Thermally adjustable intraocular lens

Abstract

A method and system provides an ophthalmic lens (110) including a lens body (120) having a chamber (126) therein, a reservoir module (130) coupled with the lens body, and an optical fluid (140). At least a portion of the lens body is flexible. The reservoir module includes a reservoir (132A, 132B) and a heat sensitive portion (134) bordering the reservoir. The reservoir has a reservoir volume and is fluidly connected with the chamber. The heat-sensitive portion has a shape responsive to a temperature of at least 45 degrees Celsius such that the reservoir volume changes in response to at least a portion of the heat-sensitive portion reaching the temperature. The optical fluid resides in the chamber and the reservoir. A change in the volume of the reservoir causes a portion of the optical fluid to flow between the reservoir and the chamber such that the flexible portion of the lens body undergoes a shape change corresponding to the base power change.

Description

[0001] This application is a divisional application of the invention patent application named "Thermally Adjustable Intraocular Lens", with a divisional filing date of March 4, 2021, and application number 202110237657.X. Technical Field

[0002] The present disclosure relates generally to ophthalmic lenses and, more particularly, to a thermo-adjustable intraocular lens. Background Art

[0003] An intraocular lens (IOL) is implanted in a patient's eye to replace the patient's lens, or in the case of a phakic IOL, to supplement the patient's lens. Some conventional IOLs are single-focal-length IOLs, while others are multifocal IOLs. Single-focal-length IOLs have a single focal length or power. Objects at the focal length of the eye / IOL are sharp, while objects closer or farther away may be blurry. Multifocal IOLs, on the other hand, have at least two focal lengths. Multifocal lenses can help patients with conditions such as myopia. Typically, a physician selects an IOL with the appropriate base power and other features for a patient. The selected IOL is implanted during eye surgery, which is usually performed for other conditions such as cataracts.

[0004] Although IOLs work acceptably well in most patients, the selected IOL may have the wrong power for the patient. The IOL can be removed and a new IOL can be selected and implanted. However, it is not desirable to perform additional ophthalmic surgery for this purpose. Other IOLs can adjust their power non-invasively. For example, an IOL may be sensitive to ultraviolet (UV) light. Such IOLs can be exposed to UV light in order to change the power of the lens. Exposure to UV light can change the shape of the IOL and thus change the basic power of the lens. Although this method allows the basic power of the IOL to be adjusted, such IOLs require the patient to wear UV light blocking glasses until the adjustment phase is completed. The adjustment phase is usually about two weeks. It is inconvenient and undesirable for the patient to wear UV light blocking glasses twenty-four hours a day for two weeks. Once the adjustment phase is completed, the changes in the IOL must be locked to prevent further changes in the IOL power due to daily exposure to UV light. Once these changes are locked, the basic power of the IOL cannot be further adjusted. There are other mechanisms for changing the basic power of the lens, such as changing tension. However, these mechanisms are accompanied by problems and disadvantages.

[0005] Therefore, there is a need for an improved mechanism for non-invasively changing the base power of an IOL. Summary of the invention

[0006] A method and system provide an ophthalmic lens, the ophthalmic lens including a lens body having a chamber therein, a reservoir module coupled to the lens body, and an optical fluid. At least a portion of the lens body is flexible. The reservoir module includes a thermosensitive portion and has a reservoir therein. The reservoir has a reservoir volume and is fluidly connected to the chamber. The thermosensitive portion of the reservoir module interfaces with at least a portion of the reservoir. The thermosensitive portion has a shape responsive to a temperature of at least forty-five degrees Celsius such that the reservoir volume changes in response to at least a portion of the thermosensitive portion reaching the temperature. The optical fluid resides in the chamber and the reservoir. The optical fluid has an optical fluid refractive index that matches the lens body refractive index to within 0.1. The change in the reservoir volume causes a portion of the optical fluid to flow between the reservoir and the chamber such that at least a portion of the lens body undergoes a shape change corresponding to a change in base power.

[0007] According to the methods and systems disclosed herein, a physician may be able to better and more easily non-invasively change the power of an implanted ophthalmic device, such as an IOL. BRIEF DESCRIPTION OF THE DRAWINGS

[0008] For a more thorough understanding of the present disclosure and its advantages, reference is now made to the following description taken in conjunction with the accompanying drawings, in which like reference numerals indicate like features, and in which:

[0009] Figures 1A to 1E depicts various views of an exemplary embodiment of an adjustable thermal ophthalmic device;

[0010] FIG. 2A to FIG. 2D depicts different views of another exemplary embodiment of an adjustable thermal ophthalmic device;

[0011] Figure 3A and Figure 3B depicts different views of another exemplary embodiment of a tunable heat ophthalmic lens;

[0012] Figure 4 depicts a perspective cutaway view of another exemplary embodiment of a tunable heat ophthalmic lens;

[0013] Figure 5 is a flow chart depicting an exemplary embodiment of a method of providing an adjustable thermal ophthalmic device; and

[0014] Figure 6 is a flow chart depicting an exemplary embodiment of a method of using an adjustable thermal ophthalmic device. DETAILED DESCRIPTION

[0015] Exemplary embodiments relate to ophthalmic devices, such as intraocular lenses (IOLs). The following description is provided to enable a person of ordinary skill in the art to make and use the invention, and is provided in the context of a patent application and its requirements. Various modifications to the exemplary embodiments and general principles and features described herein will be apparent. These exemplary embodiments are described primarily in terms of specific methods and systems provided in the specific embodiments. However, these methods and systems will operate effectively in other embodiments. Phrases such as "exemplary embodiments," "one embodiment," and "another embodiment" may refer to the same or different embodiments, as well as to multiple embodiments. These embodiments will be described with respect to systems and / or devices having certain components. However, these systems and / or devices may include more or fewer components than those shown, and the arrangement and type of these components may be changed without departing from the scope of the invention. These exemplary embodiments will also be described in the context of specific methods having certain steps. However, the methods and systems still operate effectively for other methods having different and / or additional steps and steps in different orders inconsistent with the exemplary embodiments. Therefore, the present invention is not intended to be limited to the embodiments shown, but is given the broadest scope consistent with the principles and features described herein. The methods and systems are described in terms of singular items rather than plural items. One of ordinary skill in the art will recognize that these singular terms encompass the plural.For example, a chamber may include one or more chambers.

