Accommodative posterior chamber intraocular lens

Abstract

An accommodative posterior chamber intraocular lens according to the present invention includes an optic portion and a haptic portion, wherein the optic portion is an optical portion provided at the center part thereof and the haptic portion includes at least two leg-shaped structures connected to and extending from the optic portion in order to support the optic portion within the eye, and includes a body directly attached to the haptic portion, and a variable portion formed in a section of the body and configured to be flexibly bent according to a force applied thereto.

Description

Adjustable posterior guide lens

[0001] The present invention relates to an artificial lens fixed to the ciliary sulcus, and more specifically to an adjustable artificial lens positioned in the posterial chamber that can adjust the focal length according to the movement of the ciliary muscle.

[0002] In particular, it is used when, after the removal of the lens nucleus and cortex during cataract surgery, damage is found in the capsular bag or surrounding tissues, making it more advantageous to fix the artificial lens to the ciliary sulcus rather than to fix it inside the capsular bag, and it can be utilized for cataract surgery and presbyopia correction.

[0003] With advancements in surgical techniques, the technology for posterior case intraocular lenses (PCLs), which are fixed to the sulcus of the ciliary body, has seen the introduction of aspherical designs to minimize visual distortion caused by conventional spherical lenses, and lens designs capable of adapting to various anatomical structures are being developed. These technological developments are contributing to the improvement of the performance and safety of posterior case intraocular lenses.

[0004] As the demand for cataract surgery increases due to the aging population, the market for posterior intraocular lenses is also expanding. With rising expectations for improved quality of life for patients, the demand for high-end lenses, such as multifocal and accommodative intraocular lenses, is increasing.

[0005] However, despite this increasing demand, current posterior intraocular lenses fixed to the sulcus have a haptic tip (contact area) that differs significantly from the actual inner surface shape of the sulcus, resulting in excessive pressure being applied to the sulcus or making stable position fixation difficult. Furthermore, while the sulcus is a very soft tissue whose inner diameter contracts and expands in all 360 degrees during adjustment, existing haptic parts exhibit limitations as they lack a flexible contact surface and appropriate contact points capable of sufficiently accommodating these shape changes.

[0006] In other words, there are limitations, such as restricted accommodative function as an intraocular lens or issues with lens stability and tissue compatibility. In particular, for lenses that provide focusing capabilities, the physical movement of the optical element is not smooth or the lens is not stably fixed, leading to visual distortion or discomfort during focus switching. Furthermore, inadequate design of the support structure results in problems such as applying excessive pressure to internal eye tissues or impeding the lens's accommodative function.

[0007] (Prior Art Document 1) Korean Published Patent No. 2024-0073973 (May 27, 2024)

[0008] The present invention aims to provide a posterior intraocular lens that can solve these problems by smoothly transmitting the deformational force of the ciliary muscle generated in the sulcus located in the posterior chamber, thereby allowing the haptic portion to be variable and, accordingly, the optic portion to physically move to adjust the focus.

[0009] In other words, the present invention aims to provide a posterior intraocular lens that maximizes the focus adjustment function while maintaining lens stability, by naturally changing the focus according to the contraction and relaxation of the ciliary muscle.

[0010] The adjustable rear guide lens according to the present invention is,

[0011] An adjustable posterior guide lens comprising an optical portion and a haptic portion,

[0012] The above-mentioned optic part is an optical part provided in the central part, and

[0013] The above haptic part is composed of at least two leg-shaped structures extending from the optic part and connected to support the optic part in a guide, and

[0014] A body directly attached to the above haptic part,

[0015] It is characterized by including a variable part formed in one section of the above body that can be flexibly bent according to the applied force.

[0016] At this time, it is preferable that the ratio of the diameter (A) of the optic part and the length (B) of one axis of the haptic part is 1:0 to 1:0.9.

[0017] In addition, the optic portion preferably has a contact portion that branches into at least two branches at the end of the body, and the contact portion preferably has two branches and has a shape that extends in an arc shape.

[0018] In addition, it is preferable that the cross-sectional distance ratio of the haptic part and the contact part is 1:0.25 to 1:0.5.

[0019] In addition, the haptic part (baseline) and the optic part are located on different planes, and it is preferable that the optic part has a structure in which it is tilted 2 to 5 degrees forward with respect to the reference plane of the haptic part.

