Heat tunable intraocular lens

Abstract

To provide an improved mechanism for noninvasively changing the base power of an ophthalmic lens.SOLUTION: An ophthalmic lens comprises: a lens body having a chamber therein; a reservoir fluidically connected with the chamber of the lens body and having a reservoir volume, the reservoir including multiple heat sensitive structures changing the reservoir volume by changing the shape from a first shape to a second shape in response to a temperature reaching a prescribed threshold; and an optical fluid residing in the chamber and the reservoir, where a 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 base power change.SELECTED DRAWING: Figure 1A

Description

[Technical field]

[0001] FIELD OF THE DISCLOSURE This disclosure relates generally to ophthalmic lenses, and more particularly to thermally tunable intraocular lenses. [Background technology]

[0002] An intraocular lens (IOL) is implanted in a patient's eye to replace or, in the case of phakic IOLs, to supplement the patient's crystalline lens. Some conventional IOLs are monofocal and some are multifocal. Monofocal IOLs have one focal length or one power. Objects at a focal length from the eye / IOL are in focus, while objects closer or farther away may not be in focus. In contrast, multifocal IOLs have at least two focal lengths. Multifocal lenses may assist patients with conditions such as myopia. Generally, a physician selects an IOL with an appropriate base power and other characteristics for the patient. The selected IOL is implanted during eye surgery, which is often performed for other conditions such as cataracts.

[0003] Although IOLs function acceptably well in most patients, the selected IOL may have an inappropriate power for the patient. The IOL may be removed and a new IOL selected and implanted. However, it is not desirable to perform additional eye surgery for this purpose. Other IOLs may have their power adjusted non-invasively. For example, the IOL may have sensitivity to ultraviolet (UV) light. Such an IOL may be exposed to UV light to change the power of the lens. Exposure to UV light may change the shape of the IOL and therefore the base power of the lens. Although the base power of the IOL can be adjusted in this manner, such IOLs require the patient to wear UV light blocking glasses throughout the entire period until the accommodation phase is complete. The accommodation phase typically lasts for about two weeks. Requiring the patient to wear UV light blocking glasses 24 hours a day for two weeks is inconvenient and undesirable for the patient. Once the accommodation phase is complete, the changes in the IOL must be locked to prevent further changes in the power of the IOL due to daily exposure to UV light. Once these changes are locked, the base power of the IOL may no longer be adjustable. There are other mechanisms for changing the base power of the lens, such as changing the tension, however these mechanisms have associated drawbacks. Summary of the Invention [Problem to be solved by the invention]

[0004] Therefore, what is needed is an improved mechanism for non-invasively varying the base power of an IOL. [Means for solving the problem]

[0005] The method and system provide an ophthalmic lens including a lens body having a chamber therein, a storage module coupled to the lens body, and an optical fluid. At least a portion of the lens body is flexible. The storage module includes a heat sensitive portion and has a reservoir therein. The reservoir has a storage volume and is fluidly connected to the chamber. The heat sensitive portion of the storage module abuts at least a portion of the reservoir. The heat sensitive portion has a shape responsive to a temperature of at least 45 degrees Celsius such that the storage volume changes in response to at least a portion of the heat sensitive portion reaching that temperature. The optical fluid is within the chamber and the reservoir. The optical fluid has an optical fluid refractive index that matches the refractive index of the lens body within 0.1. A change in the storage volume causes a portion of the optical fluid to flow between the reservoir and the chamber, causing at least that portion of the lens body to undergo a shape change corresponding to a change in base power.

[0006] The methods and systems described herein allow physicians to better and more easily non-invasively vary the power of implanted ophthalmic devices, such as IOLs.

[0007] For a fuller understanding of the present disclosure, and the advantages thereof, reference is now made to the following description which should be read in connection with the accompanying drawings, in which like reference numerals indicate like features and in which: [Brief description of the drawings]

[0008] [Figure 1A] 1A-1D illustrate various views of an exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 1B] 1A-1D illustrate various views of an exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 1C] 1A-1D illustrate various views of an exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 1D] 1A-1D illustrate various views of an exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 1E] 1A-1D illustrate various views of an exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 2A]10A-10C show various views of another exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 2B] 10A-10C show various views of another exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 2C] 10A-10C show various views of another exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 2D] 10A-10C show various views of another exemplary embodiment of a thermally adjustable ophthalmic device. [Figure 3A] 1A-1D show various views of other exemplary embodiments of a thermally tunable ophthalmic lens. [Figure 3B] 1A-1D show various views of other exemplary embodiments of a thermally tunable ophthalmic lens. [Figure 4] 1 shows a cross-sectional perspective view of another exemplary embodiment of a thermally tunable ophthalmic lens. [Diagram 5] 1 is a flow chart illustrating an example embodiment of a method for providing a thermally tunable ophthalmic device. [Figure 6] 1 is a flow chart illustrating an example embodiment of a method of using a thermally adjustable ophthalmic instrument. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0009] Exemplary embodiments relate to ophthalmic devices, such as intraocular lenses (IOLs). The following description is presented to enable one 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 the general principles and features described herein will be readily apparent. The exemplary embodiments are described primarily with reference to specific methods and systems provided in specific examples. However, the methods and systems will function well with other embodiments. Phrases such as "exemplary embodiment," "one embodiment," and "other embodiments" may refer to the same or different embodiments as well as multiple embodiments. The embodiments are described in the context of systems and / or devices having certain components. However, the systems and / or devices may include more or fewer components than those illustrated, and the arrangement and type of components may be modified without departing from the scope of the invention. The exemplary embodiments are also described in terms of a particular method having certain steps. However, the methods and systems will function well with other methods having different and / or additional steps and other sequences of steps not inconsistent with the exemplary embodiments. Thus, the present invention is not intended to be limited to the embodiments shown, but is to be accorded the widest scope consistent with the principles and features described herein. Methods and systems are also described in terms of singular items rather than plural items. One of ordinary skill in the art will appreciate that these singular terms encompass plural. For example, a chamber may include one or more chambers.

