Provided are crosslinked polymer compositions that include a first synthetic polymer containing multiple nucleophilic groups covalently bound to a second synthetic polymer containing multiple electrophilic groups. The first synthetic polymer is preferably a synthetic polypeptide or a polyethylene glycol that has been modified to contain multiple nucleophilic groups, such as primary amino (--NH.sub.2) or thiol (--SH) groups. The second synthetic polymer may be a hydrophilic or hydrophobic synthetic polymer, which contains or has been derivatized to contain, two or more electrophilic groups, such as succinimidyl groups. The compositions may further include other components, such as naturally occurring polysaccharides or proteins (such as glycosaminoglycans or collagen) and/or biologically active agents. Also disclosed are methods for using the crosslinked polymer compositions to effect adhesion between a first surface and a second surface; to effect tissue augmentation; to prevent the formation of surgical adhesions; and to coat a surface of a synthetic implant.

Description of the Invention

SUMMARY OF THE INVENTION

The present invention discloses a crosslinked polymer composition comprising a first synthetic polymer containing two or more nucleophilic groups, and a second synthetic polymer containing two or more electrophilic groups which are capable of covalently bonding to one another to form a three dimensional matrix.

A preferred composition of the invention comprises polyethylene glycol containing two or more primary amino groups as the first synthetic polymer, and polyethylene glycol containing two or more succinimidyl groups (a five-membered ring structure represented herein as --N(COCH.sub.2).sub.2) as the second synthetic polymer.

In a general method for preparing a composition for the delivery of a negatively charged compound (such as a protein or drug), a first synthetic polymer containing two or more nucleophilic groups is reacted with a second synthetic polymer containing two or more electrophilic groups, wherein the first synthetic polymer is present in molar excess in comparison to the second synthetic polymer, to form a positively charged matrix, which is then reacted with a negatively charged compound. In a general method for preparing a matrix for the delivery of a positively charged compound, a first synthetic polymer containing two or more nucleophilic groups is reacted with a second synthetic polymer containing two or more electrophilic groups, wherein the second synthetic polymer is present in molar excess in comparison to the first synthetic polymer, to form a negatively charged matrix, which is then reacted with a positively charged compound.

In a general method for effecting the nonsurgical attachment of a first surface to a second surface, a first synthetic polymer containing two or more nucleophilic groups is mixed with a second synthetic polymer containing two or more electrophilic groups to provide a reaction mixture; the reaction mixture is applied to a first surface before substantial crosslinking has occurred; and the first surface is contacted with a second surface to effect adhesion between the two surfaces.

In a general method for augmenting soft or hard tissue within the body of a mammalian subject, a first synthetic polymer containing two or more nucleophilic groups and a second synthetic polymer containing two or more electrophilic groups are administered simultaneously to a tissue site in need of augmentation and the reaction mixture is allowed to crosslink in situ to effect augmentation of the tissue. Alternatively, the first synthetic polymer and the second synthetic polymer may be mixed immediately prior to being administered to a tissue site, such that the majority of the crosslinking reaction proceeds in vivo.

In a general method for preventing the formation of adhesions following surgery, a first synthetic polymer containing two or more nucleophilic groups is mixed with a second synthetic polymer containing two or more electrophilic groups to provide a reaction mixture; the reaction mixture is applied to tissue comprising, surrounding, or adjacent to a surgical site before substantial crosslinking has occurred between the nucleophilic groups and the electrophilic groups; the reaction mixture is allowed to continue crosslinking in situ until equilibrium crosslinking has been achieved; and the surgical site is closed by conventional methodologies.

In a general method for coating a surface of a synthetic implant, a first synthetic polymer containing two or more nucleophilic groups is mixed with a second synthetic polymer containing two or more electrophilic groups to provide a reaction mixture; the reaction mixture is applied to a surface of a synthetic implant; and the components of the reaction mixture are allowed to crosslink with each other on the surface of the implant.

A feature of the invention is that the crosslinked polymer compositions are optically clear, making the compositions and methods of the invention particularly suited for use in ophthalmic applications in which optical clarity is a requirement. Furthermore, the compositions of the invention are comprised of biocompatible, non-immunogenic components which leave no toxic, potentially inflammatory or immunogenic reaction products at the tissue site of administration.

Another feature of the invention is that the crosslinked polymer compositions have a high compression strength and high swellability, i.e., a composition that has been dried will swell to three times (or more) its dried size upon rehydration, and is more "elastic." Since these polymers are generally very hydrophilic, they are more easily injected, i.e., the crosslinked composition stays as a "cohesive mass" when injected through a fine gauge (27-30 gauge) needle.

Yet another feature of the invention is that nucleophilic groups on the first synthetic polymer may covalently bind to primary amino groups on lysine residues of collagen molecules at the tissue site of administration, in effect, "biologically anchoring" the composition to the host tissue.

One feature of the invention is that the components of the compositions are non-immunogenic and do not require a "skin test" prior to beginning treatment, as do currently available xenogeneic collagen compositions, such as those manufactured from bovine hides.

Another feature of the invention is that, unlike collagen, the compositions of the invention are not subject to enzymatic cleavage by matrix metalloproteinases, such as collagenase, and are therefore not readily degradable in vivo and, as such, are expected to have greater long-term persistence in vivo than prior art collagen compositions.

Still another feature is that, when the groups on each of the polymers utilized react to form an amide bond, the manufacturing of the compositions of the present invention can be highly controlled rendering more consistent quality of products.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS OF THE INVENTION

In accordance with the present invention, crosslinked polymer compositions are prepared by reacting a first synthetic polymer containing two or more nucleophilic groups with a second synthetic polymer containing two or more electrophilic groups capable of covalently binding with the nucleophilic groups on the first synthetic polymer.

The components of the present invention are non-immunogenic and, as such, do not require a "skin test" prior to starting treatment, as does xenogenic collagen. Also, unlike collagen, the compositions of the invention are not subject to enzymatic cleavage by matrix metalloproteinases (e.g., collagenase) and are therefore expected to have greater long-term persistence in vivo than currently available collagen compositions.

The concept behind the present invention is that a synthetic polymer containing multiple nucleophilic groups (represented below as "X") will react with a synthetic polymer containing multiple electrophilic groups (represented below as "Y"), resulting in a covalently bound polymer network, as follows: polymer-X.sub.m+polymer-Y.sub.n.fwdarw.polymer-Z-polymer

wherein m.gtoreq.2, n.gtoreq.2, and m+n.gtoreq.5;

X=--NH.sub.2, --SH, --OH, --PH.sub.2, --CO--NH--NH.sub.2, etc., and can be the same or different;

Y=--Co.sub.2N(COCH.sub.2).sub.2, --CO.sub.2H, --CHO, --CHOCH.sub.2, --N.dbd.C.dbd.O, SO.sub.2CH.dbd.CH.sub.2, --N(COCH).sub.2), --S--S--(C.sub.5H.sub.4N), etc., and can be the same or different; and

Z=functional group resulting from the union of a nucleophilic group (X) and an electrophilic group (Y).

