Extended depth-of-focus ophthalmic lens, method for designing same, and method for manufacturing same

Abstract

The present invention provides an intraocular lens and related art thereof, the intraocular lens being provided with at least one far region for correcting farsightedness and at least one near region for correcting nearsightedness, the far and near regions being concentric with a lens center O. In the far region, the lens power is reduced so as to provide a negative longitudinal spherical aberration for at least partially offsetting a positive longitudinal spherical aberration caused by the cornea. In the near region, a positive constant power is added to an aspherical reference power across a prescribed range in a radial direction of a virtual aspherical lens that has a prescribed base power at the lens center O and that fully offsets the positive longitudinal spherical aberration caused by the cornea. The near region is provided with at least three sub-regions side by side in the radial direction, among which a sub-region 1 provides a positive power deviation with respect to a positive constant power, a sub-region 2 provides a substantially zero power deviation with respect to a positive constant power, and a sub-region 3 provides a negative power deviation with respect to a positive constant power.

Description

Extended depth of focus ophthalmic lens, design method thereof, and manufacturing method thereof

[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 distance vision and an add power for correcting near and / or intermediate vision.

[0002] The present invention relates to a novel optical design for an intraocular lens (IOL), a phakic intraocular lens (or implantable contact lens (ICL), the term "implantable" being omitted hereafter), that can be used to correct not only distance vision but also near and / or intermediate vision. This disclosure will be described in detail only with respect to intraocular lenses, as they are representative of various ophthalmic lenses. However, the present invention is applicable to the optical designs of phakic intraocular lenses and contact lenses as well.

[0003] In addition to correcting distance vision, IOLs with add power can also be used to correct near and / or intermediate vision in aphakic patients.

[0004] In this specification, the term "add power" is also referred to as "positive power addition." The use of the term "add power" is not limited to ophthalmic lenses that have an add power (ADD) as a prescription value.

[0005] As used herein, the term "extended vision range IOL" refers to an IOL that has a base power to correct distance vision and an add power to correct near and / or intermediate vision. Extended vision range IOLs are also referred to herein as "EVR IOLs."

[0006] Although infinity is exemplified as far vision in this specification, viewing an object at a finite distance (1.5 m or more (far distance)) rather than infinity may also be considered. Intermediate vision may also be considered as viewing an object at a distance of 1.5 m to 50 cm (intermediate distance). Near vision may also be considered as viewing an object at a distance of 50 cm or less (near distance). In either case, viewing a distance farther than near vision is called intermediate vision, and viewing a distance farther than intermediate vision is called far vision.

[0007] The lens center O refers to the geometric center or optical center of the intraocular lens. In this specification, the case where the geometric center and the optical center coincide is illustrated. The refractive power at this lens center O is referred to as 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 as bifocal or multifocal. Bifocal intraocular lenses (bifocal lenses) implanted in the eyes of aphakic patients tend to have two primary focal lengths. One focal length is designed to focus light rays from far distances to correct distance vision (distance vision). The other focal length is designed to focus light rays from near distances to correct near vision (near vision). Multifocal intraocular lenses (multifocal lenses) implanted in the eyes of aphakic patients have three or more focal lengths. Typically, one focal length is used to correct distance vision, and two or more focal lengths are used to correct near and intermediate vision.

[0009] The first focal length of an EVR IOL used to correct distance vision corresponds to the base power of the IOL. That is, the first focal length corresponds to the prescribed spherical power (labeled refractive power) of the IOL, e.g., 20.0 D (unit: diopters, hereinafter). The second focal length used to correct near and / or intermediate vision corresponds to the sum of the base power (labeled refractive power) and the add power of the IOL. For example, if the IOL has an add power of 3.0 D, the second focal length corresponds to a power value of 23.0 D (the sum of the labeled refractive power of 20.0 D and the add power of 3.0 D).

[0010] Refractive EVR IOLs can be classified into three IOL types (for example, Patent Document 1, WO 2021 / 111821, filed by the present applicant). For details not described in this specification, please refer to the details described in Patent Document 1. One of these three types is, for example, an enhanced monofocal IOL (commonly known as an EM-IOL), which has one or more added positive constant powers of 1.25D or less. Another type is a multifocal lens (for example, one or more added positive constant powers, i.e., an add power of 2.5D or more). Another type is an extended depth-of-focus IOL (commonly known as an EDOF), which is an intermediate lens between the two types (for example, one or more added positive constant powers greater than 1.25D but less than 2.5D (e.g., 2D)). Note that the classification in this paragraph is merely an example, and for example, a case where there are two types of positive fixed powers, one value being 1.25D or less and the other value being greater than 1.25D and less than 2.5D, is not excluded from the present invention.

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

[0012] A disadvantage of bifocal lenses is the narrow range of near distances at which an aphakic patient's eye can clearly see objects, resulting in a short near-distance range of near vision. This narrow near-distance range is particularly evident in bifocal IOLs, which have a relatively constant add power in the zone on the lens dedicated to correcting near vision. Furthermore, bifocal IOLs with a relatively large zone dedicated to correcting near vision have a disadvantage in that the lens zone dedicated to correcting distance vision is small, resulting in a loss of image quality (image sharpness and contrast) for distance vision.

[0013] When implanted in the eye of an aphakic patient, a bifocal EVR IOL with strong bifocal properties can provide the wearer with sharp images of two objects at different distances. One sharp far image (the image of an object located at a distance reconstructed on the retina) and one sharp near image (the image of an object located at a near distance reconstructed on the retina) are visible to the aphakic patient. However, an object located very close to the cornea can be clearly seen by the aphakic patient's eye if only light rays from that object are focused on the retina by the corneal optics and the EVR IOL. To be focused on the retina, the distance of the nearby object in front of the cornea must be within a specific near distance range. This specific near distance range in which near objects can still be seen is clearly related to the EVR IOL's add power and power profile (also called radial power or power distribution). A power profile is, for example, a graph with radius (in mm) on the horizontal axis and 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 of the IOL.

[0014] There are many bifocal EVR IOLs disclosed in the patent literature.

[0015] US Pat. No. 4,636,211 discloses a bifocal IOL with a two-zone design, which includes a central region for correcting near vision and an annular region surrounding the central region for correcting distance vision.

[0016] Patent document 3 (US Pat. No. 5,192,317) discloses a three-zone IOL having 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 (US Pat. No. 4,813,955) discloses a four-zone intraocular lens having a central region, a first annular region, a second annular region, and a third annular region each having the function of correcting distance vision, far vision, and near vision.

[0018] Patent Document 5 (WO 1997 / 26843) discloses a five-zone IOL with a central zone, a second annular zone, and a fourth annular zone for correcting distance vision, and a first annular zone and a third annular zone for correcting near vision. The advantage of a bifocal lens is that it can form two sharp images on the retina, one of which is a sharp image of a limited range of near objects, and the other is a sharp image of a far-distance object.

[0019] Other patents disclose IOLs with one or more zones for correcting distance vision and one or more zones for correcting near vision, with one or more transition zones between the zones for correcting distance vision and the zones for correcting near vision. Examples of these patents are U.S. Pat. No. 5,112,351 (US Pat. No. 5,112,351), U.S. Pat. No. 5,112,312 (EP Pat. No. 0,942,312 B1), and U.S. Pat. No. 6,457,826 (US Pat. No. 6,457,826). The IOLs described in these patents can improve image quality for intermediate vision. However, image quality for near vision is lower than that of bifocal IOLs. Image quality for distance vision is also lower than that of bifocal lenses. The reason for this poor image quality for distance and near vision is due to the transition zone or power of the transition zone, as characterized in these patents. That is, light rays from intermediate distances that are focused on the retina reduce the number of light rays from near distances, which reduces the number of light rays from far distances that would reconstruct the image for distance vision on the retina.

[0020] Common bifocal EVR IOLs have two-zone and three-zone optical designs. Two-zone IOLs have two zones: an inner zone (the first zone, including the center of the lens) with a power greater than the power of the outer zone, which is used to correct near vision. The outer zone has a base power for distance vision correction. Three-zone IOLs have three zones: an inner zone (the first zone, including the center of the lens) with a power greater than the base power, which is used to correct near vision. An annular zone surrounding the first zone with a power greater than the base power, which is used to correct near vision. A third zone (the third zone, including the second zone, is used to correct distance vision). The optical characteristics and performance of bifocal two-zone and bifocal three-zone IOLs for correcting distance and near vision in aphakic eyes depend on the add power and power profile of the IOL.

[0021] WO2021 / 111821 publication US4636211 specification US5192317 specification US4813955 specification WO97 / 026843 publication US5112351 specification EP0942312B1 specification US6457826 specification

[0022] For example, new power profiles for bifocal EVR IOLs are disclosed herein, which can include two-zone and three-zone optical designs.

[0023] The power profiles disclosed herein can improve the optical properties and performance of, for example, bifocal EVR IOLs for correcting distance and near vision in aphakic patients.

[0024] The object of one aspect of the present invention is to increase the depth of focus for near and / or intermediate vision and / or improve the image quality for distance vision compared to the specific examples described below to which the present invention is not applied (denoted as "Flat").

[0025] According to a first aspect of the present invention, there is provided an intraocular lens comprising at least one distance region for correcting vision for distance vision and at least one near region for correcting vision for near vision, the distance region and the near region being concentric with a lens center O, and in the distance region, the optical power of the lens decreases as the radial distance to the lens center O increases, the near region comprising at least three subregions arranged radially side by side, wherein subregion 1 provides a positive power deviation to a virtual optical power profile in the near region, the virtual optical power profile being an aspheric power profile to which a positive constant power is added, subregion 2 provides a zero power deviation to the virtual optical power profile, and subregion 3 provides a negative power deviation to the virtual optical power profile. In other words, subregion 1 provides a positive power deviation for a positive constant power, subregion 2 provides a zero power deviation for a positive constant power, and subregion 3 provides a negative power deviation for a positive constant power. It has been found that an IOL having these three subregions in the near region leads to an extended depth of focus for near vision. Preferably, in subregion 2, the power deviation is considered to be zero if the average power deviation in subregion 2 is in the range of -0.2 to 0.2D. For this reason, a zero power deviation can also be considered to be a nearly zero power deviation. The distance region, in which the optical power of the lens decreases with increasing radial distance to the lens center O, can also be considered a decreasing power distance region. Preferably, in the distance region, the optical power of the lens decreases with increasing radial distance to the lens center O, i.e., the distance region decreases in power to at least partially offset the positive vertical spherical aberration of the human cornea with negative vertical spherical aberration. Thus, preferably, in the distance 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 vertical spherical aberration of the human cornea is at least partially offset. This allows for improved distance vision. In one example, the human cornea is an average human cornea.Thus, in one example, the distance region decreases in power, i.e., the optical power decreases with increasing radial distance to the lens center in order to at least partially offset the positive vertical spherical aberration of the average human cornea with negative vertical spherical aberration. The average human cornea is an 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 cornea listed in Table 1 herein. Preferably, the aspheric power profile (which can also be considered an aspheric reference power) of the virtual optical power profile 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 the virtual optical power profile, which can also be considered a power profile of a virtual aspheric lens. In other words, the near zone has a base power at the lens center O, and a positive constant power is added to the aspherical reference power during a predetermined radial range of the virtual aspherical lens. The virtual optical power profile in the near zone is preferably such that the positive vertical spherical aberration of the human cornea, in particular the average human cornea, is offset. This offset can be partial or complete. Thus, in one embodiment, the near zone has a predetermined base power at the lens center O, and a positive constant power is added to the aspherical reference power during a predetermined radial range of the virtual aspherical lens to fully offset the positive vertical spherical aberration of the average human cornea.Thus, the first aspect is an intraocular lens having regions concentric with the lens center O, the region comprising at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, wherein the power is reduced in the distance region to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region has a predetermined base power at the lens center O and a positive fixed power is added to an 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 offsets the positive vertical spherical aberration caused by the cornea, the near region having at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation from the positive fixed power, subregion 2 provides a zero power deviation, particularly a nearly zero power deviation, from the positive fixed power, and subregion 3 provides a negative power deviation from the positive fixed power. The power reduction of the aspheric power profile in the near zone is preferably equal to the power reduction in the distance zone, in other words, in one example, the optical power in the distance zone decreases with increasing radial distance to the lens center in line with the reduction of the aspheric power profile of the virtual optical power profile in the near zone.

[0026] The near distance region includes the lens center O, and the far distance region may be positioned outward from the near distance region. Therefore, the second aspect comprises: a near region that is concentric with the lens center O, includes the lens center O, and corrects visual acuity for near vision; and a far region that is located radially outward from the lens center O and corrects visual acuity for far vision, wherein the power is reduced in the far region to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region has a predetermined base power at the lens center O and a positive fixed power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens that completely offsets the positive vertical spherical aberration caused by the cornea, and the near region comprises at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation from the positive fixed power, and subregion 2 provides a zero power deviation, particularly a nearly zero power deviation, from the positive fixed power, Sub-region 3 is an intraocular lens that provides a negative power deviation relative to the positive constant power.

