WO2003086290A2

WO2003086290A2 - Electroprocessing of materials useful in drug delivery and cell encapsulation

Info

Publication number: WO2003086290A2
Application number: PCT/US2003/010806
Authority: WO
Inventors: Gary E. Wnek; David G. Simpson; Gary L. Bowlin; Li Yao; El-Refaie Kenawy; John M. Layman; Elliot H. Sanders; John Fenn
Original assignee: Virginia Commonwealth University Intellectual Property Foundation
Priority date: 2002-04-05
Filing date: 2003-04-07
Publication date: 2003-10-23
Also published as: AU2003223513A8; WO2003086290A3; AU2003223513A1

Abstract

The invention is directed to novel compositions comprising an electroprocessed material and a substance, their formation and use. The electroprocessed material can, for example, be one or more natural materials, one or more synthetic materials, or a combination thereof. The substance can be one or more therapeutic or cosmetic substances or other compounds, molecules, cells, vesicles. The compositions can be used in substance delivery, including drug delivery within an organism by, for example, releasing substances or containing cells that release substances. The compositions can be used for other purposes, such as prostheses or similar implants.

Description

ELECTROPROCESSING OF MATERIALS USEFUL IN DRUG DELIVERY

AND CELL ENCAPSULATION

FIELD OF THE INVENTION

The present invention relates to novel compositions comprising electroprocessed materials with substances, and methods of making and using these compositions in delivery of substances.

BACKGROUND OF THE INVENTION Numerous methods exist for delivering substances to desired locations in vivo or in vitro.

One such method uses devices or objects that contain a substance and will release the substance within a desired location. One desirable application for such methods is the administration of such objects to a location within the body of an organism, followed by the subsequent release of the desired substance into the body. In these examples, the implant often contains the substance and a carrier. After implantation, the substance is released by a variety of means including, for example, diffusion from an implant or dissolution or other degradation of a capsule coat.

Biocompatibility is a desirable attribute in compositions designed for substance delivery. With surgical and subdermal implants, for example, the substance to be delivered is often contained in a matrix comprised of synthetic polymers. Where natural products are used in making bandages, the products typically comprise wood products such as cellulose or other materials that are not readily absorbed by the body of the recipient. Accordingly, such bandages must eventually be removed. Implants compressed from natural materials that may be absorbed by the body are one way to improve biocompatibility and is one area in which improvements are desired. There is also a continuing need for greater versatility and flexibility in substance delivery technology. Additional techniques for controlling release kinetics and spatial patterns of release or delivery are examples of developments that can improve substance delivery. Implants in which there is refined control of structure at the microscopic or molecular level and overall implant shape are also desired. Such methods could allow, for example, further refinements in control of pore size or other attributes that affect diffusion in and out of a matrix, or more refined control of the distribution of a substance within a matrix. New methods that allow encapsulation of living cells within a matrix are especially desired. Such methods would allow implants to contain, for example, cells that produced desired substances, cells that promote tissue growth, or cells that serve both of these functions. What is needed therefore are new compositions for use in drug delivery that provide additional and improved methods of controlling configuration of drug delivery systems. Compositions with improved biocompatibility compared to those currently used in substance delivery and/or that can contain living cells are also needed. What is further needed are new methods of substance delivery using such compositions. Finally, methods for making such compositions are also needed.

SUMMARY OF THE INVENTION

The present invention seeks to overcome the limitations in the prior art by providing compositions comprising an electroprocessed material and a substance. The substance may be the material itself, or another substance which may be delivered with the electroprocessed material to a desired site. Sometimes the compositions comprising an electroprocessed material and a substance are in the form of a matrix. The electroprocessed materials include any natural or non- natural materials or blends thereof. The substance is released from the composition or causes the release of molecules or compounds from the composition. Substance release can occur in vitro, in vivo, or both.

The present invention also includes a method for delivery of substances to a location using the present compositions comprising an electroprocessed material and a substance. The locations can be in vitro, in vivo, or both. The invention also includes methods for making the compositions of the present invention.

The compositions of the present invention include an electroprocessed material and a substance. The material can include naturally occurring materials, synthetically manufactured materials, or combinations thereof. Naturally occurring materials include natural organic or inorganic materials, genetically engineered materials and include synthetic alterations thereof. Synthetic materials include materials prepared through any method of artificial synthesis, processing, or manufacture. The invention includes materials that degrade and can absorbed by the body, or will persist in whole or in part and become portions of an extracellular tissue matrix. The compositions may be made using any electroprocessing technique, including but not limited to electrospinning, electroaerosol, electrospraying or electrosputtering techniques, or any combination thereof. Accordingly, electroprocessed droplets, particles, fibers, fibrils, or combinations thereof are all included in the compositions of the present invention. In a preferred embodiment, the electroprocessed materials form a matrix, and in some cases are similar to an extracellular matrix. Matrices may also be formed from materials that can combine to form another material, such as precursor materials. For example, fibrinogen, when combined with thrombin, will form fibrin. Any material that may be electroprocessed may be used to form an electroprocessed material to be combined, either before, during or after electroprocessing, with a substance, to form the compositions of the present invention. The compositions of the present invention contain one or more substances. The substance includes any type of substance desired, with examples including molecules, cells, objects, or combinations thereof. In some cases, the substance is the electroprocessed material itself. Molecules can be any size, complexity, or type, including both organic or inorganic molecules as well as any combination of molecules. Molecules include naturally occurring and synthetic molecules. Examples of molecules include, but are not limited to therapeutics, cosmetics, nutraceuticals, vitamins, minerals, humectants, molecules produced by cells, including normal cells, abnormal cells, genetically engineered cells and cells modified through any other process. Both eukaryotic and prokaryotic cells are included in the category of substances. Substances also include, without limitation, antigens, antimicrobials, antifungals, molecules that can cause a cellular or physiological response, metals, gases, minerals, ions, and electrically, magnetically and electromagnetically (i.e., light) reactive materials. Cells are derived from natural sources or are cultured in vitro. Combinations of different types or categories of cells can be used. Examples of objects include, but are not limited to, cell fragments, cell debris, organelles and other cellular components, tablets, viruses, vesicles, liposomes, capsules, and other structures that serve as an enclosure for molecules. It is to be understood that the composition of the present invention comprises at least one substance. Accordingly, numerous substances or combinations of similar or different substances may be combined with the electroprocessed material. The substances may be combined with the electroprocessed material through electroprocessing techniques or through other techniques. The invention also includes embodiments in which the composition comprises electroprocessed matrix materials without an additional substance. In that embodiment, the electroprocessed matrix materials may act as a substance.

The invention provides numerous uses for the compositions of the present invention. One preferred use is the delivery of substances. Substance delivery from the compositions of the present invention can occur in vivo, for example upon or within the body of a human or animal. Substance delivery can also occur in vitro, for example within a cell culture apparatus or well. Substances delivered include those substances contained within the compositions, other substances produced by the substance contained in the composition, or both. For example, a substance may be a cell contained within the electroprocessed material, and the cell may synthesize and release one or more molecules. Cells may release molecules in response to signals, so that the molecules are released in a specific desired circumstance. For example, an inducible promoter in an engineered cell within an electroprocessed material may be used to stimulate the expression and or release of a growth factor.

The compositions of the present invention are versatile with respect to control of substance release from the compositions. Release kinetics of substances can be controlled by manipulating a wide variety of matrix parameters. In various embodiments, the release rate, onset of release, release of more than one compound either at the same or different times, creation of gradients of release and spatial patterns of release may be manipulated. Compositions that contain electrical or magnetic materials can be influenced to move, cause motion, or produce a biological activity by applying an electric current or a magnetic field to the composition located on or within a body, or in vitro. Electroprocessed compositions that contain light sensitive components may be designed. These compositions may move or be induced to release or bind substances in response to specific wavelengths of light. Compositions containing nucleic acids or genetically engineered cells, for example, can be used in gene therapy. Other examples include embodiments used in wound care, tissue or organ replacements, and prostheses. In some embodiments, the electroprocessed material itself contains desired properties of substances, and acts as a substance without addition of another substance. The invention thus includes a wide variety of methods of using the compositions of the present invention in medical, veterinary, agricultural, research and other applications. The compositions of the present invention provide safer and more predictable release of substances and provide a major advance in the field of substance delivery, especially drug delivery. In some embodiments, the materials are electroprocessed from a suspension containing multiple phases. These materials possess cavities, pockets, inclusions, or enclosures that contain phases that are immiscible with the electroprocessed material and that contain substances such as compounds or cells. In some such embodiments, the substances are present in much higher amounts than they could be present in electroprocessed materials without the multiple phases. In some such embodiments, the electroprocessed materials or the cavities, pockets, inclusions, or enclosures within them also contain substances that will aid in the release of substances from the electroprocessed materials. In some embodiments, the electroprocessed materials are derivatized with substances prior to electroprocessing.

The invention also includes methods for making the compositions of the present invention using any type of electroprocessing technique, combination of electroprocessing techniques, or a combination of an electroprocessing technique and another technique, such as aerosol techniques. The method includes streaming, spraying, dropping or projecting one or more solutions, fibers, or suspensions comprising the materials to be electroprocessed toward a target under conditions effective to deposit the materials on a substrate. The substances to be combined with the electroprocessed materials may be electroprocessed toward the target either before, during or after electroprocessing the material. In this manner, the substance may be incorporated within the electroprocessed material during formation, or may coat the electroprocessed material. Accordingly, one or a plurality of sources of materials and substances is used to provide the ingredients for the electroprocessed composition of the present invention. For example, collagen and a polymer such as poly glycolic acid may be electroprocessed through any combination of electrospinning and electrospraying from two sources. At the same time or at selected times thereafter, substances may be provided from other sources: for example, a third source provides a growth factor, a fourth source provides an anti-angiogenic factor, and a fifth source provides genetically altered fibroblasts. These sources of substances may provide the substances through one or more electroprocessing techniques, such as electrospin, electrospray, electroaerosol, electrosputter or any combination thereof. These sources may also provide the substances to the electroprocessed material through non-electroprocessing techniques, such as aerosol delivery, dripping, coating, soaking or other techniques.

In one preferred embodiment, the compositions of the present invention comprise one or more electroprocessed materials that form a matrix combined with at least one substance. Either the source or target is charged, and the other is grounded. The substrate upon which electrodeposition occurs can be the target itself or another object of any shape or type. For example, the substrate can be an object disposed between the orifice and the target. In one embodiment, the substrate is a location on or within an organism, such as a tissue, a wound site, a desired location for substance delivery, or a surgical field in which the composition is to be applied . By manipulating process parameters, compositions of the present invention can be manufactured with a predetermined shape, for example, for depositing the material onto or into a molded substrate. Substrate shape can be manipulated to achieve a specific three-dimensional structure. Targets can also be rotated or otherwise moved or manipulated during electroprocessing to control distribution of the electroprocessed material and, in embodiments involving electroprocessed fibers, the orientation of the fibers. Substances included in the composition can be combined with the matrix material by any means before, during, and/or after electrodeposition.

In some embodiments, the substances are present in the solutions to be electroprocessed during electroprocesssing. Substances are dissolved or suspended along with the materials or present in a separate phase from the materials in an emulsion, dispersion or suspension containing two or more phases. In some embodiments, processing aids are combined with the solvents during electroprocessing. The processing aids perform functions such as facilitating the formation of electrospun fibers, allowing the formation of a suspension having multiple phases, or controlling the moφhology of resulting fibers. In some embodiments electroprocessing is aided by heating a material in a solvent or solvent combination in which it does not normally dissolve at room temperature.

The invention also includes methods for controlling the rate at which electroprocessed materials dissolve or degrade after formation, including, but not limited to, dissolution in vitro. The electroprocessed compositions may be formed into any desired shape. For puφoses of substance delivery, the desired shape is dictated by the application. Non-limiting examples include the following: in the form of a patch for application to the skin; in the form of a wafer or tablet for ingestion; in the form of a wafer for application to a site of removal of a glioma; in the form of a wrap to surround a tumor; in a particulate form for spraying on a surgical site; and in a particulate form for delivery of substances through inhalation.

Accordingly, it is an object of the present invention to overcome the foregoing limitations and drawbacks by providing compositions comprising an electroprocessed material and a substance.

Another object of the present invention is to provide compositions comprising an electroprocessed natural material and a substance.

Yet another object of the present invention is to provide compositions comprising an electroprocessed synthetic material and a substance.

Still another object of the present invention is to provide compositions comprising blends of an electroprocessed natural material, an electroprocessed synthetic material and a substance. Another object of the present invention is to provide compositions comprising an electroprocessed synthetic material and a substance.

It is an object of the present invention to provide compositions comprising an electroprocessed material and a substance, wherein the substances comprises comprising cells.

Another object of the present invention is to provide compositions comprising an electroprocessed material and a substance, wherein the substance comprises an object.

Still another object of the present invention is to provide compositions comprising an electroprocessed material and a substance, wherein the substance comprises a molecule.

Yet another object of the present invention is to provide compositions comprising an electroprocessed material and a substance, wherein the substance comprises a therapeutic molecule.

Another object of the present invention is to provide compositions comprising an electroprocessed material and substances comprising combinations of cells, molecules, and/or objects.

Another object of the present invention is to provide methods for delivery of a substance to a location, comprising placing the composition of the present invention at a desired location. Still another object of the present invention is to provide methods for delivery of substances to a location inside or upon the body of a human or animal.

Yet another object of the present invention is to provide methods for retrieval of substances from a location inside or upon the body of a human or animal by bonding such substances.

Yet another object of the present invention is to provide methods for delivery or retrieval of substances to in vitro locations.

Another object of the present invention is to provide methods for delivery of drugs in vivo.

Yet another object of the present invention is to provide methods of administering gene and or peptide therapy.

Another object of the present invention is to provide methods of protein or peptide therapy.

Still another object of the present invention is to provide methods of administering tissue and organ replacements and prostheses. Another object of the present invention is to provide methods for making the compositions of the present inventions.

Yet another object of the present invention is to provide a method for electroprocessing materials from solutions that have one or more liquid phase suspended, dispersed, or emulsified within another liquid phase. Another object of the present invention is to provide methods using preheating followed by cooling to allow electroprocessing of materials at temperatures at which they normally cannot be processed.

Yet another object of the present invention is to provide electroprocessed derivatized materials and methods for electroprocessing derivatized materials. Still another object of the present invention is to provide methods for electroprocessing materials using processing aids to manipulate fiber moφhology.

Another object of the present invention is to provide electroprocessed materials with desired rates at which electroprocessed materials dissolve or degrade after formation, including, but not limited to, dissolution in vitro, as well as methods for making such materials.. These and other objects, features and advantages of the present invention will become apparent after a review of the following detailed description of the disclosed embodiments and the appended drawings. BRIEF DESCRIPTION OF THE DRAWINGS

Figure 1 is a schematic drawing of an embodiment of an electroprocessing device including the electroprocessing equipment and a rotating wall bioreactor.

Figure 2 is a schematic drawing of an embodiment of an electroprocessing device including the electroprocessing equipment and a rotating wall bioreactor.

Figure 3 is a graph showing the release profile of vascular endothelial growth factor (VEGF) from one embodiment of the present invention obtained by electrospinning a solution comprising collagen, polylactic acid (PLA), polyglycolic acid (PGA), and VEGF.

Figure 4 is a graph showing the release profile of VEGF from an embodiment of the present invention obtained by electrospinning a solution comprising collagen, polylactic acid, and polyglycolic acid, and VEGF and subsequently cross-linking the electroprocessed material by exposure to glutaraldehyde vapor.

Figure 5 is a graph showing the release profile of tetracycline from several embodiments of the present invention obtained by electrospinning solutions containing tetracycline along with PLA, poly(ethylene-co- vinyl acetate) (EVA) or a combination of PLA and poly(ethylene-co-vinyl acetate).

Figure 6 is a graph comparing the release profile of tetracycline from an embodiment of the present invention and several other compositions. The embodiment of the present invention was obtained by electrospinning a solution containing tetracycline with poly(ethylene-co-vinyl acetate). The other compositions were periodontal fibers containing 25wt% tetracycline hydrochloride and films containing tetracycline with polylactic acid, poly(ethylene-co-vinyl acetate) or a combination of polylactic acid and poly(ethylene-co- vinyl acetate).

Figure 7 is a graph showing the release profile of tetracycline from several embodiments of the present invention obtained by electrospinning solutions containing tetracycline with poly(ethylene-co-vinyl acetate).

Figure 8 is a schematic drawing of another embodiment of an electroprocessing device including the electroprocessing equipment and a rotating wall bioreactor.

Figure 9 is a photograph depicting EVOH electrospun directly onto a human hand.

Figure 10 is a micrograph showing an approximately 10 micron diameter fiber of EVA electrospun from CH₂C1₂ containing water and BSA. (CH₂Cl₂:water approximately 25:1; BSA concentration approximately 0.5g/ml.

Figure 11. is a micrograph showing an approximately 10 micron diameter fiber of EVA electrospun from CH₂C1₂ containing water and BSA after immersion in water for approximately 1 hour (CH₂Cl₂:water approximately25:l; BSA cone. Approximately 0.5g/ml). Figure 12 is a photograph showing an electrospun EVOH mat connected between glass pipettes

Figure 13 is a scanning electron micrograph picture of a mat of electrospun full hydrolyzed PVA. Figure 14 is a graph demonstrating the effect of surfactant (Triton X-100) concentration on the contact angle of 100 % hydrolyzed PVA solutions on octadecyltrichlorsilane surfaces. Electrospraying dominated in the region left of all three vertical dotted lines. In the region between the left and center dotted lines, electrospraying was still dominant but accompanied with some electrospinning. Electrospinning increased and became dominant in the region between the center line and the right line. Electrospinning was heavily dominant or occurred exclusive of electrospraying in the region to the right of dotted vertical line to the right.

Figure 15 contains scanning electron micrographs of (a) original electrospun PVA mat without any methanol treatment; (b) mat of (a) after immersion in water for lh; (c) electrospun PVA mat after soaking in methanol for 24 hours; (d) mat of (c) after 3 weeks of immersion in water.

Figure 16 contains photographs comparing electrospun 100% hydrolyzed PVA mat with and without methanol treatment in water. The methanol-treated mat had been in water for 3 weeks while the mat without methanol had been in water for 4 hours, (a) in water; (b) without methanol soaking, the wet mat loses its physical integrity, whereas the methanol-treated wet mat is elastic. Figure 17 contains graphs showing the elastic modulus (E\ in figure 17(a)) and loss modulus (E", in figure 17(b)) of electrospun PVA mats. Data is provided for dry mat without methanol treatment under ambient conditions (diamonds), dry mat after soaking in methanol for

20 h. under ambient conditions (squares), water-swollen, methanol-treated (20 h) mat (triangles).

Figure 18 is a graph depicting time release curves of low, medium, and high concentration of Bromphenol Blue (BB) and Evans Blue (EB) from electrospun ethylene co-vinyl acetate copolymer. The circles that contain an open dot are data for EB at the "low" concentration. The squares that contain an open dot are data for EB at the "medium" concentration. The triangles that contain an open dot are data for EB at the "medium" concentration. The circles that do not contain an open dot are data for BB at the "low" concentration. The squares that do not contain an open dot are data for BB at the "medium" concentration. The triangles that do not contain an open dot are data for BB at the "high" concentration. "Low," "medium," and "high" concentrations for this figure are defined in Example 14. Figure 19 is a graph depicting time release curves of bovine serum albumin (BSA) from electrospun ethylene co-vinyl acetate copolymer. The triangles are data regarding release from electrospun polymer containing 0.0239 grams of BSA per gram of EVA. The squares are data regarding release from electrospun polymer containing 0.0479 grams of BSA per gram of EVA. The circles are data regarding release from electrospun polymer containing 0.0958 grams of BSA per gram of EVA.

Figure 20 is a micrograph depicting pockets of Kluyveromyces lactis cells in aqueous reservoirs in an electrospun EVA fiber.

Figure 21 contains micrographs depicting Swelling of aqueous reservoirs in electrospun EVA fibers due to osmotic pressure, (a) time zero, (b) x minutes, (c) y minutes, (d) z minutes.

Figure 22. Micrograph depicting electrospun EVA fibers showing extensive strings of swollen microencapsulated aqueous domains..

Figure 23. Electron micrograph showing plastic deformation of capsule membrane (left). The reservoir on the right underwent a more violent rupture.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The term "substance" shall be used throughout this application in its broadest definition.

The term substance includes one or more molecules, objects, or cells of any type or size, or combinations thereof. Substances can be in any form including, but not limited to solid, semisolid, wet or dry mixture, gas, solution, suspension, combinations thereof. Substances include molecules of any size and in any combination. Cells include all cell types of prokaryotic and eukaryotic cells, whether in natural state or altered by genetic engineering or any other process. Cells can be from a natural source or cultured in vitro and can be living or dead.

Combinations of different types of cells can be used. Objects can be of any size, shape, and composition that may be combined with or coupled to an electroprocessed material. Examples of objects include, but are not limited to, cell fragments, cell debris, fragments of cell walls, fragments of viral walls, organelles and other cell components, tablets, viruses, vesicles, liposomes, capsules, nanoparticulates, and other structures that serve as an enclosure for molecules. The compositions of the present invention may comprise one substance or any combination of substances.

The terms "electroprocessing" and "electrodeposition" shall be defined broadly to include all methods of electrospinning, electrospraying, electroaerosoling, and electrosputtering of materials, combinations of two or more such methods, and any other method wherein materials are streamed, sprayed, sputtered or dripped across an electric field and toward a target. The electroprocessed material can be electroprocessed from one or more grounded reservoirs in the direction of a charged substrate or from charged reservoirs toward a grounded target. "Electrospinning" means a process in which fibers are formed from a solution or melt by streaming an electrically charged solution or melt through an orifice. "Electroaerosoling" means a process in which droplets are formed from a solution or melt by streaming an electrically charged polymer solution or melt through an orifice. The term electroprocessing is not limited to the specific examples set forth herein, and it includes any means of using an electrical field for depositing a material on a target.

The term "material" refers to any compound, molecule, substance, or group or combination thereof that forms any type of structure or group of structures during or after electroprocessing. Materials include natural materials, synthetic materials, or combinations thereof. Naturally occurring organic materials include any substances naturally found in the body of plants or other organisms, regardless of whether those materials have or can be produced or altered synthetically. Synthetic materials include any materials prepared through any method of artificial synthesis, processing, or manufacture. Preferably the materials are biologically compatible materials.