[0020] In addition, the above variable part can be manufactured using a thickness thinner than the thickness of the body or using a material more flexible than the material of the body.

[0021] At this time, when the variable part is designed to have a thin thickness, it is preferable that the groove shape of the variable part be provided in a concave shape at the front or rear, and it is even more preferable that the maximum depth of the groove of the variable part be in the range of 1 / 10 to 1 / 3 of the body thickness.

[0022] In addition, when the radius of the center forming the spherical surface of the front surface of the optic part is R1 and the radius of the center forming the spherical surface of the rear surface is R2, it is preferable that R1 is equal to or greater than R2.

[0023] At this time, it is more preferable that the front and rear surfaces of the optic part form an aspherical surface that is convex in the center and becomes flatter toward the edges.

[0024] In addition, the R1 / R2 value may be 1.1 to 2.

[0025] The adjustable posterior guide lens according to the present invention provides excellent vision correction effects and stability through precise design and an organic mechanism. The optic portion of the lens moves back and forth according to the contraction and relaxation of the ciliary muscle, thereby enabling smooth and natural switching between distant and near focus.

[0026] This movement of the optic part is made possible by the design of the contact part and the variable part. When the haptic part is composed of three legs, the contact part smoothly contacts the sacrum at six points and transmits centripetal force in three axes to the variable part in response to the reduction of the inner diameter of the sacrum, and the variable part has a flexible structure that efficiently absorbs the force of the ciliary muscle and supports the focus adjustment of the lens through bending.

[0027] The haptic end of the lens is stably positioned within the sulcus, and due to the precise design of the contact surface, it effectively receives and evenly distributes the forces generated by the ciliary muscle. The contact surface makes stable contact with the sulcus, helping to ensure the lens remains securely fixed without rotating or twisting, despite sulcus diameters varying from patient to patient. This structure maintains the lens position even during focus changes and minimizes contact with internal ocular tissues, thereby reducing the risk of tissue damage or inflammation.

[0028] Optical performance is also an important feature of the present invention. The optic section, designed as an aspherical surface, maintains the optical center even during focus shifting, minimizing light scattering and aberrations and providing a clear, distortion-free image. The design of the joint section smoothly supports the forward and backward movement of the lens, ensuring seamless focus adjustment. Furthermore, the lens design does not obstruct aqueous humor flow, thereby maintaining intraocular pressure balance, and is designed to adapt to various anatomical structures, providing wide applicability.

[0029] In addition, ease of manufacturing and insertion is also an advantage of the present invention. The lens simplifies manipulation during surgery through a simple yet efficient structure and provides high stability and optical performance. Through this, the present invention realizes an innovative adjustable posterior traverse lens that satisfies all the requirements for focus adjustment, stability, and optical performance.

[0030] Figure 1 is a schematic diagram showing the state in which an adjustable posterior guide lens according to the present invention is applied by sulcus fixation.

[0031] FIG. 2 is a plan view of an embodiment of the adjustable rear guide lens of the present invention.

[0032] Figure 3 is a cross-sectional view illustrating the aspherical surface of the optic part.

[0033] Figure 4 is a cross-sectional view along the L-L' line of Figure 2.

[0034] FIG. 5 is an operation diagram of the adjustable rear guide lens according to the present invention during far focus.

[0035] Figure 6 is a diagram of the operation at near focus.

[0036] Before describing the present invention in detail below, it should be understood that the terms used in this specification are intended only to describe specific embodiments and are not intended to limit the scope of the invention, which is defined solely by the appended claims. Unless otherwise stated, all technical and scientific terms used in this specification have the same meaning as generally understood by those skilled in the art.

[0037] Throughout this specification and claims, unless otherwise noted, the terms "comprise," "comprising," and "comprising" mean including the mentioned article, step, or group of articles and steps, and are not used to mean excluding any other article, step, or group of articles or groups of steps.

[0038] Additionally, in the drawings, the width, length, thickness, angle, etc., of the components may be exaggerated for convenience. The drawings have been described from the observer's perspective, and when one component is described as being "above / below" or "on / below" another component, this includes not only the case where it is "immediately above / immediately below" the other component, but also the case where there is another component in between.

[0039] Meanwhile, various embodiments of the present invention may be combined with any other embodiments unless explicitly stated otherwise. Any feature indicated as particularly desirable or advantageous may be combined with any other features and features indicated as desirable or advantageous.