[0027] According to a third aspect of the present invention, a lens comprises a distance region including a lens center O and correcting vision for distance vision, and an outer region disposed radially outward from the lens center O outside a near region correcting vision for near vision, and correcting vision for distance vision, wherein the distance region, the near region, and the outer region are concentric with the lens center O, i.e., starting from the lens center O and facing away from the lens center O in the radial direction, and the order of the regions is the distance region, the near region, and the outer region, wherein in the outer region, the optical power of the lens decreases as the radial distance to the lens center O increases, and the near region comprises at least three sub-regions arranged radially side by side, wherein sub-region 1 provides a positive power deviation to a virtual optical power profile in the near region, which is the addition of an aspherical power profile and a positive fixed power, i.e., the virtual optical power profile is an aspherical power profile to which a positive fixed power has been added, An intraocular lens is provided in which subregion 2 provides a zero power deviation relative to the virtual optical power profile, and subregion 3 provides a negative power deviation relative to the virtual optical power profile. In other words, subregion 1 provides a positive power deviation relative to a positive constant power, subregion 2 provides a zero power deviation relative to a positive constant power, and subregion 3 provides a negative power deviation relative to a positive constant power. An IOL having these three subregions in the near region can lead to an expanded depth of focus for near vision, and the inner distance region, combined with the outer distance region, can lead to improved image quality for distance vision. Preferably, in subregion 2, a power deviation is considered to be zero if the average power deviation in subregion 2 is in the range of -0.2 to 0.2D. For this reason, a zero power deviation can also be considered to be a nearly zero power deviation. The distance region, in which the optical power of the lens decreases with increasing radial distance to the lens center O, can also be considered a distance region of decreasing power. Preferably, in the outer region, the optical power of the lens decreases with increasing radial distance to the lens center O, i.e., the outer region decreases in power in order to at least partially offset the positive longitudinal spherical aberration of the human cornea with a 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 vertical spherical aberration of the human cornea is at least partially offset. This allows for further improved distance vision. As explained above, in one example, the human cornea is an average human cornea. Thus, in one example, the outer region decreases in power, i.e., the optical power decreases with increasing radial distance to the lens center, in order to at least partially offset the positive vertical spherical aberration of the average human cornea with negative vertical spherical aberration. The average human cornea is an 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 may correspond to the corneas listed in Table 1 herein. Preferably, the aspheric power profile (which may also be considered an aspheric reference power) of the virtual optical power profile can be described as having a base power at the lens center O, and in the near zone, a positive constant power is added to the aspheric reference power to form a virtual optical power profile that may also be considered a power profile of a virtual aspheric lens. In other words, the near zone has a base power at the lens center O, and a positive constant power is added to the aspheric reference power within a predetermined radial range of the virtual aspheric lens. The virtual optical power profile in the near zone is preferably such that the positive vertical spherical aberration of the human cornea, particularly the average human cornea, is compensated for. This compensation may be partial or complete. Thus, in one embodiment, the near zone has a predetermined base power at the lens center O, and a positive constant power is added to the aspheric reference power within a predetermined radial range of the virtual aspheric lens to fully compensate for the positive vertical spherical aberration of the average human cornea.Therefore, a third aspect of the present invention is a lens comprising: a distance region concentric with a lens center O, the distance region including the lens center O and correcting visual acuity for distance vision; a near region disposed radially outward from the lens center O and correcting visual acuity for near vision; and an outer region disposed radially outward from the near region and correcting visual acuity for distance vision, wherein the outer region is reduced in power to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region has a predetermined base power at the lens center O and a positive fixed power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens that completely offsets the positive vertical spherical aberration caused by the cornea, and the near region comprises at least three sub-regions arranged radially, and sub-region 1 provides a positive power deviation for the positive fixed power, The intraocular lens has sub-region 2 providing zero power deviation, particularly nearly zero power deviation, relative to the positive constant power, and sub-region 3 providing a negative power deviation relative to the 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 reduction of the aspherical power profile of the virtual optical power profile in the near region. Furthermore, preferably, the power reduction with increasing radial distance in the outer region is equal to the power reduction with increasing radial distance in the far region. In particular, in the outer region and the far region, the optical power can decrease as the radial distance to the lens center O increases, in line with the reduction of the aspherical power profile of the virtual optical power profile in the near region. In other words, in one example, the power reduction in the outer and distance regions can be represented by an aspheric power profile of a virtual optical power profile in the near region, i.e., in one example, the IOL has an aspheric power profile extending from the lens center O through the distance region, the near region, and the outer region, and in the near region, a positive constant power is added to the aspheric power profile.

[0028] According to a fourth aspect of the present invention, there is provided an ophthalmic lens comprising at least one distance region for correcting vision for distance vision and at least one near region for correcting vision for near vision, the distance region and the near region being concentric about a lens center O, the near region comprising at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation to a virtual optical power profile in the near region, the virtual optical power profile being an aspheric power profile to which a positive fixed power is added, subregion 2 provides a zero power deviation to the virtual optical power profile, and subregion 3 provides a negative power deviation to the virtual optical power profile. In other words, subregion 1 provides a positive power deviation to the positive fixed power, subregion 2 provides a zero power deviation to the positive fixed power, and subregion 3 provides a negative power deviation to the positive fixed power. An ophthalmic lens having these three sub-zones in the near zone leads to an extension of the depth of focus for near vision. Preferably, the aspheric power profile (which can also be considered as an aspheric reference power) of the virtual optical power profile can be expressed as having a base power at the lens center O, and in the near zone, a positive constant power is added to the aspheric reference power to form a virtual optical power profile that can also be considered as the power profile of a virtual aspheric lens. In other words, in the near zone, a positive constant power is added to a reference power having a predetermined base power at the lens center O. Therefore, a fourth aspect is an ophthalmic lens comprising regions concentric with the lens center O, at least one distance region for correcting vision for distance vision and at least one near region for correcting vision for near vision, wherein in the near region, a positive fixed power is added to a reference power having a predetermined base power at the lens center O, and the near region comprises at least three sub-regions arranged radially, wherein sub-region 1 provides a positive power deviation from the positive fixed power, sub-region 2 provides a zero power deviation, particularly a substantially zero power deviation, from the positive fixed power, and sub-region 3 provides a negative power deviation from the positive fixed power.Preferably, in subregion 2, the power deviation is considered to be zero when the average power deviation in subregion 2 is in the range of -0.2 to 0.2D. For this reason, zero power deviation can also be considered to be approximately zero power deviation. In one example, also in the fourth aspect, in the distance region, the optical power of the lens decreases, in particular decreases continuously, as the radial distance to the lens center O increases. The distance region in which the optical power of the lens decreases as the radial distance to the lens center O increases can also be considered to be a distance region in which the power decreases. In one example, in the distance region, the optical power of the lens decreases as the radial distance to the lens center O increases, i.e., the distance region decreases in power to at least partially offset the positive longitudinal spherical aberration of the human cornea with negative longitudinal spherical aberration. Therefore, in one example, the decrease in optical power with increasing radial distance to the lens center in the distance zone, i.e., the corresponding power profile, is such that the positive vertical spherical aberration of the human cornea is at least partially offset. This allows for further improved distance vision. In one example, the power decrease of the aspheric power profile in the near zone is equal to the power decrease in the distance zone. In other words, in one example, the optical power decreases in the distance zone as the radial distance to the lens center increases, in line with the decrease in the aspheric power profile of the virtual optical power profile in the near zone.

[0029] A fifth aspect is an intraocular lens according to any one of the first to fourth aspects, wherein the area ratio of the sub-region 1 to the area of ​​the near region is 15 to 50%, the area ratio of the sub-region 2 is 30 to 70%, and the area ratio of the sub-region 3 is 15 to 50%.

[0030] A sixth aspect is the intraocular lens according to any one of the first to fifth aspects, wherein the average value of the positive power deviation in the subregion 1 is 0.3 to 1 D, the average value of the near-zero power deviation in the subregion 2 is -0.2 to 0.2 D, and the average value of the anterior negative power deviation in the subregion 3 is -0.3 D or less.

[0031] A seventh aspect is the intraocular lens according to any one of the first to sixth aspects, wherein the positive fixed power is 1 to 4D.

[0032] An eighth aspect is the intraocular lens according to any one of the first to seventh aspects, wherein the order of arrangement of the subregions 1 to 3 when viewed in the radial direction from the lens center O is one of the following: subregion 1, subregion 2, subregion 3 subregion 1, subregion 3, subregion 2 subregion 2, subregion 1, subregion 3 subregion 2, subregion 3, subregion 1 subregion 3, subregion 1, subregion 3, subregion 3, subregion 2, subregion 1

[0033] A ninth aspect is the ophthalmic lens according to any one of the first to eighth aspects, wherein, relative to the area of ​​the near region, the area ratio of the sub-region 1 is 15 to 50%, the area ratio of the sub-region 2 is 30 to 70%, and the area ratio of the sub-region 3 is 15 to 50%.

[0034] A tenth aspect is the ophthalmic lens according to any one of the first to ninth aspects, wherein the average value of the positive power deviation in the sub-region 1 is 0.3 to 1 D, the average value of the near-zero power deviation in the sub-region 2 is -0.2 to 0.2 D, and the average value of the anterior negative power deviation in the sub-region 3 is -0.3 D or less.

[0035] An eleventh aspect is the ophthalmic lens according to any one of the first to tenth aspects, wherein the positive fixed power is 1 to 4D.

[0036] A twelfth aspect is the ophthalmic lens according to any one of the first to eleventh aspects, wherein the order of arrangement of the subregions 1 to 3 when viewed in the radial direction from the lens center O is one of the following: Subregion 1, subregion 2, subregion 3 Subregion 1, subregion 3, subregion 2 Subregion 2, subregion 1, subregion 3 Subregion 2, subregion 3, subregion 1 Subregion 3, subregion 1, subregion 2 Subregion 3, subregion 2, subregion 1

[0037] According to a thirteenth aspect of the present invention, there is provided an intraocular lens according to any one of the first to twelfth aspects, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of the boundaries between two sub-regions of the near region and, when the near region and the far region are adjacent, at the boundary between the near region and the far region. Thus, there are several boundaries, i.e., 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 power is continuous, discontinuous, or a power jump. A power jump is preferably defined as a vertical change in a graph showing the optical power as a function of 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 power change threshold. Preferably, the predetermined power change threshold is 100 D / mm. Therefore, preferably, if the power change at a boundary is 100 D / mm or more, it is considered to be abrupt, and therefore discontinuous. A power change is considered continuous if it is not discontinuous. Therefore, the change in optical power at each boundary can also be defined as a) abrupt, b) a power jump, or c) neither abrupt nor a power jump. In one example, abrupt power changes can also be considered abrupt power changes. In one embodiment, the intraocular lens according to any one of the first to twelfth aspects may be provided, wherein the power change is smooth or abrupt, or the power jump occurs at at least one of the boundaries between two different subregions and the boundaries between each of the subregions 1 to 3 and the far region when the near region and the far region are adjacent to each other. The power variation can be considered smooth if the curve representing the power dependence on the radial distance to the lens center O is differentiable, in other words, if there are no "corners" in the curve.

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

[0039] In a fifteenth aspect, the intraocular lens according to any one of the first to fourteenth aspects is characterized in that the diameter of the near region in plan view is 1.2 to 2.5 mm. Therefore, the diameter of the near region, i.e., the radial or diametric expansion of the near region, is in the range of 1.2 to 2.5 mm.

[0040] A sixteenth aspect is the intraocular lens according to any one of the first to fifteenth aspects, wherein the change in power is continuous or discontinuous, or the power jumps at at least one of the boundaries between different sub-regions within the near region, the boundary between any of 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 sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent.

[0041] A seventeenth aspect is the intraocular lens according to any one of the first to sixteenth aspects, wherein the inner diameter of the near region in a planar view is 1.4 to 2.2 mm, and the outer diameter is 2.6 to 3.5 mm. Therefore, the inner diameter of the near 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 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] An eighteenth aspect is the ophthalmic lens according to any one of the first to seventeenth aspects, wherein the ophthalmic lens is a phakic intraocular lens, the near region includes a lens center O, the far region is disposed radially outward from the lens center O, and the diameter of the near region in a planar view is 1.4 to 3 mm. Therefore, the diameter of the near region, i.e., the radial or diametric expansion of the near region, can be in the range of 1.4 to 3 mm, particularly 1.4 to 3.0 mm.

[0043] A nineteenth aspect is the ophthalmic lens according to any one of the first to eighteenth aspects, wherein the ophthalmic lens is a phakic intraocular lens, the far region includes a lens center O, the near region is disposed radially outward from the lens center O, and an outer region is disposed radially outward from the near region and corrects visual acuity for far vision, and the near region 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. Therefore, the inner diameter of the near 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 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] A twentieth aspect is the ophthalmic lens according to any one of the first to nineteenth aspects, wherein the ophthalmic lens is a contact lens, the near region includes a lens center O, the far region is disposed radially outward from the lens center O, and the diameter of the near region in a plan view is 1.4 to 3 mm. Therefore, the diameter of the near region, i.e., the radial or diametric expansion of the near region, can be in the range of 1.4 to 3 mm, particularly 1.4 to 3.0 mm.

[0045] A twenty-first aspect is the ophthalmic lens according to any one of the first to twentieth aspects, wherein the ophthalmic lens is a contact lens, the distance region includes a lens center O, the near region is disposed radially outward from the lens center O, and an outer region is disposed radially outward from the near region and corrects vision for distance vision, and the inner diameter of 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. Therefore, the inner diameter of the near 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 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.

[0046] According to a 22nd aspect of the present invention, there is provided an intraocular lens according to any one of aspects 1 to 21, wherein the intraocular lens is a toric lens. In a preferred embodiment of any of the above aspects, in the first sub-region, the optical power decreases as the radial distance to the lens center O increases. Furthermore, preferably, the decrease in the first sub-region is concave, i.e., follows a concave curve. In the third sub-region, the optical power preferably decreases as the radial distance to the lens center O increases. Furthermore, preferably, the decrease in the third sub-region is convex, i.e., follows a convex curve. It is also preferred that the third sub-region comprises several, in particular two, sub-regions, wherein in each sub-region the optical power decreases as the radial distance to the lens center O increases. In one example, in each sub-region the decrease is convex, i.e., follows a convex curve. The previous paragraph preferably applies to intraocular lenses and / or ophthalmic lenses. It has been found that an intraocular lens or ophthalmic lens having these sub-zones in the near zone can lead to a further extension of the depth of focus for near vision. Preferably, a power profile or power curve is considered concave (specifically, concave in the negative direction of the vertical axis of the power profile) if, as one moves along the power profile or power curve in a direction away from the lens center O, it points to the right (when the vertical axis is power and the horizontal axis is radial distance, the power profile curves clockwise, i.e., from 12 o'clock to 3 o'clock). Preferably, a power profile or power curve is considered convex (specifically, convex in the negative direction of the vertical axis of the power profile) if, as one moves along the power profile or power curve in a direction away from the lens center O, it points to the left (when the vertical axis is power and the horizontal axis is radial distance, the power profile curves counterclockwise, i.e., from 9 o'clock to 6 o'clock). Hereinafter, when the vertical axis represents power and the horizontal axis represents radial distance, the concavities and convexities in the power profile will be defined in the same way as above.