One class of synthetic materials, preferably biologically compatible synthetic materials, comprises polymers. Such polymers include but are not limited to the following: poly(urethanes), poly(siloxanes) or silicones, poly(ethylene), poly(vinyl pyrrolidone), poly(2-hydroxy ethyl methacrylate), poly(N-vinyl pyrrolidone), poly(methyl methacrylate), poly(vinyl alcohol) (PVA), poly(acrylic acid), poly(vinyl acetate), polyacrylamide, poly(ethylene-co-vinyl acetate), poly(ethylene glycol), poly(methacrylic acid), polylactides (PLA), polyglycolides (PGA), poly(lactide-co-glycolides) (PLGA), polyanhydrides, and polyorthoesters or any other similar synthetic polymers that may be developed that are biologically compatible. The term "biologically compatible, synthetic polymers" shall also include copolymers and blends, and any other combinations of the forgoing either together or with other polymers generally. The use of these polymers will depend on given applications and specifications required. A more detailed discussion of these polymers and types of polymers is set forth in Brannon-Peppas, Lisa, "Polymers in Controlled Drug Delivery," Medical Plastics and Biomaterials, November 1997, which is incoφorated by reference as if set forth fully herein. "Materials" also include materials that are capable of changing into different materials during or after electroprocessing. For example, the protein fibrinogen, when combined with thrombin, forms fibrin. Fibrinogen or thrombin that are electroprocessed as well as the fibrin that later forms are included within the definition of materials. Similarly, procollagen will form collagen when combined with procollagen peptidase. Procollagen, procollagen peptidase, and collagen are all within the definition. In a preferred embodiment, the electroprocessed materials form a matrix. The term "matrix" refers to any structure comprised of electroprocessed materials. Matrices are comprised of fibers, or droplets of materials, or blends of fibers and droplets of any size or shape. Matrices are single structures or groups of structures and can be formed through one or more electroprocessing methods using one or more materials. Matrices are engineered to possess specific porosities. Substances may be deposited within, or anchored to or placed on matrices. Cells are substances which may be deposited within or on matrices.

One preferred class of materials for electroprocessing to make the compositions of the present invention comprises proteins. Extracellular matrix proteins are a preferred class of proteins in the present invention. Examples include but are not limited to collagen, fibrin, elastin, laminin, and fibronectin. Additional preferred materials are other components of the extracellular matrix, for example proteoglycans. In each case, those names are used throughout the present application in their broadest definition. There are multiple types of each of these proteins that are naturally-occurring as well as types that can be or are synthetically manufactured or produced by genetic engineering. For example, collagen occurs in many forms and types. All of these types and subsets are encompassed in the use of the proteins named herein. The term protein further includes, but is not limited to, fragments, analogs, conservative amino acid substitutions, and substitutions with non-naturally occurring amino acids with respect to each named protein. The term "residue" is used herein to refer to an amino acid (D or L) or an amino acid mimetic that is incoφorated into a protein by an amide bond. As such, the amino acid may be a naturally occurring amino acid or, unless otherwise limited, may encompass known analogs of natural amino acids that function in a manner similar to the naturally occurring amino acids (i.e., amino acid mimetics). Moreover, an amide bond mimetic includes peptide backbone modifications well known to those skilled in the art. Furthermore, one of skill will recognize that, as mentioned above, individual substitutions, deletions or additions which alter, add or delete a single amino acid or a small percentage of amino acids (typically less than 5%, more typically less than 1%) in an encoded sequence are conservatively modified variations where the alterations result in the substitution of an amino acid with a chemically similar amino acid. Conservative substitution tables providing functionally similar amino acids are well known in the art. The following six groups each contain amino acids that are conservative substitutions for one another:

1) Alanine (A), Serine (S), Threonine (T);

2) Aspartic acid (D), Glutamic acid (E);

3) Asparagine (N), Glutamine (Q); 4) Arginine (R), Lysine (K); 5) Isoleucine (I), Leucine (L), Methionine (M), Valine (V); and

6) Phenylalanine (F), Tyrosine (Y), Tryptophan (W).

It is to be understood that the term protein, polypeptide or peptide further includes fragments that may be 90 to 95% of the entire amino acid sequence, and also extensions to the entire amino acid sequence that are 5% to 10% longer than the amino acid sequence of the protein, polypeptide or peptide.

When peptides are relatively short in length (i.e., less than about 50 amino acids), they are often synthesized using standard chemical peptide synthesis techniques. Solid phase synthesis in which the C terminal amino acid of the sequence is attached to an insoluble support followed by sequential addition of the remaining amino acids in the sequence is a preferred method for the chemical synthesis of the antigenic epitopes described herein. Techniques for solid phase synthesis are known to those skilled in the art.

Alternatively, the proteins or peptides that may be electroprocessed are synthesized using recombinant nucleic acid methodology. Generally, this involves creating a nucleic acid sequence that encodes the peptide or protein, placing the nucleic acid in an expression cassette under the control of a particular promoter, expressing the peptide or protein in a host, isolating the expressed peptide or protein and, if required, renaturing the peptide or protein. Techniques sufficient to guide one of skill through such procedures are found in the literature.

When several desired protein fragments or peptides are encoded in the nucleotide sequence incoφorated into a vector, one of skill in the art will appreciate that the protein fragments or peptides may be separated by a spacer molecule such as, for example, a peptide, consisting of one or more amino acids. Generally, the spacer will have no specific biological activity other than to join the desired protein fragments or peptides together, or to preserve some minimum distance or other spatial relationship between them. However, the constituent amino acids of the spacer may be selected to influence some property of the molecule such as the folding, net charge, or hydrophobicity. Nucleotide sequences encoding for the production of residues which may be useful in purification of the expressed recombinant protein may be built into the vector. Such sequences are known in the art. For example, a nucleotide sequence encoding for a poly histidine sequence may be added to a vector to facilitate purification of the expressed recombinant protein on a nickel column.

Once expressed, recombinant peptides, polypeptides and proteins can be purified according to standard procedures known to one of ordinary skill in the art, including ammonium sulfate precipitation, affinity columns, column chromatography, gel electrophoresis and the like. Substantially pure compositions of about 50 to 99% homogeneity are preferred, and 80 to 95% or greater homogeneity are most preferred for use as therapeutic agents. Also, molecules capable of forming some of the named proteins can be mixed with other polymers during electroprocessing to obtain desired properties for uses of the formed protein in the matrix.

Throughout this application the term "solution" is used to describe the liquid in the reservoirs of the electroprocessing method. The term is defined broadly to include any liquids that contain materials to be electroprocessed. It is to be understood that any solutions capable of forming a material during electroprocessing are included within the scope of the present invention. In this application, the term "solution" also refers to suspensions, dispersions, or emulsions containing the material or anything to be electrodeposited. "Solutions" can be in organic or biologically compatible forms. "Solutions" may also consist of suspensions, dispersions or emulsions of two or more phases wherein one or more phase is dispersed, suspended, or emulsified within another phase of the liquid. This broad definition is appropriate in view of the large number of solvents or other liquids and carrier molecules, such as polyethylene glycol (PEG), that can be used in the many variations of electroprocessing. In this application, the term "solution" also refers to melts, hydrated gels and suspensions containing the materials, substances or anything to be electrodeposited. Solutions may also contain processing aids as defined herein.

Throughout this application, the term "processing aid" denotes any substance that is added to a solution that confers the ability to control a property or to confer a desirable property in a solution from which materials are electroprocessed, an electroprocessing process, or a resulting electroprocessed material. Examples of such properties include, but are not limited to: the moφhology of the materials after electroprocessing (including, for example, whether the materials form fibers, droplets, or other shapes upon electroprocessing as well as whether the resulting shapes have specific moφhologies such as "beads on a string" fiber moφhology); the ability to form an emulsion, suspension, or dispersion having two or more phases in a solution; the existence within electroprocessed materials of individual objects, bodies, or structures of the electroprocessed material (e.g. fibers, fibrils, films, sprays, particles, or droplets) possessing internal cavities, pockets, enclosures or other inclusions, and combinations thereof; and desirable mechanical properties of an electroprocessed material such as flexibility or strength. Any processing aid that controls a property or confers a desired property may be used. In some embodiments, the processing aids include surfactants. Examples of surfactants that can be used include, for example, any ionic or non-ionic surfactants known to one of ordinary skill in the art. Specific examples include, but are not limited to, bovine serum albumin, fatty acid salts (e.g., sodium lauryl sulfate), TWEEN, and non-ionic substances such as TRITON (oligoethylene oxide- modified phenols) or PLURONICS (ethylene oxide-propylene oxide-ethylene oxide block copolymers). Typical ionic or non-ionic surfactants are known to one of ordinary skill in the art and may be found in catalogs such as SIGMA (St. Louis, MO) or ALDRICH (Milwaukee, WI). In other embodiments, processing aids contain plasticizers. Example of plasticizers include, but are not limited to, glycerol and polyethylene glycols.

Solvents

Any solvent that allows delivery of the material or substance to the orifice, tip of a syringe, or other desired location under such conditions that the material or substance will be processed as desired can be used for dissolving or suspending the material or the substance to be electroprocessed. Solvents useful for dissolving or suspending a material or a substance will depend on the material or substance. Electrospinning techniques often require more specific solvent conditions. For example, collagen can be electrodeposited as a solution or suspension in water, 2,2,2-trifluoroethanol, l,l,l,3,3,3-hexafluoro-2-propanol (also known as hexafluoroisopropanol or HFIP), or combinations thereof. Fibrin monomer can be electrodeposited or electrospun from solvents such as urea, monochloroacetic acid, water, 2,2,2- trifluoroethanol, HFIP, or combinations thereof. Elastin can be electrodeposited as a solution or suspension in water, 2,2,2-trifluoroethanol, isopropanol, HFIP, or combinations thereof, such as isopropanol and water. In one desirable embodiment, elastin is electrospun from a solution of 70% isopropanol and 30% water containing 250 mg/ml of elastin. Other lower order alcohols, especially halogenated alcohols, may be used. Other solvents that may be used or combined with other solvents in electroprocessing natural matrix materials include acetamide, N- methylformamide, NN-dimethylformamide (DMF), dimethylsulfoxide (DMSO), dimethylacetamide, Ν-methyl pyrrolidone (ΝMP), acetic acid, trifluoroacetic acid, ethyl acetate, acetonitrile, trifluoroacetic anhydride, 1,1,1-trifluoroacetone, maleic acid, hexafluoroacetone. Proteins and peptides associated with membranes are often hydrophobic and thus do not dissolve readily in aqueous solutions. Such proteins can be dissolved in organic solvents such as methanol, chloroform, and trifluoroethanol (TFE) and emulsifying agents. Any other solvents known to one of skill in the protein chemical art may be used, for example solvents useful in chromatography, especially high performance liquid chromatography. Proteins and peptides are also soluble, for example, in HFTP, hexafluoroacetone, chloroalcohols in conjugation with aqueous solutions of mineral acids, dimethylacetamide containing 5% lithium chloride, and acids such as acetic acid, hydrochloric acid and formic acid, or solutions of such acids. In some embodiments, very dilute solutions of acids are used.. Ν-methyl moφholine-Ν-oxide is another solvent that can be used with many polypeptides. Other examples, used either alone or in combination with organic acids or salts, include the following: triethanolamine; dichloromethane; methylene chloride; 1,4-dioxane; acetonitrile; ethylene glycol; diethylene glycol; ethyl acetate; glycerine; propane- 1,3-diol; furan; tetrahydrofuran; indole; piperazine; pyrrole; pyrrolidone; 2- pyrrolidone; pyridine; quinoline; tetrahydroquinoline; pyrazole; and imidazole. Combinations of solvents may also be used. Synthetic polymers may be electrodeposited from, for example, HFIP, methylene chloride, ethyl acetate; acetone, 2-butanone (methyl ethyl ketone), diethyl ether; ethanol; cyclohexane; water; propanol alcohols, dichloromethane (methylene chloride); tetrahydrofuran; dimethylsulfoxide (DMSO); acetonitrile; methyl formate and various solvent mixtures. One preferred solvent mixture is water and 2-propanol. HFIP and methylene chloride are desirable solvents. Selection of a solvent will depend upon the characteristics of the synthetic polymer to be electrodeposited.

Selection of a solvent is based in part on consideration of secondary forces that stabilize polymer-polymer interactions and the solvent's ability to replace these with strong polymer- solvent interactions. In the case of polypeptides such as collagen, and in the absence of covalent crosslinking, the principal secondary forces between chains are: (1) coulombic, resulting from attraction of fixed charges on the backbone and dictated by the primary structure (e.g., lysine and arginine residues will be positively charged at physiological pH, while aspartic or glutamic acid residues will be negatively charged); (2) dipole-dipole, resulting from interactions of permanent dipoles; the hydrogen bond, commonly found in polypeptides, is the strongest of such interactions; and (3) hydrophobic interactions, resulting from association of non-polar regions of the polypeptide due to a low tendency of non-polar species to interact favorably with polar water molecules. Therefore, solvents or solvent combinations that can favorably compete for these interactions can dissolve or disperse polypeptides. For example, HFIP and TFE possess a highly polar OH bond adjacent to a very hydrophobic fluorinated region. While not wanting to be bound by the following theories, it is believed that the alcohol portion can hydrogen bond with peptides, and can also solvate charges on the backbone, thus reducing Coulombic interactions between molecules. Additionally, the hydrophobic portions of these solvents can interact with hydrophobic domains in polypeptides, helping to resist the tendency of the latter to aggregate via hydrophobic interactions. It is further believed that solvents such as HFIP and TFE, due to their lower overall polarities compared to water, do not compete well for intramolecular hydrogen bonds that stabilize secondary structures such as an alpha helix. Consequently, alpha helices in these solvents are believed to be stabilized by virtue of stronger intramolecular hydrogen bonds. The stabilization of polypeptide secondary structures in these solvents is believed desirable, especially in the cases of collagen and elastin, to preserve the proper formation of collagen fibrils during electroprocessing. Additionally, it is often desirable, although not necessary, for the solvent to have a relatively high vapor pressure to promote the stabilization of an electrospinning jet to create a fiber as the solvent evaporates. A relatively volatile solvent is also desirable for electrospraying to minimize coalescence of droplets during and after spraying and formation of dry electroprocessed materials. In embodiments involving higher boiling point solvents, it is often desirable to facilitate solvent evaporation by warming the spinning or spraying solution, and optionally the electroprocessing stream itself, or by electroprocessing in reduced atmospheric pressure. It is also believed that creation of a stable jet resulting in a fiber is facilitated by a low surface tension of the polymer/solvent mixture. Solvent choice can also be guided by this consideration.

In functional terms, solvents used for electroprocessing have the principal role of creating a mixture, suspension, or solution with one or more polymers, proteins, or other materials to be electroprocessed such that electroprocessing is feasible. The concentration of a given solvent is often an important consideration in determining the type of electroprocessing that will occur. For example, in electrospraying, the solvent should assist in the dispersion of droplets of electroprocessed material so that the initial jet of liquid disintegrates into droplets. Accordingly, solvents used in electrospraying should not create forces that will stabilize an unconfined liquid column. In electrospinning, interactions between molecules of electroprocessed material stabilize the jet, leading to fiber formation. Accordingly, for electrospun embodiments, the solvent should sufficiently dissolve or disperse the polymer to prevent the jet from disintegrating into droplets and should thereby allow formation of a stable jet in the form of a fiber. In some embodiments, the transition from electrospraying to electrospinning can be determined by examining Brookfield viscosity measurements for polymer solutions as a function of concentration. Brookfield viscosity increases as concentration of a polymer or other material to be electroprocessed increases. Above a critical concentration associated with extensive chain entanglements of materials, however, the Brookfield viscosity will increase more rapidly with concentration, as opposed to a more gradual, linear rise with concentration at lower concentrations. For example, the Brookfield viscosity of a poly(lactide) sample obtained from Alkermes dissolved in chloroform shows an upturn in the Brookfield viscosity/concentration plot at approximately 7-8 % w/v. A sample of poly(ethylene- co- vinyl acetate) from Dupont (ELVAX 40 W) shows an upturn at 14-15 % w/v. In some embodiments cases, these departures from linearity approximately coincide with the transition from electrospraying to electrospinning.

The solubility of any electroprocessed material in a solvent may be enhanced by modifying the material. Any method for modifying materials to increase their solubility may be used. For example, U.S. Patent No. 4,164,559 to Miyata et al. discloses a method for chemically modifying collagen to increase solubility.

In some embodiments, solvents materials to be electroprocessed are heated together to facilitate electroprocessing. These embodiments allow formation of solutions, suspensions, or other mixtures from which electroprocessing is possible that do not normally occur at room temperature. In some embodiments, the solution, suspension, or mixture persists after cooling, allowing electroprocessing at room temperature to occur after heating and cooling. For example, in some embodiments poly(ethylene-co-vinyl alcohol) (EVOH) is soluble above certain temperatures in about 50/50% to 90/10% v/v 2-propanol/water. A preferable solvent is 70/30% v/v 2-propanol/water, a typical composition of rubbing alcohol. In one embodiment, the temperature above which EVOH is soluble in 2-propanol/water is between about 30°C and about 120°C. In another embodiment, that temperature is between about 50°C and about 100°C. In another embodiment, that temperature is between about 60°C and about 70°C. In another embodiment, that temperature is about 65°C. In another embodiment, that temperature is between about 75°C and about 85°C. In another embodiment, that temperature is about 80°C. In some embodiments, it has been found that EVOH dissolved in a solvent such as 2-propanol/water at higher temperatures remains in solution for several hours after returning to room temperature before the EVOH begins to precipitate. Further, even after precipitation, it has been observed in some embodiments that the EVOH dissolves again readily and in a short period of time upon reheating, often at temperatures lower than that at which it was originally dissolved. In one embodiment, EVOH originally dissolved by heating to about 80°C for 2-3 hours, then was allowed to precipitate, and was dissolved again by reheating to about 50°C for about 10 minutes.

In other embodiments, processing aids are added to the solvent assist in achieving the desired electroprocessing result. One example of such processing aids is non-ionic surfactants. In some embodiments, polymers will electrospin as fibers more readily from a solvent containing one or more non-ionic surfactants than with the solvent alone. For example, poly( vinyl alcohol) (PVA) that is highly hydrolyzed will dissolve readily in water but is not readily electrospun from water. Addition of a non-ionic surfactant, such as TRITON X-100, allowed electrospinning of fully hydrolyzed PVA from an aqueous solution. TRITON X-100 is an ethoxylated alcohol. Other ethoxylated alcohols can be used. Examples of surfactants that can be used include, for example, any ionic or non-ionic surfactants known to one of ordinary skill in the art. Specific examples include, but are not limited to, bovine serum albumin, fatty acid salts (e.g., sodium lauryl sulfate), TWEEN, and non-ionic substances such as TRITON (oligoethylene oxide- modified phenols) or PLURONICS (ethylene oxide-propylene oxide-ethylene oxide block copolymers). Typical ionic or non-ionic surfactants are known to one of ordinary skill in the art and may be found in catalogs such as SIGMA (St. Louis, MO) or Aldrich Chemical (Milwaukee, WI).

In other embodiments, solvents may be an emulsion, dispersion, or suspension containing two or more phases in which one or more phases contains a liquid that is immiscible in one or more additional phases. In some embodiments, one phase contains aqueous or water-miscible liquids and another phase contains water-immiscible liquids such as organic solvents or oils. The polymer to be electroprocessed is dissolved, suspended, or otherwise contained in any phase. For example, in one embodiment a material (for example a polymer or protein) is dissolved or suspended in an organic solvent wherein the solvent has an aqueous minor or internal phase dispersed within it. In another embodiment, a water soluble material is dissolved, suspended, or otherwise contained in an aqueous phase, wherein the aqueous phase contains a dispersed organic minor or internal phase. Alternatively, the material to be electroprocessed may be in an internal or minor phase, whether aqueous or organic. Different materials may also be present in each of the phases and thereby be electroprocessed together. The existence of all phases in the solvent allows additional combinations of materials and substances having differing solubilities and miscibilities.

Any means to create an emulsion, suspension, or dispersion may also be used. Chemical means include, but are not limited to, use of surfactants such as those listed above. Physical means such as ultrasonic homogenization or other techniques of physical agitation, homogenization, or blending may be used. One example of known homogenization techniques are those used to induce a uniform distribution of lipid droplets within whole milk products. In some embodiments, physical means alone are used to create the emulsion, suspension, or dispersion. In other embodiments, chemical means alone are used to create the emulsion, suspension, or dispersion. In still other embodiments, combinations of physical and chemical means are used to create the emulsion, suspension, or dispersion.

In some embodiments, solvents are used that increase the propensity of a composition to be electroprocessed or to be electroprocessed in a specific way, such as electrospinning. In some embodiments, the use of rubbing alcohol (70/30 v/v % isopropanol/water) causes fibers to form readily during electroprocessing of EVOH. While not wanting to be bound to the following statement it is believed that the thermodynamic instability of EVOH/mbbing alcohol solutions may cause early stabilization of the jet of material during electroprocessing to form polymer fiber, perhaps accounting for the great ease of electrospinning. Solvents that promote desired types of electroprocessing are one preferred embodiment of the invention. In one embodiment involving EVOH in rubbing alcohol, the fibers formed rapidly, allowing formation of an electrospun mat at a midair location. Compositions of the present invention The electroprocessed material

One component of the compositions of the present invention is the electroprocessed material. As defined above, the electroprocessed material of the present invention can include natural materials, synthetic materials, or combinations thereof. Examples include but are not limited to amino acids, peptides, denatured peptides such as gelatin from denatured collagen, polypeptides, proteins, carbohydrates, lipids, nucleic acids, glycoproteins, lipoproteins, glycolipids, glycosaminoglycans, and proteoglycans. Some preferred materials are naturally occurring extracellular matrix materials and blends of naturally occurring extracellular matrix materials, including but not limited to collagen, fibrin, elastin, laminin, fibronectin, hyaluronic acid, chondroitin 4-sulfate, chondroitin 6-sulfate, dermatan sulfate, heparin sulfate, heparin, and keratan sulfate, and proteoglycans. These materials may be isolated from humans or other animals or cells or synthetically manufactured. Some especially preferred natural matrix materials are collagen and fibrin and fibronectin. Also included are crude extracts of tissue, extracellular matrix material, extracts of non-natural tissue, or extracellular matrix materials (i.e. extracts of cancerous tissue), alone or in combination. Extracts of biological materials, including but not limited to cells, tissues, organs, and tumors may also be electroprocessed. Collagen has been electrospun to produce a repeating, banded pattern observed with electron microscopy. This banded pattern is typical of collagen fibrils produced by natural processes (i.e. banded pattern is observed in collagen when it is produced by cells). In some embodiments, collagen is electrospun such that it has a 65 nm banding pattern.

It is to be understood that these electroprocessed materials may be combined with other materials and/or substances in forming the compositions of the present invention. For example, an electroprocessed peptide may be combined with an adjuvant to enhance immunogenicity when implanted subcutaneously. As another example, an electroprocessed collagen matrix, containing cells, may be combined with an electroprocessed biologically compatible polymer and growth factors to stimulate growth and division of the cells in the collagen matrix.

Synthetic materials include any materials prepared through any method of artificial synthesis, processing, or manufacture. The synthetic materials are preferably biologically compatible for administration in vivo or in vivo. Such polymers include but are not limited to the following: poly(urethanes), poly(siloxanes) or silicones, poly(ethylene), poly(vinyl pyrrolidone), poly(2-hydroxy ethyl methacrylate), poly(N-vinyl pyrrolidone), poly(methyl methacrylate), poly(vinyl alcohol) (PVA), poly(acrylic acid), poly(vinyl acetate), polyacrylamide, poly(ethylene- co-vinyl acetate), poly(ethylene glycol), poly(methacrylic acid), polylactic acid (PLA), polyglycolic acids (PGA), poly(lactide-co-glycolides) (PLGA), nylons, polyamides, polyanhydrides, poly(ethylene-co-vinyl alcohol) (EVOH), polycaprolactone, poly(vinyl acetate), polyvinylhydroxide, poly(ethylene oxide) (PEO) and polyorthoesters or any other similar synthetic polymers that may be developed that are biologically compatible. Some preferred synthetic matrix materials include PLA, PGA, copolymers of PLA and PGA, polycaprolactone, poly(ethylene-co-vinyl acetate), EVOH, PVA, and PEO. Matrices can be formed of electrospun fibers, electroaerosol, electrosprayed, or electrosputtered droplets, or a combination of the foregoing.

