Intraocular lens with anterior capsule contraction prevention function and method of implantation thereof

Abstract

This specification discloses intraocular lenses having a function to counteract the effects of anterior capsule contraction, and methods for implanting such intraocular lenses. In some embodiments, the intraocular lens may include an optical partial fluid chamber and a haptic having a haptic fluid internal passage that fluidly communicates with the optical partial fluid chamber. The haptic fluid internal passage may include a thickened anterior portion, so that the thickness of the anterior wall of the haptic is greater than the thickness of the posterior wall. Furthermore, the intraocular lens may include one or more struts positioned within the haptic fluid internal passage. The struts and / or thickened anterior portion of the haptic may maintain the shape of the haptic fluid internal passage in response to forces applied to the haptic as a result of anterior capsule contraction.

Description

Technical Field

[0001] Cross - Reference to Related Applications This application claims priority to U.S. Patent Application No. 63 / 492,435, filed on March 27, 2023, and U.S. Patent Application No. 63 / 492,430, filed on March 27, 2023, and incorporates by reference the entire contents of both provisional applications into this application.

[0002] This disclosure generally relates to the field of intraocular lenses, and more particularly, to accommodating intraocular lenses.

Background Art

[0003] Cataract is a condition of the patient's eye that involves clouding of the normally clear lens. Cataracts develop as a result of aging, genetic factors, trauma, inflammation, metabolic diseases, or exposure to radiation. Age - related cataracts are the most common type of cataract. In the treatment of cataracts, the surgeon removes the natural lens stroma from the patient's lens capsule and replaces it with an intraocular lens (IOL). Conventional IOLs provide one or more selected focal distances that allow the patient to see far away. However, after cataract surgery, patients with conventional IOLs often require glasses or other corrective eyewear for performing certain activities because the eye is unable to maintain a sharp image of an object or adjust (i.e., change its refractive power) to focus on an object as the distance changes.

[0004] With newer IOLs such as accommodating IOLs, the eye can regain at least some focusing ability. An accommodating IOL (AIOL) utilizes forces available within the eye to refocus the eye on a distant or near target by changing a portion of the optical system.

[0005] An AIOL (arteriovenous or optic lens) is typically implanted or inserted into the patient's lens capsule after the original lens has been removed from it. The patient's lens capsule is connected to zonular fibers that lead to the patient's ciliary muscle. The lens capsule is elastic and can be deformed via the zonular fibers by ciliary muscle movement. For example, when the ciliary muscle relaxes, the zonule stretches. This stretching causes the lens capsule to generally be pulled radially outward by a radially outward force. This stretching of the lens capsule lengthens it and creates space within it. When the patient's original lens is in the lens capsule, it usually flattens, thereby reducing its refractive power and enabling distance vision. However, when the ciliary muscle contracts, as happens when the eye tries to focus on a nearby object, the radially medial portion of the muscle moves radially inward, and the zonule relaxes. When the zonule relaxes, the elastic lens capsule contracts, applying a radially inward force to the lens within the capsule. When the patient's natural lens is within the lens capsule, it is usually more curved, thereby giving the lens greater refractive power and allowing the eye to focus on nearby objects.

[0006] An AIOL implanted within the lens capsule may also have a mechanism that increases the base power of the AIOL when the ciliary muscle contracts and decreases it when the ciliary muscle relaxes. For example, when the ciliary muscle contracts, the peripheral region of the lens capsule may apply a radially inward force to the radially lateral portion of the haptic of the AIOL. This can cause the radially lateral portion of the haptic to deform, and this deformation can reduce the volume of the haptic fluid chamber within the haptic. When the volume of the haptic fluid chamber decreases, the fluid within the haptic fluid chamber is either pushed into or moved elsewhere within the optical portion fluid chamber of the optical portion of the AIOL. In response to this fluid entering the optical portion fluid chamber, the optical portion of the AIOL can change shape (e.g., increase its curvature). This shape change may allow the patient with the AIOL to focus on nearby objects.

[0007] However, in some cases, the refractive correction outcome after IOL, particularly AIOL, implantation may be affected by the patient's own biological healing response. For example, fibrous tissue may proliferate in the area surrounding part of the lens capsule.

[0008] Careful lens capsule polishing before IOL insertion and / or aggressive postoperative steroid treatment can prevent or otherwise mitigate fibrous tissue proliferation; however, ensuring the implementation of these preventative measures can be challenging. [Overview of the project] [Problems that the invention aims to solve]

[0009] Therefore, a solution is needed to address the aforementioned problems and eliminate the need for patients to undergo additional surgery. [Means for solving the problem]

[0010] This specification discloses intraocular lenses having one or more functions to counteract the effects of anterior capsule contraction, and methods for implanting such intraocular lenses. In one embodiment, an intraocular lens is disclosed comprising an optical portion including an optical partial fluid chamber, and a haptic having a proximal end connected to the optical portion and a distal free end. The haptic includes an internal haptic fluid passage that fluidly communicates with the optical partial fluid chamber. The internal haptic fluid passage extends through at least a portion of the haptic and is surrounded by a haptic radial lateral wall, a haptic radial medial wall, a haptic anterior wall, and a haptic posterior wall. The thickness of the haptic radial medial wall may be greater than the radial thickness of the haptic radial lateral wall. Furthermore, the thickness of the haptic anterior wall may be greater than the thickness of the haptic posterior wall.

[0011] In some embodiments, the thickness of the haptic front wall can be greater than the thickness of the haptic rear wall at the corresponding (i.e., the same) radial position with respect to the optical portion.

[0012] In certain embodiments, the thickness of the haptic front wall can be greater than the thickness of the haptic rear wall at a first radial position relative to the optical portion. In these embodiments, the thickness of the haptic front wall can be greater than the thickness of the haptic rear wall at a second radial position relative to the optical portion. The second radial position can be closer to the radial direction of the optical portion than the first radial position.

[0013] The thickness of the haptic front wall can refer to the thickness of the haptic front wall measured in the anterior-posterior direction. For example, the thickness of the haptic front wall can be measured from the front wall surface of the internal passage to the furthest forward point along the outer surface of the haptic front wall. Similarly, the thickness of the haptic rear wall can be measured from the rear wall surface of the internal passage to the furthest rear point along the outer surface of the haptic rear wall.

[0014] In other embodiments, the thickness of the haptic front wall may refer to the orthogonal thickness measured in the orthogonal direction.

[0015] The thickness of the haptic anterior wall can be greater than the thickness of the haptic radial outer wall.

[0016] In some embodiments, the haptic anterior wall, the haptic posterior wall, and the rest of the haptic can be made from the same polymer material. In other embodiments, the haptic anterior wall can be made from a different material than the rest of the haptic, including the haptic posterior wall.

[0017] The haptic radial inner wall may taper in shape as it approaches the optical portion (radially).

[0018] Also disclosed is an intraocular lens including an optical portion containing an optical partial fluid chamber, and a haptic having a proximal end connected to the optical portion and a distal free end. The haptic may include an internal haptic fluid passage extending through at least a portion of the haptic and in fluid communication with the optical partial fluid chamber. The cross-sectional profile of the haptic at a position along the internal haptic fluid passage may be asymmetrical such that the anterior profile of the cross-sectional profile is not the same as the posterior profile of the cross-sectional profile.

[0019] This specification discloses another embodiment of an intraocular lens having a haptic function to counteract the effects of anterior capsule contraction. This intraocular lens includes an optical portion including an optical partial fluid chamber, and a haptic having a proximal end connected to the optical portion and a distal free end. The haptic may include an internal haptic fluid passage extending through at least a portion of the haptic and in fluid communication with the optical partial fluid chamber. The intraocular lens may include one or more struts positioned within the internal haptic fluid passage. One or more struts may be configured to maintain the shape of the internal haptic fluid passage in response to forces applied to the haptic as a result of anterior capsule contraction.

[0020] One or more support columns can extend from the front wall of the interior passageway to the rear wall of the interior passageway.

[0021] In some embodiments, one or more support columns can be made from the same material as one or more walls of the haptic. In other embodiments, one or more support columns can be made from a different material than the walls of the haptic.

[0022] The haptic fluid internal passage may be surrounded by a haptic radial outer wall, a haptic radial inner wall, a haptic front wall, and a haptic rear wall. One or more supports may be positioned radially closer to the haptic radial inner wall than to the haptic radial outer wall. Furthermore, the thickness of the haptic radial inner wall may be greater than the thickness of the haptic radial outer wall in the radial direction. In addition, the shape of the haptic radial inner wall may taper as it approaches the optical portion.

[0023] This specification further discloses another embodiment of an intraocular lens comprising a thickened anterior haptic portion and one or more struts positioned within the haptic fluid internal passage. The thickened anterior haptic portion and the one or more struts can work together to maintain the shape of the haptic fluid internal passage in response to forces applied to the haptic as a result of anterior capsule contraction. The thickened anterior haptic portion may refer to the portion of the haptic anterior wall in which the thickness of the anterior haptic wall is greater than the thickness of the haptic posterior wall and the haptic radially lateral wall. The one or more struts may be positioned radially closer to the haptic radially medial wall than to the haptic radially lateral wall.

[0024] A method for implanting an intraocular lens is also disclosed. This method may include the step of removing at least a portion of the anterior capsule wall of the patient's lens capsule to form a capsulotomy.

[0025] This method may also include the step of removing cellular material from within the lens capsule using a lens capsule polishing tool. The lens capsule polishing tool may be a lens capsule sweep polisher. For example, the lens capsule polishing tool may include a hooked end with a flattened, rounded tip. The step of removing cellular material may further include scraping the cellular material from the underside of the remaining portion of the anterior capsule wall after the formation of the capsulotomy wound.