[0047] According to a twenty-third aspect of the present invention, there is provided an optical design method for an intraocular lens according to any one of the first to twenty-second aspects. In one example, an optical design method includes the steps of: designing an aspheric power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases; adding a positive constant power to a region of the designed aspheric power profile to design a near region, wherein at least a portion of the designed aspheric power profile outside the near region forms a far region; and changing the optical power in the near region to design at least three sub-regions, wherein in sub-region 1, the power is increased to design a positive power deviation for the designed aspheric power profile to which the positive constant power has been added; in sub-region 2, the power is not changed to design a zero power deviation for the designed aspheric power profile to which the positive constant power has been added; and in sub-region 3, the power is decreased to design a negative power deviation for the designed aspheric power profile to which the positive constant power has been added. Preferably, the aspheric power profile is designed to provide 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] A twenty-fourth aspect is a method for manufacturing an intraocular lens, in which an intraocular lens designed by the optical design method for an intraocular lens according to the twenty-third aspect is manufactured by at least one of lathing, molding, and 3D printing.

[0049] A twenty-fifth aspect is the ophthalmic lens according to any one of the first to twenty-second aspects, wherein the ophthalmic lens is a toric lens.

[0050] According to a twenty-sixth aspect of the present invention, there is provided a method for optically designing an ophthalmic lens according to any one of the first to twenty-second aspects. In one example, an optical design method includes the steps of: designing an aspheric power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases; adding a positive constant power to a region of the designed aspheric power profile to design a near region, wherein at least a portion of the designed aspheric power profile outside the near region forms a far region; and changing the optical power in the near region to design at least three sub-regions, wherein in sub-region 1, the power is increased to design a positive power deviation for the designed aspheric power profile to which the positive constant power has been added; in sub-region 2, the power is not changed to design a zero power deviation for the designed aspheric power profile to which the positive constant power has been added; and in sub-region 3, the power is decreased to design a negative power deviation for the designed aspheric power profile to which the positive constant power has been added. Preferably, the aspheric power profile is designed to provide 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] A twenty-seventh aspect is a method for manufacturing an ophthalmic lens, in which an ophthalmic lens designed by the optical design method for an ophthalmic lens according to the twenty-sixth aspect is manufactured by at least one of lathing, molding, and 3D printing.

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

[0053] 3A shows an aspheric EDOF-IOL of the prior art (referred to herein as "Flat"); FIG. 1B shows a power profile when the vertical axis (unit: D) ​​in FIG. 1A is changed to add power; FIG. 1C shows a power profile when the vertical axis (unit: D) ​​in FIG. 1A is changed to total power; FIG. 1D shows how light rays from an intermediate distance are focused on the retina by the cornea and the EDOF of FIG. 1; FIG. 3E shows how the range of intermediate distances at which objects are clearly visible is wider than the range in FIG. 3A; FIG. 3F shows a power profile of a two-zone EDOF (corresponding to embodiment 1); FIG. 3G shows a power profile of a two-zone EDOF (another example corresponding to embodiment 1); FIG. 5A shows a power profile when the vertical axis (unit: D) ​​in FIG. 5A is changed to add power; FIG. 3H shows a power profile of a two-zone EDOF (yet another example corresponding to embodiment 1); FIG. 5C shows a power profile when the vertical axis (unit: D) ​​in FIG. 5C is changed to add power. 8A is a diagram showing the total power profile of the simulated eye model including the cornea and EDOF shown in FIG. 5A . FIG. 8B is a diagram showing the total power profile of the simulated eye model including the cornea and EDOF shown in FIG. 5C . FIG. 8C is a diagram showing yet another example of embodiment 1 of the present invention. FIG. 8A is a diagram showing TFR according to a pupil diameter of 2 mm at a spatial frequency of 50 lp / mm (line pairs / mm) for the simulated eye model using EDOF shown in FIG. 1 (prior art) and FIG. 7 (embodiment 1). FIG. 8A corresponds to FIG. 8A when the pupil diameter is 2.5 mm. FIG. 8A corresponds to FIG. 8A when the pupil diameter is 3 mm. FIG. 8A corresponds to FIG. 8A when the pupil diameter is 3.5 mm. FIG. 8A corresponds to FIG. 8A when the pupil diameter is 4 mm. FIG. 8A corresponds to FIG. 8A when the spatial frequency is 100 lp / mm. FIG. 9A corresponds to FIG. 9A when the pupil diameter is 2.5 mm. FIG. 9A corresponds to FIG. 9A when the pupil diameter is 3 mm. FIG. 9A corresponds to FIG. 9A when the pupil diameter is 3.5 mm. 9A is a diagram corresponding to FIG. 9A when the pupil diameter is 4 mm. FIG. 10 is a diagram showing image simulation results at each object distance when the pupil diameter is 2 mm. FIG. 11 is a diagram corresponding to FIG. 10 when the pupil diameter is 3 mm. FIG. 11 is a diagram corresponding to FIG. 10 when the pupil diameter is 4 mm. FIG. 12 is an MTF graph obtained by simulation at a long distance of 6 m and a pupil diameter of 3 mm.13A for the case of a long distance of 12 m. FIG. 13A for the case of a long distance of 25 m. FIG. 13A for the case of a long distance of 25 m. FIG. 14A for the case of a long distance of 12 m. FIG. 14A for the case of a long distance of 25 m. FIG. 14A for the case of a long distance of 25 m. FIG. 15 for the case of an image simulation result at each object distance when the pupil diameter is 2 mm. FIG. 15 for the case of an image simulation result at each object distance when the pupil diameter is 3 mm. FIG. 15 for the case of an image simulation result at each object distance when the pupil diameter is 2 mm. FIG. 18 for the case of an image simulation result at a pupil diameter of 3 mm. FIG. 20A for the case of an EM-IOL (corresponding to embodiment 2) according to the present invention. 20A (Prior Art) and FIG. 20B (Embodiment 2) show TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) for a pupil diameter of 2.5 mm for a simulated eye model using the IOL shown in FIG. 20A (Prior Art) and FIG. 20B (Embodiment 2). This figure corresponds to FIG. 21A for a pupil diameter of 3 mm. This figure corresponds to FIG. 21A for a pupil diameter of 3.5 mm. This figure corresponds to FIG. 21A for a spatial frequency of 100 lp / mm. This figure corresponds to FIG. 22A for a pupil diameter of 3 mm. This figure corresponds to FIG. 22A for a pupil diameter of 3.5 mm. This figure shows the power profile of a multifocal lens of the prior art. This figure corresponds to FIG. 23A for a multifocal lens according to the present invention (corresponding to Embodiment 3). This figure shows TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) for a pupil diameter of 2.5 mm for a simulated eye model using the IOL shown in FIG. 23A (Prior Art) and FIG. 23B (Embodiment 3). 24A when the pupil diameter is 3 mm. FIG. 24A when the pupil diameter is 3.5 mm. FIG. 24A when the spatial frequency is 100 lp / mm. FIG. 25A when the pupil diameter is 3 mm. FIG. 25A when the pupil diameter is 3.5 mm. FIG. 26A when the pupil diameter is 3.5 mm. FIG. 26B when the pupil diameter is 3 mm. FIG. 26C when the pupil diameter is 3.5 mm. FIG. 26D when the pupil diameter is 3 mm. FIG. 26E when the pupil diameter is 3.5 mm. FIG. 26F when the pupil diameter is 3 ...C when the pupil diameter is 3.5 mm.27A ; FIG. 27B ; FIG. 27C ; FIG. 27D ; FIG. 27E ; FIG. 27F ; FIG. 27G ; FIG. 27H ... 30A is a diagram integrating the patterns of FIGS. 29A to 29C . This diagram shows 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 each IOL shown in FIGS. 29A to 29C . This diagram corresponds to FIG. 30A for a pupil diameter of 3 mm. This diagram corresponds to FIG. 30A for a pupil diameter of 3.5 mm. This diagram shows the power profile of pattern b1. This diagram shows the power profile of pattern b2. This diagram shows the power profile of pattern b3. This diagram integrating the patterns of FIGS. 31A to 31C . This diagram shows 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 each IOL shown in FIGS. 31A to 31C . This diagram corresponds to FIG. 32A for a pupil diameter of 3 mm. This diagram corresponds to FIG. 32A for a pupil diameter of 3.5 mm. This diagram shows the power profile of pattern a1c1. 33A to 33D are diagrams showing the power profile of pattern a1c2, pattern a2c1, and pattern a2c2, respectively.3A to 33D . This figure shows 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 each IOL shown in FIGS. 33A to 33D . This figure corresponds to FIG. 34A for a pupil diameter of 3 mm. This figure corresponds to FIG. 34A for a pupil diameter of 3.5 mm. This figure shows the power profile of an IOL without power jump. This figure shows the power profile of a power jump IOL. This figure combines the patterns of FIGS. 35A to 35B into one. This figure shows 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 each IOL shown in FIGS. 35A to 35B . This figure corresponds to FIG. 36A for a pupil diameter of 3 mm. This figure corresponds to FIG. 36A for a pupil diameter of 3.5 mm. This figure shows the power profile of a conventional Flat setting. This figure shows the power profile of a CenterFlat setting. 38A is a diagram showing the power profile of MiddleFlat. 38B is a diagram showing the power profile of OuterFlat. 38C is a diagram combining the patterns of FIGS. 37A to 37D. 38D is a diagram showing the TFR at a spatial frequency of 50 lp / mm (line pairs / mm) for a pupil diameter of 2.5 mm for a simulated eye model using each IOL shown in FIGS. 37A to 37D. 38C is a diagram corresponding to FIG. 38A when the pupil diameter is 3 mm. 38C is a diagram corresponding to FIG. 38A when the pupil diameter is 3.5 mm. 38C is a diagram showing the power profile of OuterHigher a1c1. 38C is a diagram showing the power profile of OuterHigher a2c2. 38C is a diagram combining the patterns of FIGS. 39A to 39B. 38C is a diagram showing the TFR at a spatial frequency of 50 lp / mm (line pairs / mm) for a pupil diameter of 2 mm for a simulated eye model using each IOL shown in FIGS. 39A to 39B. 40A when the pupil diameter is 2.5 mm. FIG. 40A when the pupil diameter is 3 mm. FIG. 40A when the pupil diameter is 3.5 mm. FIG. 40A when the pupil diameter is 3.5 mm. FIG. 40B when the pupil diameter is 3.5 mm. FIG. 40C when the pupil diameter is 3.5 mm. FIG. 40D when the pupil diameter is 3.5 mm. FIG. 40E when the pupil diameter is 3.5 mm. FIG. 40F ...10 is a diagram showing a power profile of an example of a three-zone type corresponding to [Mode Group 2]. FIG. 11 is a diagram showing many further variations in which the modified example according to the fourth embodiment is extended to [Mode Group 2].

[0054] For configurations not described below, known configurations may be appropriately adopted. In particular, the contents (especially the haptics) described in a document (WO 2009 / 153873) disclosed by the present inventor may be applied to this embodiment. Furthermore, in this specification, "to" indicates 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 to B" indicate a range from A to B. Furthermore, the lens body of the intraocular lens discussed in this specification has two opposing surfaces. The surface of the lens body that comes into contact with the posterior capsule when the intraocular lens is inserted into the lens capsule can be referred to as the posterior surface, the retina-side surface, or the retina-side surface in the optical axis direction, but the term "posterior surface" will be primarily used in this specification. The other surface can be referred to as the anterior surface, the cornea-side surface, or the cornea-side surface in the optical axis direction, but the term "anterior surface" will be primarily used in this specification. The optical axis direction is also the lens thickness direction, and is the direction from the posterior surface to the anterior surface or the reverse direction. The optical axis direction is the z-axis direction. The intraocular lens viewed in the z-axis direction 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. As this embodiment, a two-zone EDOF is mainly exemplified (Embodiment 1). In this specification, "two-zone" refers to a region that exhibits lens function to achieve the wearer's prescription values, and is composed of one region (zone) that corrects near vision and includes the lens center O, and one region (zone) that corrects distance vision. Similar to this two-zone EDOF, a two-zone EM-IOL is also exemplified (Embodiment 2). Similar to this two-zone EDOF, a two-zone multifocal lens is also exemplified (Embodiment 3). In addition to this two-zone EDOF, a three-zone EDOF is also exemplified (Embodiment 1'). A three-zone EDOF refers to a region that corrects distance vision and includes the lens center O, one region (zone) that corrects near vision, and another outer region (zone) that corrects distance vision. Although not illustrated in this specification, a three-zone EM-IOL (Embodiment 2') and a three-zone multifocal lens (Embodiment 3') are also included within the technical scope of the present invention. Furthermore, various modifications relating to the behavior of the power profile in the near region for correcting near vision are also illustrated (Embodiment 4). Inventions relating to intraocular lenses including the above-mentioned embodiments are referred to as [Aspect Group 1] in this specification.

[0056] [Mode Group 2] differs from [Mode Group 1] in that it exemplifies a phakic intraocular lens or an implantable contact lens rather than a general intraocular lens.