[0040] The present invention will be described in more detail below with reference to the drawings. FIG. 1 is a schematic diagram showing the state in which an adjustable posterior guide lens according to the present invention is applied to an eyeball.

[0041] According to this, an adjustable posterior intraocular lens is fitted into the posterior sulcus and installed in front of the lens. This structure allows for the adjustment of the intraocular lens based on the deformational force of the sulcus caused by the movement of the ciliary muscle. Typically, the posterior intraocular lens is designed to be easily inserted into the sulcus, simplifying manipulation during surgery, while the lens remains stable after surgery, eliminating the need for additional adjustments.

[0042] FIG. 2 is a plan view of an embodiment of the adjustable rear guide lens of the present invention, FIG. 3 is a cross-sectional view of an embodiment of the adjustable rear guide lens of the present invention, and FIG. 4 is a cross-sectional view along the L-L' line of FIG. 2.

[0043]

[0044] The optic section is the core part responsible for the optical performance of the lens and is not limited by diameter, height, material, or thickness. The front and back surfaces of the lens are designed as aspherical to reduce spherical aberration, minimize optical distortion, and provide a clear field of view. This aspherical design contributes particularly to improved night vision and contrast sensitivity. The optic section at the center of the lens refracts light to focus it on the retina.

[0045] The diameter of the optic portion (A) is generally designed to be 4.8 to 5.2 mm. The diameter of the optic portion can have a significant impact on the flow of aqueous humor. If the diameter of the lens is excessively large, it may obstruct the flow of aqueous humor near the pupil. This can lead to an increase in intraocular pressure as the root of the iris blocks the flow through the trabecular meshwork and Schlemm's canal, which are the drainage pathways for aqueous humor, through the mechanism of acute angle-narrow glaucoma.

[0046] Conversely, if the diameter is too small, the flow of aqueous humor will be smooth, but the optical area of ​​the lens may be insufficient to respond to all light entering the eye from all external directions, which could degrade the quality of vision. Therefore, the diameter of the optic part must be designed considering the balance between the natural flow of aqueous humor and the optical performance of the lens. In the present invention, a diameter of 4.8 to 5.2 mm maintains this balance and can provide stable accommodation and vision without hindering the flow of aqueous humor.

[0047] Meanwhile, as described below, the optic part is positioned further forward (in the direction) than the haptic part, maintaining an appropriate position and ensuring adjustability.

[0048] The thickness of a lens can vary depending on the material, and thickness directly affects the lens's flexibility, durability, and optical performance. For example, acrylic material is suitable for designing high-quality lenses because it can maintain strength while remaining thin.

[0049] Considering the stability and functionality of the lens, it is desirable to set the ratio of the diameter of the optic part (A) to the length of one axis of the haptic part (B) in the range of 1:0.7 to 1:0.9. For example, if the diameter of the optic part is 5 mm, the length of one axis of the haptic part is suitable to be between a minimum of 3.5 mm and a maximum of 4.5 mm. If it falls outside the above range, the haptic part becomes excessively short, which reduces the stability of the lens and insufficient contact area with the sulcus, or the haptic part becomes excessively long, which may cause difficulty in insertion.

[0050] The front surface (110a) and rear surface (120a) of the optic part preferably have a refractive power (smaller radius of curvature) that is 1.25 to 2.5 D (diopter) higher than the refractive power of the peripheral part, and have a biconvex aspherical shape.

[0051] Aspheric designs mimic the optical properties of the eye's natural lens, providing users with a more natural visual experience. The anterior aspheric design offers better refraction even for light passing through the periphery of the eye, while the posterior aspheric design interacts with the eye's natural fluid dynamics to help maintain the position and stability of the intraocular lens, contributing to the minimization of refractive errors.

[0052] At this time, it is desirable that the degree of asphericity between the rear surface and the front surface be similar and not significantly different. For example, 1.25:1.25, 1:1.25, 1.25:1, and 2.5:2.5 are desirable.

[0053] Meanwhile, FIG. 3 is a cross-sectional view illustrating the aspherical surface of the optic portion. When the radius of the center forming the spherical surface of the front surface of the intraocular lens is R1 and the radius of the center forming the spherical surface of the rear surface is R2, R1 is equal to or greater than R2. Additionally, the spherical surface becomes flatter as it approaches the edge of the optic portion. At this time, the ratio of R1 to R2, R1 / R2, is preferably 1.1 to 2.

