FR3072787A1 - CONTACT LENSES HAVING IMPERMEABLE PORTION TO IONS AND RELATED METHODS - Google Patents

Abstract

Contact lenses that have an ion impermeable portion and an ion permeable portion that are capable of movement on the eye without binding to the eye are described. The contact lenses exhibit an average ionoflow transmittance of at least 1.34x10-4 mm / min. One or more electronic components may be included in the contact lenses. Methods of manufacturing contact lenses are also described.

Description

CONTACT LENSES HAVING A WATERPROOF PART FOR IONS AND RELATED METHODS

FIELD OF THE INVENTION The present description relates to contact lenses and related methods, and more specifically to contact lenses which manifest movement on the eye and have an ion-impermeable part, and related methods.

TECHNOLOGICAL BACKGROUND [0002] It is desirable for soft contact lenses to exhibit a clinically acceptable amount of movement on the eye in order to avoid binding of a contact lens to the eye. For rigid gas permeable contact lenses (RPG), this goal is achieved by the design of the RPG contact lens and the way it adapts to the person's cornea. For soft contact lenses, namely hydrogel and silicone hydrogel contact lenses, the movement on the eye depends on the diffusion of ions through the contact lens.

[0003] Since the development of silicone hydrogel contact lenses, it has been proposed to include electronic components in contact lenses. These electronic components block the diffusion of ions through the contact lens at the location of the electronic components. As a result, these contact lenses containing electronic components are likely to develop a clinically unacceptable amount of movement on the eye and its prone to binding the eye.

There remains a need for contact lenses which include one or more electronic components or other ion-impermeable components which exhibit clinically acceptable movement on the eye and which do not bind to the eye or eyes of the eye. 'one person.

SUMMARY The present invention provides new contact lenses and methods that meet this need, among others. It has now been determined that contact lenses which include an ion impermeable part, such as one or more electronic components, and the like, and an ion permeable part, must meet a minimum threshold relationship between a property of diffusion of ions and a thickness property so that these contact lenses exhibit clinically acceptable movement on the eye and do not bond to the eye. This relationship is described here, and is referred to as the average transmittance of the ionoflux, which is a relationship between the diffusion coefficient of the ionoflux of a contact lens, and the average thickness of the contact lens.

In one aspect, contact lenses are described. According to this aspect, a contact lens includes a lens body which includes an ion impermeable portion and an ion permeable portion.

In some embodiments, the lens body has a transmittance of the ionoflux of at least 1.34 × 10 ⁴ mm / min. In other embodiments, the lens body has a transmittance of the ionoflux of about l, 34xl0 ^'4 mm / min to about 9,0xl0 ^_1 mm / min. In still other embodiments, the lens body has a transmittance of the ionoflux from about 1.34 x 10 ' ⁴ mm / min to about 1.50 x 10' ¹ mm / min.

In other embodiments or additional embodiments, the lens body has an average thickness of at least 50 micrometers.

In other embodiments or additional embodiments, the lens body has a diffusion coefficient of the ionoflux of at least 6.7xl0 ' ⁶ mm ² / min.

In other embodiments or additional embodiments, the lens body has an ion permeable portion which extends radially inwardly from a lens edge defining the lens body at a distance d '' at least 7% of an annular diameter of the lens body.

In other embodiments or additional embodiments, the lens body has an average thickness of at least 50 micrometers, a diffusion coefficient of the ionoflux of at least 6.7xl0 ' ⁶ mm ² / min, and the ion-permeable part which extends radially inwards from a lens edge delimiting the lens body at a distance of at least 7% of an annular diameter of the lens body. As discussed here, the lens body can be worn on one eye without binding to the eye for a period of at least 6 hours.

In other embodiments, the lens body includes an ion impermeable part which includes an electronically adjustable optic which provides a first refractive power without energy, and adjusts to a second refractive power by receiving the energy, and at least one additional electronic component for supplying energy to the electronically adjustable optics, and the ion-permeable part comprises a polymeric hydrogel material or a polymeric silicone hydrogel material, and the ion-permeable part is present as a ring extending radially inwards from an edge of the lens delimiting the lens body by a distance which is at least 7% of an annular diameter of the lens body.

Another aspect of the present invention relates to methods of manufacturing the contact lenses described here. The methods include forming a lens body from at least one lens-shaped material, wherein said lens body has characteristics described herein for the present contact lenses.

Other aspects and embodiments of the present contact lenses and methods will be apparent from the description, the drawings and the claims which follow. As will be appreciated from the foregoing and following description, each and all of the features described herein, each and all combinations of two or more of these features are included within the scope of the present invention to provided that the features included in such a combination are not mutually inconsistent. In addition, any feature or combination of features can be specifically excluded from any embodiment of the present invention.

BRIEF DESCRIPTION OF THE DRAWINGS [0015] FIG. 1 is a plan view of the anterior surface of a contact lens illustrating four meridians (0 degrees, 90 degrees, 180 degrees and 270 degrees).

FIG. 2 is a cross-sectional view of a contact lens, the section being taken through the geometric center of the contact lens.

FIG. 3 is a plan view of an anterior surface of a contact lens illustrating the multiple sites for measuring the thickness of the lens along the meridians 0 and 180 degrees and the thickness of the lens along the meridians 90 and 270 degrees.

FIG. 4 is a plan view of an anterior surface of a contact lens illustrating four quadrants, each quadrant having a site for measuring the thickness of the lens.

FIG. 5 is a graph illustrating the relationship between the diffusion coefficient of the ionoflux and an average lens thickness, and the average transmittance of the ionoflux of the present contact lenses. An intersection line represents the properties of a contact lens having an average thickness of 50 micrometers. The other line of intersection represents the properties of a contact lens with an average thickness of 200 micrometers.

FIG. 6 is a plan view of a front surface of a contact lens illustrating the geometric center and an annular ion-permeable part.

FIG. 7 is a plan view of an illustration of the embodiments of the present contact lenses in which the ion-impermeable part comprises at least one electronic component.

FIG. 8 is a plan view and a sectional view of an illustration of embodiments of the present contact lenses in which the ion impermeable portion is sandwiched between a hydrogel or prior silicone hydrogel component and a component hydrogel or posterior silicone hydrogel.

FIG. 9 is a sectional view of an illustration of embodiments of the present contact lenses in which the ion impermeable portion is located against a surface (e.g., the front surface) of a hydrogel component or a hydrogel component posterior silicone.

DETAILED DESCRIPTION As described here, the present invention is based on the realization that in order for a contact lens which includes an ion impermeable part (eg, one or more ion impermeable components) and an ion permeable part ions (e.g., hydrogel or silicone hydrogel material) manifest clinically acceptable eye movement, certain properties must be present. Although the exact configuration of the ion impermeable part and the ion permeable part may vary from one embodiment to another, it has been discovered that these contact lenses must meet a minimum threshold in terms of diffusion. ions and thickness of the lens in order to move on the eye. Various embodiments and the relationship of these parameters are described below.

FIG. 1 illustrates a contact lens 10, which will be described later in order to provide the context of the present contact lenses. The contact lens 10 includes a lens body 12. As discussed herein, unlike existing contact lenses formed from a single lens formulation, the lens body of contact lenses 10 includes at least two separate parts; a part impermeable to ions and a part permeable to ions. The lens body 12 includes an optical zone 14 circumscribed by an optical zone border 16 which can be viewed with the naked eye or with the aid of an instrument. A peripheral zone 17 circumscribes the border of the optical zone 16, and a lens edge 20 circumscribes the peripheral zone 17. The geometric center 18 of the lens body is illustrated, and typically is also the geometric center of the optical zone 14. Aux For the purposes of this description, four meridians are illustrated, namely the 0 degree meridian, the 90 degree meridian, the 180 degree meridian and the 270 degree meridian. As will be appreciated by those skilled in the art, the 0 degree and 360 degree meridians are the same.