[0057] The content common to each embodiment will be explained at the beginning as a "common embodiment."

[0058] The first aspect of the present invention in [Summary of the Invention] corresponds to [Aspect Group 1]. The second aspect of the present invention in [Summary of the Invention] corresponds to Embodiments 1 to 3 in [Aspect Group 1]. The third aspect of the present invention in [Summary of the Invention] corresponds to Embodiments 1' to 3' in [Aspect Group 1]. The fourth aspect of the present invention in [Summary of the Invention] corresponds to [Aspect Group 2]. Although the fourth aspect literally includes not only [Aspect Group 2] but also [Aspect Group 1], the fourth aspect in this specification mainly envisions [Aspect Group 2].

[0059] [Common Embodiment] Contents and common inventive concepts common to the embodiments from embodiment 1 onward will be described as common embodiments. Here, an intraocular lens belonging to [Mode Group 1] will be exemplified.

[0060] The intraocular lens of the common embodiment (and other aspects described in this specification) comprises a lens body having a lens function and a support portion that supports the lens body within the lens capsule, similar to intraocular lenses of the prior art ("Flat" in the specific examples below, and the same applies hereinafter).

[0061] In a common embodiment, the intraocular lens is defined by the refractive power (power, dioptric power) relative to the distance in the radial direction from the lens center O. In this specification, the "direction radially away from the lens center O" is defined as the "outside."

[0062] The material of the intraocular lens is not limited, and may be made of at least one of silicone, hydrophobic acrylic resin, hydrophilic acrylic resin, hydrogel, PMMA, PMMA copolymer, and copolymer of HEMA (hydroxyethyl methacrylate) containing collagen (e.g., Collamer (registered trademark)).

[0063] In the common embodiment (and other aspects described herein), the entire lens body is exemplified as an optical part having a lens function. The "lens function" here refers to the lens function described above in the outline of this embodiment, which is the function of refracting incident light beams onto the retina.

[0064] In the first to third embodiments of the first aspect group, the entire lens body is illustrated as comprising one distance zone for correcting vision for distance vision and one near zone for correcting vision for near vision. However, the present invention is not limited to this example. For example, the intraocular lens may be a three-zone intraocular lens, as in the first to third embodiments described below. Furthermore, between the distance zone and the near zone, an intermediate zone may be provided that surrounds the side zone (the distance zone or the near zone) closer to the center of the lens, or an additional zone may be provided that surrounds the distance zone or the near zone radially outward. Two or more distance zones and / or two or more near zones may also be provided. However, the power change may be continuous or discontinuous, or the power may jump between each zone and / or between the subzones described below.

[0065] "Discontinuous change in power," as the name suggests, refers to a case where, in the graph of the style of Figure 2, the change in power when moving away from the lens center O is actually discontinuous, and when the graph is expressed as a function, the change in power when moving away from the lens center O is continuous but steep, and the change in power is essentially discontinuous. Conversely, "continuous change in power" refers to a state that does not fall under "discontinuous change in power."

[0066] Regarding whether or not something is "steep," for example, a power change is considered steep when it has a rate of change of 100 D / mm or more. In other words, even if the power increases discontinuously for every 0.01 mm from a point a predetermined distance away from the lens center O, it is considered steep if it has a rate of change of 100 D / mm or more between that point and 0.05 mm. As the name suggests, a "power jump" in power refers to a state in which the power change is more than steep (in the power profile, the power change is vertical and the power change is ∞ D / mm).

[0067] In a plan view, the inner region including the lens center O (referred to as the near region in Embodiments 1 to 3) is circular, and the outer region surrounding the near region (referred to as the far region in Embodiments 1 to 3) is toric. In the case of Embodiments 1' to 3', the circular region including the lens center O is the far region, and the toric region surrounding the far region is the near region. In other aspects described in this specification, the intermediate region is a small toric shape, and the additional region is a large toric shape. Note that instead of a circular shape and / or a toric shape, the intermediate region may be an elliptical shape and / or an elliptical toric shape.

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

[0069] The distance from the lens center O is also called the radius. The solid line is the power profile of an intraocular lens according to a common embodiment (and other aspects described herein). The dashed line is the power profile of a hypothetical 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, which is the hypothetical 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 has positive refractive power. Spherical aberration increases with distance from the center of the cornea. In other words, the dashed-dotted line representing the aspherical reference power profile W is a graph of a hypothetical aspherical lens that theoretically cancels out all of the positive vertical spherical aberration (axial aberration in the depth direction of the optical axis) caused by the cornea. Hereinafter, the various lines will have the same meaning.

[0071] An aspheric optically designed IOL (aspheric IOL) having an aspheric reference power profile W is designed to correct or reduce all or part of the corneal spherical aberration. The degree to which the corneal spherical aberration is reduced varies for each IOL from each company. Each company's IOL is designed to reduce the corneal spherical aberration by a specific amount (value). In the optical design of the aspheric IOL, a corneal model having a spherical aberration value equal to the specific amount of spherical aberration to be reduced is preset, and the specific amount of spherical aberration to be reduced by the aspheric 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 aspheric IOL is zero (i.e., there is no spherical aberration).

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

[0073] The aspheric reference power profile W is the power distribution of an aspheric IOL. This power distribution has power distribution characteristics that enable complete or partial reduction of the spherical aberration of the average cornea (statistical corneal optical parameters) of a population of aphakic patients. In this specification, the spherical aberration value of a predetermined corneal model is set to 0.27 μm. The dashed line in FIG. 1A is also an example of the power distribution of an aspheric IOL 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, for example, a value in the range of +0.24 to +0.30 μm.

[0074] The near zone in this specification corrects visual acuity when viewing an object at one intermediate vision distance or one near vision distance. The near zone has a power obtained by adding one positive fixed power to an aspherical reference power within a predetermined range in the radial direction of a virtual aspherical lens that has a base power at the lens center O and completely offsets the positive vertical spherical aberration caused by the cornea. This "one positive fixed power" corresponds to the add power described above in this specification.

[0075] In this specification, the aspherical reference power profile W is also referred to as a reference base power profile (RBPP). The aspherical reference power profile W to which an add power is added is also referred to as a reference add power profile (RAPP).

[0076] 1A, the power graph in the state where a single positive constant power is added in the near zone has a shape obtained by shifting the graph of the aspherical reference power upward by the same constant power. Before the existence of sub-zones 1 to 3 described below, it is preferable that the power continuously decreases in the radial direction in the power graph in the state where a single positive constant power is added in the near zone.

[0077] The positive constant power may be 1 to 4D (particularly 1.0 to 4.0D).

[0078] In each mode group, one positive fixed power is added, and then, in a predetermined radial range within the near region (subregion 1 described below), a further power is added to the added state. In other words, even if "one positive fixed power is added," the final intraocular lens (or ophthalmic lens) in this specification does not have "one" positive fixed power added.

[0079] [Mode Group 1] [Mode Group 1] will be described below. First, the concept of the present invention will be described using embodiment 1 (see FIG. 4 below). For content not described in embodiment 2 and subsequent embodiments, the description of embodiment 1 can be referenced.

[0080] <Embodiment 1> In embodiment 1, the near region including the lens center O has at least three sub-regions arranged radially, where sub-region 1 provides a positive power deviation for the positive constant power, sub-region 2 provides an approximately zero power deviation for the positive constant power, and sub-region 3 provides a negative power deviation for the positive constant power.

[0081] That is, the concept of the present invention is to radially divide a near zone to which a single positive fixed power has been added into multiple zones, as shown in Figure 4. The zones are divided into a "state where power has been further added (a in Figure 4)," a "state where power has been reduced (c and d in Figure 4)," and a "state where there is almost no change or no change at all (b in Figure 4)." As a result, as shown in the specific examples below, it is possible to widen the depth of focus for near vision and / or intermediate vision and / or improve the image quality for far vision. The mechanism behind this will be explained later.

[0082] The "state in which further power has been added" in sub-region 1 (a in FIG. 4) is a state in which a positive power deviation has been brought about relative to the fixed positive power. As a specific example, the average value of the positive power deviation in sub-region 1 is 0.3 to 1 D (particularly 0.3 to 1.0 D). This average value is the difference value obtained by subtracting the fixed positive power from the power in sub-region 1, and averaging it within sub-region 1 (for example, the average value of the difference value for each measurement point or each radial position). Hereinafter, unless otherwise specified, the average power deviation will be a value obtained in the same way.

[0083] The "state of almost no or no change (b in FIG. 4)" in subregion 2 includes the "state of slight change," and is therefore referred to as "resulting in approximately zero power deviation" (because something that is zero cannot be achieved, but something that is present can). As a specific example, the average value of the approximately zero power deviation in subregion 2 is -0.2 to 0.2D. This average value is the difference value obtained by subtracting the positive constant power from the power in subregion 2, and averaging it within subregion 2 (for example, the average value of the difference value for each measurement point or each radial position). In English, this is written as ZAPD (Zero Addition Power Deviation), omitting the "approximately" word, but the meaning remains the same as above.

[0084] The "state in which the power has been reduced" in subregion 3 (c, d in Figure 4) is a state in which a negative power deviation occurs relative to a positive constant power. As a specific example, the average value of the negative power deviation in subregion 3 is -0.3D or less. This average value is the difference value (negative value) obtained by subtracting the positive constant power from the power in subregion 3, averaged within subregion 3 (also a negative value, for example, the average value of the difference value for each measurement point or radial position). As shown in Figure 4c and d, subregion 3 may be divided into multiple regions with different power profile shapes in the radial direction. The power may be reduced in multiple stages in the radial direction. Similarly, subregions 1 and 2 may also be divided into multiple regions with different power profile shapes in the radial direction.

[0085] Furthermore, the near region may include subregions other than subregions 1 to 3. For example, subregions 1, 2, and 3 may be arranged in a row starting from the side closest to the lens center O, and subregion 4 (a region with a function equivalent to subregion 2) that provides approximately zero power deviation may be provided separately outside subregion 3. This does not exclude the possibility of dividing and separating regions with the same function into separate subregions. Furthermore, subregions 1 to 3 are not limited to being physically adjacent to each other. For example, subregions 2 and 1 may be arranged in order starting from the side closest to the lens center O, followed by subregion 4, and then subregion 3 may be arranged outside of subregion 2. In this way, the expression "including at least three subregions arranged radially" encompasses both cases where subregions 1, 2, and 3 are physically adjacent to each other and cases where they are not adjacent to each other.

[0086] There is no limitation on the order of the sub-regions 1 to 3 when viewed in the radial direction from the lens center O (in FIG. 4, the sub-regions are described in the order of 1, 2, 3). For example, the order of arrangement of the sub-regions 1 to 3 when viewed in the radial direction from the lens center O may be any of the following: Subregion 1, subregion 2, subregion 3 Subregion 1, subregion 3, subregion 2 Subregion 2, subregion 1, subregion 3 Subregion 2, subregion 3, subregion 1 Subregion 3, subregion 1, subregion 2 Subregion 3, subregion 2, subregion 1 Note that in this specification, the positive power deviation caused by subregion 1 is also referred to as PAPD (Positive Addition Power Deviation), the approximately zero power deviation caused by subregion 2 is also referred to as ZAPD (Zero Addition Power Deviation), and the negative power deviation caused by subregion 3 is also referred to as NAPD (Negative Addition Power Deviation).

[0087] Since the sub-regions 1 to 3 are arranged in the radial direction, at least the middle sub-region and the outermost sub-region are circular in shape when viewed in a plan view, as viewed in the radial direction from the lens center O. When the near region includes the lens center O, the innermost sub-region is circular, and when the near region does not include the lens center O, the innermost sub-region is also circular. The term "circular" here can be rephrased as "zonal."

[0088] It is preferable that the ratio of the area of ​​the sub-region 1 to the area of ​​the near region is 15 to 50%, the ratio of the area of ​​the sub-region 2 is 30 to 70%, and the ratio of the area of ​​the sub-region 3 is 15 to 50%. As shown in the specific examples below, it has been demonstrated that at least within these ranges, the depth of focus for near vision and / or intermediate vision can be extended and / or the image quality for far vision can be improved.

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

[0090] At least one of the boundaries between different sub-regions within the near region and the boundaries between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other, the power may change continuously or discontinuously, or the power may jump. This modification is common to Embodiments 1 and 2 and [Aspect Group 2].

[0091] Variations of the sub-regions will be described in detail in the fourth embodiment below.

[0092] In the distance region of embodiment 1 (more specifically, [mode group 1]), the power is reduced so as to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea. Specifically, the power is reduced as the distance from the lens center O increases so as to offset at least a portion (preferably 70% or more, and more preferably all) of the positive vertical spherical aberration caused by the positive refractive power of the cornea. A specific example of complete offset is a power equal to the aspherical reference power (RBPP) of a virtual aspherical lens. In other words, the power may be equal to the RBPP in the distance region.

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

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

[0095] The above is the content of the first embodiment. Figures 4 to 19 correspond to the first embodiment. In the first subregion, i.e., the positive add power deviation region, the optical power can decrease. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as shown exemplarily in Figures 5A, 5B, 5C, 6A, and 7. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex, as shown exemplarily in Figures 5A, 5B, and 6A. The third subregion can also be further divided into subregions (ca, cb, in order from the side closest to the lens center O) (reference numerals omitted in the following figures), such as the two subregions of the third subregion shown exemplarily in Figure 7. In each of these subregions shown exemplarily in Figure 7, the optical power can decrease. Each curve in each sub-subregion may comprise a respective convex curve or function, as also exemplarily shown in FIG.

[0096] Embodiment 2 Embodiment 2 is a two-zone EM-IOL in which the near zone includes the lens center O. FIGS. 20 to 22 correspond to Embodiment 2. In this embodiment, too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as exemplarily shown in FIG. 20B . In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex. The third subregion can be further divided into subregions, such as the two subregions of the third subregion exemplarily shown in FIG. 20B . In each of these subregions, the optical power can decrease. Each curve in each subregion can have its own convex curve or function, as exemplarily shown in FIG. 20B .