[0054] Since the intraocular lens according to the present invention is stably positioned in the stratum within, the shape of the aspheric surface can be implemented as desired to obtain the desired accommodative power.

[0055] The haptic part plays a primary role in stably fixing the lens inside the eye and is configured in an overall Y shape, including a body and a bridge. The Y-shaped haptic part serves as the basic support structure for the lens, stably fixing the entire lens inside the eye to fix the lens in the anatomically correct position (center). The haptic part is a structure in the shape of at least two legs extending from the optic part to support the optic part in a guide, and preferably three such structures may be provided.

[0056] The haptic part (baseline) and the optic part are located on different planes, and the optic part has a structure in which it is tilted 2 to 5 degrees forward relative to the reference plane of the haptic part.

[0057] As described, the tilted angle of the optic and haptic parts allows the lens to be stably positioned inside the eye and enables the optic part to be adjusted according to the deformation of the variable part described later. In addition, the tilted position of the optic part facilitates insertion, reduces contact with the iris or ciliary body to prevent tissue damage, and minimizes inflammation or discomfort.

[0058] The haptic portion serves to stably fix the lens to the sulcus and supports and maintains the tilted state of the optic portion. The angle between the haptic portion and the optic portion corresponds to the average angle of the sulcus to which the haptic portion is fixed, providing stability to prevent the lens from rotating or dislodging inside the eye.

[0059] In addition, the structure, which is not excessively tilted, prevents excessive contact between the iris and the optic part, thereby not obstructing the flow of aqueous humor and preventing side effects such as increased intraocular pressure.

[0060] If this angle is reduced to less than 2 degrees, the optic portion is not sufficiently forward-displaced, resulting in decreased accommodative power; however, it reduces contact with the iris, thereby lowering the risk of tissue damage and increased intraocular pressure. Conversely, if it exceeds 5 degrees, it aids in accommodative power but reduces lens stability and affects aqueous humor flow, increasing the risk of elevated intraocular pressure. Therefore, the 2 to 5-degree tilted angle of the optic and haptic portions is an optimized design that maximizes lens performance and stability while enabling harmonious operation with the internal eye environment.

[0061] The body distributes the weight and force of the lens and provides stability to prevent rotation or dislocation. Additionally, it is manufactured with a balanced combination of the necessary rigidity and flexibility to ensure the lens sits comfortably inside the eye.

[0062] The variable section is a flexible part located within a specific area of ​​the body. In other words, it is a key component responsible for the flexibility and movement of the lens, allowing the lens to move back and forth depending on the contraction and relaxation of the ciliary muscle.

[0063] The presence of a variable section enables focus adjustment based on the force applied by the ciliary muscle. In other words, it moves the lens forward when near focus is required and backward when far focus is required.

[0064] The variable part can be manufactured by using a thickness thinner than the body or by using a material more flexible than the body. When the variable part is designed to be thin, the groove may be concave in the anterior or posterior direction. However, if positioned anteriorly, it may help prevent acute glaucoma. The ideal maximum groove depth is between 1 / 10 and 1 / 3 of the body thickness. If the groove depth is designed to be less than 1 / 10, the variable part lacks flexibility, failing to respond sufficiently to the movement of the ciliary muscle, which may lead to a decrease in focusing ability. Conversely, if the depth exceeds 1 / 3, the strength of the variable part is weakened, compromising the structural stability of the lens and increasing the likelihood of breakage during repeated use.

[0065] The contact portion is located at the end of the body and serves to insert the lens into the sulcus and physically secure it. The contact portion provides a structural support to prevent the lens from rotating or slipping out inside the sulcus, and maintains the stability of the lens.

[0066] In particular, the contact portion adopts a design that is split into at least two branches, and this shape helps the lens to be stably fixed inside the sulcus and serves to provide balanced support when an external force is applied.

[0067] In particular, the structure in which the contact portion branches into two is formed by a smooth continuous curve, and the radius of curvature of each curve is formed to have a minimum value at the branching point and gradually increase toward the end, and it is desirable for the end portion to be rounded.

[0068] As a result, the end of the contact portion naturally aligns with the curvature of the sulcus, thereby increasing the contact area with the tissue and allowing the force to be distributed evenly.

[0069] In addition, the curved shape allows for stable fixation by making smooth contact with the sulcus and attaching smoothly without friction. This minimizes unnecessary resistance when the lens is mounted and provides a structure that allows for natural adaptation even if the diameter of the sulcus varies slightly from person to person.