[0010] The method and system provide an ophthalmic lens including a lens body having a chamber therein, a storage module coupled to the lens body, and an optical fluid. At least a portion of the lens body is flexible. The storage module includes a heat sensitive portion and has a reservoir therein. The reservoir has a storage volume and is fluidly connected to the chamber. The heat sensitive portion of the storage module abuts at least a portion of the reservoir. The heat sensitive portion has a shape responsive to a temperature of at least 45 degrees Celsius such that the storage volume changes in response to at least a portion of the heat sensitive portion reaching that temperature. The optical fluid is within the chamber and the reservoir. The optical fluid has an optical fluid refractive index that matches the refractive index of the lens body within 0.1. A change in the storage volume causes a portion of the optical fluid to flow between the reservoir and the chamber, causing at least that portion of the lens body to undergo a shape change corresponding to a change in base power.

[0011] 1A-1E illustrate one exemplary embodiment of a thermally adjustable ophthalmic device 100, which may be used as an IOL. For simplicity, the ophthalmic device 100 is hereinafter referred to as IOL 100. FIG. 1A illustrates a top view of the IOL 100, and FIGS. 1B-1E illustrate a side view of an ophthalmic lens 110. For clarity, FIGS. 1A-1E are not to scale. The IOL 100 includes an ophthalmic lens 110 as well as haptics 102 and 104. The portion of the ophthalmic lens 110 may include various optical materials, including, but not limited to, one or more of silicone, hydrogel, and acrylic. The haptics 102 and 104 are used (not explicitly shown) to hold the ophthalmic device 100 in place within a patient's eye. However, in other embodiments, other mechanisms may be used to hold the ophthalmic device in place within the eye. For clarity, the haptics are not depicted in FIGS. 1B-3C, discussed below. Although the ophthalmic lens 110 is depicted in plan view in FIG. 1A as having a circular cross-section, in other embodiments, other shapes may be used.

[0012] The ophthalmic lens 110 (hereafter referred to as the "lens") has an optical axis 106 as well as a lens body 120, a storage module 130, and an optical fluid 140. Although a numbered portion of the lens 110, the optical axis 106 may be considered an imaginary line passing through the centers of the anterior and posterior surfaces. Therefore, the optical axis 106 is shown as a dashed line. The optical axis 106 may also be perpendicular to the surface at the point where it passes through the surface. Although not shown, the anterior and / or posterior surfaces may have other features, including, but not limited to, a diffraction grating. Although shown as separate components, the storage module 130 and the lens body 120 may be integrated with one another as one part. For example, some or all of the lens body 120 and the storage module may be a monolithic structure formed together.

[0013] 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 storage module 130 is not designed to transmit light used in vision. The lens body 120 includes a base 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. As a result, the flexible portion 124 will hereinafter be referred to as the flexible membrane 124. However, nothing prevents the flexible portion from having other configurations. The chamber 126 may be considered the space between the base 122 and the flexible membrane 124. An optical fluid 140, described below, is located at least in the chamber 126.

[0014] In the illustrated embodiment, the base 122 has stable optical properties. Therefore, the base 122 may be relatively constant in shape. In other embodiments, the base 122 may change shape somewhat in response to changes in the volume of the chamber 126. In contrast, the flexible membrane 124 is flexible and changes shape in response to changes in the volume of the reservoir 126.

[0015] In some embodiments, the base 122 and the flexible membrane 124 may be made of the same material, for example, AcrySof®, AcrySof® 2, and / or other soft optical materials may be used. In other embodiments, the base 122 and the flexible membrane 124 may be made of different materials. The base 122 may be thick enough that the base 122 remains substantially unchanged. However, the flexible membrane 124 may be thin enough to respond to changes in the volume of the chamber 126. For example, the flexible membrane 124 may be at least 80 micrometers thick and no more than 300 micrometers thick. In other embodiments, other thicknesses are possible. In some embodiments, the flexible membrane 124 has a uniform thickness before the optical fluid 140 is provided. In other embodiments, the thickness of the flexible membrane 124 may be non-uniform.