As noted above, it is also contemplated by the present invention that X and Y may be the same or different, i.e., the polymer may have two different electrophilic groups, or two different nucleophilic groups, such as with glutathione.

The backbone of each polymer is preferably an alkylene oxide, particularly, ethylene oxide, propylene oxide, and mixtures thereof. Examples of difunctional alkylene oxides can be represented by: X-polymer-X.fwdarw.Y-polymer-Y

wherein X and Y are as defined above, and the term "polymer" represents:

--(CH.sub.2CH.sub.2O).sub.n-- or --(CH(CH.sub.3)CH.sub.2O).sub.n-- or --(CH.sub.2CH.sub.2O).sub.n--(CH(CH.sub.3)CH.sub.2O).sub.n--.

The required functional group X or Y is commonly coupled to the polymer backbone by a linking group (represented below as "Q"), many of which are known or possible. There are many ways to prepare the various functionalized polymers, some of which are listed below: polymer-Q.sup.1-X.sub.m+polymer-Q.sup.2-Y.fwdarw.polymer-Q.sup.1-Z-Q.sup.- 2-polymer -- see Original Patent.

Synthetic Polymers

In order to prepare the compositions of the present invention, it is first necessary to provide a first synthetic polymer containing two or more nucleophilic groups, such as primary amino groups or thiol groups, and a second synthetic polymer containing two or more electrophilic groups capable of covalently binding with the nucleophilic groups on the second synthetic polymer.

As used herein, the term "polymer" refers inter alia to polyalkyls, polyamino acids and polysaccharides. Additionally, for external or oral use, the polymer may be polyacrylic acid or carbopol.

As used herein, the term "synthetic polymer" refers to polymers that are not naturally occurring and that are produced via chemical synthesis. As such, naturally occurring proteins such as collagen and naturally occurring polysaccharides such as hyaluronic acid are specifically excluded. Synthetic collagen, and synthetic hyaluronic acid, and their derivatives, are included. Synthetic polymers containing either nucleophilic or electrophilic groups are also referred to herein as "multifunctionally activated synthetic polymers." The term "multifunctionally activated" (or, simply, "activated") refers to synthetic polymers which have, or have been chemically modified to have, two or more nucleophilic or electrophilic groups which are capable of reacting with one another (i.e., the nucleophilic groups react with the electrophilic groups) to form covalent bonds. Types of multifunctionally activated synthetic polymers include difunctionally activated, tetrafunctionally activated, and star-branched polymers.

Multifunctionally activated synthetic polymers for use in the present invention must contain at least two, more preferably, at least three, functional groups in order to form a three-dimensional crosslinked network with synthetic polymers containing multiple nucleophilic groups (i.e., "multi-nucleophilic polymers"). In other words, they must be at least difunctionally activated, and are more preferably trifunctionally or tetrafunctionally activated. If the first synthetic polymer is a difunctionally activated synthetic polymer, the second synthetic polymer must contain three or more functional groups in order to obtain a three-dimensional crosslinked network. Most preferably, both the first and the second synthetic polymer contain at least three functional groups.

Synthetic Polymers Containing Multiple Nucleophilic Groups

Synthetic polymers containing multiple nucleophilic groups are also referred to generically herein as "multi-nucleophilic polymers". For use in the present invention, multi-nucleophilic polymers must contain at least two, more preferably, at least three, nucleophilic groups. If a synthetic polymer containing only two nucleophilic groups is used, a synthetic polymer containing three or more electrophilic groups must be used in order to obtain a three-dimensional crosslinked network.

Preferred multi-nucleophilic polymers for use in the compositions and methods of the present invention include synthetic polymers that contain, or have been modified to contain, multiple nucleophilic groups such as primary amino groups and thiol groups. Preferred multi-nucleophilic polymers include: (i) synthetic polypeptides that have been synthesized to contain two or more primary amino groups or thiol groups; and (ii) polyethylene glycols that have been modified to contain two or more primary amino groups or thiol groups. In general, reaction of a thiol group with an electrophilic group tends to proceed more slowly than reaction of a primary amino group with an electrophilic group.

Preferred multi-nucleophilic polypeptides are synthetic polypeptides that have been synthesized to incorporate amino acids containing primary amino groups (such as lysine) and/or amino acids containing thiol groups (such as cysteine). Poly(lysine), a synthetically produced polymer of the amino acid lysine (145 MW, is particularly preferred. Poly(lysine)s have been prepared having anywhere from 6 to about 4,000 primary amino groups, corresponding to molecular weights of about 870 to about 580,000.

Poly(lysine)s for use in the present invention preferably have a molecular weight within the range of about 1,000 to about 300,000; more preferably, within the range of about 5,000 to about 100,000; most preferably, within the range of about 8,000 to about 15,000. Poly(lysine)s of varying molecular weights are commercially available from Peninsula Laboratories, Inc. of San Carlos, Calif. (acquired by Bachem AG in 1999). Polyethylene glycol can be chemically modified to contain multiple primary amino or thiol groups according to methods set forth, for example, in Chapter 22 of POLY(ETHYLENE GLYCOL) CHEMISTRY: BIOTECHNICAL AND BIOMEDICAL APPLICATIONS, J. Milton Harris, ed., Plenum Press, NY (1992). Polyethylene glycols which have been modified to contain two or more primary amino groups are referred to herein as "multi-amino PEGS." Polyethylene glycols which have been modified to contain two or more thiol groups are referred to herein as "multi-thiol PEGS." As used herein, the term "polyethylene glycol(s)" includes modified and or derivatized polyethylene glycol(s).

Various forms of multi-amino PEG are commercially available from Nektar Therapeutics, Inc. of San Carlos, Calif. (through its acquisition of Shearwater Polymers of Huntsville, Ala.), and from Texaco Chemical Company of Houston, Tex. under the name "Jeffamine." Multi-amino PEGs useful in the present invention include Texaco's Jeffamine diamines ("D" series) and triamines ("T" series), which contain two and three primary amino groups per molecule, respectively. General structures for the Jeffamine diamines and triamines are shown in FIG. 3 (see Original Patent).

Polyamines such as ethylenediamine (H.sub.2N--CH.sub.2CH.sub.2--NH.sub.2), tetramethylenediamine (H.sub.2N--(CH.sub.2).sub.4--NH2.sub.2), pentamethylenediamine (cadaverine) (H.sub.2N--(CH.sub.2).sub.5--NH.sub.2), hexamethylenediamine (H.sub.2N--(CH.sub.2).sub.6--NH.sub.2), bis(2-hydroxyethyl)amine (HN--(CH.sub.2CH.sub.2OH).sub.2), bis(2-aminoethyl)amine (HN--(CH.sub.2CH.sub.2NH.sub.2).sub.2), and tris(2-aminoethyl)amine (N--(CH.sub.2CH.sub.2NH.sub.2).sub.3) may also be used as the synthetic polymer containing multiple nucleophilic groups.