FIG. 2 illustrates a contact lens 10 which includes a lens body 12 as shown in FIG. 1. In addition, the lens body comprises an anterior surface 22 and a posterior surface 24. The posterior surface 24 is generally of concave shape and formed to be placed in contact with the film of tears of a person's eye. A thickness "h" is illustrated as the distance between the anterior surface 22 and the posterior surface 24.

In one aspect, the present invention relates to contact lenses which include or consist of an ion impermeable part and an ion permeable part.

As used here, an ion-impermeable part refers to a part of a contact lens body which has no measurable ion diffusion. As will be understood by those skilled in the art, the diffusion of ions from contact lenses into hydrogel or silicone hydrogel is defined by determining the diffusion coefficient of the ionoflux through a contact lens. A method for determining the diffusion coefficient of the ionoflux of the present contact lenses is described here. Thus, it can be understood that the ion impermeable part of the contact lens body has an undetectable Tionoflux diffusion coefficient using the method and equipment described here. In comparison, the ion permeable part of the contact lens body has a measurable Tionoflux diffusion coefficient using the method and equipment described here. It can be understood that, as used herein, an ion-impermeable part and an ion-permeable part refer to different parts having different material properties, namely different ion permeabilities. As used here, a part has no geometric limitation, unless otherwise indicated. We have found that the method and equipment described here make it possible to measure diffusion coefficients of the ionoflux greater than 5 × 10 ' ⁷ mm ² / min, so that a contact lens body or a part of the body contact lens with an ionoflux diffusion coefficient of less than 5 x 10 ' ⁷ mm ² / min is considered as not measurable and therefore impermeable to ions. For a contact lens body having an ionoflux diffusion coefficient (i.e., an ionoflux diffusion coefficient greater than 5 X IO ' ⁷ mm ² / min), the ionoflux diffusion coefficient of The entire lens body will depend on the ion-flux diffusion coefficients of the ion-permeable and ion-impermeable parts of the lens body and the proportion of the area occupied by these parts. It will often be apparent when a part of the lens body is impermeable to ions; for example, when it includes a metallic layer which extends over the entire part and therefore prevents ions from passing through this part. When it is not so apparent, the ion permeability or impermeability of a region of the lens can be measured by separately measuring the diffusion coefficient of the ionoflux of a sample of the materials constituting the region and by considering the geometric arrangement of the samples in the region; in other words, the lens region will be ion impermeable if one or more ion impermeable materials extend together or separately over the entire region. Alternatively, if the diffusion coefficient of the ionoflux of the material (s) permeable part is known or measured separately, the diffusion coefficient of the ionoflux of another part can be calculated from the ratio of areas of the permeable part and the other part and a measure of the diffusion coefficient of the ionoflux of the whole lens body.

The ion-impermeable part and the ion-permeable part together form the lens body of the contact lens. This contrasts with existing contact lenses which are formed from a single polymerizable composition, giving a contact lens having a relatively homogeneous polymer structure in the form of a contact lens, which may or may not be surface treated. In the context of the present description, the ion-impermeable part may be present in one or more regions of the lens body. Likewise, the ion permeable part may be present in one or more regions of the lens body. In embodiments in which the lens body includes multiple ion-permeable regions defining the ion-permeable portion, the ion-permeable regions may be made of the same or different materials. For example, if a lens has a posterior hydrogel component, it may have an anterior hydrogel component or an anterior silicone hydrogel component. In the context of the embodiments described here, the ion-impermeable part may include one or more electronic components, one or more components made of silicone elastomer, or combinations thereof. In the embodiments described in more detail here, the ion permeable portion may include one or more hydrogel components or one or more silicone hydrogel components, or combinations thereof. As used herein, "hydrogel" used alone means a polymeric material which is free of silicone and has an equilibrium water content (TEE) of at least 10% (by weight). In some embodiments, the hydrogel has a TEE of 10% to 90% by weight. In other embodiments, the hydrogel has a TEE of 10% to 70% by weight. As used herein, "silicone hydrogel" refers to a hydrogel that includes a silicone component, therefore a silicone hydrogel, which also has an equilibrium water content (TEE) of at least 10 % (in weight). In some embodiments, the silicone hydrogel has a TEE of 10% to 90% by weight. In other embodiments, the silicone hydrogel has a TEE of 10% to 70% by weight.

Any suitable hydrogel polymeric material or any suitable silicone hydrogel polymeric material can be used in the present contact lenses. For example, some common hydrogel and silicone hydrogel materials are known by their adopted names US (USAN), such as etafilcon A, ocufilcon A, ocufilcon B, ocufilcon C, ocufilcon D, omafilcon A, omafilcon B, methafilcon A, comfilcon A , enfilcon A, stenfilcon A, fanfilcon A, somofilcon A, riofilcon A, senofilcon A, senofilcon B, senofilcon C, narafilcon A, narafilcon B, and the like. Typically, these hydrogel materials include one or more hydrophilic monomers, such as 2hydroxyethylmethacrylate (HEMA), n-vinyl pyrrolidone (NVP), dimethylacrylamide (DMA), methacrylic acid (AMA), and the like. Silicone hydrogel materials can include any of these hydrophilic monomers, and can also include one or more polydimethylsiloxanes (PDMS). These materials may also include crosslinking agents, dyeing agents, ultraviolet (UV) absorbing agents, and the like.

As used here, “silicone elastomer” refers to a material containing silicone, which is also called in the technique “silicone rubber”, and is a material based on polyorganosiloxanes, such as, for example, polydimethylsiloxanes (PDMS). The silicone elastomer component of the present contact lenses may consist of, or consist essentially of, a crosslinked silicone elastomer. For example, the silicone elastomer component can be essentially devoid of any polymer component other than the polyorganosiloxanes. As used herein, the silicone elastomer component has a water content of less than 1% by weight based on the total weight of this component. In some examples, the silicone elastomer component has a water content of less than 0.5% by weight, or less than 0.3% by weight, for example from 0% by weight to 0.9% by weight. Crosslinkable formulations for forming the silicone elastomer component include MED 6015, MED 6755 and MED 6033, from NuSil Technology, and SYLGARD elastomers from Dow Corning. Silicone elastomer formulations can be cured in accordance with the manufacturer's recommendations.

The TEE of the lens body or any of the lens materials can be measured by wiping off excess water from the surface of the lens body or the polymerized form of the lens materials and weighing the items to get hydrated weight. The article is then dried in an oven at 80 ° C in a vacuum, then weighed. The weight difference is determined by subtracting the weight of the dry item from the weight of the hydrated item. The TEE (% by weight) of the article is = (difference in weight / hydrated weight) x 100.

The diffusion coefficient of the ionoflux of the present lenses can be determined using routine methods known to the ordinary person skilled in the art. In the context of the present application, the ionoflux was measured using a technique substantially similar to the "Ionoflux technique" described in U.S. Patent 5,849,811 which is incorporated herein by reference. Before the measurement, a hydrated lens was equilibrated with deionized water for at least 10 minutes (for example, from 10 minutes to 120 minutes). The lens to be measured is placed in a lens immobilizer between male and female parts. The male and female parts include flexible sealing rings which are positioned between the lens and the respective male and female part. After positioning the lens in the immobilizer, the lens immobilizer is then placed in a threaded cover. The cover is screwed onto a glass tube so as to define a donor chamber. The donor chamber is filled with 16 ml of 0.1 molar NaCl solution. A receiving chamber is filled with 80 ml of deionized water. The cables of a conductivity meter are immersed in the deionized water of the recipient chamber, and an agitator bar is added in the recipient chamber. The receiving chamber is placed in a water bath and the temperature is maintained at around 35 ° C. Finally, the donor chamber is immersed in the recipient chamber so that the NaCl solution in the donor chamber is level with the water in the recipient chamber. Once the temperature inside the receiving chamber is balanced at 35 degrees C, conductivity measurements are taken every 2 minutes for at least 10 minutes, and sometimes, as when the values of the diffusion coefficient of l ionoflux are low, measurements are taken for a period of time of up to about 3 hours or 4 hours. The conductivity increases substantially linearly over time. The conductivity as a function of time data was used to calculate the value of the ionoflux (ionoflux diffusion coefficient) of the lenses tested.