[0097] Embodiment 3 Embodiment 3 is a two-zone multifocal lens in which the near zone includes the lens center O. FIGS. 23 to 25 correspond to Embodiment 3. In this embodiment, too, the optical power can decrease in the first sub-zone, i.e., the positive add power deviation zone. Furthermore, in the first sub-zone, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as exemplarily shown in FIG. 23B. In the third sub-zone, i.e., the negative add power deviation zone, the optical power can decrease. Furthermore, in the third sub-zone, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex. The third sub-zone can be further divided into sub-zones, such as the two sub-zones of the third sub-zone exemplarily shown in FIG. 23B. In each of these sub-zones exemplarily shown in FIG. 23B, the optical power can decrease. Each curve in each sub-zone can have its own convex curve or function, as exemplarily shown in FIG. 23B.

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

[0099] <Embodiments 1' to 3'> Embodiment 1' is a three-zone EDOF. Figures 26 to 28 correspond to Embodiment 1'. Embodiment 1', Embodiment 2' (a three-zone EM-IOL, not shown), and Embodiment 3' (a three-zone multifocal lens, not shown) each include a distance region concentric with and including the lens center O, a near region located outside the distance region when the radial direction is taken outward from the lens center O, and an outer region located outside the near region and correcting vision for distance vision. Similarly to the distance regions of Embodiments 1 to 3, the outer region has a reduced power to provide negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea.

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

[0101] The inner diameter of the near region in plan view may be 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 increased and / or the image quality for far vision can be improved, as shown in the specific examples below. Even in these embodiments, the optical power can decrease in the first subregion, i.e., the positive add power deviation region. Furthermore, in the first subregion, the dependence of the optical power on radial distance, i.e., the corresponding curve or function, can be concave, as shown exemplarily in FIG. 26B. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on radial distance, i.e., the corresponding curve or function, can be convex. The third subregion can also be further divided into subregions, such as the two subregions of the third subregion shown exemplarily in FIG. 26B. In each of these sub-subregions, the optical power can decrease as shown by way of example in Figure 26B. Each curve in each sub-subregion can have its own convex curve or function, as also shown by way of example in Figure 26B.

[0102] Fourth Embodiment The fourth embodiment shows variations in the subregions. Figures 29 to 40 correspond to the fourth embodiment. In this embodiment, too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as shown in Figures 29A, 29B, 29C, 29D, 31A, 31B, 31C, 31D, 33A, 33B, 35A, 35B, 35C, 37B, 37C, 37D, and 37E. The curve or function of the first subregion can also increase, as shown in Figures 37D and 37E. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on radial distance, i.e., the corresponding curve or function, can be convex, as shown in Figures 29A, 29B, 29D, 31A, 31B, 31C, 31D, 33A, 33C, 35A, 35B, 37B, 37C, 37D, and 37E. The curve or function of the third subregion can also be concave, as shown in Figures 33B and 33D. The curve or function of the third subregion can also be increasing, as shown in Figures 37D and 37E. The third subregion can also be further divided into subregions, such as the two subregions of the third subregion shown in Figures 29C and 29D (pattern c3d1). In each of these subregions, as shown in Figures 29C and 29D (pattern c3d1), the optical power can decrease. Each curve in each sub-subregion can have its own convex curve or function, as also shown by way of example in Figures 29C and 29D (pattern c3d1). Each of these sub-subregions can also have its own convex curve or function, as also shown by way of example in Figures 29C and 29D (pattern c3d1).

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

[0104] [Mode Group 2] [Mode Group 2] mainly exemplifies phakic intraocular lenses or implantable (or non-implantable) contact lenses. However, [Mode Group 2] can also be applied 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, before applying the present invention ("Flat"), the power of the near zone may be constant and the power of the far zone may be constant. Then, the present invention may be applied as shown in Figure 41B.

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

[0106] In this specification (particularly the fourth aspect of the present invention in [Means for solving the problems of the present invention]), the expression "reference power having a predetermined base power at the lens center O" is used to combine both (the top two paragraphs).

[0107] 42A and 42B relate to EDOFs of a three-zone design in a phakic intraocular lens or contact lens. FIG. 43 shows many more variations obtained by extending the modifications of Embodiment 4 to [Aspect Group 2]. In this aspect group, too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as shown in FIGS. 41B, 42B, and 43. The curve or function of the first subregion can also increase. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex, as shown in FIGS. 41B, 42B, and 43. The curve or function of the third subregion can be concave. The curve or function of the third subregion can also increase. The third subregion (NAPD) can be further divided into sub-subregions, as exemplarily shown in Figure 43. In each of these sub-subregions, as exemplarily shown in Figure 43, the optical power can decrease. Each of these sub-subregions can have its own convex or concave curve or function, as shown in some examples in Figure 43. Also, the first subregion (NAPD) can have sub-subregions with concave and / or convex curves, for example, as also exemplarily shown in Figure 43.

[0108] The ophthalmic lens is a phakic intraocular lens or a contact lens, and when the near region includes a lens center O, and when the far region is positioned radially outward from the lens center O, the diameter of the near region in a planar view may be 1.4 to 3 mm.

[0109] The ophthalmic lens is a phakic intraocular lens or a contact lens, and when the far region includes a lens center O, the near region is located outside the far region when viewed radially outward from the lens center O, and the lens comprises an outer region that is located outside the near region and corrects vision for far vision, and the inner diameter of the near region in a planar view may be 1.6 to 2.4 mm and the outer diameter may be 2.9 to 3.6 mm.

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

[0111] Each example (preferred example, modified example) described in mode group 1 may be applied to mode group 2.

[0112] Furthermore, although an intraocular lens (or an ophthalmic lens) has been exemplified in each group of aspects, the technical idea (concept) of the present invention can also be applied to an optical design method for designing an intraocular lens (or an ophthalmic lens).The technical idea (concept) of the present invention can also be applied to a manufacturing method for an intraocular lens (or an ophthalmic lens) in which an intraocular lens (or an ophthalmic lens) designed by the design method for an intraocular lens (or an ophthalmic lens) is manufactured by at least one of lathing, molding, and 3D printing.

[0113] The present invention will be described in detail below, including its mechanism. Hereinafter, the term "IOL of the present invention" will be used, but the content of the following description is not intended to limit the present invention, and the term "IOL of the present invention" is used in the broad sense of an IOL that reflects the concept of the present invention (naturally including the above group aspects).

[0114] Further Details of the Invention An improvement to a bifocal EVR IOL is described herein. A two-zone optical design is provided as an example to illustrate an optical design according to the invention or a power profile according to the invention.

[0115] The present invention is applicable to the optical design of EM-IOLs, EDOF, and multifocal lenses because the optical principle of these three IOL types is the same. This optical principle means that these IOLs have a base power for correcting distance vision and near and / or intermediate powers for correcting near and / or intermediate vision. As mentioned in [Aspect Group 1], the EDOF IOL is used as the primary example in this specification.

[0116] FIG. 1A shows a prior art (referred to herein as "Flat") aspheric EDOF IOL with a base power of 20.0 D and an add power of 2.25 D. Hereinafter, unless otherwise noted, power distribution graphs are shown with the horizontal axis representing radius and the vertical axis representing power. This IOL has two zones. The first zone is the inner zone (or central zone) and the second zone is the outer zone. The second zone has a base power for correcting distance vision. The inner first zone has a power that is 2.25 D greater than the base power for correcting intermediate vision.

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

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

[0119] Correcting or reducing the spherical aberration of the cornea improves the image quality of the distance image reconstructed at the retina. 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 0 mm (the radius at the center of the lens) and decreases with increasing radius up to a radius of 0.9 mm. The power profile from a radius of 0 mm to 0.9 mm is the power profile for the near region of this IOL.

[0121] This power profile for the near region is referred to herein as the reference near power profile. This reference near power profile is synonymous with the reference add power profile (RAPP) described below. The reference near power profile is a power profile (power graph shape) that is relatively similar to the RBPP. However, the power value at a specific radius is approximately 2.25 D (the design add power value of the IOL shown in FIG. 1 ) greater than the power value of the RBPP at that specific radius.

[0122] The ADD power in Figure 1B is the design power profile of the EVR IOL minus the RBPP, i.e., the ADD power profile is the difference between the design power 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 listed in Table 1. Anterior surface of cornea refers to the anterior surface of the cornea. Posterior surface of cornea refers to the posterior surface of the cornea. Aperture refers to the opening (which corresponds to the pupil diameter of the eye, but is not an opening where no substance is present; this table lists the refractive index corresponding to the substance present in the opening). Anterior surface of intraocular lens refers to the anterior surface of the IOL. Posterior surface of lens refers to the posterior surface of the IOL. Note 1) Aspheric or aspheric curvature. The radius of curvature value at the lens center of the various IOLs described herein is approximately 17.2 mm. Note 2) The surface spacing of the various IOLs described herein is approximately 0.7 mm. Note 3) The facet spacing of the various IOLs described herein is approximately 18.8 mm.

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

[0125] 3A shows how light rays from an intermediate distance are focused onto the retina by the cornea and the EDOF of FIG. 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 of FIG. 1. Near objects located approximately 59 cm in front of the cornea can be clearly seen because light rays from the vicinity are focused onto the retina. However, objects in the near region that are not within the vicinity of the distance of approximately 59 cm cannot be clearly seen and appear blurred.

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

[0127] An ADD profile that is greater than the RBPP value by the ADD value of the IOL (e.g., greater than an ADD of about 2.25 D) is referred to herein as a Reference ADD Profile (RAPP). The Reference ADD profile is shown by the dotted line in Figures 4, 5A, and 5C.

[0128] 4 is a diagram of the power profile of a two-zone EDOF IOL with a base power of 20.0 D and an add power of 2.25 D (corresponding to embodiment 1). This IOL has an inner zone at the center of the lens for correcting intermediate vision and an outer zone surrounding the inner zone for correcting distance vision.

[0129] The inner region has four subregions. Subregion a (corresponding to subregion 1 in [Aspect Group 1]) contains power profile segments whose power values ​​are greater than the RAPP power value. Subregion b (corresponding to subregion 2 in [Aspect Group 1]) contains power profile segments whose power values ​​are the same as or similar to the RAPP power value ("same as or similar to" with respect to power values ​​may also be referred to as "equal"; the definition of "equal" has been given above). Subregion c (corresponding to subregion 3 in [Aspect Group 1]) contains power profile segments whose power values ​​are lower than the RAPP power value. Subregion d (corresponding to subregion 3 in [Aspect Group 1] (but different from the above subregion 3)) also contains power profile segments whose power values ​​are lower than the RAPP power value and different from subregion c). The power values ​​of the power profile in the outer region are the same as or similar to the RBPP power value. The power profile of the outer region can be designed to fully compensate or partially reduce the spherical aberration of the average cornea of ​​a cataract patient's eye.

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

[0131] In the following description, as illustrated in FIG. 5A , a subregion having a power value greater than the RAPP value is referred to as a subregion resulting in a positive add power deviation (PAPD), a subregion having a power value equal to or similar to the RAPP value is referred to as a subregion having a zero add power deviation (ZAPD), and a subregion having a power value less than the RAPP value is referred to as a subregion having a negative add power deviation (NAPD). NAPD is a negative value, and PAPD is a positive value. PAPD is also referred to simply as a "positive power deviation" in this specification. ZAPD is also referred to as an "almost zero power deviation" in this specification (the reason for adding "almost" has already been explained). NAPD is also referred to simply as a "negative power deviation" in this specification.

[0132] 5 shows an example of a power profile for a two-zone EDOF with a base power of 20.0 D and an add power of 2.25 D (another example corresponding to the first embodiment). The add power graph (also called a "normalized add power graph") is a graph with radius (mm) on the horizontal axis and add power (D) on the vertical axis.

[0133] The power profiles shown in Figures 5A and 5C are converted into add graphs shown in Figures 5B and 5D, respectively. Unlike the IOL of Figure 4, the two IOLs shown in Figure 5 do not have a fourth subregion d.

[0134] The power profiles of the radius vs. power (refractive power) graphs shown in Figures 5A and 5C can be expressed by four polynomials. Each of the inner region and three subregions in the RAPP in Figures 5A and 5C can be expressed by a single polynomial. The radius vs. ADD graph shown in Figure 5B can be expressed by two polynomials (for subregions a' and c') and two linear equations (for subregion b' and the outer region). The normalized ADD profile in Figure 5D can be expressed by four linear equations.

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

[0136] In the radius range of 0 mm to 0.9 mm, the total power profile of FIG. 6 has various total power values ​​set, while the total power profile of FIG. 2 has only one total power value (60.7D) set for viewing objects at intermediate distances.

[0137] Various total power values ​​of the IOL, greater or less than the 60.7D total power value shown in FIG. 6, provide a greater depth of focus for intermediate vision than the IOL of FIG. 1, as shown in FIG. 3B.

[0138] Sub-region a of the inner region of FIGS. 5A and 5B, which comprises the PAPD, has the function of extending the intermediate distance range of intermediate vision.

[0139] By providing NAPD in one or more sub-regions within the inner region, the power from the RAPP can be reduced, improving image quality for distance vision. Sub-regions of the inner region that function to reduce the RAPP power are sub-regions c and d in Figure 4 and sub-region c in Figure 5. Reducing the RAPP power in these sub-regions is expected to reduce the likelihood of halo and glare symptoms occurring at night in dark environments and the degree of visual impairment.

