ES2366968T3 - PROCESS FOR MANUFACTURING MONOMERS OF SILOXANIL CATIÓNIC HYDROPHILES. - Google Patents

Abstract

A method of preparing a medical device formation monomer, removable in water, the method comprising: providing a hydride-containing siloxane compound, dissolving the hydride-containing siloxane compound in a solvent or combination of solvents; treating the hydride containing siloxane compound dissolved with an allyl halide and a conventional hydrolyzing catalyst to form a first reaction mixture; heating the first reaction mixture in a nitrogen atmosphere for a time sufficient to result in a quantitative loss of reactants, as determined by an appropriate analytical technique thereby providing a mixture of monomers; cool the monomer mixture; concentrate the cooled mixture; dissolve the cooled mixture in a suitable solvent for nucleophilic substitution; treating the cooled mixture containing the appropriate solvent for nucleophilic substitution with a tertiary amino vinyl compound, to form a second reaction mixture; heating the second reaction mixture to a temperature sufficient to promote the reaction, without causing gelefication; remove any remaining solvent to provide a material containing product; and purify the material containing the product to produce a water-removable medical device monomer.

Description

Countryside

The present invention relates to a method of preparing certain cationic monomers, capable of polymerization to form polymeric compositions having desirable physical characteristics, useful in the manufacture of ophthalmic devices. Such properties include the ability to extract medical devices polymerized with water. This avoids the use of organic solvents, as is typical in the art. The polymer compositions comprise polymerized cationic hydrophilic siloxanyl monomers, prepared by the process disclosed herein.

Background and summary

Various items, including biomedical devices, are formed from materials containing organosilicon. A class of organosilicon materials useful for biomedical devices, such as soft contact lenses, are silicon-containing hydrogel materials. A hydrogel is a crosslinked, hydrated polymer system that contains water in a steady state. Hydrogel contact lenses offer relatively high oxygen permeability, as well as desirable biocompatibility and comfort. The inclusion of a silicon-containing material in the hydrogel formulation generally provides better oxygen permeability, since silicon-based materials have greater oxygen permeability than water.

Another class of organosilicon materials are gas permeable, rigid materials, used for hard contact lenses. Such materials are generally formed of silicon or fluorosilicon copolymers. These materials are oxygen permeable, and more rigid than the materials used for soft contact lenses. Organosilicon-containing materials useful for biomedical devices, including contact lenses, are disclosed in the following United States patents: United States Patent No. 4,696,267 (Ellis et al.); U.S. Patent No. 5,034,461 (Lai et al.); and U.S. Patent No. 5,070,215 (Bambury et al.).

In addition, traditional siloxane type monomers are hydrophobic and lenses made with them frequently require additional treatment to provide a hydrophilic surface. Although not wishing to be bound by any particular theory, the inventors believe that providing a charged siloxane type monomer, such as the quaternary siloxane type monomers disclosed herein, results in a hydrophilic siloxane type monomer. It is believed that hydrophilic quaternary groups interact with the electronegative portion of the polar water molecule.

Soft contact lens materials are manufactured by polymerizing and cross-linking hydrophilic monomers, such as 2-hydroxyethyl methacrylate, N-vinyl-2-pyrrolidone and combinations thereof. The polymers produced by polymerizing these hydrophilic monomers have a significant hydrophilic character on their own, and are capable of absorbing a significant amount of water in their polymeric matrices. Because of their ability to absorb water, these polymers are often referred to as "hydrogels." These hydrogels are optically transparent and, due to their high levels of hydration water, are particularly useful materials for making soft contact lenses. It is well known that siloxane type monomers are poorly soluble in water as well as in hydrophilic solvents and monomers and, therefore, are difficult to copolymerize by processes using conventional hydrogel techniques.

The present invention provides new monomers containing cationic organosilicon, which are useful in articles such as biomedical devices, including contact lenses.

Brief description of the drawings

Figure 1 is an NMR spectrum of a monomer prepared according to Example 1.

Detailed description

In a first aspect, the invention relates to a method of preparing a water-removable medical device, which forms a monomer as defined in claim 1.