[0016] A method and system provide an ophthalmic lens, the ophthalmic lens including a lens body having a chamber therein, a reservoir module coupled to the lens body, and an optical fluid. At least a portion of the lens body is flexible. The reservoir module includes a thermosensitive portion and has a reservoir therein. The reservoir has a reservoir volume and is fluidly connected to the chamber. The thermosensitive portion of the reservoir module interfaces with at least a portion of the reservoir. The thermosensitive portion has a shape responsive to a temperature of at least forty-five degrees Celsius such that the reservoir volume changes in response to at least a portion of the thermosensitive portion reaching the temperature. The optical fluid resides in the chamber and the reservoir. The optical fluid has an optical fluid refractive index that matches the lens body refractive index to within 0.1. The change in the reservoir volume causes a portion of the optical fluid to flow between the reservoir and the chamber such that at least a portion of the lens body undergoes a shape change corresponding to a change in base power.

[0017] Figures 1A to 1E An exemplary embodiment of a heat-adjustable ophthalmic device 100 that may be used as an IOL is depicted. For simplicity, the ophthalmic device 100 is referred to as IOL 100 hereinafter. Figure 1A A plan view of IOL 100 is depicted, and Figures 1B to 1EA side view of an ophthalmic lens 110 is depicted. For clarity, Figures 1A to 1E Not to scale. IOL 100 includes an ophthalmic lens 110 and haptics 102 and 104. Portions of ophthalmic lens 110 may include various optical materials, including but not limited to one or more of silicone, hydrogel, and acrylic. Haptics 102 and 104 are used to hold ophthalmic device 100 in place in the patient's eye (not explicitly shown). However, in other embodiments, other mechanisms may be used to hold the ophthalmic device in place in the eye. For clarity, the following discussion of Figures 1B to 4 Although the ophthalmic lens 110 is Figure 1A is depicted in plan view as having a circular cross-section, but in other embodiments other shapes may be used.

[0018] The ophthalmic lens 110 (hereinafter referred to as the "lens") has an optical axis 106 as well as a lens body 120, a reservoir module 130, and an optical fluid 140. Although referred to as a part of the lens 110, the optical axis 106 can be considered to be an imaginary line passing through the center of the front surface and the back surface. Therefore, the optical axis 106 is shown as a dotted line. The optical axis 106 can also be perpendicular to the surface at the point where it passes through the surface. Although not shown, the front surface and / or the back surface can have other features, including but not limited to diffraction gratings. The reservoir module 130 and the lens body 120, although indicated as separate components, can be integrated together into a single piece. For example, some or all of the lens body 120 and the reservoir module can be an integral structure formed together.

[0019] The lens body 120 forms the main optical component of the IOL 100. Thus, light passes through the lens body 120 and other components of the eye, allowing the patient to see. In some embodiments, the reservoir module 130 is not designed to transmit light for vision. The lens body 120 includes a bottom 122, a flexible portion 124, and a chamber 126. In the illustrated embodiment, the flexible portion 124 is considered to be a flexible membrane 124. Therefore, the flexible portion 124 is referred to as a flexible membrane 124 hereinafter. However, nothing prevents the flexible portion from having another configuration. The chamber 126 can be considered to be a space between the bottom 122 and the flexible membrane 124. The optical fluid 140 discussed below resides at least in the chamber 126.

[0020] In the illustrated embodiment, the bottom 122 has stable optical properties. Thus, the shape of the bottom 122 can be relatively fixed. In other embodiments, the bottom 122 can change shape to some extent in response to changes in the volume of the chamber 126. Conversely, the flexible membrane 124 is flexible and changes shape in response to changes in the volume of the reservoir 126.

[0021] In some embodiments, the bottom 122 and the flexible membrane 124 can be made of the same material, such as AcrySof®, AcrySof®2, and / or other soft optical materials can be used. In other embodiments, the bottom 122 and the flexible membrane 124 can be made of different materials. The bottom 122 can be thick enough so that the shape of the bottom 122 remains substantially unchanged. However, the flexible membrane 124 is thin enough to respond to changes in the volume of the chamber 126. For example, the flexible membrane 124 can be at least eighty microns thick and no more than three hundred microns thick. In other embodiments, other thicknesses can be present. In some embodiments, the flexible membrane 124 has a uniform thickness before providing the optical fluid 140. In other embodiments, the thickness of the flexible membrane 124 can be non-uniform.

[0022] The reservoir module 130 is located at the periphery of the lens body 120 and includes a reservoir 132A / 132B and a heat-sensitive portion 134. Figures 1B to 1D . Thus, reservoirs 132A and 132B (collectively, reservoirs 132A / 132B) and thermally sensitive portions 134A and 134B are shown. In some embodiments, reservoirs 132A and 132B are connected within reservoir module 130 so that fluid can flow around the periphery of lens body 120. For example, reservoirs 132A and 132B can simply be part of a hollow ring (i.e., a tube). In other embodiments, reservoirs 132A and 132B can be disconnected so that any fluid flow between reservoirs 132A and 132B is achieved through chamber 126 of lens body 120. In other embodiments, reservoirs 132A and 132B can have different shapes.

[0023] The reservoirs 132A and 132B are fluidly connected to the chamber 126 of the lens body 120. In the illustrated embodiment, there is simply an inlet / outlet (i.e., a hole or channel) between the chamber 126 and the reservoirs 132A and 132B. In other embodiments, the fluid path between the chamber 126 and the reservoirs 132A and / or 132B can be more complex.

