneas. The average human cornea can be any average of human corneas. For example, the average can correspond to the corneas in human eyeball models of optical design software such as Zemax®, particularly Zemax® 13. The average may correspond to the corneas listed in Table 1 of this specification. Preferably, the aspheric power profile of the virtual optical power profile (which can also be considered as an aspheric reference power) can be expressed as having a base power at the lens center O, and in the near region, a positive constant power is added to the aspheric reference power to form a virtual optical power profile which can also be considered as the power profile of a virtual aspheric lens. In other words, in the near region, a positive constant power is added to the aspheric reference power within a predetermined radial range in the virtual aspheric lens, which has a base power at the lens center O. The virtual optical power profile in the near region is preferably such that the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea, is canceled out. This cancellation may be partial or complete. In one embodiment, the near region has a predetermined base power at the lens center O, and a constant positive power is added to the aspheric base power within a predetermined radial range of the virtual aspheric lens to completely cancel out the positive longitudinal spherical aberration of the average human cornea. Therefore, the third aspect is, A region concentric with the lens center O, comprising: a distance region that includes the lens center O and corrects distance vision; a near region located outside the distance region when the radial direction from the lens center O is taken outward and corrects near vision; and an outer region located outside the near region and corrects distance vision. In the aforementioned outer region, the power is reduced so that a negative longitudinal spherical aberration is present that at least partially cancels out the positive longitudinal spherical aberration caused by the cornea. In the aforementioned near region, a positive constant power is added to the aspherical reference power within a predetermined radial range of a virtual aspherical lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a zero frequency deviation, particularly a nearly zero frequency deviation, for the aforementioned positive constant frequency. Subregion 3 is an intraocular lens that produces a negative power deviation relative to the aforementioned positive constant power. The power reduction of the aspherical power profile in the near region is preferably equal to the power reduction in the outer region. In other words, in one example, in the outer region, the optical power decreases as the radial distance to the lens center O increases, in line with the power reduction of the aspherical power profile of the virtual optical power profile in the near region. Furthermore, preferably, the decrease in power with increasing radial distance in the outer region is equal to the decrease in power with increasing radial distance in the far region. In particular, in the outer and far regions, the optical power can decrease as the radial distance to the lens center O increases, in line with the decrease in the aspheric power profile of the virtual optical power profile in the near region. In other words, in one example, the decrease in power in the outer and far regions can be represented by the aspheric power profile of the virtual optical power profile in the near region; that is, in one example, the IOL has an aspheric power profile extending from the lens center O through the far region, near region, and outer region, and in the near region, a constant positive power is added to the aspheric power profile.

[0028] According to a fourth aspect of the present invention, the lens comprises at least one distance region for correcting distance vision and at least one near region for correcting near vision, wherein the distance region and the near region are concentric with respect to the lens center O. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 introduces a positive frequency deviation to the virtual optical frequency profile in the near region, and the virtual optical frequency profile is an aspherical frequency profile with a constant positive frequency added. Sub-region 2 results in a zero frequency deviation with respect to the virtual optical frequency profile. Subregion 3 provides an ophthalmic lens that results in a negative power deviation with respect to the virtual optical power profile. In other words, sub-region 1 results in a positive frequency deviation for a constant positive frequency, sub-region 2 results in a zero frequency deviation for a constant positive frequency, and sub-region 3 results in a negative frequency deviation for a constant positive frequency. Ophthalmic lenses that have these three sub-regions in the near field of view lead to an extension of the depth of focus for near vision. Preferably, the aspherical power profile of the virtual optical power profile (which can also be considered as an aspherical reference power) can be expressed as having a base power at the lens center O, and in the near region, a positive constant power is added to the aspherical reference power to form a virtual optical power profile which can also be considered as the power profile of a virtual aspherical lens. In other words, in the near region, a positive constant power is added to a reference power which has a predetermined base power at the lens center O. Therefore, the fourth aspect is, A region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision, In the aforementioned near region, a positive constant power is added to a reference power having a predetermined base power at the lens center O. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a zero frequency deviation, particularly a nearly zero frequency deviation, for the aforementioned positive constant frequency. Sub-region 3 is an ophthalmic lens that produces a negative power deviation relative to the aforementioned positive constant power. Preferably, in sub-region 2, a frequency deviation is considered to be zero if the mean of the frequency deviations in sub-region 2 is in the range of -0.2 to 0.2D. For this reason, a zero frequency deviation can also be considered to be approximately zero. In one example, also in the fourth embodiment, in the far region, the optical power of the lens decreases, particularly continuously, as the radial distance to the lens center O increases. The far region in which the optical power of the lens decreases as the radial distance to the lens center O increases can also be considered a far region that reduces power. In one example, in the far region, the optical power of the lens decreases as the radial distance to the lens center O increases, that is, the far region reduces power in order to at least partially offset the positive longitudinal spherical aberration of the human cornea with negative longitudinal spherical aberration. Thus, in one example, the decrease in optical power in the far region as the radial distance to the lens center increases, i.e., the corresponding power profile, is such that the positive longitudinal spherical aberration of the human cornea is at least partially offset. This enables further improved distance vision. In one example, the power reduction of the aspherical power profile in the near region is equal to the power reduction in the far region. In other words, in one example, in the far region, the optical power decreases as the radial distance to the lens center increases, in line with the decrease in the aspherical power profile of the virtual optical power profile in the near region.

[0029] The fifth aspect is, With respect to the area of ​​the aforementioned nearby region, The area ratio of the aforementioned sub-region 1 is 15-50%. The area ratio of the aforementioned sub-region 2 is 30-70%. The intraocular lens according to any one of the first to fourth embodiments, wherein the area ratio of the sub-region 3 is 15 to 50%.

[0030] The sixth aspect is, The mean of the positive frequency deviation in the sub-region 1 is 0.3 to 1D. The mean value of the near-zero frequency deviation in the sub-region 2 is -0.2 to 0.2D. The intraocular lens according to any one of the first to fifth embodiments, wherein the mean value of the negative frequency deviation in the subregion 3 is -0.3D or less.

[0031] The seventh aspect is, The aforementioned positive constant power is 1 to 4D, and the intraocular lens is as described in any one of the first to sixth embodiments.

[0032] The eighth aspect is, The arrangement of the sub-regions 1 to 3 when viewed radially from the lens center O is one of the following, and this is an intraocular lens according to any one of the first to seven embodiments. ·Sub area 1, sub area 2, sub area 3 ·Sub area 1, sub area 3, sub area 2 ·Sub area 2, sub area 1, sub area 3 ·Sub area 2, sub area 3, sub area 1 ·Sub area 3, sub area 1, sub area 2 ·Sub area 3, sub area 2, sub area 1

[0033] The ninth aspect is, With respect to the area of ​​the aforementioned nearby region, The area ratio of the aforementioned sub-region 1 is 15-50%. The area ratio of the aforementioned sub-region 2 is 30-70%. The ophthalmic lens according to any one of the first to eight embodiments, wherein the area ratio of the sub-region 3 is 15 to 50%.

[0034] The tenth aspect is, The mean of the positive frequency deviation in the sub-region 1 is 0.3 to 1D. The mean value of the near-zero frequency deviation in the sub-region 2 is -0.2 to 0.2D. The ophthalmic lens according to any one of the first to nine embodiments, wherein the mean value of the negative frequency deviation in the sub-region 3 is -0.3D or less.

[0035] The eleventh aspect is, The aforementioned positive constant power is 1 to 4D, and this is an ophthalmic lens according to any one of the 1 to 10 embodiments.

[0036] The twelfth aspect is, The arrangement of the sub-regions 1 to 3 when viewed radially from the lens center O is one of the following, and this is an ophthalmic lens according to any one of the 1 to 11 embodiments. ·Sub area 1, sub area 2, sub area 3 ·Sub area 1, sub area 3, sub area 2 ·Sub area 2, sub area 1, sub area 3 ·Sub area 2, sub area 3, sub area 1 ·Sub area 3, sub area 1, sub area 2 ·Sub area 3, sub area 2, sub area 1

[0037] According to a thirteenth aspect of the present invention, an intraocular lens is provided in which the optical power changes continuously, discontinuously, or with a power jump at least one of the boundaries between two sub-regions of the near region, and the boundary between the near region and the far region when the near region and the far region are adjacent. Therefore, there exist several boundaries, namely, boundaries between different sub-regions of the near region, and at least one boundary between the near region and the far region when the near region and the far region are adjacent, and at least one of these boundaries, the change in frequency is continuous, discontinuous, or a power jump. The power jump is preferably defined as the vertical change in a graph showing the optical power dependent on the radial distance to the lens center O. This vertical change can be defined as ∞D / mm. A change in optical power is preferably considered discontinuous if the change in power is steep, i.e., greater than a predetermined threshold for change in power. Preferably, the predetermined threshold for change in power is 100 D / mm. Therefore, preferably, if the change in power at the boundary is 100 D / mm or more, it is considered steep and therefore discontinuous. A change in power is considered continuous if it is not discontinuous. Therefore, the change in optical frequency at each boundary can also be defined as a) steep, b) a power jump, or c) neither steep nor a power jump. For example, a steep frequency change can also be considered a rapid frequency change. In one embodiment, an intraocular lens according to any one of the first to twelve embodiments is provided, wherein the change in power is smooth or abrupt, or the power jumps, at least one of the boundaries between two different sub-regions, and at the boundary between each of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent. The change in power can be considered smooth if the curve representing the power, which depends on the radial distance to the lens center O, is differentiable. In other words, the curve has no "corners."

[0038] According to a fourteenth aspect of the present invention, an ophthalmic lens is provided in which the optical power changes continuously, discontinuously, or with a power jump at least one of the boundaries between two sub-regions of the near region, and the boundary between the near region and the far region when the near region and the far region are adjacent. Therefore, there exist several boundaries, namely, boundaries between different sub-regions of the near region, and at least one boundary between the near region and the far region when the near region and the far region are adjacent, and at least one of these boundaries, the change in frequency is continuous, discontinuous, or a power jump. As described above, power jump is preferably defined as the vertical change in the graph showing the optical power that depends on the radial distance to the lens center O. This vertical change can be defined as ∞D / mm. As mentioned above, a change in optical frequency is preferably considered discontinuous if the change in frequency is steep, i.e., greater than a predetermined frequency change threshold. Preferably, the predetermined frequency change threshold is 100 D / mm. Therefore, preferably, if the frequency change at the boundary is 100 D / mm or more, it is considered steep and therefore discontinuous. A change in frequency is considered continuous if it is not discontinuous. Therefore, the change in optical frequency at each boundary can also be defined as a) steep, b) a power jump, or c) neither steep nor a power jump. For example, a steep frequency change can also be considered a rapid frequency change. In one embodiment, an ophthalmic lens according to any one of the first to thirteen embodiments is provided, wherein the change in power is smooth or abrupt, or the power jumps, at least at the boundary between two different sub-regions, and at the boundary between the distant region and each of the sub-regions 1 to 3 when the near region and the far region are adjacent. As explained above, the change in power can be considered smooth if the curve representing the power, which depends on the radial distance to the lens center O, is differentiable. In other words, the curve has no "corners."

[0039] The 15th aspect is, The intraocular lens described in any one of the 1 to 14 embodiments has a diameter of 1.2 to 2.5 mm in a planar view of the aforementioned near region. Therefore, the diameter of the adjacent region, i.e., the radial or diametrical expansion of the adjacent region, will be in the range of 1.2 to 2.5 mm.

[0040] The 16th aspect is, An intraocular lens according to any one of the 1 to 15 embodiments, wherein in at least one of the following: the boundary between different sub-regions within the near region; the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent; and the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent, the change in power is continuous or discontinuous, or the power jumps.

[0041] The 17th aspect is, The intraocular lens described in any one of the 1 to 16 embodiments has an inner diameter of 1.4 to 2.2 mm and an outer diameter of 2.6 to 3.5 mm in a planar view of the aforementioned near region. Therefore, the inner diameter of the near-field region, i.e., the radial distance between the inner diameter and the lens center O, can be in the range of 1.4 to 2.2 mm. The outer diameter of the near-field region, i.e., the radial distance between the outer diameter and the lens center O, can be in the range of 2.6 to 3.5 mm.

[0042] The 18th aspect is, The aforementioned ophthalmic lens is a phakic intraocular lens. The aforementioned near region includes the lens center O. The aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O. The ophthalmic lens described in any one of the 1 to 17 embodiments has a diameter of 1.4 to 3 mm in a planar view of the aforementioned near region. Therefore, the diameter of the adjacent region, i.e., the radial or diametrical extension of the adjacent region, can be in the range of 1.4 to 3 mm, particularly 1.4 to 3.0 mm.

[0043] The 19th aspect is, The aforementioned ophthalmic lens is a phakic intraocular lens. The aforementioned far region includes the lens center O. The near region is located outside the far region when the radial direction is taken outward from the lens center O. It is positioned outside the aforementioned near region and includes an outer region that corrects distance vision, The ophthalmic lens described in any one of the 1 to 18 embodiments has an inner diameter of 1.6 to 2.4 mm and an outer diameter of 2.9 to 3.6 mm in a planar view of the aforementioned near region. Therefore, the inner diameter of the near-field region, i.e., the radial distance between the inner diameter and the lens center O, can be in the range of 1.6 to 2.4 mm. The outer diameter of the near-field region, i.e., the radial distance between the outer diameter and the lens center O, can be in the range of 2.9 to 3.6 mm.

[0044] The 20th aspect is, The aforementioned ophthalmic lens is a contact lens. The aforementioned near region includes the lens center O. The aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O. The ophthalmic lens described in any one of the 1 to 19 embodiments has a diameter of 1.4 to 3 mm in a planar view of the aforementioned near region. Therefore, the diameter of the adjacent region, i.e., the radial or diametrical extension of the adjacent region, can be in the range of 1.4–3 mm, particularly 1.4–3.0 mm.

[0045] The 21st aspect is, The aforementioned ophthalmic lens is a contact lens. The aforementioned far region includes the lens center O. The near region is located outside the far region when the radial direction is taken outward from the lens center O. It is positioned outside the aforementioned near region and includes an outer region that corrects distance vision, The ophthalmic lens described in any one of the 1st to 20th embodiments has an inner diameter of 1.6 to 2.4 mm and an outer diameter of 2.9 to 3.6 mm in a planar view of the aforementioned near region. Therefore, the inner diameter of the near region, i.e., the radial distance between the inner diameter and the lens center O, may be in the range of 1.6 to 2.4 mm. The outer diameter of the near region, i.e., the radial distance between the outer diameter and the lens center O, may be in the range of 2.9 to 3.6 mm.

[0046] According to a 22nd aspect of the present invention, an intraocular lens is provided, wherein the intraocular lens is a toric lens, as described in any one of the 1st to 21st aspects. In any preferred embodiment of the above-described configuration, in the first sub-region, the optical power decreases as the radial distance to the lens center O increases. More preferably, the decrease in the first sub-region is concave, i.e., follows a concave curve. In the third sub-region, preferably, the optical power decreases as the radial distance to the lens center O increases. More preferably, the decrease in the third sub-region is convex, i.e., follows a convex curve. It is also preferable that the third sub-region comprises several, particularly two, sub-sub-regions, in each sub-sub-region, the optical power decreases as the radial distance to the lens center O increases. In one example, in each sub-sub-region, the decrease is convex, i.e., follows a convex curve. The preceding paragraph preferably applies to intraocular lenses and / or ophthalmic lenses. Intraocular or ophthalmic lenses having these sub-regions in the near region have been found to lead to a further extension of the depth of focus for near vision. Preferably, a power profile or power curve is considered concave (more specifically, concave in the negative direction of the vertical axis of the power profile) if it curves to the right when moving away from the lens center O along the power profile or power curve (when the vertical axis is power and the horizontal axis is radial distance, the power profile curves clockwise, from 12 o'clock to 3 o'clock on a clock). Preferably, a power profile or power curve is considered convex (more specifically, convex in the negative direction of the vertical axis of the power profile) if it curves to the left when moving away from the lens center O along the power profile or power curve (when the vertical axis is power and the horizontal axis is radial distance, the power profile curves counterclockwise, from 9 o'clock to 6 o'clock on a clock). Hereafter, when the vertical axis represents frequency and the horizontal axis represents radial distance, the definition of irregularities in the frequency profile will be the same as described above.