[0070] The contact area is made of a material (e.g., silicone, acrylic) that can provide both flexibility and strength. This choice of material ensures that the contact area makes harmonious contact with the sulcus and enables stable interaction with the internal tissues of the eye.

[0071] To optimize the contact area with the sulcus, the contact portion has a curved or rounded cross-section at the end to minimize friction and damage to the sulcus tissue. It may also have a tapered shape that gradually thins toward the end. This helps to strengthen adhesion with the sulcus and prevent excessive pressure on the tissue.

[0072] Considering anatomical characteristics, it is appropriate to design the cross-sectional distance ratio between the haptic part (B) and the contact part (B1) to be in the range of 1:0.25 to 1:0.5. If the length of the haptic part is 4mm, the length of the contact part is suitable to be between a minimum of 1mm and a maximum of 2mm. If this ratio range is exceeded, the following problems may occur.

[0073] When the ratio is less than 1:0.25, the contact area becomes excessively short, resulting in insufficient contact area with the sulcus, which leads to a lack of flexibility and reduced control. In patients with small sulcus diameters, the shortened contact area may excessively compress the sulcus tissue locally, increasing the likelihood of inflammation or tissue damage.

[0074] Conversely, if the ratio exceeds 1:0.5, the difficulty of accurately inserting the excessively long and flexible contact portion into the sulcus during surgery increases, and in the case of patients with a large sulcus diameter, only the end of the contact portion is inserted into the sulcus, making it difficult to ensure fixation stability.

[0075] The contact portion can achieve maximum accommodation and significant fixation stability while minimizing tissue damage, even when patients have different diameters ranging from large to small. Therefore, the release of an intraocular lens with a single diameter can satisfy almost all patients. It is desirable for the curvature of the contact portion tip to be small, equal to or similar to the curvature of the entire intraocular lens diameter.

[0076] The operation of the adjustable rear guide lens according to the present invention will be described below. FIG. 5 is a diagram of the operation of the adjustable rear guide lens according to the present invention at far focus, and FIG. 6 is a diagram of the operation at near focus due to the reduction of the stratum diameter and the forward displacement of the stratum itself.

[0077] The adjustable rear guide lens according to the present invention is composed of an optic part, a haptic part, and a variable part installed on the body of the haptic part, and these structures enable far and near focus adjustment. Focus switching is based on a mechanism in which the ciliary muscle moves in a similar manner simultaneously with the movement of the ciliary muscle, and the lens responds fluidly accordingly.

[0078] The near-distance focus adjustment mechanism begins with the contraction of the circular ciliary muscle. When the circular ciliary muscle contracts, a centripetal force reducing the diameter is applied to the sulcus or structures surrounding the lens capsule. This centripetal force is transmitted to the contact point of the haptic portion of the intraocular lens, which is fixed to the sulcus. With the contact point stably fixed to the sulcus, the force reducing the inner diameter of the sulcus is transmitted to the six branched portions of the contact point. Because the contact point is divided into multiple branches—for example, six—it can receive and transmit the force more evenly and efficiently. As the total diameter of the contact point decreases and the force converges into three bodies, the haptic portion receives a force moving toward the optic portion; consequently, the variable portion exhibits a bending response, causing the optic portion to move forward. This response induces changes in the entire lens structure and provides an environment where the lens can deform while maintaining stability within the sulcus.

[0079] In other words, the force transmitted to the contact portion is transferred to the variable portion. The variable portion is responsible for lens movement and focus adjustment, and thanks to its flexible design, it deforms according to the centripetal force of the convolution. The deformation of the variable portion is controlled by the depth and flexibility of the groove, thereby transmitting the force to the optic portion. During this process, the optic portion moves forward, aligning the lens's optical center with the near-distance focal point on the retina. Due to its aspherical design, the forward-protruding optic portion minimizes visual distortion during focus switching and provides a clear field of view.