The articles can be formed from monomer mixtures that form devices, which comprise the monomers manufactured by the process described above. The article may be the polymerization product of a mixture comprising the monomers mentioned above and at least one second monomer. Preferred articles are optically transparent and useful as contact lenses.

Useful articles made of these materials may require silicon-containing monomers, possibly hydrophobic. Preferred compositions have both hydrophilic and hydrophobic monomers. The invention is applicable to a wide variety of polymeric, rigid or soft materials. Especially preferred polymeric materials are lenses, including contact lenses, phakic and aphakic intraocular lenses and corneal implants.

Especially preferred are hydrogels containing silicon.

The monomers obtained by the process of the invention can also be used to provide medical devices, such as heart valves, films, surgical devices, vessel substitutes, intrauterine devices, membranes, diaphragms, surgical implants, blood vessels, artificial ureters, artificial breast tissue and membranes intended to come into contact with the body fluid outside the body, for example membranes for kidney dialysis and heart / lung machines and the like, catheters, mouthguards and denture covers, ophthalmic devices.

Silicon containing hydrogels are prepared by polymerizing a mixture containing at least one silicon-containing monomer and at least one hydrophilic monomer. The silicon-containing monomer may function as a crosslinking agent (a crosslinker being defined as a monomer having multiple polymerizable functionalities), or a different crosslinker may be employed.

A prior example of a contact lens material containing silicon is disclosed in US Patent No. 4,153,641 (Delchert et al. Assigned to Bausch & Lomb Incorporated). The lenses are manufactured from polypeptide monomers (organosiloxane), which are α, ω terminally linked by a divalent hydrocarbon group to an unsaturated, activated and polymerized group. Various hydrophobic silicon-containing prepolymers were copolymerized, such as 1,3-bis (methacryloxyalkyl) -polysiloxanes with known hydrophilic monomers, such as 2-hydroxyethyl methacrylate (HEMA).

US Patent No. 5,365,995 (Lai et al.) Discloses a silicon-containing hydrogel which is comprised of a polysiloxane prepolymer terminated in acrylic ester, polymerized with a bulky polysiloxyanyl alkyl (meth) acrylate monomer and at least , a hydrophilic monomer. Lai et al. It is assigned to Bausch & Lomb Incorporated, and all of its description is incorporated herein by reference. The acrylic ester terminated polysiloxane prepolymer, commonly known as M2 Dx, consists of two terminal groups of acrylic ester and an "x" number of dimethylsiloxane repeating units. The bulky polysiloxanylalkyl (meth) acrylate monomers are of the TRIS (methacryloxypropyl tris (trimethylsiloxy) silane) type, containing the acrylic or vinyl hydrophilic monomers.

Other examples of the silicon-containing monomer mixtures that can be used with this invention include the following: mixtures of vinyl carbonate monomer and vinyl carbamate, as disclosed in U.S. Patent Nos. 5,070,215 and 5,610,252 ( Bambury et al.); mixtures of fluorosilicon monomer, as disclosed in US Pat. Nos. 5,321,108; 5,387,662 and 5,539,016 (Kunzler et al.); mixtures of fumarate monomers, as disclosed in US Pat. Nos. 5,374,662; 5,420,324 and 5,496,871 (Lai et al.) And mixtures of urethane monomer, as disclosed in US Pat. Nos. 5,451,651; 5,648,515; 5,639,908 and 5,594,085 (Lai et al.), All of which are assigned in common to the assignee of this document, Bausch & Lomb Incorporated, and their complete descriptions are incorporated herein by reference.

Examples of hydrophobic materials other than silicon include acrylates and alkyl methacrylates.

Cationic silicon-containing monomers can be copolymerized with a wide variety of hydrophilic monomers to produce silicon hydrogel lenses. Suitable hydrophilic monomers include: unsaturated carboxylic acids, such as methacrylic acid and acrylic; acrylic substituted alcohols, such as 2-hydroxyethyl methacrylate and 2-hydroxyethyl acrylate; vinyl lactams, such as N-vinyl pyrrolidone (NVP) and 1-vinyllazonan-2-one; and archylamides, such as methacrylamide and N, N-dimethylacrylamide (DMA).