[0140] The radial arrangement order of the subregions in the inner region of a two-zone IOL can be changed (as described in [Aspect Group 1]). The subregions of the two-zone IOL in FIG. 4 are arranged in the following order from the lens center O toward the lens periphery (radial direction): first, the subregion containing PAPD, second, the subregion containing ZAPD, and third, the subregion containing NAPD. Of course, other arrangements are also possible. For example, from the lens center, the subregion containing ZAPD, second, the subregion containing PAPD, and third, the subregion containing NAPD may be arranged.

[0141] The size of each subregion of the inner region affects the optical properties and performance of the EDOF for correcting distance and intermediate vision. For example, if the subregion b with ZAPD is too large compared to the subregion a with PAPD and the subregion c with NAPD, the optical performance of the 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 the subregion c with NAPD is too large compared to the subregion a with PAPD and the subregion b with ZAPD, the optical performance of the EDOF for correcting intermediate vision will decrease, but the optical performance for correcting distance vision will improve.

[0142] The area ratio of each sub-region in the inner region can be determined by setting the radius value of these sub-regions. In one 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 mm. ２ It is assumed that the area percentages of sub-region a, sub-region b, and sub-region c relative to the entire inner region (near region) are 30%, 40%, and 30%, respectively. To achieve this, the radius value (ra) of sub-region a is set to 0.548 mm, the radius value (rb) of sub-region b is set to 0.837 mm, and the radius value (rc) of sub-region c is set 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 spherical aberration (approximately 0.27 μm) of the average cornea of ​​a cataract patient. On the other hand, the reference base power profile of the EVR IOL (or bifocal two-zone and three-zone IOL) according to the present invention is not limited to compensating for the 0.27 μm spherical aberration of the cornea. 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. It can also be designed to fully correct or partially reduce a specific longitudinal spherical aberration (longitudinal spherical aberration of a geometric optical system) of a human cornea model that is modeled or defined based on a database or statistical data of the human cornea.

[0144] The power profile according to the present invention exemplified in this specification can be set by calculating or designing the anterior and posterior surface shapes of the optical portion of the IOL. By utilizing specific known design or manufacturing techniques, it is possible to set an intended power profile for the anterior and posterior surface shapes of the optical portion of the IOL. Specific known design techniques include various common methods or approaches, such as calculations using geometric optics and numerical methods, calculations using ray tracing, and design using commercially available optical design software.

[0145] The aspheric sag or shape that produces the power profile can be on the anterior or posterior surface of the lens, or on both surfaces. The EVR IOL of the present invention can be designed and manufactured to correct astigmatism in the eye of a phakic patient. This is achieved by providing a toric or cylindrical surface on the anterior or posterior surface of the lens optic. In a toric-type EVR IOL, the aspheric sag 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 a toric surface. For information on sag values, see WO 2018 / 043366.

[0146] FIG. 7 shows another example of embodiment 1 of the present invention. The radius of the inner region is 0.9 mm. The inner region has four subregions. Subregion a includes PAPD and has a radius ra of 0.5 mm. Subregion b includes ZAPD and is located between radii ra and rb (0.7 mm). Subregion c includes NAPD and is located between radii rb and rc (0.8 mm). Subregion d includes NAPD and is located between radii rc and rd (0.9 mm). If the total area of ​​the inner region is 100%, the percentages of the areas of subregion a, subregion b, and subregion c plus subregion d (c + d) are approximately 31%, 30%, and 39%, respectively. The RAPP is approximately 2.25D greater than the reference base power (RBPP).

[0147] To compare the optical properties and performance of this IOL (Embodiment 1, FIG. 7) with the prior art ("Flat") EDOF shown in FIG. 1, 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 properties and characteristics evaluated were TFR (Through Focus Response) and MTF (Modulated Transfer Function).

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

[0149] The TFR indicates 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 , a pupil diameter of 3 mm provides high MTF values ​​at approximately 0 D (far distance) and approximately 1.7 D defocus (at a distance of approximately 59 cm) in both the conventional technology and the embodiment. The pupil diameter of 3 mm is a value commonly used or assumed as the average pupil diameter of an aphakic patient's eye under normal lighting conditions.

[0150] The depth of focus of an EVR IOL is the range of defocus (or range of viewing distances) over which objects are still clearly or appropriately viewed by the aphakic patient's eye. In this specification, an MTF value of 0.1 or greater at a spatial frequency of 50 lp / mm is considered useful for correcting visual acuity, and an MTF value of 0.05 or greater at a spatial frequency of 100 lp / mm is considered useful for correcting visual acuity. A state above these values ​​is also referred to as "appropriate." In this specification, "depth of focus" refers to the range of object distances (defocus values ​​on the horizontal axis of the graph) that have appropriate MTF values. A wide range is also referred to as 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 for 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 for a pupil diameter of 2 mm in FIG. 9.

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

[0152] It is known that under normal lighting conditions, images appear sharper (better) with smaller pupil diameters than with larger pupil diameters. In a two-zone IOL with an inner zone in a lens optical system for correcting intermediate and / or near vision, the MTF (i.e., a parameter that indicates whether an image appears sharper or not) for near and intermediate vision is higher with smaller pupil diameters (e.g., 2 mm and 2.5 mm) than with larger pupil diameters (e.g., 3.5 mm and 4 mm). This is illustrated in Figures 8 and 9 by the higher MTF values ​​for pupil diameters of 2 mm and 2.5 mm over the range of 0.75 D (visual distance of approximately 133 cm) to 2.25 D (visual distance of approximately 44 cm) compared to the same range (0.75 to 2.25 D) for pupil diameters of 3.5 mm and 4 mm. Hereinafter, intermediate vision and / or near vision will also be simply referred to as "intermediate-near vision," 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 quality of vision for near and intermediate vision with a small pupil diameter (e.g., less than 2.75 mm) are superior to the depth of focus and quality of vision for near and intermediate vision with a large pupil diameter (e.g., greater than 3.25 mm). As a result, aphakic patients are thought to view 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, a smaller pupil diameter is better for visual acuity. This is also true for aphakic patients. Even aphakic patients can adjust the size of their pupil diameter to achieve higher visual acuity. A smaller pupil diameter improves visual acuity rather than a larger one. Therefore, aphakic patients reduce their pupil diameter.

[0154] The MTF for distance vision of the IOLs of the present invention is also higher than that of the prior art IOLs, as evidenced by the higher MTF value (vertical axis value) of the IOLs of the present invention at defocus values ​​of approximately 0 D (horizontal axis value) than that of the prior art IOLs in the TFR graphs for pupil diameters of 2.5 to 4 mm shown in Figures 8 and 9.

[0155] When the pupil diameter is large, a two-zone optical design IOL 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 (to correct distance vision) that focuses light rays onto the retina also increases. This increases the amount of light rays that are focused onto the retina. As a result, objects are perceived more clearly than when the pupil diameter is small.

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

[0157] The primary function of the EDOF is to correct distance vision. The benefit of the present IOL for improving distance image quality or image appearance is demonstrated by the image simulation results shown in Figures 10-12. The distance image obtained with the present IOL is less blurry than the distance image obtained with prior art IOLs, making the distance image sharper.

[0158] The far-viewing MTF ("Segment" in Figures 13 and 14) of the EDOF according to the present invention is higher than that of the prior art EDOF at pupil diameters of 3 mm and 4 mm, as shown in the MTF graphs of Figures 13 and 14, respectively. These MTF graphs were simulated at far distances of 6 m, 12 m, and 25 m.

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

[0160] The benefit of the present IOL in extending depth of focus for intermediate vision is illustrated in Figures 15-19. As can be seen in the TFR graph for a pupil diameter of 3 mm in Figure 8, the best viewing distance for the prior art IOL and the present IOL is approximately 59 cm (corresponding to a defocus of 1.7D).

[0161] The images at different distances (40-60 cm) in Figures 15, 16, and 17 are simulated images with pupil diameters of 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 viewing distance of 59 cm. The images at different distances (70-110 cm) in Figures 18 and 19 are simulated images with pupil diameters of 2 mm and 3 mm. These distances are farther than the optimal viewing distance (59 cm) for both intraocular lenses.

[0162] In Figure 15 (pupil diameter 2 mm), the Landolt C (Landolt ring) patterns are clearly visible in images of the prior art intraocular lens and the present invention IOL at distances of 60 cm and 55 cm. In images at distances of 50 to 40 cm, which is closer to the cornea than the best viewing distance, the ring pattern of the present invention IOL is more distinct than the ring pattern of the prior art IOL.

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

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

[0165] 15 to 19 show that the depth of focus for intermediate vision of the EDOF IOL of the present invention is wider than the depth of focus for intermediate vision of the EDOF of the prior art. In this specification, "wide depth of focus" means that the range of distances (the range of the horizontal axis in the graph) over which an appropriate MTF value can be obtained is wide.

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

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

[0168] FIG. 20B shows an 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 subregions. Subregion a contains PAPD and its radius ra is 0.5 mm. Subregion b contains ZAPD and is located between radii ra and rb (0.7 mm). Subregion c contains NAPD and is located between radii rb and rc (0.8 mm). Subregion d contains NAPD and is located between radii rc and rd (0.9 mm). When the total area of ​​the inner region is 100%, the percentages of the areas of subregions a, b, and c plus subregion d (c + d) are approximately 31%, 30%, and 39%, respectively. The RAPP is approximately 1.0 D greater than the reference base power (RBPP).

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

[0170] The depth of focus of 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 EM-IOL of the prior art, as shown in Figures 21A, 21B, 22A, and 22B, respectively. The MTF values ​​near 0D (distance of far vision) for all pupil diameters are higher for the EM-IOL of the present invention (embodiment 2) than for the EM-IOL of the prior art.

[0171] The advantage of the EM-IOL of embodiment 2 over the prior art 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 at all pupil diameters.

[0172] 23A shows the power profile of a prior art multifocal lens (corresponding to embodiment 3) with a base power of 20.0D and an add power of 3.25D. This IOL uses a two-zone multifocal optical design. The IOL has two optical zones that actually reflect this design. The outer zone has a RBPP for correcting distance vision. The inner zone has a power that is 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 contains four subregions. Subregion a contains PAPD and has a radius ra of 0.45 mm. Subregion b contains ZAPD and is located between radii ra and rb (0.71 mm). Subregion c contains NAPD and is located between radii rb and rc (0.875 mm). Subregion d contains NAPD and is located between radii rc and rd (1 mm). If the total area of ​​the inner region is 100%, the percentages of the areas of subregions a, b, and c plus subregion d (c + d) are approximately 20%, 30%, and 50%, respectively. The RAPP is approximately 3.25 D greater than the reference base power (RBPP).

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

[0175] The depth of focus for 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 the multifocal lens of the prior art, as shown in Figures 24A, 24B, 25A, and 25B, respectively. The MTF values ​​near 0D (distance of far vision) for all pupil diameters are higher for the multifocal lens of the present invention (embodiment 3) than for the multifocal lens of the prior art.

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

[0177] Figure 26A shows the power profile of a prior art three-zone EDOF, and Figure 26B shows the power profile of a three-zone EDOF according to the present invention (embodiment 1').

[0178] The three-zone EDOF of embodiment 1' comprises three zones. The first zone, which includes the lens center O, is used for distance vision correction, and the second zone is used for intermediate vision correction. The second zone is an annular zone surrounding the first zone and has a power greater than the base power. The third zone is used for distance vision correction. The third zone is an annular zone surrounding the second zone.

[0179] The second region exists between the radius ra0 (0.6 mm) and the radius rd (1.2 mm). This second region has four subregions (a, b, c, d). The RAPP of the second region is 2.25D larger than the RBPP.

[0180] In this example, subregion a has a positive ADD deviation, subregion b has zero ADD deviation, and subregions c and d have negative ADD deviation.

[0181] Subregion a exists between radius ra (0.6 mm) and radius ra (0.885 mm). Subregion b exists between radius ra (0.885 mm) and radius rb (1.05 mm). Subregion c exists between radius rb (1.05 mm) and radius rc (1.125 mm). Subregion d exists between radius rc (1.125 mm) and radius rd (1.2 mm). If the total area of ​​the inner region is 100%, the percentages of the area of ​​subregion a, subregion b, and subregion c plus subregion d (c + d) are approximately 39%, 30%, and 31%, respectively.

[0182] FIG. 27 shows TFR as a function of pupil diameter at a spatial frequency of 50 lp / mm (line pair / mm) for the simulated eye model using the EDOF shown in FIG. 26A (prior art) and FIG. 26B (embodiment 1').

[0183] 28 shows the MTF as a function of pupil diameter near 0D (distance for far vision) for the conventional technology and embodiment 1'. The MTF graph for embodiment 1' is higher than the MTF value for the conventional technology, except that the conventional technology showed a higher MTF value at a pupil diameter of 2 mm.

[0184] The above results demonstrate that the three-zone EDOF embodiment 1' offers the advantage of extending the depth of focus for intermediate vision at smaller (average) pupil diameters while improving image quality for distance vision at all pupil diameters compared to prior art three-zone EDOFs.

[0185] Figure 29 shows the power profiles of three IOLs (pattern c1, pattern c2, and pattern c3d1) with different NAPD graphs for subregions in the inner region. The absolute value of NAPD in subregion c1 of the pattern c1 IOL is greater than the absolute value of NAPD in subregion c2 of the pattern c2 IOL. The NAPD value is, in other words, the amount of reduction from RAPP, or, in other words, the average value of the negative values ​​obtained by subtracting the RAPP value from the vertical axis value of each pattern c graph at each horizontal axis value within subregion c(+d). The "absolute value of NAPD" is the absolute value of the average value, and is, for example, the average value of the vertical axis width when the horizontally hatched portion of Figure 5A is viewed in the horizontal direction. The sum of the absolute value of the NAPD of subregion c3 and the absolute value of the NAPD of subregion d1 in the IOL with pattern c3d1 is greater than the absolute value of the NAPD of subregion c2 in the IOL with pattern c2.