[0047] According to a 23rd aspect of the present invention, an optical design method for an intraocular lens described in any one of the 1st to 22nd aspects is provided. For example, the optical design method is: The steps include designing an aspherical power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases, A step of designing a near region, by adding a positive constant frequency to the region of the designed aspherical frequency profile, wherein at least a portion of the designed aspherical frequency profile outside the near region forms a far region. A step of modifying the optical power in the near region to design at least three sub-regions, the step of increasing the power in sub-region 1 to design a positive power deviation to the designed aspherical power profile with a positive constant power added; leaving the power unchanged in sub-region 2 to design a zero power deviation to the designed aspherical power profile with a positive constant power added; and decreasing the power in sub-region 3 to design a negative power deviation to the designed aspherical power profile with a positive constant power added. Preferably, the aspherical power profile is designed to produce a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea.

[0048] The 24th aspect is, A method for manufacturing an intraocular lens, wherein the intraocular lens designed by the optical design method for intraocular lenses described in the 23rd aspect is manufactured by at least one of turning, molding, or 3D printing.

[0049] The 25th aspect is, The ophthalmic lens is a toric lens, or an ophthalmic lens according to any one of the 1st to 22th embodiments.

[0050] According to the 26th aspect of the present invention, an optical design method for an ophthalmic lens described in any one of the first to 22 aspects is provided. For example, the optical design method is: - A step of designing an aspherical power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases, - A step of adding a positive constant frequency to the region of the designed aspherical frequency profile in order to design a near region, wherein at least a portion of the designed aspherical frequency profile outside the near region forms a far region. - A step of modifying the optical power in the near region in order to design at least three sub-regions, wherein in sub-region 1, the power is increased to design a positive power deviation to the designed aspherical power profile with a positive constant power added; in sub-region 2, the power is left unchanged to design a zero power deviation to the designed aspherical power profile with a positive constant power added; and in sub-region 3, the power is decreased to design a negative power deviation to the designed aspherical power profile with a positive constant power added. Includes. Preferably, the aspherical power profile is designed to produce a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea.

[0051] The 27th aspect is, A method for manufacturing an ophthalmic lens, wherein an ophthalmic lens designed by the optical design method for ophthalmic lenses described in the 26th aspect is manufactured by at least one of turning, molding, or 3D printing. [Effects of the Invention]

[0052] According to the present invention, compared to the specific examples listed below to which the present invention is not applied (described as "Flat"), the depth of focus for near and / or intermediate vision can be widened, and / or the image quality for far vision can be improved. [Brief explanation of the drawing]

[0053] [Figure 1A]This figure shows a conventional (referred to as "Flat") aspherical EDOF-IOL. [Figure 1B] This figure shows the frequency profile when the vertical axis (unit: D) ​​in Figure 1A is changed to the add frequency. [Figure 2] This figure shows the frequency profile when the vertical axis (unit: D) ​​in Figure 1A is changed to the total frequency. [Figure 3A] This figure shows how light rays from an intermediate distance are focused onto the retina by the cornea and the EDOF shown in Figure 1. [Figure 3B] This figure shows that the range of intermediate distances in which an object can be clearly seen is wider than the range shown in Figure 3A. [Figure 4] This is a diagram of the frequency profile of the 2-zone EDOF (corresponding to Embodiment 1). [Figure 5A] This is a diagram of the frequency profile of the 2-zone EDOF (another example corresponding to Embodiment 1). [Figure 5B] Figure 5A shows the frequency profile when the vertical axis (unit: D) ​​is changed to the add frequency. [Figure 5C] This figure shows the frequency profile of the 2-zone EDOF (another example corresponding to Embodiment 1). [Figure 5D] Figure 5C shows the frequency profile when the vertical axis (unit: D) ​​is changed to the add frequency. [Figure 6A] This figure shows the total power profile of a simulated eye model consisting of the cornea and EDOF, as shown in Figure 5A. [Figure 6B] Figure 5C shows the total power profile of a simulated eye model consisting of the cornea and EDOF. [Figure 7] Here is yet another example of Embodiment 1 of the present invention. [Figure 8A] Figure 1 (Prior Art) and Figure 7 (Embodiment 1) show the TFR corresponding to a pupil diameter of 2 mm at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using EDOF. [Figure 8B] This figure corresponds to Figure 8A, where the pupil diameter is 2.5 mm. [Figure 8C] This figure corresponds to Figure 8A, where the pupil diameter is 3 mm. [Figure 8D] This figure corresponds to Figure 8A, where the pupil diameter is 3.5 mm. [Figure 8E] This figure corresponds to Figure 8A when the pupil diameter is 4 mm. [Figure 9A] This figure corresponds to Figure 8A when the spatial frequency is 100 lp / mm. [Figure 9B] This figure corresponds to Figure 9A, where the pupil diameter is 2.5 mm. [Figure 9C] This figure corresponds to Figure 9A when the pupil diameter is 3 mm. [Figure 9D] This figure corresponds to Figure 9A, where the pupil diameter is 3.5 mm. [Figure 9E] This figure corresponds to Figure 9A when the pupil diameter is 4 mm. [Figure 10] This figure shows the image simulation results for various object distances, assuming a pupil diameter of 2 mm. [Figure 11] This figure corresponds to Figure 10 when the pupil diameter is 3 mm. [Figure 12] This figure corresponds to Figure 10 when the pupil diameter is 4 mm. [Figure 13A] This MTF graph was obtained by simulating a long-distance measurement of 6m with a pupil diameter of 3mm. [Figure 13B] This diagram corresponds to Figure 13A, which represents the case where the distance is 12m. [Figure 13C] This diagram corresponds to Figure 13A, which represents a long distance of 25m. [Figure 14A] This MTF graph was obtained by simulating a long-distance measurement of 6m with a pupil diameter of 4mm. [Figure 14B] This diagram corresponds to Figure 14A, which represents the case where the distance is 12m. [Figure 14C] This diagram corresponds to Figure 14A, which represents a long distance of 25m. [Figure 15] This figure shows the image simulation results for various object distances, assuming a pupil diameter of 2 mm. [Figure 16] This figure corresponds to Figure 15 when the pupil diameter is 3 mm. [Figure 17] This figure corresponds to Figure 15 when the pupil diameter is 4 mm. [Figure 18] This figure shows the image simulation results for various object distances, assuming a pupil diameter of 2 mm. [Figure 19] This figure corresponds to Figure 18 when the pupil diameter is 3 mm. [Figure 20A] This figure shows the power profile of a conventional aspherical EM-IOL. [Figure 20B] This figure corresponds to Figure 20A when the EM-IOL according to the present invention (corresponding to Embodiment 2) is used. [Figure 21A] Figures 20A (Prior Art) and 20B (Embodiment 2) show the TFR corresponding to a pupil diameter of 2.5 mm at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using an IOL. [Figure 21B] This figure corresponds to Figure 21A, where the pupil diameter is 3 mm. [Figure 21C] This figure corresponds to Figure 21A, where the pupil diameter is 3.5 mm. [Figure 22A] This figure corresponds to Figure 21A when the spatial frequency is 100 lp / mm. [Figure 22B] This figure corresponds to Figure 22A, where the pupil diameter is 3 mm. [Figure 22C] This figure corresponds to Figure 22A, where the pupil diameter is 3.5 mm. [Figure 23A] This figure shows the power profile of a conventional multifocal lens. [Figure 23B] This figure corresponds to Figure 23A when the multifocal lens according to the present invention (corresponding to Embodiment 3) is used. [Figure 24A] Figures 23A (Prior Art) and 23B (Embodiment 3) show the TFR corresponding to a pupil diameter of 2.5 mm at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using an IOL. [Figure 24B] This figure corresponds to Figure 24A, where the pupil diameter is 3 mm. [Figure 24C] This figure corresponds to Figure 24A, where the pupil diameter is 3.5 mm. [Figure 25A] This figure corresponds to Figure 24A when the spatial frequency is 100 lp / mm. [Figure 25B] This figure corresponds to Figure 25A, where the pupil diameter is 3 mm. [Figure 25C] This figure corresponds to Figure 25A, where the pupil diameter is 3.5 mm. [Figure 26A] This diagram shows the frequency profile of the conventional 3-zone EDOF technology. [Figure 26B] This figure corresponds to Figure 26A when the present invention uses a 3-zone EDOF (corresponding to Embodiment 1'). [Figure 27A] Figures 26A (Prior Art) and 26B (Embodiment 1') show the TFR for a simulated eye model using an IOL at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2 mm. [Figure 27B] This figure corresponds to Figure 27A, which shows the case where the pupil diameter is 2.5 mm. [Figure 27C] This figure corresponds to Figure 27A, where the pupil diameter is 3 mm. [Figure 27D] This figure corresponds to Figure 27A, which shows the result when the pupil diameter is 3.5 mm. [Figure 27E] This figure corresponds to Figure 27A when the pupil diameter is 4 mm. [Figure 28A] This figure shows the MTF corresponding to a pupil diameter of 2 mm at around 0D (distance for distant viewing). [Figure 28B] This figure corresponds to Figure 28A, which shows the result when the pupil diameter is 2.5 mm. [Figure 28C] This figure corresponds to Figure 28A, where the pupil diameter is 3 mm. [Figure 28D] This figure corresponds to Figure 28A, which shows the result when the pupil diameter is 3.5 mm. [Figure 28E] This figure corresponds to Figure 28A, where the pupil diameter is 4 mm. [Figure 29A] This figure shows the frequency profile of pattern c1. [Figure 29B] This figure shows the frequency profile of pattern c2. [Figure 29C] This figure shows the frequency profile of pattern c3d1. [Figure 29D] This figure combines all the patterns from Figures 29A to 29C into a single figure. [Figure 30A] Figures 29A to 29C show the TFR (Total Frequency Refractometer) for simulated eye models using each IOL (Intraocular Eye) at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2.5 mm. [Figure 30B] This figure corresponds to Figure 30A, where the pupil diameter is 3 mm. [Figure 30C] This figure corresponds to Figure 30A, where the pupil diameter is 3.5 mm. [Figure 31A] This figure shows the frequency profile of pattern b1. [Figure 31B] This figure shows the frequency profile of pattern b2. [Figure 31C] This is a diagram showing the frequency profile of pattern b3. [Figure 31D] This figure combines all the patterns from Figures 31A to 31C into a single diagram. [Figure 32A] Figures 31A to 31C show the TFR (Total Frequency Refractometer) for simulated eye models using each IOL (Intraocular Eye) at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2.5 mm. [Figure 32B] This figure corresponds to Figure 32A, where the pupil diameter is 3 mm. [Figure 32C] This figure corresponds to Figure 32A, where the pupil diameter is 3.5 mm. [Figure 33A] This figure shows the frequency profile of pattern a1c1. [Figure 33B] This figure shows the frequency profile of pattern a1c2. [Figure 33C] This figure shows the frequency profile of pattern a2c1. [Figure 33D]This figure shows the frequency profile of pattern a2c2. [Figure 33E] This figure combines all the patterns from Figures 33A to 33D into a single diagram. [Figure 34A] Figures 33A to 33D show the TFR (Total Frequency Response) for simulated eye models using each IOL (Intraocular Eye) at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2.5 mm. [Figure 34B] This figure corresponds to Figure 34A, where the pupil diameter is 3 mm. [Figure 34C] This figure corresponds to Figure 34A, where the pupil diameter is 3.5 mm. [Figure 35A] This figure shows the power profile of IOLs without power jumps. [Figure 35B] This diagram shows the degree profile of the Power Jump IOL. [Figure 35C] This figure combines all the patterns from Figures 35A to 35B into a single diagram. [Figure 36A] Figures 35A and 35B show the TFR (Total Frequency Refractometer) for simulated eye models using each IOL (Intraocular Eye) at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2.5 mm. [Figure 36B] This figure corresponds to Figure 36A, where the pupil diameter is 3 mm. [Figure 36C] This figure corresponds to Figure 36A, where the pupil diameter is 3.5 mm. [Figure 37A] This figure shows the frequency profile of a conventional Flat device. [Figure 37B] This is a diagram showing the frequency profile of CenterFlat. [Figure 37C] This is a diagram showing the frequency profile of MiddleFlat. [Figure 37D] This is a diagram showing the frequency profile of OuterFlat. [Figure 37E] This figure combines all the patterns from Figures 37A to 37D into a single figure. [Figure 38A]Figures 37A to 37D show the TFR (Total Frequency Response) for simulated eye models using each IOL (Intraocular Eye) at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2.5 mm. [Figure 38B] This figure corresponds to Figure 38A, where the pupil diameter is 3 mm. [Figure 38C] This figure corresponds to Figure 38A, which shows the case where the pupil diameter is 3.5 mm. [Figure 39A] This is a diagram showing the frequency profile of OuterHigher a1c1. [Figure 39B] This figure shows the frequency profile of OuterHigher a2c2. [Figure 39C] This figure combines all the patterns from Figures 39A to 39B into a single diagram. [Figure 40A] Figures 39A and 39B show the TFR (Total Frequency Refractometer) for simulated eye models using each IOL (Intraocular Eye) at a spatial frequency of 50 lp / mm (line pairs / mm) corresponding to a pupil diameter of 2 mm. [Figure 40B] This figure corresponds to Figure 40A, where the pupil diameter is 2.5 mm. [Figure 40C] This figure corresponds to Figure 40A, where the pupil diameter is 3 mm. [Figure 40D] This figure corresponds to Figure 40A, where the pupil diameter is 3.5 mm. [Figure 41A] This figure shows the power profile of a conventional 2-zone type. [Figure 41B] This figure shows the frequency profile of a 2-zone type example corresponding to [Pattern Group 2]. [Figure 42A] This diagram shows the power profile of a conventional 3-zone type. [Figure 42B] This figure shows the frequency profile of a 3-zone type example corresponding to [Pattern Group 2]. [Figure 43] This figure shows many more variations, extending the modified examples of Embodiment 4 to [Aspect Group 2]. [Modes for carrying out the invention]

[0054] For configurations not described below, publicly known configurations may be adopted as appropriate. In particular, the contents described in the document disclosed by the inventor (WO2009 / 153873) (especially the support part) may be applied to this embodiment. Furthermore, in this specification, "~" refers to a value greater than or equal to a predetermined value and less than or equal to a predetermined value. In particular, expressions such as "A~B" represent a range from A to B. Furthermore, the lens body of the intraocular lens discussed herein has two opposing surfaces. When the intraocular lens is inserted into the crystalline capsule, the surface of the lens body that contacts the posterior capsule can be referred to as the posterior surface, the retinal surface, or the retinal surface in the optical axis direction, but in this specification, "posterior surface" will be used primarily. The other surface can be referred to as the anterior surface, the corneal surface, or the corneal surface in the optical axis direction, but in this specification, "anterior surface" will be used primarily. The optical axis direction is also the lens thickness direction, and is the direction from the posterior surface to the anterior surface or vice versa. The optical axis direction is defined as the z-axis direction. When the intraocular lens is viewed in the z-axis direction, it is referred to as a "planar view," and unless otherwise specified, this planar view will be described.