In embodiments in which natural materials are used, those materials can be derived from a natural source, synthetically manufactured, or manufactured by genetically engineered cells. For example, genetically engineered proteins can be prepared with specific desired sequences of amino acids that differ from the natural proteins. In one illustrative embodiment, desirable sequences that form binding sites on a collagen protein for cells or peptides can be included in higher amounts than found in natural collagen. By selecting different materials, or combinations thereof, many characteristics of the electroprocessed material can be manipulated. The properties of the matrix comprised of electroprocessed material and a substance may be adjusted. As discussed in greater detail below, electroprocessed materials themselves can provide a therapeutic effect when applied. In addition, selection of matrix materials can affect the permanency of an implanted matrix. For example, matrices made of fibrin will degrade more rapidly while matrices made of collagen are more durable and synthetic matrix materials are more durable still. Use of matrices made of natural materials such as proteins also minimize rejection or immunological response to an implanted matrix. Accordingly selection of materials for electroprocessing and use in substance delivery is influenced by the desired use. In one embodiment, a skin patch of electroprocessed fibrin or collagen combined with healing promoters and anti-rejection substances may be applied to the skin and may subsequently dissolve into the skin. In another embodiment, an implant for delivery to bone may be constructed of materials useful for promoting bone growth, osteoblasts and hydroxyapatite, and may be designed to endure for a prolonged period of time.

Synthetic components, such as biocompatible substances can be used to modulate the release of materials from an electroprocessed composition. For example, a drug, or series of drugs or other materials to be released in a controlled fashion can be electroprocessed into a series of layers. One layer is composed of PGA plus a drug, the next layer PLA plus a drug, a third layer is composed of polycaprolactone plus a drug. The layered construct can be implanted, and as the successive layers dissolve or breakdown, the drug (or drugs) is released in turn as each successive layer erodes. Unlayered structures can also be used, and release is controlled by the relative stability of each component of the construct. Another advantage of the synthetic materials is that different solvents can be used. This can be important for the delivery of some materials. For example, a drug may be soluble in some organics, and using synthetics increases the number of materials that can be electroprocessed. The breakdown of these synthetic materials can be tailored and regulated in ways that are not available to natural materials. The synthetics are usually not subject to enzymatic breakdown, and many spontaneously undergo hydrolysis. In addition to these characteristics, substances can be released from electroprocessed materials in response to electrical, magnetic and light based signals. Polymers that are sensitive to such signals can be used, or the polymers may be derivatized in a way to provide such sensitivity. These properties provide flexibility in making and using electroprocessed materials designed to deliver various substances, in vivo and in vitro.

In some embodiments, electroprocessing of an emulsion, suspension, or dispersion having multiple phases results in the formation of electroprocessed materials in which the individual objects, bodies, or structures of electroprocessed material (e.g. fibers, fibrils, films, sprays, particles, or droplets) possess internal cavities, pockets, enclosures or other inclusions that contain substances that were present in the solvent phase that did not contain the material prior to electroprocessing. In one embodiment, a polymer electrospun from an organic solvent possessed enclosures that contained water-miscible protein that had been present in an aqueous internal phase of the organic solvent during electroprocessing. Thus, the ability to electroprocess solvents containing two or more phases allows formation of electroprocessed materials and matrices that have substances incoφorated into individual objects, bodies, or structures of electroprocessed material (e.g. fibers, fibrils, films, sprays, particles, or droplets), instead of or in addition to incoφorating the substances into the interstices of a matrix made from the electroprocessed material. The internal cavities, pockets, enclosures or other inclusions within the electroprocessed materials are in a phase different from that of the electroprocessed material in which they are dispersed (e.g. aqueous vs. nonaqueous). As a result the internal cavities, pockets, enclosures or other inclusions in some embodiments allow the electroprocessed material to contain a higher overall amount or concentration of substances than would be possible by addition of the substances directly to the liquid in which the cavities are dispersed, since poor solubility would limit the amount of substance incoφorated into that liquid.

In some embodiments, the boundary between the internal cavities, pockets, enclosures or other inclusions and the electroprocessed material and/or the outer wall of the electroprocessed material (i.e. the walls of the individual fibers, sprays, films, fibrils, droplets, particles, etc.) is not permeable to molecules greater than a certain size. Such selective permeability is particularly advantageous in some embodiments used for cell encapsulation. In some embodiments, the electroprocessed materials are used to deliver one or more large molecules (e.g. large polypeptides or proteins) by release of the molecules from the electroprocessed materials. In such embodiments, the electroprocessed materials optionally include features that help assure that the release of the molecules is not unduly inhibited by the low permeability or impermeability of either the outer wall of the electroprocessed material or the boundary between the cavities and the electroprocessed material. Any such features can be used. In some examples, the phase that surrounds the cavities, pockets, enclosures or other inclusions is saturated with polypeptide that has limited or no solubility in that phase, such that the insoluble polypeptide acts to form channels in the surface of the electroprocessed material and allows polypeptide from the cavities to be released. Alternatively, a second component that erodes, dissolves, dissipates, biodegrades, or otherwise breaks down over time can be added to the outer phase, resulting in channels forming from the surface of the electroprocessed material to the aqueous core. For example, poly(ethylene-co-vinyl acetate) (EVA) can be electrospun along with poly(glycolide). When placed in water, the latter polymer will be lost from the electroprocessed material through hydrolysis, the result being a porous network within the EVA fiber. This type of treatment produces a honey-combed fiber, providing a site for the incoφoration and or release of materials from the internal sites.

In some embodiments of the present invention, the electroprocessed material itself provides a therapeutic effect. For example, in some embodiments electroprocessed collagen promotes cellular infiltration and differentiation, so an electroprocessed collagen matrix alone assists with healing. The P-15 site, a 15 amino acid sequence within the collagen molecule, promotes osteoblasts to produce and to secrete hydroxyapatite, a component of bone. Another example of specific sites and sequences within collagen molecules that can be manipulated and processed in a similar fashion includes the RGD binding sites of the integrin molecule. The RGD site is a sequence of three amino acids (Arg-Gly-Asp) present in many matrix materials that serves as a binding site for cell adhesion. It is recognized and bound, for example, by integrins. In addition, electroprocessed materials can be enriched with specific desired sequences before, during, or after electroprocessing. Sequences can be added in linear or other forms. In some embodiments, the RGD sequences are arranged in a cyclic form referred to as cycloRGD. Another embodiment of matrix materials that have a therapeutic effect is electroprocessed fibrin. Fibrin matrix material assists in arrest of bleeding. Fibrin is a component of the provisional matrix that is laid down during the early stages of healing and may also promote the growth of vasculature in adjacent regions, and in many other ways is a natural healing promoter. Fibrinogen as an electroprocessed material can also assist in healing. When placed in contact with a wound, for example, fibrinogen will react with thrombin present in the blood plasma from the wound and form fibrin, thereby providing the same healing properties of a fibrin material.

Derivatized Electroprocessed Materials An electroprocessed material, such as a matrix, can also be composed of specific subdomains of a matrix constituent and can be prepared with a synthetic backbone that can be derivatized. For example, the RGD peptide sequence, and/or a heparin binding domain and/or other sequences, can be chemically coupled to synthetic materials. The synthetic polymer with the attached sequence or sequences can be electroprocessed into a construct. This produces a matrix with unique properties. In these examples the RGD site provides a site for cells to bind to and interact with the matrix. The heparin-binding site provides a site for the anchorage of peptide growth factors to the synthetic backbone. Angiogenic peptides, genetic material, growth factors, cytokines, enzymes and drugs are other non-limiting examples of substances that can be attached to the backbone of an electroprocessed material to provide functionality. Peptide side chains may also be used to attach molecules to functional groups on polymeric backbones. Molecules and other substances can be attached to a material to be electroprocessed by any technique known in the art.

In some embodiments, derivatization of electφrocessed material allows, for example: (1) changing the moisture absorbing properties of the material; (2) tailoring surface wettability of electrospun fibers; (3) covalently attaching compounds that can be slowly released via hydrolysis of, for example, an ester linkage; (4) covalently attaching compounds that confer surface specificity for various biological reactions or cell line growth; or (5) attaching compounds that are capable of sequestering molecules from blood, urine, intestinal, or wound fluids. In some embodiments, derivatization is used to accomplish a combination of the foregoing aspects. Derivatization can occur before, during or after electroprocessing. Derivatized electroprocessed materials have several applications. In some embodiments, reactive sites are used to bond materials with agents such as peptides prior to electrospinning. In some embodiments, a material is customized and enriched in specific peptide moieties that have biological activity. In one such embodiment, the P15 site, a 15 amino acid sequence found on Type I collagen, is isolated or synthesized in vitro, and coupled this sequence to a backbone of a polymer such as EVOH. A matrix is prepared that is highly porous (allows cells to penetrate) and composed of filaments enriched in the P15 site designed to be a side chain. The matrix is useful, for example, as a seeding site for the formation of bone because the PI 5 site promotes osteoblasts to produce and to secrete hydroxyapatite, a component of bone. In other embodiments, polymeric matrices are supplemented with complex mixtures of peptides, producing a natural matrix with a synthetic backbone.

In other embodiments, reactive side groups of the electroprocessed material are used to fabricate diagnostic filtration systems. In one embodiment, antibodies or other binding agents are coupled to the EVOH backbone and then the derivatized EVOH is electroprocessed into a fibrous mat or an aerosol droplet preparation. The electroprocessed matrix provides a solid phase site for the binding of antibodies. This embodiment has a number of uses. For example, this type of matrix is placed into a device such as a syringe filter and a sample for which the presence or concentration of an analyte is to be evaluated is injected into the matrix and allowed to incubate for an interval of time before passing a wash solution through the matrix to rinse un-reacted analyte or other materials from the matrix. A second antibody coupled with a chromophore, enzyme, radiolabel or other detection agent is then passed through the matrix to detect the presence of the antigens that are now bound to the antibodies coupled to the EVOH backbone. One advantage of this approach is that a relatively large amount of material can be passed through the matrix, allowing concentration or isolation of antigens or other analytes from samples. Another advantage is that the matrix with antibodies or other binding agents bound to it provides a large surface area for reactions to occur. In other embodiments, this type of device is used to detect airborne materials such as airborne pathogens.

In some embodiments, the polymeric backbone derivatized with a binding agent is used as a backbone to detect binding protein binding pairs or nucleic acid sequences. In one embodiment, nucleic acid sequences (e.g. DNA, RNA, peptide nucleic acid (PNA) etc.) are coupled to the matrix and reacted with a sample to allow hybridization to complementary strands in the sample. Complementary sequences are thereby isolated from the sample. This system allows a large amount of genetic material to be retained and reacted in a very small volume of electroprocessed material. In another embodiment, protein binding partners are identified and detected in a sample, again the attractive feature being the large amount of material placed within the small volume of an electrospun matrix.

In some embodiments, protein G or protein R is coupled to the matrix. Antibodies are then mixed with a sample under conditions that allow the antibodies to bind antigen present within the solution. The combined sample and antibodies are then passed through the matrix. The protein G and R bind the antibodies and serve as a solid phase chromatography support to pull the bound antigens from solution. The antigens are either released from the matrix by acid shock or detected as described in the preceding discussion. In other embodiments, the basic design is used to prepare a chromatography column, for example, to capture antigens for purification. Such columns are far more stable than the columns in present use. Any type of derivatization of any type of material may be used. As examples, some possible derivatization chemistries at the hydroxyl groups of EVOH and PVA include, but are not limited to, esterification (e.g., with acyl halides, acid anhydrides, carboxylic acids, or esters via interchange reactions), ether formation (for example, via the Williamson ether synthesis), urethane formation via reactions with isocyanates, sulfonation with, for example, chlorosulfonic acid, and reaction of b-sulfato-ethylsulfonyl aniline to afford an amine derivative that can be converted to a diazo for reaction with a wide variety of compounds. Such chemistries can be used to attach a wide variety of substances to EVOH and PVA, including but not limited to crown ethers (Kimura et al., J. Polym. Sci. Part A Polym. Chem., 21, 2777, 1983), enzymes (Chase and Yang, Biotechnol. Appl. Biochem., 27, 205, 1998), and nucelotides (Overberger and Chang, J. Polym. Sci. Part A Polym. Chem., 27, 3589, 1989). Additional methods for immobilizing proteins to EVOH polymers are providing in L. Jianguo, C. Wei, W. Shuai, O. Fran, Studies of poly(vinyl acetate-co-divinyl benzene) beads as a carrier for the immobilization of penicillin acylase, Reactive & Functional Polymers, 48 (2001) 75-84. The articles cited in this paragraph are (incoφorated herein by reference).

In other embodiments a modified electroprocessed material such as EVOH is used as a replacement for polystyrene styrene-supported quaternary ammonium salts which are often used as phase transfer catalysts in organic synthesis. The catalytic activity of the modified electroprocessed material is much higher than polystyrene-based systems, especially when electrospun fibers are used, due to high surface area of the fibers. In addition, electroprocessed material is considered more environmentally friendly than polystyrene.

Properties of Electroprocessed Materials

When the electroprocessed materials form fibers, a wide range of fiber diameters are achievable, since electroprocessed fibers have been observed to have cross-sectional diameters ranging from several μm to below 100 nm. In one embodiment, the fibers have an average diameter of about 20 microns or less. In another embodiment, the fibers range between about 10 nm and about 100 μm in average diameter. In another embodiment, the fibers range between about 10 nm and about 10 μm in average diameter. In another embodiment, the fibers range between about 10 nm and about 1 μm in average diameter. In another embodiment, the fibers range between about 50 nm and about 1 μm in average diameter. In another embodiment, the fibers range between about 100 nm and about 1 μm in average diameter. In another embodiment, the fibers range between about 100 nm and about 10 μm in average diameter. In another embodiment, the fibers range between about 50 nm and about 10 μm in average diameter. In another embodiment, the fibers range between about 50 nm and about 100 nm in average diameter.

The present invention permits design and control of pore size in an electroprocessed material through manipulation of the composition of the material and the parameters of electroprocessing. In some embodiments, the electroprocessed material has a pore size that is small enough to be impermeable to one or more types of cells. In some embodiments, for example, the pore size is such that the electroprocessed material is impermeable to red blood cells. In some embodiments, the pore size is such that the electroprocessed material is impermeable to platelets. In one embodiment, the average pore diameter is about 500 nanometers or less. In another embodiment, the average pore diameter is about 1 micron or less. In another embodiment, the average pore diameter is about 2 microns or less. In another embodiment, the average pore diameter is about 5 microns or less. In another embodiment, the average pore diameter is about 8 microns or less. Some embodiments have pore sizes that do not impede cell infiltration at all. One preferred embodiment has a pore size between about 0.1 and about 100 μm². A further preferred embodiment has a pore size between about 0.1 and about 50 μm². A further preferred embodiment has a pore size between about 1.0 μm and about 25 μm. A further preferred embodiment has a pore size between about 1.0 μm and about 5 μm. Infiltration can also be accomplished with implants with smaller pore sizes. For porous structures, the interaction of the device/material with the host surrounding tissue is dependent on the size, size distribution, and continuity of pores within the stmcture of the device. It was previously thought that pore size must be greater than about 10 microns for cells to be capable of migrating into, out of, or through the structure. It has been observed, however, that implants comprised of electrospun nanofibers of at least some types of natural proteins are not subject to this limitation. In one embodiment significant cellular migration occurred into an electrospun collagen/elastin with an average pore size of 3.7 microns. Pore size of an electroprocessed matrix can be readily manipulated through control of process parameters, for example by controlling fiber deposition rate through electric field strength and mandrel motion, by varying solution concentration (and thus fiber size). Porosity can also be manipulated by mixing porogenic materials, such as salts or other extractable agents, the dissolution of which will leave holes of defined sizes in the matrix. If desired, the degree to which cells infiltrate a matrix can be controlled by the amount of cross-linking present in the matrix. A highly cross-linked matrix is not as rapidly infiltrated as a matrix with a low degree of cross-linking. Adding synthetic materials to a matrix also limit the degree to which cells infiltrate the material in some embodiments. Cell infiltration is also limited in some embodiments by incoφorating agents that act to actively suppress cell migration (for example, cell toxins such as sodium azide, bacterial toxins or certain pharmaceuticals). Various embodiments of the present invention possess varying mechanical properties. Examples include but are not limited to: a dry sample of Type I collagen electrospun fiber scaffold, crosslinked by exposure to glutaraldehyde vapor for approximately 2.5 hours, having an elastic modulus of 52 MPa and a peak stress of 1.5 MPa; a Type I collagen electrospun fiber scaffold, also crosslinked by exposure to glutaraldehyde vapor for approximately 2.5 hours, then hydrated in PBS for three hours, having an elastic modulus of 0.2 MPa with a peak stress of 0.1 MPa; a Type I collagen electrospun fiber scaffold, crosslinked by exposure to glutaraldehyde vapor for 24 hours, then hydrated in PBS for three hours, having a modulus of 1.5 MPa with a peak stress of 0.25 MPa; an uncrosslinked Type π collagen scaffolds having a tangent modulus of 172.5 MPa and an ultimate tensile strength of 3.298 MPa.. In preferred embodiments, mechanical properties of the electroprocessed matrix are within ranges found within natural extracellular matrix materials and tissues. Examples include, but are not limited to, matrices with an elastic modulus between about 0.5 and about 10 MPa and matrices with an elastic modulus between about 2 and about 10 MPa. These values for elastic modulus and peak stress are not intended to be limiting, and electroprocessed matrices with any type of mechanical properties are within the scope of this invention.

Substances

As discussed above, the word "substance" in the present invention is used in its broadest definition. In embodiments in which the compositions of the present invention comprise one or more substances, substances can include any type or size of molecules, cells, objects or combinations thereof. The compositions of the present invention may comprise one substance or any combination of substances.

In embodiments in which the substances are molecules, any molecule can be used. Molecules may, for example, be organic or inorganic and may be in a solid, semisolid, liquid, or gas phase. Molecules may be present in combinations or mixtures with other molecules, and may be in solution, suspension, or any other form. Examples of classes of molecules that may be used include human or veterinary therapeutics, cosmetics, nutraceuticals, agriculturals such as herbicides, pesticides and fertilizers, vitamins, amino acids, peptides, polypeptides, proteins, carbohydrates, lipids, nucleic acids, glycoproteins, lipoproteins, glycolipids, glycosaminoglycans, proteoglycans, growth factors, hormones, neurotransmitters, pheromones, chalones, prostaglandins, immunoglobulins, monokines and other cytokines, humectants, metals, gases, minerals, ions, electrically and magnetically reactive materials, light sensitive materials, anti- oxidants, molecules that may be metabolized as a source of cellular energy, antigens, and any molecules that can cause a cellular or physiological response. Any combination of molecules can be used as well as agonists or antagonists.

Several preferred embodiments using therapeutic molecules include use of any therapeutic molecule including, without limitation, any pharmaceutical or drug. Examples of pharmaceuticals include, but are not limited to, anesthetics, hypnotics, sedatives and sleep inducers, antipsychotics, antidepressants, antiallergics, antianginals, antiarthritics, antiasthmatics, antidiabetics, antidiarrheal drugs, anticonvulsants, antigout drugs, antihistamines, antipruritics, emetics, antiemetics, antispasmondics, appetite suppressants, neuroactive substances, neurotransmitter agonists, antagonists, receptor blockers and reuptake modulators, beta-adrenergic blockers, calcium channel blockers, disulfarim and disulfarim-like drugs, muscle relaxants, analgesics, antipyretics, stimulants, anticholinesterase agents, parasympathomimetic agents, hormones, anticoagulants, antithro botics, coagulants, thrombotics, thrombolytics, immunoglobulins, immunosuppressants, hormone agonists/antagonists, vitamins, antimicrobial agents, antineoplastics, antacids, digestants, laxatives, cathartics, antiseptics, diuretics, disinfectants, fungicides, ectoparasiticides, antiparasitics, heavy metals, heavy metal antagonists, chelating agents, gases and vapors, alkaloids, salts, ions, autacoids, digitalis, cardiac glycosides, antiarrhythmics, antihypertensives, vasodilators, vasoconstrictors, antimuscarinics, ganglionic stimulating agents, ganglionic blocking agents, neuromuscular blocking agents, adrenergic nerve inhibitors, anti-oxidants, vitamins, cosmetics, anti-inflammatories, wound care products, antithrombogenic agents, antitumoral agents, antithrombogenic agents, antiangiogenic agents, anesthetics, antigenic agents, wound healing agents, plant extracts, growth factors, emollients, humectants, rejection/anti-rejection drugs, spermicides, conditioners, antibacterial agents, antifungal agents, antiviral agents, antibiotics, tranquilizers, cholesterol-reducing drugs, antitussives, histamine-blocking drugs, monoamine oxidase inhibitors. All substances listed by the U.S. Pharmacopeia are also included within the substances of the present invention.

Antibiotics useful in the present invention include, but are not limited to, amoxicillin, amphotericin, ampicillin, bacitracin, beclomethasone, benzocaine, betamethasone, biaxin, cephalosporins, chloramphenicol, ciprofloxacin, clotrimazole, cyclosporin, docycline, enoxacin, erythromycin, gentamycin, miconazole, neomycin, norfloxacin, nystatin, ofloxacin, pefloxacin, penicillin, pentoxifylline, phenoxymethylpenicillin, poly ixin, rifampicin, tetracycline, tobrmycin, triclosan, vancomycin, zithromax, derivatives, metabolites, and mixtures thereof, or compounds having similar antimicrobial activity.