Synthetic Polymers Containing Multiple Electrophilic Groups

Synthetic polymers containing multiple electrophilic groups are also referred to herein as "multi-electrophilic polymers." For use in the present invention, the multifunctionally activated synthetic polymers must contain at least two, more preferably, at least three, electrophilic groups in order to form a three-dimensional crosslinked network with multi-nucleophilic polymers

Preferred multi-electrophilic polymers for use in the compositions of the invention are polymers which contain two or more succinimidyl groups capable of forming covalent bonds with electrophilic groups on other molecules. Succinimidyl groups are highly reactive with materials containing primary amino (--NH.sub.2) groups, such as multi-amino PEG, poly(lysine), or collagen. Succinimidyl groups are slightly less reactive with materials containing thiol (--SH) groups, such as multi-thiol PEG or synthetic polypeptides containing multiple cysteine residues.

As used herein, the term "containing two or more succinimidyl groups" is meant to encompass polymers which are commercially available containing two or more succinimidyl groups, as well as those that must be chemically derivatized to contain two or more succinimidyl groups. As used herein, the term "succinimidyl group" is intended to encompass sulfosuccinimidyl groups and other such variations of the "generic" succinimidyl group. The presence of the sodium sulfite moiety on the sulfosuccinimidyl group serves to increase the solubility of the polymer.

Hydrophilic Polymers

Hydrophilic polymers and, in particular, various polyethylene glycols, are preferred for use in the compositions of the present invention. As used herein, the term "PEG" refers to polymers having the repeating structure (OCH.sub.2CH.sub.2).sub.n.

Structures for some specific, tetrafunctionally activated forms of PEG are shown in FIGS. 4 to 13 (see Original Patent), as are generalized reaction products obtained by reacting tetrafunctionally activated PEGs with multi-amino PEGS. As depicted in the Figures, the succinimidyl group is a five-member ring structure represented as --N(COCH.sub.2).sub.2. In FIGS. 4 to 13, the symbol ^^^ denotes an open linkage.

FIG. 4 (see Original Patent) shows the reaction of tetrafunctionally activated PEG succinimidyl glutarate, referred to herein as SG-PEG, with multi-amino PEG, and the reaction product obtained thereby.

Another activated form of PEG is referred to as PEG succinimidyl propionate (SE-PEG). The structural formula for tetrafunctionally activated SE-PEG and the reaction product obtained by reacting it with multi-amino PEG are shown in FIG. 5 (see Original Patent). In a general structural formula for the compound, the subscript 3 is replaced with an "m." In the embodiment shown in FIG. 4, m=3, in that there are three repeating CH.sub.2 groups on either side of the PEG.

The structure in FIG. 5 results in a conjugate which includes an "ether" linkage which is less subject to hydrolysis. This is distinct from the conjugate shown in FIG. 4, wherein an ester linkage is provided. The ester linkage is subject to hydrolysis under physiological conditions.

Yet another functionally activated form of polyethylene glycol, wherein m=2, is shown in FIG. 6 (see Original Patent), as is the conjugate formed by reacting the tetrafunctionally activated PEG with a multi-amino PEG.

Another functionally activated PEG similar to the compounds of FIGS. 5 and 6 is provided when m=1. The structural formula of the tetrafunctionally activated PEG and resulting conjugate formed by reacting the activated PEG with multi-amino PEG are shown in FIG. 7 (see Original Patent). It is noted that this conjugate includes both an ether and a peptide linkage. These linkages are stable under physiological conditions.

Another functionally activated form of PEG is referred to as PEG succinimidyl succinamide (SSA-PEG). The structural formula for the tetrafunctionally activated form of this compound and the reaction product obtained by reacting it with multi-amino PEG are shown in FIG. 8 (see Original Patent). In the structure shown in FIG. 8, m=2; however, related compounds, wherein m=1 or m=3-10, may also be used in the compositions of the invention.

The structure in FIG. 8 results in a conjugate which includes an "amide" linkage which, like the ether linkage previously described, is less subject to hydrolysis and is therefore more stable than an ester linkage.

Yet another activated form of PEG is provided when m=0. This compound is referred to as PEG succinimidyl carbonate (SC-PEG). The structural formula of tetrafunctionally activated SC-PEG and the conjugate formed by reacting it with multi-amino PEG are shown in FIG. 9 (see Original Patent).

As discussed above, preferred activated polyethylene glycol derivatives for use in the invention contain succinimidyl groups as the reactive group. However, different activating groups can be attached at sites along the length of the PEG molecule. For example, PEG can be derivatized to form functionally activated PEG propionaldehyde (A-PEG), the tetrafunctionally activated form of which is shown in FIG. 10 (see Original Patent), as is the conjugate formed by the reaction of A-PEG with multi-amino PEG. The linkage shown in FIG. 10 is referred to as a --(CH.sub.2).sub.m--NH-- linkage, where m=1-10.

Yet another form of activated polyethylene glycol is functionally activated PEG glycidyl ether (E-PEG), of which the tetrafunctionally activated compound is shown in FIG. 11 (see Original Patent), as is the conjugate formed by reacting such with multi-amino PEG.

Another activated derivative of polyethylene glycol is functionally activated PEG-isocyanate (I-PEG), which is shown in FIG. 12 (see Original Patent), along with the conjugate formed by reacting such with multi-amino PEG.

Another activated derivative of polyethylene glycol is functionally activated PEG-vinylsulfone (V-PEG), which is shown in FIG. 13 (see Original Patent), below, along with the conjugate formed by reacting such with multi-amino PEG.

Preferred multifunctionally activated polyethylene glycols for use in the compositions of the present invention are polyethylene glycols containing succinimidyl groups, such as

SG-PEG and SE-PEG (shown in FIGS. 4-7), preferably in trifunctionally or tetrafunctionally activated form.

Many of the activated forms of polyethylene glycol described above are now available commercially from Nektar Therapeutics and Union Carbide of South Charleston, W.V.

Hydrophobic Polymers

Hydrophobic polymers can also be used to prepare the compositions of the present invention. Hydrophobic polymers for use in the present invention preferably contain, or can be derivatized to contain, two or more electrophilic groups, such as succinimidyl groups, most preferably, two, three, or four electrophilic groups. As used herein, the term "hydrophobic polymer" refers to polymers which contain a relatively small proportion of oxygen or nitrogen atoms.

Hydrophobic polymers which already contain two or more succinimidyl groups include, without limitation, disuccinimidyl suberate (DSS), bis(sulfosuccinimidyl) suberate (BS.sup.3), dithiobis(succinimidylpropionate) (DSP), bis(2-succinimidooxycarbonyloxy)ethyl sulfone (BSOCOES), and 3,3'-dithiobis(sulfosuccinimidylpropionate (DTSPP), and their analogs and derivatives. The above-referenced polymers are commercially available from Pierce (Rockford, Ill.), under catalog Nos. 21555, 21579, 22585, 21554, and 21577, respectively. Structural formulas for the above-referenced polymers, as well as generalized reaction products obtained by reacting each of these polymers with amino PEG, are shown below in FIGS. 14-18 (see Original Patent), respectively.