[0026] The method can further include inserting one of the intraocular lenses disclosed herein into the lens capsule from the capsulotomy opening. The intraocular lens can include an optical portion that includes an optical portion fluid chamber, and a haptic having a proximal end connected to the optical portion and a distal free end. The haptic can include a haptic fluid internal passage that extends through at least a portion of the haptic and is in fluid communication with the optical portion fluid chamber. The haptic can be configured to maintain the shape of the haptic fluid internal passage in response to a force being applied to the haptic as a result of anterior capsule shrinkage after implantation.

Brief Description of the Drawings

[0027] [Figure 1A-1C] FIG. 1A is a black and white image showing fibrotic anterior capsule opacity of a patient's eye caused by proliferation of fibrous tissue. FIG. 1B shows an example of fibrous tissue applying a tensile force to the anterior capsule portion of the patient. FIG. 1C shows the haptic of an IOL that is deformed as a result of anterior capsule shrinkage. [Figure 2] FIG. 2 shows a top view of one embodiment of an IOL having one or more anterior capsule contraction prevention (ACC prevention) functions. [Figure 3A-3B] FIGS. 3A and 3B show cross-sectional views along the cut plane A-A of the IOL of FIG. 2. [Figure 4A-4C] FIG. 4A shows a cross-sectional view of one embodiment of the haptic of an IOL having an ACC prevention function. FIG. 4B shows a cross-sectional view of another embodiment of the haptic of an IOL having an ACC prevention function. FIG. 4C shows a cross-sectional view of yet another embodiment of the haptic of an IOL having multiple ACC prevention functions. [Figure 5A-5B] FIG. 5A shows a perspective view of one embodiment of the haptic of an IOL having an ACC prevention function. FIG. 5B shows the haptic of FIG. 5A with the distal end of the haptic removed to show the cross-section of the haptic. [Figure 6] FIG. 6 shows one embodiment of a method of implanting an IOL having one or more ACC prevention functions. [Figure 7]Figure 7 shows a lens capsular polishing tool that extends into the lens capsule from the capsular incision to scrape off cellular material from the underside of the anterior wall of the lens capsule. [Modes for carrying out the invention]

[0028] Figure 1A is a black and white image showing fibrous anterior capsule opacity (ACO) caused by proliferation of fibrous tissue. This is also known as anterior capsule contraction (ACC), anterior capsule phymosis (AC phymosis), or anterior capsule contraction syndrome. As shown in Figure 1B, this fibrous tissue can exert tensile force on the anterior capsule by pulling and contracting it. Figure 1C shows that, unfavorably, this contraction of the lens capsule can deform the haptics of the IOL, causing the fluid in the haptic fluid chamber to be pushed into or otherwise moved into the optical portion fluid chamber of the IOL. As mentioned above, when fluid enters the optical portion fluid chamber, the optical portion of the IOL can change shape (e.g., increase its curvature). This unintended shape change can manifest as an undesirable myopia shift in the patient's refractive power, potentially negatively impacting the patient's refractive correction outcome.

[0029] Figure 2 shows a top view of one embodiment of IOL 100 having one or more anterior capsule contraction prevention (ACC prevention) functions. In some embodiments, IOL 100 can be a controllable IOL (AIOL).

[0030] Although AIOL is described and explained in this disclosure, any reference to AIOL may refer to one of the AIOLs discussed and described in the following U.S. Patent Publications: U.S. Patent Publication No. 2021 / 0100652, U.S. Patent Publication No. 2021 / 0100650, U.S. Patent Publication No. 2020 / 0337833, U.S. Patent Publication No. 2018 / 0153682, and the following issued U.S. Patents: U.S. Patent No. 11,426,270, U.S. Patent No. 10,433,949, U.S. Patent No. 10,299,913, U.S. Patent No. 10,195,020, and U.S. Patent No. 8,968,396, the entirety of which is incorporated herein by reference.

[0031] IOL 100 can be implanted in a patient's eye to correct defocus aberration, corneal astigmatism, spherical aberration, or a combination thereof. IOL 100 may include an optical portion 102 and one or more haptics 104, including a first haptic 104A and a second haptic 104B coupled to the optical portion 102 and extending from there along the periphery. IOL 100 can be positioned in the natural lens capsule after the natural lens has been removed.

[0032] The optical portion 102, when implanted in the natural lens capsule, can be configured to refract light entering the eye towards the retina. One or more haptics 104 can be configured to engage with the lens capsule and deform in response to ciliary muscle movements (e.g., muscle relaxation, muscle contraction, or a combination thereof) in connection with the reshaping of the lens capsule.

[0033] Each of the haptic 104 may include a haptic fluid internal passage 106 extending over at least a portion of the haptic 104. For example, the first haptic 104A may include a first haptic fluid internal passage 106A extending over at least a portion of the first haptic 104A, and the second haptic 104B may include a second haptic fluid internal passage 106B extending over at least a portion of the second haptic 104B. The haptic fluid internal passage 106 (for example, either the first haptic fluid internal passage 106A or the second haptic fluid internal passage 106B) may be in fluid communication with or fluidly connected to the optical part fluid chamber 108 in the optical part 102.

[0034] The optical partial fluid chamber 108 can communicate fluidly with one or more haptic fluid internal passages 106 through one or more fluid channels 110. The fluid channels 110 can be conduits or passages that fluidly connect the optical partial fluid chamber 108 to the haptic fluid internal passages 106. The fluid channels 110 can be spaced apart from each other. For example, a pair of fluid channels 110 can be spaced apart by about 0.1 mm to about 1.0 mm. In some embodiments, the diameter of each of the pair of fluid channels 110 can be about 0.4 mm to about 0.6 mm.

[0035] The haptic 104 can be coupled to the optical portion 102 at the reinforcing portion 112. The reinforcing portion 112 can serve as a haptic-optical portion boundary. A pair of fluid channels 110 can be defined or formed within a portion of the reinforcing portion 112.

[0036] As shown in Figure 2, the optical partial fluid chamber 108 can communicate fluidly with the first haptic fluid internal passage 106A through the first pair of fluid channels 110A. The optical partial fluid chamber 108 can also communicate fluidly with the second haptic fluid internal passage 106B through the second pair of fluid channels 110B.

[0037] In some embodiments, the first pair of fluid channels 110A and the second pair of fluid channels 110B can be positioned substantially opposite each other on the optical portion 102. The first pair of fluid channels 110A can be positioned substantially directly opposite the second pair of fluid channels 110B. The first pair of fluid channels 110A and the second pair of fluid channels 110B can be defined or extend through a portion of the optical portion 102. The first pair of fluid channels 110A and the second pair of fluid channels 110B can be defined or extend through a rear element 132 of the optical portion 102 (see, for example, Figures 3A and 3B).

[0038] Figure 2 also shows that each of the haptic 104 (for example, either the first haptic 104A or the second haptic 104B) may have a proximal attachment end 114 and a distal free end 116. A haptic fluid port 502 (see, for example, Figures 5A and 5B) may be defined at the proximal attachment end 114 of the haptic 104. The haptic fluid port 502 may serve as an opening for the haptic fluid internal passage 106. When the haptic 104 is coupled to the optical portion 102, the fluid in the haptic fluid internal passage 106 can exit the haptic fluid internal passage 106 through the haptic fluid port 502 and flow into the optical portion fluid chamber 108 via the fluid channel 110. Similarly, the fluid in the optical partial fluid chamber 108 can exit the optical partial fluid chamber 108 through a pair of fluid channels 110 and flow into the haptic fluid internal passage 106 through the haptic fluid port 502.

[0039] Each of the haptic 104 may include a haptic radial outer wall 118 and a haptic radial inner wall 120. The haptic radial outer wall 118 (also called the radial outer lateral portion of the haptic 104) may be configured to face and contact the inner surface of the patient's lens capsule (see, for example, Figure 1B) when the IOL 100 is implanted in the lens capsule. The haptic radial inner wall 120 (also called the radial inner lateral portion of the haptic 104) may be configured to face the outer circumferential surface 122 of the optical portion 102.

[0040] The IOL 100 can be implanted or inserted into the patient's lens capsule after the natural lens has been removed from that capsule. The patient's lens capsule is connected to zonular fibers that lead to the patient's ciliary muscle (see, for example, Figure 1B). The lens capsule is elastic and can be deformed via the zonular fibers by ciliary muscle movement. For example, when the ciliary muscle relaxes, the zonule stretches. This stretching causes the lens capsule to be pulled generally radially outward by a radially outward force. This stretching of the lens capsule lengthens it and creates space within it. When the patient's natural lens is in the lens capsule, the natural lens is usually flattened (anterior-posterior direction), thereby reducing its refractive power and enabling distance vision. In this configuration, the patient's natural lens is said to be in a distance-view accommodative state or to have performed distance-view accommodation.

[0041] However, when the ciliary muscle contracts, as happens when the eye attempts to focus on a nearby object, the radially medial portion of the muscle moves radially inward, and the zonule relaxes. This relaxation of the zonule causes the elastic capsule to contract, applying a radially inward force to the lens within the capsule. When the patient's natal lens is within the capsule, it is usually more curved (for example, the anterior portion of the lens is more curved), thereby giving the lens greater refractive power and enabling the eye to focus on nearby objects. In this configuration, the patient's natal lens is said to be in a near-vision accommodation state, or to have performed near-vision accommodation.

[0042] When IOL 100 is implanted in the patient's natural lens capsule, the haptic radial lateral wall 118 of the haptic 104 can directly engage with or physically contact the portion of the lens connected to the zonule or zonular fibers. Thus, the haptic radial lateral wall 118 can be configured to respond to the radially applied lens capsule deformable force when the zonule relaxes and stretches as a result of ciliary muscle movement.