The thickness of parts or regions of the present contact lenses can be measured using conventional techniques. For example, thickness can be measured using a Rehder Model ET-3 electronic thickness gauge or equivalent instrument for measuring thickness, including instruments that give optical measurements of contact lenses. In embodiments in which the ion-permeable part of the body of the contact lens is a hydrogel or a silicone hydrogel, it is desirable to measure the thickness in a hydrated state since the hydrogel or silicone hydrogel is likely to swell when hydrated. As used here, thickness measurements are reported without correction, which may be due to mechanical compression as when a Rehder gauge is used. In the context of the present description, an average thickness of a region of the contact lens or the average thickness of the entire contact lens is determined. The average thickness can be determined using any suitable technique which will be apparent to the ordinary skill in the art. For example, the thickness of a contact lens is measured at multiple locations on the lens body. The measured thickness values are then summed, and the sum is divided by the number of measurements taken to obtain the average thickness. For example, thickness measurements can be taken at multiple points along a straight line from one edge of the lens to the opposite edge of the lens, for example along the meridians 0 / 180 degrees or along the 90/270 degrees meridians (as shown in FIG. 3, the thickness measurement sites are illustrated by the dots in FIG. 3, some of which are shown 30). It may be desirable to measure four or more points, and possibly up to 20 separate points. In certain embodiments, the thickness measurements are made in a number of sites numbered from 4 to 200. As another example, the contact lens can be visually divided into four quadrants defined by the meridians 0 degrees, 90 degrees, 180 degrees and 270 degrees, and at least one thickness measurement is taken in each quadrant (as illustrated in FIG. 4, where the thickness measurement sites are illustrated by dots marked 30). Any suitable number of thickness measurements can be obtained as long as the person taking the measurements thinks that the average calculated from the measurements is an exact representation of the average thickness of the contact lens or average thickness of the contact lens region. In the embodiments described here, the average thickness is calculated using at least four thickness measurements. In some embodiments, at least eight thickness measurements are obtained. In other embodiments, at least twelve thickness measurements are obtained. In some embodiments, the average thickness is determined by measuring the thickness at a minimum of four locations and up to a hundred locations.

Using the diffusion coefficient of the ionoflux, as measured above, and the measurements of the average thickness, as described above, the inventors calculated the average transmittance of the ionoflux. Consequently, the average transmittance of the ionoflux of a contact lens body is understood to be the diffusion coefficient of the ionoflux of the contact lens body divided by the average thickness of the contact lens body. .

Alternatively, the average transmittance of the ionoflux from the lens body, which is composed of a number n of different components having different diffusion coefficients of the ionoflux (D _lon ) and values of d 'thickness (h) different, respectively, can be determined using Formula 1:

vn _Λ ^D ioni Ζί = 1 ^Λ ί _h .

_A ¹ (Formula 1) ^ ί = ι ^Λ ί [0037] where is the transmittance of the ionoflux (mm / min) of the z-th component, and A, “À is the transverse area of the z-th component of a plan view.

If Formula 1 is used to determine the average transmittance of the ionoflux, the transport of ions through a component of the lens body comprising multiple layers of different materials having different diffusion coefficients of the ionoflux must be considered as the diffusion through various layers arranged in series, and therefore, the coefficient of diffusion of the effective ionoflux D _ione ^ can be obtained as = Σ> ι (Formula 2) ^u ion _e ff ^u ionj where h _e ff is the total thickness of the lens body; m is the total number of layers, hj and D _ion . are the average thickness and the diffusion coefficient of the ionoflux of the j-th layer, respectively. (If the j-th layer is impermeable, D _ion j = 0, so that D _ione j, j, is also zero.) By way of example illustrating this function, a lens body can consist of a disc of silicone elastomer having a diameter of 10 mm, embedded in (for example, see FIG. 8 reference number 42) or on a surface of a lens in hydrogel or in silicone hydrogel or a disc in hydrogel or in silicone hydrogel, the disc having a diameter of 14 mm (for example, see FIG. 9 reference number 42). In this example, n = 2 because there are two components from the plan view; i = l as index of the central region of the lens body containing the silicone elastomer component; and i = 2 as an index of the hydrogel or silicone hydrogel component in the external region which circumscribes the central region. Consequently, D _lon i is the diffusion coefficient of the effective ionoflux of the central region containing the ion-elastomeric silicone elastomer component, and will therefore be zero based on Formula 2, h} is l average thickness of the central region containing the silicone elastomer component, and A; is the area of the silicone elastomer component seen in plan, which is 78.54 mm ² in this example. Similarly, D _lon2 is the diffusion coefficient of the ionoflux of the hydrogel or silicone hydrogel component, h ₂ is the thickness of the hydrogel or silicone hydrogel component in the external region, and A ₂ is the area of the hydrogel or silicone hydrogel component in the plan view external region, which is 75.40 mm ² in this example. If there are 3 layers in the central region (i.e., a posterior hydrogel or silicone hydrogel layer, a silicone elastomer disc and an anterior hydrogel or silicone hydrogel layer, as shown in FIG. 8), m = 3 in Formula 2 for the central region. Likewise, using the embodiment of FIG. 8, the external region has 2 layers which are either a hydrogel material or a silicone hydrogel material, and therefore, m = 2 in formula 2 for the external region.

The relationship between the Tionoflux diffusion coefficient and the average thickness of the present contact lenses is illustrated in the graph of FIG. 5. The straight line 100 represents the mean minimum transmittance of Tionoflux of the present contact lenses, which is 1.34 x 10 ' ⁴ mm / min. The hatched region 101 represents the average Tionoflux transmittance values for the contact lenses according to the present invention. In other words, provided that the lens body comprises an ion-impermeable part and an ion-permeable part, and that the average transmittance of Tionoflux is at least 1.34 × 10 ⁴ mm / min, the contact lens will demonstrate clinically acceptable eye movement without binding to the eye. An embodiment of a contact lens having an average thickness of 50 micrometers is illustrated in 102. Another embodiment of a contact lens having an average thickness greater than 200 micrometers is illustrated in 104. The average thickness of the present contact lenses described is typically less than 1000 micrometers. In some embodiments, the average thickness is less than 800 micrometers. In other embodiments, the average thickness is less than 600 micrometers. For example, the average thickness of any of the embodiments of the contact lenses described herein can be from 50 to 1000 micrometers. As another example, the average thickness of any of the embodiments of the contact lenses described herein can be from 50 to 800 micrometers. As another example, the average thickness of any of the embodiments of the contact lenses described herein can be from 50 to 600 micrometers. As another example, the average thickness of any of the embodiments of the contact lenses described herein can be from 200 to 1000 micrometers. As another example, the average thickness of any of the embodiments of the contact lenses described herein can be from 200 to 800 microns. As another example, the average thickness of any of the embodiments of the contact lenses described herein can be from 200 to 600 micrometers.

Consequently, one embodiment of the present contact lenses is a contact lens which comprises a lens body. The lens body includes an ion impermeable portion and an ion permeable portion. And, the lens body has an average transmittance of Tionoflux of at least 1.34 x 10 ⁴ mm / min. As mentioned above, the average transmittance of Tionoflux can be calculated by determining the diffusion coefficient of the ionoflux from the contact lens, and dividing this value by the average thickness of the contact lens.

By way of example, such a contact lens is illustrated in FIG. 6. The contact lens 10 comprises a lens body 12, which comprises an ion-impermeable part 42 and an ion-permeable part 40. In this contact lens, the lens body has an average ion-flux transmittance. at least 1.34X10 ' ⁴ mm / min.

As used herein, the lens body of the contact lens refers to the lens which is placed on a person's tear film. Accordingly, the lens body can be understood to have an anterior surface and a posterior surface which is formed to be placed on the cornea of the eye, as described in FIG. 2. The anterior surface is typically and generally convex in shape, and the posterior surface is typically and generally concave in shape. The anterior and posterior surfaces meet at the edge of the lens. The edge of the lens can be understood as the radially outermost point of the body of the contact lens from the geometric center of the lens body. The edge of the lens circumscribes the body of the lens.