Preferred hydrophobic polymers for use in the invention generally have a carbon chain that is no longer than about 14 carbons. Polymers having carbon chains substantially longer than 14 carbons generally have very-poor solubility in aqueous solutions and, as such, have very long reaction times when mixed with aqueous solutions of synthetic polymers containing multiple nucleophilic groups.

Derivatization of Polymers to Contain Functional Groups

Certain polymers, such as polyacids, can be derivatized to contain two or more functional groups, such as succinimidyl groups. Polyacids for use in the present invention include, without limitation, trimethylolpropane-based tricarboxylic acid, di(trimethylol propane)-based tetracarboxylic acid, heptanedioic acid, octanedioic acid (suberic acid), and hexadecanedioic acid (thapsic acid). Many of these polyacids are commercially available from DuPont Chemical Company of Wilmington, Del.

According to a general method, polyacids can be chemically derivatized to contain two or more succinimidyl groups by reaction with an appropriate molar amount of

N-hydroxysuccinimide (NHS) in the presence of NN'-dicyclohexylcarbodiimide (DCC).

Polyalcohols such as trimethylolpropane and di(trimethylol propane) can be converted to carboxylic acid form using various methods, then further derivatized by reaction with NHS in the presence of DCC to produce trifunctionally and tetrafunctionally activated polymers, respectively, as described in commonly owned, copending U.S. application Ser. No. 08/403,358. Polyacids such as heptanedioic acid (HOOC--(CH.sub.2).sub.5--COOH), octanedioic acid (HOOC--(CH.sub.2).sub.6--COOH), and hexadecanedioic acid (HOOC--(CH.sub.2).sub.14--COOH) are derivatized by the addition of succinimidyl groups to produce difunctionally activated polymers.

Polyamines such as ethylenediamine (H.sub.2N--CH.sub.2CH.sub.2--NH.sub.2), tetramethylenediamine (H.sub.2N--(CH.sub.2).sub.4--NH.sub.2), pentamethylenediamine (cadaverine) (H.sub.2N--(CH.sub.2).sub.5--NH.sub.2), hexamethylenediamine (H.sub.2N--(CH.sub.2).sub.6--NH.sub.2), bis(2-hydroxyethyl)amine (HN--(CH.sub.2CH.sub.2OH).sub.2), bis(2)aminoethyl)amine (HN--(CH.sub.2CH.sub.2NH.sub.2).sub.2), and tris(2-aminoethyl)amine (N--(CH.sub.2CH.sub.2NH.sub.2).sub.3) can be chemically derivatized to polyacids, which can then be derivatized to contain two or more succinimidyl groups by reacting with the appropriate molar amounts of N-hydroxysuccinimide in the presence of DCC, as described in U.S. Pat. No. 5,580,923. Many of these polyamines are commercially available from DuPont Chemical Company.

Preparation of Crosslinked Polymer Compositions

In a general method for preparing the crosslinked polymer compositions of the invention, a first synthetic polymer containing multiple nucleophilic groups is mixed with a second synthetic polymer containing multiple electrophilic groups. Formation of a three-dimensional crosslinked network occurs as a result of the reaction between the nucleophilic groups on the first synthetic polymer and the electrophilic groups on the second synthetic polymer.

Hereinafter, the term "first synthetic polymer" will be used to refer to a synthetic polymer containing two or more nucleophilic groups, and the term "second synthetic polymer" will be used to refer to a synthetic polymer containing two or more electrophilic groups. The concentrations of the first synthetic polymer and the second synthetic polymer used to prepare the compositions of the present invention will vary depending upon a number of factors, including the types and molecular weights of the particular synthetic polymers used and the desired end use application.

In general, we have found that when using multi-amino PEG as the first synthetic polymer, it is preferably used at a concentration in the range of about 0.5 to about 20 percent by weight of the final composition, while the second synthetic polymer is used at a concentration in the range of about 0.5 to about 20 percent by weight of the final composition. For example, a final composition having a total weight of 1 gram (1000 milligrams) would contain between about 5 to about 200 milligrams of multi-amino PEG, and between about 5 to about 200 milligrams of the second synthetic polymer.

Use of higher concentrations of both first and second synthetic polymers will result in the formation of a more tightly crosslinked network, producing a stiffer, more robust gel. As such, compositions intended for use in tissue augmentation will generally employ concentrations of first and second synthetic polymer that fall toward the higher end of the preferred concentration range. Compositions intended for use as bioadhesives or in adhesion prevention do not need to be as firm and may therefore contain lower polymer concentrations.

Because polymers containing multiple electrophilic groups will also react with water, the second synthetic polymer is generally stored and used in sterile, dry form to prevent the loss of crosslinking ability due to hydrolysis which typically occurs upon exposure of such electrophilic groups to aqueous media. Processes for preparing synthetic hydrophilic polymers containing multiple electrophilic groups in sterile, dry form are set forth in commonly assigned, U.S. application Ser. No. 08/497,573, filed Jun. 30, 1995, now U.S. Pat. No. 5,563,464. For example, the dry synthetic polymer may be compression molded into a thin sheet or membrane, which can then be sterilized using gamma or, preferably, e-beam irradiation. The resulting dry membrane or sheet can be cut to the desired size or chopped into smaller size particulates.

Polymers containing multiple nucleophilic groups are generally not water-reactive and can therefore be stored in aqueous solution.

The crosslinked polymer compositions can also be prepared to contain various imaging agents such as iodine or barium sulfate, or fluorine, in order to aid visualization of the compositions after administration via X-ray, or .sup.19F-MRI, respectively.

Incorporation of Other Components into the Crosslinked Synthetic Polymer

Naturally occurring proteins, such as collagen, and derivatives of various naturally occurring polysaccharides, such as glycosaminoglycans, can additionally be incorporated into the compositions of the invention. When these other components also contain functional groups which will react with the functional groups on the synthetic polymers, their presence during mixing and/or crosslinking of the first and second synthetic polymer will result in formation of a crosslinked synthetic polymer-naturally occurring polymer matrix. In particular, when the naturally occurring polymer (protein or polysaccharide) also contains nucleophilic groups such as primary amino groups, the electrophilic groups on the second synthetic polymer will react with the primary amino groups on these components, as well as the nucleophilic groups on the first synthetic polymer, to cause these other components to become part of the polymer matrix.

In general, glycosaminoglycans must be chemically derivatized by deacetylation, desulfation, or both in order to contain primary amino groups available for reaction with electrophilic groups on synthetic polymer molecules. Glycosaminoglycans that can be derivatized according to either or both of the aforementioned methods include the following: hyaluronic acid, chondroitin sulfate A, chondroitin sulfate B (dermatan sulfate), chondroitin sulfate C, chitin (can be derivatized to chitosan), keratan sulfate, keratosulfate, and heparin. Derivatization of glycosaminoglycans by deacetylation and/or desulfation and covalent binding of the resulting glycosaminoglycan derivatives with synthetic hydrophilic polymers is described in further detail in commonly assigned, allowed U.S. application Ser. No. 08/146,843, filed Nov. 3, 1993, now U.S. Pat. No. 5,510,418.