[0055] The outline of this embodiment is as follows: This embodiment primarily illustrates a two-zone EDOF (Embodiment 1). In this specification, "two zones" refers to a region that provides the lens function necessary to achieve the wearer's prescription, consisting of one region (zone) that corrects near vision and includes the lens center O, and another region (zone) that corrects far vision. Furthermore, a two-zone EM-IOL is also exemplified, similar to this two-zone EDOF (Embodiment 2). Furthermore, a two-zone multifocal lens, similar to this two-zone EDOF, is also exemplified (Embodiment 3). In addition to the two-zone EDOF, a three-zone EDOF is also exemplified (Embodiment 1'). The three-zone EDOF is composed of one region (zone) that corrects distance vision and includes the lens center O, one region (zone) that corrects near vision, and one further outer region (zone) that corrects distance vision. Although not illustrated herein, a 3-zone EM-IOL (Embodiment 2') and a 3-zone multifocal lens (Embodiment 3') are also included in the technical scope of the present invention. Furthermore, various modifications concerning the behavior of the power profile in the near region for correcting near vision are also illustrated (Embodiment 4). The invention relating to an intraocular lens, including the embodiments described above, is [Aspect Group 1] in this specification.

[0056] Unlike [Aspect Group 1], [Aspect Group 2] exemplifies phakic intraocular lenses or implantable contact lenses, rather than general intraocular lenses.

[0057] The common elements of each embodiment are explained at the beginning as [Common Embodiments].

[0058] The first aspect of the present invention in [Means for Solving the Problems of the Present Invention] corresponds to [Aspect Group 1]. The second aspect of the present invention in [Means for Solving the Problems of the Present Invention] corresponds to Embodiments 1 to 3 in [Aspect Group 1]. The third aspect of the present invention in [Means for Solving the Problems of the Present Invention] corresponds to embodiments 1' to 3' in [Aspect Group 1]. The fourth aspect of the present invention in [Means for Solving the Problems of the Present Invention] corresponds to [Aspect Group 2]. Although the fourth aspect is worded to include not only [Aspect Group 2] but also [Aspect Group 1], the fourth aspect in this specification mainly refers to [Aspect Group 2].

[0059] [Common Embodiments] The common features and inventive concepts of the embodiments from Embodiment 1 onward will be described as common embodiments. Here, an intraocular lens belonging to [Aspect Group 1] will be given as an example.

[0060] The intraocular lens according to the common embodiment (and other embodiments described herein) comprises, like the intraocular lenses of the prior art ("Flat" in the specific examples below, hereafter the same), a lens body having a lens function and a support portion that supports the lens body within the lens capsule.

[0061] In common embodiments, the intraocular lens is defined by its refractive power (power, degree) with respect to the distance radially away from the lens center O. In this specification, the "direction radially away from the lens center O" is defined as "outer."

[0062] The material of the intraocular lens is not limited and may consist of at least one of the following: silicone, hydrophobic acrylic resin, hydrophilic acrylic resin, hydrogel, PMMA, and a copolymer of PMMA, or a copolymer of HEMA (hydroxyethyl methacrylate) (e.g., Collamer®) containing collagen.

[0063] In the common embodiment (and other embodiments described herein), the entire lens body is an optical part that provides the lens function. The "lens function" referred to here is the lens function described above in the outline of this embodiment, which refers to the function of refracting the incident light beam onto the retina.

[0064] Embodiments 1 to 3 in Embodiment Group 1 exemplify a case where the entire lens body consists of one distance region that corrects distance vision and one near region that corrects near vision. However, the present invention is not limited to this example. For example, it may be a three-zone intraocular lens as in Embodiments 1' to 3' shown below. Furthermore, an intermediate region may be provided between the distance region and the near region, surrounding the lateral region (distance region or near region) closer to the center of the lens, or an additional region may be provided radially outward surrounding the distance region or near region. In addition, two or more distance regions and / or two or more near regions may be provided. However, the change in power may be continuous or discontinuous, or the power may jump, between each region and / or between the sub-regions shown below.

[0065] "Discontinuous change in frequency" means, as the name suggests, in a graph of the type shown in Figure 2, that in addition to the actual discontinuity of the change in frequency when moving away from the lens center O, when the graph is expressed as a function, the change in frequency when moving away from the lens center O is continuous but steep, and the change in frequency is effectively discontinuous. Conversely, "continuous change in frequency" refers to a state that does not fall under "discontinuous change in frequency".

[0066] To determine whether a change is "steep," for example, a change of 100 D / mm or more is considered steep. In other words, even if the power increases discontinuously for every 0.01 mm away from a predetermined distance from the lens center O, a change of 100 D / mm or more is considered steep if it occurs within 0.05 mm from that point. A "power jump in power" refers, as the name suggests, to a state where the change in power exceeds steepness (on the power profile, the change in power is vertical and the change in power is ∞ D / mm).

[0067] In a plan view, the inner region (near region in Embodiments 1-3) containing the lens center O is circular, and the outer region (far region in Embodiments 1-3) surrounding the near region is annular. In Embodiments 1'-3', the circular region containing the lens center O becomes the far region, and the annular region surrounding the far region becomes the near region. In other embodiments described herein, the intermediate region is a small annular, and the additional region is a large annular. Note that instead of a circular and / or annular shape, an elliptical and / or elliptic annular shape may be used.

[0068] Figure 1A shows a power profile for a specific example described herein to which the present invention does not apply (described as "Flat," and hereafter simply referred to as "Flat"), with the horizontal axis (unit: mm) representing the position viewed radially from the lens center O, and the vertical axis (unit: D) ​​representing the power. Hereafter, unless otherwise specified, this type of power profile will be discussed. The specific straight lines and / or curves on the power profile are also called graphs. Figure 1B shows the frequency profile when the vertical axis (unit: D) ​​in Figure 1A is changed to the add frequency. Figure 2 shows the frequency profile when the vertical axis (unit: D) ​​in Figure 1A is changed to the total frequency.

[0069] The distance from the lens center O is also called the radius. The solid line represents the power profile of the intraocular lens according to the common embodiment (and other embodiments described herein). The dashed line represents the power profile of a virtual aspherical lens that has a base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. This is a virtual optical power profile. This power profile is also called the aspherical reference power profile W. The aspherical reference power profile is also simply called the aspherical power profile.

[0070] The cornea possesses positive refractive power. Furthermore, spherical aberration increases with distance from the center of the cornea. In other words, the dashed line representing the aspherical reference power profile W is a graph of a hypothetical aspherical lens that theoretically cancels out all of the positive longitudinal spherical aberration (axial aberration in the depth direction of the optical axis) caused by the cornea. From now on, the meaning of each line will be the same.

[0071] An aspherical optical design IOL (aspherical IOL) with an aspherical reference power profile W is designed to correct or reduce all or part of the spherical aberration of the cornea. The degree to which the spherical aberration of the cornea is reduced varies depending on the IOL of each company. Each company's IOL is designed to reduce the spherical aberration of the cornea by a specific amount (value). In the optical design of the aspherical IOL, a corneal model with the same spherical aberration value as the specific amount of spherical aberration to be reduced is predetermined, and the specific amount of spherical aberration to be reduced by the aspherical IOL is determined by selecting the optical parameters of the corneal model. During the optical design process, the total spherical aberration of the optical system (optical system) consisting of the predetermined corneal model and the designed aspherical IOL is zero (i.e., no spherical aberration exists).

[0072] The spherical aberration value of a given corneal model is determined as follows: Assume that the spherical aberration value of the given corneal model used in the optical design of the aspherical IOL is the same as the mean value of spherical aberration for a population of eye patients wearing IOLs. Alternatively, determine the spherical aberration value of a given corneal model by setting it to a spherical aberration value that partially reduces the corneal spherical aberration of the population of eye patients.

[0073] The aspherical reference frequency profile W is the frequency distribution of aspherical IOLs. This frequency distribution has the characteristic of being able to completely or partially reduce the spherical aberration of the mean cornea (statistical corneal optical parameters) of a population of aphakia patients. In this specification, the spherical aberration value of a given corneal model is assumed to be 0.27 μm. The dashed line in Figure 1A is also an example of the frequency distribution of aspherical IOLs that can completely reduce the spherical aberration of a corneal model with a spherical aberration value of 0.27 μm. 0.27 μm may also be expressed as +0.27 μm. Furthermore, the present invention is not strictly limited to 0.27 μm, and may be a value in the range of, for example, +0.24 to +0.30 μm.

[0074] In the near region as described herein, visual acuity is corrected when viewing objects at one intermediate distance or one near distance. The near region comprises a power obtained by adding a single positive constant power to a predetermined radial range of aspherical reference power in a virtual aspherical lens that has a base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. This "single positive constant power" corresponds to the add power described herein up to this point.

[0075] In this specification, the aspheric base power profile W is also referred to as the Reference Base Power Profile (RBPP). The aspheric base power profile W with added power is also referred to as the Reference Addition Power Profile (RAPP).

[0076] As shown in Figure 1A, the frequency graph in the near region with a fixed positive frequency added has a shape obtained by shifting the aspherical reference frequency graph upward by that fixed frequency. Before the existence of the sub-regions 1 to 3 described later, it is preferable that the frequency decreases continuously in the radial direction in the frequency graph in the near region with a fixed positive frequency added.

[0077] The aforementioned positive constant degree may be 1 to 4D (especially 1.0 to 4.0D).

[0078] In each embodiment group, a single positive constant power is added, and then in a predetermined radial range within the near region (sub-region 1 shown later), an additional power is added on top of the initial added power. In other words, even though "a single positive constant power is added," the final intraocular lens (or ophthalmic lens) in this specification does not have "a single" positive constant power added.

[0079] [Aspect Group 1] The following describes [Aspect Group 1]. First, the concept of the present invention will be explained using Embodiment 1 (Figure 4 shown later). For details not described in Embodiment 2 and later, refer to the description in Embodiment 1.

[0080] <Embodiment 1> In Embodiment 1, the near region including the lens center O comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a nearly zero frequency deviation for the aforementioned positive constant frequency. Subregion 3 results in a negative frequency deviation with respect to the aforementioned positive constant frequency.

[0081] In other words, the concept of the present invention, as shown in Figure 4, divides a near-field region to which a single positive constant power has been added into multiple regions radially. This division is carried out separately for "a state in which further power has been added (a in Figure 4)", "a state in which power has been reduced (c and d in Figure 4)", and "a state in which there is almost no change (b in Figure 4)". As a result, as shown in the specific examples below, the depth of focus for near and / or intermediate vision can be widened, and / or the image quality for far vision can be improved. The mechanism will be described later.

[0082] The "state where the frequency is further increased (a in Figure 4)" in sub-region 1 is a state in which a positive frequency deviation is produced relative to a constant positive frequency. As a specific example, the average value of the positive frequency deviation in sub-region 1 is 0.3 to 1D (especially 0.3 to 1.0D). This average value is the average value obtained by subtracting the constant positive frequency from the frequency in sub-region 1 within sub-region 1 (for example, the average value of the difference values ​​for each measurement point or each radial position). Hereafter, unless otherwise specified, the average value of the frequency deviation will be the value obtained in the same manner.

[0083] In sub-region 2, the "almost or no change (b in Figure 4)" is referred to as "resulting in a nearly zero frequency deviation" because it includes the "slightly changing state" (it cannot produce something that is absent, but it can produce something that is present). As a specific example, the average value of the nearly zero frequency deviation in sub-region 2 is -0.2 to 0.2D. This average value is the average value obtained by subtracting the positive constant frequency from the frequency in sub-region 2, within sub-region 2 (for example, the average value of the difference values ​​for each measurement point or each radial position). In English, it is written as ZAPD (Zero Addition Power Deviation), omitting the "abbreviated," but the meaning remains the same as above.

[0084] In sub-region 3, the "state where the frequency is reduced in the opposite direction (c and d in Figure 4)" is a state in which a negative frequency deviation is produced relative to a constant positive frequency. As a specific example, the average value of the negative frequency deviation in sub-region 3 is -0.3D or less. This average value is the average value (also a negative value, for example, the average of the difference values ​​for each measurement point or each radial position) obtained by subtracting the constant positive frequency from the frequency in sub-region 3. As shown in c and d in Figure 4, sub-region 3 may be divided into multiple regions in which the shape of the frequency profile in the radial direction is different from each other. The frequency may be reduced in multiple steps in the radial direction. Similarly, sub-regions 1 and 2 may also be divided into multiple regions in which the shape of the frequency profile in the radial direction is different from each other.

[0085] Furthermore, the near region may also have sub-regions separate from sub-regions 1-3. For example, sub-regions 1, 2, and 3 may be arranged in order from the side closest to the lens center O, and a separate sub-region 4 (a region with the same function as sub-region 2) that provides a nearly zero degree deviation may be provided outside of sub-region 3. In this way, it is not excluded to divide regions with the same function and arrange them separately as different sub-regions. Also, sub-regions 1-3 are not limited to being physically touching each other. For example, sub-regions 2 and 1 may be arranged in order from the side closest to the lens center O, followed by sub-region 4, and then sub-region 3 may be placed outside of it. Thus, the expression "having at least three sub-regions arranged radially" encompasses both cases where sub-regions 1, 2, and 3 are physically touching each other and cases where they are not.

[0086] There are no restrictions on the order in which sub-regions 1 to 3 are arranged when viewed radially from the lens center O (in Figure 4, they are shown in the order of sub-regions 1, 2, and 3). For example, the arrangement of sub-regions 1 to 3 when viewed radially from the lens center O may be any of the following: ·Sub area 1, sub area 2, sub area 3 ·Sub area 1, sub area 3, sub area 2 ·Sub area 2, sub area 1, sub area 3 ·Sub area 2, sub area 3, sub area 1 ·Sub area 3, sub area 1, sub area 2 ·Sub area 3, sub area 2, sub area 1 In this specification, the positive frequency deviation resulting from subregion 1 is also referred to as PAPD (Positive Addition Power Deviation), the near-zero frequency deviation resulting from subregion 2 is also referred to as ZAPD (Zero Addition Power Deviation), and the negative frequency deviation resulting from subregion 3 is also referred to as NAPD (Negative Addition Power Deviation).

[0087] In a plan view, the shapes of sub-regions 1-3 are, due to their arrangement in the radial direction, at least the middle sub-region and the outermost sub-region are annular when viewed radially from the lens center O. If the near region includes the lens center O, the innermost sub-region is circular, and if the near region does not include the lens center O, the innermost sub-region is also annular. Here, "annular" can be rephrased as "ring band."

[0088] With respect to the area of ​​the aforementioned nearby region, The area ratio of the aforementioned sub-region 1 is 15-50%. The area ratio of the aforementioned sub-region 2 is 30-70%. The area ratio of the sub-region 3 is preferably 15-50%. At least within this range, it has been demonstrated that the depth of focus for near and / or intermediate vision can be widened and / or the image quality for far vision can be improved, as shown in the specific examples below.

[0089] Furthermore, the lower limit of (ratio of the area of ​​sub-region 1) / (ratio of the area of ​​sub-region 3) may be 0.33 or 0.4. The upper limit may be 3.3, 3.0, 2.5, 2.0, 1.5, or 1.3.

[0090] Within the aforementioned near region, at least one of the boundaries between different sub-regions, and at the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, the change in frequency may be continuous or discontinuous, or the frequency may undergo a power jump. This modification is common to Embodiments 1 and 2 and [Aspect Group 2].

[0091] Variations of the sub-region will be described in detail in Embodiment 4 below.

[0092] In Embodiment 1 (more specifically, [Aspect Group 1]), the power is reduced in the distance region so that negative longitudinal spherical aberration is present, which at least partially cancels out the positive longitudinal spherical aberration caused by the cornea. Specifically, the power is reduced as you move away from the lens center O so that at least a portion (preferably 70% or more, more preferably all) of the positive longitudinal spherical aberration caused by the positive refractive power of the cornea is canceled out. A concrete example of complete cancellation is a power equal to the aspheric reference power (RBPP) in a virtual aspheric lens. In other words, in the distance region, the power may be equal to the RBPP.