[0024] The optical fluid 140 resides in the chamber 126 and the reservoirs 132A / 132B. For simplicity, the optical fluid 140 is only Figure 1B In the Figure 1C to Figure 1E1, the optical fluid is labeled with the reservoir 132A / 132B and the chamber 126. The optical fluid 140 can flow between the chamber 126 and the reservoir 132A / 132B. Because the optical fluid 140 can be in the chamber 126, the optical fluid 140 is in the path of the light used for vision. Thus, the optical fluid 140 transmits the light. Because the light is refracted by the lens body 120, the optical fluid 140 can also have a refractive index that matches the refractive index of the lens body 120 (e.g., at least the bottom 122 and in some embodiments, the bottom 122 and the flexible membrane 124) to within certain limits. For example, in some embodiments, the refractive index of the optical fluid 140 is within 0.1 of the refractive index of the lens body 120. In some embodiments, the refractive index of the optical fluid 140 differs from the refractive index of the lens body 120 by no more than 0.05. If the lens body 120 is made of a material such as AcrySof® or AcrySof®2, the optical fluid 140 can be a high molecular weight aromatic silicone copolymer liquid.

[0025] The thermosensitive portion 134A and 134B of the reservoir module 130 can be a part of a single thermosensitive portion. For example, the thermosensitive portion 134A and 134B can be a part of a torus occupying a wall of the reservoir 132A / 132B. The thermosensitive portion 134A / 134B can have different shapes in other embodiments. For example, the thermosensitive portion 134A and / or 134B can be spherical, hemispherical, cubic, elliptical or have other discrete shapes. These shapes can be connected or separated. In addition, the thermosensitive portion 134A can have a shape different from the thermosensitive portion 134B. In the illustrated embodiment, the thermosensitive portion 134A and 134B have different sizes. But, in other embodiments, the thermosensitive portion 134A and 134B can have the same size.

[0026] The heat-sensitive portions 134A and 134B change shape in response to reaching a specific temperature (hereinafter referred to as the "glass transition temperature"). In the illustrated embodiment, the heat-sensitive portions 134A and 134B are formed of the same material and have the same glass transition temperature. In other embodiments, the heat-sensitive portions 134A and 134B may be formed of different materials and / or have different glass transition temperatures. It is desirable that such a glass transition temperature of the heat-sensitive portions 134A and 134B is greater than the normal temperature of the eye. It is also desirable that the glass transition temperature is low enough so that the heat-sensitive portions 134A and 134B can reach the glass transition temperature without damaging the eye. In some embodiments, the heat-sensitive portions 134A and 134B are small enough so that even if the temperature reached by the portions 134A and 134B greatly exceeds the normal temperature of the eye, the local heat of these portions 134A and 134B will not adversely affect the eye. For example, it is desirable that the normal temperature of the eye in which the IOL 100 resides may be approximately thirty-five degrees Celsius to forty degrees Celsius. The glass transition temperature of the heat sensitive portions 134A and 134B can be at least forty-five degrees Celsius. In some embodiments, the glass transition temperature can be at least sixty degrees Celsius. In other embodiments, the glass transition temperature can be at least ninety degrees Celsius in some embodiments. In addition, it can be desirable that the glass transition temperature be less than one hundred degrees Celsius.

[0027] At normal temperature of the eye, the shape of the heat-sensitive portions 134A and 134B is constant. If one or both of the heat-sensitive portions 134A and 134B are heated to the glass transition temperature, the shape changes. When cooled, the heat-sensitive portions 134A and 134B maintain the new shape. Then this shape remains unchanged. Thus, normal wear of the IOL 100 does not affect the basic focal length of the lens 110 or the shape of the heat-sensitive portions 134A and 134B. For example, the heat-sensitive portions 134A and 134B can be formed of a shape memory material, such as a shape memory polymer (SMP). In addition, the SMP can have an additive (e.g., a dye or other material) that is added to absorb light in the wavelength range provided by the laser used for heating.

[0028] The operation of IOL 100 can be Figures 1B to 1E First, Figure 1BAs shown, the heat-sensitive portion 134A and 134B have a specific shape. The heat-sensitive portion 134A can be heated to or above the glass transition temperature. In some embodiments, this heating is completed via a laser. For example, the laser can be aimed and emitted to the heat-sensitive portion 134A. The wavelength of the laser is selected to transmit through the cornea and vitreous humor of the eye. In some embodiments, the laser can have a characteristic wavelength of about 1064 nm. In other embodiments, the laser can be within a wavelength bandwidth of 750-850 nanometers. The heat-sensitive portion 134A is heated to at least the glass transition temperature and changes shape.

[0029] Figure 1C The lens 110 is depicted after the heat-sensitive portion 134A has been heated to at least the glass transition temperature. The lens 110 may also have cooled. The heat-sensitive portion 134A' has changed shape. As a result, the volume of the reservoir 132A' has decreased. This forces some of the optical fluid 140 into the chamber 126'. Because the flexible membrane 124' is not rigid, the movement of the optical fluid 140 into the chamber 126' increases the volume of the chamber 126' and changes the shape of the flexible membrane 124'. Thus, the focal power of the lens 110 has changed. Based on the changes in the volumes of the reservoir 132A' and the chamber 126' and the properties of the flexible membrane 124' and the optical fluid 140, the change in the basic focal power of the lens 110 can be determined.

[0030] Alternatively, the heat sensitive portion 134B may be heated to or above the glass transition temperature. The heating may be accomplished using a laser or similar mechanism in the same manner as described above. Figure 1D The lens 110 is depicted after the heat-sensitive portion 134B has been heated. The lens 110 may also have cooled. The heat-sensitive portion 134B' has changed shape. As a result, the volume of the reservoir 132B' has decreased. This forces some of the optical fluid 140 to enter the chamber 126". Because the flexible membrane 124" is not rigid, the movement of the optical fluid 140 into the chamber 126" increases the volume of the chamber 126" and changes the shape of the flexible membrane 124". Thus, the focal length of the lens 110 has changed. Based on the changes in the volumes of the reservoir 132B' and the chamber 126", as well as the characteristics of the flexible membrane 124" and the optical fluid 140, the change in the basic focal length of the lens 110 can be determined. However, because the volume change of the reservoir 132B' is small, the basic focal length of the lens 110 is less than that of the flexible membrane 124". Figure 1D The change in Figure 1C changes in .