[0186] The TFRs of IOLs at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm are shown in Figure 30. It has been demonstrated that IOLs with larger absolute values ​​of NAPD provide better distance MTF values ​​(at defocus near 0 D) than IOLs with smaller absolute values ​​of NAPD. This means that the image quality of distance vision in aphakic patients wearing IOLs with larger absolute values ​​of NAPD is better than that of aphakic patients wearing IOLs with smaller absolute values ​​of NAPD. This effect occurs because an IOL with larger absolute values ​​of NAPD can focus a larger amount of light rays coming from farther away onto the retina than an IOL with smaller absolute values ​​of NAPD.

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

[0188] Figure 31 shows the power profiles of three EDOFs (patterns b1, b2, and b3) with different area percentages of the ZAPD subregion. 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%, the radius of the subregion that accounts for 40% of that area and is composed of PAPD, the radius of the subregion that accounts for 20% of that area and is composed of ZAPD, and the radius of the subregion that accounts for 40% of that area and is composed of NAPD can be calculated. For the IOL with pattern b1, the area percentages of the subregions that comprise PAPD, ZAPD, and NAPD are 40%, 20%, and 40%, respectively. For the IOL with pattern b2, the area percentages of each subregion are 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%. The IOL of pattern b1 has the lowest area ratio of the subregion with ZAPD, and the IOL of pattern b3 has the highest area ratio of the subregion with ZAPD.

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

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

[0191] Figure 33 shows the power profiles of four EDOFs (patterns a1c1, a1c2, a2c1, and a2c2) with different power profiles for subregions with add power. The PAPD of the IOLs in patterns a1c1 and a1c2 is greater than the PAPD of the IOLs in patterns a2c1 and a2c2. The PAPD value is, in other words, the increase from RAPP, or, in other words, the average value of the positive values ​​obtained by subtracting the RAPP value from the vertical axis value of each pattern ac at each horizontal axis value within subregion a. For example, it is the average value of the vertical axis width when viewing the vertically hatched portion of Figure 5A in the horizontal direction. The absolute value of the NAPD of the IOLs in patterns a1c1 and a2c1 is greater than the absolute value of the NAPD of the IOLs in patterns a1c2 and a2c2.

[0192] The TFRs of the IOLs shown in Figure 33 at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm are shown in Figure 34. It has been demonstrated that the IOLs with larger absolute values ​​of NAPD (patterns a1c1 and a2c1) provide higher distance visual acuity MTF values ​​at defocus near 0 D than the IOLs with smaller absolute values ​​of NAPD (patterns a1c2 and a2c2).

[0193] IOLs with a high area ratio of the subregions comprising PAPD (patterns a1c1 and a1c2) have appropriate MTF values ​​for intermediate and near vision in the defocus range from 2D (approximately 50 cm distance) to approximately 2.5D (approximately 40 cm distance), and the MTF values ​​for intermediate and near vision of these IOLs are higher than the MTF values ​​for intermediate and near vision of IOLs with a small area ratio of the subregions comprising PAPD (patterns a2c1 and a2c2).

[0194] Figure 35 shows the power profiles of an IOL with a power jump (hereinafter referred to as a power jump IOL) and an IOL without a power jump (hereinafter referred to as a no-power jump IOL). The PAPD of the power jump IOL is larger than the PAPD of the no-power jump IOL. The absolute value of the NAPD of the power jump IOL is larger than the absolute value of the NAPD of the no-power jump IOL.

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

[0196] In the present invention, the power jump between the subregions in the inner region and the power jump between the inner and outer regions of the two zones can be utilized to change the power profile of the subregions with PAPD and NAPD. By changing the power profile of the subregions in the inner 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 of distance vision correction and intermediate-near vision correction.

[0197] The order of the subdomains comprising PAPD, ZAPD, and NAPD in the present invention can be varied.

[0198] FIG. 37 shows example power profiles of four EDOFs (Flat (only the prior art), CenterFlat, MiddleFlat, and OuterFlat) with different radial arrangement orders of subregions including PAPD, ZAPD, and NAPD.

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

[0200] The TFRs of these IOLs at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm are shown in Figure 38. At all pupil diameters, the distance MTF values ​​for the CenterFlat IOL at defocus near 0 D were higher than those for the Flat IOL (conventional technology), MiddleFlat IOL, and OuterFlat IOL. At all pupil diameters, the distance MTF values ​​for the MiddleFlat IOL and OuterFlat IOL at defocus near 0 D were higher than those for the Flat IOL.

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

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

[0203] 39 shows the power profiles of two EDOFs (Outer Higher a1c1 and Outer Higher a2c2) arranged in a different radial order from the EDOFs shown in FIG. 37. From the subregion including the lens center O to the subregions outside the inner region, the subregions are, in order, a subregion including NAPD, a subregion including ZAPD, and a subregion including PAPD. In the Outer Higher a2c2 region, there is a power jump between each subregion.

[0204] The TFRs of these intraocular lenses at different pupil diameters are shown in Figure 40. The MTF values ​​for distance vision at defocus near 0D for OuterHigher a1c1 and OuterHigher a2c2 are higher than that for the prior art Flat. The depth of focus for near and intermediate vision for these three IOLs is relatively similar even with different pupil sizes.

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

[0206] These results indicate that different orders of sub-regions comprising PAPD, ZAPD, and NAPD in the inner region of the present invention can provide several advantages over prior art IOLs, such as higher image quality (MTF) for distance vision at different pupil diameters, wider depth of focus at a specific pupil diameter, and higher MTF at near distances. Also, different orders can provide different advantages over prior art IOLs.

[0207] The present invention is applicable to other prior art two-zone and three-zone type ophthalmic lenses ([Aspect Group 2]) with a constant base power profile and a constant add power profile, as illustrated in Figures 41A and 42A.

[0208] In these figures, the base power at different radius values ​​is 20.0D, and the add power at different radius values ​​is 2.25D.

[0209] Unlike the reference base power profiles of the prior art "Flat" two-zone IOL of Figure 1 and the prior art "Flat" three-zone IOL of Figure 26A, which are designed to compensate for or reduce the spherical aberration of the average human cornea, the base power profiles of Figures 41A and 42A have a constant (20.0 D) power value. 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 focus for near and intermediate vision, and better near image quality for near distances, or improved visual acuity, can also be obtained by applying the present invention to the prior art IOLs shown in Figures 41A and 42A.

[0211] Figure 41B shows an example of the power profile of the prior art two-zone IOL shown in Figure 41A to which the present invention has been applied to improve distance and near-intermediate vision. Figure 42B shows an example of the power profile of the prior art three-zone IOL shown in Figure 42A to which the present invention has been applied to improve distance and near-intermediate vision.

[0212] The preferred radius of the inner zone of the EVR IOL of the present invention, 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). For the phakic EVR IOL of the present invention, the preferred radius of the inner zone is 0.7 to 1.5 mm (diameter 1.4 to 3 mm). For the EVR contact lenses of the present invention, the preferred radius of the inner zone is 0.85 to 1.75 mm (diameter 1.7 to 3.5 mm).

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

[0214] The inner diameter of the second region at the boundary between the first region and the second region having the add power is preferably 0.7 to 1.1 mm (diameter 1.4 to 2.2 mm). The outer diameter of the second region at the boundary between the second region and the third region is preferably 1.3 to 1.75 mm (diameter 2.6 to 3.5 mm). For the three-zone type of 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). For the three-zone type of 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 power of the 2-zone and 3-zone types of the EVR IOL and phakic EVR IOL of the present invention is 1 to 4 D at the optical surface of the IOL, and in the case of the EVR contact lens of the present invention, it is 0.75 to 4 D at the corneal surface. Note that the preferred add power of the 2-zone and 3-zone types of the EM-IOL of the present invention in [Aspect Group 1] is 1 to 2 D, 2 to 2.75 D for the EDOF of the present invention, and 2.75 D or more for the multifocal lens.

[0216] The subregions provided with add power for correcting a small range of near vision, intermediate vision, and distance vision very close to intermediate vision are a subregion provided with PAPD, a subregion provided with ZAPD, and a subregion provided with NAPD. In the present invention, the subregions provided with add power may not only include two or more subregions provided with NAPD, but also two or more subregions provided with ZAPD and two or more subregions provided with PAPD.

[0217] The subregions containing PAPD may have different PAPD graph shapes. Figure 43 shows several examples of possible PAPD graphs in addition to the PAPD graphs shown in the previous figures of the EVR IOL of the present invention. Of course, other PAPD graph shapes not shown in this specification are also applicable to the EVR IOL of the present invention. Furthermore, the PAPD shapes shown in this specification may be modified as appropriate. Furthermore, PAPD graph shapes not shown in the figures of the present application may be designed as appropriate.

[0218] A PAPD graph, with radius on the horizontal axis and add power on the vertical axis, can be composed of one or more straight lines, one or more curved lines, or a combination of at least one straight line and one curved line. Each line can be represented by a linear equation, and each curved line can be represented by a polynomial. The polynomial equation is preferably of degree 4 to 8. However, higher degrees, such as 9 to 16, may be used if necessary. The straight line increases, decreases, or remains unchanged with increasing radius (in the radial direction from the center of the lens to the periphery of the lens). The curve can also correspond to a power increase, decrease, increase and then decrease, or decrease and then increase with increasing radius.

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

[0220] The NAPD graph, with radius on the horizontal axis and add power on the vertical axis, can be composed of one or more straight lines, one or more curved lines, or a combination of at least one straight line and one curved line. Each line can be represented by a linear equation, and each curved line can be represented by a polynomial. The polynomial equation is preferably of degree 4 to 8. However, higher degrees, such as 9 to 16, may be used if necessary. The straight line decreases or remains unchanged with increasing radius (in the radial direction from the center of the lens to the periphery of the lens). The curve can also correspond to a decrease, an increase, a decrease followed by an increase, or an increase followed by a decrease with increasing radius.

[0221] For the EVR IOL of the present invention, the preferred average value of PAPD 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, or within the lens when the subregion comprising PAPD is viewed frontally (in a planar view), is 0.3D to 1.0D.

[0222] The preferred average power difference between the design power profile and the reference add power profile of the subregions with ZAPD is between -0.2D and 0.2D. The preferred average value of the NAPD of the present invention is less than -0.3D. In other words, the preferred average absolute value of the NAPD is greater than 0.3D. This value of 0.3D takes into consideration that the power at the corneal surface is approximately 0.21D. This value of 0.21D at the corneal surface is very close to 0.25D, the minimum power interval in eyeglasses used for vision and visual field correction. In eyeglasses, 0.25D changes the visual acuity of the eyeglass wearer and the image quality of the objects viewed by the wearer. Therefore, setting the minimum PAPD value to 0.3D and the minimum absolute value of the NAPD to 0.3D can result in a difference (improvement) in near vision correction and / or intermediate vision correction compared to when vision is corrected using a conventional IOL.

[0223] The area ratios of the sub-areas of PAPD, ZAPD, and NAPD in the lens area with the ADD power are preferably within specific percentage ranges, when the total area of ​​the lens area with the ADD power is taken as 100%, which influence the optical properties and performance of the EVR IOL of the present invention for vision correction in the eye of a phakic patient.

[0224] The preferred area ratio of the subregions with PAPD is 15% to 50% of the total area of ​​the near region with ADD power, the preferred area ratio of the subregions with ZAPD is 30% to 70%, and the preferred area ratio of the subregions with NAPD is 15% to 50%.

[0225] By maintaining the area ratio of the subregions comprising ZAPDs at 30% to 60% of the total area of ​​the near region comprising the add power, the near and / or intermediate distance ranges at which objects can still be seen clearly / distinctly in a phakic patient's eye implanted with the EVR IOL of the present invention can be maintained or remain equivalent to the near and / or intermediate distance ranges of prior art ("Flat") IOLs. The area ratio of the subregions comprising PAPDs can improve near and / or intermediate visual acuity, and the area ratio of the subregions comprising NAPDs can improve distance visual acuity.

[0226] The IOLs of the present invention can be made from a variety of IOL materials, including acrylic, silicone, PMMA, hydrogel, etc. They can be manufactured using a variety of known manufacturing processes, including lathing, casting / molding, printing, and combinations of different manufacturing processes.