[0043] When the ciliary muscle contracts, the peripheral region of the elastic lens capsule deforms, applying a radially inward force to each of the haptic radial outer walls 118 of the haptic 104. As a result, the haptic radial outer walls 118 deform or change shape, and this deformation or change in shape may reduce the volume of the haptic fluid internal passage 106. When the volume of the haptic fluid internal passage 106 decreases, the fluid within the haptic fluid internal passage 106 moves into or is pushed into the optical partial fluid chamber 108.

[0044] The optical portion 102 can change shape in response to fluid entering the optical portion fluid chamber 108 from the haptic fluid internal passage 106. This increases the base power or base spherical power of the IOL 100, thereby enabling the patient with the IOL 100 implanted in their eye to focus on nearby objects. In this state, the IOL 100 can be considered to have performed near-vision accommodation.

[0045] When the ciliary muscle relaxes, the peripheral region of the elastic lens capsule stretches radially outward, lengthening the lens capsule and creating a larger space within it. The haptic radial outer wall 118 of the haptic 104 can be configured to respond to this deformation of the lens capsule by returning to its undeformed or unstressed state. This increases or decreases the volume of the haptic fluid internal passage 106, returning it to its undeformed volume. Such an increase in the volume of the haptic fluid internal passage 106 allows the fluid in the optical partial fluid chamber 108 to be drawn out of the optical partial fluid chamber 108 or otherwise drain out and return to the haptic fluid internal passage 106. As previously mentioned, the fluid exits the optical partial fluid chamber 108 and moves into the haptic fluid internal passage 106 through the same fluid channel 110 that is formed in the optical portion 102.

[0046] As described above, the optical portion 102 can change shape in response to fluid leaving the optical portion fluid chamber 108 and entering the haptic fluid internal passage 106. This reduces the base power or base spherical power of the IOL 100, thereby enabling the patient with the IOL 100 implanted in their eye to focus on distant objects or achieve distance vision. In this state, the IOL 100 can be considered to have performed distance vision accommodation.

[0047] In some embodiments, the IOL 100 can be designed such that the haptic radial inner wall 120 of the haptic 104 is radially separated from the outer surface 122 of the optical portion 102 by a gap 124 or void. This allows a portion of the haptic 104 to change shape or expand in response to external energy (e.g., laser light 125, see Figures 3A and 3B) directed at the haptic 104.

[0048] As will be discussed in more detail in the following sections, each haptic 104 may include an ACC prevention function 200 (support 300 and / or thickened anterior portion 310, see Figures 4A-4C) that can counteract the effects of anterior capsule contraction caused by fibrous tissue proliferation after transplantation.

[0049] Figures 3A and 3B show cross-sectional views of IOL 100 in Figure 2 along the cross-section AA. The optical portion 102 may include a front element 130 and a rear element 132. The fluid-filled optical portion fluid chamber 108 can be defined between the front element 130 and the rear element 132.

[0050] The front element 130 may include a front optical surface 134 and a front inner surface 136 opposite to the front optical surface 134. The rear element 132 may include a rear optical surface 138 and a rear inner surface 140 opposite to the rear optical surface 138. Any of the front optical surface 134, the rear optical surface 138, or any combination thereof can be considered and referred to as an outer optical surface. The front inner surface 136 and the rear inner surface 140 can face the optical partial fluid chamber 108. At least a portion of the front inner surface 136 and at least a portion of the rear inner surface 140 can serve as the chamber wall of the optical partial fluid chamber 108.

[0051] As shown in Figures 3A and 3B, the optical portion 102 may have an optical axis 142 extending in the front-rear direction through the center of the optical portion 102. The optical axis 142 may extend through the centers of both the front element 130 and the rear element 132.

[0052] The thickness of the front element 130 can be increased from the periphery of the front element 130 towards or near the optical axis 142. In some embodiments, the thickness of the front element 130 can be gradually increased from the periphery towards the optical axis 142.

[0053] In certain embodiments, the thickness of the front element 130 at or near the optical axis 142 can be approximately 0.45 mm to approximately 0.55 mm. In these and other embodiments, the thickness of the front element 130 near the periphery can be approximately 0.20 mm to approximately 0.40 mm. Furthermore, the front inner surface 136 of the front element 130 can be made to have a smaller curvature than the front optical surface 134, i.e., flattened.

[0054] The thickness of the rear element 132 can be greater at or near the optical axis 142 than at the portion of the rear element 132 radially outward from the optical axis 142, but before reaching the raised peripheral portion 144 of the rear element 132. The thickness of the rear element 132 can be gradually reduced from the optical axis 142 to the portion radially outward from the optical axis 142 (but before reaching the raised peripheral portion 144). As shown in Figures 3A and 3B, the thickness of the rear element 132 can again be increased from the radially inner portion of the raised peripheral portion 144 to the radially outer portion of the raised peripheral portion 144.

[0055] In certain embodiments, the thickness of the rear element 132 at or near the optical axis 142 can be approximately 0.45 mm to approximately 0.55 mm. In these and other embodiments, the thickness of the rear element 132 radially outward from the optical axis 142 (but before reaching the raised peripheral portion 144) can be approximately 0.20 mm to approximately 0.40 mm. The thickness of the rear element 132 near the radially outward portion of the raised peripheral portion 144 can be approximately 1.00 mm to approximately 1.15 mm. Furthermore, the rear inner surface 140 of the rear element 132 can be made flatter, i.e., have a smaller curvature than the rear optical surface 138.

[0056] The optical portion 102 may have a base degree or a base spherical degree. The base degree of the optical portion 102 may be configured to change based on the internal fluid pressure in the fluid chamber 108 of the fluid-filled optical portion. The base degree of the optical portion 102 may be configured to increase or decrease as the fluid enters or exits the fluid chamber 108 of the fluid-filled optical portion.

[0057] The base degree of the optical portion 102 can be configured to increase as the fluid enters the fluid-filled optical portion fluid chamber 108 from the haptic fluid internal passage 106, as shown by the curved dashed arrow in Figure 3A. For example, the forward element 130 of the optical portion 102 can be configured to increase its curvature in response to the fluid entering the optical portion fluid chamber 108. Similarly, the rear element 132 of the optical portion 102 can be configured to increase its curvature in response to the fluid entering the optical portion fluid chamber 108. In another embodiment, both the forward element 130 and the rear element 132 can be configured to increase their curvature in response to the fluid entering the optical portion fluid chamber 108. These shape changes may enable the patient with the IOL 100 to focus on nearby objects. If at least one of the forward element 130 and the rear element 132 increases its curvature due to the fluid entering the optical partial fluid chamber 108, the IOL 100 is considered to be in a near-vision accommodative state or has been near-vision accommodated.

[0058] The base degree of the optical portion 102 can be configured to decrease as the fluid exits the fluid-filled optical portion fluid chamber 108 or is drawn out and enters the haptic fluid internal passage 106, as shown by the curved dashed arrow in Figure 3B. For example, the front element 130 of the optical portion 102 can be configured to decrease its curvature (i.e., flatten) in response to the fluid exiting the optical portion fluid chamber 108. Similarly, the rear element 132 of the optical portion 102 can be configured to decrease its curvature (i.e., flatten) in response to the fluid exiting the optical portion fluid chamber 108. In another embodiment, both the front element 130 and the rear element 132 can be configured to decrease their curvature in response to the fluid exiting the optical portion fluid chamber 108. These shape changes may enable the patient with the IOL 100 to focus on distant objects. If at least one of the forward element 130 and the rear element 132 has its curvature reduced by fluid flowing out of the optical partial fluid chamber 108, then the IOL 100 is considered to be in a distance-view accommodating state or has performed distance-view accommodating.

[0059] Figures 3A and 3B show the fluid entering the optical partial fluid chamber 108 from the haptic fluid internal passage 106 with curved dashed arrows, but it should be noted that the fluid enters and exits the optical partial fluid chamber 108 through the fluid channel 110 and the opening 146 defined along the rear element 132. The opening 146 can be a hole or opening defined along the rear element 132 that serves as the end of the fluid channel 110. If the IOL 100 includes a pair of fluid channels 110, the pair of openings 146 that serve as the ends of the fluid channels 110 can be spaced about 0.1 mm to about 1.0 mm apart from each other.

[0060] As described above, the haptic 104 can be configured to deform or otherwise change shape in response to interaction with or engagement with the patient's lens capsule when the IOL 100 is implanted in the patient's eye. More specifically, the haptic radial lateral wall 118 of the haptic 104 can be made thinner than the haptic radial medial wall 120 so that the haptic 104 can maintain high sensitivity to radial forces applied to the equatorial region of the haptic 104 due to changes in the shape of the lens capsule as a result of ciliary muscle movement.

[0061] As shown in Figures 3A and 3B, the haptic radial inner wall 120 of the haptic 104 can be designed to be thicker or bulkier than the haptic radial outer wall 118 to provide the haptic 104 with rigidity or elasticity in the anterior-posterior direction. In certain embodiments, the haptic radial inner wall 120 can be designed to taper as it approaches the optical portion 102. When designed in this way, the haptic 104 may be less sensitive to forces from the lens capsule applied in the anterior-posterior direction. For example, when a force from the lens capsule is applied to the haptic 104 in the anterior-posterior direction, the fluid movement between the haptic fluid internal passage 106 and the optical portion fluid chamber 108 is less than when the force is applied radially. Because less fluid movement occurs, the change in the base power of the IOL 100 is also smaller.