[0031] Both heat sensitive portions 134A and 134B may be heated to or above the glass transition temperature. Heating may be accomplished using a laser or similar mechanism in the same manner as described above. Figure 1EThe lens 110 is depicted after the heat-sensitive portions 134A and 134B have been heated. The lens 110 may also have cooled. The heat-sensitive portions 134A' and 134B' have changed shape. As a result, the volume of the reservoirs 132A' and 132B' has decreased. This forces some of the optical fluid 140 to enter the chamber 126'''. Because the flexible membrane 124''' is not rigid, the movement of the optical fluid 140 into the chamber 126''' increases the volume of the chamber 126''' and changes the shape of the flexible membrane 124'''. Thus, the focal length of the lens 110 has changed. Based on the changes in the volumes of the reservoirs 132A' and 132B' and the chamber 126''' and the characteristics of the flexible membrane 124''' and the optical fluid 140, the change in the basic focal length of the lens 110 can be determined. Because the volume changes of the reservoirs 132A' and 132B' are large, the basic focal length of the lens 110 is Figure 1E The change in Figure 1C and Figure 1D For example, if the basic focal length of lens 110 is Figure 1D In the case shown, the basic focal power can be changed by 0.25 diopters. Figure 1C The case shown changes 0.5 diopters and Figure 1E The case shown changes by 0.75 diopters. Further, Figure 1C , Figure 1D as well as Figure 1E The changes shown need not occur simultaneously. Alternatively, these changes can be made later based on updated information and / or changes in the patient's eyes.

[0032] If the lens 110 has an incorrect basic focal power due to changes in the patient or the patient's vision over time, the basic focal power of the lens 110 and therefore the IOL 100 can be changed. In some configurations, the focal power of the lens 110 can be adjusted up or down depending on whether the volume of the reservoir 132A / 132B is reduced or increased. Because the heat-sensitive portions 134A and 134B can be changed via laser, the focal power of the lens 110 can be changed non-invasively. Thus, the risk of invasive procedures, such as changing the IOL, can be avoided. Alternatively, only a simple clinic visit may be required. Changing the basic focal power of the lens 110 via laser heating can also be more cost-effective than changing the entire IOL. In addition, the disadvantages of other non-invasive mechanisms for changing the basic focal power of the lens can be avoided. For example, the change does not need to be limited to the lens 110. Alternatively, additional heat can be applied at any time throughout the life of the lens 110. Further, the lens 110 does not require special glasses, such as UV light protection glasses, to be worn at every moment when the basic focal power is adjusted. Furthermore, a single clinic visit may be sufficient to adjust the power of lens 110. Adjustment may also be faster. In some cases, heating, rapid change in shape of heat-sensitive portion 134A / 134B, flow of fluid between reservoir 132A / 132B and chamber 126, change in volume of chamber 126, and concomitant change in the basic power of the lens may take a few minutes or less. Thus, lens 110 may be more easily adjusted to meet the needs of the patient.

[0033] FIG. 2A to FIG. 2D Another exemplary embodiment of a heat-adjustable ophthalmic lens 150 that may be used as or for an IOL is depicted. For simplicity, the ophthalmic lens 150 is referred to as lens 150 hereinafter. Figures 2A to 2D A side view of an ophthalmic lens 110 is depicted. For clarity, FIG. 2A to FIG. 2D Not to scale. Lens 150 may be an IOL, for example, including lens 150 and may include a haptic ( FIG. 2A to FIG. 2D 1 and 10. In the embodiment of the present invention, a portion of IOL 100 is shown (not shown).

[0034] The lens 150 has an optical axis 156 and a lens body 160, a reservoir module 170, and an optical fluid 190. The lens body 160, the reservoir module 170, the optical fluid 190, and the optical axis 156 are similar to the lens body 120, the reservoir module 130, the optical fluid 140, and the optical axis 106, respectively. Thus, the lens body 160, the bottom 162, the flexible membrane 164, and the chamber 166 are similar to the lens body 120, the bottom 122, the flexible membrane 124, and the chamber 126, respectively. Similarly, the reservoir module 170, the reservoir 172A / 172B, and the thermally sensitive portions 174A and 174B are similar to the reservoir module 130, the reservoir 132A / 132B, and the thermally sensitive portions 134A and 134B, respectively. Finally, the optical fluid 190 is similar to the optical fluid 140. Thus, the structures, functions, and materials of these components can be similar to those discussed above. For example, the refractive index of the optical fluid 190 can be matched to the refractive index of the lens body 160 to within the tolerances discussed above. Although not shown, the front surface and / or the back surface can have other features, including but not limited to diffraction gratings. The reservoir module 170 and the lens body 160, although indicated as separate components, can be integrated together into a single piece.

[0035] Also shown is a microfluidic path 180 that connects the reservoir 172A / 172B with the chamber 166. The ends of the microfluidic path 180 are shown as dashed lines indicating the inlet / outlet of the chamber 166 and the reservoir 172A / 172B. In some embodiments, the microfluidic path 180 is simply a straight channel. However, in other embodiments, the microfluidic path 180 can have another more complex structure.

[0036] The lens body 170 forms the main optical component of the lens 150. In contrast, the reservoir module 170 may not be designed to transmit light for vision. In the illustrated embodiment, the flexible membrane 164 is flexible and has optical properties that can change in response to changes in the volume of the chamber 166. In contrast, the bottom 162 has stable optical properties and the shape can be relatively fixed. In other embodiments, the bottom 162 can change shape to some extent in response to changes in the volume of the chamber 166.

[0037] The reservoir module 170 is located at the periphery of the lens body 160. In some embodiments, the reservoirs 172A and 172B are connected within the reservoir module 170 so that the fluid can flow around the periphery of the lens body 160. In other embodiments, the reservoirs 172A and 172B can be disconnected so that any fluid flow between the reservoirs 172A and 172B is achieved through the chamber 166 of the lens body 160. In other embodiments, the reservoirs 172A and 172B can have different shapes.