[0016] The storage module 130 is located at the periphery of the lens body 120 and includes reservoirs 132A / 132B and a heat sensitive portion 134. A cross section is shown in FIGS. 1B-1D. Thus, reservoirs 132A and 132B (collectively referred to as reservoirs 132A / 132B) and heat sensitive portions 134A and 134B are shown. In some embodiments, reservoirs 132A and 132B are connected within the storage module 130 to allow fluid to flow around the periphery of the lens body 120. For example, reservoirs 132A and 132B may simply be portions of a hollow annulus (i.e., tube). In other embodiments, reservoirs 132A and 132B may be separated such that no fluid flow between reservoirs 132A and 132B occurs through the chamber 126 of the lens body 120. In other embodiments, reservoirs 132A and 132B may have different shapes.

[0017] The reservoirs 132A and 132B are fluidly connected to the chamber 126 of the lens body 120. In the illustrated embodiment, there are simply inlets / outlets (i.e., openings or passageways) between the chamber 126 and the reservoirs 132A and 132B. In other embodiments, the fluid paths between the chamber 126 and the reservoirs 132A and 132B may be more complex.

[0018] Optical fluid 140 resides in chamber 126 and reservoirs 132A / 132B. For simplicity, in FIG. 1B, optical fluid 140 is only labeled individually. In FIGS. 1C-1E, optical fluid is labeled with reservoirs 132A / 132B and chamber 126. Optical fluid 140 may flow between chamber 126 and reservoirs 132A / 132B. Because optical fluid 140 may reside in chamber 126, optical fluid 140 is in the path of light used for vision. Therefore, optical fluid 140 transmits light. Because light is refracted by lens body 120, optical fluid 140 may also have a refractive index that matches that of lens body 120 (e.g., base 122, and in some embodiments base 122 and flexible membrane 124) to certain limits. For example, in some embodiments, the refractive index of optical fluid 140 is within 0.1 of that of lens body 120. In some embodiments, the refractive index of optical fluid 140 differs from that of lens body 120 by no more than 0.05. When lens body 120 is made of a material such as AcrySof® or AcrySof® 2, optical fluid 140 may be a high molecular weight aromatic silicone copolymer liquid.

[0019] The heat sensitive portions 134A and 134B of the storage module 130 may be part of one heat sensitive portion. For example, the heat sensitive portions 134A and 134B may be part of an annular body occupying one wall of the reservoir 132A / 132B. In other embodiments, the heat sensitive portions 134A / 134B may have different shapes. For example, the heat sensitive portions 134A and / or 134B may have a spherical, hemispherical, cubic, elliptical, or other different shapes. These shapes may be connected or separate. In addition, the heat sensitive portion 134A may have a different shape than the heat sensitive portion 134B. In the illustrated embodiment, the heat sensitive portions 134A and 134B have different sizes. However, in other embodiments, the heat sensitive portions 134A and 134B may have the same size.

[0020] The heat sensitive portions 134A and 134B change shape in response to reaching a certain 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. The glass transition temperatures of the heat sensitive portions 134A and 134B are desirably higher than the normal temperature of the eye. The glass transition temperature is also desirably low enough so that the heat sensitive portions 134A and 134B do not cause damage to the eye even if they reach their glass transition temperature. In some embodiments, the heat sensitive portions 134A and 134B are small enough so that localized heating of these portions 134A and 134B does not negatively affect the eye even if the temperature reaches a temperature well above the normal temperature of the eye. For example, the normal temperature of the eye in which IOL 100 is desired to reside may be approximately 35 degrees Celsius to 40 degrees Celsius. The glass transition temperature of heat sensitive portions 134A and 134B may be at least 45 degrees Celsius. In some embodiments, the glass transition temperature may be at least 60 degrees Celsius. In other embodiments, the glass transition temperature may be at least 90 degrees Celsius in some embodiments. Additionally, it may be desirable for the glass transition temperature to be less than 100 degrees Celsius.

[0021] At the normal eye temperature, the shape of the heat sensitive portions 134A and 134B is constant. When one or both of the heat sensitive portions 134A and 134B are heated to their glass transition temperature, the shape changes. Upon cooling, the heat sensitive portions 134A and 134B retain their new shape. This shape then remains constant. Therefore, normal wear of the IOL 100 does not affect the base power of the lens 110 or the shape of the heat sensitive portions 134A and 134B. For example, the heat sensitive portions 134A and 134B may be formed from a shape memory material, such as a shape memory polymer (SMP). In addition, the SMP may be doped with an additive (e.g., a dye or other material) that absorbs light within the wavelength range provided by the laser for heating.

[0022] The operation of IOL 100 may be seen from FIGS. 1B-1E. First, as shown in FIG. 1B, heat-sensitive portions 134A and 134B have a particular shape. Heat-sensitive portion 134A may be heated to or above its glass transition temperature. In some embodiments, this heating is accomplished via a laser. For example, a laser may be aimed and fired at heat-sensitive portion 134A. The wavelength of the laser is selected to penetrate the cornea and vitreous humor of the eye. In some embodiments, the laser may have a characteristic wavelength of about 1064 nm. In other embodiments, the laser may be in the wavelength range of 750-850 nanometers. Heat-sensitive portion 134A is heated to at least its glass transition temperature, causing it to change shape.

[0023] FIG. 1C shows the lens 110 after the heat sensitive portion 134A has been heated to at least the glass transition temperature. The lens 110 may be 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'. Therefore, the power of the lens 110 has changed. Based on the change in the volume of the reservoir 132A' and the chamber 126' and the properties of the flexible membrane 124' and the optical fluid 140, a change in the base power of the lens 110 may be determined.