[0093] "Equal to the aspheric reference power" means that at a predetermined distance from the lens center O, the deviation from the aspheric reference power is less than ±0.30D (preferably less than ±0.15D). The definition of "equal" for power in this specification is the same as the definition in this paragraph. This "equal" is also referred to as "identical or similar". Alternatively, "equal to the aspheric reference power" may be considered as "a power in which the average value of the power deviation relative to the aspheric reference power is -0.2 to 0.2D".

[0094] In addition, "a power obtained by adding a single positive constant power to the aspherical reference power" indicates that, at a predetermined distance from the lens center O, the deviation from the graph obtained by adding a single positive constant power to the aspherical reference power is less than ±0.30D (preferably less than ±0.15D). Alternatively, "a power obtained by adding a single positive constant power to the aspherical reference power" may be considered as "a power in which the average value of the power deviation for a power obtained by adding a single positive constant power to the aspherical reference power is -0.2 to 0.2D."

[0095] The above describes the contents of the first embodiment. Figures 4 to 19 correspond to the first embodiment. In the first sub-region, i.e., the region of positive additional frequency deviation, the optical frequency can decrease. Furthermore, in the first sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be concave, as illustrated in Figures 5A, 5B, 5C, 6A, and 7. In the third sub-region, i.e., the negative additional power deviation region, the optical power can decrease. Furthermore, in the third sub-region, the dependence of the optical power on radial distance, i.e., the corresponding curve or function, can be convex, as illustrated in Figures 5A, 5B, and 6A. The third sub-region can also be further divided into sub-sub-regions (ca, cb, in order from the lens center O) (signs omitted in subsequent figures), such as the two sub-sub-sub-regions of the third sub-region illustrated in Figure 7. In each of these sub-sub-regions illustrated in Figure 7, the optical power can decrease. Each curve in each sub-sub-region can have its own convex curve or function, as also illustrated in Figure 7.

[0096] <Embodiment 2> Embodiment 2 is a two-zone EM-IOL in which the near region includes the lens center O. Figures 20 to 22 correspond to Embodiment 2. In this embodiment as well, the optical frequency can decrease in the first sub-region, i.e., the positive additional frequency deviation region. Furthermore, in the first sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be concave, as illustrated in Figure 20B. In the third sub-region, i.e., the negative additional frequency deviation region, the optical frequency can decrease. Furthermore, in the third sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be convex. The third sub-region can also be further divided into sub-sub-regions, such as the two sub-sub-regions of the third sub-region shown exemplarily in Figure 20B. In each of these sub-sub-regions shown exemplarily in Figure 20B, the optical frequency can decrease. Each curve in each sub-sub-region can have its own convex curve or function, as also exemplarily shown in Figure 20B.

[0097] <Embodiment 3> Embodiment 3 is a two-zone multifocal lens in which the near region includes the lens center O. Figures 23 to 25 correspond to Embodiment 3. In this embodiment as well, the optical frequency can decrease in the first sub-region, i.e., the positive additional frequency deviation region. Furthermore, in the first sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be concave, as illustrated in Figure 23B. In the third sub-region, i.e., the negative additional frequency deviation region, the optical frequency can decrease. Furthermore, in the third sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be convex. The third sub-region can also be further divided into sub-sub-regions, such as the two sub-sub-sub-regions of the third sub-region shown exemplarily in Figure 23B. In each of these sub-sub-regions shown exemplarily in Figure 23B, the optical frequency can decrease. Each curve in each sub-sub-region can have its own convex curve or function, as also exemplarily shown in Figure 23B.

[0098] In embodiments 1 to 3, the diameter of the near region in plan view may be 1.2 to 2.5 mm. At least within this range, it has been demonstrated that the depth of focus for near and / or intermediate vision can be widened and / or the image quality for far vision can be improved, as shown in the specific examples below.

[0099] <Embodiment 1'~3'> Embodiment 1' is a 3-zone EDOF. Figures 26 to 28 correspond to Embodiment 1'. Embodiments 1', 2' (3-zone EM-IOL, not shown), and 3' (3-zone multifocal lens, not shown) have a distance region concentric with the lens center O and including the lens center O, a near region positioned outside the distance region when the radial direction from the lens center O is considered outward, and an outer region positioned outside the near region and correcting distance vision. In the outer region, similar to the distance region of Embodiments 1 to 3, the power is reduced so that there is negative longitudinal spherical aberration that at least partially cancels out the positive longitudinal spherical aberration caused by the cornea.

[0100] In embodiments 1' to 3', at least one of the following may be a continuous or discontinuous change in frequency, or the frequency may undergo a power jump: the boundary between different sub-regions within the near region, the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, and the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent.

[0101] The inner diameter in the near region in plan view is 1.4 to 2.2 mm, and the outer diameter may be 2.6 to 3.5 mm. At least within this range, it has been demonstrated that the depth of focus for near and / or intermediate vision can be widened, and / or the image quality for far vision can be improved, as shown in the specific examples below. In these embodiments as well, the optical frequency can decrease in the first sub-region, i.e., the positive additional frequency deviation region. Furthermore, in the first sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be concave, as illustrated in Figure 26B. In the third sub-region, i.e., the negative additional frequency deviation region, the optical frequency can decrease. Furthermore, in the third sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be convex. The third sub-region can also be further divided into sub-sub-regions, such as the two sub-sub-regions of the third sub-region shown exemplarily in Figure 26B. In each of these sub-sub-regions shown exemplarily in Figure 26B, the optical frequency can decrease. Each curve in each sub-sub-region can have its own convex curve or function, as also exemplarily shown in Figure 26B.

[0102] <Embodiment 4> Embodiment 4 shows a variation of the sub-region. Figures 29 to 40 correspond to Embodiment 4. In this embodiment as well, the optical frequency can decrease in the first sub-region, i.e., the positive additional frequency deviation region. Furthermore, in the first sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be concave, as illustrated in Figures 29A, 29B, 29C, 29D, 31A, 31B, 31C, 31D, 33A, 33B, 35A, 35B, 35C, 37B, 37C, 37D, and 37E. The curve or function in the first sub-region can also increase, as illustrated in Figures 37D and 37E. In the third sub-region, i.e., the negative additional frequency deviation region, the optical frequency can decrease. Furthermore, in the third sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be convex, as exemplified in Figures 29A, 29B, 29D, 31A, 31B, 31C, 31D, 33A, 33C, 35A, 35B, 37B, 37C, 37D, and 37E. The curve or function in the third sub-region may also be concave, as exemplified in Figures 33B and 33D. The curve or function in the third sub-region can also increase, as exemplified in Figures 37D and 37E. The third sub-region can be further divided into sub-sub-regions, such as the two sub-sub-regions of the third sub-region shown exemplarily in Figures 29C and 29D (pattern c3d1). In each of these sub-sub-regions, shown exemplarily in Figures 29C and 29D (pattern c3d1), the optical intensity can decrease. Each curve in each sub-sub-region can have its own convex curve or function, as also exemplarily in Figures 29C and 29D (pattern c3d1). Each of these sub-sub-regions can also have its own convex curve or function, as also exemplarily in Figures 29C and 29D (pattern c3d1).

[0103] The intraocular lens in [Aspect Group 1] may be a toric lens.

[0104] [Pattern Group 2] [Aspect Group 2] mainly exemplifies phakic intraocular lenses or implantable (or non-implantable) contact lenses. However, [Aspect Group 2] is also applicable to general intraocular lenses. With phakic intraocular lenses or contact lenses, visual acuity is less affected by corneal spherical aberration. Therefore, it is not necessary to adopt an aspheric reference power profile W. As shown in Figure 41A of the EDOF of a two-zone design in a phakic intraocular lens or contact lens, the power in the near region and the power in the far region may be kept constant before applying the present invention ("Flat"). Then, as shown in Figure 41B, the present invention may be applied.

[0105] Of course, in [Aspect Group 2] as described in [Aspect Group 1], it is also acceptable to adopt "an aspheric reference power within a predetermined radial range in a virtual aspheric lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea."

[0106] In this specification (particularly in the fourth aspect of the present invention in [Means for Solving the Problems of the Invention]), the expression "reference power having a predetermined base power at the lens center O" is used as a combined expression of both (the two paragraphs above).

[0107] Figures 42A and 42B relate to EDOF (End-of-Day Focus) with a 3-zone design in phakic intraocular lenses or contact lenses. Figure 43 shows many more variations, extending the modified form of Embodiment 4 to [Aspect Group 2]. In this group of embodiments, too, the optical frequency can decrease in the first sub-region, i.e., the positive additional frequency deviation region. Furthermore, in the first sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be concave, as illustrated in Figures 41B, 42B, and 43. The curve or function in the first sub-region can also increase. In the third sub-region, i.e., the negative additional frequency deviation region, the optical frequency can decrease. Furthermore, in the third sub-region, the dependence of the optical frequency on radial distance, i.e., the corresponding curve or function, can be convex, as illustrated in Figures 41B, 42B, and 43. The curve or function in the third sub-region may also be concave. The curve or function in the third sub-region can also increase. The third subregion (NAPD) can be further divided into sub-subregions, as illustrated in Figure 43. In each of these sub-subregions illustrated in Figure 43, the optical intensity can decrease. Each of these sub-subregions may also have its own convex or concave curve or function, as shown in some examples in Figure 43. Furthermore, the first sub-region (NAPD) may include sub-sub-regions having concave and / or convex curves, for example, as also illustrated in Figure 43.

[0108] The aforementioned ophthalmic lens is either a phakic intraocular lens or a contact lens. If the aforementioned near region includes the lens center O, When the aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O, The diameter of the aforementioned near region in a plan view may be 1.4 to 3 mm.

[0109] The aforementioned ophthalmic lens is either a phakic intraocular lens or a contact lens. If the aforementioned far region includes the lens center O, The near region is located outside the far region when the radial direction is taken outward from the lens center O. It is positioned outside the aforementioned near region and includes an outer region that corrects distance vision, The inner diameter in the aforementioned near region, viewed from the plan, may be 1.6 to 2.4 mm, and the outer diameter may be 2.9 to 3.6 mm.

[0110] The aforementioned ophthalmic lens may be a toric lens.

[0111] Each example (preferred example, modified example) described in Group 1 of Embodiments may also be applied to Group 2 of Embodiments.

[0112] Furthermore, while each embodiment group uses intraocular lenses (or ophthalmic lenses) as examples, the technical concept of the present invention is also applicable to optical design methods for designing intraocular lenses (or ophthalmic lenses). The technical concept of the present invention is also applicable to manufacturing methods for intraocular lenses (or ophthalmic lenses), which involve manufacturing the intraocular lenses (or ophthalmic lenses) designed by the intraocular lens (or ophthalmic lens) design method by at least one of turning, molding, or 3D printing.

[0113] The following describes the details of the present invention, including its mechanism. Hereafter, the term "IOL of the present invention" will be used, but the following description is not intended to limit the present invention. Rather, the term "IOL of the present invention" is used in a broad sense that reflects the concept of the present invention (naturally encompassing the above-mentioned group of embodiments).

[0114] [Further details of the invention] Improvements to bifocal type EVR IOLs are described herein. A two-zone optical design is given as an example to illustrate the optical design or power profile according to the present invention.

[0115] The present invention is applicable to the optical design of EM-IOLs, EDOFs, and multifocal lenses because the optical principles of these three types of IOLs are identical. This optical principle involves these IOLs having a base power for correcting distance vision and near and / or intermediate powers for correcting near and / or intermediate vision. As described in [Aspect Group 1], the EDOF IOL is given as a primary example herein.

[0116] Figure 1A shows a conventional (as "Flat" in this specification) aspherical EDOF-IOL with a base power of 20.0D and an add power of 2.25D. Hereafter, unless otherwise specified, the frequency distribution graphs will have the horizontal axis as radius and the vertical axis as frequency. This IOL has two regions. The first region is the medial region (or central region), and the second region is the lateral region. The second region has a base power for correcting distance visual acuity. The medial first region has a power 2.25D greater than the base power for correcting intermediate visual acuity.

[0117] Figure 1B shows the frequency profile shown in Figure 1A converted into an add frequency graph (a graph with radius on the horizontal axis and add frequency on the vertical axis). The optical design of the EVR IOL shown in Figure 1 is well known as a two-zone optical design. The two-zone IOL shown in Figure 1 has pure bifocal characteristics.

[0118] The dashed line graph in Figure 1 shows the power profile for the base power of this IOL. This base power profile decreases from a power value of 20.0D at a radius of 0mm (radius from the lens center O) to approximately 16.4D at a radius of 3mm. This base power profile can be designed to fully compensate for or partially reduce the average corneal spherical aberration of a cataract patient. The average corneal spherical aberration is approximately 0.27 μm. The example base power profile shown in Figure 1 is designed to correct the average corneal spherical aberration of 0.27 μm in a cataract patient. In other words, this base power profile is the aspherical reference power profile W described above.

[0119] By correcting or reducing corneal spherical aberration, the image quality of the distance image reconstructed on the retina can be improved. In this specification, the base power profile is referred to as the reference base power profile (RBPP, previously mentioned herein).

[0120] This IOL has a power value of 22.25D at a radius of 0mm (radius of the lens center), and the power decreases as the radius increases up to a radius of 0.9mm. The power profile from a radius of 0mm to 0.9mm is the power profile for the near-vision range of this IOL.

[0121] This frequency profile in the near region is referred to herein as the reference near frequency profile. This reference near frequency profile is synonymous with the reference add frequency profile (RAPP) described later. The reference near frequency profile has a frequency profile (frequency graph shape) that is relatively similar to that of the RBPP. However, the frequency values ​​at a particular radius are approximately 2.25D (the value of the IOL design add frequency shown in Figure 1) greater than the frequency values ​​of the RBPP at that particular radius.

[0122] The add frequency in Figure 1B is the value obtained by subtracting the RBPP from the design frequency profile of the EVR IOL. In other words, the add frequency profile is the difference between the design frequency profiles of the EVR IOL and the RBPP.

[0123] Figure 2 shows the total power profile of the simulated eye model consisting of the cornea and EDOF IOL shown in Figure 1. The parameters of the simulated eye model are shown in Table 1. [Table 1] The anterior surface of the cornea refers to the front surface of the cornea. The posterior surface of the cornea refers to the back surface of the cornea. Aperture refers to an opening (corresponding to the pupil diameter of the eye, but not necessarily an opening where no substance exists; this table lists the refractive index corresponding to the substance present in the opening). The anterior surface of an intraocular lens refers to the front surface of the IOL. The posterior surface of the lens refers to the rear surface of the IOL (intraocular lens). Note 1) Aspherical or aspherical curvature. The radius of curvature at the lens center of the various IOLs described herein is approximately 17.2 mm. Note 2) The interplanar spacing of the various IOLs described herein is approximately 0.7 mm. Note 3) The interplanar spacing of the various IOLs described herein is approximately 18.8 mm.

[0124] As shown in Figure 2, the total power profile exhibits pure bifocal characteristics. The total corneal power and the base power of the EDOF are approximately 59.0D, and the total corneal power and the add power of the EDOF are approximately 60.7D. The difference between the add power of the EDOF (60.7D) and the base power of the EDOF (59.0D) is 1.7D at the corneal surface. The value of 1.7D at the corneal surface corresponds to a viewing distance of 59cm. The value of 59cm (=0.59m) is obtained by dividing 1.000 (this value is the refractive index of air) by the difference power of 1.7D (D (diopter) is in units of (1 / m)).