[0038] The heat-sensitive portions 174A and 174B of the reservoir module 130 may be part of a single heat-sensitive portion. For example, the heat-sensitive portions 174A and 174B may be part of a ring that occupies one wall of the reservoir 172A / 172B. Alternatively, the heat-sensitive portions 174A and 174B may be composed of discrete units. For example, FIG. 2A to FIG. 2D , each thermally sensitive portion 174A and 174B includes a plurality of capsules 175A and 17B, respectively. For simplicity, only one capsule 175A and 175B is labeled in each thermally sensitive portion 174A and 174B, respectively. In some embodiments, each capsule 175A and / or 175B is a single thermally sensitive structure that can be thermally isolated from other capsules. In other embodiments, capsules 175A and 175B are part of a single thermally sensitive structure. Selected areas of thermally sensitive portions 174A and 174B can be individually heated to or above their glass transition temperatures. In the illustrated embodiment, capsules 175A and 175B are generally hemispherical. However, nothing prevents the use of another shape. In the illustrated embodiment, each of capsules 175A and 175B has the same size. Thus, each capsule 175A and 175B can contain / discharge the same volume of optical fluid 190. In other embodiments, capsules 175A and / or 175B can have different sizes. Still, it is desirable to know the volume of optical fluid contained / displaced in each capsule 175A and 175B and to correspond to a known change in base power. For example, each capsule 175A and 175B may correspond to a base power change of 0.25 diopters within a desired tolerance. In some cases, this corresponds to a 0.2 mm diameter change in each capsule 175A and 175B. 3 However, other volumes and other basic focal changes may be used. For example, one capsule 175A may correspond to a 0.25 diopter change, another capsule 175A may correspond to a 0.5 diopter change, and so on. In some embodiments, a focal change of four diopters (e.g., ±2 diopters) may be provided.

[0039] Each of capsules 175A and 175B changes shape in response to the glass transition temperature reached by capsules 175A and 175B. After cooling, this new shape is stable. The shape is basically fixed into a capsule or a flat surface below the glass transition temperature. It is hoped that this glass transition temperature of heat-sensitive portions 174A and 174B significantly exceeds the normal temperature of the eye and is low enough so that heat-sensitive portions 174A and 174B can reach the glass transition temperature without damaging the eye. In some embodiments, capsules 175A and 175B are small enough so that even if the temperature reached by portions 174A and 174B greatly exceeds the normal temperature of the eye, the local heat of these capsules 175A and 175B will not adversely affect the eye. Capsules 175A and 175B can be formed by the SMP described above and can have the glass transition temperature described above.

[0040] As in Figure 2A 172A and 172B. In particular, each of the capsules 175A displaces a substantially hemispherical volume of optical fluid 190 from reservoir 172A. Each of the capsules 175B includes a substantially hemispherical volume of optical fluid 190 in reservoir 172B. As a result, the base power of lens 150 can be increased or decreased by varying amounts depending on whether capsule 175A or capsule 175B is heated to or above its glass transition temperature and the number of capsules 175A or 175B that are so heated.

[0041] The operation of lens 150 is related to FIG. 2A to FIG. 2D In the following discussion, it is assumed that the lens 150 initially has Figure 2A The configuration shown. If the base power of lens 150 is too high, it is desirable for lens 150 to refract less light. This can be accomplished by reducing the curvature of flexible membrane 164. Due to the orientation of capsule 175A / thermosensitive portion 174A relative to reservoir 172A, shape change of the capsule / thermosensitive portion can be used. More specifically, heat is applied to one or more of capsules 175A, such as via a laser. The temperature of this capsule 175A rises above its glass transition temperature. As a result, capsule 175A changes shape.

[0042] Figure 2B An exemplary embodiment of the lens 150 is depicted after sufficient heat has been applied to the capsule 175A, which is closest to the microfluidic path 180, to raise the temperature of the capsule 175A to or above the glass transition temperature. The lens 150 can then be cooled to the ambient temperature of the eye. The capsule 175A closest to the chamber 166' has now become flattened. This capsule has changed from a first shape (hemispherical) to a second shape (substantially flat). This shape change is stable after cooling. As a result, the reservoir 172A' has increased in volume by approximately the volume of the capsule 175A. The reservoir 172B remains unchanged. Therefore, the optical fluid 190 has flowed from the chamber 166' through the microfluidic path 180 to the reservoir 172A'. The pressure of the optical fluid 190 on the flexible membrane 164' is reduced. The flexible membrane 164' becomes flattened and the volume of the chamber 166' is correspondingly reduced. Therefore, the optical power of the lens body 160 is reduced. Therefore, the basic power of the lens 150 has been reduced non-invasively.

[0043] On the contrary, assuming that Figure 2AIn the case shown, it is desirable to increase the base power of the lens 150. To do this, it is desirable that the curvature of the flexible membrane 164 be increased. If one or more of the capsules 175B are heat-treated to obtain a temperature that reaches or exceeds the glass transition temperature, the capsule 175B becomes flat. It is assumed that heat is applied to a single capsule 175B, for example, via a laser. The temperature of this capsule 175B rises to exceed the glass transition temperature of the capsule 175B. As a result, the capsule 175B changes shape.

[0044] Figure 2C An exemplary embodiment of the lens 150 is depicted after sufficient heat has been applied to the capsule 175B', which is closest to the microfluidic path 180, to raise the temperature of the capsule 175B' to or above the glass transition temperature. The lens 150 may also subsequently be cooled to the ambient temperature of the eye. In the heat-sensitive portion 174B' of the reservoir module 170, the capsule closest to the chamber 166" has now become flat. This capsule has changed from a hemispherical shape to a substantially flat shape. As a result, the volume of the reservoir 172B' has been reduced by approximately the volume of the capsule 175B. The reservoir 172A remains unchanged. Therefore, the optical fluid 190 has flowed from the reservoir 172B' through the microfluidic path 180 to the chamber 166". The pressure of the optical fluid 190 on the flexible membrane 164" increases. The volume of the chamber 166" increases and the curvature of the flexible membrane 164" increases accordingly. The change in volume of the chamber 166" may, but need not, be equal to the volume of the capsule 175B. Thus, the optical power of lens 110 is increased. Thus, the basic power of lens 150 can be increased non-invasively.

