the present invention is related to ophthalmic devices and their compositions derived from crystalline polymeric materials having a crystalline melting temperature ( t m ) in the range of about 0 ° c . to about 37 ° c ., preferably in the range of about 14 ° c . to about 30 ° c . in addition to the t m , these crystalline polymeric materials also have a t g ( glass transition temperature ) which is lower than the t m for the given composition and is in the range from about − 100 ° c . to about 37 ° c ., preferably about − 100 ° c . to about 20 ° c . in one embodiment , the crystalline polymeric material has a t g from about − 100 ° c . to about − 17 ° c . unlike the hydrogel materials taught in the stay , et al . patent , discussed above , the t m and t g properties of the materials used in the present invention are not dependent on being in osmotic equilibrium in the body ( i . e ., t m and t g do not change in the presence of eye liquids ). although there are many different polymer structures which can form the desired crystalline regions , the preferred embodiments of the present invention include side chain crystalline - inducing polymers . the more preferred embodiments are the acrylic family of polymers with long side chain alkyls ( more than twelve carbons ) as the crystalline - inducing groups . it is well known to whose who are skilled in the art that as the length of the side chain of an acrylic ester monomer increases , the t g of the homopolymer decreases . for example , consider where r ═ h or ch 3 ; and r ′= alkyl groups , such as ch 3 —( ch 2 ) n —, n = 0 to 19 . when r ═ ch 3 , and r ′ is the alkyl group where n increases from 0 to 17 , then t g of the homopolymer of the respective monomer decreases . the trend is illustrated in table 1 . additionally , as n increases from 11 ( lauryl methacrylate ) to 17 ( stearyl methacrylate ), side chain crystallinity starts to form . for example , polystearyl methacrylate ( n = 17 in r ′) has a side chain crystalline formation with a t m of about 36 ° c . the melting temperature , or t m , is a characteristic of crystalline or semi - crystalline polymers . melting may be observed visually in some materials , as the temperature increases when a material changes from white or opaque to hazy or transparent . before the advent of sophisticated instrumental methods , melting temperatures were determined by viewing the melting polymer under a microscope between crossed polarizers . dilatometry , where volume changes are measured , is another method for finding t m . the use of a differential scanning calorimeter ( dsc ) is a popular method for examining the melting transition and is used for the determination of the t m in the present invention . polystearyl methacrylate ( sma ) is a white solid polymer at room temperature in its crystalline form . however , polystearyl methacrylate is found to be transparent when it is warmed to a temperature higher than its melting temperature and its side chain crystalline structure melts . because polystearyl methacrylate has a t g of about − 100 ° c ., it is an elastomer after it melts . these dual thermodynamic properties , one corresponding to t g and another corresponding to t m , are required for the crystalline polymers in the present invention . however , the homopolymer of stearyl methacrylate is tacky after it melts . this tackiness can be reduced by copolymerization with other monomers , such as methyl methacrylate ( mma ). this tackiness can be further reduced by adding and increasing the amount of crosslinkers . crosslinkers ( for example , egdma , ethylene glycol dimethacrylate ) can also improve the elasticity of the crystalline polymer , and therefore increase its capability for recovery from a deformed state . table 2 is a summary of examples for the present invention . examples of polymeric materials which may be used in the ophthalmic devices of the present invention include polymers , homopolymers , cross - linked polymers and copolymers of silicones , acrylic esters , polyurethane , hydrocarbon polymers , and combinations thereof . specific materials include , for example , acrylic esters , copolymers of long chain methacrylates with short chain methacrylates ( such as copolymers of polystearylmethacrylate with polymethylmethacrylate ), and side - chain crystalizible polymers which comprise an acrylic ester of the formula : wherein x is h or a c 1 - c 6 alkyl , and r is a linear c 10 - c 26 alkyl . one of the applications for the present invention is to provide an alternative and superior method for implanting an iol of various designs through a small incision . the iol can be phakic or aphakic and it may be located in the posterior chamber of the eye or in the anterior chamber of the eye , or within the cornea , or a combination of them . samples for the iol design of the present invention are illustrated in , but not limited to , fig1 - 14 . of particular interest is the full size lens , such as the one in fig5 . a full size lens has a diameter in the range from about 8 to about 11 mm and a central lens thickness in the range from about 1 to about 5 mm . the present invention can allow such a full size lens to be implanted