Additional examples are the hydrophilic monomers of vinyl carbonate or vinyl carbamate, disclosed in U.S. Patent No. 5,070,215, and hydrophilic oxazolone monomers, disclosed in U.S. Patent No. 4,910,277. Other suitable hydrophilic monomers will be apparent to one skilled in the art.

Hydrophobic crosslinkers include methacrylates, such as ethylene glycol dimetracylate (EGDMA) and allyl methacrylate (AMA). In contrast to traditional silicon hydrogel monomer mixtures, monomer mixtures containing the quaternized silicon monomer obtained by the process of the invention herein are relatively water soluble. This feature provides advantages over traditional silicon hydrogel monomer mixtures in that there is less risk of phase separation incompatibility resulting in opacified lenses. Also, the polymerized materials can be extracted with water. However, when desired, traditional organic extraction methods can also be used. In addition, the removed lenses demonstrate a good combination of oxygen permeability (Dk) and low modulus, properties that are known to be important for obtaining desirable contact lenses. Water contents suitable for materials manufactured with the monomers of the invention herein will vary from 0% by weight to approximately 80% by weight. The appropriate oxygen permeability (Dk) will vary from about 10 to about 200. The suitable module will vary from about 20 g / mm2 to about 2000 g / mm2. In addition, lenses prepared with the quaternized silicon monomers obtained by the process of the invention herein can be wetted, even without surface treatment, to provide dry mold release, they do not require solvents in the monomer mixture (although solvents such may be used such as glycerol), the extracted polymerized material is not cytotoxic and the surface is lubricated to the touch. In cases where the polymerized monomer mixture, which contains the quaternized silicon monomers obtained by the process of the invention herein, does not demonstrate a desirable tear strength, reinforcing agents, such as TBE (methacrylate of 4-t-butyl-2-hydroxycyclohexyl) to the monomer mixture. Other reinforcing agents are well known to those skilled in the art and can be used when necessary.

Although an advantage of the cationic silicon-containing monomers referred to herein is that they are relatively soluble in water and also soluble in their comonomers; An organic diluent can be included in the initial monomer mixture. As used herein, the term "organic diluent" encompasses organic compounds that minimize the incompatibility of the components in the initial monomer mixture, and are substantially non-reactive with the components in the initial mixture. Additionally, the organic diluent serves to minimize the phase separation of the polymerized products produced by polymerization of the monomer mixture. Also, the organic diluent will generally be relatively non-flammable.

The organic diluents contemplated include tert-butanol (TBA); diols, such as ethylene glycol and polyols, such as glycerol. Preferably, the organic diluent is sufficiently soluble in the extraction solvent to facilitate its removal from a cured article during the extraction stage. Other suitable organic diluents will be apparent to one skilled in the art.

The organic diluent is included in an amount effective to provide the desired effect. Generally, the diluent is included as 5 to 60% by weight of the monomer mixture, with 10 to 50% by weight being especially preferred.

In accordance with the present process, the monomer mixture, which comprises at least one hydrophilic monomer, at least one cationic silicon-containing monomer and, optionally, the organic diluent, is shaped and cured by conventional methods, such as static molding or molding. by centrifugation.

Lens formation may be by free radical polymerization, such as azobisisobutyronitrile (AIBN) and peroxide catalysts using initiators and under conditions such as those set forth in US Patent No. 3,808,179, incorporated herein by reference. Photoinitiation of the polymerization of the monomer mixture is also known in the art and can be used in the process of forming an article, as disclosed herein. Dyes and the like can be added before the monomer polymerization.

Subsequently, a sufficient amount of unreacted monomer and, when present, of organic diluent, is removed from the cured article to improve the biocompatibility of the article. The release of unpolymerized monomers in the eye after the installation of a lens can cause irritation and other problems. Unlike other monomer mixtures that must be extracted with flammable solvents, such as isopropyl alcohol, due to the properties of the new quaternized siloxane monomers disclosed herein, non-flammable solvents can be used for the extraction process.

Once the biomaterials formed from the polymerized monomer mixture are formed, which contains cationic silicon-containing monomers, disclosed herein, they are then extracted to prepare them for packaging and final use. Extraction is achieved by exposing the polymerized materials to various solvents, such as water, tert-butanol, etc. for various periods of time. For example, an extraction process is to immerse the polymerized materials in water for approximately three minutes, remove the water and then immerse the polymerized materials in another aliquot of water for approximately three minutes, remove that aliquot of water and then autoclave the material. polymerized in water or buffer solution.

