specific embodiments of the invention will now be described in detail with reference to the accompanying figures . like elements in the various figures are denoted by like reference numerals for consistency . further , the use of “ fig .” in the drawings is equivalent to the use of the term “ figure ” in the description . in the following detailed description of embodiments of the invention , numerous specific details are set forth in order to provide a more thorough understanding of the invention . however , it will be apparent to one of ordinary skill in the art that the invention may be practiced without these specific details . in other instances , well - known features have not been described in detail to avoid unnecessarily complicating the description . embodiments of the claimed invention relate to an intraocular liquid ( iol ) lens that contains two immiscible liquids in contact , without any physical separation between liquids . iol devices are typically scrolled or folded prior to injection in the eye , to operate as non - invasively as possible . if such an iol is a liquid lens , the scrolling or folding operation is likely to move liquids out of their confinement area or disperse on liquid in the other due to shear stress and , thus , degrade the performance of the liquid lens . one or more embodiments of the invention relate to a liquid lens and method of manufacturing a liquid lens that remains undisturbed by scrolling or folding . european patent ep1996968 from varioptic is hereby incorporated by reference in its entirety . ep1996868 describes an iol based on electrowetting actuation and made of two immiscible liquids standing on an insulating and hydrophobic surface , encapsulated in a foldable structure . ep1996968 does not disclose the fluids used in such a iol device or how to fold the device without disturbing the liquid &# 39 ; s confinement . one of the issues associated with iol devices is the ability of the device to be folded in order to reduce ocular incision . the present invention provides a solution to this technical issue . in one or more embodiments of the invention , an iol device based on electrowetting actuation , containing two immiscible liquids , enables device folding prior to injection into the patient eye without disturbing the liquid &# 39 ; s confinement . in one or more embodiments of the invention , there are two liquids , one conducting and the other non - conducting . the non - conducting liquid is in a solid state while lens is folded and injected in the patient &# 39 ; s eye . then , the fluid becomes a liquid state once in the patient eye , at intraocular temperature ( typically between 33 ° c . and 37 ° c . using an ambient air temperature of 20 ° c .). in one or more embodiments of the invention , the non - conducting liquid has a melting temperature below intraocular temperature and above 0 ° c . in one or more embodiments , the melting temperature of the non - conducting liquid is above 10 ° c . in one or more embodiments , the melting temperature of the non - conducting liquid is above 20 ° c . because the non - conducting liquid is solid during folding process , it is unlikely that it will move out of its confinement area , and embodiments of the iol device in the present invention may be injected through a reduced corneal incision while having an optimized performance . in one or more embodiments of the invention , a membrane made of a non - conducting compound , may separate the non - conducting and conducting fluid during the folding and injection process . in one or more embodiments of the invention , the conducting liquid has a melting temperature below intraocular temperature and above 0 ° c . in one or more embodiments , the melting temperature of the conducting liquid is above 10 ° c . in one or more embodiments , the melting temperature of the conducting liquid is above 20 ° c . in one or more embodiments of the invention , a membrane made of a polar compound , may separate the non - conducting and conducting fluid during the folding and injection process and melt in the conducting fluid below intraocular temperature . in one or more embodiments of the invention , either the conducting or non - conducting liquid may include a gelling agent , forming a gel when incorporated , or dissolved , into the liquid , and having a melting temperature below intraocular temperature and above 0 ° c . in one or more embodiments , the melting temperature of the jellified fluid is above 10 ° c . in one or more embodiments , the melting temperature of the jellified fluid is above 20 ° c . in one or more embodiments of the invention , the conducting liquid may contain a gelling agent like alginic acid , sodium alginate , potassium alginate , ammonium alginate , calcium alginate , gelatin , furcellaran or polysaccharides like agarose , carrageenan , or pectin . fig1 shows an ophthalmic implant as described in european patent application ep1996968 , in accordance with one or more embodiments of the claimed invention . the implant is made from transparent and flexible materials , examples include , but are not limited to , transparent polymers like polymethyl methacrylate ( pmma ), polycarbonate , epoxies , polyesters , fluoropolymers , fluorinated ethylene propylene ( fep ), ptfe ( polytetrafluoroethylene ), polyolefins , and polycycloolefins . inside the implant , two liquids are trapped : the first liquid ( 4 ) is a non - polar liquid , non - conducting ( or insulating liquid ) forming a drop inside the capsule . the second liquid ( 5 ) is a conducting polar liquid ( may be based on water solution ). both liquids are immiscible , with approximately the same density , and different indices of refraction . a first electrode ( 11 ) in the shape of a ring may be covered with a thin insulator film ( 2 ) for electrowetting actuation . in the embodiment described in fig1 , the thin insulator film ( 2 ) is also playing the role of the capsule window . a second electrode ( 10 ) is in direct contact with the conducting liquid ( 5 ). electrowetting actuation is used to activate the lens . using a control signal , a voltage is applied between electrodes ( 10 ) and ( 11 ). the voltage induces an