[0024] Alternatively, the heat sensitive portion 134B may be heated to or above its glass transition temperature. Heating may be accomplished using a laser or similar mechanism, as previously described. FIG. 1D shows the lens 110 after heating the heat sensitive portion 134B. The lens 110 may be cooled. The heat sensitive portion 134B' has changed shape. As a result, the volume of the reservoir 132B' has decreased. This forces a portion of the optical fluid 140 into the chamber 126''. Since 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''. Therefore, the power of the lens 110 has changed. Based on the change in the volume of the reservoir 132B'' and the chamber 126'' and the properties of the flexible membrane 124'' and the optical fluid 140, a change in the base power of the lens 110 may be determined. However, because the change in volume of reservoir 132B'' is smaller, the change in base power of lens 110 is smaller in FIG. 1D than in FIG. 1C.

[0025] Both heat sensitive portions 134A and 134B may be heated to or above their glass transition temperatures. Heating may be achieved using a laser or similar mechanism, as previously described. FIG. 1E shows lens 110 after heating heat sensitive portions 134A and 134B. Lens 110 may be cooled. Heat sensitive portions 134A' and 134B' have changed shape. As a result, the volumes of reservoirs 132A' and 132B' have decreased. This forces some of the optical fluid 140 into chamber 126'''. Because flexible membrane 124''' is not rigid, the movement of optical fluid 140 into chamber 126''' increases the volume of chamber 126''' and changes the shape of flexible membrane 124'''. Hence, the power of lens 110 has changed. Based on the change in the volume of reservoirs 132A' and 132B' and chamber 126''' and the properties of flexible membrane 124''' and optical fluid 140, a change in the base power of lens 110 may be determined. Because the volume change of reservoirs 132A' and 132B' is greater, the change in the base power of lens 110 is greater in FIG. 1E than in FIGS. 1C and 1D. For example, if the base power of lens 110 changes by 0.25 diopters in the situation shown in FIG. 1D, the base power may change by 0.5 diopters in the case shown in FIG. 1C and by 0.75 diopters in the case shown in FIG. 1E. Furthermore, the changes shown in FIGS. 1C, 1D, and 1E do not have to occur simultaneously. Instead, these changes may be made at a later time based on updated information and / or changes to the patient's eye.

[0026] The base power of the lens 110, i.e., the IOL 100, may be changed if the lens 110 has an inappropriate base power for the patient or if the patient's vision changes over time. In some configurations, the power of the lens 110 may be adjusted up or down based on whether there is an increase or decrease in volume in the reservoirs 132A / 132B. The heat-sensitive portions 134A and 134B may be changed by a laser, so the power of the lens 110 may be changed non-invasively. Thus, the risk of an invasive procedure such as an IOL exchange may be avoided. Instead, one may simply go to the clinic. Changing the base power of the lens 110 through heating by a laser may also be more cost-effective than replacing the entire IOL. In addition, the drawbacks of other non-invasive mechanisms for changing the base power of the lens may be avoided. For example, the change needs to be locked into the lens 110. Instead, additional heat may be applied at any time throughout the life of the lens 110. Furthermore, the lens 110 does not require the wearer to wear special glasses, such as UV light protection glasses, around the clock, around the adjustment of the base power. In addition, the power of the lens 110 can be adjusted simply by visiting the clinic. The adjustment can also be made more quickly. In some cases, the heating, the rapid change in shape of the heat-sensitive portion 134A / 134B, the flow of fluid between the reservoir 132A / 132B and the chamber 126, the change in the volume of the chamber 126, and the associated change in the base power of the lens can take only a few minutes or less. Therefore, the lens 110 may be more easily adjusted to the needs of the patient.

[0027] 2A-2D show another exemplary embodiment of a thermally tunable ophthalmic lens 150 that may be used as or in an IOL. For simplicity, the ophthalmic lens 150 will hereafter be referred to as lens 150. FIGS. 2A-2D show a side view of an ophthalmic lens 110. For clarity, FIGS. 2A-2D are not to scale. The lens 150 may be part of an IOL, such as IOL 100, which includes the lens 150 and may also include heptics (not shown in FIGS. 2A-2E).

[0028] Lens 150 has an optical axis 156 as well as a lens body 160, a storage module 170, and an optical fluid 190. Lens body 160, storage module 170, optical fluid 190, and optical axis 156 are similar to lens body 120, storage module 130, optical fluid 140, and optical axis 106, respectively. Thus, lens body 160, base 162, flexible membrane 164, and chamber 166 are similar to lens body 120, base 122, flexible membrane 124, and chamber 126, respectively. Similarly, storage module 170, reservoirs 172A / 172B, and heat sensitive portions 174A and 174B are similar to storage module 130, reservoirs 132A / 132B, and heat sensitive portions 134A and 134B, respectively. Finally, optical fluid 190 is similar to optical fluid 140. Thus, the structure, function, and materials of these components may be similar to those described above. For example, the refractive index of the optical fluid 190 may match that of the lens body 160 within the tolerances described above. Although not shown, the front and / or rear surfaces may have other features, including but not limited to, a diffraction grating. Although shown as separate components, the storage module 170 and the lens body 160 may be integrated together into a unitary part.