[0045] It can be determined that it is desirable to further increase the power of the lens 150. In such a case, more capsules 175B can be heated. Figure 2D . As can be seen from the heat-sensitive portion 174B", the other capsule 175B has been heat-treated and is therefore flat. The volume of the reservoir 172B" is further reduced. The optical fluid 190 flows from the reservoir 172B" to the chamber 166". The increase in pressure of the optical fluid in the chamber 164" causes the flexible membrane 164" to further deform and the volume of the chamber 166" to increase. Therefore, the optical power of the lens 150 is further increased. Note that the optical power of the lens 150 can be reduced again by heat-treating one or more of the capsules 175A.

[0046] The properties of lens 150 can be adjusted non-invasively. More specifically, the base power of lens 150 can be increased and / or decreased non-invasively. Thus, benefits similar to those discussed above for lens 110 can be achieved.

[0047] Figure 3A and Figure 3BDepicted are different views of another exemplary embodiment of a tunable thermal ophthalmic lens 200. For simplicity, the ophthalmic lens 200 is referred to as lens 200 hereinafter. Figure 3A and Figure 3B Side and perspective views of various portions of lens 200 are depicted. For clarity, Figure 3A and Figure 3B Not to scale. Lens 200 may be an IOL, for example, comprising a lens and a haptic ( Figure 3A -and Figure 3B 1 (not shown) of a portion of an IOL 100. For simplicity, the optical axis is not shown.

[0048] The lens 200 has a lens body 210, a reservoir module 220, a microfluidic path 230, and an optical fluid ( Figure 3A and Figure 3B 170). The lens body 210, the reservoir module 220, the microfluidic path 230, and the optical fluid are similar to the lens body 120 / 160, the reservoir module 130 / 170, the microfluidic path 180, and the optical fluid 140 / 190, respectively. Thus, the lens body 210, the bottom 212, the flexible membrane 214, and the chamber 216 are similar to the lens body 120 / 160, the bottom 122 / 162, the flexible membrane 124 / 164, and the chamber 126 / 166, respectively. Similarly, the reservoir module 220, the reservoir 222, and the thermal sensitive portion 224 are similar to the reservoir module 130 / 170, the reservoir 132A / 132B / 172A / 172B, and the thermal sensitive portion 134A / 134B / 174A / 174B, respectively. The structure, function, and materials of these components can be similar to those discussed above. Although not shown, the front and / or rear surfaces may have other features including, but not limited to, diffraction gratings.The reservoir module 210 and the lens body 220, although indicated as separate components, may be integrated together into a single piece.

[0049] In the illustrated embodiment, the reservoir 222 has a wall comprising individually formed capsules. Each capsule has a heat sensitive portion 224 that forms the wall of the capsule. Thus, the heat sensitive portion 224 and the capsule 224 are effectively synonymous with respect to the lens 200. The capsule 224 may be an SMP. In the illustrated embodiment, each capsule 224 is discrete. Each capsule 224 is shown as having the same volume and orientation. In other embodiments, one or more of the capsules 224 may have a different volume and / or a different orientation. For example, eight of the sixteen capsules 224 shown may have an orientation opposite to that shown. Thus, the capsules 224 may have an orientation similar to Figure 2A 174A and 174B are depicted in FIG. Thus, both an increase and a decrease in the base power of the lens 200 can be provided.

[0050] The lens 200 functions in a manner similar to the lenses 110 and 150. Thus, the lens 200 can share the benefits of the lenses 110 and / or 150. In particular, the basic focal power of the lens 200 can be non-invasively customized for the patient. This can be accomplished by heat treating one or more of the capsules 224, for example, via a laser. Thus, the basic focal power of the lens 200 can be relatively quickly and easily adjusted throughout the life of the lens 200.

[0051] Figure 4 A perspective cross-sectional view of another exemplary embodiment of an adjustable thermal ophthalmic lens 200' is depicted. For simplicity, the ophthalmic lens 200' is hereinafter referred to as lens 200'. For clarity, Figure 4 Not to scale. Lens 200' may be an IOL, for example, comprising a lens and a haptic ( Figure 4 1 (not shown) of a portion of an IOL 100. For simplicity, the optical axis is not shown.

[0052] The lens 200' has a lens body 210', a reservoir module 220', and an optical fluid ( Figure 4 1 ). The lens body 210', the reservoir module 220', the microfluidic path 230', and the optical fluid are similar to the lens body 120 / 160 / 210, the reservoir module 130 / 170 / 220, the microfluidic path 180 / 230, and the optical fluid 140 / 190, respectively. Thus, the lens body 210', the bottom 212', the flexible membrane 214', and the chamber 216' are similar to the lens body 120 / 160 / 210, the bottom 122 / 162 / 212, the flexible membrane 124 / 164 / 214, and the chamber 126 / 166 / 216, respectively. Similarly, reservoir module 220', reservoir 222', and thermal sensitive portion 224' are similar to reservoir module 130 / 170 / 220, reservoir 132A / 132B / 172A / 172B / / 222, and thermal sensitive portion 134A / 134B / 174A / 174B / 220, respectively. The structure, function, and materials of these components can be similar to those discussed above. Although not shown, the front surface and / or the rear surface can have other features, including but not limited to diffraction gratings. Reservoir module 210' and lens body 220', although indicated as separate components, can be integrated together into a single piece.

[0053] In the illustrated embodiment, the reservoir 222' has a wall comprising separately formed spherical capsules. Thus, the capsules of the lens 200' are spherical rather than hemispherical. Each capsule has a heat-sensitive portion 224', which forms the wall of the capsule. Thus, the heat-sensitive portion 224' and the spherical capsule 224' are actually synonymous with the lens 200. The spherical capsule 224' can be an SMP. In the illustrated embodiment, each spherical capsule 224' is discrete. Each spherical capsule 224' is shown as having the same volume. In other embodiments, one or more of the capsules 224' may have different volumes. In the illustrated embodiment, the upper hemispherical heat-sensitive portion and the lower hemispherical heat-sensitive portion 224' of the spherical capsule can be heat-treated separately.

[0054] Lens 200' functions in a manner similar to lenses 110, 150, and 200. Thus, lens 200' can share the benefits of lenses 110, 150, and / or 200. In particular, the base power of lens 200' can be non-invasively customized for a patient. This can be accomplished by heat treating one or more of capsules 224', for example, via a laser. Thus, the base power of lens 200' can be relatively quickly and easily adjusted throughout the life of lens 200'.