Similarly, Electrophilic groups on the second synthetic polymer will react with primary amino groups on lysine residues or thiol groups on cysteine residues of certain naturally occurring proteins. Lysine-rich proteins such as-collagen and its derivatives are especially reactive with electrophilic groups on synthetic polymers. As used herein, the term "collagen" is intended to encompass collagen of any type, from any source, including, but not limited to, collagen extracted from tissue or produced recombinantly, collagen analogues, collagen derivatives, modified collagens, and denatured collagens such as gelatin. Covalent binding of collagen to synthetic hydrophilic polymers is described in detail in commonly assigned U.S. Pat. No. 5,162,430, issued Nov. 10, 1992, to Rhee et al.

In general, collagen from any source may be used in the compositions of the invention; for example, collagen may be extracted and purified from human or other mammalian source, such as bovine or porcine corium and human placenta, or may be recombinantly or otherwise produced. The preparation of purified, substantially non-antigenic collagen in solution from bovine skin is well known in the art. Commonly owned U.S. Pat. No. 5,428,022, issued Jun. 27, 1995, to Palefsky et al., discloses methods of extracting and purifying collagen from the human placenta. Commonly owned, U.S. application Ser. No. 08/183,648, filed Jan. 18, 1994, now U.S. Pat. No. 5,667,839, discloses methods of producing recombinant human collagen in the milk of transgenic animals, including transgenic cows. The term "collagen" or "collagen material" as used herein refers to all forms of collagen, including those which have been processed or otherwise modified.

Collagen of any type, including, but not limited to, types I, II, III, IV, or any combination thereof, may be used in the compositions of the invention, although type I is generally preferred. Either atelopeptide or telopeptide-containing collagen may be used; however, when collagen from a xenogeneic source, such as bovine collagen, is used, atelopeptide collagen is generally preferred because of its reduced immunogenicity compared to telopeptide-containing collagen.

Collagen that has not been previously crosslinked by methods such as heat, irradiation, or chemical crosslinking agents is preferred for use in the compositions of the invention, although previously crosslinked collagen may be used. Noncrosslinked atelopeptide fibrillar collagen is commercially available from Angiotech Pharmaceuticals, Inc. of Palo Alto, Calif. (through its acquisition of Cohesion Technologies, Inc. in 2003) at collagen concentrations of 35 mg/ml and 65 mg/ml under the trademarks Zyderm.RTM. I Collagen and Zyderm II Collagen, respectively. Glutaraldehyde crosslinked atelopeptide fibrillar collagen is commercially available from Angiotech Pharmaceuticals at a collagen concentration of 35 mg/ml under the trademark Zyplast.RTM. Collagen

Collagens for use in the present invention are generally in aqueous suspension at a concentration between about 20 mg/ml to about 120 mg/ml; preferably, between about 30 mg/ml to about 90 mg/ml.

Although intact collagen is preferred, denatured collagen, commonly known as gelatin, can also be used in the compositions of the invention. Gelatin may have the added benefit of being degradable faster than collagen.

Because of its tacky consistency, nonfibrillar collagen is generally preferred for use in compositions of the invention that are intended for use as bioadhesives. The term "nonfibrillar collagen" refers to any modified or unmodified collagen material that is in substantially nonfibrillar form at pH 7, as indicated by optical clarity of an aqueous suspension of the collagen.

Collagen that is already in nonfibrillar form may be used in the compositions of the invention. As used herein, the term "nonfibrillar collagen" is intended to encompass collagen types that are nonfibrillar in native form, as well as collagens that have been chemically modified such that they are in nonfibrillar form at or around neutral pH. Collagen types that are nonfibrillar (or microfibrillar) in native form include types IV, VI, and VII.

Chemically modified collagens that are in nonfibrillar form at neutral pH include succinylated collagen and methylated collagen, both of which can be prepared according to the methods described in U.S. Pat. No. 4,164,559, issued Aug. 14, 1979, to Miyata et al., which is hereby incorporated by reference in its entirety. Due to its inherent tackiness, methylated collagen is particularly preferred for use in bioadhesive compositions, as disclosed in commonly owned U.S. Pat. No. 5,614,587.

Collagens for use in the crosslinked polymer compositions of the present invention may start out in fibrillar form, then be rendered nonfibrillar by the addition of one or more fiber disassembly agent. The fiber disassembly agent must be present in an amount sufficient to render the collagen substantially nonfibrillar at pH 7, as described above. Fiber disassembly agents for use in the present invention include, without limitation, various biocompatible alcohols, amino acids, inorganic salts, and carbohydrates, with biocompatible alcohols being-particularly preferred. Preferred biocompatible alcohols include glycerol and propylene glycol. Non-biocompatible alcohols, such as ethanol, methanol, and isopropanol, are not preferred for use in the present invention, due to their potentially deleterious effects on the body of the patient receiving them. Preferred amino acids include arginine. Preferred inorganic salts include sodium chloride and potassium chloride. Although carbohydrates, such as various suL7ars including sucrose, may be used in the practice of the present invention, they are not as preferred as other types of fiber disassembly agents because they can have cytotoxic effects in vivo.

Because it is opaque and less tacky than nonfibrillar collagen, fibrillar collagen is less preferred for use in bioadhesive compositions. However, as disclosed in commonly owned U.S. Pat. No. 5,614,587, fibrillar collagen, or mixtures of nonfibrillar and fibrillar collagen, may be preferred for use in adhesive compositions intended for long-term persistence in vivo, if optical clarity is not a requirement.

For compositions intended for use in tissue augmentation, fibrillar collagen is preferred because it tends to form stronger crosslinked gels having greater long-term persistency in vivo than those prepared using nonfibrillar collagen.

In general, the collagen is added to the first synthetic polymer, then the collagen and first synthetic polymer are mixed thoroughly to achieve a homogeneous composition. The second synthetic polymer is then added and mixed into the collagen/first synthetic polymer mixture, where it will covalently bind to primary amino groups or thiol groups on the first synthetic polymer and primary amino groups on the collagen, resulting in the formation of a homogeneous crosslinked network. Various deacetylated and/or desulfated glycosaminoglycan derivatives can be incorporated into the composition in a similar manner as that described above for collagen.

For use in tissue adhesion as discussed below, it may also be desirable to incorporate proteins such as albumin, fibrin or fibrinogen into the crosslinked polymer composition to promote cellular adhesion.

In addition, the introduction of hydrocolloids such as carboxymethylcellulose may promote tissue adhesion and/or swellability.

Administration of the Crosslinked Synthetic Polymer Compositions

The compositions of the present invention may be administered before, during or after crosslinking of the first and second synthetic polymer. Certain uses, which are discussed in greater detail below, such as tissue augmentation, may require the compositions to be crosslinked before administration, whereas other applications, such as tissue adhesion, require the compositions to be administered before crosslinking has reached "equilibrium." The point at which crosslinking has reached equilibrium is defined herein as the point at which the composition no longer feels tacky or sticky to the touch.