After extraction of unreacted monomers and any organic diluent, the shaped article, for example an RGP lens, is optionally machined by various processes known in the art. The machining stage includes lathe cutting of the surface of a lens, lathe cutting of the edge of a lens, scraping the edge of a lens or polishing the edge or surface of a lens. The present process is particularly advantageous for processes in which a lens surface is cut around, since the machining of a lens surface is especially difficult when the surface is sticky or rubbery.

Generally, said machining process is performed before the article is released from a part of the mold. After the machining operation, the lens can be released from the mold part and hydrated. Alternatively, the article can be machined after removal of the mold part and then hydrated. The

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ophthalmic monomers of the type described are prepared using the two-step synthetic procedure detailed below, such that R1 is CH3 or O (Si [CH3] 3), R2 is the same as R1 or H (Si [CH3] 2O) n, X is Cl, Br or I, R3 is CH3, a linear or branched alkyl chain, a linking group L is a linear or branched alkyl chain, ester, amide, ether, ureido, urethane, carbamate or a combination of the themselves, R4 is CH3, H or F and R5 is H or F.

image 1

Examples

Example 1.

Preparation of a general ophthalmic monomer. A hydride-containing siloxane compound is dissolved in a solvent, or combination of solvents, and treated with allyl halide and a conventional hydrolyzing catalyst known in the art, and heated under a nitrogen atmosphere for a sufficient time to result quantitative loss of reactants, as determined by GC, NMR or other appropriate analytical technique. The cooled solution is then concentrated under reduced pressure and, optionally, purified by one, or a combination of techniques, to remove the residual catalyst and / or other contaminants, including column chromatography, liquid-liquid extraction and distillation. The resulting material is dissolved in a suitable solvent for nucleophilic substitution, treated with the desired tertiary amino vinyl compound, and heated to a temperature sufficient to promote the reaction without causing gelation. The solvents are removed under reduced pressure and the resulting material can be purified by one of the combinations of various techniques well known in the art, including vacuum separation, liquid-liquid extraction and column chromatography.

Example 2

Analytical measurements

NMR: The 1H-NMR characterization was performed using a 400 MHz Varian spectrometer using conventional techniques in the art. The samples were dissolved in chloroform-d (99.8 of D atoms) at a concentration of 20 mg / ml, unless otherwise indicated. Chemical shifts were determined by assigning the residual chloroform peak at 7.25 ppm. Peak areas were determined by integration of the peaks separated from the initial measurement and are presented as a proportion of the total normalized area of all peaks produced, rounded to the nearest 0.01. The division patterns (s = singlet, d = doublet, t = triplet, c = quadruplet, m = multiplet, a = width) and the coupling constants (J / Hz) are shown when they are present, and are clearly distinguishable, but as one skilled in the art can appreciate, the lack of information about a division does not necessarily indicate an absence of division in the disclosed ophthalmic monomers.

Mechanical properties and oxygen permeability: Module and elongation tests were performed in accordance with ASTM D-1708a, using an Instron instrument (model 4502) where the hydrogel film sample is immersed in borate buffered saline; an appropriate size of the film sample of a gauge with a length of 22 mm and a width of 4.75 mm, where the sample additionally has ends that form a dog bone shape to accommodate the grip of the sample with the jaws of the Instron instrument, and a thickness of 200 + 50 micrometers.

The oxygen permeability (also called Dk) was determined by the following procedure. Other methods and / or instruments may be used, as long as the oxygen permeability values obtained therefrom are equivalent to those of the described method. The oxygen permeability of silicone hydrogels is measured by the polarographic method (ANSI Z80.20-1998) using a Permemeter 02, model 201T instrument (Createch, Albany, California, USA) that has a probe that contains a Circular gold cathode, central, at its end, and a silver anode isolated from the cathode. Measurements are taken only on pre-inspected flat silicon silicone hydrogel film samples to verify that they have no pitting, of three different central thicknesses, ranging from 150 to 600 micrometers. The center thickness measurements of the film samples can be measured using a Rehder ET-1 electronic film thickness gauge. Generally, the film samples are in the form of a circular disk. Measurements are taken with the film and probe sample immersed in a bath containing phosphate buffered saline (PBS) equilibrated at 35 ° C +/- 0.2 °. Before immersing the probe and the film sample in the PBS bath, the film sample is placed and centered on the cathode pre-moistened with the balanced PBS, ensuring that there are no air bubbles or excess PBS between the cathode and the film sample, and the film sample is then secured to the