[0125] Figure 3A shows how light rays from an intermediate distance are focused onto the retina by the cornea and the EDOF shown in Figure 1. Light rays from a distance of 59 cm in front of the cornea are also focused onto the retina by the cornea and the EDOF shown in Figure 1. Near objects located approximately 59 cm in front of the cornea are clearly visible because the light rays from that vicinity are focused onto the retina. However, objects in the near region that are not in the vicinity of this approximately 59 cm distance are not clearly visible and appear blurred.

[0126] The range of near distances in which objects in the near field can be clearly seen is influenced by the power difference between the constant add power profile and the reference base power in this IOL. The EDOF shown in Figure 1 narrows the depth of focus for intermediate vision. Figure 3B shows a wider depth of focus in intermediate vision. In Figure 3B, the range of intermediate distances in which objects can be clearly seen is wider than in Figure 3A.

[0127] In this specification, an add frequency profile that is greater than the RBPP value by the value of the IOL's add frequency (for example, greater than an add frequency of approximately 2.25D) is referred to as the reference add frequency profile (RAPP). Reference add frequency profiles are shown by dotted lines in Figures 4, 5A, and 5C.

[0128] Figure 4 shows the power profile of a 2-zone EDOF with a base power of 20.0D and an add power of 2.25D (corresponding to Embodiment 1). This IOL comprises an inner region at the center of the lens for correcting intermediate vision and an outer region surrounding the inner region for correcting distance vision.

[0129] The inner region contains four subregions. Sub-region a (corresponding to sub-region 1 in [Aspect Group 1]) contains frequency profile segments whose frequency values ​​are greater than RAPP. Sub-region b (corresponding to sub-region 2 in [Aspect Group 1]) contains frequency profile segments whose frequency values ​​are identical or similar to the frequency values ​​of RAPP (it is also acceptable to refer to "identical or similar" with respect to frequency values ​​as "equal," and the definition of "equal" has already been given). Sub-region c (corresponding to sub-region 3 in [Aspect Group 1]) contains frequency profile segments whose frequency values ​​are lower than those of RAPP. Sub-region d (corresponding to sub-region 3 in [Aspect Group 1] (however, a different sub-region 3 from the above sub-region 3)) also contains frequency profile segments whose frequency values ​​are lower than those of RAPP and which are different from those of sub-region c. The power values ​​of the lateral region power profile are identical or similar to those of the RBPP power profile. The lateral region power profile can be designed to fully compensate for or partially reduce the average corneal spherical aberration of a cataract patient's eye.

[0130] The frequency profile shown in Figure 4 can be represented by five polynomials. Each of the four subdomains in the inner region and RAPP can be represented by a single polynomial.

[0131] In the following description, as illustrated in FIG. 5A, a sub-region having a frequency value greater than the RAPP value is referred to as a sub-region that brings about a positive joining frequency deviation (PAPD), a sub-region having a frequency value identical to or similar to the RAPP value is referred to as a sub-region having a zero joining frequency deviation (ZAPD), and a sub-region having a frequency value lower than the RAPP value is referred to as a sub-region having a negative joining frequency deviation (NAPD). The NAPD is a negative value, and the PAPD is a positive value. In this specification, the PAPD is also simply referred to as a "positive frequency deviation". In this specification, the ZAPD is also referred to as a "substantially zero frequency deviation" (the reason for attaching "substantially" has been described above). In this specification, the NAPD is also simply referred to as a "negative frequency deviation".

[0132] FIG. 5 shows an example of a power profile of a two-zone EDOF having a base power of 20.0 D and an addition power of 2.25 D (another example corresponding to Embodiment 1). Note that the addition power graph (also referred to as a "normalized addition power graph") is a graph in which the radius (mm) is set on the horizontal axis and the addition power (D) is set on the vertical axis.

[0133] The power profiles shown in FIGS. 5A and 5C converted into addition power graphs are shown in FIGS. 5B and 5D, respectively. Different from the IOL of FIG. 4, the two IOLs shown in FIG. 5 do not have the fourth sub-region d.

[0134] The power profiles of the radius vs. power (refractive power) graphs shown in FIGS. 5A and 5C can be represented by four polynomials. Each partial region of the three sub-regions in the inner region and RAPP of FIGS. 5A and 5C can be represented by a single polynomial. The graph of radius vs. addition power shown in FIG. 5B can be represented by two polynomials (in the case of sub-regions a' and c') and two linear equations (in the case of sub-regions b' and the outer region). The normalized addition power profile of FIG. 5D can be represented by four linear equations.

[0135] Figures 6A and 6B show the total power profiles of the simulated eye model consisting of the cornea and EDOF, respectively, as shown in Figures 5A and 5C. The total power profiles shown in Figures 6A and 6B differ from the total power profile shown in Figure 2.

[0136] In the radius range of 0 mm to 0.9 mm, the total frequency profile in Figure 6 is set to various total frequency values, whereas the total frequency profile in Figure 2 is set to only one total frequency value (60.7 D) for viewing an object at an intermediate distance.

[0137] Various total power values ​​for IOLs that are greater or less than the 60.7D total power value shown in Figure 6 result in a wider depth of focus for intermediate visual acuity compared to the IOL in Figure 1, as shown in Figure 3B.

[0138] The sub-region a of the inner region in Figures 5A and 5B, which is equipped with PAPD, has the function of extending the intermediate distance range of mid-vision.

[0139] By incorporating NAPD in one or more sub-regions within the medial region, the power from RAPP can be reduced, improving the image quality of distance visual acuity. The sub-regions of the medial region that have the function of reducing the power of RAPP are sub-regions c and d in Figure 4, and sub-region c in Figure 5. Reducing the power of RAPP in these sub-regions can also be expected to reduce the likelihood of the appearance of nocturnal halos and glare symptoms in dark environments, as well as the degree of visual impairment.

[0140] The radial arrangement order of the sub-regions in the inner region of a two-zone IOL can be changed (as previously shown in [Aspect Group 1]). In Figure 4, the sub-regions of the two-zone IOL are arranged in the following order from the lens center O toward the outer edge of the lens (radial direction): first, the sub-region with PAPD; second, the sub-region with ZAPD; and third, the sub-region with NAPD. Of course, other arrangements are also possible. For example, the sub-regions could be arranged in the following order from the lens center: first, the sub-region with ZAPD; second, the sub-region with PAPD; and third, the sub-region with NAPD.

[0141] The size of each sub-region in the medial region affects the optical properties and performance of this EDOF for correcting distance and intermediate vision. For example, if sub-region b with ZAPD is too large compared to sub-region a with PAPD and sub-region c with NAPD, the optical performance of this EDOF for correcting distance and intermediate vision will be similar to that of an EDOF with a power profile as shown in Figure 1. If the region size of sub-region c with NAPD is too large compared to sub-region a with PAPD and sub-region b with ZAPD, the optical performance of this EDOF for correcting intermediate vision will decrease, but the optical performance for correcting distance vision will improve.

[0142] The proportion of the area of ​​each sub-region within the inner region can be determined by setting the radius values ​​of these sub-regions. For example, the inner region has three sub-regions a(PAPD), b(ZAPD), and c(NAPD), and the radius of the inner region is 1 mm (diameter 2 mm). In this example, the area of ​​the inner region is 3.142 mm². 2 That is the case. We assume that the area percentages of sub-regions a, b, and c relative to the entire inner region (proximal region) are 30%, 40%, and 30%, respectively. To achieve this, we set the radius value (ra) of sub-region a to 0.548 mm, the radius value (rb) of sub-region b to 0.837 mm, and the radius value (rc) of sub-region c to 1 mm.

[0143] The reference base power profile (dashed line, RBPP) of the IOL shown in Figures 4 and 5 (both corresponding to Embodiment 1) is designed to fully compensate for the average corneal spherical aberration (approximately 0.27 μm) of cataract patients. On the other hand, the reference base power profile of the EVR IOL (or bifocal type 2-zone and 3-zone IOL) according to the present invention is not limited to compensating only for 0.27 μm corneal spherical aberration. The reference base power profile of the EVR IOL according to the present invention can be designed to compensate for different corneal spherical aberration values, for example, 0.20 μm, 0.16 μm, 0.10 μm, and 0 μm corneal spherical aberrations. It can also be designed to fully correct or partially reduce specific longitudinal spherical aberrations (longitudinal spherical aberrations of geometric optics) of human corneal models modeled or defined based on human corneal databases or statistical data.

[0144] The frequency profiles according to the present invention, as illustrated in this specification, can be set by calculating or designing the front and rear shapes of the optical portion of the IOL. By utilizing known specific design or manufacturing techniques, it is possible to set the desired frequency profile for the front and rear shapes of the optical portion of the IOL. Known specific design techniques include various general methods or approaches, such as calculations using geometrical optics and numerical methods, calculations using ray tracing methods, and designs using commercially available optical design software.

[0145] The aspherical sag value or shape that produces the power profile may be located on the front, rear, or both surfaces of the lens. The EVR IOL of the present invention can be designed and manufactured to correct astigmatism in the eyes of phakic patients. Such design or manufacture is achieved by making the front or rear surface of the lens optical system toric or cylindrical. In toric-type EVR IOLs, the aspherical sag value or surface shape that produces the power profile of the EVR IOL of the present invention is provided on a lens optical surface that is not toric. For sag values, refer to WO2018 / 043366.

[0146] Figure 7 shows yet another example of Embodiment 1 of the present invention. The radius of the inner region is 0.9 mm. The inner region has four sub-regions. Subregion a is equipped with a PAPD, and its radius ra is 0.5 mm. Subregion b contains a ZAPD, located between radii ra and rb (0.7 mm). Subregion c contains a NAPD, located between radii rb and rc (0.8 mm). Subregion d contains a NAPD, located between radii rc and rd (0.9 mm). When the total area of ​​the inner region is taken as 100%, the proportions of the areas of subregions a, b, and c plus subregion d (c+d) are approximately 31%, 30%, and 39%, respectively. RAPP is approximately 2.25D greater than the reference-based frequency (RBPP).

[0147] To compare the optical characteristics and performance of the conventional EDOF ("Flat") shown in Figure 1 with this IOL (Embodiment 1, Figure 7), optical evaluation and retinal image simulation were performed using the model eye parameters shown in Table 1 and the optical design software Zemax® 13. Zemax is a registered trademark of Radiant Zemax LLC. The optical characteristics and properties evaluated were TFR (Through Focus Response) and MTF (Modulated Transfer Function).

[0148] Figure 8 shows the TFR according to pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using EDOF as shown in Figure 1 (prior art) and Figure 7 (Embodiment 1). Figure 9 shows the TFR according to pupil diameter at a spatial frequency of 100 lp / mm.

[0149] The TFR shows the defocus and MTF characteristics of the simulated EDOF. The MTF represents the image quality reconstructed by the optical system of the simulated eye model. As shown in FIG. 8, when the pupil diameter is 3 mm, high MTF values are given at defocuses of approximately 0 D (distance) and approximately 1.7 D (distance of approximately 59 cm) in both the prior art and the embodiments. A pupil diameter of 3 mm is a value that is generally used or assumed as the average pupil diameter of the aphakic patient's eye under normal lighting conditions.

[0150] The depth of focus of the EVR IOL is the range of defocus (or the range of display distances) within which an object can still be seen clearly or appropriately by the aphakic patient's eye. In this specification, the MTF value at a spatial frequency of 50 lp / mm useful for vision correction is regarded as 0.1 or more, and the MTF value at a spatial frequency of 100 lp / mm useful for vision correction is regarded as 0.05 or more. A state above this value is also expressed as "appropriate". The "depth of focus" in this specification refers to the range of object distances (defocus values on the horizontal axis of the graph) with appropriate MTF values. A wide range of this is also said to be "a wide (or large) depth of focus". The depth of focus at a spatial frequency of 50 lp / mm is shown in the TFR graph with a pupil diameter of 2 mm in FIG. 8. The depth of focus at a spatial frequency of 100 lp / mm is shown in the TFR graph with a pupil diameter of 2 mm in FIG. 9.

[0151] As shown by the TFR graphs with pupil diameters of 2 mm and 2.5 mm in FIG. 8, and the TFR graphs with pupil diameters of 2 mm, 2.5 mm, and 3 mm in FIG. 9, in the present invention, the depth of focus for intermediate vision is set wider in the horizontal axis direction than the depth of focus of the prior art IOL.

[0152] Under normal lighting conditions, it is known that smaller pupil diameters result in sharper vision (better vision) than larger pupil diameters. In two-zone IOLs with an inner region in the lens optical system for correcting intermediate and / or near vision, the MTF (in other words, the parameter indicating whether the image appears sharper or not) for intermediate and near vision is higher for smaller pupil diameters (e.g., 2mm and 2.5mm) than for larger pupil diameters (e.g., 3.5mm and 4mm). This is shown in Figures 8 and 9, where the MTF values ​​for pupil diameters of 2mm and 2.5mm in the range of 0.75D (viewing distance approximately 133cm) to 2.25D (viewing distance approximately 44cm) are higher than those for pupil diameters of 3.5mm and 4mm in the same range (0.75~2.25D). Hereafter, intermediate visual acuity and / or near visual acuity will also be simply referred to as "intermediate-near visual acuity," and intermediate vision and / or near vision will also be simply referred to as "intermediate-near vision."

[0153] The above also means that the depth of focus and visual quality for near and intermediate vision with a small pupil diameter (e.g., less than 2.75 mm) are superior to those for near and intermediate vision with a large pupil diameter (e.g., greater than 3.25 mm). As a result, it is thought that patients with aphakia see objects at close range with a small pupil diameter (e.g., with a pupil diameter smaller than the average pupil diameter of 3 mm). In other words, visual acuity is better with a smaller pupil diameter. This is true even for patients with aphakia. Even in patients with aphakia, the pupil size is adjusted to aim for higher visual acuity. Visual acuity is improved by reducing the pupil diameter rather than increasing it. Therefore, patients with aphakia reduce their pupil diameter.

[0154] The MTF of the IOL according to the present invention is also higher than that of the conventional IOL. This is demonstrated in the TFR graphs for pupil diameters of 2.5 to 4 mm shown in Figures 8 and 9, where the MTF value (vertical axis value) of the IOL according to the present invention at a defocus value of approximately 0D (horizontal axis value) is higher than that of the conventional IOL (vertical axis value).

[0155] When the pupil diameter is large, a two-zone optical design IOL (in-the-lens) makes distant objects appear sharper than when the pupil diameter is small. As the pupil diameter increases, the area of ​​the outer region of the lens optics (which corrects distance vision) that focuses light rays onto the retina also increases. This increases the amount of light rays focused onto the retina. As a result, objects are seen more clearly than when the pupil diameter is small.

[0156] When the pupil diameter is large (e.g., 4 mm), the MTF (representing image quality) of distance visual acuity is higher (better) than when the pupil diameter is small (e.g., 2 mm). This is demonstrated in Figures 8 and 9, where the vertical axis values ​​around 0D (far distance) are higher in the TFR graphs for pupil diameters of 3.5 mm and 4 mm than in the TFR graphs for pupil diameters of 2 mm and 2.5 mm.

[0157] The primary function of EDOF is to correct distance vision. The advantages of the present invention's IOL, which is designed to improve the image quality or how the image appears in distance vision, are demonstrated by the image simulation results shown in Figures 10 to 12. The distance vision image obtained with the present invention's IOL is less blurred and sharper than the distance vision image obtained with conventional IOLs.

[0158] The distance-view MTF (Segment in Figures 13 and 14) of the EDOF according to the present invention is higher than that of the conventional EDOF at pupil diameters of 3 mm and 4 mm. This is shown in the MTF graphs in Figures 13 and 14, respectively. These MTF graphs are simulated at distances of 6 m, 12 m, and 25 m.