[0055] Figure 5 is a flow chart depicting an exemplary embodiment of a method 300 for providing an ophthalmic lens. For simplicity, some steps may be omitted, interleaved, and / or combined. The method 300 is also described in the context of an ophthalmic device 100 and an ophthalmic lens 110. However, the method 300 may be used with one or more of the ophthalmic lenses 110, 150, 200, 200' and / or similar ophthalmic devices.

[0056] The lens body 120 is provided via step 302. Step 302 includes providing a bottom 122, a flexible membrane 124, and a cavity 126. Some or all of the microfluidic paths, such as microfluidic paths 180 or 230, may be provided as part of shaping the lens body 120. Step 302 may include forming and / or connecting the bottom 122 and the flexible membrane 124 so that an empty space for the cavity 126 resides between the bottom and the flexible membrane. Step 302 may also include forming any diffraction gratings on the flexible membrane 124 and / or the bottom 122.

[0057] The reservoir module 130 is set up via step 304. Step 304 may include setting up thermally sensitive portions 134A and 134 at the boundaries of the reservoirs 132A / 132B. For example, a desired SMP having a suitable shape, size, glass transition temperature, and laser absorption is set up. Step 304 may also include forming some or all of the microfluidic paths.

[0058] If the microfluidic pathway 180 or 230 is not completed in steps 302 and 304, it is provided via step 306. Step 306 may simply include providing a hole or channel between the chamber 126 and the reservoir 132A / 132B. Alternatively, a more complex pathway may be formed.

[0059] The optical fluid 140 is disposed in the lens 110, via step 308. Step 308 may include filling the lens 110 with the desired optical fluid 140 and sealing the lens 110. Thus, the optical fluid 140 may flow between the chamber 126 and the reservoirs 132A / 132B. The haptics 102 and 104 may be optionally disposed, via step 310.

[0060] The IOL 100 and the ophthalmic lenses 110, 150, 200, and / or 200' may be provided using the method 300. Thus, the benefits of one or more of the lenses 110, 150, 200, and / or 200' may be achieved.

[0061] Figure 6 1 is a flow chart depicting an exemplary embodiment of a method 350 for treating an ophthalmic condition of a patient and adjusting a lens. For simplicity, some steps may be omitted, interleaved, and / or combined. Method 350 is also described in the context of using IOL 100 and lens 110. However, method 350 may be used with one or more of lenses 150, 200, and / or 200'.

[0062] The adjustable heat IOL 100 is selected for implantation in the patient's eye, via step 352. The IOL 100 includes a lens body 120, a reservoir module 130, a fluid connection between the chamber 126 and the reservoir 132A / 132B, and an optical fluid 140. Part of the selection process may involve determining the correction needs of the patient's vision and selecting an IOL 100 with the appropriate power.

[0063] IOL 100 is implanted in the patient's eye, via step 354. Step 354 may include replacing the patient's own lens with IOL 100 or augmenting the patient's lens with IOL 100.

[0064] Via step 150, determine whether the implanted IOL 100 has the correct basic focal power. Step 150 may include re-measuring the patient's vision. This step may be performed shortly after implantation or at a longer interval. This is because in some embodiments the IOL 100 may be adjusted throughout its life. If the basic focal power is correct, the method terminates.

[0065] However, if the base power is incorrect, then the base power of IOL 100 can be non-invasively adjusted via step 358. If it is desired to correct an increase or decrease in base power, then a lens similar to lens 150 can be selected in step 352. Step 358 can include locating the area of ​​the heat-sensitive portion 134A and / or 134B that is desired to be heated. The laser can then be aimed and fired at the desired portion of the heat-sensitive portion 134A and / or 134B until the glass transition temperature has been reached or exceeded. In some embodiments, a low duty cycle can be used to reduce the laser from heating the eye. Step 358 can be performed during a single outpatient visit. In addition, steps 356 and 358 can be repeated repeatedly until the desired power of lens 110 is obtained. Further, steps 356 and 358 can be repeated at different times throughout the life of lens 110.

[0066] Using method 350, a physician may be able to more quickly and easily use heat to adjust the base power of IOL 100. This can be accomplished without requiring additional glasses for the patient or locking changes to IOL 100. Thus, the burden on the physician and patient may be reduced. Method 350 may also be safer for the patient because method 350 may be implemented non-invasively. Thus, the benefits of adjustable heat IOL 100 and lenses 110, 150, 200, and / or 200' may be achieved.

[0067] A method and system for providing a thermo-adjustable IOL has been described. The method and system have been described based on the exemplary embodiments shown, and one of ordinary skill in the art will readily recognize that the embodiments may be varied, and any variation will be within the spirit and scope of the method and system. Therefore, many modifications may be made by one of ordinary skill in the art without departing from the spirit and scope of the appended claims.

Claims

1. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber, the reservoir comprising a plurality of thermally sensitive structures that change shape in response to receiving optical energy from the laser; as well as an optical fluid residing in said chamber and said reservoir, Wherein, at least one of the multiple thermosensitive structures is configured to absorb light energy and change its shape, thereby causing a portion of the optical fluid to flow between the reservoir and the chamber, wherein the fluid flow between the reservoir and the chamber causes the basic focal length of the ophthalmic lens to change in response to the shape change of the lens body.

2. The ophthalmic lens according to claim 1, wherein: The lens body has a lens body refractive index; the optical fluid has an optical fluid refractive index, and the lens body refractive index and the optical fluid refractive index are matched within 0.

1.

3. The ophthalmic lens according to claim 1, wherein: The ophthalmic lens further comprises a fluid path connecting the reservoir with the chamber.

4. The ophthalmic lens according to claim 1, wherein: The plurality of thermosensitive structures include a first thermosensitive structure and a second thermosensitive structure.

5. The ophthalmic lens according to claim 4, wherein: The shape change of the first thermosensitive structure is used to flow a first volume of the optical fluid between the reservoir and the chamber, and the shape change of the second thermosensitive structure is used to flow a second volume of the optical fluid between the reservoir and the chamber, the first volume and the second volume being the same.