[0062] In some embodiments, the fluid in the optical partial fluid chamber 108 and the haptic fluid internal passage 106 can be an oil. More specifically, in certain embodiments, the fluid in the optical partial fluid chamber 108 and the haptic fluid internal passage 106 can be a silicone oil or fluid. For example, the fluid can be a silicone oil made in part with diphenylsiloxane. In other embodiments, the fluid can be a silicone oil made in part with a ratio of 2 units of dimethylsiloxane to 1 unit of diphenylsiloxane. More specifically, in some embodiments, the fluid can be a silicone oil made in part with diphenyltetramethylcyclotrisiloxane or a copolymer of diphenylsiloxane and dimethylsiloxane. In yet another embodiment, the fluid can be a silicone oil containing a branched polymer.

[0063] The fluid (e.g., silicone oil) may be refractive index-matched with the lens body material used to fabricate the optical portion 102. When the fluid is refractive index-matched with the lens body material, the entire optical portion 102 containing the fluid can function as a single lens. For example, the fluid may be selected to have a refractive index of about 1.48 to 1.53 (or about 1.50 to 1.53). In some embodiments, the polydispersity index of the fluid (e.g., silicone oil) may be about 1.2 to 1.3. In other embodiments, the polydispersity index of the fluid (e.g., silicone oil) may be about 1.3 to 1.5. In other embodiments, the polydispersity index of the fluid (e.g., silicone oil) may be about 1.1 to 1.2. Other exemplary fluids are described in U.S. Patent Application Publication No. 2018 / 0153682, which is incorporated herein by reference in its entirety.

[0064] In some embodiments, the front element 130 can be configured such that the front optical surface 134 changes shape from a spherical configuration to an aspherical configuration in response to the fluid entering the optical partial fluid chamber 108. The aspherical surface configuration can correct higher-order aberrations such as spherical aberration. The front optical surface 134 may be compressed into an aspherical configuration if the center or central portion of the front element 130 bends or bulges further than the outer peripheral portion of the front element 130 which is held down by the adhesive 150 or adhesive layer.

[0065] In other embodiments, the rear element 132 may be configured such that the rear optical surface 138 changes shape from a spherical configuration to an aspherical configuration in response to the fluid entering the optical partial fluid chamber 108. The rear optical surface 138 may be compressed into an aspherical configuration if the center or central portion of the rear element 132 bends or protrudes further than the outer peripheral portion of the front element 130, which is held down by the adhesive 150 or adhesive layer.

[0066] In certain embodiments, the forward optical surface 134 can be manufactured to have an aspherical optical surface before the IOL 100 is implanted in the patient's eye. In these embodiments, the forward optical surface 134 can remain aspherical despite any fluid pressure changes within the optical partial fluid chamber 108. In these embodiments, the forward optical surface 134 can also maintain its asphericity with respect to all base power changes.

[0067] In other embodiments, the posterior optical surface 138 can be manufactured to have an aspherical optical surface before the IOL 100 is implanted in the patient's eye. In these embodiments, the posterior optical surface 138 can remain aspherical despite any fluid pressure changes within the optical partial fluid chamber 108. In these embodiments, the posterior optical surface 138 can maintain its asphericity even with all base power changes.

[0068] The optical portion 102 can be made in part from a deformable or flexible material. In some embodiments, the optical portion 102 can be made in part from a deformable or flexible polymer material. For example, the front element 130, the rear element 132, or a combination thereof can be made in part from a deformable or flexible polymer material. One or more haptics 104 (e.g., a first haptic 104A, a second haptic 104B, or a combination thereof) can be made in part from the same deformable or flexible material as the optical portion 102. In other embodiments, one or more haptics 104 can be made in part from a material different from that of the optical portion 102.

[0069] In some embodiments, the optical portion 102 may include, or be made of, a lens body material. The lens body portion may be made of a crosslinked copolymer including a copolymer blend. The copolymer blend may include alkyl acrylates or methacrylates, fluoroalkyl (meth)acrylates, and phenyl-alkyl acrylates. It is intended by this disclosure, and should be understood as such by those skilled in the art, that these types of acrylic crosslinked copolymers may generally be copolymers of multiple acrylates, methacrylates, or combinations thereof, and the term “acrylate” as used herein, unless otherwise specified, should be understood to mean interchangeable acrylates, methacrylates, or combinations thereof. The crosslinked copolymer used to make the lens body material may contain about 3% to 20% (wt%) of alkyl acrylate, about 10% to 35% (wt%) of fluoroalkyl acrylate, and about 50% to 80% (wt%) of phenyl-alkyl acrylate. In some embodiments, the crosslinked copolymer comprises or can be fabricated in part from n-butyl acrylate as an alkyl acrylate, trifluoroethyl methacrylate as a fluoroalkyl acrylate, and phenylethyl acrylate as a phenylalkyl acrylate. More specifically, the crosslinked copolymer used in the fabrication of the lens body material may contain n-butyl acrylate in an amount of about 3% to 20% (wt%) (e.g., about 12% to 16%), trifluoroethyl methacrylate in an amount of about 10% to 35% (wt%) (e.g., about 17% to 21%), and phenylethyl acrylate in an amount of about 50% to 80% (wt%) (e.g., about 64% to 67%).

[0070] The final composition of the crosslinked copolymer used in the manufacture of the lens body material may also include a crosslinker, i.e., a crosslinking agent, such as ethylene glycol dimethacrylate (EGDMA). For example, the final composition of the crosslinked copolymer used in the manufacture of the lens body material may also include a crosslinker, i.e., a crosslinking agent (e.g., EGDMA) in an amount of about 1.0%. The final composition of the crosslinked copolymer used in the manufacture of the lens body material may also include an initiator, i.e., a UV absorber (e.g., Percadox 16) and a UV absorber.

[0071] One or more haptic 104 may contain or be made in part from haptic material. The haptic material may contain or be made in part from a crosslinked copolymer comprising a copolymer blend. The copolymer blend may include alkyl acrylates, fluoroalkyl acrylates, and phenyl-alkyl acrylates. For example, the crosslinked copolymer used to make the haptic material may contain alkyl acrylates in an amount of about 10% to 25% (wt%), fluoroalkyl acrylates in an amount of about 10% to 35% (wt%), and phenyl-alkyl acrylates in an amount of about 50% to 80% (wt%). In some embodiments, the crosslinked copolymer used to produce the haptic material may contain about 10% to 25% (wt%) (e.g., about 19% to 23%) of n-butyl acrylate, about 10% to 35% (wt%) (e.g., about 14% to 18%) of trifluoroethyl methacrylate, and about 50% to 80% (wt%) (e.g., about 58% to 62%) of phenylethyl acrylate. The final composition of the crosslinked copolymer used to produce the haptic material may also contain about 1.0% of a crosslinker, i.e., a crosslinking agent, such as EGDMA. The final composition of the crosslinked copolymer used to produce the haptic material may also contain several photoinitiators, i.e., photoinitiators (e.g., camphorquinone, 1-phenyl-1,2-propanedione, and 2-ethylhexyl-4-(dimethylamino)benzoic acid).

[0072] In some embodiments, the refractive index of the lens body material can be approximately 1.48 to approximately 1.53. In certain embodiments, the refractive index of the lens body material can be approximately 1.50 to approximately 1.53 (for example, approximately 1.5178).

[0073] The front element 130 can be attached to the rear element 132 via adhesive 150 or an adhesive layer, or otherwise bonded. The adhesive layer can be substantially annular in shape. The adhesive 150 or adhesive layer can be positioned at the peripheral edge of the optical portion 102 between the front element 130 and the rear element 132. For example, the adhesive 150 can be positioned on the raised peripheral portion 144 of the rear element 132.

[0074] The adhesive 150 or adhesive layer may contain or be made in part from a biocompatible adhesive. The adhesive 150 or adhesive layer may contain or be made in part from a biocompatible polymer adhesive.

[0075] Adhesive 150 or adhesive layer may contain or be made in part from a crosslinked polymer precursor formulation. The crosslinked polymer precursor formulation may contain or be made in part from a copolymer blend, a hydroxyl-functionalized acrylic monomer, and a photoinitiator.

[0076] The copolymer blend may include alkyl acrylates (e.g., about 41% to about 45% (wt%) of n-butyl acrylate), fluoroalkyl acrylates (e.g., about 20% to about 24% (wt%) of trifluoroethyl methacrylate), and phenylalkyl acrylates (about 28% to about 32% (wt%) of phenylethyl acrylate). The hydroxyl-functionalized acrylic monomer may be 2-hydroxyethyl acrylate (HEA). A photoinitiator may be used to facilitate the curing of the adhesive. For example, the photoinitiator may be Darocur 4265 (a 50 / 50 blend of diphenyl(2,4,6-trimethylbenzoyl)phosphine oxide and 2-hydroxy-2-methylpropiophenone).

[0077] In some embodiments, the same adhesive 150 used to bond the front element 130 to the rear element 132 can also be used to bond or fix one or more haptics 104 to the optical portion 102.

[0078] As will be discussed in more detail in the following sections, each haptic 104 may include one or more ACC prevention functions 200 that can counteract the effects of anterior capsule contraction caused by post-transplant fibrous tissue proliferation.

[0079] Figure 4A shows a cross-sectional view of one embodiment of a haptic 104 having a support column 300 positioned within the haptic fluid internal passage 106. The support column 300 can be an example of an ACC prevention function 200. The support column 300 can be configured to maintain the shape of the haptic fluid internal passage 106 in response to a force applied to the haptic 104 as a result of the lens capsule contracting due to the proliferation of fibrous tissue.

[0080] The support column 300 can extend from the front wall surface 302 of the internal passage to the rear wall surface 304 of the internal passage. As shown in Figure 4A, the support column 300 can be positioned in the front-rear direction so that it is substantially parallel to the optical axis 142 of the optical section 102 (see, for example, Figures 3A and 3B).