[0080] The far-distance focusing mechanism is initiated by the relaxation of the annular ciliary muscle and the contraction of the longitudinal ciliary muscle. When the annular ciliary muscle relaxes, an efferent force of diameter increase is applied to the sulcus or structures surrounding the lens capsule. This efferent force is transmitted to the contact point of the haptic portion of the intraocular lens, which is fixed to the sulcus. With the contact point stably fixed to the sulcus, the force that expands the inner diameter of the sulcus is transmitted to the six branched portions of the contact point. Because the contact point is divided into multiple branches—for example, six—it can receive and transmit the force more evenly and efficiently; as the total diameter of the contact point increases, the force is transmitted to three bodies, and the haptic portion receives a force that moves toward the optic portion; consequently, the variable portion exhibits a spreading response, causing the optic portion to move backward. This response induces changes in the entire lens structure and provides an environment where the lens can deform while maintaining stability within the sulcus.

[0081] In other words, the force transmitted to the contact portion is transferred to the variable portion. The variable portion is responsible for lens movement and focus adjustment, and thanks to its flexible design, it deforms in response to the centrifugal force of the striations. The deformation of the variable portion is controlled by the depth and flexibility of the groove, thereby transmitting the force to the optic portion. During this process, the optic portion moves backward, aligning the lens's optical center with the distant focus position on the retina. Due to its aspherical design, the optic portion positioned backward minimizes visual distortion during focus transitions and provides a clear field of view.

[0082] The advantage of this mechanism is that efficient focus switching is possible with only small movements of the ciliary muscle, and the lens is stably fixed to the sulcus, maintaining its position even during focus adjustment. In addition, the flexible design of the variable and haptic parts does not apply pressure to internal eye tissues, preventing tissue damage, while the optic part maintains central alignment even during focus switching, providing a clear, distortion-free field of vision.

[0083] The features, structures, effects, etc. exemplified in each of the aforementioned embodiments may be combined or modified and implemented in other embodiments by a person skilled in the art to which the embodiments belong. Therefore, details regarding such combinations and modifications should be interpreted as being included within the scope of the present invention.

[0084] (Explanation of symbols)

[0085] R1 Radius of the center forming the sphere

[0086] R2 Radius of the center forming the spherical surface of the rear face

[0087] 110a Front side

[0088] 120a Rear side

[0089] The present invention can be applied to cataract surgery, lens removal surgery, and presbyopia correction surgery, and can be usefully utilized in the manufacturing industry of ophthalmic intraocular lenses and the medical device industry.

Claims

1. An adjustable rear guide lens comprising an optical portion and a haptic portion, wherein The above-mentioned optic part is an optical part provided in the central part, and The above haptic part is composed of at least two leg-shaped structures extending from the optic part and connected to support the optic part in a guide, and A body directly attached to the above-mentioned haptic part, An adjustable rear guide lens comprising a variable portion formed in a section of the body and capable of being flexibly bent according to the applied force.

2. In Paragraph 1, An adjustable rear guide lens in which the ratio of the diameter (A) of the optic part to the length (B) of one axis of the haptic part is 1:0 to 1:0.

9.

3. In Paragraph 1, The above-described optic portion is an adjustable rear guide lens having a contact portion that branches into at least two branches at the end of the body.

4. In Paragraph 3, The above contact portion has two branches and an adjustable rear guide lens having an arc-shaped extension.

5. In Paragraph 1, An adjustable rear guide lens in which the cross-sectional distance ratio of the haptic portion and the contact portion is 1:0.25 to 1:0.

5.

6. In Paragraph 1, An adjustable rear guide lens having a structure in which the haptic portion (reference line) and the optic portion are located in different planes, and the optic portion is tilted 2 to 5 degrees forward with respect to the reference plane of the haptic portion.

7. In Paragraph 1, The above variable part is an adjustable rear guide lens that can be manufactured using a thickness thinner than the thickness of the body or a material more flexible than the material of the body.

8. In Paragraph 7, An adjustable rear guide lens in which, when the above variable part is designed to have a thin thickness, the groove shape of the variable part is provided in a concave shape at the front or rear.

9. In Paragraph 8, An adjustable rear guide lens in which the maximum depth of the groove of the above-mentioned variable part is in the range of 1 / 10 to 1 / 3 of the body thickness.

10. In Paragraph 1, When the radius of the center forming the spherical surface of the front surface of the optic part is R1 and the radius of the center forming the spherical surface of the rear surface is R2, the intraocular lens is such that R1 is equal to or greater than R2.

11. In Paragraph 10, An intraocular lens in which the front and rear surfaces of the optic part form an aspherical surface that is convex in the center and becomes flatter toward the edges.

12. In Paragraph 10, An intraocular lens having an R1 / R2 value of 1.1 to 2.

Images