In order to administer the composition prior to crosslinking, the first synthetic polymer and second synthetic polymer may be contained within separate barrels of a dual-compartment syringe. In this case, the two synthetic polymers do not actually mix until the point at which the two polymers are extruded from the tip of the syringe needle into the patient's tissue. This allows the vast majority of the crosslinking reaction to occur in situ, avoiding the problem of needle blockage which commonly occurs if the two synthetic polymers are mixed too early and crosslinking between the two components is already too advanced prior to delivery from the syringe needle. The use of a dual-compartment syringe, as described above, allows for the use of smaller diameter needles, which is advantageous when performing soft tissue augmentation in delicate facial tissue, such as that surrounding the eyes.

Alternatively, the first synthetic polymer and second synthetic polymer may be mixed according to the methods described above prior to delivery to the tissue site, then injected to the desired tissue site immediately (preferably, within about 60 seconds) following mixing.

In another embodiment of the invention, the first synthetic polymer and second synthetic polymer are mixed, then extruded and allowed to crosslink into a sheet or other solid form. The crosslinked solid is then dehydrated to remove substantially all unbound water. The resulting dried solid may be ground or comminuted into particulates, then suspended in a nonaqueous fluid carrier, including, without limitation, hyaluronic acid, dextran sulfate, dextran, succinylated noncrosslinked collagen, methylated noncrosslinked collagen, glycogen, glycerol, dextrose, maltose, triglycerides of fatty acids (such as corn oil, soybean oil, and sesame oil), and egg yolk phospholipid. The suspension of particulates can be injected through a small-gauge needle to a tissue site. Once inside the tissue, the crosslinked polymer particulates will rehydrate and swell in size at least five-fold.

Use of Crosslinked Synthetic Polymers to Deliver Charged Compounds

By varying the relative molar amounts of the first synthetic polymer and the second synthetic polymer, it is possible to alter the net charge of the resulting crosslinked polymer composition, in order to prepare a matrix for the delivery of a charged compound (such as a protein or drug). As such, the delivery of charged proteins or drugs, which would normally diffuse rapidly out of a neutral carrier matrix, can be controlled.

For example, if a molar excess of a first synthetic polymer containing multiple nucleophilic groups is used, the resulting matrix has a net positive charge and can be used to ionically bind and deliver negatively charged compounds. Examples of negatively charged compounds that can be delivered from these matrices include various drugs, cells, proteins, and polysaccharides. Negatively charged collagens, such as succinylated collagen, and glycosaminoglycan derivatives, such as sodium hyaluronate, keratan sulfate, keratosulfate, sodium chondroitin sulfate A, sodium dermatan sulfate B, sodium chondroitin sulfate C, heparin, esterified chondroitin sulfate C, and esterified heparin, can be effectively incorporated into the crosslinked polymer matrix as described above.

If a molar excess of a second synthetic polymer containing multiple electrophilic groups is used, the resulting matrix has a net negative charge and can be used to ionically bind and deliver positively charged compounds. Examples of positively charged compounds that can be delivered from these matrices include various drugs, cells, proteins, and polysaccharides. Positively charged collagens, such as methylated collagen, and glycosaminoglycan derivatives, such as esterified deacetylated hyaluronic acid, esterified deacetylated desulfated chondroitin sulfate A, esterified deacetylated desulfated chondroitin sulfate C, deacetylated desulfated keratan sulfate, deacetylated desulfated keratosulfate, esterified desulfated heparin, and chitosan, can be effectively incorporated into the crosslinked polymer matrix as described above.

Use of Crosslinked Synthetic Polymers to Deliver Biologically Active Agents

The crosslinked polymer compositions of the present invention may also be used for localized delivery of various drugs and other biologically active agents. Biologically active agents such as growth factors may be delivered from the composition to a local tissue site in order to facilitate tissue healing and regeneration.

The term "biologically active agent" or "active agent" as used herein refers to organic molecules which exert biological effects in vivo. Examples of active agents include, without limitation, enzymes, receptor antagonists or agonists, hormones, growth factors, autogenous bone marrow, antibiotics, antimicrobial agents and antibodies. The term "active agent" is also intended to encompass various cell types and genes which can be incorporated into the compositions of the invention. The term "active agent" is also intended to encompass combinations or mixtures of two or more active agents, as defined above.

Preferred active agents for use in the compositions of the present invention include growth factors, such as transforming growth factors (TGFs), fibroblast growth factors (FGFs), platelet derived growth factors (PDGFs), epidermal growth factors (EGFs), connective tissue activated peptides (CTAPs), osteogenic factors, and biologically active analogs, fragments, and derivatives of such growth factors. Members of the transforming growth factor (TGF) supergene family, which are multifunctional regulatory proteins, are particularly preferred. Members of the TGF supergene family include the beta transforming growth factors (for example, TGF-.beta.1, TGF-.beta.2, TGF-.beta.3); bone morphogenetic proteins (for example, BMP-1, BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, BMP-7, BMP-8, BMP-9); heparin-binding growth factors (for example, fibroblast growth factor (FGF), epidermal growth factor (EGF), platelet-derived growth factor (PDGF), insulin-like growth factor (IGF)); Inhibins (for example, Inhibin A, Inhibin B); growth differentiating factors (for example, GDF-1); and Activins (for example, Activin A, Activin B, Activin AB).

Growth factors can be isolated from native or natural sources, such as from mammalian cells, or can be prepared synthetically, such as by recombinant DNA techniques or by various chemical processes. In addition, analogs, fragments, or derivatives of these factors can be used, provided that they exhibit at least some of the biological activity of the native molecule. For example, analogs can be prepared by expression of genes altered by site-specific mutagenesis or other genetic engineering techniques.

Biologically active agents may be incorporated into the crosslinked synthetic polymer composition by admixture. Alternatively, the agents may be incorporated into the crosslinked polymer matrix, as described above, by binding these agents with the functional groups on the synthetic polymers. Processes for covalently binding biologically active agents such as growth factors using functionally activated polyethylene glycols are described in commonly assigned U.S. Pat. No. 5,162,430, issued Nov. 10, 1992, to Rhee et al. Such compositions preferably include linkages that can be easily biodegraded, for example as a result of enzymatic degradation, resulting in the release of the active agent into the target tissue, where it will exert its desired therapeutic effect.

A simple method for incorporating biologically active agents containing nucleophilic groups into the crosslinked polymer composition involves mixing the active agent with the first synthetic polymer (or first synthetic polymer/collagen mixture) prior to adding the second synthetic polymer. This procedure will result in covalent binding of the active agent to the crosslinked polymer composition, producing a highly effective sustained release composition.

The type and amount of active agent used will depend, among other factors, on the particular site and condition to be treated and the biological activity and pharmacokinetics of the active agent selected.

Use of Crosslinked Synthetic Polymers to Deliver Cells or Genes

The crosslinked polymer compositions of the present invention can also be used to deliver various types of living cells or genes to a desired site-of administration in order to form new tissue. The term "genes" as used herein is intended to encompass genetic material from natural sources, synthetic nucleic acids, DNA, antisense-DNA and RNA.