[0081] In other embodiments not shown but conceivable by this disclosure, the support column 300 can be inclined or tilted. For example, the support column 300 can be positioned at an angle with respect to the optical axis 142.

[0082] As shown in Figure 4A, the support 300 can be positioned radially closer to the haptic radial inner wall 120 than to the haptic radial outer wall 118 (see Figures 3A and 3B). This allows the support 300 to counteract the effects of fibrous ACC without substantially adversely affecting the sensitivity of the haptic radial outer wall 118 to radial forces applied to the lens capsule by ciliary muscle movement.

[0083] For example, the support column 300 (or the side of the support column 300 closest to the haptic radial inner wall 120) can be separated from the haptic radial inner wall 120 by an inner separation distance. The support column 300 (or the side of the support column 300 closest to the haptic radial outer wall 118) can be separated from the haptic radial outer wall 118 by an outer separation distance. The outer separation distance can be greater than the inner separation distance. In some embodiments, the outer separation distance can be 1.5 times (1.5 ×) to 3 times (3 ×) the inner separation distance.

[0084] For example, the support column 300 can be positioned between the haptic radial inner wall 120 and the center line that bisects the haptic fluid internal passage 106.

[0085] In some embodiments, the support column 300 can be cylindrical. In other embodiments, the support column 300 can be elongated rectangular parallelepiped, square prism, truncated cone, triangular prism, or elongated oval (i.e., having an elliptical or elliptical cross-section).

[0086] In some embodiments, the support column 300 can be made from the same material as the rest of the haptic 104. For example, the support column 300 can be made from the same cross-linked copolymer as the walls of the haptic 104. In certain embodiments, the support column 300 can be integrated with the rest of the haptic 104. For example, the entire haptic 104, including the support column 300, can be formed by injection molding.

[0087] In other embodiments, the support column 300 can be made of a different material from the rest of the haptic 104. In these embodiments, the support column 300 can be bonded to the front wall surface 302 and the rear wall surface 304 of the internal passage after the rest of the haptic 104 has been formed.

[0088] The support column 300 may have a support column height 306 and a support column width 308. In some embodiments, the support column height 306 can be about 1.5 mm to 2.0 mm. For example, the support column height 306 can be about 1.75 mm to 1.85 mm.

[0089] The column width 308 can be approximately 0.20 mm to 0.60 mm. For example, the column width 308 can be approximately 0.30 mm to 0.50 mm. In some embodiments, the column width 308 can be less than 0.20 mm or greater than 0.60 mm, depending on the width of the haptic fluid internal passage 106.

[0090] As shown in Figure 4A, the column width 308 can remain constant along the length or height of the column 300. In other embodiments, the column width 308 can be wider than the rest of the column 300 near the end of the column 300 (i.e., closer to the front wall surface 302 and / or rear wall surface 304 of the internal passage). For example, the column 300 can be wider at its front and / or rear ends.

[0091] Although Figure 4A shows only one support column 300 within the haptic fluid internal passage 106, the present disclosure suggests that the haptic fluid internal passage 106 may include multiple supports column 300 (e.g., 3 to 14 supports column 300) positioned along the length of the haptic fluid internal passage 106 (see, for example, Figure 2).

[0092] Figure 4B shows a cross-sectional view of another embodiment of the haptic 104 having a thickened front section 310. The thickened front section 310 is another example of the ACC prevention function 200. As shown in Figure 4B, the haptic fluid internal passage 106 may be surrounded by a haptic radial outer wall 118, a haptic radial inner wall 120, a haptic front wall 312, and a haptic rear wall 314. All four walls can be connected integrally to form a haptic fluid chamber.

[0093] In some embodiments, the thick front portion 310 can refer to the portion of the haptic front wall 312 in which the thickness of the haptic front wall 312 is greater than the thickness of the haptic rear wall 314. For example, the thick front portion 310 can refer to the portion of the haptic front wall 312 in which the thickness of the haptic front wall 312 is greater than the thickness of the haptic rear wall 314 at the corresponding radial position (i.e., the same radial position) with respect to the optical portion 102.

[0094] The thickened front portion 310 can also refer to a portion of the haptic front wall 312 in which the thickness of the haptic front wall 312 changes radially (for example, decreases or increases radially), but the changing thickness is thicker than the thickness of the haptic rear wall 314 at the corresponding radial position (i.e., the same radial position) with respect to the optical portion 102. For example, the thickness of the haptic front wall 312 at a first radial position with respect to the optical portion 102 can be thicker than the thickness of the haptic rear wall 314 at the same first radial position. In this example, the thickness of the haptic front wall 312 at a second radial position closer to the optical portion 102 than the first radial position can be thinner or thicker than the thickness of the haptic front wall 312 at the first radial position, but nevertheless can be thicker than the thickness of the haptic rear wall 314 at the same second radial position.

[0095] In other embodiments, the thickened front portion 310 can be thicker than the haptic radial outer wall 118 (i.e., thicker than the radial thickness of the haptic radial outer wall 118).

[0096] In one embodiment of the embodiments described above, a reference to the thickness of the haptic front wall 312 or the thickness of the haptic rear wall 314 may refer to the longitudinal thickness 316 of such wall measured in the longitudinal direction (Figure 4B). Alternatively or additionally, a reference to the thickness of the haptic front wall 312 or the thickness of the haptic rear wall 314 may also refer to the orthogonal thickness 318 of such wall measured in the orthogonal direction.

[0097] For example, Figure 4B shows that the longitudinal thickness 316 of the haptic front wall 312 at the first radial position is thicker than the longitudinal thickness 316 of the haptic rear wall 314 at the same first radial position. Furthermore, Figure 4B also shows that the longitudinal thickness 316 of the haptic front wall 312 at the first radial position is thicker than the orthogonal thickness 318 of the haptic front wall 312 at the second radial position, which is closer to the optical portion 102 than the first radial position. Furthermore, Figure 4B also shows that the orthogonal thickness 318 of the haptic front wall 312 at the second radial position is thicker than the orthogonal thickness 318 of the haptic rear wall 314 at the same radial position. In this example, the thickened front portion 310 may include the portion of the haptic front wall 312 between the first radial position and the second radial position.

[0098] In some embodiments, the longitudinal thickness 316 of the haptic front wall 312 can be measured from the front wall surface 302 of the internal passage to the furthest forward point 320 along the outer surface of the haptic front wall 312. In these and other embodiments, the longitudinal thickness 316 of the haptic rear wall 314 can be measured from the rear wall surface 304 of the internal passage to the furthest rear point 322 along the outer surface of the haptic rear wall 314.

[0099] In certain embodiments, the haptic front wall 312 and the haptic rear wall 314 can be made from the same polymer material. For example, the haptic front wall 312 and the haptic rear wall 314 can be made from the same cross-linked copolymer as the wall of the haptic 104.

[0100] In other embodiments, at least a portion of the haptic front wall 312 can be made of a different material from the haptic rear wall 314. For example, the thick front portion 310 can be made of a different material from the rest of the haptic 104, including the haptic rear wall 314.

[0101] As a more specific example, the thick front portion 310 can be made of a polymer material that is harder than the rest of the haptic 104, including the haptic rear wall 314 and / or the haptic radial outer wall 118. In certain embodiments, this can be achieved by adding a larger amount of crosslinker, i.e., a crosslinking agent. In other embodiments, this can be achieved by varying the amounts of alkyl acrylate, fluoroalkyl acrylate, phenylalkyl acrylate, or a combination thereof.

[0102] One technical challenge faced by the applicants is how to counteract the effects of fibrous ACC without impairing the sensitivity of the fluid-filled haptic 104 to radial forces applied by the lens capsule as a result of ciliary muscle movement. The technical solution discovered and developed by the applicants is an ACC prevention function 200 disclosed herein, which includes a strut 300 positioned within the thickened front section 310 and / or the haptic fluid internal passage 106. As previously stated, the strut 300 can be positioned radially closer to the haptic radial inner wall 120 than to the haptic radial outer wall 118 (see also Figures 3A and 3B). The thickened front section 310 and / or the strut 300 can counteract the effects of fibrous ACC without substantially adversely affecting the sensitivity of the haptic radial outer wall 118 to radial forces applied by the lens capsule by ciliary muscle movement.

[0103] As can be seen from Figure 4B, the cross-sectional profile of the haptic 104 (at a position along the haptic fluid internal passage 106) is asymmetrical. This asymmetry can be seen by comparing the forward profile 324 of the cross-sectional profile of the haptic 104 with the rear profile 326 of the haptic 104. For example, the cross-sectional profile shows that the forward profile 324 of the haptic 104 is not the same as the rear profile 326 of the haptic 104.

[0104] Figure 4C shows a cross-sectional view of yet another embodiment of the haptic 104 having both a thickened front section 310 and a support column 300 positioned within the haptic fluid internal passage 106. Both the thickened front section 310 and the support column 300 can be configured to maintain the shape of the haptic fluid internal passage 106 in response to forces applied to the haptic 104 as a result of anterior capsule contraction due to fibrous tissue proliferation.

[0105] The support column 300 can extend from the rear wall surface 304 of the internal passage to the front wall surface 302 of the internal passage, which serves as the underside or rearside of the thick front portion 310. The support column 300 shown in Figure 4C can otherwise be the same as the support column 300 shown and described in relation to Figure 4A. For example, the support column 300 can be positioned in the front-rear direction so that it is substantially parallel to the optical axis 142 of the optical portion 102 (see, for example, Figures 3A and 3B). In other embodiments not shown in the figures but conceivable by this disclosure, the support column 300 can be inclined or tilted. Also, for example, the support column 300 can be positioned radially closer to the haptic radial inner wall 120 than to the haptic radial outer wall 118.