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probe with a mounting cap, with the cathode portion of the probe in contact only with the film sample. For silicon hydrogel films, it is often useful to use a Teflon polymer membrane, which for example has a circular disk shape, between the cathode of the probe and the film sample. In such cases, the Teflon membrane is placed first on the pre-moistened cathode, and then the film sample is placed on the Teflon membrane, ensuring that there are no air bubbles or excess PBS below the membrane. Teflon or film sample. Once measurements are collected, only data with a correlation coefficient (R2) value of 0.97 or greater should be entered in the calculation of the value of Dk. At least two measurements of Dk per thickness are obtained, which satisfy the value of R2. Using known regression analysis, oxygen permeability (Dk) is calculated from film samples having at least three different thicknesses. Any of the hydrated film samples with solutions other than PBS are first soaked in purified water and allowed to equilibrate for at least 24 hours and then soaked in PHB and allowed to equilibrate for at least 12 hours The instruments are cleaned regularly and are regularly calibrated using RGP standards. The upper and lower limits are established by calculating +/- 8.8% of the Replacement values established by William J. Benjamin, et al., The Oxygen Permeability of Reference Materials, Optom Vis Sci 7 (12s): 95 (1997 ), whose description is incorporated in this

document in its entirety:

Material name

Deposit Securities Lower limit Upper limit

Fluoroperm 30

26.2 24 29

Menicon EX

62.4 56 66

Quantum II

92.9 85 101

Unless specifically indicated otherwise or made clear through its use, all numbers used in this application should be considered modified by the term "approximately."

The films were removed from glass plates and hydrated / extracted in deionized H2O for a minimum of 4 hours, transferred to deionized H2O and autoclaved 30 minutes at 121 ° C. The cooled films were then analyzed for the selected properties of interest in ophthalmic materials, as described in Table 2. Mechanical tests were performed on borate buffered saline according to ASTM D-1708a, discussed above. The oxygen permeabilities presented in Dk (or sweeping) units were measured in a phosphate buffered saline solution at 35 ° C, using acceptable films with three different thicknesses, as discussed above.

Abbreviations

NVP 1-Vinyl-2-pyrrolidone DMA N, N-Dimethylacrylamide TRIS Methacryloxypropyltris (trimethylsiloxy) silane HEMA 2-hydroxyethyl methacrylate AIBN 2,2'-Azobis (2-methylpropionitrile) Darocur 2-Hydroxy-2-methylbapton TBE 4-tert-butyl-2-hydroxy-cyclohexyl methacrylate MMA Methyl methacrylate

Example 3

Reagents

Reagents allyl bromide, 2- (dimethylamino) ethyl methacrylate, platinum-1,3-divinyl-1,1,3,3-tetramethyldisiloxane complex in xylenes, N, N-dimethylacrylamide, 2,2'-azobis (2- methylpropionitrile), chloroform-d, tert-butanol, methyl methacrylate and all solvents were purchased from Sigma-Aldrich, Milwaukee, Wl, and used without further purification. 1-Vinyl-2-pyrrolidone and 2-hydroxyethyl methacrylate were purchased from Sigma-Aldrich, Milwaukee, Wl, and distilled before use. 4-tert-Butyl-2-hydroxycyclohexyl methacrylate was obtained from Aron Chemicals. Tris (trimethylsiloxy) silane, methacryloxypropyltris (trimethylsiloxy) silane and poly (dimethylsiloxane) hydride terminated reagents (average molecular weight 1000-1100 g / mol) were purchased from Gelest, Inc., Morrisville, PA.