[0029] Also shown is a microfluidic pathway 180 connecting reservoirs 172A / 172B with chamber 166. The ends of microfluidic pathway 180 are shown as dashed lines, indicating the inlets / outlets of chamber 166 and reservoirs 172A / 172B. In some embodiments, microfluidic pathway 180 is simply a straight passageway. However, in other embodiments, microfluidic pathway 180 may have other, more complex structures.

[0030] Lens body 170 forms the primary optical component of lens 150. In contrast, storage module 170 may not be designed to transmit light used in vision. In the illustrated embodiment, flexible membrane 164 is pliable and has optical properties that may change in response to variations in the volume of chamber 166. In contrast, base 162 may have stable optical properties and be relatively constant in shape. In other embodiments, base 162 may change shape somewhat in response to changes in the volume of chamber 166.

[0031] The storage module 170 is at the periphery of the lens body 160. In some embodiments, the reservoirs 172A and 172B are connected within the storage module 170 and fluid may flow around the lens body 160. In some embodiments, the reservoirs 172A and 172B are not connected and no fluid flow between the reservoirs 172A and 172B may occur through the chamber 166 of the lens body 160. In other embodiments, the reservoirs 172A and 172B may have different shapes.

[0032] The heat-sensitive portions 174A and 174B of the storage module 130 may be part of one heat-sensitive portion. For example, the heat-sensitive portions 174A and 174B may be part of an annular body occupying one wall of the storage portion 172A / 172B. Alternatively, the heat-sensitive portions 174A and 174B may be composed of separate units. For example, in Figs. 2A-2D, each heat-sensitive portion 174A and 174B includes a plurality of capsules 175A and 175B, respectively. For the sake of simplicity, only one capsule 175A and 175B, respectively, of each heat-sensitive portion 174A and 174B is labeled. In some embodiments, each capsule 175A and / or 175B is a heat-sensitive structure, which may be insulated from the other capsules. In other embodiments, the capsules 175A and 175B are part of a heat-sensitive structure. Selected regions of the heat sensitive portions 174A and 174B may be individually heated to or above their glass transition temperatures. In the illustrated embodiment, the capsules 175A and 175B are approximately hemispherical. However, nothing prevents the use of other shapes. In the illustrated embodiment, each of the capsules 175A and 175B has the same size. Therefore, each capsule 175A and 175B may contain / transfer the same volume of optical fluid 190. In other embodiments, the capsules 175A and / or 175B may have different sizes. It is still desirable for the volume of optical fluid contained / transferred in each capsule 175A and 175B to be known and to correspond to a known change in base power. For example, each capsule 175A and 175B may correspond to a change in base power of 0.25 diopters within a desired error. In some cases, this corresponds to a volume of 0.2 mm3 for each capsule 175A and 175B. However, other volumes and other changes in base power may also be used. For example, one capsule 175A may accommodate a 0.25 diopter change, another capsule 175A may accommodate a 0.5 diopter change, etc. In some embodiments, a 4 diopter power change (e.g., ±2 diopters) may be provided.

[0033] Each of the capsules 175A and 175B changes shape in response to the capsules 175A and 175B reaching their glass transition temperature. After cooling, this new shape is stable. Below the glass transition temperature, the shape is substantially constant as either a capsule or a flat surface. This glass transition temperature of the heat sensitive portions 174A and 174B is desirably significantly higher than the normal temperature of the eye, but low enough to prevent damage to the eye even if the heat sensitive portions 174A and 174B reach their glass transition temperature. In some embodiments, the capsules 175A and 175B are small enough that localized heating of these capsules 175A and 175B does not negatively affect the eye, even if the portions 174A and 174B reach a temperature significantly higher than the normal temperature of the eye. The capsules 175A and 175B may be formed of the SMPs described above and may have the glass transition temperatures described above.

[0034] 2A, capsules 175A and 175B have different orientations with respect to reservoirs 172A and 172B. In particular, capsules 175A each displace a substantially hemispherical volume of optical fluid 190 from reservoir 172A. Capsules 175B each contain a substantially hemispherical volume of optical fluid 190 within reservoir 172B. As a result, the base power of lens 150 may be increased or decreased by different 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 so heated.

[0035] The operation of the lens 150 will be described with reference to Figures 2A-2D. In the following description, it will be assumed that the lens 150 has the configuration shown in Figure 2A first. If the base power of the lens 150 is too high, it is desirable for the lens 150 to refract light less. This may be achieved by reducing the curvature of the flexible membrane 164. Depending on their orientation with respect to the reservoir 172A, a change in the shape of the capsules 175A / heat-sensitive portions 174A may be utilized. More specifically, heat is applied to one or more of the capsules 175A, for example via a laser. The temperature of this capsule 175A is raised above its glass transition temperature. As a result, the capsule 175A changes shape.