When used to deliver cells, for example, mesenchymal stem cells can be delivered to produce cells of the same type as the tissue into which they are delivered. Mesenchymal stem cells are not differentiated and therefore can. differentiate to form various types of new cells due to the presence of an active agent or the effects (chemical, physical, etc.) of the local tissue environment. Examples of mesenchymal stem cells include osteoblasts, chondrocytes, and fibroblasts. Osteoblasts can be delivered to the site of a bone defect to produce new bone; chondrocytes can be delivered to the site of a cartilage defect to produce new cartilage; fibroblasts can be delivered to produce collagen wherever new connective tissue is needed; neurectodermal cells can be delivered to form new nerve tissue; epithelial cells can be delivered to form new epithelial tissues, such as liver, pancreas, etc.

The cells or genes may be either allogeneic or xenogeneic in origin. For example, the compositions can be used to deliver cells or genes from other species which have been genetically modified. Because the compositions of the invention are not easily degraded in vivo, cells and genes entrapped within the, crosslinked polymer compositions will be isolated from the patient's own cells and, as such, will not provoke an immune response in the patient. In order to entrap the cells or genes within a crosslinked polymer matrix, the first polymer and the cells or genes may be pre-mixed, then the second polymer is mixed into the first polymer/cell or gene mixture to form a crosslinked matrix, thereby entrapping the cells or genes within the matrix.

As discussed above for biologically active agents, when used to deliver cells or genes, the synthetic polymers preferably also contain biodegradable groups to aid in controlled release of the cells or genes at the intended site of delivery.

Use of the Crosslinked Synthetic Polymers as Bioadhesives

We have found that the preferred compositions of the invention tend to have unusually high tackiness, making them particularly suitable for use as bioadhesives, for example, for use in surgery. As used herein, the terms "bioadhesive," "biological adhesive," and "surgical adhesive" are used interchangeably to refer to biocompatible compositions capable of effecting temporary or permanent attachment between the surfaces of two native tissues, or between a native tissue surface and a non-native tissue surface or a surface of a synthetic implant.

In a general method for effecting the attachment of a first surface to a second surface, the first synthetic polymer and the second synthetic polymer are applied to a first surface, then the first surface is contacted with a second surface to effect adhesion between the first surface and the second surface. Preferably, the first synthetic polymer and second synthetic polymer are first mixed to initiate crosslinking, then delivered to a first surface before substantial crosslinking has occurred between the nucleophilic groups on the first synthetic polymer and the electrophilic groups on the second synthetic polymer. The first surface is then contacted with the second surface, preferably immediately, to effect adhesion between the two surfaces. At least one of the first and second surfaces is preferably a native tissue surface.

For example, the first synthetic polymer and second synthetic polymer are generally provided in separate syringes, the contents of which are then mixed together using syringe-to-syringe mixing techniques just prior to delivery to a first surface. The first synthetic polymer and second synthetic polymer are preferably mixed for a minimum of 20 (preferably 20 to 100, more preferably 30 to 60) passes to ensure adequate mixing. As crosslinking between the corresponding reactive groups on the two synthetic polymers is generally initiated during the mixing process, it is important to deliver the reaction mixture to the first surface as soon as possible after mixing.

The reaction mixture can be extruded onto the first surface from the opening of a syringe or other appropriate extrusion device. Following application, the extruded reaction mixture can be spread over the first surface using a spatula, if necessary. Alternatively, the first synthetic polymer and the second synthetic polymer can be mixed together in an appropriate mixing dish or vessel, then applied to the first surface using a spatula.

In another method for preparing the reaction mixture, the first synthetic polymer and second synthetic polymer are contained in separate chambers of a spray can or bottle with a nozzle, or other appropriate spraying device. In this scenario, the first and second polymers do not actually mix until they are expelled together from the nozzle of the spraying device. Following application of the reaction mixture to a surface containing collagen, the first surface is contacted with a second surface. If the two surfaces are contacted before substantial crosslinking has occurred between the synthetic polymer and the crosslinking agent, the reactive groups on the crosslinking agent will also covalently bond with primary amino groups on lysine residues of collagen molecules present on either or both of the surfaces, providing improved adhesion.

The two surfaces may be held together manually, or using other appropriate means, while the crosslinking reaction is proceeding to completion. Crosslinking is typically complete within 5 to 60 minutes after mixing of the first and second synthetic polymers. However, the time required for complete crosslinking to occur is dependent on a number of factors, including the types and molecular weights of the two synthetic polymers and, most particularly, the concentrations of the two synthetic polymers (i.e., higher concentrations result in faster crosslinking times).

At least one of the first and second surfaces is preferably a native tissue surface. As used herein, the term "native tissue" refers to biological tissues that are native to the body of the specific patient being treated. As used herein, the term "native tissue" is intended to include biological tissues that have been elevated or removed from one part of the body of a patient for implantation to another part of the body of the same patient (such as bone autografts, skin flap autografts, etc.). For example, the compositions of the invention can be used to adhere a piece of skin from one part of a patient's body to another part of the body, as in the case of a burn victim.

The other surface may be a native tissue surface, a non-native tissue surface, or a surface of a synthetic implant. As used herein, the term "non-native tissue" refers to biological tissues that have been removed from the body of a donor patient (who may be of the same species or of a different species than the recipient patient) for implantation into the body of a recipient patient (e.g., tissue and organ transplants). For example, the crosslinked polymer compositions of the present invention can be used to adhere a donor cornea to the eye of a recipient patient.

As used herein, the term "synthetic implant" refers to any biocompatible material intended for implantation into the body of a patient not encompassed by the above definitions for native tissue and non-native tissue. Synthetic implants include, for example, artificial blood vessels, heart valves, artificial organs, bone prostheses, implantable lenticules, vascular grafts, stents, and stent/graft combinations, etc.

Use of Crosslinked Synthetic Polymers in Ophthalmic Applications

Because of their optical clarity, the crosslinked polymer compositions of the invention which do not contain collagen are particularly well suited for use in ophthalmic applications. For example, a synthetic lenticule for correction of vision can be attached to the Bowman's layer of the cornea of a patient's eye using the methods of the present invention. As disclosed in commonly assigned, allowed U.S. application Ser. No. 08/147,227, filed Nov. 3, 1993, by Rhee et al., now U.S. Pat. No. 5,565,519, a chemically modified collagen (such as succinylated or methylated collagen) which is in substantially nonfibrillar form at pH 7 can be crosslinked using a synthetic hydrophilic polymer, then molded into a desired lenticular shape and allowed to complete crosslinking. The resulting crosslinked collagen lenticule can then be attached to the Bowman's layer of a de-epithelialized cornea of a patient's eye using the methods of the present invention. By applying the reaction mixture comprising the first and second synthetic polymers to the anterior surface of the cornea, then contacting the anterior surface of the cornea with the posterior surface of the lenticule before substantial crosslinking has occurred, electrophilic groups on the second synthetic polymer will also covalently bind with collagen molecules in both the corneal tissue and the lenticule to firmly anchor the lenticule in place. (Alternatively, the reaction mixture can be applied first to the posterior surface of the lenticule, which is then contacted with the anterior surface of the cornea.)

The compositions of the present invention are also suitable for use in vitreous replacement.