[0159] Figures 13 and 14 show the MTF graphs for both IOLs simulated at distances of 6m, 12m, and 25m with pupil diameters of 3mm and 4mm. These graphs show that the distance visual acuity MTF of the EDOF according to the present invention is higher than that of the conventional EDOF. In these graphs, a spatial frequency of 50 lp / mm corresponds to a visual acuity of 0.5 (Snellen equivalent 20 / 40) or logMAR (common logarithm of minimum visual angle, log-mar, hereafter the same) of 0.3, and a spatial frequency of 100 lp / mm corresponds to a visual acuity of 1 (Snellen equivalent 20 / 20) or logMAR of approximately 0.

[0160] The advantages of the present invention's IOL in widening the depth of focus for intermediate visual acuity are shown in Figures 15-19. As seen in the TFR graph at a pupil diameter of 3 mm in Figure 8, the best viewing distance for both the conventional IOL and the present invention is approximately 59 cm (corresponding to a defocus of 1.7 D).

[0161] The images in Figures 15, 16, and 17 at different distances (40-60 cm) are simulation images with pupil diameters 2, 3, and 4, respectively. Distances from 40 cm to 55 cm are closer to the cornea of ​​the simulated eye model than the optimal display distance of 59 cm. The images in Figures 18 and 19 at different distances (70-110 cm) are simulation images with pupil diameters of 2 mm and 3 mm. These distances are greater than the optimal viewing distance (59 cm) for both intraocular lenses.

[0162] In Figure 15 (pupil diameter 2 mm), the Landolt C (Landolt ring) pattern is clearly visible in images taken at distances of 60 cm and 55 cm with conventional intraocular lenses and the IOL of the present invention. At distances of 50-40 cm, which are closer to the cornea than the optimal viewing distance, the ring pattern of the IOL of the present invention is clearer than that of the conventional IOL.

[0163] In Figures 16 (pupil diameter 3 mm) and 17 (pupil diameter 4 mm), the ring patterns of both IOLs are clearly visible in images taken at distances of 60 cm and 55 cm. In images taken at distances of 50-40 cm, the ring pattern of the IOL of the present invention is clearer than that of the IOL of the prior art.

[0164] In Figures 18 (pupil diameter 2 mm) and 19 (pupil diameter 3 mm), the ring pattern in the image of the IOL of the present invention at a distance of 90 cm to 110 cm is clearer than the ring pattern of the conventional IOL.

[0165] The image simulation results shown in Figures 15 to 19 indicate that the depth of focus for intermediate visual acuity of EDOF, one of the IOLs of the present invention, is wider than that of conventional EDOF. In this specification, "wide depth of focus" means a wide distance range (horizontal axis range in the graph) over which an appropriate MTF value can be secured.

[0166] The advantage of the EDOF of Embodiment 1 over the conventional EDOF is that, when the pupil diameter is less than 3 mm, the depth of focus for near and intermediate vision is widened, and the MTF value for far vision is higher for all pupil diameters.

[0167] Figure 20A shows the power profile of a conventional aspherical EM-IOL (hereinafter simply referred to as EM-IOL) with a base power of 20.0D and an add power of 1.0D. This IOL employs a two-zone type extended single-focus optical design. The IOL has two optical regions that reflect this design. The outer region has a RBPP for correcting distance vision. The inner region has a power 1.0D greater than the base power to correct intermediate vision.

[0168] Figure 20B shows the EM-IOL according to the present invention (corresponding to Embodiment 2). The radius of the inner region is 0.9 mm. The inner region has four sub-regions. Subregion a is equipped with a PAPD, and its radius ra is 0.5 mm. Subregion b contains a ZAPD, located between radii ra and rb (0.7 mm). Subregion c contains a NAPD, located between radii rb and rc (0.8 mm). Subregion d contains a NAPD, located between radii rc and rd (0.9 mm). When the total area of ​​the inner region is taken as 100%, the proportions of the areas of subregions a, b, and c plus subregion d (c+d) are approximately 31%, 30%, and 39%, respectively. RAPP is approximately 1.0D greater than the reference-based frequency (RBPP).

[0169] Figure 21 shows the TFR according to pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using an EM-IOL as shown in Figure 20A (prior art) and Figure 20B (embodiment 2). Figure 22 shows the TFR according to pupil diameter at a spatial frequency of 100 lp / mm.

[0170] The depth of focus in the EM-IOL of the present invention (Embodiment 2) at pupil diameters of 2.5 mm and 3 mm, and at a spatial frequency of 50 lp / mm, is wider than that of the conventional EM-IOL, as shown in Figures 21A, 21B, 22A, and 22B, respectively. The MTF value near 0D (distance for distant viewing) for all pupil diameters is higher for the EM-IOL of the present invention (Embodiment 2) than for the conventional EM-IOL.

[0171] The advantage of the EM-IOL of Embodiment 2 over the conventional EM-IOL is that, when the pupil diameter is less than 3 mm, the depth of focus for intermediate vision is wider, and the MTF value for distance vision is higher for all pupil diameters.

[0172] Figure 23A shows the power profile of a conventional multifocal lens (corresponding to Embodiment 3) with a base power of 20.0D and an add power of 3.25D. This IOL employs a two-zone multifocal optical design. The IOL has two optical regions in which this design is actually reflected. The outer region has a RBPP for correcting distance vision. The inner region has a power 3.25D greater than the base power to correct intermediate vision.

[0173] Figure 23B shows a multifocal lens according to the present invention. The radius of the inner region is 1 mm. The inner region has four sub-regions. Subregion a is equipped with a PAPD, and its radius ra is 0.45 mm. Subregion b is equipped with a ZAPD, located between radii ra and rb (0.71 mm). Subregion c is equipped with NAPD, located between radii rb and rc (0.875 mm). Subregion d is equipped with NAPD, located between radii rc and rd (1 mm). When the total area of ​​the inner region is taken as 100%, the proportions of the areas of subregions a, b, and c plus subregion d (c+d) are approximately 20%, 30%, and 50%, respectively. RAPP is approximately 3.25D greater than the reference-based frequency (RBPP).

[0174] Figure 24 shows the TFR according to pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using a multifocal lens as shown in Figure 23A (prior art) and Figure 23B (Embodiment 3). Figure 25 shows the TFR according to pupil diameter at a spatial frequency of 100 lp / mm.

[0175] The depth of focus in the multifocal lens of the present invention (Embodiment 3) at pupil diameters of 2.5 mm and 3 mm, and at a spatial frequency of 50 lp / mm, is wider than that of conventional multifocal lenses, as shown in Figures 24A, 24B, 25A, and 25B, respectively. The MTF value near 0D (distance for distant viewing) for all pupil diameters is higher for the multifocal lens of the present invention (Embodiment 3) than for conventional multifocal lenses.

[0176] The advantage of the multifocal lens of Embodiment 3 over conventional multifocal lenses is that, when the pupil diameter is less than 3 mm, the depth of focus for near and intermediate vision is widened, and the MTF value for far vision is higher for all pupil diameters.

[0177] Figure 26A shows the frequency profile of a conventional 3-zone EDOF. Figure 26B shows the frequency profile of a 3-zone EDOF (Embodiment 1') according to the present invention.

[0178] The 3-zone EDOF of Embodiment 1' comprises three regions. The first region, including the lens center O, is used for correcting distance vision, and the second region is used for correcting intermediate vision. The second region is an annular region surrounding the first region and has a power greater than the base power. The third region is used for correcting distance vision. The third region is an annular region surrounding the second region.

[0179] The second region lies between radii ra0 (0.6 mm) and rd (1.2 mm). This second region contains four sub-regions (a, b, c, d). The RAPP of the second region is 2.25 D greater than the RBPP.

[0180] In this example, sub-region a has a positive join frequency deviation, sub-region b has a zero join frequency deviation, and sub-regions c and d have negative join frequency deviations.

[0181] Subregion a lies between radii ra0 (0.6 mm) and radii ra (0.885 mm). Subregion b lies between radii ra (0.885 mm) and radii rb (1.05 mm). Subregion c lies between radii rb (1.05 mm) and radii rc (1.125 mm). Subregion d lies between radii rc (1.125 mm) and radii rd (1.2 mm). When the total area of ​​the inner region is considered 100%, the proportions of the areas of sub-regions a, b, and c plus sub-region d (c+d) are approximately 39%, 30%, and 31%, respectively.

[0182] Figure 27 shows the TFR (Total Flow Rate) according to pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for a simulated eye model using EDOF as shown in Figure 26A (Prior Art) and Figure 26B (Embodiment 1').

[0183] Figure 28 shows the MTF values ​​for the conventional technology and Embodiment 1' according to pupil diameter at around 0D (distance of distant viewing). The MTF graph for Embodiment 1' shows higher values ​​than the conventional technology, except that the conventional technology showed higher MTF values ​​at a pupil diameter of 2 mm.

[0184] The above results demonstrate that Embodiment 1' of the 3-zone EDOF offers the advantage of improving the image quality of distance visual acuity at all pupil sizes while widening the depth of focus for intermediate visual acuity at smaller (average) pupil diameters compared to the conventional 3-zone EDOF.

[0185] Figure 29 shows the frequency profiles of three IOLs (pattern c1, pattern c2, and pattern c3d1) with different NAPD graphs for the subregions within the medial region. The absolute value of NAPD in sub-region c1 of the IOL in pattern c1 is greater than the absolute value of NAPD in sub-region c2 of the IOL in pattern c2. In other words, the value of NAPD is the decrease from RAPP, or more precisely, the average value (negative value) obtained by subtracting the vertical axis value of RAPP from the vertical axis value of the graph for each pattern c for each horizontal axis value within sub-region c(+d). The "absolute value of NAPD" is the absolute value of this average, and is, for example, the average value of the vertical axis width when the horizontal hatched area in Figure 5A is viewed in the horizontal axis direction. In an IOL with pattern c3d1, the sum of the absolute values ​​of the NAPD of subregion c3 and subregion d1 is greater than the absolute value of the NAPD of subregion c2 in an IOL with pattern c2.

[0186] Figure 30 shows the TFR of IOLs at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. It has been demonstrated that IOLs with a larger absolute value of NAPD provide better distance visual acuity MTF values ​​(when defocused near 0D) than IOLs with a smaller absolute value of NAPD. This means that the image quality of distance visual acuity in aphakia patients wearing IOLs with a larger absolute value of NAPD is better than that of aphakia patients wearing IOLs with a smaller absolute value of NAPD. The reason for this effect is that IOLs with a larger absolute value of NAPD can focus more light rays coming from a distance onto the retina than IOLs with a smaller absolute value of NAPD.

[0187] The depth of focus for near and intermediate vision of these three IOLs is relatively similar at pupil diameters of 2.5 mm and 3 mm. IOLs with a smaller absolute value of NAPD can provide a more appropriate near and intermediate vision MTF value in the defocus range of 0.75 D (at a distance of approximately 133 cm) to 2.25 D (at a distance of approximately 44 cm) than IOLs with a larger absolute value of NAPD. This effect occurs because IOLs with a smaller absolute value of NAPD can focus more light rays from near and intermediate distances onto the retina than IOLs with a larger absolute value of NAPD.

[0188] Figure 31 shows the frequency profiles of three EDOFs (patterns b1, b2, and b3) with different area ratios of subregions containing ZAPD. The inner diameter of each IOL in Figure 31 is 0.9 mm. If the circular area of ​​the inner region of the lens with a radius of 0.9 mm is taken as 100%, then the radius of the sub-region with PAPD (40% of the area), the radius of the sub-region with ZAPD (20% of the area), and the radius of the sub-region with NAPD (40% of the area) can be calculated. In the IOL of pattern b1, the area ratios of the subregions with PAPD, ZAPD, and NAPD are 40%, 20%, and 40%, respectively. In the IOL of pattern b2, the area ratio of each subregion is PAPD:ZAPD:NAPD = 30%:40%:30%. In the IOL of pattern b3, the area ratio of each subregion is PAPD:ZAPD:NAPD = 20%:60%:20%. IOLs in pattern b1 have the lowest proportion of subregion area containing ZAPD, while IOLs in pattern b3 have the highest proportion of subregion area containing ZAPD.

[0189] Figure 32 shows the TFR of IOLs shown in Figure 31 for pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. It can be seen that IOLs with a high area ratio of the subregion with ZAPD have higher MTF values ​​for near and intermediate vision in the defocus range of 1 D (distance of approximately 100 cm) to approximately 2.2 D (distance of approximately 45 cm) than IOLs with a low area ratio of the subregion with ZAPD. The image quality of intermediate visual acuity of IOLs with a high area ratio of the subregion with ZAPD is higher than that of IOLs with a low area ratio of the subregion with ZAPD. This is because IOLs with a high area ratio of the subregion with ZAPD focus a much larger amount of light rays coming from intermediate distances onto the retina than IOLs with a low area ratio of the subregion with ZAPD.

[0190] The distance visual acuity MTF value of the IOL in pattern b1 at a pupil diameter of 2.5 mm is higher than that of the IOLs in patterns b2 and b3. Conversely, the intermediate and near visual acuity MTF value is lower than that of the IOLs in patterns b2 and b3. The IOL in pattern b1, which has a smaller proportion of the area of ​​the subregion with ZAPD and a larger proportion of the area of ​​the subregion with NAPD, focuses a much larger amount of light coming from farther away onto the retina than the IOLs in patterns b2 and b3 at a pupil diameter of 2.5 mm (the MTF value of pattern b1 is higher than that of the other patterns near 0D). Therefore, its distance visual acuity MTF value is higher than that of the IOLs in patterns b2 and b3. At pupil diameters of 3 mm and 3.5 mm, the MTF values ​​of these three IOLs are relatively similar for distance visual acuity MTF.

[0191] Figure 33 shows the frequency profiles of four EDOFs (pattern a1c1, pattern a1c2, pattern a2c1, pattern a2c2) whose subregions with added frequencies are all different from each other. The PAPD of the IOLs in patterns a1c1 and a1c2 is greater than the PAPD of the IOLs in patterns a2c1 and a2c2. In other words, the value of PAPD is the increase from RAPP, or more precisely, the average value (positive value) obtained by subtracting the vertical axis value of RAPP from the vertical axis value of the graph of each pattern ac for each horizontal axis value within sub-region a. For example, it is the average value of the vertical axis width when viewing the vertical hatched portion of Figure 5A in the horizontal direction. The absolute values ​​of NAPD for IOLs in patterns a1c1 and a2c1 are greater than the absolute values ​​of NAPD for IOLs in patterns a1c2 and a2c2.

[0192] Figure 34 shows the TFR of the IOLs shown in Figure 33 for pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. It has been demonstrated that IOLs with a large absolute value of NAPD (patterns a1c1 and a2c1) give higher distance visual acuity MTF values ​​at defocus around 0D than IOLs with a small absolute value of NAPD (patterns a1c2 and a2c2).

[0193] IOLs with a sub-region (pattern a1c1 and pattern a1c2) equipped with a PAPD and a high area ratio of said sub-region have appropriate mid-near vision MTF values ​​in the defocus range from 2D (distance approximately 50cm) to approximately 2.5D (distance approximately 40cm). Furthermore, the mid-near vision MTF values ​​of such IOLs are higher than the intermediate-near vision MTF values ​​of IOLs with a small area ratio of the sub-region equipped with a PAPD (pattern a2c1 and pattern a2c2).

[0194] Figure 35 shows the frequency profiles of IOLs with and without power jumps (hereinafter referred to as power jump IOLs). The PAPD of a power jump IOL is greater than that of a non-power jump IOL. The absolute value of NAPD for power jump IOLs is greater than the absolute value of NAPD for IOLs without power jumps.