In another embodiment, the ion permeable part is in a region of the lens body which extends over at least 1.1 mm from the edge of the lens to the geometric center of the lens body. For example, as illustrated in FIG. 6, the ion-permeable portion 40 is illustrated at a location extending inwardly from the edge of the lens 20 radially to the geometric center 18. The dotted line 21 is provided to illustrate a distance of at least 1.1 mm (for a contact lens having a diameter of at least 14.2 mm. The width "w" of the ion-permeable part 40 is illustrated as extending from the lord of the lens 20 to at the dotted line 21. In other words, it can be seen that in this embodiment, the ion-permeable part is provided as a ring extending from the edge of the lens towards the center of the body of the lens and having a radial width of at least 1.1 mm. In some embodiments, the radial width of the ion-permeable portion is from 1.1 mm to 4.6 mm. In other embodiments, the width radial of the ion-permeable part is from 1.1 mm to 3.5 mm. In these embodiments, the ion-permeable part can also be provided in other regions of the lens body, but at a minimum, it is present in the form of a 1.1 mm ring around the body of the lens. lens. For example, the ion permeable portion may also form the posterior surface of the lens body, the anterior surface of the lens body, or fractions thereof. As discussed here, the ion permeable part, such as a hydrogel or silicone hydrogel, can be provided as a backing layer, and the ion impermeable part, such as a silicone elastomer, can be provided as an anterior layer in contact with the posterior layer. Alternatively, the ion permeable part, such as a hydrogel or silicone hydrogel material, can be provided as a front layer, and the ion impermeable part, such as a material The silicone elastomer can be provided as a posterior layer in contact with the anterior layer. In addition, the ion permeable part and / or the ion impermeable part may consist of non-contiguous regions. For example, the ion permeable part can be integrated between ion impermeable components of the ion impermeable part which can be included in the ion permeable part. For example, a hydrogel or silicone hydrogel material can be provided between two electronic components which are included in the hydrogel or silicone hydrogel material. Furthermore, the ring of the ion-permeable part 40 may have a width "w" which is at least 1.1 mm. For example, the width "w" can have a value of 1.1 mm to 3.2 mm. In some embodiments, the radial width of the ion-permeable portion is from 1.1 mm to 4.6 mm. In other embodiments, the radial width of the ion-permeable part is

1.1 mm to 3.5 mm.

In a further embodiment of the contact lenses which have an average transmittance of the ionoflux of at least 1.34 × 10 ^-4 mm / min, the body of the lens has an average thickness and a diffusion coefficient of the ionoflux, as determined using the method described here, wherein the average thickness of the lens body is at least fifty micrometers and the diffusion coefficient of the ionoflux is at least 6.7xl0 ' ⁶ mm ² / min. An example of such a contact lens is illustrated at 102 in FIG. 5. In certain embodiments of these contact lenses, the diffusion coefficient of the ionoflux is from 6.7 × 10 ⁶ mm ² / min to 9.0 × 10 ² mm ² / min. In other embodiments, the diffusion coefficient of the ionoflux is from 6.7 × 10 ' ⁶ mm ² / min to 8.9 × 10' ² mm ² / min.

In another embodiment of the contact lenses, a contact lens includes a lens body which includes an ion impermeable portion and an ion permeable portion, and the lens body has an average thickness of at least minus 50 micrometers, and a calculated ionoflux diffusion coefficient of at least 6.7xl0 ' ⁶ mm ² / min, and the ion-permeable part extends radially inward from a lens edge defining the body lens at a distance of at least 7% of an annular diameter from the lens body. For example, in some embodiments, the ion permeable portion may extend radially inward from the edge of the lens over a distance which is between 7% and 35% of the annular diameter of the lens body. In other embodiments, the radial distance can be from 7% to 25% of the annular diameter of the lens body. As described herein, this embodiment of the contact lens can be worn on one eye for at least 6 hours (for example, 6 hours to 24 hours) without binding to the eye. For example, the contact lens, when worn for a 6 hour study, exhibits clinically acceptable eye movement, as shown by eye movement from 0.1 mm / second to 4 mm / second. In certain embodiments of these contact lenses, the diffusion coefficient of the ionoflux is from 6.7 × 10 ⁶ mm ² / min to 9.0 × 10 ² mm ² / min. In other embodiments, the diffusion coefficient of the ionoflux is from 6.7 × 10 ⁶ mm ² / min to 8.9 × 10 ² mm ² / min.

As will be readily understood by the ordinary specialist in the art, typically, the contact lenses are illustrated by a plan view (as illustrated in the appended figures) and the diameter of the contact lens corresponds to the annular diameter. The annular diameter of the present contact lenses can range from 12 mm to 17 mm. In certain embodiments, the annular diameter of the present contact lenses ranges from 13.5 mm to 14.5 mm. For example, the annular diameter of the present contact lenses can be about 14.0 mm, 14.1 mm, 14.2 mm, 14.3 mm and the like. In these embodiments, if a contact lens has an annular diameter of 12.0 mm, the ion-permeable portion extends from the edge of the lens by at least 0.84 mm. Likewise, if a contact lens body has an annular diameter of 15 mm the ion-permeable part extends from the edge of the lens by at least 1.05 mm.

In another embodiment, the ion-permeable part of the lens body extends over at least 1.1 mm from the edge of the lens towards its geometric center. It has been found that when contact lenses are fabricated to have an ion permeable portion which extends at least 1.1mm from the edge of the lens to its geometric center, it is possible to maintain an average transmittance of the ionoflux of at least 1.34xl0 ' ⁴ mm / min, and to prevent the contact lens from binding to a person's eye (i.e., the contact lens manifests movement on the eye clinically acceptable). In some embodiments, the radial width of the ion-permeable portion is from 1.1 mm to 4.6 mm. In other embodiments, the radial width of the ion-permeable portion is from 1.1 mm to 3.5 mm.

As mentioned above, in some embodiments, including the illustrated embodiments, the ion-permeable part defines a ring having an outer edge radially defined by the edge of the lens of the lens body .

In any of the foregoing embodiments, the ion impermeable portion may constitute less than 75% of the area of the lens body when viewed in plan. Therefore, it will be understood that the ion impermeable part may have an area which is from 1% to 74% of the area of the lens body when viewed in plan. In some embodiments, the ion-impermeable portion does not constitute more than 70% of the area of the lens body. In other words, the ion-impermeable part occupies 70% or less of the body area of the lens. For example, the ion impermeable part may have an area which is 1% to 70% of the area of the lens body. It has been found that by controlling the size and shape of the ion impermeable part to be confined to a region which is less than 75% of the area of the lens body, for example 70% or less, it is possible to maintain the desired average transmittance of the ionoflux to obtain clinically acceptable eye movement.

In any of the previous embodiments, and as referred to herein, the ion impermeable portion may include at least one electronic component. As used herein, an "electronic component" refers to one or more devices that control or direct an electric current. These electronic components can be used to cause a change in the contact lens, for example a change in the refractive power of the contact lens, or a change in the visual image provided by the contact lens, among other things. In some embodiments, the at least one electronic component can be at least one electrode, at least one power supply, at least one sensor or at least one transmitter, or combinations thereof.