Some specific examples of pharmaceutical agents that are useful as substances include, but are not limited to, quinolones, such as oxolinic acid, norfloxacin, and nalidixic acid, sulfonamides, nonoxynol 9, fusidic acid, cephalosporins, cyclosporine, acebutolol, acetylcysteine, acetylsalicyhc acid, acyclovir, AZT, alprazolam, alfacalcidol, allantoin, allopurinol, ambroxol, amikacin, amiloride, aminoacetic acid, aminodarone, amitriptyline, amlodipine, ascorbic acid, aspartame, astemizole, atenolol, benserazide, benzalkonium hydrochloride, benzoic acid, bezafibrate, biotin, biperiden, bisoprolol, bromazepam, bromhexine, bromocriptine, budesonide, bufexamac, buflomedil, buspirone, caffeine, camphor, captopril, carbamazepine, carbidopa, carboplatin, cefachlor, cefalexin, cefatroxil, cefazolin, cefixime, cefotaxime, ceftazidime, ceftriaxone, cefuroxime, selegiline, chloramphenicol, chloφheniramine, chlortalidone, choline, cilastatin, cimetidine, cisapride, cisplatin, clarithromycin, clavulanic acid, clomipramine, clozapine, clonazepam, clonidine, codeine, cholestyramine, cromoglycic acid, cyanocobalamin, cyproterone, desogestrel, dexamethasone, dexpanthenol, dextromethoφhan, dextropropoxiphen, diazepam, diclofenac, digoxin, dihydrocodeine, dihydroergotamine, dihydroergotoxin, diltiazem, diphenhydramine, dipyridamole, dipyrone, disopyramide, domperidone, dopamine, doxycycline, enalapril, ephedrine, epinephrine, ergocalciferol, ergotamine, erythromycin, estradiol, ethinylestradiol, etoposide, Eucalyptus globulus, famotidine, felodipine, fenofibrate, fenoterol, fentanyl, flavin mononucleotide, fluconazole, flunarizine, fluorouracil, fluoxetine, flurbiprofen, furosemide, gallopamil, gemfibrozil, Gingko biloba, glibenclamide, glipizide, Glycyrrhiza glabra, grapefruit seed extract, grape seed extract, griseofulvin, guaifenesin, haloperidol, heparin, hyaluronic acid, hydrochlorothiazide, hydrocodone, hydrocortisone, hydromoφhone, ipratropium hydroxide, ibuprofen, imipenem, indomethacin, iohexol, iopamidol, isosorbide dinitrate, isosorbide mononitrate, isotretinoin, ketotifen, ketoconazole, ketoprofen, ketorolac, labetalol, lactulose, lecithin, levocamitine, levodopa, levoglutamide, levonorgestrel, levothyroxine, lidocaine, lipase, imipramine, lisinopril, loperamide, lorazepam, lovastatin, medroxyprogesterone, menthol, methotrexate, methyldopa, methylprednisolone, metoclopramide, metoprolol, miconazole, midazolam, minocycline, minoxidil, misoprostol, moφhine, N-methylephedrine, naftidrofuryl, naproxen, nicardipine, nicergoline, nicotinamide, nicotine, nicotinic acid, nifedipine, nimodipine, nitrazepam, nitrendipine, nizatidine, norethisterone, norfloxacin, norgestrel, nortriptyline, omeprazole, ondansetron, pancreatin, panthenol, pantothenic acid, paracetamol, phenobarbital, derivatives, metabolites, and other such compounds have similar activity. Some preferred drugs or compounds include, but are not limited to, estrogen, androgen, cortisone, and cyclosporin.

Growth factors useful in the present invention include, but are not limited to, transforming growth factor-α ("TGF- "), transforming growth factor-β ("TGF-β"), platelet-derived growth factors ("PDGF"), fibroblast growth factors ("FGF"), including FGF acidic isoforms 1 and 2, FGF basic form 2 and FGF 4, 8, 9 and 10, nerve growth factors ("NGF") including NGF 2.5s, NGF 7.0s and beta NGF and neurotrophins, brain derived neurotrophic factor, cartilage derived factor, bone growth factors (BGF), basic fibroblast growth factor, insulin-like growth factor (IGF), vascular endothelial growth factor (VEGF), granulocyte colony stimulating factor (G-CSF), insulin like growth factor (IGF) I and π, hepatocyte growth factor, glial neurotrophic growth factor (GDNF), stem cell factor (SCF), keratinocyte growth factor (KGF), transforming growth factors (TGF), including TGFs alpha, beta, betal, beta2, beta3, skeletal growth factor, bone matrix derived growth factors, and bone derived growth factors and mixtures thereof.

Cytokines useful in the present invention include, but are not limited to, cardiotrophin, stromal cell derived factor, macrophage derived chemokine (MDC), melanoma growth stimulatory activity (MGSA), macrophage inflammatory proteins 1 alpha (MTP-lalpha), 2, 3 alpha, 3 beta, 4 and 5, IL-1, E -2, IL-3, IL-4, IL-5, IL-6, IL-7, IL-8, IL-9, IL-10, IL-11, IL-12, IL- 13, TNF-α, and TNF-β. Immunoglobulins useful in the present invention include, but are not limited to, IgG, IgA, IgM, IgD, IgE, and mixtures thereof. Some preferred growth factors include NEGF (vascular endothelial growth factor), ΝGFs (nerve growth factors), PDGF-AA, PDGF-BB, PDGF-AB, FGFb, FGFa, and BGF. Other molecules useful as substances in the present invention include but are not limited to growth hormones, leptin, leukemia inhibitory factor (LIF), tumor necrosis factor alpha and beta, endostatin, thrombospondin, osteogenic protein- 1, bone moφhogenetic proteins 2 and 7, osteonectin, somatomedin-like peptide, osteocalcin, , interferon alpha, interferon alpha A, interferon beta, interferon gamma, interferon 1 alpha, and interleukins 2, 3, 4, 5 6, 7, 8, 9, 10, 11, 12,13, 15, 16, 17 and 18.

Embodiments involving amino acids, peptides, polypeptides, and proteins may include any type or combinations of such molecules of any size and complexity. Examples include, but are not limited to structural proteins, enzymes, and peptide hormones. These compounds can serve a variety of functions. In some embodiments, the matrix may contain peptides containing a sequence that suppresses enzyme activity through competition for the active site. In other applications antigenic agents that promote an immune response and invoke immunity can be incoφorated into a construct.

In substances such as nucleic acids, any nucleic acid can be present. Examples include, but are not limited to deoxyribonucleic acid (DΝA), ent-DΝA, and ribonucleic acid (RΝA). Embodiments involving DΝA include, but are not limited to, cDΝA sequences, natural DΝA sequences from any source, and sense or anti-sense oligonucleotides. For example, DΝA can be naked (e.g., U.S. Patent Νos. 5,580,859; 5,910,488) or complexed or encapsulated (e.g., U.S. Patent Νos. 5,908,777; 5,787,567). DΝA can be present in vectors of any kind, for example in a viral or plasmid vector. In some embodiments, nucleic acids used will serve to promote or to inhibit the expression of genes in cells inside and/or outside the electroprocessed matrix. The nucleic acids can be in any form that is effective to enhance its uptake into cells.

Cells as a Substance In embodiments in which cells are a substance, any cell can be used. Cells that can be used include, but are not limited to stem cells, committed stem cells, and differentiated cells. Examples of stem cells that can be used include but are not limited to embryonic stem cells, bone marrow stem cells and umbilical cord stem cells. Other examples of cells used in various embodiments include but are not limited to: osteoblasts, myoblasts, neuroblasts, fibroblasts, glioblasts; germ cells, hepatocytes, chondrocytes, keratinocytes, smooth muscle cells, cardiac muscle cells, connective tissue cells, epithelial cells, endothelial cells, hormone-secreting cells, cells of the immune system, and neurons. In some embodiments it is unnecessary to pre-select the type of stem cell that is to be used, because many types of stem cells can be induced to differentiate in an organ specific pattern once delivered to a given organ. For example, a stem cell delivered to the liver can be induced to become a liver cell simply by placing the stem cell within the biochemical environment of the liver. Cells in the matrix can serve the puφose of providing scaffolding or seeding, producing certain compounds, or both.

Embodiments in which the substance comprises cells include cells that can be cultured in vitro, derived from a natural source, or produced by any other means. Any natural source of prokaryotic or eukaryotic cells may be used. Embodiments in which the matrix is implanted in an organism can use cells from the recipient, cells from a conspecific donor or a donor from a different species, or bacteria or microbial cells. Cells harvested from a source and cultured prior to use are also included.

Some embodiments use cells that are abnormal in some way. Examples include cells that have been genetically engineered, transformed cells, and immortalized cells. One example of genetically engineered cells useful in the present invention is a genetically engineered cell that makes and secretes one or more desired molecules. When electroprocessed matrices comprising genetically engineered cells are implanted in an organism, the molecules produced can produce a local effect or a systemic effect, and can include the molecules identified above as possible substances. Cells can also produce antigenic materials in embodiments in which one of the puφoses of the matrix is to produce an immune response. Cells may produce substances to aid in the following non-inclusive list of puφoses: inhibit or stimulate inflammation; facilitate healing; resist immunorejection; provide hormone replacement; replace neurotransmitters; inhibit or destroy cancer cells; promote cell growth; inhibit or stimulate formation of blood vessels; augment tissue; and to supplement or replace the following tissue, neurons, skin, synovial fluid, tendons, cartilage, ligaments, bone, muscle, organs, dura, blood vessels, bone marrow, and extracellular matrix.

Genetic engineering can involve, for example, adding or removing genetic material to or from a cell, altering existing genetic material, or both. Embodiments in which cells are transfected or otherwise engineered to express a gene can use transiently or permanently transfected genes, or both. Gene sequences may be full or partial length, cloned or naturally occurring.

Substances in the electroprocessed compositions of the present invention also comprise objects. Examples of objects include, but are not limited to, cell fragments, cell debris, organelles and other cell components, tablets, and viruses as well as vesicles, liposomes, capsules, nanoparticles, and other structures that serve as an enclosure for molecules. In some embodiments, the objects constitute vesicles, liposomes, capsules, or other enclosures that contain compounds that are released at a time after electroprocessing, such as at the time of implantation or upon later stimulation or interaction. In one illustrative embodiment, transfection agents such as liposomes contain desired nucleotide sequences to be incoφorated into cells that are located in or on the electroprocessed material or matrix. In other embodiments, cell fragments or cell debris are incoφorated into the matrix. The presence of cell fragments is known to promote healing in some tissues.

Magnetically or electrically reactive materials are also examples of substances that are optionally included within compositions of the present invention. Examples of magnetically active materials include but are not limited to carbon black or graphite, carbon nanotubes, ferrofluids (colloidal suspensions of magnetic particles), and various dispersions of electrically conducting polymers. Ferrofluids containing particles approximately 10 nm in diameter, polymer-encapsulated magnetic particles about 1-2 microns in diameter, and polymers with a glass transition temperature below room temperature are particularly useful. Examples of electrically active polymers include, but are not limited to, electrically conducting polymers such as polyanilines, polypyrroles and ionically conducting polymers such as sulfonated polyacrylamides are related materials.

In other embodiments, some substances in the electroprocessed material or matrix supplement or augment the function of other substances. For example, when the composition comprises cells that express a specific gene, the composition can contain oligonucleotides that are taken up by the cells and affect gene expression in the cells. Fibronectin is optionally incoφorated into the matrix to increase cellular uptake of oligonucleotides by pinocytosis.

As discussed in detail above, the electroprocessed material itself can provide a therapeutic effect. The invention thus includes embodiments involving methods of causing a therapeutic effect through delivery of an electroprocessed material to a location without incoφorating additional substances in the electroprocessed material. Embodiments in which the matrix material alone is delivered as well as those in which other substances are included in the matrix are within the scope of the present invention.

Methods of Making the Composition Electroprocessing

The method of making the compositions includes electroprocessing the materials and optionally electroprocessing the substances. As defined above, one or more electroprocessing techniques, such as electrospin, electrospray, electroaerosol, electrosputter or any combination thereof may be employed to make the electroprocessed materials and matrices in the compositions of the present invention. In the most fundamental sense, the electroprocessing apparatus for electroprocessing material includes a electrodepositing mechanism and a target substrate. The electrodepositing mechanism includes a reservoir or reservoirs to hold the one or more solutions that are to be electroprocessed or electrodeposited. The reservoir or reservoirs have at least one orifice or nozzle to allow the streaming of the solution from the reservoirs. One or a plurality of nozzles may be configured in an electroprocessing apparatus. If there are multiple nozzles, each nozzle is attached to one or more reservoirs containing the same or different solutions. Similarly, there can be a single nozzle that is connected to multiple reservoirs containing the same or different solutions. Multiple nozzles may be connected to a single reservoir. Because different embodiments involve single or multiple nozzles and/or reservoirs, any references herein to one or nozzles or reservoirs should be considered as referring to embodiments involving single nozzles, reservoirs, and related equipment as well as embodiments involving plural nozzles, reservoirs, and related equipment. The size of the nozzles can be varied to provide for increased or decreased flow of solutions out of the nozzles. One or more pumps used in connection with the reservoirs can be used to control the flow of solution streaming from the reservoir through the nozzle or nozzles. The pump can be programmed to increase or decrease the flow at different points during electroprocessing. In this invention pumps are not necessary but provide a useful method to control the rate at which material is delivered to the electric field for processing. Material can be actively delivered to the electric field as a preformed aerosol using devices such as air brushes, thereby increasing the rate of electrodeposition and providing novel combinations of materials. Nozzles may be programmed to deliver material simultaneously or in sequence.

The electroprocessing occurs due to the presence of a charge in either the orifices or the target, while the other is grounded. In some embodiments, the nozzle or orifice is charged and the target is shown to be grounded. Those of skill in the electroprocessing arts will recognize that the nozzle and solution can be grounded and the target can be electrically charged. The creation of the electrical field and the effect of the electrical field on the electroprocessed materials or substances that will form the electroprocessed composition.

The target substrate can also be used as a variable feature in the electroprocessing of materials used to make the electroprocessed composition. Specifically, the target can be the actual substrate for the materials used to make electroprocessed matrix, or electroprocessed matrix itself is deposited. Alternatively, a substrate can be disposed between the target and the nozzles. For instance, a petri dish can be disposed between a nozzles and a target, and a matrix can be formed in the dish. Other variations include but are not limited to non-stick surfaces between the nozzles and target and placing tissues or surgical fields between the target and nozzles. In some embodiments, the use of disinfecting solvents (for example, rubbing alcohol) affords the opportunity to electrospin disinfected materials directly onto living tissue, suggesting an interesting approach for wound care. Electrospun fibers are electrically charged and thus mild static dissipation will generally occur upon grounding, but maintaining very low currents renders the process safe for deposition directly on tissue. This can be seen in Figure 9, where a hand was coated over the course of 30 minutes with a thick mat of EVOH. Tubes can be readily prepared by electrospinning materials onto a syringe needle or other cylindrical objects. Such structures are used as nerve guidance channels, among other cylindrical applications.

The target can also be specifically charged or grounded along a preselected pattern so that the solution streamed from the orifice is directed into specific directions. The electric field can be controlled by a microprocessor to create an electroprocessed matrix having a desired geometry. The target and the nozzle or nozzles can be engineered to be movable with respect to each other thereby allowing additional control over the geometry of the electroprocessed matrix to be formed. The entire process can be controlled by a microprocessor that is programmed with specific parameters that will obtain a specific preselected electroprocessed matrix. It is to be understood that any electroprocessing technique may be used, alone or in combination with another electroprocessing technique, to make the compositions of the present invention.

Any material that can be electroprocessed is within the method of the present invention. Forms of electroprocessed collagen include but are not limited to preprocessed collagen in a liquid suspension or solution, gelatin, particulate suspension, or hydrated gel. An example for fibrin is a preformed gel electroprocessed by subjecting it to pressure, for example by using a syringe or airbrush apparatus with a pressure head behind it to extrude the fibrin gel into the electrical field. In general, when producing fibers using electroprocessing techniques, especially electrospinning, it is preferable to use the monomer of the polymer fiber to be formed. In some embodiments it is desirable to use monomers to produce finer filaments. In other embodiments, it is desirable to include partial fibers to add material strength to the matrix and to provide additional sites for incoφorating substances. Matrix materials such as collagen in a gelatin form may be used to improve the ability of the material to dissolve. Acid extraction method can be used in preparing such gels to maintain the structure of the monomeric subunits. Units can then be treated with enzymes to alter the structure of the monomers.

In embodiments in which two materials combine to form a third material, the solutions containing these components can be mixed together immediately before they are streamed from an orifice in the electroprocessing procedure. In this way, the third material forms literally as the microfibers or microdroplets are formed in the electrospinning process. Alternatively, such matrices can be formed by electrospraying a molecule that can form matrix materials into a moist or otherwise controlled atmosphere of other molecules necessary to allow formation of the matrix to form filaments within the electric field. For example, fibrinogen can be sprayed into a moist atmosphere of thrombin. Materials such as fibrinogen that are capable of forming other materials such as fibrin can also be electrosprayed onto a target that has thrombin. Alternatively thrombin can also be electrosprayed onto a target that has fibrinogen.

In embodiments in which two or more matrix materials are combined to form a third (for example, combining fibrinogen and thrombin to form fibrin) the matrix materials can be electroprocessed in conjunction with or separately from each other, typically under conditions that do not allow the two molecules to form the third until the desired time. This can be accomplished several ways. Using fibrinogen and thrombin as an example, the two matrix materials can be electroprocessed from a solvent that does not allow thrombin to function. Alternatively, the fibrinogen or thrombin can be packaged in a carrier material. In this application the fibrinogen is electroprocessed onto the target from one solution source (by itself or with a carrier), and the thrombin is deposited in an electroaerosol manner from a separate source. The thrombin can be encapsulated and sprayed as a fine mist of particles. Alternatively, thrombin and fibrinogen can be mixed with a carrier, such as PEG, or other synthetic or natural polymers such as collagen. The carrier acts to hold the reactants in place until they are initiated. These methods are not limited to thrombin and fibrinogen and also are used with embodiments involving other combinations of matrix materials that combine to form a third material. The entire product is preferably stored under dry conditions to prevent the reaction of the two materials. When the material is placed in a moist environment, the materials are able to combine and the product matrix material is formed.

As stated above, it is to be understood that carriers can be used in conjunction with matrix materials. Different materials, such as extracellular matrix proteins, and or substances, can be mixed with PEG or other known carriers that form filaments. For example, fibrinogen and collagen can be mixed with PEG or other known carriers that form filaments. This produces "hairy filaments" with the hair being fibrin. The "hairs" cross-link the surrounding matrix carrier into a gel, or provide reactive sites for cells to interact with the substance within the matrix carrier, such as immunoglobulins. This approach can be used for forming a matrix or gelling molecules that do not normally gel. For example, in embodiments in which a specific type of matrix material will not form filaments, then the matrix material can be combined with fibrin and PEG and electrosprayed to form an electroprocessed fibrin-containing matrix. Once fibrin formation begins, a gel of the matrix material and fibrin together is produced.

Alternatively, the material can be sputtered with another molecule that forms a sheet. Examples of molecules that form sheets include PGA, PLA, a copolymer of PGA and PLA, collagen, and fibronectin. In some embodiments, a sheet is formed with two or more materials that can combine to form a third material. This sheet can be placed in a wet environment to allow conversion to the third material.

In addition to the multiple equipment variations and modifications that can be made to obtain desired results, similarly the electroprocessed solution can be varied to obtain different results. For instance, any solvent or liquid in which the material is dissolved, suspended, or otherwise combined without deleterious effect on the process or the safe use of the matrix can be used. Materials or the compounds that form materials can be mixed with other molecules, monomers or polymers to obtained desired results. In some embodiments, polymers are added to modify the viscosity of the solution. In still a further variation, when multiple reservoirs are used, the ingredients in those reservoirs are electrosprayed separately or joined at the nozzle so that the ingredients in the various reservoirs can react with each other simultaneously with the streaming of the solution into the electric field. Also, when multiple reservoirs are used, the different ingredients in different reservoirs can be phased in temporally during the processing period. These ingredients may include substances.

Embodiments involving alterations to the electroprocessed materials themselves are within the scope of the present invention. Some materials can be directly altered, for example, by altering their carbohydrate profile. Also, other materials can be attached to the matrix materials before, during or after electroprocessing using known techniques such as chemical cross-linking or through specific binding interactions (e.g. PDGF binds to collagen at a specific binding site).

Further, the temperature and other physical properties of the process can be modified to obtain different results. The matrix may be compressed or stretched to produce novel material properties.

Still further chemical variations are possible. Fibrin, for example, is formed in different ways. Building an electroprocessed matrix comprised of fibrin, therefore, involves different ways of bringing the molecules capable of forming fibrin, such as fibrinogen and thrombin, together through electroprocessing methods. Electroprocessed materials and matrices can also be manipulated after they are formed with the electroprocessing methods.

A matrix of electroprocessed fibers, in accordance with the present invention, can be produced as described below. In the case of electrospun fibrin, while any molecules capable of forming fibrin can be used, it is preferable to electroprocess fibrinogen or thrombin to make fibrin fibers.

Electroprocessing using multiple jets of different polymer solutions and/or the same solutions with different types and amounts of substances (e.g., growth factors) can be used to prepare libraries of biomaterials for rapid screening. Such libraries are desired by those in the pharmaceutical, advanced materials and catalyst industries using combinatorial synthesis techniques for the rapid preparation of large numbers (e.g., libraries) of compounds that can be screened. For example, the minimum amount of growth factor to be released and the optimal release rate from a fibrous polymer scaffold to promote the differentiation of a certain type of cell can be investigated using the compositions and methods of the present invention. Other variables include fiber diameter and fiber composition. Electroprocessing permits access to an array of samples on which cells can be cultured in parallel and studied to determine selected compositions which serve as promising cell growth substrates.

Any effective conditions can be used to electroprocess a matrix. While the following is a description of a preferred method, other protocols can be followed to achieve the same result. Referring to Figure 1 in electrospinning fibers, micropipettes 10 are filled with materials and suspended above a grounded target 11, for instance, a metal ground screen placed inside the central cylinder of the RCCS bioreactor. Although this embodiment involves two micropipettes acting as sources of materials, the present invention includes embodiments involving only one source or more than two sources. A fine wire 12 is placed in the solution to charge the solution in each pipette tip 13 to a high voltage. At a specific voltage determined for each solution and apparatus arrangement, the solution suspended in each pipette tip is directed towards the grounded target. This stream 14 of materials may form a continuous filament, for example when collagen is the material, that upon reaching the grounded target, collects and dries to form a three- dimensional, ultra thin, interconnected matrix of electroprocessed collagen fibers. Depending upon reaction conditions a single continuous filament may be formed and deposited in a non- woven matrix.

As noted above, combinations of electroprocessing techniques and substances are used in some embodiments. Referring now to Figure 2, micropipette tips 13 are each connected to micropippettes 10 that contain different materials or substances. The micropipettes are suspended above a grounded target 11. Again, fine wires 12 are used to charge the solutions. One micropipette produces a stream of collagen fibers 14. Another micropipette produces a steam of electrospun PLA fibers 16. A third micropipette produces an electroaerosol of cells 17. A fourth micropipette produces an electrospray of PLA droplets 18. Although the micropipettes are attached to the same voltage supply 15, PLA is electrosprayed rather than electrospun from the fourth micropipette due to variation in the concentration of PLA in the solutions. Alternatively, separate voltage supplies (not shown) can be attached to each micropipette to allow varying electroprocessing methods to be used through application of different voltage potentials.

Similarly, referring now to Figure 8, the same material can be applied as electrospun fibers 19 from one of the two micropipettes and electrosprayed droplets 20 from the other micropipette disposed at a different angles with respect to the grounded substrate 11. Again, the micropipette tips 13 are attached to micropipettes 10 that contain varying concentrations of materials and thus produce different types of electroprocessed streams despite using the same voltage supply 15 through fine wires 12.