electrowetting effect , thus changing the contact angle of the drop of liquid ( 4 ), passing from shape a ( flat drop ) to shape b ( a more curved drop ). because the indices of refraction of the two liquids are different , the device forms a variable power lens . in one or more embodiment of the invention , the dioptre variation may range from a few dioptres to several tens of dioptres . in one or more embodiments of the invention , the non - conducting fluid includes one or more non - conducting compounds with a melting temperature below intraocular temperature , and above the temperature during the injection process . fig2 is a schematic of the process in accordance with one or more embodiments of the invention . table 1 describes several compounds with corresponding melting temperatures . examples of specific conducting and non - conducting fluids in accordance with one or more embodiments of the invention are given in formulations 1 and 4 ( respectively conducting and non - conducing fluids ), formulations 2 and 5 , and formulations 3 and 6 . however , the claimed invention is not limited to these specific combinations of conducting and non - conduction fluids . the liquid lens may filled with both conducting and non - conducting fluids at a temperature above melting temperature , then cooled until the non - conducting fluid is solidified . iol may then be scrolled or folded at a temperature below the melting point temperature in preparation for surgery . once the iol is within the patient &# 39 ; s eye , and unfolded , the non - conducting fluid melts and the liquid lens becomes operational . in one or more embodiments of the invention , the conducting fluid comprises water and at least one organic or inorganic ion , typically at least one organic or inorganic ionic or ionizable salt , or a mixture thereof , conferring conductive properties to said fluid . in the following specification , “ ionic salts ” refers to salts that are totally or substantially totally dissociated ( such as a bromine - anion and a cation ) in water . “ ionizable salts ” refers to salts that are totally or substantially totally dissociated in water , after chemical , physical or physico - chemical treatment . ions that are suitable in the present invention include both cations and anions , which may be simultaneously , but not necessarily , present together in the conducting fluid . examples of anions include , but are not limited to , halides , e . g . chloride , bromide , iodide , sulphate , carbonate , hydrogen carbonate , acetate , and the like , as well as mixtures thereof . examples of cations include , but are not limited to alkali , and alkaline - earth . organic and inorganic ionic and ionizable salts are thus well known in the art , and examples of these include , but are not limited to potassium acetate , magnesium chloride , zinc bromide , lithium bromide , sodium bromide , lithium chloride , calcium chloride , sodium sulphate , sodium dibasic phosphate , sodium monobasic phosphate , phosphoric acid , acetic acid , sodium acetate , carboxylic acid ( rcooh , where r being an alkyl group c 2n h 2n + 1 , with n being between 1 and 10 ) and corresponding sodium carboxylate salt , phosphocholine salt and the like , as well as mixtures thereof . mixtures of one or more ionic salts together with one or more ionizable salts are also encompassed by the present invention . as already mentioned , the conductive fluid comprises an organic or inorganic ionic or ionizable salt . said salt is dissolved in water . water to be used in the conductive fluid should be as pure as possible , i . e . free , or substantially free , of any other dissolved components that could alter the optical properties of the optical electrowetting device , namely an optical lens driven by electrowetting . ultra pure water is most preferably used . the concentration of the dissolved salt in the conductive fluid may vary in large proportions , keeping in mind a too high concentration may result in undesirable increase of density , refractive index , turbidity , haze , or loss of transparency for the optical device , lens or else . in one or more embodiments of the invention , the non - conducting fluid is a mixture of compounds , where at least one compound has a melting temperature above intraocular temperature , but the mixture thereof has a melting temperature below intraocular temperature . this is possible because most liquids have a melting temperature depression when mixed with other compounds , when all compounds are miscible . fig3 shows a schematic of the process in accordance with one or more embodiments of the invention . compounds having the highest melting temperature may be injected in the liquid lens at a temperature above its melting temperature then cooled to a temperature above melting point of the next compound to be injected . at this stage , the injected compounds may have been solidified as a result of the cooling . therefore , all compounds may be injected separately . the order of injection may be from the highest melting point to the lowest melting point . when the last compound is injected , the iol may be cooled until the non - conducting fluid is fully solidified . iol may be folded at temperature below melting point temperature and is ready for the surgery operation . once the iol is within the patient eye , and unfolded , the non - conducting fluid compounds melt , mix together , and liquid lens becomes operational . one specific example of the above embodiment is the formulation 1 and 7 ; however , the above embodiment is not limited as such . fig4 is a schematic of a process to fill , fold and inject an iol using two separate non - conducting fluids , where one has a melting temperature ( mp # 2 ) below injection temperature and the other has a melting temperature ( mp # 1 ) above injection temperature , but below the intraocular temperature in accordance with one or more embodiments of the invention . the fluid having the lowest melting temperature , below injection temperature , is injected in the liquid lens at a temperature above its melting temperature , and then cool down until solidification . that fluid is kept at a temperature below