[0195] Figure 36 shows the TFR of the IOLs shown in Figure 35 for pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. Power jump IOLs with a large PAPD have appropriate intermediate-near vision MTF values ​​in the defocus range from 1 D (distance approximately 100 cm) to approximately 2.0 D (distance approximately 50 cm), and have higher intermediate-near vision MTF values ​​than non-power jump IOLs with a small PAPD. However, for defocus ranges of 2 D or more (distance less than 50 cm), power jump IOLs with a large PAPD have higher intermediate-near vision MTF values. The distance vision MTF value at defocus around 0D is higher for power jump IOLs with a large absolute NAPD value than for non-power jump IOLs with a small absolute NAPD value.

[0196] In this invention, the power jump between sub-regions in the medial region and the power jump between the medial and lateral regions in the two-zone system can be utilized to change the power profile of the sub-regions, which are equipped with PAPD and NAPD. By changing the power profile of the sub-regions in the medial region, the values ​​of PAPD and NAPD can be changed. As a result, the TFR characteristics of the IOL can be adjusted to provide the intended performance for distance vision correction and intermediate / near vision correction.

[0197] The order of the subregions comprising PAPD, ZAPD, and NAPD in this invention can be changed.

[0198] Figure 37 shows examples of frequency profiles for four EDOFs (Flat (the only one prior art), CenterFlat, MiddleFlat, and OuterFlat) with different radial arrangements of subregions containing PAPD, ZAPD, and NAPD.

[0199] In CenterFlat, the subregions are arranged in the following order from the subregion containing the lens center O to the subregion outside the inner region: a subregion with ZAPD, a subregion with PAPD, and a subregion with NAPD. In OuterFlat, the order is a subregion with NAPD, a subregion with PAPD, and a subregion with ZAPD.

[0200] Figure 38 shows the TFRs of these IOLs at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. For all pupil diameters, the distance visual acuity MTF values ​​at defocus near 0D for CenterFlat are higher than the MTF values ​​for Flat (conventional technology), MiddleFlat, and OuterFlat. For all pupil diameters, the distance visual acuity MTF values ​​at defocus near 0D for MiddleFlat and OuterFlat IOLs are higher than the distance visual acuity MTF values ​​for Flat IOLs.

[0201] The depth of focus for CenterFlat at pupil diameters of 2.5mm and 3mm is wider than that of Flat. When the defocus exceeds 2D, the MTF value for CenterFlat is higher than that of Flat at all pupil diameters. This means that the image quality of CenterFlat is higher than that of Flat at distances less than 50cm.

[0202] The depth of focus for MiddleFlat at a pupil diameter of 2.5mm is wider than that for Flat. When defocus exceeds 2.2D, the MTF value for MiddleFlat is higher than that of Flat for all pupil diameters. When defocus exceeds 1.7D, the MTF value for OuterFlat is higher than that of Flat for all near vision.

[0203] Figure 39 shows the power profiles of two EDOFs (OuterHigher a1c1 and OuterHigher a2c2) with a different radial arrangement than that shown in Figure 37. From the subregion containing the lens center O to the subregion outside the inner region, they are, in order, subregions with NAPD, subregions with ZAPD, and subregions with PAPD. There are power jumps between each subregion in the OuterHigher a2c2 region.

[0204] Figure 40 shows the TFR of these intraocular lenses at different pupil diameters. The distance visual acuity MTF values ​​for OuterHigher a1c1 and OuterHigher a2c2 at defocus around 0D are higher than those of the conventional Flat lens. The depth of focus for intermediate and near visual acuity of these three IOLs is relatively similar despite the difference in pupil size.

[0205] The MTF value for intermediate-near vision during defocus is less than approximately 1.6D. The MTF values ​​for intermediate-near vision in OuterHigher a1c1 and OuterHigher a2c2 are slightly higher than those in Flat.

[0206] These results demonstrate that different orders of subregions comprising PAPD, ZAPD, and NAPD within the inner region of the present invention can provide several advantages compared to conventional IOLs, including higher distance visual acuity (MTF) values ​​for different pupil diameters, wider depth of focus at specific pupil diameters, and higher MTF values ​​at close range. Furthermore, different orders can also provide different advantages compared to conventional IOLs.

[0207] The present invention can be applied to other prior art 2-zone and 3-zone type ophthalmic lenses ([Aspect Group 2]) having a constant base power profile and a constant add power profile, as illustrated in Figures 41A and 42A.

[0208] In these figures, the base frequency value is 20.0D for different radius values, and the add frequency is 2.25D for different radius values.

[0209] Unlike the reference base power profiles of the conventional “Flat” 2-zone IOL (Figure 1) and the conventional “Flat” 3-zone IOL (Figure 26A), which are designed to compensate for or reduce the spherical aberration of the average human cornea, the base power profiles in Figures 41A and 42A have a constant power value of 20.0D. These power profiles are not intended to correct or reduce the spherical aberration of the human cornea.

[0210] Advantages such as higher distance image quality, wider depth of field for intermediate and near vision, and better near image quality for close distances, or improved visual acuity, can also be obtained by applying the present invention to the conventional IOLs shown in Figures 41A and 42A.

[0211] Figure 41B shows an example of a power profile in which the present invention has been applied to improve the distance visual acuity and near and intermediate visual acuity of the conventional two-zone IOL shown in Figure 41A. Figure 42B shows an example of a power profile in which the present invention has been applied to improve the distance visual acuity and near and intermediate visual acuity of the conventional 3-zone IOL shown in Figure 42A.

[0212] In the present invention, the preferred radius of the inner region of the EVR IOL, which is a two-zone type and has an add power, is 0.6 to 1.25 mm (diameter 1.2 to 2.5 mm). In the case of the phakic EVR IOL of the present invention, the preferred radius of the inner region is 0.7 to 1.5 mm (diameter 1.4 to 3 mm). In the case of the EVR contact lens of the present invention, the preferred radius of the inner region is 0.85 to 1.75 mm (diameter 1.7 to 3.5 mm).

[0213] The three-zone type of the EVR IOL of this invention has three regions (zones). The first region, which includes the center of the lens, is used for correcting distance vision, and the second region is used for correcting near vision and / or intermediate vision. The second region is an annular region surrounding the first region and has a power greater than the base power. The third region is used for correcting distance vision. The third region is an annular region surrounding the second region.

[0214] Preferably, the inner diameter of the second region at the boundary between the first region and the second region having the add power is 0.7 to 1.1 mm (diameter 1.4 to 2.2 mm). Preferably, the outer diameter of the second region at the boundary between the second and third regions is between 1.3 and 1.75 mm (diameter 2.6 and 3.5 mm). In the case of the three-zone type of the phakic EVR IOL of the present invention, the inner diameter of the second region is preferably 0.8 to 1.2 mm (diameter 1.6 to 2.4 mm), and the outer diameter of the second region is preferably 1.45 to 1.9 mm (diameter 2.9 to 3.6 mm). In the case of the 3-zone type contact lens of the present invention, the inner diameter of the second region is preferably 0.9 to 1.45 mm (diameter 1.8 to 2.9 mm), and the outer diameter of the second region is preferably 1.7 to 2.3 mm (diameter 3.4 to 4.6 mm).

[0215] The preferred add powers for the 2-zone and 3-zone types of the EVR IOL and phakic EVR IOL of the present invention are 1 to 4D on the optical surface of the IOL, and 0.75 to 4D on the corneal surface in the case of the EVR contact lens of the present invention. In addition, in [Aspect Group 1], the preferred add power for the 2-zone and 3-zone types of the EM-IOL of the present invention is 1 to 2D, for the EDOF of the present invention it is 2 to 2.75D, and for the multifocal lens it is 2.75D or higher.

[0216] Subregions having add power to correct a small range in near vision, intermediate vision, and far vision very close to intermediate vision are subregions having PAPD, subregions having ZAPD, and subregions having NAPD. In the present invention, a subregion having add power may have not only two or more subregions having NAPD, but also two or more subregions having ZAPD and two or more subregions having PAPD.

[0217] Subregions equipped with PAPDs may have PAPD graphs with different shapes from each other. Figure 43 shows several examples of possible PAPD graphs in addition to the PAPD graphs shown in previous figures of the EVR IOL of the present invention. Of course, other PAPD graph shapes not shown herein are also applicable to the EVR IOL of the present invention. Furthermore, the NAPD shapes shown herein may be modified as appropriate. In addition, PAPD graph shapes not shown in the figures of this application may be designed as appropriate.

[0218] A PAPD graph, where the horizontal axis is radius and the vertical axis is add frequency, can be composed of one or more straight lines, one or more curves, or a combination of at least one straight line and one curve. Each line can be represented by a linear equation, and each curve can be represented by a polynomial. The preferred degree of the polynomial equation is between 4 and 8. However, a higher degree, such as 9 to 16, may be set as needed. This straight line increases, decreases, or remains unchanged as the radius increases (in the radial direction from the lens center to the lens periphery). This curve can also accommodate cases where the frequency increases, decreases, increases and then decreases, or decreases and then increases as the radius increases.

[0219] Subregions equipped with NAPDs may have NAPD graphs with different shapes from each other. Figure 43 shows several examples of possible NAPD graphs in addition to the NAPD graphs shown in earlier figures of the EVR IOL of the present invention. Of course, other NAPD graph shapes not shown herein are also applicable to the EVR IOL of the present invention. Furthermore, the NAPD shapes shown herein may be modified as appropriate. In addition, NAPD graph shapes not shown in the figures of this application may be designed as appropriate.

[0220] A NAPD graph, where the horizontal axis is radius and the vertical axis is add frequency, can be composed of one or more straight lines, one or more curves, or a combination of at least one straight line and one curve. Each line can be represented by a linear equation, and each curve can be represented by a polynomial. The preferred degree of the polynomial equation is 4 to 8, however, a higher degree, such as 9 to 16, may be set as needed. This straight line either decreases or remains unchanged as the radius increases (in the radial direction from the lens center to the lens periphery). This curve can also accommodate cases where the frequency decreases, increases, decreases and then increases, or increases and then decreases as the radius increases.

[0221] With respect to the EVR IOL of the present invention, the preferred average value of PAPD within the lens when viewing the sub-region with PAPD in a frontal view (planar view), either in a graph with radius on the horizontal axis and power on the vertical axis, or in a graph with radius on the horizontal axis and add power on the vertical axis, is 0.3D to 1.0D.

[0222] The preferred mean value of the power difference between the design power profile of the subregion with ZAPD and the reference add power profile is -0.2D to 0.2D. The preferred mean value of NAPD in this invention is less than -0.3D. In other words, the preferred mean value of the absolute value of NAPD is greater than 0.3D. This value of 0.3D takes into account that the power of the corneal surface is approximately 0.21D. This value of 0.21D of the corneal surface is very close to 0.25D, which is the smallest power interval in eyeglasses used for visual acuity and visual field correction. In eyeglasses, 0.25D makes a difference in the visual acuity of the wearer and also makes a difference in the image quality of objects seen by the wearer. Therefore, setting the minimum value of PAPD to 0.3D and the minimum absolute value of NAPD to 0.3D may result in differences (improvements) in near vision correction and / or intermediate vision correction compared to correcting visual acuity using conventional IOLs.

[0223] When the total area of ​​the lens region with this add power is taken as 100%, it is preferable that the area ratio of the sub-regions containing PAPD, ZAPD, and NAPD within the lens region with the add power be within a specific percentage range. These area ratios affect the optical properties and performance of the EVR IOL of the present invention for correcting visual acuity in the eye of patients with phakic vision.

[0224] The preferred area ratio of the subregion containing PAPD is 15% to 50% of the total area of ​​the proximal region containing the add frequency. The preferred area ratio of the subregion containing ZAPD is 30% to 70%. The preferred area ratio of the subregion containing NAPD is 15% to 50%.

[0225] By maintaining the area ratio of the subregion with ZAPD to 30% to 60% of the total area of ​​the near region with the add power, the near and / or intermediate distance range in which objects can still be seen clearly in the phakic patient eye implanted with the present invention can be maintained or remain equivalent to that of a prior art ("Flat") IOL. The area ratio of the subregion with PAPD can improve near and / or intermediate visual acuity, and the area ratio of the subregion with NAPD can improve distance visual acuity.

[0226] The IOLs of this invention can be made from various IOL materials, such as acrylic, silicone, PMMA, and hydrogel. They can be manufactured using various known manufacturing processes, such as turning, casting / molding, printing, and combinations of different manufacturing processes.

[0227] In the ophthalmic lenses taught herein, the power profiles and optical designs according to the present invention are also applicable to phakic IOLs (or implantable contact lenses) and EVR contact lenses.