Minimal electrical current is involved in this process, and, therefore, electroprocessing, in this case electrospinning, does not denature the materials that form the electroprocessed materials, because the current causes little or no temperature increase in the solutions during the procedure. In melt electrospinning, there is some temperature increase associated with the melting of the material. In such embodiments, care is exercised to assure that the materials or substances are not exposed to temperatures that will denature or otherwise damage or injure them. An electroaerosoling process can be used to produce a dense, matte-like matrix of electroprocessed droplets of material. The electroaerosoling process is a modification of the electrospinning process in that the electroaerosol process utilizes a lower concentration of matrix materials or molecules that form electroprocessed materials during the procedure. Instead of producing a splay of fibers or a single filament at the charge tip of the nozzle, small droplets are formed. These droplets then travel from the charged tip to the grounded substrate to form a sponge-like matrix composed of fused droplets. In some embodiments, the droplets are less than 10 microns in diameter. In other embodiments a construct composed of fibrils with droplets, like "beads on a string" may be produced. Droplets may range in size from 100 nanometers to 10 microns depending on the polymer and solvents. Where such moφhology is undesirable, processing aids are added to the solution prior to electroprocessing. For example, bead formation in a solution of PNA and TRITON X-100 was reduced or removed by adding acetic acid to the PV A/Triton solution prior to electrospinning to afford smoother fibers. The amount of acetic acid added was about 5-14% by weight relative to the weight of the PVA in solution. Any processing aid that will augment or reduce the formation of beads as desirable may be used. While not wanting to be bound to the following statement it is believed that acetic acid increased the net charge density of the polymer solution by addition of acetic acid. Acids or other materials or substances that increase the net charge density of the polymer solution can be used. In some embodiments, higher net charge density not only favors formation of polymer fibers without beads but also leads toward formation of thinner fibers. Addition of surfactant also facilitates formation of smooth fibers because the surface tension drives toward the formation of beads. While not wanting to be bound to the following statement it is believed that reducing surface tension with surfactant favors formation of fibers without beads. Moreover, additional isopropanol also helps in electrospinning since it increases the volatility of the solvent.

As with the electrospinning process described earlier, the electroaerosol process can be carried out using various effective conditions. The same apparatus that is used in the electrospinning process, for instance as shown in Figure 1, is utilized in the electroaerosol process. The differences from electrospinning include the concentration of the materials or substances that form matrix materials placed in solution in the micropipette reservoir and/or the voltage used to create the stream of droplets. One of ordinary skill in the art recognizes that changes in the concentration of materials or substances in the solutions requires modification of the specific voltages to obtain the formation and streaming of droplets from the tip of a pipette.

The electroprocessing process can be manipulated to meet the specific requirements for any given application of the electroprocessed compositions made with these methods. In one embodiment, the micropipettes can be mounted on a frame that moves in the x, y and z planes with respect to the grounded substrate. The micropipettes can be mounted around a grounded substrate, for instance a tubular mandrel. In this way, the materials or molecules that form materials streamed from the micropipettes can be specifically aimed or patterned. Although the micropipettes can be moved manually, the frame onto which the micropipettes are mounted is preferably controlled by a microprocessor and a motor that allow the pattern of streaming collagen to be predetermined by a person making a specific matrix. Such microprocessors and motors are known to one of ordinary skill in the art. For instance, matrix fibers or droplets can be oriented in a specific direction, they can be layered, or they can be programmed to be completely random and not oriented. In the electrospinning process, the stream or streams can branch out to form fibers. The degree of branching can be varied by many factors including, but not limited to, voltage, ground geometry, distance from micropipette tip to the substrate, diameter of micropipette tip, and concentration of materials or compounds that will form the electroprocessed materials. As noted, not all reaction conditions and polymers may produce a true multifilament, under some conditions a single continuous filament is produced. Materials and various combinations can also be delivered to the electric field of the system by injecting the materials into the field from a device that will cause them to aerosol. This process can be varied by many factors including, but not limited to, voltage (for example ranging from about 0 to 30,000 volts), distance from micropipette tip to the substrate (for example from 0-40 cm), the relative position of the micropipette tip and target (i.e. above, below, aside etc.), and the diameter of micropipette tip (approximately 0-2 mm). Several of these variables are well-known to those of skill in the art of electrospinning microfiber textile fabrics.

The geometry of the grounded target can be modified to produce a desired matrix. By varying the ground geometry, for instance having a planar or linear or multiple points ground, the direction of the streaming materials can be varied and customized to a particular application. For instance, a grounded target comprising a series of parallel lines can be used to orient electrospun materials in a specific direction. The grounded target can be a cylindrical mandrel whereby a tubular matrix is formed. Most preferably, the ground is a variable surface that can be controlled by a microprocessor that dictates a specific ground geometry that is programmed into it. Alternatively, for instance, the ground can be mounted on a frame that moves in the x, y, and z planes with respect to a stationary micropipette tip streaming collagen.

The substrate onto which the materials are streamed, sprayed or sputtered can be the grounded target itself or it can be placed between the micropipette tip and the grounded target. The substrate can be specifically shaped, for instance in the shape of a nerve guide, skin patch, fascial sheath, or a vascular graft for subsequent use in vivo. The electroprocessed compositions can be shaped to fit a defect or site to be filled. Examples include a site from which a tumor has been removed, an injury site in the skin (a cut, a biopsy site, a hole or other defect) and a missing or shattered piece of bone. The electroprocessed compositions may be shaped into shapes useful for substance delivery, for example, a skin patch, a lozenge for ingestion, an intraperitoneal implant, a subdermal implant, the interior lining of a stent, a cardiovascular valve, a tendon, a ligament a dental prosthesis, a muscle implant, or a nerve guide. Electroprocessing allows great flexibility and allows for customizing the construct to virtually any shape needed. Many matrices are sufficiently flexible to allow them to be formed to virtually any shape. In shaping matrices, portions of the matrix may be sealed to one another by, for example, heat sealing, chemical sealing, and application of mechanical pressure or a combination thereof. An example of heat sealing is the use of crosslinking techniques discussed herein to form crosslinking between two portions of the matrix. Sealing may also be used to close an opening in a shaped matrix. Suturing may also be used to attach portions of matrices to one another or to close an opening in a matrix. It has been observed that inclusion of synthetic polymers enhances the ability of matrices to be heat sealed. Other variations of electroprocessing, particularly electrospinning and electroaerosoling include, but are not limited to the following:

1. Using different solutions to produce two or more different fibers or droplets simultaneously (fiber or droplet array). In this case, the single component solutions can be maintained in separate reservoirs.

2. Using mixed solutions (for example, materials along with substances such as cells, growth factors, or both) in the same reservoir(s) to produce fibers or droplets composed of electroprocessed materials as well as one or more substances (fiber composition "blends"). Nonbiological but biologically compatible material can be mixed with a biological molecule. 3. Utilizing multiple potentials applied for the different solutions or the same solutions.

4. Providing two or more geometrically different grounded targets (i.e. small and large mesh screens).

5. Placing the mold or mandrel or other ungrounded target in front of the grounded target.

6. Applying agents such as Teflon onto the target to facilitate the removal of electroprocessed materials from the target (i.e. make the material more slippery so that the electroprocessed materials do not stick to the target).

7. Forming an electroprocessed material that includes materials applied using multiple electroprocessing methods. For example, electrospun fibers and electroaerosol droplets in the same composition can be beneficial for some applications depending on the particular structure desired. This combination of fibers and droplets can be obtained by using the same micropipette and solution and varying the electrical charge; varying the distance from the grounded substrate; varying the polymer concentration in the reservoir; using multiple micropipettes, some for streaming fibers and others for streaming droplets; or any other variations to the method envisioned by those of skill in this art. The fibers and droplets can be layered or mixed together in same layers. In applications involving multiple micropipettes, the micropipettes can be disposed in the same or different directions and distances with reference to the target. 8. Using multiple targets.

9. Electroprocessing to form the electroprocessed material upon or at an object or location suspended in midair in the space between the source and the target.

10. Preheating the solution and allowing it to cool to aid in the dissolution or suspension of a material within a solvent. 11. Use of processing aids to facilitate electroprocessing or to control fiber moφhology.

12. Electroprocessing from a suspension, emulsion, or dispersion containing two or more phases of liquids. All these variations can be done separately or in combination to produce a wide variety of electroprocessed materials and substances.

The various properties of the electroprocessed materials can be adjusted in accordance with the needs and specifications of the cells to be suspended and grown within them. The porosity, for instance, can be varied in accordance with the method of making the electroprocessed materials or matrix. Electroprocessing a particular matrix, for instance, can be varied by fiber (droplet) size and density. If the cells to be grown in the matrix require a great deal of nutrient flow and waste expulsion, then a loose matrix can be created. On the other hand, if the tissue to be made requires a very dense environment, then a dense matrix can be designed. Porosity can be manipulated by mixing salts or other extractable agents. Removing the salt will leave holes of defined sizes in the matrix.

One embodiment for appropriate conditions for electroprocessing fibrin is presented below. For electroprocessing fibrin by combining fibrinogen and thrombin, the appropriate approximate ranges are: voltage 0-30,000 volts; pH 7.0 to 7.4; calcium 3 to 10 mM; temperature 20 to 40°C; ionic strength 0.12 to 0.20 M; thrombin 0.1 to 1.0 units per milliliter (ml); and fibrinogen 5 to 25 mg/ml. For electroprocessing fibrin monomer, the pH starts at 5 and increases to 7.4 while the ionic strength starts above 0.3 M and decreases to 0.1 M. The other conditions are similar as stated within this paragraph. Electroprocessed fibrin matrices of varying properties can be engineered by shifting the pH, changing the ionic strength, altering the calcium concentration, or adding additional polymeric substrates or cationic materials. For electroprocessing collagen, the appropriate approximate ranges are: voltage 0-30,000 volts; pH 7.0 to 8.0; temperature 20 to 42°C; and collagen 0 to 5 mg/ml. Electroprocessed collagen matrices of varying properties can be engineered by shifting the pH, changing the ionic strength (e.g. addition of organic salts), or adding additional polymeric substrates or cationic materials.

The material to be electroprocessed can be present in the solution at any concentration that will allow electroprocessing. In one embodiment, the materials to be electroprocessed are present in the solution at concentrations between 0 and about 1.000 g/ml. In another embodiment, the materials to be electroprocessed are present in the solution at concentrations between 0 and about 0.100 g/ml. In another embodiment, the materials to be electroprocessed are present in the solution at concentrations between 0 and about 0.085 g/ml. In another embodiment, the materials to be electroprocessed are present in the solution at concentrations between 0 and about 0.045 g/ml. In another embodiment, the materials to be electroprocessed are present in the solution at concentrations between 0 and about 0.025 g/ml. In another embodiment, the materials to be electroprocessed are present in the solution at concentrations between 0 and about 0.005 g/ml. Examples of embodiments also include, without limitation, those in which the materials to be electroprocessed are present in the solution at concentrations in each of the following ranges: between approximately 0.025 g/ml and approximately 0.045 g/ml; between approximately 0.045 g/ml and approximately 0.085 g/ml; between approximately 0.085 g/ml and approximately 0.100 g/ml; and between approximately 0.100 g/ml; and approximately 1.000 g/ml.

Shapes of Electroprocessed Materials and Matrices

Electroprocessed materials can be electrodeposited inside a specifically shaped mold. For instance, a particular type of organ or tissue that to be replaced has a specific shape, such as a skin patch to fit a biopsy site or a large scalp area following a wide area removed after discovering a malignant melanoma. That shape is then reproduced and created inside a mold designed to mimic that shape. This mold can be filled by electrodepositing the material into it. In this way, the matrix exactly mimics the mold shape. In some embodiments, matrices that will become extracellular matrices and that have a specific shape are used in the creation of a new organ. Hollow and solid organs can be made. Mixing cells with the material during electrospraying forms cells within the matrix so that they do not have to migrate into a matrix.

Methods of Combining Substances with Electroprocessed Materials

Substances can be combined with the electroprocessed materials by a variety of means. In some embodiments, the substance comprises molecules to be released from the electroprocessed material and is therefore added to or incoφorated within the matrix of electroprocessed material. Substances can be mixed in the solvent carriers or solutions of materials for electroprocessing. In this system materials can be mixed with various substances and directly electroprocessed. The resulting composition comprising an electroprocessed matrix and substance can be topically applied to a specific site and the substances released from the material as a function of the material undergoing breakdown in the surrounding environment. Substances may also be released from the electroprocessed compositions of the present invention through diffusion.

The state of the electroprocessed material in relation to the incoφorated substances is dictated and can be controlled by the chemistry of the system and varies based on the selection of matrix materials, solvent(s) used, and solubility of the matrix materials in those solvents. These parameters can be manipulated to control the release of the substances (or other elements into the surrounding environment). If substances to be incoφorated into the electroprocessed material are not miscible with the material, separate solvent reservoirs for the different components can be used. Mixing in such an embodiment occurs prior to, during, and/or after deposition on the target, or a combination thereof. It is to be understood that substances may be entrapped or entangled within an electroprocessed material, bonded to a material before the material undergoes electroprocessing, contained within cavities, enclosures, inclusions, or pockets of the individual objects, bodies, or structures of electroprocessed material (e.g. fibers, fibrils, films, sprays, particles, or droplets) or bound to specific sites within the matrix material.

In a variation of this embodiment, the substance is a particle or aggregate comprising a matrix of compounds or polymers such as alginate that, in turn, contain one or more compounds that will be released from the electroprocessed material. Drugs can be combined with alginate by, for example, combining a drug suspension or drug particulate in the alginate in the presence of calcium. Alginate is a carbohydrate that forms aggregates when exposed to calcium, the aggregates can be used to trap drugs. The aggregates dissolve over time, releasing the trapped substances, such as cells trapped in alginate. The particles, which are then incoφorated within the larger electroprocessed matrix, are biologically compatible but relatively stable and will degrade gradually. In some circumstances, the electroprocessed materials resemble a string of pearls. This is a physical aspect of the electroprocessing. If the polymer concentration is low, electrospraying of beads occurs. As polymer concentration increases there are some beads and some fibers. A further increase in polymer concentration leads to predominantly or all fibers. Therefore, the appearance of the pearls on a string is a transition phase.

If a drug (for example, penicillin) does not bind or interact with an electrospun matrix material, the drug can be entrapped in PGA or PLA pellets or electroaerosoled to produce pellets in the electrospun material. The pellets or electroaerosoled droplets containing the drug begin to dissolve after administration to deliver the entrapped material. Some agents can be coupled to synthetic, or natural polymer by a covalent bond, prior to or after spinning.

In other embodiments, the substance is electroprocessed. Substances can be electroprocessed from the same orifice as the materials or from different orifices. Substances can also be subjected to the same or a different type of electroprocessing as the material. A molecule can be bonded to the electroprocessed material directly or through linking to a molecule that has an affinity for the material. An example of this embodiment involves bonding polypeptide substances to heparin, which has an affinity for collagen materials. This embodiment allows release relate to be controlled by controlling the rate of degradation of the material, for example by enzymatic or hydrolytic breakdown.

In other embodiments, the electroprocessed material can entrap substance during the electrodeposition process. This can be accomplished by disposing substances in the space between the source of the electroprocessed stream and the target for the electroprocessed material. Placing such substances in the space between the source and target can be accomplished by a number of methods, including but not limited to, suspending in air or other gases, dripping, spraying, or electroprocessing the substances. The substances can be present in that space in, for example, particulate, aerosol, colloidal, or vapor form. In these embodiments, the electroprocessed material or matrix will physically entrap the substances. This embodiment can also be used to encapsulate larger particles, such as cells, large particles, or tablets. For example, if a tablet is dropped through the matrix as it forms, the tablet is surrounded by the matrix. If a small object, like a cell is dropped through the matrix as it forms or placed in an aerosol within the matrix, the object may be trapped between filaments, within filaments or "attached to the outside of the filaments. For example, by suspending cells in a solution or within a matrix, the cells can become part of an electrospun matrix during fabrication of the filaments. Alternatively, encapsulation can occur by dropping substances onto or through a matrix material stream as a matrix forms. The cells thus become surrounded by a matrix of electroprocessed material. These embodiments can be used to incoφorate within a matrix substances that are not soluble and/or are too large to form a suspension in the solvent used for the production of the material. For substances in a mist or vapor form, controlling distribution and composition of substances in the space between the source and target can be used to alter the physical and chemical properties of the electroprocessed material and the pattern of distribution of the substances in the electroprocessed material. For all of the foregoing embodiments, the substances can be placed in the electroprocessed material in capsules, vesicles, or other containments for subsequent release. Since the solvent carrier often evaporates in the electroprocessing technique as the electroprocessed material forms, such as a filament, substances may be placed in the electroprocessed matrix and solvent toxicity is greatly reduced or eliminated. In embodiments wherein the substance comprises cells, the cells can, for example, be suspended in a solution or other liquid that contains the material to be electroprocessed, disposed in the area between the solutions and target, or delivered to a target or substrate from a separate source before, during, or after electroprocessing. Cells can be dripped through the matrix, onto the matrix as it deposits on the target or suspended within an aerosol as a delivery system for the cells to the electroprocessed material. The cells can be delivered in this manner while the matrix is being formed. As an example, cardiac fibroblasts were suspended in phosphate-buffered saline (PBS) at a concentration of approximately one million cells per milliliter. The suspension of cells was placed within a reservoir of a Paasche air brush. To test the efficacy of using this type of device to deliver cells, the cell suspension was initially sprayed onto a 100 mm culture dish. Some of the cells survived, attached to the dish and spread out over the substratum. In a second trial, the culture dish was located further away from the air brush and the experiment was repeated. Cells were observed on the dish. They appeared to be flattened by the impact and were partially spread out over the surface of the substratum. Culture media was added to the dish and the cells were placed into an incubator. After one hour of culture, the cells were inspected again, and many were found to have spread out further over the substratum. These results demonstrate that a simple airbrush device can be used to place cells into an aerosol droplet and deliver them on demand to a surface or site of interest. Cell viability can be improved by restricting this technique to cells that are resistant to the shear forces produced in the technique, developing a cell suspension with additives that cushions the cells or refining the aerosolizing device to produce a more laminar flow. In addition, directing the cell aerosol into matrix materials as the matrix is forming in the space between the target or mandrel and the source(s) of molecules being electroprocessed produces the effect of cushioning the cells. While not wanting to be bound by the following statement, it is believed that the cells will be trapped in the storm of filaments or other bodies produced by electrospinning or electroprocessing and pulled onto the mandrel. This situation may be less traumatic to the cells than directly spraying the cells onto a solid surface.

In some embodiments, the cells are placed in a liquid phase that is dispersed, emulsified, or suspended within a phase that contains the material to be electroprocessed. This results in the formation of electroprocessed materials possessing cells contained within cavities, inclusions, enclosures, or pockets in individual objects, bodies, or structures of electroprocessed material (e.g. fibers, fibrils, films, sprays, particles, or droplets)..

In one embodiment, the cells are added either before or at the same time as the materials or compounds that form electroprocessed materials are brought together. In this way, the cells are suspended throughout the three-dimensional matrix. In embodiments in which the electroprocessed material comprises fibrin formed by combining thrombin and fibrinogen, the cells are typically included in the mixture that contains the fibrinogen (whether it is plasma or purified fibrinogen). Whenever materials comprise two or more separate materials that combine to form a different material (such as fibrinogen and thrombin) bringing the materials together immediately prior to insertion into a mold, or immediately prior to the streaming step in the electrospinning process helps result in a good distribution of cells in suspension in the resulting extracellular matrix.

Cells can be added as the filaments are produced in the space between the target and polymer source. This is accomplished by dripping the cells onto the target, dripping the cells into the matrix as it forms, aerosoling the cells into the matrix or onto the target or electrospraying the cells into the matrix as it condenses and forms near or on the grounded target. In another embodiment, cells are sprayed or dribbled into a forming electroprocessed material or matrix and thereby trapped as the electroprocessed material crosses the air gap between the source solutions and target.

An alternative method to deliver cells to an electroprocessed material involves electroaerosol delivery of the cells. Cells can be deposited by electrostatic spraying at, foi example, 8kV directly onto standard polystyrene culture dishes, suggesting that electrostatic cell spraying is a viable approach. Cardiac fibroblasts in phosphate buffered saline (PBS) have been electroaerosoled up to a 20 Kv potential difference. In another example, Schwann cells (rat) were plated on a PS petri dish by conventional methods after one day. Schwann cells were also electrosprayed onto a PS petri dish with a metal ground plate behind the dish at lOkV after one day. Both samples grew to almost confluence after one week. The electroaerosol approach provides some distinct advantages. First, the shear forces produced during the delivery phase (i.e. the production of the aerosol) appear to be much less traumatic to the cells. Second, the direction of the aerosol can be controlled with a high degree of fidelity. In essence the cell aerosol can be painted onto the surface of interest. This allows the cell to be targeted to specific sites. In electroaerosol delivery, cells are suspended in an appropriate media (e.g. culture media, physiological salts, etc.) and charged to a voltage, and directed towards a grounded target. This process is very similar to that used in electroprocessing, particularly electrospinning. The produces a fine mist of cells trapped within the droplets as they are produced and directed at the grounded target. Cells can be delivered using aerosol and electroaerosol techniques onto an electroprocessed material that is forming by an electroprocessing technique. The electroaerosol of cells can be delivered in parallel (i.e. alongside) the electroprocessing material or from a separate site. The cells can be delivered to the storm of filaments or particles produced within the air gap in the electrodeposition process or directed at the target. The cells and electroprocessed material also can be delivered in an alternating sequence to the target, i.e. electrodeposit the material, aerosol the cells, electrodeposit the material, aerosol the cells. This allows for the discrete layering of the construct in separate layers. Furthermore, a vapor source can be provided that directs water onto the mandrel of target used to collect the cells. Providing this moisture improves cell viability by keeping the cells from dehydrating during processing. Cells can be added to the electroprocessed material at any time or from any orientation in any aerosol strategy. Again the advantage of the process in general is that collagen, for example, collects in a dried state on the target mandrel. Accordingly, although some solvents for collagen may be toxic, they are lost from the system before the filaments collect on the target.

Cells can also be trapped within a carrier prior to producing an aerosol. For example, cells can be encapsulated within a material like alginate. The encapsulated cells are physically protected from shear and trauma during processing. Cells delivered in this form to the electroprocessed material will have higher viability when sprayed or electrostatically seeded.

An electroaerosol or otherwise electroprocessed material can also be delivered directly to an in situ site. For example, an electroprocessed material can be produced directly onto a skin wound, with or without substances such as molecules or cells. Additional cells or materials can then be aerosolized or electroprocessed onto or into the wound site. Other surgical sites can also be amenable the delivery of materials using various electrodeposition techniques or combinations thereof of these methods.

In other embodiments, substances can be applied to the electroprocessed material after formation, for example by soaking the electroprocessed material in the substance or by spraying the substance onto the electroprocessed material.

Persons skilled in the art will recognize that more than one method for combining the substances with electroprocessed materials can be used in a single embodiment or application. Combining methods can be especially useful in embodiments involving release of more than one compound or compounds intended to have complex release kinetics, although such combinations are not limited to those embodiments.

Magnetically and electrically active materials can be electroprocessed, including, for example, preparing conducting polymer fibers produced by electrospinning. In addition, conducting polymers can be prepared in-situ in the matrix by, for example, incoφoration of a monomer (e.g., pyrrole) followed by treatment with polymerization initiator and oxidant (e.g., FeCl₃). Finally, conducting polymers can be grown in the material after electroprocessing by using a matrix-coated conductor as the anode for electrochemical synthesis of, for example, polypyrrole or polyaniline. Compounds that can form electroprocessed materials can be added to an aqueous solution of pyrrole or aniline to create a conducting polymer at the anode with the entrapped electroprocessed material-forming compounds, which can then be treated with other compounds to allow formation of the material to occur.