through a small incision . because the iol nearly fills the whole capsular bag , it may be possible that such a full size lens can inhibit secondary cataract formation . the present invention also allows such a full size lens to support the capsule . the support reduces the risk for physicians choosing to open a capsulorhexsis , or opening in the capsular bag , on both the anterior and posterior surfaces using manual or laser techniques such as femtosecond laser capsulotomy ( see friedman , n . et al , femtosecond laser capsulotomy , j cataract refract surg 2011 , 37 : 1189 - 1198 , for one description of this technique ). this is done to prevent loss of vision due to secondary capsular opacification . the present invention also allows a phakic lens to be designed with larger dimensions . increased diameter of the clear aperture of the phakic lens optic may benefit visual quality and reduce dysphotopsias such as glare , halos , and ghost images . the dimensions of the optic have been limited by the widely practiced use of the smallest possible incision size for lens implantation . the present invention will allow a phakic lens with an optic diameter between 5 and 8 mm to be deformed to a cross sectional area that may be inserted through an incision of less than 3 mm with reduced risk of trauma to tissues of the eye such as the cornea and endothelium . some phakic lenses are designed using flexible polymers with relatively thin cross sections to better fit eyes with small anterior or posterior spaces . such dimensional constraints could increase the risk of lens structural damage , such as tears , during insertion . increased dimensional deformation and used of a material with crystallized side chains will reduce stress and increase durability during implantation . the lenses will become thin , soft and flexible after shape recovery . one feature of the crystalline polymers used in the present invention is that they provide materials with a very wide range of properties , such as hardness ( or softness ) as measured by durometers . because t g and t m are two distinctly different thermodynamic transitions in polymer properties , it is possible to provide very soft materials by the present invention . for instance , example 1 in table 2 has a melting point of 34 ° c . corresponding to the crystalline structure formed by the side chain stearyl group , and a t g of − 100 ° c . corresponding mainly to the long polymeric backbone structure . at room temperature , it is a hard white solid . however , when the copolymer is heated up to the melting temperature or higher , it becomes transparent after all crystalline side chains have melted . it also becomes very soft because the melted side chain stearyl groups function as a plasticizer or as if it were a “ solvent ”. this low hardness can be a very useful property in the case of a full size lens design which may possibly accommodation for the presbyopia patients . the “ fluid ” property due to the melted crystalline side chain is also the driving force in the present invention for the ophthalmic device to adapt to a new configuration shaped by the surrounding tissue . on the other hand , the elasticity due to the long chain of the polymer backbone and the crosslinking is the driving force for the shape recovery of the ophthalmic devices from the deformed shape to the pre - deformed shape . this crystalline - fluid interphase change of the long side chain provides a novel mechanism for achieving the goals of the present invention . in order to understand the way the present invention is practiced , an intraocular lens ( iol ) is used as an example . the iol of the present invention is made from crystalline polymeric materials having the following properties : ( 1 ) crystalline melting temperature , t m , in the range from about 0 ° c . to about 37 ° c ., preferably from about 15 ° c . to about 30 ° c . ( 2 ) glass transition temperature , t g , in the range from about − 100 ° c . to about 20 ° c ., preferably from about − 100 ° c . to about − 17 ° c . in all cases , t g , should not be higher than room temperature . ( 3 ) being optically transparent at or above the t m . on the other hand , it is not necessary for the iol made from the crystalline polymeric material to be transparent below the t m . it may not be a requirement for non - lens related applications that the crystalline polymer be transparent at any given temperature . furthermore , other additives may be added to the crystalline polymer composition as required by the specific circumstances . for example , an ultraviolet ( uv ) absorber may be incorporated into lenses for the protection of human eyes from damage caused by uv light exposure . another example is that barium sulfate may be added to a non - lens device for rendering it radio - opaque . therefore , the device can be examined by a radiological method if needed . the method for implanting the iol ( or other ophthalmic device ) of the present invention includes the following steps : ( a ) warm the iol to a temperature at or above the t m , then deform the iol into a shape , such as folded , rolled , and / or stretched at the same time , which can be implanted through