6. The ophthalmic lens of claim 4, wherein: The shape change of the first thermosensitive structure is used to flow a first volume of the optical fluid between the reservoir and the chamber, and the shape change of the second thermosensitive structure is used to flow a second volume of the optical fluid between the reservoir and the chamber, the first volume and the second volume being different.

7. The ophthalmic lens of claim 4, wherein: The first thermo-sensitive structure and the second thermo-sensitive structure have different orientations.

8. The ophthalmic lens of claim 1, wherein: At least a portion of the lens body is a flexible film.

9. The ophthalmic lens of claim 1, wherein: The thermosensitive structure is configured to change shape in response to a temperature reaching at least forty-five degrees Celsius.

10. The ophthalmic lens of claim 1, wherein: The thermally sensitive structure includes an additive that absorbs light energy within a selected wavelength range.

11. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber, the reservoir comprising a plurality of structures that change shape in response to receiving optical energy from the laser; as well as an optical fluid residing in said chamber and said reservoir, wherein at least one of the plurality of structures is configured to absorb light energy and change shape, thereby causing a portion of the optical fluid to flow between the reservoir and the chamber, wherein the flow of fluid between the reservoir and the chamber causes the basic focal power of the ophthalmic lens to change, Wherein, the lens body has a lens body refractive index; The optical fluid has an optical fluid refractive index, The refractive index of the lens body and the refractive index of the optical fluid are matched to within 0.

1.

12. An ophthalmic lens comprising: a lens body including a chamber; a first reservoir in fluid communication with the chamber of the lens body, the first reservoir comprising a plurality of first thermosensitive structures that change shape in response to receiving optical energy from a laser; a second reservoir in fluid communication with the chamber of the lens body, the second reservoir comprising a plurality of second thermally sensitive structures that change shape in response to receiving optical energy from the laser; an optical fluid residing in the chamber, the first reservoir, and the second reservoir, wherein at least one of the plurality of first thermosensitive structures is configured to absorb light energy and change shape, thereby driving the optical fluid from the first reservoir to the chamber, At least one of the plurality of second thermally sensitive structures is configured to absorb light energy and change shape, thereby driving the optical fluid from the second reservoir to the chamber, The first reservoir and the second reservoir are disconnected, and any fluid flow between the first reservoir and the second reservoir is achieved through the chamber.

13. An ophthalmic lens comprising: a lens body including a chamber; a first reservoir in fluid communication with the chamber of the lens body, the first reservoir comprising a plurality of first thermosensitive structures that change shape in response to receiving optical energy from a laser; a second reservoir in fluid communication with the chamber of the lens body, the second reservoir comprising a plurality of second thermally sensitive structures that change shape in response to receiving optical energy from the laser; an optical fluid residing in the chamber, the first reservoir, and the second reservoir, wherein at least one of the plurality of first thermosensitive structures is configured to absorb light energy and change shape, thereby driving the optical fluid from the first reservoir to the chamber, At least one of the plurality of second thermally sensitive structures is configured to absorb light energy and change shape, thereby driving the optical fluid from the chamber to the second reservoir, The first reservoir and the second reservoir are disconnected, and any fluid flow between the first reservoir and the second reservoir is achieved through the chamber.

14. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising a first thermosensitive structure and a second thermosensitive structure that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber to cause a change in the base power of the ophthalmic lens, The first thermosensitive structure and the second thermosensitive structure are part of a ring, wherein the first thermosensitive structure is configured to absorb light energy and change its shape, thereby driving the optical fluid from the reservoir to the chamber, The second thermally sensitive structure is configured to absorb light energy and change shape, thereby driving the optical fluid from the chamber to the reservoir.

15. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising a first thermosensitive structure and a second thermosensitive structure that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber to cause a change in the base power of the ophthalmic lens, The first thermosensitive structure and the second thermosensitive structure are part of a ring, wherein at least one of the first thermosensitive structure and the second thermosensitive structure is configured to absorb light energy and change shape, thereby driving the optical fluid from the reservoir to the chamber, The first temperature-sensitive structure is positioned radially offset from the second temperature-sensitive structure.

16. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising first and second thermosensitive structures that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber to cause a change in the base power of the ophthalmic lens, The first thermosensitive structure and the second thermosensitive structure are discrete units separated from each other, At least one of the first and second thermally sensitive structures is configured to absorb light energy to drive the optical fluid from the reservoir to the chamber to change the base focal power.

17. An ophthalmic lens comprising: A lens body, wherein the lens body has a chamber therein, and at least a portion of the lens body is flexible; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising first and second thermosensitive structures that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber to cause a change in the base power of the ophthalmic lens, The first thermosensitive structure and the second thermosensitive structure are spherical units, At least one of the first and second thermally sensitive structures is configured to absorb light energy to drive the optical fluid from the reservoir to the chamber to change the base focal power.

18. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising first and second thermosensitive structures that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber to cause a change in the base power of the ophthalmic lens, At least one of the first and second thermosensitive structures is configured to absorb light energy and change shape, thereby driving the optical fluid from the reservoir to the chamber, The first thermo-sensitive structure and the second thermo-sensitive structure have different shapes from each other.

19. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising first and second thermosensitive structures that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber, the first thermally sensitive structure being configured to absorb light energy and change shape, thereby driving the optical fluid from the reservoir to the chamber to increase the base power of the ophthalmic lens, The second thermally sensitive structure is configured to absorb light energy and change shape, thereby driving the optical fluid from the reservoir to the chamber to further increase the base power of the ophthalmic lens.

20. An ophthalmic lens comprising: a lens body including a chamber; a reservoir in fluid communication with the chamber of the lens body, the reservoir comprising first and second thermosensitive structures that change shape in response to receiving optical energy from a laser; an optical fluid residing in the chamber and in a reservoir, wherein the optical fluid is adapted to move between the reservoir and the chamber, the first thermally sensitive structure being configured to absorb light energy and change shape, thereby driving the optical fluid from the chamber to the reservoir to reduce the base power of the ophthalmic lens, The second thermally sensitive structure is configured to absorb light energy and change shape, thereby driving the optical fluid from the chamber to the reservoir to further reduce the base power of the ophthalmic lens.

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