Patterns of electroprocessed materials and substance distribution

Many embodiments of the present invention involve means for manipulating the pattern or distribution of electroprocessed materials and/or substances within an electroprocessed material. For example, an electroprocessing target can also be specifically charged or grounded along a preselected pattern so that electroprocessed materials streamed toward the target are directed into specific directions or distributions on the target or on a substrate. The electric field can be controlled by a microprocessor to create a matrix having a desired geometry. The target and the electroprocessing nozzle or nozzles can be movable with respect to each other and to the target thereby allowing additional control over the geometry of the electroprocessed material to be formed. In embodiments in which substances are electroprocessed, this manipulation will also allow control of the distribution of substances within the electroprocessed materials. For example a matrix can be prepared on a mandrel, and substances from a separate reservoir can be sprayed, dripped, electroprocessed in a specific pattern over the existing matrix. This may also be accomplished by simultaneously electrospraying a matrix from one source and a substance from another source. In this example the matrix source may be stationary and the substance source is moved with respect to the target mandrel.

Other features that allow establishment of such a pattern include, but are not limited to, the ability to deposit multiple layers of the same or different materials, combining different electroprocessing methods, the use multiple orifices with different contents for electroprocessing, and the existence of numerous methods for combining substances with the materials. For example, a gradient of substances can be created along a electroprocessed material. In embodiments in which the matrix is shaped into a cylindrical construct, for example, the gradient can be prepared along the long axis of a constmct (left to right) or the peφendicular axis (inside to out). This configuration is used to provide a chemoattractant gradient to guide the movement of cells within a specified site. Thus, for example, in some embodiments in which neovasculai agents are prepared in a peφendicular gradient along a collagen-based constmct, the agents can be concentrated on the dorsal surface of a sheet of the material. The ventral side can be placed against a wound and the higher concentration of angiogenic materials on the dorsal surface of the constmct will increase the migration of endothelial cells through the electrospun material. Again, embodiments with complex patterns can use a microprocessor programmed with the specific parameters to obtain a specific, preselected electroprocessed pattern of one or more electroprocessed polymers, optionally with one or more substances.

Uses for the Compositions of the Present Invention Substance delivery

One use of the compositions of the present invention is the delivery of one or more substances to a desired location. In some embodiments, the electroprocessed materials are used simply to deliver the materials itself. In other embodiments, the electroprocessed materials are used to deliver substances that are contained in the electroprocessed material or that are produced or released by substances contained in the electroprocessed material. For example, an electroprocessed material containing cells can be implanted in a body and used to deliver molecules produced by the cells after implantation. The present compositions can be used to deliver substances to an in vivo location, an in vitro location, or other locations. The present compositions can be administered to these locations using any method.

In the field of substance delivery, the compositions of the present invention have many attributes that allow delivery of substances using a wide variety of release profiles and release kinetics. For example, selection of the substance and the method by which the substance is combined with the electroprocessed material affects the substance release profile. To the extent that the substances are not immobilized by the electroprocessed material, release from the electroprocessed material is a function of diffusion. An example of such an embodiment is one in which the substance is sprayed onto the electroprocessed material. To the extent that the substances are immobilized by the electroprocessed material, release rate is more closely related to the rate at which the electroprocessed material degrades. An example of such an embodiment is one in which the substance is covalently bonded to the electroprocessed material. For a substance is trapped within an electrospun aggregate or filament, release kinetics would be determined by the rate at which the surrounding material degrades or disintegrates. Still other examples are substances that are coupled to the electroprocessed material by a light sensitive bond. Exposing such a bond to light releases the substance from the electroprocessed material. Conversely, in some embodiments of this invention, materials can be exposed to light to cause binding of agents in vivo or in vitro. Combining the compound with the electroprocessed material in solution, rather than in suspension, will result in a different pattern of release and thereby provide yet another level of control for the process. Further, the porosity of the electroprocessed material can be regulated, which affects the rate of release of a substance. Enhanced porosity facilitates release. Substance release is also enhanced by fragmenting or pulverizing the electroprocessed material. Pulverized material can, for example be applied to a wound site, ingested or formed into another shape such as a capsule or a tablet. In embodiments in which the substance is present in the form of a large particle such as a tablet encapsulated in the electroprocessed material or a molecule trapped inside an electroprocessed filament, release is dictated by a complex inteφlay of the rate the particles dissolve or degrade and any breakdown or degradation of the electroprocessed material structure. In embodiments in which the substance comprises cells that will express one or more desired compounds, factors that affect the function and viability of the cells and the timing, intensity, and duration of expression can all affect the release kinetics. Chemicals that affect cell function, such as oligonucleotides, promoters or inhibitors of cell adhesion, hormones, and growth factors, for example, can be incoφorated into the electroprocessed material and the release of those substances from the electroprocessed material can provide a means of controlling expression or other functions of cells in the electroprocessed material. Release kinetics in some embodiments are manipulated by cross-linking electroprocessed material through any means. In some embodiments, cross-linking will alter, for example, the rate at which the electroprocessed material degrades or the rate at which a compound is released from the electroprocessed material by increasing structural rigidity and delaying subsequent dissolution of the electroprocessed material. Electroprocessed materials can be formed in the presence of cross-linking agents or can be treated with cross-linking agents after electrodeposition. Any technique for cross-linking materials may be used as known to one of ordinary skill in the art Examples of techniques include application of cross-linking agents and application of certain cross-linking radiations. Examples of cross-linking agents that work with one or more proteins include but are not limited to condensing agents such as aldehydes e.g., glutaraldehyde, carbodiimide EDC (l-ethyl-3(3 dimethyl aminopropyl)), photosensitive materials that cross link upon exposure to specific wavelengths of light, osmium tetroxide, carbodiimide hydrochloride, and NHS (n-hydroxysuccinimide), and Factor XHIa. Ultraviolet radiation is one example of radiation used to crosslink matrix materials in some embodiments. Natural materials can be cross- linked with other natural materials. For example, collagen can be cross-linked and or stabilized by the addition of fibronectin and or heparin sulfate. For some polymers heat can be used to alter the matrix and cross link elements of the matrix by fusing adjacent components of the constmct. Polymers may also be partially solubilized to alter the structure of the material, for example brief exposure of some synthetics to alcohols or bases can partially dissolve and anneal adjacent filaments together. In some embodiments, polymers are cross-linked using chemical fusion or heat fusion techniques. Synthetic polymers generally can be cross-linked using high energy radiation (e.g., electron beams, gamma rays). These typically work by the creation of free radicals on the polymer backbone which then couple, affording cross links. Backbone free radicals can also be generated via peroxides, azo compounds, aryl ketones and other radical- producing compounds in the presence of heat or light. Reduction-oxidation reactions that produce radicals (e.g., peroxides in the presence of transition metal salts) can also be used. In many cases, functional groups on polymer backbones or side chains can be reacted to form cross-links. For example, polysaccharides can be treated with diacylchlorides to form diester cross-links. Cross- linking may also occur after application of a matrix where desirable. For example, a matrix applied to a wound may be cross-linked after application to enhance adhesion of the matrix to the wound.

In other embodiments, the rate at which the electroprocessed material degrades or dissolves is manipulated by other means. One example is treatment with a compound that will make the electroprocessed material resistant to dissolution in aqueous solutions. In some embodiments, materials are treated with chemicals that increase the crystallinity of their structure. In some embodiments, materials are treated with lower alcohols. In one embodiment, poly(vinyl alcohol) is treated with methanol, resulting in a resistance to dissolution in water.

The release kinetics of the substance is also controlled by manipulating the physical and chemical composition of the electroprocessed material. For example, small fibers of PGA are more susceptible to hydrolysis than larger diameter fibers of PGA. An agent delivered within an electroprocessed material composed of smaller PGA fibers is released more quickly than when prepared within a material composed of larger diameter PGA fibers.

In some embodiments substances such as peptides can be released in a controlled manner in a localized domain. Examples include embodiments in which the substance is chemically or covalently bonded to the electroprocessed material. The formation of peptide gradients is a critical regulatory component of many biological processes, for example in neovasculogenesis. In surgical applications, anti-vascular peptides or anti-sense oligonucleotides can be incoφorated into an electroprocessed material that is then wrapped around or placed within a tumor that is inaccessible to conventional treatments to allow for localized release and effect. Release of the anti-vascular substances suppresses tumor growth. Antisense oligonucleotides can be released from the construct into the tumor and used to suppress the expression gene sequences of interest. In another example anti-sense sequences directed against gene sequences that control proliferation can be delivered within an electroprocessed matrix coated stent. The stretch normally associated with the placement of the stent initiates smooth muscle cell proliferation, and anti-sense sequences designed to suppress cell division reduce the deleterious effects of the smooth muscle cell proliferation associated with the procedure. In another embodiments, the electroprocessed material delivers sense and antisense oligonucleotides to promote or to inhibit localized cell function for a period of time. For example, an antisense oligonucleotide is released from an electroprocessed material to suppress the expression of a deleterious enzyme in a wound. Examples of such enzymes are matrix metalloproteinases (MMPs), which are often overexpressed in chronic wounds. In another example, the electroprocessed material applied to a wound releases plasmids that contain nucleotide sequences coding for tissue inhibitors of metalloproteinases (TIMPs). Cells in the wound will express TIMPs, resulting in local delivery of TIMPs that will inhibit MMP function. Physical processing of the formed electroprocessed material is another way to manipulate release kinetics. In some embodiments, mechanical forces, such as compression, applied to an electroprocessed material hasten the breakdown of the matrix by altering the crystalline structure of the material. Structure of the matrix is thus another parameter that can be manipulated to affect release kinetics. Polyurethanes and other elastic materials such as poly(ethylene-co-vinyl acetate), silicones, and polydienes (e.g., polyisoprene), polycaprolactone, polyglycolic acid and related polymers are examples of materials whose release rate can be altered by mechanical strain. The use of multi-phase compositions for use in electroprocessing provides an additional level of control of release profiles. It also provides additional uses of electroprocessed materials and compositions to produce desired biological effects. For example, in some embodiments, substances are used to enhance or deter growth of selected cell types by providing extracellular cues. Examples of such embodiments include incoφoration of species-specific cell surface molecules to reduce host immune responses when electrospun fibers are used as scaffolds for cell and tissue growth. In some embodiments, the use of electroprocessed materials containing more than one phase allows control of behavior of the electroprocessed material. For example, a fiber is prepared containing aqueous cavities within an organic polymer such as EVA. The cavities contain water, salts, and bovine serum albumin (BSA). Immersion of the fiber in water results in what appear to be surface bubbles. This effect can be seen by comparing Figures 10 and 11. While not wanting to be bound by the following theory, it is believed that the bubbles form due to osmotic swelling of the salt BSA/aqueous reservoirs in the fiber by water diffusing into the fiber. In some embodiments, bursting of cavities is triggered. For example, including a base or alkali in aqueous phase cavities provides a means for causing the cavities and, in some embodiments, the fibers, to burst by exposing the fibers to an acid that will penetrate the fiber wall and react with the alkaline substance. The resulting action causes swelling of the cavities and bursting of cavities and fibers. In one such embodiment, the cavities contain sodium bicarbonate and the fibers are treated with a dilute acetic acid (such as vinegar). Such embodiments may be used, for example, to deliver substances to low pH environments such as the stomach. Alternatively, incoφoration of poly(acrylic acid) (PAA) in the aqueous reservoirs allows bursting to be triggered at pH values above 7. Treatment of lightly crosslinked PAA (e.g., Carbopol) with a base leads to extensive swelling. Such embodiments provide another means for controlling release profile. In other embodiments osmotic pressure is enhanced due the presence of high concentrations of substances in the cavities, pockets, enclosures, or inclusions. In such embodiments, the substances are present in the appropriate phase of the solvent from which electrospinning occurs. In one embodiment, the cavities contain high concentrations of glucose or sucrose.

In other embodiments, solid particulate materials are incoφorated into the electroprocessed material. Particles are incoφorated into the cavities, the phase surrounding the cavities, or both. In some embodiments, for example, small (ca. 10 nm diameter) magnetic particles that are dispersible in water are incoφorated in a water-miscible phase (in either the cavities or the surrounding phase). Application of a magnetic field causes movement or change in the conformation of the magnetic aqueous phase. This affords an additional means of affecting the release profile of a substance. In other embodiments, conductive particles (e.g., carbon black or intrinsically conductive polymers such as polyaniline) are incoφorated into the electroprocessed material to impart electrical conductivity. Such materials are used, for example, to make fibrous electrode materials for use in sensors, batteries, and fuel cells.

Still other embodiments involve immobilization of a redox-active enzyme (e.g., glucose oxidase) in aqueous reservoirs with carbon black in an electroprocessed material to allow electrical communication between the enzyme and the surrounding fiber. The sensing of glucose is important for diabetics who need to know when blood sugar (glucose) levels are depressed or elevated, although electrodes used for such a puφose sometimes suffer from interference from other substances in blood. Immobilization of enzymes in conductive structures mitigates this problem while providing the advantage of high sensitivity due to the high surface area of electrospun fibers. Another advantage of electroprocessing two or more phases is that the enzyme in this embodiment is immobilized in an aqueous reservoir and thus the enzyme is expected to remain in its native active state. In some embodiments, the polymer forming the electroprocessed material is tailored to allow diffusion of certain molecules while rejecting others (for example, allowing charged but not uncharged molecules to pass by diffusion). In other embodiments, the polymer acts like a dialysis membrane, allowing low molecular weight molecules to pass freely while limiting transport of higher molecular weight molecules. Release kinetics can also be controlled by preparing laminates comprising layers of electroprocessed materials with different properties and substances. For example, layered structures composed of alternating electroprocessed materials can be prepared by sequentially electroprocessing different materials onto a target. The outer layers can, for example, be tailored to dissolve faster or slower than respect the inner layers. Multiple agents can be delivered by this method, optionally at different release rates. Layers can be tailored to provide a complex, multi- kinetic release profile of a single agent over time. Using combinations of the foregoing can provide for release of multiple substances released, each with a complex profile.

Suspending a substance in particles that are incoφorated in the electroprocessed material provides another means for controlling release profile. Selection of the composition of these smaller particle matrices provides yet another way to control the release of compounds from the electroprocessed material. The release profile can be tailored by the composition of the material used in the process.

Embodiments also exist in which the substances are contained in liposomes or other vesicles in the electroprocessed matrix. Vesicles are prepared that will release one or more compounds when placed in fluids at a specific pH range, temperature range, or ionic concentration. Methods for preparing such vesicles are known to persons of skill in the art. The electroprocessed material can be delivered to a site of interest immediately or is stored either drv or at a pH at which release will not occur, and then delivered to a location containing liquids that have a pH at which release will occur. An example of this embodiment is an electroprocessed material containing vesicles that will release a desired compound at the pH of blood or other fluids released from a wound. The matrix is placed over a wound and releases fluids upon discharge of fluids from the wound.

Incoφorating constituents that are magnetically sensitive or electrically sensitive into the electroprocessed material provides another means of controlling the release profile. A magnetic or electric field can then be subsequently applied to some or all of the matrix to alter the shape, porosity and/or density of the electroprocessed material. For example, a field can stimulate movement or conformational changes in the matrix due to the movement of magnetically or electrically sensitive particles. Such movement can affect the release of compounds from the electroprocessed material. For example, altering the conformation of the material can increase or decrease the extent to which the material is favorable for compound release.

In some embodiments, magnetic or electrically sensitive constituents that have been processed or co-processed with an electroprocessed material can be implanted subdermally to allow delivery of a drug over a long interval of time. By passing a magnetic field or an electrical field across the material, drug release is induced. The electroprocessed material structure is stable and does not substantially change without electromagnetic stimulation. Such embodiments provide controlled drug delivery over a long period of time. For example, an electroprocessed material that has magnetic or electrical properties and insulin can be fabricated and placed subdermally in an inconspicuous site. By passing a magnetic field or an electrical field across the composition, insulin release can be induced. A similar strategy may be used to release compounds from a construct that has light sensitive elements, exposing these materials to light will either cause the material itself to breakdown and or cause the release of substances that are bound to the electroprocessed material by the light sensitive moiety.

In other embodiments, the substances comprise vesicles encapsulated within the electroprocessed material along with electrical or magnetic materials. The vesicles contain a compound to be released from the vesicles. Placing an electrical or magnetic field across the electroprocessed material causes the compounds within the vesicles can be released by, for example, deforming the vesicles to the point of rupture or by changing the permeability (in some cases reversibly) of the vesicle wall. Examples of these embodiments include transfection agents, such as liposomes, that contain nucleic acids that enhance the efficiency of the process of gene delivery to the cell. In other embodiments, the composition comprising an electroprocessed material and substance is used as a transdermal patch for localized delivery of medication, or of a component of such a patch. In some of these embodiments, electrically conductive materials are incoφorated into such a composition, which is then used as a component of an iontophoresis system in which one or more substances is delivered in response to the passage of electric current. Electrically conductive materials can have a direct healing effect on bone injuries. For example placing a small electric current across a fracture site promotes healing. An electroprocessed bone mimetic that conducts or produces current can be made and placed within a fracture. The addition of the electrical current will promote healing at a rate that is faster than the addition of the electroprocessed composition alone.

In other embodiments, an electroprocessed material or a portion thereof containing electromagnetic properties is stimulated by exposure to a magnet to move and thereby to apply or to release physical pressure to a pressure-sensitive capsule or other enclosure that contains molecules to be released from the material. Depending on the embodiment, the movement will affect the release relate of the encapsulated molecules.

Response of the composition to electric and magnetic fields can be regulated by features such as the composition of the electroprocessed material, size of the filaments, and the amount of conductive material added. Electromechanical response from polyaniline is the result of doping- induced volume changes, whereas ion gradients leading osmotic pressure gradients are responsible for field-induced deformation in ionic gels such as poly(2-acrylamido-2-methy] propanesulfonicacid). In each case, ion transport kinetics dominates the response, and facile transport is observed with the small fibers. Gel swelling and shrinking kinetics have been shown to be proportional to the square of the diameter of a gel fiber. Electromechanical response times of fiber bundles of less than 0.1s, are possible in the regime of typical muscle. Embodiments involving delivery of molecules produced by cells provide many means by which rejection and immune response to cells can be avoided. Embodiments using cells from a recipient thus avoid the problems associated with rejection and inflammatory and immunological response to the cells. In embodiments in which cells from an organism other than the recipient are used, the matrix can sequester the cells from immune surveillance by the recipient's immune system. In other embodiments, cells contained within cavities, pockets, enclosures, or inclusions in an electroprocessed material prepared from a multiple phase suspension are shielded by the wall of the material (i.e. the walls of the individual fibers, fibrils, films, sprays, droplets, particles, etc.) from immune surveillance while still maintaining cell viability and allowing transport of nutrients and metabolic products through the fiber walls. This invention thus provides another method for minimizing exposure to aspects of the external environment. By controlling parameters such as the pore size of the electroprocessed material or matrix, nutritive support to the cells trapped in the matrix can be permitted while the cells are protected from detection and response by the recipient's immune system. As an example, pancreatic islet cells that manufacture insulin collected from a donor can be encapsulated in an electroprocessed matrix and implanted in a recipient who cannot make insulin. Such an implant can be placed, foi example, subdermally, within the liver, or intramuscularly. For some immune responses permanent sequestration from the host system may not be necessary. The electroprocessed material can be designed to shield the implanted material for a given length of time and then begin to breakdown. In still other embodiments, bacteria or other microbial agents engineered to manufacture the desired compound can be used. This embodiment provides the advantages of using cells that are more easily manipulated than cells from the recipient or a donor. Again, the electroprocessed material can serve to shield the bacteria from immune response in this embodiment. The advantage of using a bacteria carrier is that these microbes are more easilv manipulated to express a wide variety of products. Embodiments in which cells are transientlv transfected allow for expression to be limited to a defined period. Transient genetic engineering allows cells to revert to their original state in embodiments in which such reversion is desired to minimize the risks of complications.

In some embodiments, cells are genetically engineered such that the expression of a specific gene may be promoted or inhibited through various means known in the art. For example, a tetracycline sensitive promoter can be engineered into a gene sequence. That sequence is not expressed until the tetracycline is present. Cell markers or bacterial markers can also be used to identify the inserted material. For example, green fluorescent proteins placed within an engineered genetic material glow green when expressed. Embodiments using this feature allow verification of the viability of the cells, bacteria, or gene sequences in a matrix. The visibility of such a marker also assists in recovering an implanted electroprocessed composition.

Although the present invention provides versatility in release kinetics, embodiments also exist in which one or more substances are not released at all from the electroprocessed material.

Substances may perform a function at a desired site. For example, in some embodiments, antibodies for a specific molecule are immobilized on an electroprocessed matrix and the composition is placed at a desired site. In this embodiment, the antibodies act to bind the molecules in the vicinity of the composition. This embodiment is useful for isolating molecules that bind to an antibody. Another example is an electroprocessed matrix containing immobilized substrates that will bind irreversibly to an undesirable enzyme and thereby inactivate the enzyme.

The compositions of the present invention may be combined with pharmaceutically or cosmetically acceptable carriers and administered as compositions in vitro or in vivo. Forms of administration include but are not limited to injections, solutions, creams, gels, implants, pumps, ointments, emulsions, suspensions, dispersions, microspheres, particles, microparticles, nanoparticles, liposomes, pastes, patches, tablets, transdermal delivery devices, sprays, aerosols, or other means familiar to one of ordinary skill in the art. Such pharmaceutically or cosmetically acceptable carriers are commonly known to one of ordinary skill in the art. Pharmaceutical formulations of the present invention can be prepared by procedures known in the art using well known and readily available ingredients. For example, the compounds can be formulated with common excipients, diluents, or carriers, and formed into tablets, capsules, suspensions, powders, and the like. Examples of excipients, diluents, and carriers that are suitable for such formulations include the following: fillers and extenders (e.g., starch, sugars, mannitol, and silicic derivatives); binding agents (e.g., carboxymethyl cellulose and other cellulose derivatives, alginates, gelatin, and polyvinyl-pyrrolidone); moisturizing agents (e.g., glycerol); disintegrating agents (e.g., calcium carbonate and sodium bicarbonate); agents for retarding dissolution (e.g., paraffin); resoφtion accelerators (e.g., quaternary ammonium compounds); surface active agents (e.g., cetyl alcohol, glycerol monostearate); adsoφtive carriers (e.g., kaolin and bentonite); emulsifiers; preservatives; sweeteners; stabilizers; coloring agents; perfuming agents; flavoring agents; lubricants (e.g., talc, calcium and magnesium stearate); solid polyethyl glycols; and mixtures thereof.

The terms "pharmaceutically or cosmetically acceptable carrier" or "pharmaceutically or cosmetically acceptable vehicle" are used herein to mean, without limitations, any liquid, solid or semi-solid, including but not limited to water or saline, a gel, cream, salve, solvent, diluent, fluid ointment base, ointment, paste, implant, liposome, micelle, giant micelle, and the like, which is suitable for use in contact with living animal or human tissue without causing adverse physiological or cosmetic responses, and which does not interact with the other components of the composition in a deleterious manner. Other pharmaceutically or cosmetically acceptable carriers or vehicles known to one of skill in the art may be employed to make compositions for delivering the molecules of the present invention.

The formulations can be so constituted that they release the active ingredient only or preferably in a particular location, possibly over a period of time. Such combinations provide yet a further mechanism for controlling release kinetics. The coatings, envelopes, and protective matrices may be made, for example, from polymeric substances or waxes.