[0036] FIG. 2B illustrates an exemplary embodiment of lens 150 after applying sufficient heat to capsule 175A closest to microfluidic pathway 180 to raise the temperature of capsule 175A to or above its glass transition temperature. Lens 150 may then be cooled to the ambient eye temperature. Capsule 175A closest to chamber 166′ is flattened. The capsule changes from a first shape (hemispherical) to a second shape (substantially flat). This shape change is stable after cooling. As a result, reservoir 172A′ increases in volume by approximately the volume of capsule 175A. Reservoir 172B remains unchanged. As a result, optical fluid 190 flows from chamber 166′ through microfluidic pathway 180 to reservoir 172A′. The pressure exerted by optical fluid 190 on flexible membrane 164′ is reduced. Flexible membrane 164′ is flattened, resulting in a corresponding decrease in the volume of chamber 166′. Thus, the optical power of the lens body 160 is reduced. As a result, the base power of the lens 150 has been non-invasively reduced.

[0037] On the other hand, suppose one wishes to increase the optical base power of lens 150 from the situation shown in FIG. 2A. To do so, one desires to increase the curvature of flexible membrane 164. When one or more of capsules 175B are heat treated to reach a temperature up to or above their glass transition temperature, capsules 175B become flattened. Suppose heat is applied to one capsule 175B, for example via a laser. The temperature of this capsule 175B is raised above the glass transition temperature of capsule 175B. As a result, capsule 175B changes shape.

[0038] FIG. 2C illustrates an exemplary embodiment of lens 150 after application of sufficient heat to capsule 175B′ closest to microfluidic pathway 180 to raise the temperature of capsule 175B′ to or above its glass transition temperature. Lens 150 may then be cooled to the ambient eye temperature. In heat sensitive portion 174B′ of storage module 170, the capsule closest to chamber 166″ is flattened. This capsule changes from a hemispherical shape to a substantially flat shape. As a result, reservoir 172B′ has a reduced volume by approximately the volume of capsule 175B. Reservoir 172A remains unchanged. As a result, optical fluid 190 flows from reservoir 172B′ through microfluidic pathway 180 to chamber 166″. The pressure exerted by optical fluid 190 on flexible membrane 164″ increases. The volume of chamber 166″ increases, and the curvature of flexible membrane 164″ correspondingly increases. The change in volume of chamber 166'' can be, but need not be, equal to the volume of capsule 175B. Thus, the optical power of lens 110 is increased. As a result, the base power of lens 150 has been non-invasively increased.

[0039] It may be determined that it is desired to further increase the power of lens 150. In such a case, more capsules 175B may be heat treated. Such a situation is illustrated in FIG. 2D. As can be seen from heat-sensitive portion 174B'', other capsules 175B have been heat treated and are therefore flat. The volume of reservoir 172B'' further decreases. Optical fluid 190 flows from reservoir 172B'' to chamber 166''. Due to the increased pressure of the optical fluid in chamber 164'', flexible membrane 164'' further deforms and the volume of chamber 166'' increases. As a result, the optical power of lens 150 is further increased. It is noted that the optical power of lens 150 may be reduced again by heat treating one or more of capsules 175A.

[0040] The properties of lens 150 may be non-invasively adjusted. More specifically, the base power of lens 150 may be non-invasively increased and / or decreased. Thus, advantages similar to those discussed for lens 110 may be obtained.

[0041] 3A-3B show various views of another exemplary embodiment of a thermally tunable ophthalmic lens 200. For simplicity, the ophthalmic lens 200 will hereafter be referred to as lens 200. FIGS. 3A-3B show side and perspective views of a portion of the lens 200. For clarity, FIGS. 3A-3B are not to scale. The lens 200 may be part of an IOL, such as IOL 100, which includes haptics (not shown in FIGS. 3A-3B) as well as a lens. For simplicity, the optical axis is not shown.

[0042] Lens 200 includes lens body 210, storage module 220, microfluidic pathway 230, and optical fluid (not specifically shown in FIGS. 3A-3B). Lens body 210, storage module 220, microfluidic pathway 230, and optical fluid are similar to lens body 120 / 160, storage module 130 / 170, microfluidic pathway 180, and optical fluid 140 / 190, respectively. Thus, lens body 210, base 212, flexible membrane 214, and chamber 216 are similar to lens body 120 / 160, base 122 / 162, flexible membrane 124 / 164, and chamber 126 / 166, respectively. Similarly, the storage module 220, storage portion 222, and heat sensitive portion 224 are similar to the storage module 130 / 170, storage portion 132A / 132B / 172A / 172B, and heat sensitive portion 134A / 134B / 174A / 174B, respectively. The structure, function, and materials of these components may be similar to those described above. Although not shown, the front and / or rear surfaces may have other features, including, but not limited to, a diffraction grating. Although shown as separate components, the storage module 210 and the lens body 220 may be integrated with each other as one part.

[0043] In the illustrated embodiment, the reservoir 222 has walls that include individually formed capsules. Each capsule has a heat-sensitive portion 224 that forms the capsule wall. Therefore, the heat-sensitive portion 224 and the capsule 224 are effectively synonymous with respect to the lens 200. The capsules 224 may be SMPs. In the illustrated embodiment, each capsule 224 is individual. Each capsule 224 is shown to have the same volume and orientation. In other embodiments, one or more of the capsules 224 may have different volumes and / or different orientations. 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 the heat-sensitive portions 174A and 174B shown in FIG. 2A. Therefore, both increased and decreased base power of the lens 200 may be provided.