In any of the previous embodiments, the lens body can include an optical area which includes electronically adjustable optics. The optical zone of the contact lens corresponds to the region of the contact lens that covers the pupil of an eye when the contact lens is located on the eye. Typically, the geometric center of the optical zone is the same as the geometric center of the body of the contact lens. The optical zone can have a diameter of about 5 mm to about 9 mm. In some embodiments, the optical area has a diameter of 5 mm to 8.5 mm long. Thus, in these embodiments, an electronically adjustable optic can be provided in the optical zone, and can modify the refractive power on the basis of an electrical activity supplied to the electronically adjustable optic. In some embodiments, the electronically adjustable optics include a liquid crystal component. In such an embodiment, the liquid crystal optic may be located between an anterior ion permeable component and a posterior ion permeable component, as illustrated in FIG. 8, and described below. In other embodiments, the electronically adjustable optics include a fluid filled membrane component. In such an embodiment, the fluid-filled membrane optic may be located on an anterior surface of a posterior ion-permeable component, as shown in FIG. 9, and described below. In these embodiments, it is possible to pass an electric current through the liquid crystal component or the component filled with fluid membrane and cause the variation of the refractive power of the optics and its change from a first refractive power to a second different refractive power. An example of a contact lens 10 comprising a lens body which includes an ion impermeable part 42 and an ion permeable part 40, in which the ion impermeable part 42 comprises one or more electronic components 50, is illustrated in FIG. 7. In this embodiment, the electronic components 50 include an electronically adjustable optic 52, one or more electrodes 54, at least one power supply 56, at least one sensor 58 and at least one transmitter 60. Some embodiments may have fewer than five electronic components, if desired.

Any of the electronic components 50 of these contact lenses can be coated with an ion permeable material or an ion impermeable material, if desired. For example, one or more of the electronic components may be coated with a parylene material or an ion-impermeable material, including optionally, a silicone elastomeric material, or a material to facilitate attachment between the electronic component and the lens body. The coatings can be of any suitable thickness, provided that the relationship between the ion-impermeable part of the lens body and the ion-permeable part of the lens body is maintained in accordance with the present description.

As discussed here, in any of the present embodiments, the lens body may include a hydrogel component, a silicone hydrogel component, or a silicone elastomer component, or combinations thereof. that the hydrogel component or the silicone hydrogel component forms the ion-permeable part of the body of the contact lens, and that the silicone elastomer component forms the ion-impermeable part of the body of the contact lens. The silicone elastomer component and the electronic component or electronic components can also form the ion-impermeable part of the body of the contact lens.

In any of the previous embodiments, the ion impermeable portion may have a substantially circular shape when viewed in plan, and it may have a diameter of 12 mm or less. For example, the diameter of the ion-impermeable part can be from 5 mm to 12 mm. In some embodiments, the diameter of the ion impermeable portion can be from 7 mm to 12 mm. This would include an ion impermeable part in the shape of a circular or hemispherical disc, and which has a diameter of not more than 12 mm, or it could include an annular electrode component which has an external diameter of not more than 12 mm, and a or several additional components which are located radially inwards relative to the annular electrode.

In view of the present description, it will be appreciated that another embodiment of the present contact lenses can be understood to include a lens body which comprises a part impermeable to ions and a part permeable to ions, the impermeable part ion ion includes electronically adjustable optics which provide a first refractive power without energy, and adjusts to a second refractive power by receiving energy, and at least one additional electronic component to supply energy to the optics electronically adjustable, and the ion-permeable part comprises a polymeric hydrogel material or a polymeric silicone hydrogel material, and the ion-permeable part is present in the form of a ring extending radially inwards from an edge of the lens defining the lens body by a distance which is at least 7% of an annular diameter of the lens lens orps. In some embodiments, the ion-permeable portion may extend radially inward from the edge of the lens over a distance that is between 7% and 35% of the annular diameter of the lens body. In other embodiments, the radial distance can be from 7% to 25% of the annular diameter of the lens body.

In this embodiment, the electronically adjustable optics comprises a liquid crystal component or a membrane filled component with fluid. In addition, or according to another possibility, the ring of the ion-permeable part may have a radial width of at least 1.1 mm from the edge of the lens. In certain embodiments, the radial width of the ion-permeable part is from 1.1 mm to 4.6 mm. In other embodiments, the radial width of the ion-permeable portion is from 1.1 mm to 3.5 mm. In addition, any of these embodiments can have an average transmittance of Tionoflux of at least 1.34 × 10 ⁴ mm / min. And, in any of these embodiments, the ion impermeable portion may also include a silicone elastomeric material.

In any of the foregoing embodiments, the lens body includes an ion impermeable portion, and an ion permeable portion, and the lens body has a thickness of at least 200 micrometers, and a Tionoflux diffusion coefficient of at least 2.68x10 ' ⁵ mm ² / min. For example, the diffusion coefficient of ionoflux is 2.68 x 10 ' ⁵ mm ² / min to 9.0 x 10' ² mm ² / min, or the diffusion coefficient of Tionoflux is 2.68 x 10 ' ⁵ mm ² / min at 8.9x10 ' ² mm ² / min.

In some additional embodiments, the lens body includes an ion impermeable portion, and an ion permeable portion, and the lens body has a thickness of at least 201 micrometers, and a diffusion coefficient ionoflux of at least 2,693xl0 ' ⁵ mm ² / min. As an example, see 104 in FIG. 5. For example, the diffusion coefficient of the ionoflux is 2,693xl0 ' ⁵ mm ² / min to 9.0xl0' ² mm ² / min, or the diffusion coefficient of the ionoflux is 2,693xl0 ' ⁵ mm ² / min at 8.9 x 10 ' ² mm ² / min.

In other embodiments of the present contact lenses, the contact lenses comprising the ion impermeable part and an ion permeable part have a central thickness greater than 200 micrometers.

As mentioned here, any of the present embodiments may include a lens body which manifests movement on the eye from 0.1mm / second to 4.0mm / second.

According to another aspect of the present invention, methods of manufacturing the contact lenses described here are provided. The methods include a step of forming a lens body from at least one lens material, wherein the lens body includes an ion impermeable portion and an ion permeable portion. The resulting lens body exhibits any of the characteristics of the contact lenses described herein. For example, in some embodiments, the lens body has an average ionoflux transmittance of at least 1.34 x 10 ⁴ mm / min. In other embodiments, the lens body has an average thickness of at least 50 micrometers, a diffusion coefficient of the ionoflux of at least 6.7 x 10 ⁶ mm ² / min, and the permeable part ions extend radially inward from a lens edge defining the lens body at a distance which is at least 7% of an annular diameter of the lens body. For example, in some embodiments, the ion permeable portion may extend radially inward from the edge of the lens over a distance which is between 7% and 35% of the annular diameter of the lens body. In other embodiments, the radial distance can be from 7% to 25% of the annular diameter of the lens body. In certain embodiments of these contact lenses, the diffusion coefficient of the ionoflux is from 6.7 × 10 ⁻⁶ mm ² / min to 9.0 × 10 ⁻² mm ² / min. In other embodiments, the diffusion coefficient of the ionoflux is from 6.7 × 10 ⁶ mm ² / min to 8.9 × 10 ² mm ² / min. In still other embodiments, the ion impermeable part includes an electronically adjustable optic which provides a first refractive power without energy, and adjusts to a second refractive power by receiving energy, and at least one additional electronic component for supplying power to the electronically adjustable optics, and the ion permeable part comprises a polymer hydrogel material or a polymeric silicone hydrogel material, and the ion permeable part is present as an extending ring radially inwards from an edge of the lens delimiting the body of the lens by a distance which is at least 7% of an annular diameter of the lens body. In some embodiments, the ion permeable portion may extend radially inward from the edge of the lens over a distance which is between 7% and 35% of the annular diameter of the lens body. In other embodiments, the radial distance can be from 7% to 25% of the annular diameter of the lens body.

For example, the lens bodies of the present contact lenses can be formed by casting molding methods, centrifugal molding methods, or machining methods, or a combination thereof. As will be appreciated by those skilled in the art, casting molding refers to the molding of a contact lens by placing lens material between a female member of the mold having a concave surface forming a lens and a male member of the mold having a surface convex lens. In addition, the formation of the lens bodies may include the coupling of two molded elements by casting. One of the two casting components is a polymeric hydrogel material or a polymeric silicone hydrogel material, and the other casting component is a polymeric hydrogel material or a polymeric silicone hydrogel material, or even a material made of silicone elastomer. Coupling can be achieved by using an adhesive, or by curing the components with each other, and the like. The lens body can even receive a surface treatment, if desired, provided that the surface treatment material does not decrease by the diffusion coefficient of the ionoflux or the average transmittance of the ionoflux to below threshold values described here.