Methods of in vivo administration of the compositions of the present invention, or of formulations comprising such compositions and other materials such as carriers of the present invention that are particularly suitable for various forms include, but are not limited to, oral administration (e.g. buccal or sublingual administration), anal administration, rectal administration, administration as a suppository, topical application, aerosol application, inhalation, intraperitoneal administration, intravenous administration, transdermal administration, intradermal administration, subdermal administration, intramuscular administration, intrauterine administration, vaginal administration, administration into a body cavity, surgical administration at the location of a tumor or internal injury, administration into the lumen or parenchyma of an organ, and parenteral administration. Techniques useful in the various forms of administrations above include but are not limited to, topical application, ingestion, surgical administration, injections, sprays, transdermal delivery devices, osmotic pumps, electrodepositing directly on a desired site, or other means familiar to one of ordinary skill in the art. Sites of application can be external, such as on the epidermis, or internal, for example a gastric ulcer, a surgical field, or elsewhere.

The compositions of the present invention can be applied in the form of creams, gels, solutions, suspensions, liposomes, particles, or other means known to one of skill in the art of formulation and delivery of therapeutic and cosmetic compounds. Ultrafine particle sizes of electroprocessed materials can be used for inhalation delivery of therapeutics. Some examples of appropriate formulations for subcutaneous administration include but are not limited to implants, depot, needles, capsules, and osmotic pumps. Some examples of appropriate formulations for vaginal administration include but are not limited to creams and rings. Some examples of appropriate formulations for oral administration include but are not limited to: pills, liquids, sy ps, and suspensions. Some examples of appropriate formulations for transdermal administration include but are not limited to gels, creams, pastes, patches, sprays, and gels. Some examples of appropriate delivery mechanisms for subcutaneous administration include but are not limited to implants, depots, needles, capsules, and osmotic pumps. Formulations suitable for parenteral administration include but are not limited to aqueous and non-aqueous sterile injection solutions which may contain anti-oxidants, buffers, bacteriostats and solutes which render the formulation isotonic with the blood of the intended recipient; and aqueous and non-aqueous sterile suspensions which may include suspending agents and thickening agents. Extemporaneous injection solutions and suspensions may be prepared from sterile powders, granules and tablets commonly used by one of ordinary skill in the art. Embodiments in which the compositions of the invention are combined with, for example, one or more "pharmaceutically or cosmetically acceptable carriers" or excipients may conveniently be presented in unit dosage form and may be prepared by conventional pharmaceutical techniques. Such techniques include the step of bringing into association the compositions containing the active ingredient and the pharmaceutical carrier(s) or excipient(s). In general, the formulations are prepared by uniformly and intimately bringing into association the active ingredient with liquid carriers. Preferred unit dosage formulations are those containing a dose or unit, or an appropriate fraction thereof, of the administered ingredient. It should be understood that in addition to the ingredients particularly mentioned above, formulations comprising the compositions of the present invention may include other agents commonly used by one of ordinary skill in the art. The volume of administration will vary depending on the route of administration. For example, intramuscular injections may range in volume from about 0.1 ml to 1.0 ml.

The compositions of the present invention may be administered to persons or animals to provide substances in any dose range that will produce desired physiological or pharmacological results. Dosage will depend upon the substance or substances administered, the therapeutic endpoint desired, the desired effective concentration at the site of action or in a body fluid, and the type of administration. Information regarding appropriate doses of substances are known to persons of ordinary skill in the art and may be found in references such as L.S. Goodman and A. Gilman, eds, The Pharmacological Basis of Therapeutics. Macmillan Publishing, New York, and Katzung, Basic & Clinical Pharmacology. Appleton & Lang, Norwalk, Connecticut, (6^th Ed. 1995). One desirable dosage range is 0.01 μg to 100 mg. Another desirable dosage range is 0.1 μg to 50 mg. Another desirable dosage range is 0.1 pg to 1.0 μg. A clinician skilled in the art of the desired therapy may chose specific dosages and dose ranges, and frequency of administration, as required by the circumstances and the substances to be administered. For example, a clinician skilled in the art of hormone replacement therapy may chose specific dosages and dose ranges, and frequency of administration, for a substance such as progesterone, to be administered in combination with the estrogenic and estrogenic modulatory molecules as required by the circumstances. For example, progesterone, and other progestins known to one of skill in the art may be administered in amounts ranging from about 50 μg to 300 mg, preferably 100 μg to 200 mg, more preferably 1 mg to 100 mg. Specific dosages and combinations of dosages of estrogenic and estrogenic modulatory molecules and progestins will depend on the route and frequency of administration, and also on the condition to be treated. For example, when the composition is formulated for oral administration, preferably in the form of a dosage unit such as a capsule, each dosage unit may preferably contain 1 μg to 5 mg of estrogenic and estrogenic modulatory molecules and 50 μg to 300 mg of progesterone. U.S. Patent No. 4,900,734 provides additional examples of acceptable dose combinations of estrogenic molecules and progestins.

Other uses involving electrically or magnetically active constituents

The compositions of the present invention have a number of additional uses aside from substance delivery. Embodiments exist in which the incoφoration of electrically or magnetically active constituents in the electroprocessed material allows the electroprocessed material to move rhythmically in response to an oscillating electric or magnetic field. Such an electroprocessed material can be used, for example, in a left ventricular assist device by providing a pumping action or a ventricular massage to a heart patent. Oscillations can be accomplished by passive movement of a magnetic or electric field with respect to the conductive material, or vice versa. By manipulating material selection, the electroprocessed material can be designed to remain in place permanently or to dissolve over time, eliminating the need for surgery to recover the device once the heart had recovered sufficiently.

Embodiments also exist in which an implanted electroprocessed material is used to convey an electric charge or current to tissue. For example, electrically active constituents can be electrically stimulated to promote neural ingrowth, stem cell differentiation, or contraction of engineered muscle, or to promote the formation of bone in orthopedic applications in which electroprocessed material is used as a carrier to reconstruct bone. In one embodiment, for example, an electroprocessed material is applied to a bone injury site and used to apply an electric current to the material to facilitate and to promote healing. The application of a small electric current to an injured bone is known to accelerate healing or promote the healing of bone injuries.

In other embodiments involving magnetically reactive materials, a magnetic field is used to position an electroprocessed material containing substances by relatively non-invasive means, for example by directing the movement of the material within the peritoneum. In other embodiments, a composition containing electrically active compounds is used to produce electric field-driven cell migration. This approach accelerates the healing process and minimize the risk of bacterial colonization. In one example, an orthopedic implant is coated with a very thin (< 100 microns) layer of an electrically active polymer. With a very thin electrode attached to the coating, upon post-implantation, an electric field can be applied via an external electrode such that the electric field-driven cell migration is towards the implant surface. The direction can be reversed if so desired. Field orientation depends on the geometry of the implant and external electrode.

Use in gene therapy Compositions of the present invention are also useful for testing and applying various gene therapies. By working with the compositions in vitro, different types of gene therapy and manipulation can be achieved by inserting preselected DNA in suspensions of cells, materials, etc. For example, nonviral techniques such as electroporation are used to treat cultured cells prior to insertion into the matrix of the present invention. In other embodiments, cells are treated within the matrix before the composition is inserted into a recipient. In vitro gene transfer avoids the exposure of a recipient to viral products, reduces risk of inflammation from residual viral particles and avoids the potential for germ cell line viral incoφoration. It avoids the problem of finding or engineering viral coats large enough to accept large genes such as the one for Factor NOT (anti- hemophilic factor). However, in vivo gene therapy is accomplished in some embodiments by, foi example, incoφorating DΝA into the electroprocessed material as it is created through the electroprocessing techniques of the present invention, whereby some DΝA will be incoφorated into the in vivo cells in contact with the composition after application of the composition to the recipient. This is especially true of small gene sequences, such as antisense oligonucleotides.

Use of an electroprocessed composition as tissue or organ replacement

The ability to combine cells in an electroprocessed material provides the ability to use the compositions of the present invention to build tissue, organs, or organ-like tissue. Cells included in such tissues or organs can include cells that serve a function of delivering a substance, seeded cells that will provide the beginnings of replacement tissue, or both. Many types of cells can be used to create tissue or organs. Stem cells, committed stem cells, and/or differentiated cells are used in various embodiments. Also, depending on the type of tissue or organ being made, specific types of committed stem cells are used. For instance, myoblast cells are used to build various muscle structures, neuroblasts are employed to build nerves, and osteoblasts are chosen to build bone. Examples of stem cells used in these embodiments include but are not limited to embryonic stem cells, bone marrow stem cells and umbilical cord stem cells used to make organs or organlike tissue such as livers, kidneys, etc. Examples of tissue embodiments that use differentiated cells include fibroblasts in a matrix used for a patch, for example a hernia patch, endothelial cells for skin, osteoblasts for bone, and differentiated cells like cadaver donor pancreatic islet cells for a delivery device to place these cells in a specific site, for example the liver. In some embodiments the shape of the electroprocessed composition helps send signals to the cells to grow and reproduce in a specific type of desired way. Other substances (for example, differentiation inducers) can be added to the electroprocessed matrix to promote specific types of cell growth. Further, different mixtures of cell types are incoφorated into the composition in some embodiments. In certain disease states, organs are scarred to the point of being dysfunctional. A classic example is cirrhosis. In cirrhosis, normal hepatocytes are trapped in fibrous bands of scar tissue. In one embodiment of the invention, the liver is biopsied, viable liver cells are obtained then cultured in an electroprocessed matrix, and re-implanted in the patient as a bridge to or replacement for routine liver transplantations. Mixing of committed cell lines in a three dimensional electroprocessed matrix can be used \ to produce structures that mimic complex organs. For example, by growing glucagon secreting cells, insulin secreting cells, somatostatin secreting cells, and/or pancreatic polypeptide secreting cells, or combinations thereof, in separate cultures, and then mixing them together with electroprocessed materials through electroprocessing, an artificial pancreatic islet is created. These structures are then placed under the skin, retroperitoneally, intrahepatically or in other desirable locations, as implantable, long-term treatments for diabetes.

In other examples, hormone-producing cells are used, for example, to replace anterior pituitary cells to affect synthesis and secretion of growth hormone secretion, luteinizing hormone, follicle stimulating hormone, prolactin and thyroid stimulating hormone, among others. Gonadal cells, such as interstitial (Leydig) cells and follicular cells are employed to supplement testosterone or estrogen levels. Specially designed combinations are useful in hormone replacement therapy in post and perimenopausal women, or in men following decline in endogenous testosterone secretion. Dopamine-producing neurons are used and implanted in a matrix to supplement defective or damaged dopamine cells in the substantia nigra. In some embodiments, stem cells from the recipient or a donor can be mixed with slightly damaged cells, for example pancreatic islet cells, or hepatocytes, and placed in an electroprocessed matrix and later harvested to control the differentiation of the stem cells into a desired cell type. This procedure is performed in vitro or in vivo. The newly formed differentiated cells are introduced into the patient. The ability to use electroprocessed materials and matrices to bioengineer tissue or organs creates a wide variety of bioengineered tissue replacement applications. Examples of bioengineered components include, but are not limited to, skeletal muscle, cardiac muscle, nerve guides, brain constructs as a filler for damaged/removed areas of the brain that are lost during accident or disease, a filler for other missing tissues, cartilage scaffoldings, sheets for cosmetic repairs, skin (sheets with cells added to make a skin equivalent), vascular grafts and components thereof, and sheets for topical applications (skin covering but no additional cells, just a patch). In some embodiments, such matrices are combined with drug and substance delivery electroprocessed matrices of the present invention in ways that will improve the function of the implant. For example, antibiotics, anti-inflammatories, local anesthetics or combinations thereof, can be added to the matrix of a bioengineered organ to speed the healing process and reduce discomfort.

One method or preparing implants of the present invention is use of a bioreactor. There are several kinds of commercially available bioreactors, devices designed to provide a low-shear, high nutrient perfusion environment. Until recently, most of the available bioreactors maintained cells in suspension and delivered nutrients and oxygen by sparging, through the use of impellers, or other means of stirring. The RCCS bioreactor (Synthecon) is a rotating wall bioreactor. Il consists of a small inner cylinder, the substrate for the electrospinning process, positioned inside a larger outer cylinder. Although the electrospun or electroaerosol matrix can be fabricated on the inner cylinder, other locations within the bioreactor also can be used for placement of a matrix for seeding. The gap between the inner and outer cylinders serves as the culture vessel space for cells. Culture medium is oxygenated via an external hydrophobic membrane. The low shear environment of the Synthecon RCCS bioreactor promotes cell-cell and cell-extracellular matrix (ECM) interactions without the damage or "washing away" of nutrients that occurs with active stirring or sparging. Typically, the RCCS device is operated at rotation rates of 8 up to 60 RPM. as required to maintain cells in suspension, and at less than 8 RPM (preferably 2-3 RPM) for cultures immobilized along the center shaft of the vessel. The Synthecon bioreactor can be used in a standard tissue culture incubator. These values for spin rates and other parameters can be varied depending on the specific tissue created.

Electroprocessed materials, such as matrices, are useful in formation of prostheses. One application of the electroprocessed matrices is in the formation of medium and small diameter vascular prostheses. Some preferred materials for this embodiment are collagen and elastin. especially collagen type I and collagen type HI. Some examples include, but are not limited to coronary vessels for bypass or graft, femoral artery, popliteal artery, brachial artery, tibial artery, radial artery or corresponding veins. The electroprocessed material is useful especially when combined with endothelial cells on the inside of the vascular prosthesis, and smooth muscle cells, for example a collagen tube, and also when combined with fibroblasts on the outside of the collagen tube. More complicated shapes including tapered and/or branched vessels can also be constructed. A different-shaped mandrel is necessary to wind the large fibers around or to orient the electrospun/electroaerosol polymer. Combination of electroprocessed matrix materials and wound polymer fibers can provide optimal growth conditions for cells. The polymer forms a basic structural matrix and the electroprocessed matrix is used to deliver the cells. This facilitates cell attachment onto the structural matrix. Furthermore the stress in the polymer also orients fibers in the matrix providing further spatial cues for the cells. In an alternative fabrication strategy, a cylindrical constmct is electrospun onto a suitable target, for example a cylindrical mandrel. Other shapes can be used if desirable based upon the shape of the site into which the implant will be placed. Matrices in this embodiment are composed, for example, of electroprocessed fibrinogen/fibrin (for example to promote neovascularization, cellular integration and infiltration from the surrounding tissue), electroprocessed collagen (to promote cell infiltration and lend mechanical integrity), and other components, for example PGA, PLA, and PGA-PLA blends, PEO, PVA or other blends. The relative ratio of the different components of this constmct is tailored to specific applications (e.g. more fibrin, less collagen for enhanced vascularization in a skin graft). To fabricate a cylindrical muscle the constmct is filled with muscle or stem cells or other cell type and the distal ends of the electrospun constructs are sutured or sealed shut. In some embodiments, cells are mixed with various matrix materials to enhance their distribution within the constmct. For example, the cells can be mixed with electroprocessed fibrin or collagen prior to insertion into the constmct. The objective of this strategy is to provide additional mechanical support to the constmct and provide the cells with a three dimensional matrix within the construct to promote growth. This also helps to maintain the cells in an even distribution within the construct. This method can be used to enhance the alignment of the cells within the construct. This filling material can be extruded directly into the cylindrical constmct, as the filling is extruded, alignment occurs. Mixing endothelial cells with the other cells inserted into the constmct (or other cell types) can be done to accelerate neovascularization. Another method to accomplish this objective is to electrodeposit endothelial cells directly into the electroprocessed collagen-matrix that aids in formation of the cylindrical sheath. The alignment of the fibers within the electroprocessed matrix that comprises the construct are optionally controlled by controlling the relative movement of the target and source solution with respect to one another. Other cell types, such as tendon fibroblasts, are optionally electrospun into or onto the outer surface of the construct to enhance the formation of the outer connective tissue sheath that forms the construct.

In another example a sheet of electroprocessed material is prepared, rolled into a cylinder and inserted into an electroprocessed cylinder. The construct is filled with cells as described above, sutured shut and placed in a bioreactor or directly in situ. By aligning the fibrils of the electrospun sheet of material in parallel with the long axis of the outer cylinder a muscle-like, electroprocessed composition is produced. Cells in contact with the fibrils that are arrayed along the long axis of the sheet spread in parallel with the fibrils of the sheet, forming a muscle constmct of cells arrayed and layered in a pattern of organization similar to that present in vivo. The cylindrical tissue construct is then implanted or placed within a RCCS bioreactor. Rates of rotation to maintain this type of constmct in suspension range from 4-20 rpm, depending upon the over mass of the tissue and the specific materials used to fabricate the outer cylinder.

Vascularization of the engineered tissue containing electroprocessed matrix material will occur in situ several days after surgery. In some embodiments, neovascularization of an engineered constmct containing electroprocessed material is enhanced by mixing endothelial cells into the construct during fabrication. Another alternative for supplying engineered tissue containing electroprocessed material with a vascular supply is to temporarily transplant the tissue into the omentum. The omentum has an extensive and rich vascular supply that can be used like a living incubator for the support of engineered tissue. The engineered tissue is removed from a bioreactor, wrapped in the omentum and supported by the diffusion of nutrients and oxygen from the surrounding tissue in the omentum. Alternatively, or in addition to this approach, engineered tissue is connected directly to the endogenous vascular supply of the omentum. A blood vessel can be partially perforated or cut or left dissected free of the omentum. The engineered tissue containing electroprocessed collagen, fibrin, or other materials, depending upon the constmct, is wrapped around the vessel. The engineered tissue is supported by nutrients leaking from the perforated vessel or by the simple diffusion of nutrients if the vessel is left intact. Regardless of strategy, the engineered tissue is surrounded by the omentum and its rich vascular supply.

Tissue containing electroprocessed material can be engineered with an endogenous vascular system. This vascular system can be composed of artificial vessels or blood vessels excised from a donor site on the transplant recipient. The engineered tissue containing electroprocessed matrix material is then assembled around the vessel. By enveloping such a vessel with the tissue during or after assembly of the engineered tissue, the engineered tissue has a vessel that can be attached to the vascular system of the recipient. In this example, a vessel in the omentum, or other tissue is cut, and the vessel of the engineered tissue is connected to the two free ends of the omental vessel. Blood passes from the omental vessel into the vascular system of the engineered tissue, through the tissue and drains back into the omentum vessel. By wrapping the tissue in the omentum and connecting it to an omental blood vessel, the engineered tissue is supported by the diffusion of nutrients from the omentum and the vessel incoφorated into the tissue during its fabrication. After a suitable period of time the tissue is removed from the omentum and placed in the correct site in the recipient. By using this strategy the engineered tissue containing electroprocessed material is supported in a nutrient rich environment during the first several days following removal from the bioreactor. The environment of the omentum also promotes the formation of new blood vessels in implanted tissue. This omental incubator strategy can be combined with the other strategies such as combining angiogenic factors in the matrix material during electroprocessing. Several options are available. First, the implants can be seeded with angioblasts and/or endothelial cells to accelerate the formation of vascular elements once the engineered tissue is placed in situ. Second, angiogenic peptides can be introduced into the engineered tissue via an osmotic pump. The use of an osmotic pump permits delivery of peptides or, as noted, angiogenic peptides or growth factors directly to the site of interest in a biologically efficient and cost-effective manner. VEGF delivered to ischemic hind limbs of rabbits accelerated capillary bed growth, increased vascular branching and improved muscular performance with respect to ischemic controls. An alternative approach is to seed fully differentiated tissue constructs containing electroprocessed matrix material with additional endothelial cells and or angioblasts shortly before they are implanted in situ.

In some embodiments, the stem cells or other cells used to constmct the implant are isolated from the subject, or other compatible donor requiring tissue reconstruction. This provides the advantage of using cells that will not induce an immune response, because they originated with the subject (autologous tissue) requiring the reconstruction. Relatively small biopsies can be used to obtain a sufficient number of cells to construct the implant. This minimizes functional deficits and damage to endogenous tissues that serve as the donor site for the cells.

In some embodiments, the matrices of the present invention include substances in the matrix that will improve the performance of the implanted electroprocessed matrix. Examples of substances that can be used include peptide growth factors, antibiotics, and/or anti-rejection drugs. Alternatively, cells that are engineered to manufacture desired compounds can be included. The entire constmct is, for example, cultured in a bioreactor or conventional culture or placed directly in vivo. For example, neovascularization can be stimulated by angiogenic and growth-promoting factors, administered, as peptides, proteins or as gene therapy. Angiogenic agents can be incoφorated into the electroprocessed matrix. Nerve growth factors can be electrospun into the matrix to promote growth or neurons into the matrix and tissue. In a degradable matrix, the gradual degradation/breakdown of the matrix will release these factors and accelerate growth of desired tissues. Electroprocessed matrices can also be used in connection with other matrix building processes. In other words, an extruded tube can have an outside layer electrospun onto it wherein the different layers complement each other and provide an appropriate matrix to promote a specific type of cell growth. As an example, a vascular graft comprised primarily of a collagen tube can have an electrospun layer of both other materials such as collagen or fibrin and cells added to promote the acceptability of the graft in a particular recipient. A second example is an in vitro skin preparation formed by growing fibroblasts in one layer, covering the first layer with electroprocessed collagen, and then growing a second layer composed of epidermal cells in the fibrin matrix. This layering technique can be used to make a variety of tissues.

Other uses of Electroprocessed Compositions That Contain Cells

The ability to use a fibrous matrix to entrap cells allows use in numerous other embodiments beyond organs and tissues. Embodiments include any technology involving cells. Examples include, but are not limited to whole cell biocatalysis and bioconversion, diagnostic devices, biosensors and biofiltrations. The electrospinning technology provides a simple and broadly applicable approach to immobilize cells. Stability and Storage of the Electroprocessed Compositions

The stability of the compositions of the present invention comprising electroprocessed materials combined with substances also allows for long term storage of the compositions between formation and use. Stability allows greater flexibility for the user in embodiments in which a drug or other substance is applied after formation of the electroprocessed material, for example by soaking and spraying. A formed electroprocessed matrix can be fabricated and stored, and then the exact substance composition to be delivered to an individual patient can be prepared and tailored to a specific need shortly before implantation or application. This feature allows users greater flexibility in both treatment options and inventory management. Many electroprocessed materials are dry once they are spun, essentially dehydrated, thereby facilitating storage in a dry or frozen state. Further, the electroprocessed compositions are substantially sterile upon completion, thereby providing an additional advantage in therapeutic and cosmetic applications. Storage conditions for the compositions of the present invention will depend on the electroprocessed materials and substances therein. In embodiments involving proteins, for example, it may be necessary or desirable to store the compositions at temperatures below 0°C, under vacuum, or in a lyophilized condition. Other storage conditions can be used, for example, at room temperature, in darkness, in vacuum or under reduced pressure, under inert atmospheres, at refrigerator temperature, in aqueous or other liquid solutions, or in powdered form. Persons of ordinary skill in the art recognize appropriate storage conditions for the materials and substances contained in the compositions and will be able to select appropriate storage conditions.

The compositions of the present invention and formulations comprising those compositions may be sterilized through conventional means known to one of ordinary skill in the art. Such means include but are not limited to filtration, radiation, and heat. The compositions the present invention may also be combined with bacteriostatic agents, such as thimerosal, to inhibit bacterial growth.