[0106] Furthermore, the thickened front portion 310 shown in Figure 4C can be the same as the thickened front portion 310 shown and described in Figure 4B. For example, the thickened front portion 310 can be the portion of the haptic front wall 312 where the thickness of the haptic front wall 312 is greater than the thickness of the haptic rear wall 314 at the corresponding radial position (i.e., the same radial position) with respect to the optical portion 102. Alternatively, for example, the thickened front portion 310 can be the portion of the haptic front wall 312 where the thickness of the haptic front wall 312 changes radially, but the thickness of the haptic front wall 312 is still greater than the thickness of the haptic rear wall 314 along the same radial direction. As a more specific example, the thickness of the haptic front wall 312 at a first radial position (with respect to the optical portion 102) can be greater than the thickness of the haptic rear wall 314 at the same first radial position. Furthermore, the thickness of the haptic front wall 312 at the second radial position, which is closer to the optical portion 102 (than the first radial position), may be thinner or thicker than the thickness of the haptic front wall 312 at the first radial position, but it can nevertheless be thicker than the thickness of the haptic rear wall 314 at the same second radial position.

[0107] Figure 4C also shows that the cross-sectional profile of the haptic 104 is asymmetrical. This asymmetry can be seen by comparing the front profile 324 of the cross-sectional profile of the haptic 104 with the rear profile 326 of the haptic 104. For example, the cross-sectional profiles show that the front profile 324 of the haptic 104 is not the same as the rear profile 326 of the haptic 104.

[0108] Figures 4A–4C also show that a portion of the haptic 104 can be fabricated from a composite material. The composite material may contain, or be partially fabricated from, the same cross-linked copolymer used to fabricate the energy-absorbing component, the multiple inflatable microspheres, and the rest of the haptic 104. For example, the composite material may be any of the composite materials disclosed in U.S. Patent Application Publication No. 2021 / 0100650, the entirety of which is incorporated herein by reference.

[0109] The optical portion 102 (see, for example, Figures 2, 3A, and 3B) can be configured to change shape in response to external energy (e.g., light energy 125, see Figures 3A and 3B) being directed to the composite material constituting part of the haptic 104 of the IOL 100 after implantation. As a result, the base power of the optical portion 102 can be adjusted after the IOL 100 has been implanted in the patient's eye by directing external energy (e.g., light energy 125, see Figures 3A and 3B) to the composite material constituting part of the haptic 104.

[0110] For example, the base frequency of the optical portion 102 can be configured to vary between approximately ±0.05D and approximately ±0.5D in response to external energy (e.g., pulses of laser light 125) being directed onto the composite material. The total base frequency of the optical portion 102 can be configured to vary between approximately ±1.0D and approximately ±2.0D. The change in base frequency can be a continuous change.

[0111] In some embodiments, the external energy can be optical energy. In these embodiments, the optical energy can be laser light 125 (see, for example, Figures 3A and 3B). Laser light 125 can have a wavelength of about 488 nm to about 650 nm. For example, laser light 125 can be green laser light. Green laser light can have a wavelength of about 532 nm. In other embodiments, laser light 125 can have a wavelength of about 946 nm to about 1120 nm. For example, laser light 125 can have a wavelength of about 1030 nm. Also, for example, laser light 125 can have a wavelength of about 1064 nm. In some embodiments, laser light 125 can be emitted by a neodymium-doped yttrium aluminum garnet (Nd:YAG) laser. In other embodiments, laser light 125 can be emitted by a femtosecond laser.

[0112] In some embodiments, the energy-absorbing component may include an energy-absorbing pigment or dye. For example, the energy-absorbing pigment may be graphitized carbon black. Alternatively, for example, the energy-absorbing pigment may be an azo dye such as Disperse Red 1 dye. In these and other embodiments, the expandable component may be an expandable microsphere comprising a thermoplastic shell and a foaming agent contained within the thermoplastic shell.

[0113] As shown in Figures 4A to 4C, the composite material can be configured as an internal passage expander 128 and an internal passage space filler 126. The internal passage expander 128 can be a portion of the haptic 104 made of composite material, designed to expand the haptic fluid internal passage 106, i.e., increase its volume, in response to external energy being directed toward the internal passage expander 128. The internal passage space filler 126 can be a portion of the haptic 104 made of composite material, designed to reduce the volume of the haptic fluid internal passage 106 in response to external energy being directed toward the internal passage space filler 126.

[0114] The internal passage expansion member 128 can be positioned within a channel 148 defined within the haptic radial inner wall 120. The channel 148 can be in fluid communication with the haptic fluid internal passage 106 or can be part of the haptic fluid internal passage 106. A portion of the channel 148 can extend into the haptic radial inner wall 120.

[0115] In some embodiments, the internal passage expander 128 can be positioned in the innermost radial portion of the channel 148. As shown in Figures 4A-4C, the haptic radial inner wall 120 can taper as it approaches the optical portion 102. The internal passage expander 128 can be positioned within the channel 148 near the tapered tip of the haptic radial inner wall 120.

[0116] The volume of the haptic fluid internal passage 106 can be increased when the internal passage expander 128 expands in response to external energy being directed toward the internal passage expander 128 (thus widening the channel 148). This allows the fluid in the optical partial fluid chamber 108 (see, for example, Figures 2, 3A, and 3B) to be drawn out of the optical partial fluid chamber 108 and into the haptic fluid internal passage 106. As a result, in response to external energy being directed toward the internal passage expander 128, at least one of the forward element 130 and the rear element 132 can decrease its curvature, and the base degree of the optical portion 102 can be reduced.

[0117] The internal passage space filler 126 can function as part of the haptic radial inner wall 120. For example, the internal passage space filler 126 can function as part of the haptic radial inner wall 120 behind the channel 148.

[0118] The volume of the haptic fluid internal passage 106 can contract as the internal passage space filler 126 expands (therefore occupying space within the haptic fluid internal passage 106) in response to external energy being directed toward it. This allows the fluid within the haptic fluid internal passage 106 to be pushed into or otherwise moved into the optical partial fluid chamber 108 (see, for example, Figures 2, 3A, and 3B). As a result, in response to external energy being directed toward the internal passage space filler 126, at least one of the forward element 130 and the rear element 132 can increase its curvature, and the base degree of the optical portion 102 can increase.

[0119] One technical challenge faced by the applicants is how to counteract the effects of fibrous ACC without interfering with the expandable portions of the haptic 104 made of composite material (e.g., internal passage space filler 126 and internal passage expander 128). The technical solution discovered and developed by the applicants is an ACC prevention function 200 disclosed herein, which includes a thickened front section 310 and / or a support 300 positioned within the haptic fluid internal passage 106. The thickened front section 310 and / or the support 300 (not made of the same composite material used to manufacture the internal passage space filler 126 and / or internal passage expander 128) can counteract the effects of fibrous ACC without substantially affecting the ability of the internal passage space filler 126 to expand and occupy space within the haptic fluid internal passage 106 and the ability of the internal passage expander 128 to expand and increase the volume of the haptic fluid internal passage 106.

[0120] In fact, one additional advantage of the IOL 100, which includes the ACC prevention function 200 and composite material, is the ability to adjust the base power of the IOL 100 after implantation by directing external energy (e.g., laser light 125) to the composite material (e.g., by a clinician such as an ophthalmologist). For example, this can be done specifically to counteract the effects of anterior capsule contraction when the ACC prevention function 200 (e.g., the thickened anterior portion 310 and the support 300) is not sufficient to counteract all of the unwanted myopia shift caused by the proliferation of fibrous tissue along the anterior portion of the lens capsule after implantation.

[0121] Figure 5A shows a perspective view of one embodiment of the haptic 104 of the IOL 100, including the ACC prevention function 200. As shown in Figure 5B, the support column 300 can be an example of the ACC prevention function 200. Figure 5B shows the haptic 104 with its distal end 116 removed to show a cross-section of the haptic 104.

[0122] As shown in Figures 5A and 5B, the proximal mounting end 114 of the haptic 104 can be terminated with a substantially flat interface 500. The flat interface 500 allows the haptic 104 to be bonded to a corresponding interface (also flat) protruding from the reinforcing portion 112 of the optical portion 102, or otherwise joined. In some embodiments, the haptic 104 can be bonded or attached to the optical portion 102 via the same biocompatible adhesive 150 used to bond the front element 130 to the rear element 132.

[0123] The corresponding interface can extend radially from the optical portion 102. For example, the corresponding interface can extend radially beyond the outer circumferential surface 122 of the optical portion 102 (for example, by about 10 micrometers to 1.0 mm beyond the outer circumferential surface 122 of the optical portion 102).

[0124] Figures 5A and 5B also show that a substantially flat interface 500 can define a haptic fluid port 502. The haptic fluid port 502 can be an opening that serves as the proximal end of the haptic fluid internal passage 106. When the flat interface 500 of the haptic 104 is coupled to the corresponding interface of the optical portion 102, the haptic fluid port 502 can be fluid-connected to or fluid-communicated with one or more outward-facing openings that serve as the end of the fluid channel 110 (see, for example, Figure 2). Fluid entering the optical portion fluid chamber 108 (e.g., silicone oil) can exit the haptic fluid internal passage 106 through the haptic fluid port 502 and enter the fluid channel 110. Furthermore, fluid exiting the optical portion fluid chamber 108 can enter the haptic fluid internal passage 106 through the haptic fluid port 502.

[0125] Although Figure 5B shows only one support column 300 within the haptic fluid internal passage 106, the present disclosure suggests that the haptic fluid internal passage 106 may include multiple support columns 300 positioned along its length (see, for example, Figure 2). In some embodiments, the support columns 300 may be positioned at regular intervals along the length of the haptic fluid internal passage 106. In other embodiments, the support columns 300 may be positioned at variable distances from one another along the length of the haptic fluid internal passage 106.