a small incision into the eye . the ideal size for the incision is from about 2 to about 4 mm . ( b ) cool down the deformed iol to a temperature below the t m while the deforming force , such as folding , rolling , clamping , and / or stretching , etc ., is still applied to the iol . after removing the deforming force , the cooled iol will remain in its deformed shape . ( c ) implant the deformed lens at a temperature below the t m through a small incision into the eye so that the lens remains in the solid deformed form and that it is relatively easy to insert into the soft tissue opening . ( d ) when warmed up to and above the t m , by the body temperature of the eye , the deformed iol will return to its pre - deformed shape , providing the desirable optical power and resolution for the patient . to a round - bottomed flask , equipped with a magnetic stir bar , is added a mixture of 4 . 75 grams of sma , 0 . 25 gram of mma , 5 microliters of ethylene glycol dimethacrylate , and 0 . 01 gram of benzoyl peroxide . the flask is purged with nitrogen gas for about 2 minutes and subsequently maintained under positive nitrogen atmosphere . the reaction mixture is then heated to about 110 ° c . while stirring . after approximately 5 minutes , evolving of gas is observed , indicating decomposition of the benzoyl peroxide initiator to form benzoyloxy radicals initiating the polymerization reaction . after approximately 5 minutes from when the initial gas evolution is first observed , the reaction mixture becomes obviously viscous , indicating the polymerization and crosslinking reaction has occurred . before the reaction mixture becomes too viscous to be poured out from the flask , a small amount of the mixture is taken out with a spatula and is transferred into an iol mold . the mold is then closed and is placed into a preheated oven at 110 ° c . for 16 hours . after the mold is taken out from the oven and cools down to room temperature , the mold is placed in a refrigerator for about 2 hours . the mold is then opened . a white or translucent solid iol is carefully removed from the mold . the iol prepared from above procedure is placed in warm water ( 37 ° c ., for example ), and the iol gradually changes from the white or translucent solid to a transparent soft lens . this soft lens can be stretched to reduce the intersectional area in the warm water bath . the stretched iol is then removed from the warm water bath and allowed to cool down to the room temperature . the stretched iol retains its stretched shape after about 3 minutes . the stretched iol gradually changes from transparent to translucent and then to white hard solid . if an ice water bath is used instead of room temperature air , this “ freezing ” process can be completed in about 1 minute . when the stretched iol is warmed again in a 37 ° c . saline solution or water bath , it returns to its pre - stretched shape in about 1 minute . the recovered lens is transparent and soft as long as the temperature is maintained at 37 ° c . or higher . other compositions in table 2 are prepared in a similar manner . when a uv absorber is used , it can be added to the initial reaction mixture before the heating step . in addition , ice water is preferably used for these compositions with the t m less than 20 ° c . for the freezing step . a mixture of 5 grams of stearyl methacrylate and 0 . 01 gram of benzoyl peroxide is warmed to about 40 ° c . so that it becomes a homogenous solution . the mixture is degassed and refilled with nitrogen . after the mixture is transferred into a polypropylene tube with an internal diameter of about 1 mm and with one end pre - sealed by heating , the open end is also sealed by heating . the sealed tube is about 2 inches long and is placed in an oven at 110 ° c . for 16 hours . at the end of the reaction , the oven is cooled down to room temperature . then both ends of the sealed tube are cut off . the white solid rod inside the tube can be pushed out from the tube with a metal wire . the white solid rod prepared from above procedure can be warmed up in a water bath ( 45 ° c ., for example ). it becomes transparent and soft almost instantly . the soft rod is stretched in the water bath until the diameter of the rod becomes about 0 . 3 mm . the stretched rod is then lifted from the warm water bath to the room temperature air . it becomes solid in about 1 minute and retains its stretched shape as long as the temperature remains below its melting temperature . when the stretched rod is warmed up in a saline solution , such as 37 ° c ., it becomes soft and its diameter changes back to 1 mm in about 1 minute .
ophthalmic devices suitable for implantation into the eye through small incisions or insertion into an existing orifice are disclosed . these devices are made from a composition comprising crystalline or semi - crystalline polymeric materials which have a glass transition temperature of from about − 100 ° c . to about 37 ° c ., and wherein t g for the material is lower than t m for the composition . disclosed devices include intraocular lenses , corneal inlays , drug delivery devices and implants for reducing intraocular pressure in glaucoma patients .