[0044] Lens 200 functions similarly to lenses 110 and 150. Thus, lens 200 may share the advantages of lenses 110 and / or 150. In particular, the base power of lens 200 may be non-invasively tailored to the patient. This may be achieved by heat treating one or more of capsules 224, for example via a laser. As a result, the base power of lens 200 may be relatively quickly and easily adjusted throughout the life of lens 200.

[0045] FIG. 4 illustrates a cross-sectional perspective view of another exemplary embodiment of a thermally tunable ophthalmic lens 200'. For simplicity, the ophthalmic lens 200' is hereinafter referred to as lens 200'. For clarity, FIG. 4 is not to scale. The lens 200' may be part of an IOL, such as IOL 100, which includes haptics (not shown in FIG. 4) as well as a lens. For simplicity, the optical axis is not shown.

[0046] Lens 200' includes lens body 210', storage module 220', and optical fluid (not specifically shown in FIG. 4). Lens body 210', storage module 220', microfluidic pathway 230', and optical fluid are similar to lens body 120 / 160 / 210, storage module 130 / 170 / 220, microfluidic pathway 180 / 230, and optical fluid 140 / 190, respectively. Thus, lens body 210', base 212', flexible membrane 214', and chamber 216' are similar to lens body 120 / 160 / 210, base 122 / 162 / 212, flexible membrane 124 / 164 / 214, and chamber 126 / 166 / 216, respectively. Similarly, the storage module 220', storage section 222', and heat sensitive section 224' are similar to the storage module 130 / 170 / 220, storage section 132A / 132B / 172A / 172B / 222, and heat sensitive section 134A / 134B / 174A / 174B / 220, respectively. The structure, function, and materials of these components may be similar to those described above. Although not shown, the front and / or rear surfaces may have other features, including, but not limited to, a diffraction grating. Although shown as separate components, the storage module 210' and the lens body 220' may be integrated with each other as one part.

[0047] In the illustrated embodiment, the reservoir 222' has walls that include individually formed spherical capsules. Therefore, the capsules for the lens 200' are spherical rather than hemispherical. Each capsule has a heat sensitive portion 224' that forms the capsule wall. Therefore, the heat sensitive portion 224' and the spherical capsule 224' are effectively synonymous for the lens 200. The spherical capsules 224' may be SMPs. In the illustrated embodiment, each spherical capsule 224' is individual. Each capsule 224' is shown to have the same volume. In other embodiments, one or more of the capsules 224' may have different volumes. In the illustrated embodiment, the upper and lower hemispherical heat sensitive portions 224' of the spherical capsule may be heat treated separately.

[0048] Lens 200' functions similarly to lenses 110, 150, and 200. Thus, lens 200' may share the advantages of lenses 110, 150, and / or 200. In particular, the base power of lens 200' may be non-invasively tailored to the patient. This may be achieved by heat treating one or more of capsules 224', for example via a laser. As a result, the base power of lens 200' may be relatively quickly and easily adjusted throughout the life of lens 200'.

[0049] 5 is a flow chart illustrating an example embodiment of a method 300 for providing an ophthalmic lens. For the sake of brevity, some steps may be omitted, interleaved, and / or combined. The method 300 is also described in terms of the ophthalmic device 100 and the 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.

[0050] At step 302, the lens body 120 is provided. Step 302 includes providing a base 122, a flexible membrane 124, and a cavity 126. Some or all of the microfluidic pathways, such as microfluidic pathways 180 or 230, may be provided in forming the lens body 120. Step 302 may include forming and / or connecting the base 122 and the flexible membrane 124 with a space for the chamber 126 therebetween. Step 302 may also include forming a diffraction grating, if formed, on the flexible membrane 124 and / or base 122.

[0051] At step 304, the storage module 130 is provided. Step 304 may include providing heat sensitive portions 134A and 134B at the boundaries of the reservoirs 132A / 132B. For example, a desired SMP having an appropriate shape, size, glass transition temperature, and absorption of laser light is provided. Step 304 may also include forming some or all of the microfluidic pathways.

[0052] If not already completed in steps 302 and 304, the microfluidic pathway 180 or 230 is provided in step 306. Step 306 may simply involve providing an opening or passage between the chamber 126 and the reservoir 132A / 132B. Alternatively, a more complex pathway may be formed.

[0053] At step 308, optical fluid 140 is provided to lens 110. Step 308 may include filling lens 110 with the desired optical fluid 140 and sealing lens 110. Thus, optical fluid 140 may flow between chamber 126 and reservoirs 132A / 132B. Haptics 102 and 104 may optionally be provided at step 310.

[0054] Using the method 300, the IOL 100 and the ophthalmic lenses 110, 150, 200, and / or 200' may be provided. Thus, one or more of the advantages of the lenses 110, 150, 200, and / or 200' may be obtained.

[0055] 6 is a flow chart illustrating an example embodiment of a method 350 for treating a patient's ophthalmic condition and fitting a lens. For the sake of brevity, some steps may be omitted, interleaved, and / or combined. The method 350 is also described in terms of using the ophthalmic instrument 100 and the ophthalmic lens 110. However, the method 350 may be used with the ophthalmic lenses 150, 200, and / or 200'.

[0056] At step 352, a thermally tunable IOL 100 is selected for implantation into the patient's eye. The IOL 100 includes a lens body 120, a storage module 130, a chamber 126, and connections between the reservoirs 132A / 132B and the optical fluid 140. Part of the selection process may include identifying the correction needed for the patient's vision and selecting an IOL 100 having the appropriate power.