[0126] Figure 6 shows one embodiment of method 600 for implanting an IOL 100 having one or more ACC prevention functions. Method 600 may include removing at least a portion of the anterior capsule wall of the patient's lens capsule in step 602 to form a capsulotomy. The term “capsulotomy” can refer to either a circular opening formed along the anterior capsule wall of the lens capsule, or the procedure for forming such an opening. In some embodiments, the capsulotomy can be formed using a cystotome needle, a lens capsulcus (e.g., an Utrata forceps), or a combination thereof. In other embodiments, the capsulotomy can be formed using a femtosecond laser. The capsulotomy may be formed as part of phacoemulsification. In certain embodiments, phacoemulsification may be any of the phacoemulsification procedures disclosed in U.S. Patent No. 9,149,388; U.S. Patent No. 9,119,701; and U.S. Patent No. 8,784,361, the entirety of which is incorporated herein by reference.

[0127] In other embodiments, the capsulotomy may be formed as part of a manual micro-incision cataract surgery (MSICS) procedure.

[0128] Method 600 may also include a step in step 604 in which cellular material is removed from within the lens capsule using a lens capsule polishing tool. Step 604 can be performed after the patient's natural lens has been removed. For example, step 604 can be performed after emulsifying the natural lens using an ultrasonic lens emulsification and aspiration probe and aspirating it from the lens capsule. Cellular material may include residual lens epithelial cells, lens capsule, or a combination thereof that remain after the patient's natural lens has been removed.

[0129] Removal of cellular material may include scraping the cellular material from the underside of the remaining portion of the anterior capsule wall (see, for example, Figure 7). For example, step 604 may include scraping the cellular material from the underside of the anterior capsule wall surrounding the capsule incision.

[0130] In some embodiments, the lens capsule polishing tool may include a hooked end having a flattened, rounded tip. In certain embodiments, the flattened, rounded tip may be coated with silicone or otherwise covered. For example, the lens capsule polishing tool may be a lens capsule sweep polisher (e.g., a Singer sweep polisher).

[0131] Step 604 may further include perfusing the lens capsule with a viscoelastic fluid as part of a procedure to remove tissue fragments, etc., and using a suction device to aspirate the viscoelastic fluid and any cellular material scraped off from the lens capsule. In certain embodiments, the lens capsule may be perfused and aspirated using an irrigator-suction device.

[0132] Method 600 may further include, in step 606, inserting the IOL 100 disclosed herein into the lens capsule through a capsulotomy. As already disclosed, the IOL 100 may include an optical portion 102 and one or more haptics 104, the haptics including an ACC prevention function configured to maintain the shape of the haptic fluid internal passage 106 in response to a force applied to one or more haptics 104 as a result of anterior capsule contraction after implantation.

[0133] Figure 7 shows a lens capsule polishing tool 700 that extends from the capsulotomy incision 704 into the lens capsule 702 and is used to scrape off cellular material 706 from the lower side 708 of the anterior capsule wall.

[0134] As mentioned above, cellular material may include residual lens epithelial cells, lens capsule, or a combination thereof, remaining after the patient's natural lens has been removed. One technical challenge faced by the applicants is that residual cellular material (e.g., lens epithelial cells remaining after phacoemulsification) can proliferate and transform into fibrous tissue, which can pull and contract the anterior capsule. One technical solution discovered and developed by the applicants is to have a clinician (e.g., an ophthalmologist) use a lens capsule polishing tool to scrape off the cellular material from the underside of the anterior capsule wall of the lens capsule, and then insert an IOL containing one or more haptic with ACC prevention functions into the lens capsule. With such a solution, the design of the IOL is not complicated, and the IOL can be manufactured in a cost-effective manner.

[0135] Figure 7 shows that the lens capsule polishing tool 700 may include a hooked end 710 having a flattened, rounded tip 712. For example, the lens capsule polishing tool 700 may be a lens sweep polisher such as a Singer sweep polisher. In certain embodiments, the flattened, rounded tip 712 may be covered with silicone or by other means.

[0136] This disclosure also covers the following:

[0137] Article 1. An intraocular lens comprising an optical portion including an optical partial fluid chamber, and a haptic having a proximal end and a distal free end connected to the optical portion, wherein the haptic includes a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical partial fluid chamber, the haptic fluid internal passage being surrounded by a haptic radial lateral wall, a haptic radial medial wall, a haptic anterior wall, and a haptic outer wall, the thickness of which is greater than that of the haptic posterior wall.

[0138] Paragraph 2. The intraocular lens of Paragraph 1, wherein the thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall at the corresponding radial position with respect to the optical portion.

[0139] Paragraph 3. The intraocular lens of Paragraph 1, wherein the thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall at a first radial position with respect to the optical portion, and the thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall at a second radial position with respect to the optical portion, and the second radial position is radially closer to the optical portion than the first radial position.

[0140] Section 4. The thickness refers to the anterior-posterior thickness measured in the anterior-posterior direction, as defined in Section 1 of the intraocular lens.

[0141] Section 5. The thickness of the anterior haptic wall is measured from the anterior wall surface of the internal passage to the anterior point along the outer surface of the anterior haptic wall, and the thickness of the posterior haptic wall is measured from the posterior wall surface of the internal passage to the posterior point along the outer surface of the posterior haptic wall, as described in Section 4.

[0142] Section 6. The thickness refers to the orthogonal thickness measured in the orthogonal direction, as defined in Section 1 of the intraocular lens.

[0143] Section 7. The intraocular lens of Section 1, wherein the thickness of the anterior haptic wall is greater than the thickness of the radially lateral haptic wall.

[0144] Section 8. The intraocular lens of Section 1, with the haptic anterior and haptic posterior walls made from the same polymer material.

[0145] Section 9. The intraocular lens of Section 1, wherein the haptic anterior wall is made of a different material from the haptic posterior wall.

[0146] Section 10. The intraocular lens of Section 1, wherein the thickness of the haptic radial medial wall is radially greater than the thickness of the haptic radial lateral wall.

[0147] Section 11. The haptic radial medial wall is the intraocular lens of Section 1, in which the shape of the haptic radial medial wall tapers as it approaches the optical portion.

[0148] Section 12. An intraocular lens of Section 1, further comprising one or more struts positioned within a haptic fluid internal passage, wherein the one or more struts are configured to maintain the shape of the haptic fluid internal passage in response to a force haptically applied as a result of anterior capsule contraction.

[0149] Item 13. One or more struts extending from the anterior wall of the internal passage to the posterior wall of the internal passage, the intraocular lens as described in Item 12.

[0150] Paragraph 14. An intraocular lens as described in Paragraph 12, consisting of one or more supports made of the same material as one or more walls of the haptic.

[0151] Section 15. An intraocular lens as described in Section 12, wherein one or more struts are positioned radially closer to the haptic radial medial wall than to the haptic radial lateral wall.

[0152] Paragraph 16. An intraocular lens comprising an optical portion including an optical partial fluid chamber, a haptic having a proximal end and a distal free end connected to the optical portion, the haptic including a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical partial fluid chamber, and one or more struts disposed within the haptic fluid internal passage, the one or more struts configured to maintain the shape of the haptic fluid internal passage in response to a force applied to the haptic as a result of anterior capsule contraction.

[0153] Item 17. One or more struts extending from the anterior wall of the internal passage to the posterior wall of the internal passage, the intraocular lens as described in Item 16.

[0154] Paragraph 18. An intraocular lens as described in Paragraph 16, consisting of one or more supports made of the same material as one or more walls of the haptic.

[0155] Section 19. The intraocular lens of Section 16, wherein the haptic fluid internal passage is surrounded by a haptic radially lateral wall, a haptic radially medial wall, a haptic anterior wall, and a haptic posterior wall.

[0156] Section 20. An intraocular lens as described in Section 19, wherein one or more struts are positioned radially closer to the haptic radial medial wall than to the haptic radial lateral wall.

[0157] Section 21. An intraocular lens as described in Section 19, wherein the thickness of the haptic radial medial wall is greater in the radial direction than the thickness of the haptic radial lateral wall.

[0158] Section 22. The haptic radial medial wall is an intraocular lens as described in Section 19, in which the shape of the haptic radial medial wall tapers as it approaches the optical portion.

[0159] Paragraph 23. A method for implanting an intraocular lens, comprising the steps of: removing at least a portion of the anterior capsule wall of the patient's lens capsule to form a capsular incision; removing cellular material from within the lens capsule using a lens capsule polishing tool; and inserting an intraocular lens into the lens capsule through the capsular incision, wherein the intraocular lens comprises an optical portion including an optical partial fluid chamber, and a haptic having a proximal end and a distal free end connected to the optical portion, the haptic comprising a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical partial fluid chamber, and the haptic being configured to maintain the shape of the haptic fluid internal passage in response to force applied to the haptic as a result of anterior capsule contraction after implantation.

[0160] Section 24. The method of Section 23, wherein the step of removing cellular material further includes the step of scraping off the cellular material from the underside of the remaining portion of the anterior capsule wall after the capsule incision has been formed.

[0161] Section 25. The lens capsule polishing tool is a lens capsule sweep polisher, as described in Section 23.

[0162] Section 26. A lens capsule polishing tool comprising a hooked end with a flattened, rounded tip, as described in Section 23.

[0163] Section 27. The method of Section 23, wherein the haptic fluid internal passage of the intraocular lens is surrounded by a haptic radially lateral wall, a haptic radially medial wall, a haptic anterior wall, and a haptic posterior wall, the thickness of which is greater than the thickness of the haptic posterior wall.