Preparation of the ophthalmic monomer 1. Allyl bromide (40 ml, 0.46 mol) and tris (trimethylsiloxy) silane (168 ml, 0.48 mol) were treated in 2: 1 v / v tetrahydrofuran / dioxane solution (920 ml) ) with the 10% platinum complex -1,3-divinyl1,1,3,3-tetramethyldisiloxane in xylenes (1.2 ml) and heated at 60 ° C for 15 hours under a nitrogen atmosphere. The cooled solution was concentrated under reduced pressure, divided into two parts, passed through a silica gel column (5 120 cm, pentane), recombined and the solvents removed again under reduced pressure. The resulting colorless liquid was dissolved in ethyl acetate (375 ml), treated with 2- (dimethylamino) ethyl methacrylate (71 ml, 0.42 mol) and heated at 60 ° C in the dark. The conversion was controlled using GC. After about 50 hours, the solution was cooled to room temperature, at which time a crystalline solid precipitated from the solution. The precipitate was filtered and recrystallized from ethyl acetate twice, giving ophthalmic monomer 1 as a colorless, crystalline solid (109.2 g): 1 H NMR (CDCI3, 400 MHz) δ 6.13 (s, 0, 02 H), 5.66 (s, 0.02 H), 4.65-4.63 (m, 0.04 H), 4.18-4.16 (m, 0.04 H), 3, 69-3.62 (m, 0.08 H), 3.49 (s, 0.12 H), 1.93-1.82 (m, 0.12 H), 1.62-1.56 ( m, 0.04 H), 0.09 (s, 0.51 H); mp 114-116 ° C, The proton NMR spectrum of the ophthalmic monomer 1 is included as Figure 1.

image 1

Example 4

Light curing of articles containing the ophthalmic monomer 1

10 Liquid monomer solutions, containing ophthalmic monomer 1, were clamped between silanized glass plates at various thicknesses, and polymerized using photochemical decomposition of the free radical generation additive. Each of the examples shown in Table 1 represents a formulation that results in an insoluble, non-adherent, transparant film.

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Table 1. Photopolymerization of transparent articles containing the ophthalmic monomer 1

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Examples 5

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Thermal polymerization of articles containing the ophthalmic monomer 1

Liquid monomer solutions containing ophthalmic monomer 1 were clamped between silanized glass plates at various thicknesses and polymerized using thermal decomposition of the free radical generation additive by heating 2 hours at 100 ° C under a nitrogen atmosphere. Each of the representative formulation examples shown in Table 2 gave an insoluble, non-adherent and transparent film.

Table 2. Thermal polymerization of transparent articles containing the ophthalmic monomer 1.

ID 1 TRIS NVP HEMA TBE ECDMA MMA Glycerol TBA v-64

F 47.6 31.9 0.3 19.8 0.4 G 55.5 23.9 0.3 19.9 0.4 H 47.1 31.5 0.3 20.6 0.4 I 47 , 8 31.8 5.0 15.0 0.4 J 57.1 24.6 1.1 16.7 0.5 K 33.0 33.0 33.4 0.3 0.3 L 28.1 28.1 28.2 0.3 14.9 0.4 M 28.1 14.3 28.0 0.4 13.6 15.1 0.5 N 21.9 22.4 43.9 0.3 10.9 0.5 O 16.7 17.1 17.1 33.0 0.7 14.8 P 17.8 17.9 17.9 35.7 0.3 9.9 0.5

Example 6

Properties of processed articles containing the ophthalmic monomer 1. Representative films containing the ophthalmic monomer 1 of the above examples were subjected to hydration and extraction in deionized water for a minimum of 4 h, followed after autoclaving, also in water deionized Then, the properties of interest for ophthalmic applications were determined (Table 3).