[0057] The IOL 100 is implanted into the patient's eye at step 354. Step 354 may involve replacing the patient's own lens with the IOL 100 or supplementing the patient's lens with the IOL 100.

[0058] At step 150, it is determined whether the implanted IOL 100 has the correct base power. Step 150 may include re-measuring the patient's visual acuity. This step may be performed immediately after implantation or at some later time, since the IOL 100 may be adjusted throughout its life in some embodiments. If the base power is correct, the method ends.

[0059] However, if the base power is not correct, the base power of the IOL 100 may be non-invasively adjusted in step 358. If it is desired to correct an increase or decrease in base power, a lens similar to the lens 150 may be selected in step 352. Step 358 may include positioning the desired area of ​​the heat sensitive portion 134A and / or 134B to be heated. A laser may then be aimed at the desired portion of the heat sensitive portion 134A and / or 134B and fired until the glass transition temperature is reached or exceeded. In some embodiments, a low duty cycle may be used for the laser to reduce heating of the eye. Step 358 may be performed during a single outpatient visit. Additionally, steps 356 and 358 may be repeated multiple times until the desired power of the lens 110 is reached. Additionally, steps 356 and 358 may be repeated at various times throughout the life of the lens 110.

[0060] Using method 350, a physician may be able to more quickly and easily adjust the base power of IOL 100 using heat. This may be accomplished without requiring additional glasses for the patient or locking changes into IOL 100. As a result, the burden on both the physician and the patient may be reduced. Method 350 may also be safer for the patient because method 350 may be performed non-invasively. As a result, the advantages of a thermally adjustable IOL 100 and lenses 110, 150, 200, and / or 200' may be achieved.

[0061] Methods and systems for providing a thermally adjustable IOL have been described. These methods and systems have been described with exemplary embodiments as shown in the figures, and those skilled in the art will readily recognize that there may be modifications to these embodiments, all of which are within the spirit and scope of these methods and systems. Accordingly, numerous modifications may be made by those skilled in the art without departing from the spirit and scope of the appended claims. [Explanation of symbols]

[0062] 102 Haptics 106 Optical axis 110 Ophthalmic Lenses 120 Lens body 122 Base 124 Flexible part 126 Chamber 130 Storage Module 132A Storage Unit 132B Storage 134A Heat-sensitive part 134B Heat-sensitive part 140 Optical fluid

Claims

1. An ophthalmic lens, a lens body having a chamber therein, at least a portion of the lens body being flexible and having a lens body refractive index; a reservoir fluidly connected to the chamber of the lens body and positioned at least partially circumferentially around the chamber of the lens body, the reservoir including a plurality of heat sensitive structures that change shape in response to absorbing light energy from a laser; an optical fluid in the chamber and the reservoir, the optical fluid having an optical fluid refractive index, the optical fluid flowing between the reservoir and the chamber to effect a change in base power of the ophthalmic lens; Including, a first portion of the plurality of heat sensitive structures configured to absorb optical energy to change shape and direct optical fluid from the reservoir to the chamber; An ophthalmic lens, wherein a second portion of the plurality of heat sensitive structures is configured to absorb light energy to change shape and direct optical fluid from the chamber to the reservoir.

2. The ophthalmic lens of claim 1 , wherein each thermal sensitive structure of the first portion of the plurality of thermal sensitive structures is further configured to transfer a first volume of optical fluid from the reservoir to the chamber.

3. The ophthalmic lens of claim 2 , wherein each thermal sensitive structure of the second portion of the plurality of thermal sensitive structures is further configured to transfer a second volume of optical fluid from the chamber to the reservoir.

4. The ophthalmic lens of claim 3 , wherein the first volume of optical fluid and the second volume of optical fluid are the same.

5. The ophthalmic lens of claim 3 , wherein the first volume of optical fluid and the second volume of optical fluid are different.

6. The ophthalmic lens of claim 2 , wherein the first volume of optical fluid corresponds to a base power change of 0.25 diopters or less.

7. The ophthalmic lens of claim 1 , wherein each thermal sensitive structure of the first portion of the plurality of thermal sensitive structures is further configured to transfer a predetermined volume of optical fluid from the reservoir to the chamber.

8. The ophthalmic lens of claim 7 , wherein each of said predetermined volumes is the same.

9. The ophthalmic lens of claim 7 , wherein each of the predetermined volumes is equal to either the first volume or the second volume.

10. The ophthalmic lens of claim 1 , wherein the plurality of thermally sensitive structures are configured to change shape in response to reaching a temperature of at least 45 degrees Celsius.

11. The ophthalmic lens of claim 10, wherein the temperature is at least 60 degrees Celsius and no greater than 100 degrees Celsius.

12. The ophthalmic lens of claim 1 , wherein the at least a portion of the lens body includes a flexible membrane.

13. The ophthalmic lens of claim 1 , wherein at least a portion of each of the plurality of heat-sensitive structures comprises a shape memory polymer having a glass transition temperature equal to or greater than a threshold temperature.

14. The ophthalmic lens of claim 13 , wherein the shape memory polymer includes an additive that absorbs light energy within a selected wavelength range.

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