[0164] Paragraph 28. The method of paragraph 27, further comprising one or more supports positioned within a haptic fluid internal passage for the intraocular lens.

[0165] Paragraph 29. The method of paragraph 23, further comprising one or more supports positioned within a haptic fluid internal passage for the intraocular lens.

[0166] Paragraph 30. An intraocular lens comprising an optical portion including an optical partial fluid chamber, and a haptic having a proximal end and a distal free end connected to the optical portion, wherein the haptic includes a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical partial fluid chamber, and the cross-sectional profile of the haptic at a certain position along the haptic fluid internal passage is asymmetrical such that the anterior profile of the cross-sectional profile is not the same as the posterior profile of the cross-sectional profile.

[0167] Several embodiments have been described. Nevertheless, those skilled in the art will understand that various changes and modifications can be made to this disclosure without departing from the spirit and scope of the embodiments. Elements of systems, devices, apparatus and methods shown in any embodiment are illustrative for that particular embodiment and can be used in combination or otherwise in other embodiments within this disclosure. For example, the steps of any method depicted in the figures or described in this disclosure do not require a specific sequence or sequence shown or described in order to achieve the desired result. In addition, other step operations may be provided, or steps or operations may be excluded or omitted from the described method or process. Furthermore, any component or part of any apparatus or system described in the figures or described in this disclosure may be removed, excluded or omitted in order to achieve the desired result. In addition, certain components or parts of systems, devices or apparatus shown or described herein have been omitted for brevity and clarity.

[0168] Therefore, other embodiments are included within the scope of the claims set forth below, and this specification and / or drawings may be considered illustrative rather than restrictive.

[0169] Each of the individual variations or embodiments described and illustrated herein has individual components and features that may be readily separated from or readily combined with any of the features of any other variation or embodiment. Modifications can be made to adapt specific situations, materials, substance compositions, processes, process actions, or steps to the object, spirit, or scope of the invention.

[0170] The methods described herein may be performed in any logically possible order of the events described, or in the order in which the events are described. Furthermore, additional steps or operations may be provided or omitted to achieve the desired result.

[0171] Furthermore, if a range of values ​​is provided, all values ​​between the upper and lower limits of that range, as well as any other specified values ​​within that specified range or values ​​contained therein, are also included in the present invention. Any optional feature of the described variant of the present invention may be expressed and claimed, either independently or in combination with any one or more of the features described herein. For example, a statement of a range of 1 to 5 should be considered to disclose partial ranges such as 1 to 3, 1 to 4, 2 to 4, 2 to 5, 3 to 5, and individual numerical values ​​within those ranges, such as 1.5, 2.5, etc., and any whole or partial increments between them.

[0172] All existing subject matter referenced herein (e.g., publications, patents, patent applications) is incorporated herein by reference in its entirety, except where such subject matter may conflict with the subject matter of the present invention (in which case the material present herein shall prevail). References are provided only with respect to disclosures prior to the filing date of this application. Nothing in this specification should be construed as acknowledging that the present invention is not entitled to a prior date by prior art.

[0173] References to singular items include the possibility of multiple identical items existing. More specifically, where used herein and in the accompanying claims, the singular forms “a,” “an,” “the said,” and “the” include the plural form unless the context clearly requires a different interpretation. Furthermore, it should be noted that claims may be drafted to exclude optional elements. Therefore, this statement is intended to serve as a prior basis for using exclusive terms such as “alone,” “only,” or for using “negative” limitations in connection with specifying claim elements. Unless otherwise specified, all technical and scientific terms used herein have the same meaning as generally understood by those skilled in the art to which the invention pertains.

[0174] A reference to the phrase "at least one of ~" means any combination of one or more of the items or components (or a list of items or components) that such a phrase modifies. For example, the phrase "at least one of A, B, and C" means (i) A, (ii) B, (iii) C, (iv) A, B, and C, (v) A and B, (vi) B and C, or (vii) A and C.

[0175] For understanding the scope of this disclosure, “comprising” and its derivatives are intended to be open-ended terms, as used herein, specifying the presence of a specified feature, element, component, group, integer and / or step, but not excluding the presence of other unspecified features, elements, components, group, integer and / or step. The same applies to similar words, such as “including,” “having,” and their derivatives. The terms “part,” “section,” “part,” “component,” “element,” or “component” may have a dual meaning when used in the singular, referring to one part or more parts. As used herein, the directional terms “forward, backward, upward, downward, vertical, horizontal, downward, transverse, lateral, and vertical” and other similar directional terms refer to their positions on a device or apparatus or their directions on a device or apparatus being translated or moved.

[0176] Finally, when used herein, terms of degree such as “substantially,” “about,” and “approximately” mean the stated value, or the stated value plus a reasonable amount of deviation from the stated value such that the final result does not change significantly or substantially (e.g., a maximum deviation of ±0.1%, ±1%, ±5%, or ±10%, such variation is appropriate). For example, “about 1.0 cm” can be interpreted as “1.0 cm” or “0.9 cm to 1.1 cm.” When terms of degree such as “about” or “approximately” are used to refer to a number or value that is part of a range, the terms can be used to modify both the minimum and maximum number or value.

[0177] This disclosure is not intended to be limited to any specific form described herein, but rather to encompass alternative forms, modifications, and equivalents of any variations or embodiments described herein. Furthermore, the scope of this disclosure includes all other variations or embodiments that may be obvious to those skilled in the art in view of this disclosure.

Claims

1. It is an intraocular lens, Optical part including an optical fluid chamber, and A haptic having a proximal end coupled to the optical portion and a distal free end, comprising a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical portion fluid chamber, Includes, The haptic fluid internal passage is surrounded by a haptic radial outer wall, a haptic radial inner wall, a haptic front wall, and a haptic rear wall. The thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall. Intraocular lens.

2. The intraocular lens according to claim 1, wherein the thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall at a corresponding radial position with respect to the optical portion.

3. The intraocular lens according to claim 1, wherein the thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall at a first radial position with respect to the optical portion, the thickness of the anterior haptic wall is greater than the thickness of the posterior haptic wall at a second radial position with respect to the optical portion, and the second radial position is closer to the optical portion radially than the first radial position.

4. The intraocular lens according to claim 1, wherein the thickness refers to the thickness measured in the anterior-posterior direction.

5. The intraocular lens according to claim 4, wherein the thickness of the anterior haptic wall is measured from the anterior wall surface of the internal passage to the foremost point along the outer surface of the anterior haptic wall, and the thickness of the posterior haptic wall is measured from the posterior wall surface of the internal passage to the posterior point along the outer surface of the posterior haptic wall.

6. The intraocular lens according to claim 1, wherein the thickness refers to the orthogonal thickness measured in the orthogonal direction.

7. The intraocular lens according to claim 1, wherein the thickness of the anterior haptic wall is greater than the thickness of the radially lateral haptic wall.

8. The intraocular lens according to claim 1, wherein the anterior haptic wall and the posterior haptic wall are made of the same polymer material.

9. The intraocular lens according to claim 1, wherein the anterior haptic wall is made of a different material from the posterior haptic wall.

10. The intraocular lens according to claim 1, wherein the thickness of the haptic radial inner wall is radially thicker than the thickness of the haptic radial outer wall.

11. The intraocular lens according to claim 1, wherein the haptic radial medial wall tapers in shape as it approaches the optical portion.

12. The intraocular lens according to claim 1, further comprising one or more struts positioned within the haptic fluid internal passage, wherein the one or more struts are configured to maintain the shape of the haptic fluid internal passage in response to a force applied to the haptic as a result of anterior capsule contraction.

13. The intraocular lens according to claim 12, wherein the one or more support columns extend from the front wall surface of the internal passage to the rear wall surface of the internal passage.

14. The intraocular lens according to claim 12, wherein the one or more support columns are made of the same material as the one or more walls of the haptic.

15. The intraocular lens according to claim 12, wherein one or more of the support columns are positioned radially closer to the haptic radial inner wall than to the haptic radial outer wall.

16. It is an intraocular lens, Optical part including the optical fluid chamber, A haptic having a proximal end and a distal free end coupled to the optical portion, comprising a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical portion fluid chamber, and An intraocular lens comprising one or more struts positioned within the haptic fluid internal passage, wherein the one or more struts are configured to maintain the shape of the haptic fluid internal passage in response to a force applied to the haptic as a result of anterior capsule contraction.

17. The intraocular lens according to claim 16, wherein one or more support columns extend from the front wall surface of the internal passage to the rear wall surface of the internal passage.

18. The intraocular lens according to claim 16, wherein the one or more support columns are made of the same material as the one or more walls of the haptic.

19. A method for implanting an intraocular lens, The steps include removing at least a portion of the anterior capsule wall of the patient's lens capsule to form a capsulotomy, The steps include removing cellular material from within the lens capsule using a lens capsule polishing tool, The steps include inserting the intraocular lens into the lens capsule through the capsular incision, Includes, The aforementioned intraocular lens is Optical part including an optical fluid chamber, and A haptic having a proximal end and a distal free end coupled to the optical portion, comprising a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical portion fluid chamber, wherein the haptic is configured to maintain the shape of the haptic fluid internal passage in response to a force applied to the haptic as a result of anterior capsule contraction after implantation. method.

20. It is an intraocular lens, Optical part including an optical fluid chamber, and A haptic having a proximal end coupled to the optical portion and a distal free end, comprising a haptic fluid internal passage extending through at least a portion of the haptic and in fluid communication with the optical portion fluid chamber, Includes, An intraocular lens in which the cross-sectional profile of the haptic at a position along the haptic fluid internal passage is asymmetric, and the anterior profile of the cross-sectional profile is not the same as the posterior profile of the cross-sectional profile.

Images