melting temperature of the other compounds . then a fluid having a melting temperature between the injection temperature and the intraocular temperature is injected and , thus , solidified at the surface of the first injected compounds . therefore , in accordance with one or more embodiments of the invention , the fluids may be injected separately with the fluid having the highest melting temperature physically located at the interface between the conducting fluid and the other non - conducting fluid . examples of the conducting and non - conducting fluids that may be used include , but are not limited to , the formulations 1 and 8 and formulations 3 and 9 . in one or more embodiment of the present invention , the non conducting fluid is injected in the liquid lens at a temperature above its melting temperature , and then cool down until solidification . a further compound is then deposited on the solidified non - conducting fluid prior to the conducting fluid injection to form a solid membrane . the membrane remains solid during the folding process and injection but is soluble in the conducting or the non - conducting fluid at intraocular temperature after injection in the patient &# 39 ; s eye . in one or more embodiment of the present invention , the solid membrane is made of water soluble polymers like hydroxyethylcellulose , ethylcellulose polymers , cellulose ethers , poly ( acrylic acids ), polyvinyl alcohol , or water soluble resins , or hydrocarbon soluble polymers . in one or more embodiment of the present invention , the solid membrane formed between the conducting and non conducting fluids is made soluble in fluids by irradiation during the capsulotomy operation . the iol may then be folded at temperature below melting point temperature of the compounds at the interface and warmed up at the injection temperature . the fluid at the interface may act as a membrane between the conducting fluid and the other non - conducting fluid that has a melting temperature below the injection temperature . at this point , the iol is ready for surgical implantation . once the iol is within the patient &# 39 ; s eye and unfolded , the non - conducting fluids may melt and mix together . at this point , the liquid lens becomes operational . in one or more embodiments of the invention , the insulating coating may be made of poly - para - xylylene linear polymers , for example , parylene c ; parylene n , parylene vt4 , and parylene ht . in one or more embodiments of the invention , the insulating coating may be coated with a thin layer of a low surface energy coating such as teflon ® or fluoropel ®. table 1 is a list of compounds that may be used in the present invention . in one or more embodiments of the invention , the non conductive fluid may contain a linear alkane ( c n h 2n + 2 , where 22 & gt ; n & gt ; 15 , such as hexadecane , nonadecane , eicosane ), a diphenyl alkane ( c 2 h 2n —( c 6 h 5 ) 2 , where 5 & gt ; n & gt ; 1 , such as diphenylmethane , diphenylethane ), or vinyl triphenylsilane . in one or more embodiments of the invention , the non - conductive fluid may contain one or more of the following specific compounds : diphenylsulfide , palmitic acid , 1 , 4 - di - ter - butylbenzene , 1 - methylfluorene , 9 , 10 - dihydroanthracene , and fluorene . in one or more embodiments , the non - conductive fluid may contain one or more cycloalkane c n h 2n , where 6 & lt ; n & lt ; 15 , such as cyclooctane , cyclohexane , or cyclododecane . in one or more embodiments , the non - conductive fluid may contain one or more organosilanes of formula si —( r ) 4 , where at least three of the r groups are represented independently by ( hetero ) aryl , ( hetero ) arylalkyl , ( hetero ) arylalkenyl and ( hetero ) arylalkynyl . in such embodiments , the at least one of the r groups may be an alkyl ( c n h 2n + 1 ) or alkene group ( c n h 2n − 1 ), where n = 1 , 2 or 3 . examples include , but are not limited to methyltriphenylsilane , allyltriphenylsilane , and ethyltriphenylsilane . the non - conductive fluid may contain one or more germane based species , for example hexamethyldigermane , diphenyldimethylgermane , and phenyltrimethyl - germane . table 2 describes mixtures of compounds depending on temperature and indicates when mixture is in solid and liquid state in accordance with one or more embodiments of the invention . the solid state should be used during folding and injection . in particular table 2 demonstrates that a small amount of compound having a very low melting temperature ( for example & lt ; 20 ° c . for phenyltrimethyl germane ) mixed with a large amount of a high melting temperature compound ( for example diphenylmethane ) will result in a mixture with a melting temperature in the required range , i . e . between 10 ° c . and 32 ° c . embodiments of the invention may be used in any application that using a device containing two immiscible liquids , such that the liquids are contact with each other , and the device is folded during the application at a given temperature , and then unfolded at another temperature above the first temperature , where the liquids must be confined in a given volume , when the performance of the device may be disturbed and / or lowered if liquids are temporarily mixed during the folding and unfolding process . while the invention has been described with respect to a limited number of embodiments , those skilled in the art , having benefit of this disclosure , will appreciate that other embodiments can be devised which do not depart from the scope of the invention as disclosed herein . accordingly , the scope of the invention should be limited only by the attached claims .
according to a first aspect , the invention relates to an intraocular variable focus implant comprising a non - conducting liquid with a melting temperature above 0 ° c ., a conducting liquid , a liquid interface formed by the non - conducting and conducting liquids , a first electrode in contact with the conducting liquid , a second electrode insulated from the conducting liquid , wherein the liquid interface is movable by electro wetting according to a change in a voltage applied between the first and second electrodes .