Use of Crosslinked Synthetic Polymer Compositions in Tissue Augmentation

The crosslinked polymer compositions of the invention can also be used for augmentation of soft or hard tissue within the body of a mammalian subject. As such, they may be better than currently marketed collagen-based materials product for soft tissue augmentation, because they are less immunogenic and more persistent. Examples of soft tissue augmentation applications include sphincter (e.g., urinary, anal, esophageal) sphincter augmentation and the treatment of rhytids and scars. Examples of hard tissue augmentation applications include the repair and/or replacement of bone and/or cartilaginous tissue.

The compositions of the invention are particularly suited for use as a replacement material for synovial fluid in osteoarthritic joints, where the crosslinked polymer compositions serve to reduce joint pain and improve joint function by restoring a soft hydrogel network in the joint. The crosslinked polymer compositions can also be used as a replacement material for the nucleus pulposus of a damaged intervertebral disk. As such, the nucleus pulposus of the damaged disk is first removed, then the crosslinked polymer composition is injected or otherwise introduced into the center of the disk. The composition may either be crosslinked prior to introduction into the disk, or allowed to crosslink in situ.

In a general method for effecting augmentation of tissue within the body of a mammalian subject, the first and second synthetic polymers are injected simultaneously to a tissue site in need of augmentation through a small-gauge (e.g., 25-32 gauge) needle. Once inside the patient's body, the nucleophilic groups on the first synthetic polymer and the electrophilic groups on the second synthetic polymer will react with each other to form a crosslinked polymer network in situ. Electrophilic groups on the second synthetic polymer may also react with primary amino groups on lysine residues of collagen molecules within the patient's own tissue, providing for "biological anchoring" of the compositions with the host tissue.

Use of the Crosslinked Synthetic Polymer Compositions to Prevent Adhesions

Another use of the crosslinked polymer compositions of the invention is to coat tissues in order to prevent the formation of adhesions following surgery or injury to internal tissues or organs. In a general method for coating tissues to prevent the formation of adhesions following surgery, the first and second synthetic polymers are mixed, then a thin layer of the reaction mixture is applied to the tissues comprising, surrounding, and/or adjacent to the surgical site before substantial crosslinking has occurred between the nucleophilic groups on the first synthetic polymer and the electrophilic groups on the second synthetic polymer. Application of the reaction mixture to the tissue site may be by extrusion, brushing, spraying (as described above), or by any other convenient means.

Following application of the reaction mixture to the surgical site, crosslinking is allowed to continue in situ prior to closure of the surgical incision. Once crosslinking has reached equilibrium, tissues which are brought into contact with the coated tissues will not stick to the coated tissues. At this point in time, the surgical site can be closed using conventional means (sutures, etc.).

In general, compositions that achieve complete crosslinking within a relatively short period of time (i.e., 5-15 minutes following mixture of the first synthetic polymer and the second synthetic polymer) are preferred for use in the prevention of surgical adhesions, so that the surgical site may be closed relatively soon after completion of the surgical procedure.

Use of the Crosslinked Synthetic Polymers to Coat Implants

Another use of the crosslinked polymer compositions of the invention is as a coating material for synthetic implants. In a general method for coating a surface of a synthetic implant, the first and second synthetic polymers are mixed, then a thin layer of the reaction mixture is applied to a surface of the implant before substantial crosslinking has occurred between the nucleophilic groups on the first synthetic polymer and the electrophilic groups on the second synthetic polymer. In order to minimize cellular and fibrous reaction to the coated implant, the reaction mixture is preferably prepared to have a net neutral charge. Application of the reaction mixture to the implant surface may be by extrusion, brushing, spraying (as described above), or by any other convenient means. Following application of the reaction mixture to the implant surface, crosslinking is allowed to continue until complete crosslinking has been achieved.

Although this method can be used to coat the surface of any type of synthetic implant, it is particularly useful for implants where reduced thrombogenicity is an important consideration, such as artificial blood vessels and heart valves, vascular grafts, vascular stents, and stent/graft combinations. The method may also be used to coat implantable surgical membranes (e.g., monofilament polypropylene) or meshes (e.g., for use in hernia repair). Breast implants may also be coated using the above method in order to minimize capsular contracture.

The compositions of the present invention may also be used to coat lenticules, which are made from either naturally occurring or synthetic polymers.

Use of the Crosslinked Synthetic Polymers--To Treat Aneurism

The crosslinked polymer compositions of the invention can be extruded or molded in the shape of a string or coil, then dehydrated. The resulting dehydrated string or coil can be delivered via catheter to the site of a vascular malformation, such as an aneurysm, for the purpose of vascular occlusion and, ultimately, repair of the malformation. The dehydrated string or coil can be delivered in a compact size and will rehydrate inside the blood vessel, swelling several times in size compared to its dehydrated state, while maintaining its original shape.

Other Uses for the Crosslinked Synthetic Polymers

As discussed in commonly assigned, U.S. application Ser. No. 08/574,050, filed Dec. 18, 1995, now U.S. Pat. No. 5,752,974, which is incorporated herein by reference, the crosslinked polymer compositions of the invention can be used to block or fill various lumens and voids in the body of a mammalian subject. The compositions can also be used as biosealants to seal fissures or crevices within a tissue or structure (such as a vessel), or junctures between adjacent tissues or structures, to prevent leakage of blood or other biological fluids.

The crosslinked polymer compositions can also be used as a large space-filling device for organ displacement in a body cavity during surgical or radiation procedures, for example, to protect the intestines during a planned course of radiation to the pelvis.

The crosslinked polymer compositions of the invention can also be coated onto the interior surface of a physiological lumen, such as a blood vessel or Fallopian tube, thereby serving as a sealant to prevent restenosis of the lumen following medical treatment, such as, for example, balloon catheterization to remove arterial plaque deposits from the interior surface of a blood vessel, or removal of scar tissue or endometrial tissue from the interior of a Fallopian tube. A thin layer of the reaction mixture is preferably applied to the interior surface of the vessel (for example, via catheter) immediately following mixing of the first and second synthetic polymers. Because the compositions of the invention are not readily degradable in vivo, the potential for restenosis due to degradation of the coating is minimized. The use of crosslinked polymer compositions having a net neutral charge further minimizes the potential for restenosis.
 

Claim 1 of 40 Claims

1. A method for augmenting soft or hard tissue within a mammalian body, comprising: (a) providing a first crosslinkable component, wherein the first crosslinkable component is a synthetic polylysine; (b) providing a second crosslinkable component, wherein the second crosslinkable component is poly(alkylene oxide) having n electrophilic groups capable of reaction with the synthetic polylysine to form covalent bonds, wherein n is 2, 3 or 4, and each electrophilic group is independently succinimidyl ester, succinimidyl carbonate, sulfosuccinimidyl ester, maleimido, epoxy, isocyanato, thioisocyanato, or ethenesulfonyl; (c) applying the first and second crosslinkable components to the tissue; and (d) allowing the first and second crosslinkable components to crosslink in situ, wherein the first and second crosslinkable components are biocompatible, synthetic, and nonimmunogenic.

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