After the lens material, which includes the ion-permeable material and the ion-impermeable materials or components, is placed in contact with a mold assembly for contact lens formed from male and female mold members, the contact lens is polymerized to form the lens body. The lens body can then be removed from the mold assembly, and optionally washed with or without organic solvents, water, or combinations thereof, and packaged in a contact lens package. The contact lens package is then sealed and sterilized using conventional techniques.

In certain embodiments, the lens body comprises a posterior member which is formed of a polymer material in hydrogel or in silicone hydrogel and of an anterior member which is formed of a polymer material in hydrogel or in silicone hydrogel. A silicone elastomer member, or one or more electronic components, or a combination thereof, may be placed on a posterior surface of the forelimb, and the anterior surface of the hind limb may be placed in contact with the anterior member for sandwich the silicone elastomer member, or the electronic components, or both, between the anterior member and the posterior member. The resulting sandwich assembly can be understood to be a lens body in the context of this description.

An example of such a lens body is illustrated in FIG. 8. A contact lens 10 includes a lens body 12 as described herein. The lens body 12 comprises an ion-impermeable part 42 and an ion-permeable part 40. The annular diameter of the lens body 12 is marked D _C h _O rdi, and the annular diameter of the impermeable part 42 is marked D _C h _O rd2- The thickness of the anterior component permeable to ions 40 is marked “hl”, the thickness of the posterior component permeable to ions 40 is marked “h3”, and the thickness of the component impermeable to ions 42 is marked “h2” . In this embodiment the ion impermeable part is trapped between the anterior and posterior ion permeable components.

In another example, as illustrated in FIG. 9, an ion-impermeable part 42 may be provided on a surface (in this case, the anterior surface) of the ion-permeable part 40. The combination of the ion-impermeable part 42 and the ion-permeable part 40 define the lens body 12 of the contact lens 10.

In the embodiment illustrated in FIG. 8, the ion-impermeable part 42 can be an electronically adjustable optic, such as a liquid crystal optic. In the embodiment illustrated in FIG. 9, the ion-impermeable part 42 can be an electronically adjustable optic, such as a fluid-filled membrane optic. For example, an optical membrane may include two elastic or deformable membranes, at least one of which is made of a silicone elastomer material, and an optically transparent fluid may be present between the membranes. In this example, the posterior membrane will be adjacent to the anterior surface of the ion permeable portion.

Alternatively, the ion impermeable components can be placed in the cavity of a female mold member, and the ion permeable material can be placed in the cavity so as to surround the ion impermeable components and the trap in the lens body after the lens body has been hardened or polymerized.

The present contact lenses show movement on the clinically acceptable eye, and have not shown any connection to a person's eye. The clinically acceptable eye movement of the present contact lenses can be determined by slit lamp examination using a standard slip test. In one example, a contact lens can be pushed by a person's finger of about 1-5 mm and it has a rate of recovery of the push from 0.1 mm / s to 4 mm / s, as determined using the method described by Wolfssohn et al. (Cont. Lens Anterior Eye. (2009) 32: 37-42). This recovery speed after the push can be understood as a speed of movement over the eye, as used here. Accordingly, the present contact lenses can be used by placing them on one eye and evaluating movement on the eye for a period of time such as multiple periods of time, for example, once an hour for about six hours. . When the present contact lenses include an electronically adjustable optic. Contact lenses can be used to correct the vision of contact lens wearers who may benefit from having multiple refractive powers. For example, the present contact lenses can be useful in correcting presbyopia by providing basic refractive power, and when electronically adjustable optics are activated, and the refractive power can then change and become relatively more positive to facilitate intermediate or near view. The optics can then be turned off to return to basic refractive power.

Examples [0074] Examples of contact lenses according to the present invention are described below. Contact lenses have been tested on the eyes of subjects for up to and including 6 hours. Contact lenses were assessed for movement over the eye using the slip test as described here. For the purposes of these experiments, the contact lenses consisted of a combination of a silicone elastomer component and a hydrogel component or a silicone hydrogel component. The silicone elastomer component has been provided as an example of the ion impermeable part of the contact lens, and the hydrogel component or the silicone hydrogel component has been provided as an example of the ion permeable part of the contact lens. contact lens. The hydrogel or silicone hydrogel component has been provided as a posterior component, so that the posterior surface of the hydrogel or silicone hydrogel component is in contact with the surface of the eye. A silicone elastomer component was located on the anterior surface of the posterior component. In some examples, an additional silicone hydrogel or hydrogel component was located in front of (i.e., over) the silicone elastomer component (for example, the silicone elastomer component was embedded between the front components and posterior, which are hydrogel materials or silicone hydrogel materials). The silicone elastomer component had no detectable Tionoflux diffusion coefficient (i.e., it was impermeable to ions, in the sense used here), and is identified as having a Tionoflux diffusion coefficient of 0.

Example 1:

A contact lens was formed consisting of a posterior component permeable to ions and a front component impermeable to ions. The rear component was a silicone hydrogel, and the front component was a silicone elastomer. The anterior silicone elastomer component had an annular diameter of 14.2 mm; and the posterior silicone hydrogel component had an annular diameter of 14.2 mm. The average thickness of the contact lens was approximately 470 micrometers. The diffusion coefficient of Tionoflux was 0 for the anterior component in silicone elastomer and 5034 × 10 ⁶ mm ² / min for the posterior component in silicone hydrogel. The average transmittance of Tionoflux was determined to be 0 mm / min. The relative area of the contact lens with an ion flux of 0 was 100% (the area of the anterior component impermeable to ions was equal to the area of the posterior component permeable to ions, when viewed in plan). This contact lens bonded to the eye, and showed no movement on the eye after being worn for 6 hours.

Example 2:

A contact lens was formed, consisting of an ion permeable posterior component, an ion permeable front component and an ion impermeable component located between the anterior component and the posterior component (i.e., the ion impermeable component was trapped between the anterior ion permeable component and the posterior ion permeable component (see FIG. 8 for an example). The posterior component was a hydrogel, the anterior component was a silicone hydrogel, and the ion impermeable component was a silicone elastomer. The silicone elastomer component had an annular diameter of 7.8 mm; the posterior hydrogel component had an annular diameter of 14.2 mm; and the anterior silicone hydrogel component had an annular diameter of 14.2 mm. The average thickness of the contact lens in the outer region (identified by reference number 40) was 635 micrometers and the average thickness of the central region (identified by reference number 42) was 988 micrometers. The diffusion coefficient of the ionoflux was 0 for the silicone elastomer component, 7500xl0 ' ⁶ mm ² / min for the posterior hydrogel component, and 47xl0' ⁶ mm ² / min for the anterior hydrogel component silicone. The average transmittance of the ionoflux was determined to be 1.81 × 10 ⁴ mm / min. The relative area of the contact lens with an ion-flux of 0 was 30.2% (the area of the ion-impermeable component was less than the area of the ion-permeable component (i.e. the combination of the anterior and posterior component) ), when viewed in plan). This contact lens did not bind to the eye, and showed clinically acceptable eye movement after being worn for 6 hours.

Example 3:

A contact lens was formed, consisting of an ion permeable posterior component, an ion permeable front component and an ion impermeable component located between the anterior component and the posterior component (i.e., the ion impermeable component was trapped between the anterior ion permeable component and the posterior ion permeable component). The posterior component was a hydrogel, the anterior component was a silicone hydrogel, and the ion impermeable component was a silicone elastomer. The silicone elastomer component had an annular diameter of 10 mm; the posterior hydrogel component had an annular diameter of 14.2 mm; and the anterior silicone hydrogel component had an annular diameter of 14.2 mm. The average thickness of the contact lens in the outer region (identified by reference number 40 in FIG. 8 for example) was 635 micrometers and in the central region 988 micrometers (reference number 42 in FIG. 8 for example). The diffusion coefficient of the ionoflux was 0 for the silicone elastomer component, 7500xl0 ' ⁶ mm ² / min for the posterior hydrogel component, and 47x10' ⁶ mm ² / min for the anterior hydrogel component silicone. The average transmittance of the ionoflux was determined to be 1.34 × 10 ⁴ mm / min. The relative area of the contact lens with an ion-flux of 0 was 49.6% (the area of the ion-impermeable component was less than the area of the ion-permeable component (i.e. the combination of the anterior and posterior component) ), when viewed in plan). This contact lens did not bind to the eye, and showed clinically acceptable eye movement after being worn for 6 hours.