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

[0228] The following describes aspects of the present invention: Aspect 1: An intraocular lens comprising at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, the distance region having a negative vertical spherical aberration to reduce power to at least partially offset the positive vertical spherical aberration of the average human cornea, the near region having a predetermined base power at the lens center O, and a positive fixed power added to an aspherical base power within a predetermined radial range of a virtual aspherical lens to completely offset the positive vertical spherical aberration of the average human cornea, the near region comprising at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation from the positive fixed power, subregion 2 provides a power deviation of approximately zero from the positive fixed power, and subregion 3 provides a negative power deviation from the positive fixed power. Aspect 2: An intraocular lens comprising: a near region that includes the lens center O and corrects vision for near vision, and a far region that is positioned radially outward from the lens center O and corrects vision for far vision; wherein in the far region, power is reduced to at least partially offset the positive vertical spherical aberration of the average human cornea by negative vertical spherical aberration; and in the near region, a predetermined base power is provided at the lens center O, and a positive fixed power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens so as to completely offset the positive vertical spherical aberration of the average human cornea; and the near region comprises at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation from the positive fixed power, subregion 2 provides a power deviation of approximately zero from the positive fixed power, and subregion 3 provides a negative power deviation from the positive fixed power.Aspect 3: An intraocular lens comprising: a distance region concentric with a lens center O, the distance region including the lens center O and correcting visual acuity for distance vision; and an outer region positioned radially outward from the lens center O and positioned outer than the near region and correcting visual acuity for distance vision; wherein the outer region reduces power to at least partially offset the positive vertical spherical aberration of the average human cornea by negative vertical spherical aberration; the near region has a predetermined base power at the lens center O, and adds a positive fixed power to an aspherical reference power within a predetermined radial range of a virtual aspherical lens so as to completely offset the positive vertical spherical aberration of the average human cornea; and the near region comprises at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation for the positive fixed power, subregion 2 provides a power deviation of approximately zero for the positive fixed power, and subregion 3 provides a negative power deviation for the positive fixed power. Aspect 4: An ophthalmic lens comprising at least one distance region for correcting vision for distance vision and at least one near region for correcting vision for near vision, the regions being concentric about a lens center O, wherein a positive fixed power is added in the near region to a reference power having a predetermined base power at the lens center O, the near region comprising at least three sub-regions arranged radially, wherein Sub-region 1 provides a positive power deviation for the positive fixed power, Sub-region 2 provides a power deviation of approximately zero for the positive fixed power, and Sub-region 3 provides a negative power deviation for the positive fixed power. Aspect 5: An intraocular lens according to any one of Aspects 1 to 3, wherein, with respect to the area of ​​the near region, the area ratio of Sub-region 1 is in the range of 15 to 50%, the area ratio of Sub-region 2 is in the range of 30 to 70%, and the area ratio of Sub-region 3 is in the range of 15 to 50%. Aspect 6: The intraocular lens of any one of Aspects 1 to 3, wherein the average positive power deviation in subregion 1 is in the range of 0.3 to 1 D, the average near-zero power deviation in subregion 2 is in the range of -0.2 to 0.2 D, and the average negative power deviation in subregion 3 is in the range of -0.3 D or less. Aspect 7: The intraocular lens of any one of Aspects 1 to 3, wherein the positive constant power is in the range of 1 to 4 D.Aspect 8: The intraocular lens according to any one of Aspects 1 to 3, wherein the order of arrangement of the subregions 1 to 3 when viewed in the radial direction from the lens center O is one of the following: Subregion 1, subregion 2, subregion 3 Subregion 1, subregion 3, subregion 2 Subregion 2, subregion 1, subregion 3 Subregion 2, subregion 3, subregion 1 Subregion 3, subregion 1, subregion 2 Subregion 3, subregion 2, subregion 1. Aspect 9: The ophthalmic lens according to Aspect 4, wherein, with respect to the area of ​​the near region, the area ratio of subregion 1 is in the range of 15 to 50%, the area ratio of subregion 2 is in the range of 30 to 70%, and the area ratio of subregion 3 is in the range of 15 to 50%. Aspect 10: The ophthalmic lens of Aspect 4, wherein the average value of the positive power deviations in subregion 1 is in the range of 0.3 to 1 D, the average value of the nearly zero power deviations in subregion 2 is in the range of -0.2 to 0.2 D, and the average value of the negative power deviations in subregion 3 is in the range of -0.3 D or less. Aspect 11: The ophthalmic lens of Aspect 4 above, wherein the positive constant power is in the range of 1 to 4 D. Aspect 12: The ophthalmic lens of Aspect 4, wherein the arrangement order of subregions 1 to 3 when viewed in the radial direction from the lens center O is one of the following: subregion 1, subregion 2, subregion 3 subregion 1, subregion 3, subregion 2 subregion 2, subregion 1, subregion 3 subregion 2, subregion 3, subregion 1 subregion 3, subregion 1, subregion 2 subregion 3, subregion 2, subregion 1. Aspect 13: The intraocular lens of Aspect 1 or 2, wherein the change in power is smooth or abrupt, or the power jumps at at least one of the boundaries between two different subregions, and between each of subregions 1 to 3 and the far region when the near region and the far region are adjacent. Aspect 14: The ophthalmic lens of Aspect 4, wherein the change in power is smooth or abrupt, or the power jumps at at least one of the boundaries between two different subregions, and between the far region and each of subregions 1 to 3 when the near region and the far region are adjacent. Aspect 15: The intraocular lens of Aspect 2, wherein the diameter of the near region in a plan view is in the range of 1.2 to 2.5 mm.Aspect 16: The intraocular lens of Aspect 3, wherein the power change is smooth or abrupt, or the power jumps at at least one of the boundaries between two different sub-regions, the boundaries between each of sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, and the boundaries between each of sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent. Aspect 17: The intraocular lens of Aspect 3, wherein the inner diameter of the near region in a planar view is in the range of 1.4 to 2.2 mm, and the outer diameter of the near region in a planar view is in the range of 2.6 to 3.5 mm. Aspect 18: The ophthalmic lens of Aspect 4, wherein the ophthalmic lens is a phakic intraocular lens, wherein the near region includes a lens center O, and the far region is positioned radially outward from the lens center O, and the diameter of the near region in a planar view is in the range of 1.4 to 3 mm. Aspect 19: The ophthalmic lens according to Aspect 4, wherein the ophthalmic lens is a phakic intraocular lens, the far region includes a lens center O, the near region is disposed radially outward from the lens center O outward from the far region, and an outer region is disposed radially outward from the lens center O outward from the near region and corrects vision for distance, the inner diameter of the near region in a planar view is in the range of 1.6 to 2.4 mm, and the outer diameter of the near region in a planar view is in the range of 2.9 to 3.6 mm. Aspect 20: The ophthalmic lens according to Aspect 4, wherein the ophthalmic lens is a contact lens, the near region includes a lens center O, the far region is disposed radially outward from the lens center O outward from the near region, and the diameter of the near region in a planar view is in the range of 1.4 to 3 mm.Aspect 21: The ophthalmic lens according to Aspect 4, wherein the ophthalmic lens is a contact lens, wherein the distance region includes a lens center O, and the near region is disposed radially outward from the lens center O, outward from the distance region, and wherein an outer region is disposed radially outward from the lens center O, outward from the near region, and corrects vision for distance vision, wherein an inner diameter of the near region in a plan view is in the range of 1.6 to 2.4 mm, and an outer diameter of the near region in a plan view is in the range of 2.9 to 3.6 mm. Aspect 22: The intraocular lens according to any one of Aspects 1 to 3, wherein the intraocular lens is a toric lens. Aspect 23: An optical design method for an intraocular lens according to any one of Aspects 1 to 3. Aspect 24: A method for manufacturing an intraocular lens, comprising manufacturing an intraocular lens designed by the optical design method according to Aspect 23 using at least a lathe, molding, or 3D printing. Aspect 25: The ophthalmic lens according to Aspect 4, wherein the intraocular lens is a toric lens. Aspect 26: An optical design method for an ophthalmic lens according to Aspect 4. Aspect 27: A method for manufacturing an ophthalmic lens, comprising manufacturing an ophthalmic lens designed by the optical design method according to Aspect 26 using at least a lathe, molding, or 3D printing.

Claims

1. An intraocular lens comprising at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, the distance region and the near region being concentric about a lens center O, the optical power of the lens decreasing as the radial distance to the lens center O increases in the distance region, the near region comprising at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation to a virtual optical power profile in the near region, the virtual optical power profile being an aspheric power profile with a positive constant power added, subregion 2 provides a zero power deviation to the virtual optical power profile, and subregion 3 provides a negative power deviation to the virtual optical power profile.

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

3. An intraocular lens according to claim 1, wherein said virtual optical power profile is such that the positive longitudinal spherical aberration of the human cornea, in particular of the average human cornea, is at least partially compensated for.

4. The intraocular lens of claim 1, comprising regions concentric with the lens center O, at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, wherein the power is reduced in the distance region to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region adds a positive fixed power to an 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 offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region comprises at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation from the positive fixed power, subregion 2 provides an approximately zero power deviation from the positive fixed power, and subregion 3 provides a negative power deviation from the positive fixed power.

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

6. The intraocular lens of claim 1, wherein the far region includes the lens center O, and the intraocular lens further comprises an outer region that is positioned radially outward from the lens center O more outward than the near region and that also corrects vision for distance, the far region, the near region, and the outer region are concentric with 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. An intraocular lens as described in claim 6, wherein in the outer region, the optical power of the lens decreases with increasing radial distance to the lens center O in order to at least partially offset the positive vertical spherical aberration of the human cornea, in particular the average human cornea, by negative vertical spherical aberration.

8. A lens having a lens center O as its center, comprising a distance region that includes the lens center O and corrects vision for distance vision, a near region that is positioned radially outward from the lens center O and corrects vision for near vision, and an outer region that is positioned radially outward from the near region and corrects vision for distance vision, wherein the outer region has a reduced power to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region has a predetermined base power at the lens center O and a positive fixed power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens that completely offsets the positive vertical spherical aberration caused by the cornea, and wherein the near region has at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation from the positive fixed power, and subregion 2 provides an approximately zero power deviation from the positive fixed power, 2. The intraocular lens of claim 1, wherein the subregion 3 provides a negative power deviation relative to the positive constant power.

9. An ophthalmic lens comprising at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, the distance region and the near region being concentric about a lens center O, the near region comprising at least three subregions arranged radially, wherein subregion 1 provides a positive power deviation to a virtual optical power profile in the near region, the virtual optical power profile being an aspheric power profile to which a positive constant power has been added, subregion 2 provides a zero power deviation to the virtual optical power profile, and subregion 3 provides a negative power deviation to the virtual optical power profile.

10. An ophthalmic lens as claimed in claim 9, comprising regions concentric with a lens center O, at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, wherein in the near region, a positive fixed power is added to a reference power having a predetermined base power at the lens center O, and wherein the near region comprises at least three sub-regions arranged radially, wherein sub-region 1 provides a positive power deviation from the positive fixed power, sub-region 2 provides an approximately zero power deviation from the positive fixed power, and sub-region 3 provides a negative power deviation from the positive fixed power.

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

12. The intraocular lens of claim 10, wherein the average positive power deviation in subregion 1 is 0.3 to 1 D, the average near-zero power deviation in subregion 2 is -0.2 to 0.2 D, and the average anterior negative power deviation in subregion 3 is -0.3 D or less.

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

14. The intraocular lens according to claim 1, wherein the order of arrangement of the subregions 1 to 3 when viewed in the radial direction from the lens center O is one of the following: subregion 1, subregion 2, subregion 3 subregion 1, subregion 3, subregion 2 subregion 2, subregion 1, subregion 3 subregion 2, subregion 3, subregion 1 subregion 3, subregion 1, subregion 3, subregion 3, subregion 2, subregion 1 15. The intraocular lens of claim 1, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of 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 the change in power is continuous or discontinuous, or the power jumps at at least one of the boundaries between different sub-regions within the near region, and the boundaries between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other.

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

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

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

20. The ophthalmic lens according to claim 9, wherein the ophthalmic lens is a phakic intraocular lens, the near region includes a lens center O, the far region is positioned radially outward from the lens center O, and the diameter of the near region in a planar view is 1.4 to 3 mm.

21. The ophthalmic lens according to claim 9, wherein the ophthalmic lens is a phakic intraocular lens, the distance region includes a lens center O, the near region is located outside the distance region when viewed radially outward from the lens center O, and the ophthalmic lens comprises an outer region located outside the near region and correcting visual acuity for distance vision, and the inner diameter of 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 ophthalmic lens according to claim 9, wherein the ophthalmic lens is a contact lens, the near region includes a lens center O, the far region is positioned radially outward from the lens center O, and the diameter of the near region in a planar view is 1.4 to 3 mm.

23. The ophthalmic lens according to claim 9, wherein the ophthalmic lens is a contact lens, the distance region includes a lens center O, the near region is located outside the distance region when viewed radially outward from the lens center O, and the ophthalmic lens further comprises an outer region located outside the near region and correcting visual acuity for distance vision, and the inner diameter of 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 of claim 1, wherein the intraocular lens is a toric lens.

25. The intraocular lens of claim 4, wherein in subregion 1, the optical power decreases as the radial distance to the lens center O increases, and the decrease in subregion 1 is concave, and in subregion 3, the optical power decreases as the radial distance to the lens center O increases, and the decrease in subregion 3 is convex.

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

27. The ophthalmic lens of claim 10, wherein the average positive power deviation in subregion 1 is 0.3 to 1 D, the average near-zero power deviation in subregion 2 is -0.2 to 0.2 D, and the average anterior negative power deviation in subregion 3 is -0.3 D or less.

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

29. An ophthalmic lens according to claim 9, wherein the order of arrangement of the subregions 1 to 3 when viewed in the radial direction from the lens center O is one of the following: Subregion 1, subregion 2, subregion 3 Subregion 1, subregion 3, subregion 2 Subregion 2, subregion 1, subregion 3 Subregion 2, subregion 3, subregion 1 Subregion 3, subregion 1, subregion 2 Subregion 3, subregion 2, subregion 1 30. An ophthalmic lens according to claim 9, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of 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. An ophthalmic lens according to claim 9, wherein the change in power is continuous or discontinuous, or the power jumps at at least one of the boundaries between different sub-regions within the near region, and the boundaries between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other.

32. An ophthalmic lens according to claim 9, wherein in subregion 1, the optical power decreases with increasing radial distance to the lens center O, the decrease in subregion 1 being concave, and in subregion 3, the optical power decreases with increasing radial distance to the lens center O, the decrease in subregion 3 being 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 optical design method according to claim 33, comprising the steps of: designing an aspheric power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases; adding a positive constant power to a region of the designed aspheric power profile to design a near region, wherein at least a portion of the designed aspheric power profile outside the near region forms a distance region; and changing the optical power in the near region to design at least three subregions, wherein in subregion 1, the power is increased to design a positive power deviation for the designed aspheric power profile to which the positive constant power has been added; in subregion 2, the power is not changed to design a zero power deviation for the designed aspheric power profile to which the positive constant power has been added; and in subregion 3, the power is decreased to design a negative power deviation for the designed aspheric power profile to which the positive constant power has been added.

35. A method for manufacturing an intraocular lens, comprising manufacturing an intraocular lens or ophthalmic lens designed by the optical design method according to claim 33 by at least one of lathing, molding, and 3D printing.

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