[0228] The embodiments of the present invention will be described below. Embodiment 1: A region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision, In the aforementioned distant region, the power is reduced in order to at least partially offset the positive longitudinal spherical aberration of the average human cornea by negative longitudinal spherical aberration. In the aforementioned near region, the lens center O has a predetermined base power, and a constant positive power is added to the aspherical reference power within a predetermined radial range in the virtual aspherical lens so as to completely cancel out the positive longitudinal spherical aberration of the average human cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a frequency deviation of approximately zero for the aforementioned positive constant frequency. Subregion 3 is an intraocular lens that produces a negative power deviation relative to the aforementioned positive constant power. Embodiment 2: A region concentric with the lens center O, comprising a near region that includes the lens center O and corrects near vision, and a far region that is located outside the near region when the radial direction from the lens center O is taken outward and corrects far vision, In the aforementioned distant region, the power is reduced in order to at least partially offset the positive longitudinal spherical aberration of the average human cornea by negative longitudinal spherical aberration. In the aforementioned near region, the lens center O has a predetermined base power, and a constant positive power is added to the aspherical reference power within a predetermined radial range in the virtual aspherical lens so as to completely cancel out the positive longitudinal spherical aberration of the average human cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a frequency deviation of approximately zero for the aforementioned positive constant frequency. Subregion 3 is an intraocular lens that produces a negative power deviation relative to the aforementioned positive constant power. Embodiment 3: A region concentric with the lens center O, comprising a distance region that includes the lens center O and corrects distance vision, and an outer region that is located outside the near region when the radial direction from the lens center O is taken outward, and corrects distance vision, In the aforementioned outer region, the power is reduced in order to at least partially offset the positive longitudinal spherical aberration of the average human cornea by negative longitudinal spherical aberration. The aforementioned near region has a predetermined base power at the lens center O, and a constant positive power is added to the aspherical reference power within a predetermined radial range in the virtual aspherical lens so as to completely cancel out the positive longitudinal spherical aberration of the average human cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a frequency deviation of approximately zero for the aforementioned positive constant frequency. Subregion 3 is an intraocular lens that produces a negative power deviation relative to the aforementioned positive constant power. Embodiment 4: A region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision, In the aforementioned near region, a positive constant power is added to a reference power having a predetermined base power at the lens center O. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 yields a positive frequency deviation for the aforementioned positive constant frequency, Subregion 2 yields a frequency deviation of approximately zero for the aforementioned positive constant frequency. Sub-region 3 is an ophthalmic lens that produces a negative power deviation with respect to the aforementioned positive constant power. Embodiment 5: With respect to the area of ​​the nearby region, The area ratio of the aforementioned sub-region 1 is in the range of 15-50%. The area ratio of the aforementioned sub-region 2 is in the range of 30-70%. The intraocular lens according to any one of embodiments 1 to 3, wherein the area ratio of the subregion 3 is in the range of 15 to 50%. Embodiment 6: The mean value of the positive frequency deviation in the sub-region 1 is in the range of 0.3 to 1D. The mean value of the frequency deviation of approximately zero in the sub-region 2 is in the range of -0.2 to 0.2D. The intraocular lens according to any one of embodiments 1 to 3, wherein the mean value of the negative frequency deviation in the subregion 3 is in the range of -0.3D or less. Embodiment 7: An intraocular lens according to any one of Embodiments 1 to 3, wherein the positive constant power is in the range of 1 to 4D. Embodiment 8: The arrangement of the sub-regions 1 to 3 when viewed radially from the lens center O is one of the following, the intraocular lens according to any one of Embodiments 1 to 3: Subarea 1, Subarea 2, Subarea 3 Subarea 1, Subarea 3, Subarea 2 Sub-area 2, Sub-area 1, Sub-area 3 Subarea 2, Subarea 3, Subarea 1 Sub-area 3, Sub-area 1, Sub-area 2 Subarea 3, Subarea 2, Subarea 1. Embodiment 9: With respect to the area of ​​the nearby region, The area ratio of the aforementioned sub-region 1 is in the range of 15-50%. The area ratio of the aforementioned sub-region 2 is in the range of 30-70%. The ophthalmic lens according to embodiment 4, wherein the area ratio of the sub-region 3 is in the range of 15 to 50%. Embodiment 10: The mean value of the positive frequency deviation in the sub-region 1 is in the range of 0.3 to 1D. The mean value of the frequency deviation of approximately zero in the sub-region 2 is in the range of -0.2 to 0.2D. The ophthalmic lens according to embodiment 4, wherein the average value of the negative frequency deviation in the subregion 3 is in the range of -0.3D or less. Embodiment 11: The ophthalmic lens according to Embodiment 4, wherein the positive constant power is in the range of 1 to 4D. Embodiment 12: The arrangement of the sub-regions 1 to 3 when viewed radially from the lens center O is one of the following, for the ophthalmic lens according to Embodiment 4: Subarea 1, Subarea 2, Subarea 3 Subarea 1, Subarea 3, Subarea 2 Sub-area 2, Sub-area 1, Sub-area 3 Subarea 2, Subarea 3, Subarea 1 Sub-area 3, Sub-area 1, Sub-area 2 Subarea 3, Subarea 2, Subarea 1. Embodiment 13: An intraocular lens according to Embodiment 1 or 2, wherein the change in power is smooth or abrupt, or the power jumps, at least one of the boundaries between two different sub-regions, and the boundaries between each of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent. Embodiment 14: The ophthalmic lens according to Embodiment 4, wherein the change in power is smooth or abrupt, or the power jumps, at least at the boundary between two different sub-regions, and at the boundary between the far region and each of the sub-regions 1 to 3 when the near region and the far region are adjacent. Embodiment 15: The intraocular lens according to Embodiment 2, wherein the diameter of the near region in a planar view is in the range of 1.2 to 2.5 mm. Embodiment 16: The intraocular lens according to Embodiment 3, wherein the change in power is smooth or abrupt, or the power jumps, at least one of the following: the boundary between two different sub-regions; the boundary between each of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent; and the boundary between each of the sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent. Embodiment 17: The inner diameter in the near region in a plan view is in the range of 1.4 to 2.2 mm. The intraocular lens according to embodiment 3, wherein the outer diameter in a plan view of the aforementioned near region is in the range of 2.6 to 3.5 mm. Embodiment 18: The ophthalmic lens is a phakic intraocular lens, The aforementioned near region includes the lens center O. The aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O. The ophthalmic lens according to embodiment 4, wherein the diameter of the near region in a planar view is in the range of 1.4 to 3 mm. Embodiment 19: The ophthalmic lens is a phakic intraocular lens, The aforementioned far region includes the lens center O. The near region is located outside the far region when the radial direction is taken outward from the lens center O. The lens has an outer region that is positioned outside the near region when the radial direction is taken outward from the lens center O, and corrects the visual acuity for distance vision. The inner diameter in the aforementioned near region, viewed from the plan, is in the range of 1.6 to 2.4 mm. The ophthalmic lens according to embodiment 4, wherein the outer diameter in a planar view of the aforementioned near region is in the range of 2.9 to 3.6 mm. Embodiment 20: The ophthalmic lens is a contact lens, The aforementioned near region includes the lens center O. The aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O. The ophthalmic lens according to embodiment 4, wherein the diameter of the near region in a planar view is in the range of 1.4 to 3 mm. Embodiment 21: The ophthalmic lens is a contact lens, The aforementioned far region includes the lens center O. The aforementioned near region is located outside the far region when the radial direction is taken outward from the lens center O. The lens has an outer region that is positioned outside the near region when the radial direction is taken outward from the lens center O, and corrects the visual acuity for distance vision. The inner diameter in the aforementioned near region, viewed from the plan, is in the range of 1.6 to 2.4 mm. The ophthalmic lens according to embodiment 4, wherein the outer diameter in a planar view of the aforementioned near region is in the range of 2.9 to 3.6 mm. Embodiment 22: The intraocular lens according to any one of Embodiments 1 to 3, wherein the intraocular lens is a toric lens. Embodiment 23: Optical design method for an intraocular lens according to any one of Embodiments 1 to 3. Embodiment 24: A method for manufacturing an intraocular lens, comprising manufacturing an intraocular lens designed by the optical design method described in Embodiment 23 using at least a lathe, molding, or 3D printing. Embodiment 25: The ophthalmic lens according to Embodiment 4, wherein the intraocular lens is a toric lens. Embodiment 26: Optical design method for ophthalmic lenses as described in Embodiment 4. Embodiment 27: A method for manufacturing an ophthalmic lens, comprising manufacturing an ophthalmic lens designed by the optical design method described in Embodiment 26 using at least a lathe, molding, or 3D printing.

Claims

1. The lens comprises at least one distance region for correcting distance vision and at least one near region for correcting near vision, wherein the distance region and the near region are concentric with respect to the lens center O. In the aforementioned far region, as the radial distance to the lens center O increases, the optical power of the lens decreases. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 introduces a positive frequency deviation to the virtual optical frequency profile in the near region, and the virtual optical frequency profile is an aspherical frequency profile with a constant positive frequency added. Subregion 2 provides a zero frequency deviation to the virtual optical frequency profile. Subregion 3 is an intraocular lens that provides a negative power deviation to the virtual optical power profile.

2. The intraocular lens according to claim 1, wherein, in the far region, the decrease in optical power with increasing radial distance to the center of the lens is such that the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea, is at least partially offset.

3. The intraocular lens according to claim 1, wherein the virtual optical power profile is such that the positive longitudinal spherical aberration of a human cornea, particularly an average human cornea, is at least partially canceled out.

4. A region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision, In the aforementioned distant region, the power is reduced so that a negative longitudinal spherical aberration is present that at least partially cancels out the positive longitudinal spherical aberration caused by the cornea. In the aforementioned near region, a positive constant power is added to the aspherical reference power within a predetermined radial range of a virtual aspherical lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 brings about a positive frequency deviation with respect to the aforementioned positive constant frequency. Subregion 2 yields a nearly zero frequency deviation for the aforementioned positive constant frequency. The intraocular lens according to claim 1, wherein the sub-region 3 provides a negative power deviation with respect to the positive constant power.

5. An intraocular lens according to claim 1, characterized in that the near region includes the lens center O.

6. The intraocular lens according to claim 1, wherein the distant region includes the lens center O, the intraocular lens is positioned outside the near region when the radial direction from the lens center O is taken outward, and further comprises an outer region which also corrects the visual acuity of distance vision, the distant region, the near region and the outer region are concentric with respect to the lens center O, and in the outer region, the optical power of the lens decreases as the radial distance to the lens center O increases.

7. The intraocular lens according to claim 6, wherein in the outer region, the optical power of the lens decreases as the radial distance to the lens center O increases, in order to at least partially offset the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea, with negative longitudinal spherical aberration.

8. A region concentric with the lens center O, comprising: a distance region that includes the lens center O and corrects distance vision; a near region located outside the distance region when the radial direction from the lens center O is taken outward and corrects near vision; and an outer region located outside the near region and corrects distance vision. In the aforementioned outer region, the power is reduced so that a negative longitudinal spherical aberration is present that at least partially cancels out the positive longitudinal spherical aberration caused by the cornea. In the aforementioned near region, a positive constant power is added to the aspherical reference power within a predetermined radial range of a virtual aspherical lens that has a predetermined base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 brings about a positive frequency deviation with respect to the aforementioned positive constant frequency. Subregion 2 yields a nearly zero frequency deviation for the aforementioned positive constant frequency. The intraocular lens according to claim 1, wherein the sub-region 3 provides a negative power deviation with respect to the positive constant power.

9. The lens comprises at least one distance region for correcting distance vision and at least one near region for correcting near vision, wherein the distance region and the near region are concentric with respect to the lens center O. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 introduces a positive frequency deviation to the virtual optical frequency profile in the near region, and the virtual optical frequency profile is an aspherical frequency profile with a constant positive frequency added. Subregion 2 provides a zero frequency deviation to the virtual optical frequency profile. Sub-region 3 is an ophthalmic lens that provides a negative power deviation to the virtual optical power profile.

10. A region concentric with the lens center O, comprising at least one distance region for correcting distance vision and at least one near region for correcting near vision, In the aforementioned near region, a positive constant power is added to a reference power having a predetermined base power at the lens center O. The aforementioned near region comprises at least three sub-regions arranged radially, Subregion 1 brings about a positive frequency deviation with respect to the aforementioned positive constant frequency. Subregion 2 yields a nearly zero frequency deviation for the aforementioned positive constant frequency. The ophthalmic lens according to claim 9, wherein the sub-region 3 provides a negative power deviation with respect to the positive constant power.

11. With respect to the area of ​​the aforementioned nearby region, The area ratio of the aforementioned sub-region 1 is 15-50%. The area ratio of the aforementioned sub-region 2 is 30-70%. The intraocular lens according to claim 4, wherein the area ratio of the subregion 3 is 15 to 50%.

12. The mean value of the positive frequency deviation in the sub-region 1 is 0.3 to 1D. The mean value of the approximate zero frequency deviation in the sub-region 2 is -0.2 to 0.2D. The intraocular lens according to claim 10, wherein the average value of the negative frequency deviation in the subregion 3 is -0.3D or less.

13. The intraocular lens according to claim 1, wherein the positive constant power is 1 to 4D.

14. The intraocular lens according to claim 1, wherein the arrangement of the sub-regions 1 to 3 when viewed radially from the lens center O is one of the following: ・Sub-area 1, sub-area 2, sub-area 3 ・Sub area 1, sub area 3, sub area 2 ・Sub area 2, sub area 1, sub area 3 ・Sub area 2, sub area 3, sub area 1 ・Sub area 3, sub area 1, sub area 2 ・Sub area 3, sub area 2, sub area 1

15. The intraocular lens according to claim 1, wherein the optical power changes continuously, discontinuously, or with a power jump in at least one of the following: the boundary between two sub-regions of the near region, and the boundary between the near region and the far region when the near region and the far region are adjacent.

16. The intraocular lens according to claim 1, wherein in at least one of the following: the boundary between different sub-regions within the near region, and the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, the change in power is continuous or discontinuous, or the power jumps.

17. The intraocular lens according to claim 5, wherein the diameter in a plan view of the aforementioned near region is 1.2 to 2.5 mm.

18. The intraocular lens according to claim 1, wherein in at least one of the following: the boundary between different sub-regions within the near region described in claim 6; the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent; and the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent, the change in power is continuous or discontinuous, or the power jumps.

19. The intraocular lens according to claim 1, wherein the inner diameter in a plan view of the near region according to claim 6 is 1.4 to 2.2 mm and the outer diameter is 2.6 to 3.5 mm.

20. The aforementioned ophthalmic lens is a phakic intraocular lens. The aforementioned near region includes the lens center O, The aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O. The ophthalmic lens according to claim 9, wherein the diameter of the near region in a planar view is 1.4 to 3 mm.

21. The aforementioned ophthalmic lens is a phakic intraocular lens. The aforementioned distant region includes the lens center O. The near region is located outside the far region when the radial direction is taken outward from the lens center O. It is positioned outside the aforementioned near region and includes an outer region that corrects distance vision, The ophthalmic lens according to claim 9, wherein the inner diameter in the near region in a plan view is 1.6 to 2.4 mm and the outer diameter is 2.9 to 3.6 mm.

22. The aforementioned ophthalmic lens is a contact lens. The aforementioned near region includes the lens center O, The aforementioned far region is located outside the aforementioned near region when the radial direction is taken outward from the lens center O. The ophthalmic lens according to claim 9, wherein the diameter of the near region in a planar view is 1.4 to 3 mm.

23. The aforementioned ophthalmic lens is a contact lens. The aforementioned distant region includes the lens center O. The near region is located outside the far region when the radial direction is taken outward from the lens center O. It is positioned outside the aforementioned near region and includes an outer region that corrects distance vision, The ophthalmic lens according to claim 9, wherein the inner diameter in the near region in a plan view is 1.6 to 2.4 mm and the outer diameter is 2.9 to 3.6 mm.

24. The intraocular lens according to claim 1, wherein the intraocular lens is a toric lens.

25. In the sub-region 1, the optical power decreases as the radial distance to the lens center O increases, and the decrease in the sub-region 1 is concave; in the sub-region 3, the optical power decreases as the radial distance to the lens center O increases, and the decrease in the sub-region 3 is convex, as described in claim 4.

26. With respect to the area of ​​the aforementioned nearby region, The area ratio of the aforementioned sub-region 1 is 15-50%. The area ratio of the aforementioned sub-region 2 is 30-70%. The ophthalmic lens according to claim 9, wherein the area ratio of the sub-region 3 is 15 to 50%.

27. The mean value of the positive frequency deviation in the sub-region 1 is 0.3 to 1D. The mean value of the approximate zero frequency deviation in the sub-region 2 is -0.2 to 0.2D. The ophthalmic lens according to claim 10, wherein the average value of the negative frequency deviation in the subregion 3 is -0.3D or less.

28. The ophthalmic lens according to claim 9, wherein the positive constant power is 1 to 4D.

29. The ophthalmic lens according to claim 9, wherein the arrangement of the sub-regions 1 to 3 when viewed radially from the lens center O is one of the following: ・Sub-area 1, sub-area 2, sub-area 3 ・Sub area 1, sub area 3, sub area 2 ・Sub area 2, sub area 1, sub area 3 ・Sub area 2, sub area 3, sub area 1 ・Sub area 3, sub area 1, sub area 2 ・Sub area 3, sub area 2, sub area 1

30. The ophthalmic lens according to claim 9, wherein the optical power changes continuously, discontinuously, or with a power jump in at least one of the following: the boundary between two sub-regions of the near region, and the boundary between the near region and the far region when the near region and the far region are adjacent.

31. The ophthalmic lens according to claim 9, wherein in at least one of the following: the boundary between different sub-regions within the near region, and the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, the change in power is continuous or discontinuous, or the power jumps.

32. The ophthalmic lens according to claim 9, wherein in the sub-region 1, the optical power decreases as the radial distance to the lens center O increases, and the decrease in the sub-region 1 is concave, and in the sub-region 3, the optical power decreases as the radial distance to the lens center O increases, and the decrease in the sub-region 3 is convex.

33. An optical design method for designing an intraocular lens according to any one of claims 1 to 8, 11 to 19, 24 and 25, or an ophthalmic lens according to any one of claims 9, 10, 20 to 23 and 26 to 32.

34. The steps include designing an aspherical power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases, A step of designing a near region by adding a positive constant frequency to the region of the designed aspherical frequency profile, wherein at least a portion of the designed aspherical frequency profile outside the near region forms a far region. A step of modifying the optical power in the near region in order to design at least three sub-regions, wherein in sub-region 1, the power is increased to design a positive power deviation to the designed aspherical power profile to which a constant positive power is added; in sub-region 2, the power is left unchanged to design a zero power deviation to the designed aspherical power profile to which a constant positive power is added; and in sub-region 3, the power is decreased to design a negative power deviation to the designed aspherical power profile to which a constant positive power is added. The optical design method according to claim 33, including the method described in claim 33.

35. A method for manufacturing an intraocular lens or ophthalmic lens designed by the optical design method described in claim 33, comprising manufacturing the lens by turning, molding, or 3D printing, at least one of these methods.

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