Example 4:

A contact lens was formed, consisting of an ion permeable posterior component, an ion permeable front component and an ion impermeable component located between the anterior component and the posterior component (i.e., the ion impermeable component was trapped between the anterior ion permeable component and the posterior ion permeable component). The posterior component was a hydrogel, the anterior component was a hydrogel, and the ion impermeable component was a silicone elastomer. The silicone elastomer component had an annular diameter of 12.0 mm; the posterior hydrogel component had an annular diameter of 14.2 mm; and the anterior hydrogel component had an annular diameter of 14.2 mm. The average thickness of the contact lens in the outer region (identified by reference numeral 40 in FIG. 8 for example) was 646 micrometers and in the central region 988 micrometers (reference number 42 in FIG. 8 for example). The diffusion coefficient of the ionoflux was 0 for the silicone elastomer component, 7500xl0 ' ⁶ mm ² / min for the posterior hydrogel component, and 15370xl0' ⁶ mm ² / min for the anterior hydrogel component. The average transmittance of the ionoflux was determined to be 3.92 × 10 ³ mm / min. The relative area of the contact lens with an ion-flux of 0 was 71.4% (the area of the ion-impermeable component was less than the area of the ion-permeable component (i.e. the combination of the anterior and posterior component) ), when viewed in plan). This contact lens did not bind to the eye, and showed clinically acceptable eye movement after being worn for 6 hours.

Additional aspects of the present invention are presented below. The contact lens according to the invention comprises a lens body which comprises an ion impermeable part and an ion permeable part, the lens body having an average transmittance of the ionoflux of at least 1.34 × 10 '. ⁴ mm / min.

The lens body of the previous contact lens further comprises an anterior surface, a posterior surface formed to be placed on a cornea of an eye, a lens edge which circumscribes the lens body, and leave it permeable. ion is present in a region of the lens body extending at least 1.1 mm from the edge of the lens to the geometric center of the lens body.

The lens body of one of the preceding contact lenses has an average thickness and a diffusion coefficient of the ionoflux, the average thickness being at least 50 micrometers and the diffusion coefficient of the ionoflux at least 6.7xl0 ' ⁶ mm ² / min.

The contact lens according to the invention comprises a lens body which comprises an ion impermeable part and an ion permeable part, and the lens body has an average thickness of at least 50 micrometers, and a coefficient diffusing the ionoflux by at least 6.7 x 10 ' ⁶ mm ² / min, and the ion-permeable part extends radially inwards from an edge of the lens delimiting the lens body at a distance of at least 7% of a lens body diameter, in which the lens body can be worn for at least six hours without binding to the eye.

In the previous contact lens, the ion-permeable part extends over at least 1.1 mm from the edge of the lens towards the geometric center.

In one of the previous contact lenses, the ion-permeable part defines a ring having an outer edge radially defined by the edge of the lens of the body of the lens.

In one of the previous contact lenses, the ion-impermeable part constitutes less than 75% of the surface area of the lens body when it is viewed in plan.

In the previous contact lens, the ion-impermeable part does not constitute more than 70% of the surface area of the lens body.

In one of the previous contact lenses, the ion-impermeable part comprises at least one electronic component.

In the previous contact lens, the at least one electronic component comprises at least one electrode, at least one power supply, at least one sensor or at least one transmitter, or combinations thereof.

In one of the previous contact lenses, the lens body includes an optical zone which includes an electronically adjustable optic.

In the previous contact lens, the electronically adjustable optics comprises a liquid crystal component or a component filled with a fluid membrane.

In one of the preceding contact lenses, the lens body can comprise a hydrogel component, a silicone hydrogel component, or a silicone elastomer component, or combinations thereof.

In one of the previous contact lenses, the ion impermeable part has a substantially circular shape when viewed in plan, and the ion impermeable part has a diameter of not more than 12 mm.

The contact lens according to the invention comprises a lens body which comprises an ion impermeable part and an ion permeable part, in which the ion impermeable part comprises an electronically adjustable optic which provides a first refractive power without energy, and adjusts to a second different refractive power by receiving energy, and at least one additional electronic component for supplying energy to the electronically adjustable optics, and in which the ion-permeable part comprises a material hydrogel polymer or a silicone hydrogel polymeric material, and the ion-permeable part is present in the form of a ring which extends radially inwards from a lens edge delimiting the lens body at a distance of at least 7% of an annular diameter of the lens body. In the previous contact lens, the electronically adjustable optics comprises a liquid crystal component or a component filled with a fluid membrane.

In one of the previous contact lenses, the ion-permeable part has a radial width of at least 1.1 mm from the edge of the lens.

In one of the preceding contact lenses, the lens body has an average transmittance of the ionoflux of at least 1.34 × 10 ^-4 mm / min.

In one of the previous contact lenses, the ion-impermeable part further comprises a silicone elastomer material.

The contact lens according to the invention comprises a lens body which comprises an ion-impermeable part and an ion-permeable part, the lens body having a thickness of at least 200 micrometers, and a diffusion coefficient ionoflux of at least 2.68 x 10 ' ⁵ mm ² / min.

In the previous contact lens, the lens body manifests a speed of movement on the eye from 0.1 mm / second to 4.0 mm / second.

In one of the previous contact lenses, the lens body has an average transmittance of the ionoflux of at least 1.34 × 10 ^-4 mm / min.

In one of the preceding contact lenses, the lens body also comprises an anterior surface, a posterior surface formed to be placed on a cornea of an eye, a lens edge which circumscribes the lens body, and the ion-permeable part is present in a region of the lens body extending at least 1.1 mm from the edge of the lens to the geometric center of the lens body.

In one of the previous contact lenses, the ion-impermeable part does not constitute more than 70% of the surface area of the lens body when it is viewed in plan.

In one of the previous contact lenses, the ion-impermeable part comprises at least one electronic component.

In the previous contact lens, the at least one electronic component comprises at least one electrode, at least one power supply, at least one sensor or at least one transmitter, or combinations thereof.

In one of the previous contact lenses, the lens body includes an optical zone which includes an electronically adjustable optic.

In the previous contact lens, the electronically adjustable optics comprises a liquid crystal component or a fluid filled membrane component.

In one of the preceding contact lenses, the body of the lens may comprise a hydrogel component, a silicone hydrogel component, or a silicone elastomer component, or combinations thereof.

The method of manufacturing a contact lens according to the invention comprises the formation of a lens body from a lens-forming material, the lens body comprising a part impermeable to ions and a part permeable to ions, the lens body having an average transmittance of the ionoflux of at least 1.34 × 10 ^-4 mm / min.

The method of manufacturing a contact lens according to the invention comprises the formation of a lens body from a lens-forming material, the lens body comprising a part impermeable to ions and a part permeable to ions, and the lens body has an average thickness of at least 50 micrometers, and a calculated ionoflux diffusion coefficient of at least 6.7xl0 ' ⁶ mm ² / min, and the part permeable to ions s 'extends radially inward from a lens edge defining the lens body at a distance of at least 7% of an annular diameter of the lens body.

The method of manufacturing a contact lens according to the invention comprises the formation of a lens body from at least one lens-forming material, the lens body comprising an ion-impermeable part and a part ion permeable, in which the ion impermeable part includes an electronically adjustable optic which provides a first refractive power without energy, and adjusts to a second different refractive power by receiving energy, and at least one electronic component additional for supplying energy to the electronically adjustable optics, and wherein the ion permeable part comprises a polymeric hydrogel material or a polymeric silicone hydrogel material, and the ion permeable part is present in the form of a ring which extends radially inward from a lens edge defining the lens body at a distance of at least 7 % of an annular diameter of the lens body.