Table 3. Selected properties of processed items containing the ophthalmic monomer 1. ID

Water content (%) Dk (barrers) Module (g / mm-1) Tear (g / mm)

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OR

62 151

56 1.4 90 100 11

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Example 7

Preparation of ophthalmic monomer 2. To a solution of poly (dimethylsiloxane) terminated in hydride (99.3 g, Mn 1000-1100) and allyl bromide (25 ml, 287 mmol) in tetrahydrofuran / 1,4-dioxane (570 ml v / v 2: 1) under a nitrogen atmosphere the 10% platinum complex -1,3-divinyl-1,1,3,3-tetramethyldisiloxane in xylenes (0.7 ml) was added and the solution was added heated 15 hours at 60 ° C. The cooled solution was concentrated under reduced pressure, redissolved in pentane (250 ml), stirred for 15 hours on silica gel (40 g), filtered and the solvents were removed again under reduced pressure. The colorless liquid was then dissolved in ethyl acetate (140 ml), treated with 2 (dimethylamino) ethyl methacrylate (94 ml, 557 mmol) and heated 100 hours at 60 ° C under a nitrogen atmosphere and in the dark. The cooled solution was removed in vacuo to remove the solvent and residual 2- (dimethylamino) ethyl methacrylate, giving ophthalmic monomer 2 as a waxy solid (99.4 g): 1 H NMR (CDCI3, 400 MHz) δ 6.19 (s, 0.01 H), 5.66 (s, 0.01), 4.64 (a, 0.02 H), 1.76 (a, 0.02 H), 3.70 -3.64 (m, 0.04 H), 3.50 (0.06 H), 1.94-1.83 (m, 0.05 H), 1.63-1.55 (m, 0 , 02 H), 0.05 (s, 0.78 H). The proton NMR spectrum of ophthalmic monomer 2 is substantially similar in appearance to that of ophthalmic monomer 1, as shown in Figure 1, except with

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Example 8

Thermal polymerization of articles containing ophthalmic monomer 2

Solutions of the liquid monomer containing the ophthalmic monomer 2 were clamped between silanized glass plates at various thicknesses, and polymerized using the thermal decomposition of the free radical generation additive by heating 2 hours at 100 ° C under a nitrogen atmosphere. Each of the representative formulation examples shown in Table 4 gave an insoluble, non-adherent, transparent film.

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Table 4. Thermal polymerization of transparent articles containing the ophthalmic monomer 2.

ID

Monomer 2 NVP DMA HEMA TRIS TBE v-64 Glycerol

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Q

49.8 49.7 0.5 49.8 24.9 0.5 49.7 10 24.9 0.5 49.7 24.9 0.5 39.8 19.9 0.5 35.3 17 , 6 0.5 11.3 39.5 10.1 20.2 0.5 39.8 10.0 24.9 0.5

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Example 9

Properties of processed items containing ophthalmic monomer 2

5 Representative films containing the ophthalmic monomer 2 of the previous examples were subjected to hydration and extraction in deionized water, for a minimum of 4 h, followed after autoclaving, also in deionized water. Then, the properties of interest for ophthalmic applications were determined (Table 5).

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Table 5. Selected properties of processed articles containing ophthalmic monomer 2.

ID

Water (%) Dk (barrers) Module (g / mm2) Tear (g / mm)

Q

30 37 231

R

fifty 51 60 2

S

51 70 79 2

V

56 64 75 2

Y

59 ND 100 3

Z

54 248 9

AA

68 3. 4 one

AB

64 54 Four. Five 2

Claims (2)

1. A method of preparing a medical device formation monomer, removable in water, the method comprising: 5 to provide a hydride-containing siloxane compound, dissolve the hydride-containing siloxane compound in a solvent or combination of solvents; treating the hydride containing siloxane compound dissolved with an allyl halide and a conventional hydrolyzing catalyst to form a first reaction mixture; 10 heating the first reaction mixture in a nitrogen atmosphere for a time sufficient to result in a quantitative loss of reactants, as determined by an appropriate analytical technique thereby providing a mixture of monomers; cool the monomer mixture; concentrate the cooled mixture; Dissolving the cooled mixture in a suitable solvent for nucleophilic substitution; treating the cooled mixture containing the appropriate solvent for nucleophilic substitution with a tertiary amino vinyl compound, to form a second reaction mixture; heating the second reaction mixture to a temperature sufficient to promote the reaction, without causing gelefication; 20 remove any remaining solvent to provide a material containing product; and purify the material containing the product to produce a water-removable medical device monomer. 2. The method of claim 1, wherein the hydride-containing siloxane compound is of formula 25 image 1 where R1 is CH3 or O (Si [CH3] 3) and R2 is the same as R1 or H (Si [CH3] 2O) n, The method of claim 2, wherein the allyl halide is allyl bromide.