The method of manufacturing a contact lens according to the invention comprises the formation of a lens body from a lens-forming material, the lens body comprises a part impermeable to ions, and a permeable part to ions, the lens body having a thickness of at least 200 micrometers, and a diffusion coefficient of the ionoflux of at least 2.68x10 ' ⁵ mm ² / min.

In one of the preceding contact lenses, the lens body has an average thickness of at least 200 micrometers, and an average transmittance of the ionoflux of at least 2.68 × 10 ⁵ mm ² / min.

The contact lens of clause 34, in which the lens body exhibits a speed of movement over the eye from 0.1 mm / second to 4.0 mm / second.

Although the present description refers to certain exemplified embodiments, it should be understood that these embodiments are presented by way of example and not to limit the present invention. The intent of the foregoing detailed description, while discussing exemplary embodiments, should be interpreted as covering all modifications, alternatives and equivalents of the embodiments which may fall within the spirit and scope of the invention as defined by the claims.

Claims (31)

1. A contact lens (10), comprising: a lens body (12) which comprises an ion-impermeable part (42) and an ion-permeable part (40), the lens body having an average ionoflux transmittance of at least 1.34 × 10 ⁴ mm / min. 2. The contact lens of claim 1, wherein the lens body has an ionoflux transmittance of from about 1.34 x 10 ⁴ mm / min to about 1.50 x 10 ^_1 mm / min. 3. The contact lens according to one of the preceding claims, in which the lens body has an average thickness and a diffusion coefficient of the ionoflux, the average thickness being at least 50 micrometers and the diffusion coefficient ionoflux of at least 6.7xl0 ' ⁶ mm ² / min. 4. The contact lens according to one of the preceding claims, wherein the lens body further comprises an anterior surface (22), a posterior surface (24) formed to be placed on a cornea of an eye, an edge lens (20) which circumscribes the lens body, and the ion permeable part is present in a region of the lens body extending at least 1.1 mm from the edge of the lens to the geometric center of the body of lens. 5. The contact lens according to any one of the preceding claims, wherein the ion impermeable portion constitutes less than 75% of the area of the lens body when viewed in plan. 6. The contact lens according to any one of the preceding claims, wherein the ion-impermeable part comprises at least one electronic component (50,52,54,56,58,60). 7. The contact lens according to any one of the preceding claims, wherein the lens body comprises an optical area which includes an electronically adjustable optic (52). 8. The contact lens of claim 7, wherein the electronically adjustable optics comprises a liquid crystal component or a fluid filled membrane component. 9. The contact lens of one of the preceding claims, wherein the lens body has an average thickness of at least 200 micrometers, and an average transmittance of the ionoflux of at least 2.68 × 10 ⁵ mm ² / min. 10. The contact lens of claim 6, wherein the at least one electronic component comprises at least one electrode (54), at least one power supply (56), at least one sensor (58) or at least one transmitter ( 60), or combinations thereof. 11. The contact lens according to any one of the preceding claims, wherein the lens body may comprise a hydrogel component, a silicone hydrogel component, or a silicone elastomer component, or combinations thereof. 12. The contact lens according to any one of the preceding claims, wherein the ion impermeable part has a substantially circular shape when viewed in plan, and the ion impermeable part has a diameter of not more than 12 mm. 13. A contact lens (10), comprising: a lens body (12) which includes an ion impermeable part (42) and an ion permeable part (40), wherein the ion impermeable part includes an electronically adjustable optic (52) which provides a first refractive power without energy, and adjusts to a second different refractive power by receiving energy, and at least one additional electronic component to supply energy to the electronically adjustable optics, and in which the ion-permeable part comprises a material hydrogel polymer or a silicone hydrogel polymeric material, and the ion-permeable part is present in the form of a ring which extends radially inwards from a lens edge delimiting the lens body at a distance of at least 7% of an annular diameter of the lens body. 14. The contact lens of claim 13, wherein the electronically adjustable optics comprises a liquid crystal component or a fluid filled membrane component. 15. The contact lens of one of claims 13 or 14, wherein the ring of the ion permeable part has a radial width of at least 1.1 mm from the edge of the lens. 16. The contact lens of one of claims 13 to 15, wherein the lens body has an average transmittance of Tionoflux of at least 1.34 x 10 ⁴ mm / min. 17. The contact lens of one of claims 13 to 16, wherein the ion impermeable portion further comprises a silicone elastomer material. 18. A contact lens (10), comprising: a lens body (12) which includes an ion impermeable portion (42), and an ion permeable portion (40), the lens body having a thickness of at least 200 micrometers, and a diffusion coefficient of the ionoflux of at least 2.68xl0 ' ⁵ mm ² / min. 19. The contact lens of claim 18, wherein the lens body exhibits a speed of movement over the eye from 0.1 mm / second to 4.0 mm / second. 20. The contact lens of claim 18 or 19, wherein the lens body has an average transmittance of the ionoflux of at least 1.34 x 10 ⁴ mm / min. 21. The contact lens of one of claims 18 to 20, wherein the lens body further comprises an anterior surface (22), a posterior surface (24) formed to be placed on a cornea of an eye, a lens edge which circumscribes the lens body, and the ion-permeable part is present in a region of the lens body extending at least 1.1 mm from the edge of the lens to the geometric center of the lens body . 22. The contact lens according to any one of claims 18 to 21, wherein the ion impermeable portion does not constitute more than 70% of the area of the lens body when viewed in plan. 23. The contact lens according to any one of claims 18 to 22, wherein the ion impermeable part comprises at least one electronic component (50,52,54,56,58,60). 24. The contact lens of claim 23, wherein the at least one electronic component comprises at least one electrode (54), at least one power supply (56), at least one sensor (58) or at least one transmitter ( 60), or combinations thereof. 25. The contact lens according to any one of claims 18 to 24, wherein the lens body comprises an optical area which includes an electronically adjustable optic (52). 26. The contact lens of claim 25, wherein the electronically adjustable optics comprises a liquid crystal component or a fluid filled membrane component. 27. The contact lens according to any one of claims 18 to 26, wherein the lens body may comprise a hydrogel component, a silicone hydrogel component, or a silicone elastomer component, or combinations thereof. 28. A method of manufacturing a contact lens, comprising: forming a lens body from a lens material, the lens body comprising an ion impermeable portion and an ion permeable portion, the lens body having an average ionoflux transmittance of at least l, 34xl0 ' ⁴ mm / min. 29. A method of manufacturing a contact lens, comprising: forming a lens body from a lens material, the lens body comprising an ion impermeable portion and an ion permeable portion, and the lens body has an average thickness of at least 50 micrometers , and a diffusion coefficient of the ionoflux calculated of at least 6.7 × 10 ' ⁶ mm ² / min, and the ion-permeable part extends radially inwards from a lens edge delimiting the lens body to a distance of at least 7% of an annular diameter of the lens body. 30. A method of manufacturing a contact lens, comprising: forming a lens body from at least one lens material, the lens body comprising an ion impermeable portion and an ion permeable portion, wherein the ion impermeable portion includes an electronically adjustable optic which provides a first refractive power without energy, and adjusts to a second different refractive power by receiving energy, and at least one additional electronic component for supplying energy to the electronically adjustable optics, and in which the part ion-permeable comprises a hydrogel polymeric material or a silicone hydrogel polymeric material, and the ion-permeable part is present in the form of a ring which extends radially inwards from a lens edge delimiting the body lens at a distance of at least 7% of an annular diameter from the lens body. 31. A method of manufacturing a contact lens, comprising: forming a lens body from a lens material, the lens body comprises an ion impermeable part, and an ion permeable part, the lens body having a thickness of at least 200 micrometers, and a diffusion coefficient of the ionoflux of at least 2.68 × 10 ⁵ mm ² / min.