Formulations comprising the compositions of the present invention may be presented in unit-dose or multi-dose containers, for example, sealed ampules and vials, and may be stored in a freeze-dried (lyophilized) condition requiring only the addition of the sterile liquid carrier, for example, water for injections, immediately prior to use. Extemporaneous injection solutions and suspensions may be prepared from sterile powders, granules and tablets commonly used by one of ordinary skill in the art. Preferred unit dosage formulations are those containing a dose or unit, or an appropriate fraction thereof, of the administered ingredient. It should be understood that in addition to the ingredients particularly mentioned above, the formulations of the present invention may include other agents commonly used by one of ordinary skill in the art.

The compositions of the present invention may be packaged in a variety of ways depending upon the method used for administering the composition. Generally, an article for distribution includes a container which contains the composition or a formulation comprising the composition in an appropriate form. Suitable containers are well-known to those skilled in the art and include materials such as bottles (plastic and glass), sachets, ampules, plastic bags, metal cylinders, and the like. The container may also include a tamper-proof assemblage to prevent indiscreet access to the contents of the package. In addition, the container has deposited thereon a label which describes the contents of the container. The label may also include appropriate warnings.

In some embodiments, the compositions are treated with chemicals, solutions, or processes that confer stability in storage and transports. Examples include, but are not limited to, resistance to dissolution in aqueous solutions and ability to maintain the shape and moφhology of electroprocessed materials in aqueous solutions. In one embodiment, an matrix of PVA fibers has been treated with a chemical or solution that increases its ability to retain its fibrous moφhology in aqueous solutions. Any chemical or solution may be used. A preferred chemical or solution is one or more alcohols, more preferably lower alcohols such as methanol and ethanol.

The present invention is further illustrated by the following examples, which are not to be constmed in any way as imposing limitations upon the scope thereof. On the contrary, it is to be clearly understood that resort can be had to various other embodiments, modifications, and equivalents thereof, which, after reading the description herein, can suggest themselves to those skilled in the art without departing from the spirit of the present invention.

EXAMPLE 1

Fibroblast growth factor (FGF, obtained from Chemicon, Temecula, CA) was dissolved in a solution of matrix material comprised of type I collagen (80%), PGA (10%) and PLA (10%). The percentages refer to the weight of the materials with respect to one another. These materials were dissolved in HFIP at a final concentration of 0.08 gm per ml. Sufficient FGF was added to 1 ml of solution to provide an FGF concentration of 50 ng/ml of the collagen/PGA/PLA electrospinning solution. The material was electrospun into the shape of a cylinder onto the outer surface of a grounded and spinning 16 gauge needle about 25-35 mm in length. After application, the cylinder was sutured shut looping a suture around the outside of the constmct and pulling tight to seal the ends. Alternatively, a hot forceps is used to pinch the ends together and literally heat seal the ends shut. These methods formed a hollow, enclosed construct. The constmct was then surgically implanted within the vastus lateralis muscle of a rat. The construct was left in place for seven days and recovered for inspection. FGF in the matrix accelerated muscle formation within the electrospun matrix by promoting muscle formation within the wall of the electrospun cylinder.

EXAMPLE 2

Vascular endothelial growth factor (VEGF, obtained from Chemicon, Temecula, CA) was dissolved in a solution of matrix material comprised of type I collagen (80%), PGA (10%) and PLA (10%) as described in EXAMPLE 1. These materials were dissolved in HFIP at a final concentration of 0.08 gm per ml. Sufficient VEGF was added to 1 ml of solution to provide a VEGF concentration of 50 ng/ml of the collagen/PGA/PLA electrospinning solution. The material was electrospun to form a construct and implanted into a rat muscle using the same procedures set forth in Example 1. VEGF increased the density of functional capillaries that were present throughout the constmct. This was evidenced by the presence of capillaries containing red blood cells (RBCs).

EXAMPLE 3 Constmcts of electroprocessed collagen and PGA:PLA copolymer, with VEGF spun into the matrix were prepared using 80% collagen and 20% PGA:PLA. The collagen and PGA:PLA were dissolved in HFIP at a final combined concentration of 0.08 gm per ml. Solutions were prepared in which different amounts of VEGF were added to 1 ml of the solution of collagen and PGA:PLA copolymer. Separate solutions were prepared containing 0 ng, 25 ng, 50 ng, and 100 ng each in 1 ml. Constmcts were prepared for each solution by electrospinning one ml. The constructs were cut into smaller sections and placed in a phosphate buffer solution (PBS). Release of VEGF into the PBS was measured as a function of time by the ELISA method. The ELISA kit for VEGF was purchased from Chemicon International (part number cyt214) and the directions provided in the kit were followed to perform the ELISA. Samples were centrifuged to remove particulate matter and stored at -20 °C prior to use.

An identical construct was subjected to crosslinking by exposing it to glutaraldehyde vapor at room temperature and subjected to an identical ELISA assay. A sample of the electroprocessed construct was placed in a 100 mm tissue culture dish. A 35 mm tissue culture dish containing 1 ml of 50% glutaraldehyde was placed inside the 100 mm tissue culture dish. The lid of the 100 mm tissue culture dish was replaced and the sample was allowed to sit for 15 minutes at room temperature. The sample was rinsed in sterile water or culture media. The amount of VEGF (expressed in picograms per 1 mg of electrospun material) for the non cross- linked and cross-linked samples was measured at different times are presented in Figures 3 and 4, respectively.

In Figure 3 and Figure 4, the open diamonds represent release from the fibers electrospun from the solution containing PGA:PLA copolymer and collagen to which no VEGF was added. The open squares represent release from fibers electrospun from the solution containing PGA:PLA copolymer and collagen to which 25 ng of VEGF were added. The open circles represent release from the fibers electrospun from a solution containing PGA:PLA copolymer and collagen to which 50 ng of VEGF were added. The open triangles represent release from the fibers electrospun from a solution containing PGA:PLA copolymer and collagen to which 100 ng of VEGF were added. Results demonstrate not only that the matrix releases VEGF in PBS but also that cross-linking with glutaraldehyde slows release from the matrix.

EXAMPLE 4 Poly(ethylene-co-vinyl acetate) (EVA) was a gift from DuPont (Elvax 40, 40 vinyl acetate). EVA pellets were soaked in ethanol for several days to remove antioxidants. Poly(lactic acid) (100 L PLA) was a gift from by Alkermes, Inc. (Medisorb®) with a number-average molecular weight, M_n, of 205 KD and polydispersity of 1.7. All solvents were analytical grade and were used as received. Tris(hydroxymethyl)aminomethane hydrochloride (Trizma® HCl) and trishydroxymethylaminomethane (Trizma®-base) were supplied by Sigma and were used without further purification to prepare buffer solutions of pH 7.35. Tetracycline hydrochloride was also obtained from Sigma. Actisite® periodontal fiber (0.5rrim EVA) containing 25wt% tetracycline hydrochloride was a gift from Alza Coφoration (Palo Alto, CA).

Electrospinning was carried out using 14 % wt/v solutions of 100% EVA, 100% PLA, or mixtures of the two in chloroform. The mixtures used were 25% EVA/75% PLA, 50%/50% of each, and 75% EVA/25% PLA, with percentages by weight. Tetracycline hydrochloride, which is insoluble in chloroform, was solubilized in a small amount of methanol and added to the polymer solutions prior to electrospinning. The resulting solutions were yellow but clear, indicating homogeneous solubilization of both the polymers and drug.

The electrospinning set-up consisted of a glass pipette (held parallel to ground or angled at 45° downward), 0.32 mm diameter silver-coated copper wire (positive lead), a copper sheet (ground electrode) ca. 30 cm from the pipette, and a Spellman CZE100OR high voltage supply. A positive voltage (15 kV) was applied through the copper wire to the polymer solution inside the glass pipette. The solutions were delivered via syringe pumps to control the mass flow rate, which ranged from 10-18 ml/h. More conveniently, the solution can be held in a plastic syringe with the high voltage supply connected to the metal syringe needle. The solutions were delivered via syringe pumps to control the mass flow rate, which ranged from 10-18 ml/h. The resulting electrically charged fibers were collected on a rotating metal plate to produce a sheet of non-woven fabric.

A 100L PLA containing 5% tetracycline hydrochloride (by weight) was electrospun from 14% W/N solution in chloroform, with a mass flow rate of the polymer solution between 18-21 ml/h. EVA containing 5% tetracycline hydrochloride (expressed herein as by weight of total polymer) was electrospun from 14 % W/V solution with a mass flow rate of 3 ml/h. Blends containing 5% tetracycline hydrochloride and consisting of 25% PLA and 75% EVA were electrospun at mass flow rates of 13-18 ml/h. A 50/50 PLA/EVA blend with 5% tetracycline hydroxide was spun at a mass flow rate of 10-13 ml/h. A 50/50 PLA/EVA blend with 25% tetracycline hydroxide (by weight of total polymer weight) was spun at a mass flow rate of 15ml/hr. A blend containing 75/25 PLA/EVA with 5% tetracycline hydroxide was spun with a mass flow rate of 17 ml/h. The collected 'fabric' was used for studying the release of tetracycline hydrochloride. For comparative puφoses, cast films were made from different compositions of PLA and

EVA. As with the fibers, films were made of 25% EVA/75% PLA, 50%/50% of each, and 75% EVA/25% PLA and 5% tetracycline hydrochloride was added to each. The solutions in chloroform were cast onto glass petri dishes, left at room temperature until the chloroform was evaporated, then dried at 25 °C under vacuum for 3 hours. The release of tetracycline hydrochloride from ACTISITE® (EVA) periodontal fiber was also compared.

Release of tetracycline hydrochloride was determined using UN- VIS measurements carried out at Perkin-Elmer UV/VIS Lambda 40 Spectrophotometer. The molar extinction coefficient for tetracycline hydrochloride in Tris buffer was found to be 15,800 from a linear Beer-Lambert plot of absorbance at 360 nm vs. concentration. Release of tetracycline hydrochloride was determined by placing a known mass of polymer and dmg in tris buffer and monitoring the absorbance at 360 nm as a function of time. The buffer solution was changed if the released dmg gave absorbance higher than 2.0. Data are reported as the % tetracycline hydrochloride released based upon the expected amount in the samples from the feed composition. The moφhology of the electrospun samples were studied with JSM-820 Scanning electron microscope (JEOL Ltd.).

The release profiles of tetracycline hydrochloride from electrospun fibers and the cast films are shown in Figures 5 and 6. In Figure 5, the solid diamonds denote release from the fibers electrospun from the solution in which the polymer was 50% EVA and 50% PLA and 5% tetracycline was added. The open circles denote release from the fibers electrospun from the solution in which the polymer was 50% EVA and 50% PLA and 25% tetracycline was added. The open triangles denote release from the fibers electrospun from the solution in which the polymer was 100% PLA and 5% tetracycline was added. The solid squares denote release from the fibers electrospun from the solution in which the polymer was 100% EVA and 5% tetracycline was added. In Figure 6, the open diamonds denote release from the fibers electrospun from the solution containing 100% EVA. The open squares denote release from the ACTISITE® (EVA) periodontal fiber. The open triangles denote release from the film in which the polymer was 50% PLA and 50% EVA. The open circles denote release from the film in which the polymer was 25% PLA and 75% EVA. The solid diamonds connected by a thick line denote release from the film containing 100% PLA. The solid triangles denote release from the film in which the polymer was 75% PLA and 25% EVA. The solid squares denote release from the fibers electrospun from the solution containing 25% PLA and 75% EVA. The solid diamonds connected by a thin line denote release from film containing 100% EVA.

Electrospun EVA showed a higher release rate than the mats derived from PLA/EVA (50/50) or pure PLA. Electrospun EVA released 65% of its drug content within 100 hours, whereas the electrospun 50/50 mixture of EVA and PLA released about 40% over the same time period. Mats of PLA fibers with no EVA exhibit some instantaneous release, with negligible release over 50 hours. The 50:50 sample with 25wt% tetracycline hydrochloride releases the dmg more rapidly than the 5% sample, although the % released of the former approaches that of the latter after 150 hrs.

Figure 7 shows release profiles of three electrospun EVA samples, two from the same batch of mat and another from a different preparation under identical conditions. The release amounts of each sample are denoted by solid diamonds, solid squares, and open triangles, respectively. The profiles are quite similar indicating very good reproducibility. In general, the initial rate of release of all formulations including ACTISITE® (denoted as Alza) is high during the first 10-12 hours, most likely due to release of drug sequestered on the sample surfaces. The total percent released from the cast films (Figure 6) were lower than that of the electrospun mats, as would be expected due to the much lower surface area of the former. The PLA/EVA 75/25 film released 30% of its tetracycline hydrochloride in 120 hrs, whereas the film of 50/50 PLA/EVA showed a slightly lower percent of release (25%) in the same period of time. Release from the PLA film was much lower, only 6% released in 120 hrs, whereas the EVA film showed 8% release over the same period.

EXAMPLE 5 A mixture of cultured insulin secreting cells is seeded into an electroprocessed collagen matrix to form an electroprocessed collagen-containing tissue. The electroprocessed matrix containing the insulin secreting cells is implanted into a diabetic recipient in need of insulin. This electroprocessed collagen or fibrin-containing tissue optionally contains a vessel. The matrix is implanted into the retroperitoneal space and the vessel is anastomosed into the hepatic portal circulation. Insulin is released from the insulin-containing cell and transmitted to the circulation. The electroprocessed matrix containing the insulin secreting cells is optionally supplemented with cells that synthesize and secrete glucagon, somatostatin, pancreatic polypeptide, or combinations thereof, in order to mimic the hormonal complement of the pancreatic islet. Optionally, heterologous cells, (for example, engineered bacteria or cells from a conspecific donor) are placed in a matrix with a pore size that will allows diffusion of nutrients to the cells but does not allow or inhibits or delays the detection of the cells by the recipient's immune system.

EXAMPLE 6

Keratinocytes are harvested from a healthy site of a patient suffering from a chronic wound. The cells are grown in culture and transfected by electroporation to express VEGF. Next, the transfected cells are mixed or prepared in an electrospun collagen matrix. Antisense oligonucleotide for matrix metalloproteinases (MMPs) are also spun into the matrix. The matrix is topically applied to the surface of the wound. The cells near and in the implant take up the antisense sequences, express their transfected gene sequences and MMP production is reduced. In other applications the cells may be genetically engineered to secrete VEGF, thereby promoting healing. Release of the antisense oligonucleotides suppress expression of MMPs, which are typically overexpressed in a chronic wound. Thus the wound site is repaired with an implant that simultaneously promotes natural healing responses. Optionally, the matrix is comprised of fibrin or a mix of fibrin and collagen. The fibrin assists in cessation of bleeding and promotes healing.

EXAMPLE 7 Osteoblasts from a patient with a bone injury are cultured and incoφorated into an electrospun matrix comprising type I collagen. The matrix is formed in the shape of a cavity or defect at the injury site. Bone growth factor (BGF), bone moφhogenic protein (BMP) or sequences of genes encoding for these proteins, are electrospun into the matrix are optionally incoφorated into the electrospun matrix. The matrix assists in growth of new bone, and the BGF or BMP in the matrix promotes bone growth. Optionally, the collagen used is produced in vitro by genetically engineered cells that express a collagen polymer with more P-15 sites than in normal collagen. The excess of P-15 sites promotes osteoblasts to produce and secretes hydroxyapatite and further aid bone growth.

Optionally, the matrix is further electroprocessed with polypyrroles, which are electrically active materials. Electrodes are attached to each end of the implanted matrix. Charged electrodes are later applied to the surface over the electrodes to create a small electric current across the implant to further facilitate healing of the bone injury. In another embodiment piezoelectric elements may be electrospun into the matrix to produce electric discharges that promote healing.

EXAMPLE 8

In another example, similar to that described for skeletal muscle a cardiac patch is prepared. A sheet of electroprocessed material is prepared with aligned filaments of collagen. The sheet is folded into a pleated sheet in the desired shape and or rolled into a cylinder. A second constmct is electrospun in the desired shape, for example a rectangle. The pleated sheet that mimics the cellular layers of the intact heart is inserted into the electroprocessed rectangular form. The constmct is filled with cells, sutured shut and placed in a bioreactor or directly in situ. By aligning the fibrils of the pleated electrospun sheet of material in parallel with the long axis of the outer rectangular form, a cardiac, muscle-like construct is obtained. Native cardiac tissue is composed of layers of cells arrayed along a common axis with adjacent cell layers slightly off axis with the overlaying and underlying layers. This stmcture is more precisely mimicked by the methods described below in which a matrix is prepared and cells are directly electroprocessed, dribbled or sprayed onto the matrix as it is prepared. Cells in contact with the fibrils that are arrayed along the long axis of the sheet spread in parallel with the underlying fibrils of the sheet, forming a muscle constmct of cells arrayed and layered in an in vivo-like pattern of organization. The constmct can be directly implanted or placed within a RCCS bioreactor. Rates of rotation to maintain this type of construct in suspension range from 4-20 φm, depending upon the mass of the tissue and the specific materials used to fabricate the outer cylinder. Variations of this design include the addition of angiogenic factors in the matrix, gene sequences, and agents to suppress inflammation and/or rejection. Other cell types may be added to the constmct, for example microvascular endothelial cells, to accelerate the formation of a capillary system within the construct. Other variations in this design principle can be used. For example, cells may be electroprocessed into the matrix as it is deposited on the ground target. By varying the pitch of the fibers during spinning and spraying, dribbling or electroprocessing cells onto the fibers as they are deposited very precisely controls the positioning of the cells within the construct. EXAMPLE 9 Electrospinning EVOH from 2-propanol and water

Several samples of EVOH were obtained from Soarus LLC (Arlington Heights, IL) having compositions of 56 - 71 mol% vinyl alcohol repeat units. 2-propanol (isopropanol) was obtained from Aldrich Chemical (Milwaukee, WI) and 70/30% v/v alcohol/water solutions were made using distilled, deionized water. Solutions of EVOH and 2-propanol/water with EVOH concentrations ranging from 2.5 - 20 w/v% were prepared by warming the appropriate amounts of polymer and solvent to about 80oC for about 2-3 hours until complete dissolution of polymer occurred. Dissolution was also accomplished at 65oC and 70oC, although this generally required more time. Solutions for electrospinning were cooled to room temperature (ca. 22-24oC). Precipitation of polymer occurred after heating, but not for several hours after reaching room temperature. For example, a 50 ml solution of EVOH (62 mol% vinyl alcohol) in 2- propanol/water (10 w/v% EVOH concentration) in a 100 ml round-bottom flask did not show signs of precipitation until after about 7 hours at room temperature, making it possible to use room-temperature solutions for electrospinning within several hours of preparation. The precipitated mixture could be solubilized again by warming back to about 50oC for about 10 minutes, and subsequent precipitation and re-dissolution could be repeated many times.

The electrospinning set-up consisted of a syringe and blunt-end needle, a ground electrode (stainless steel sheet on a drum whose rotation speed can be varied) approximately 30 centimeters from the needle, and a Spellman CZEIOOOR high voltage supply (0-30 kV CZEIOOOR; Spellman High Voltage Electronics Coφ.) with a low current output (limited to a few microamperes). A positive voltage (15 kV) was applied to the polymer solution with the distance between the syringe tip and the target surface being approximately 20 centimeters. EVOH solutions in 2- propanol-water, prepared as described above, were electrospun within 2 to 3 hours after the solution cooled to room temperature. The solution was delivered via a syringe pump to control the mass flow rate, which ranged from 10-18 ml/h. The resulting fibers were collected on a rotating (1000 φm) metal drum to produce a sheet of non-woven fabric. Interestingly, dielectrics (e.g., a plastic petri dish) inteφosed between the syringe and grounded target were easily coated, as was a human hand (Figure 9). The following Table 1 provides data regarding electroprocessing of 10% W/V solutions of various EVOH copolymers with various ethylene contents. Table 1

Addition of a plasticizer (glycerol) to the EVOH solution appeared to improve the flexibility and mechanical properties of the spun fibers

EXAMPLE 10

Combining Cells With an EVOH Matrix Either Before or After Spinning

An EVOH solution (Soamol ET380362 mol% vinyl alcohol, 10% w/v solution of 70/30 v/v 2-propoanol/water) was electrospun over the top of a polystyrene 6-well culture plate by placing the plate in the polymer fiber stream for a few minutes to produce a thin mat (a few fibers thick) on the upper surface of the plate. The mat was then cut into four circles of approximately 12 millimeter radii, which were then placed individually into sterile culture wells (24 well culture plates). After the mats were set, approximately one milliliter of smooth muscle cells or fibroblasts (approximately 10⁶ cells) were added on the tops of the mats for seeding. After a seeding time of one hour, each culture well was topped off with medium and warmed to 37°C. The medium was composed of Dulbecco's Modified Eagle Medium (DMEM) and F12 Nutrient Mixture (F12) (2:1 - DMEM:F12 with high glucose plus L-glutamine, sodium pyruvate and pyridoxine hydrochloride) supplemented with 15% fetal bovine serum and 1% Penicillin-Streptomycin (10,000 Units/ml). Once the medium was added, the culture wells were covered with a sterile cover and placed in an incubator for 7 days. The medium was changed only once, at day 3, during this cell culture period. After 7 days in culture, the individual mats were removed from their respective wells and fixed in 3 % glutaraldehyde.

Scanning electron microscopy (SEM) of the electrospun samples and the cell-seeded mats was performed with a JEOL JSM-820 IE (JEOL Ltd.) electron microscope. Fiber samples required only mounting on an aluminum stub and sputter coating with gold for analysis. The cell- seeded samples were dehydrated with a series of ethanol/water solutions, critical point dried, mounted on stub, and sputter-coated with gold for analysis by SEM.

Matrices containing cells were also obtained by combining cells with the electroprocessing solution before electroprocessing. Overnight grown E. coli cells were harvested by centrifugation and mixed with EVOH to form a polymer solution in 70% isopropyl alcohol, 30% aqueous suspension. The resulting suspension was electrospun into a mat using the methodologies of the present invention. To allow comparison of these cells with E. coli cells seeding without exposure to the high voltage associated with the electrospinning process, cells were inoculated on one side of an electrospun mat by pippetting a solution of cells onto the mat or immersing the mat in such a solution. Another layer of electrospun EVOH mat was then electrospun over the previous mat, sealing the cells in place. The immobilized cells in both matrices were washed with large amounts of water and placed in a buffered solution supplemented with glucose (5 grams per liter). The cellular metabolic activity was monitored by measuring the pH in the solution. A rapid acidification of medium was observed in both the matrix in which the cells were electrospun with the EVOH and the matrix in which the cells were added after electrospinning, indicating that cellular metabolic activity occurred irrespective of whether the cells were exposed to high voltage associated with electrospinning.

EXAMPLE 11 Midair Electrospinning.

Similar to conventional electrospinning, midair electrospinning uses the same experimental set-up as other electrospinning techniques described above. However, in order to precipitate fibers before they reach the rotating drum, the distance from the needle tip to the dmm was increased. For example, increasing from the 20-30 cm distance used in experiments similar to Example 9 to a distance of 30-40 cm. In this embodiment the field strength of 0.5 kV/cm was maintained and was controlled by increasing the applied potential at the needle tip. Increasing the distance from the needle tip to the rotating target allows the polymer jet to experience a longer "flight time". While not wanting to be bound by the following statement, it is believed that with added time of flight, the 2-propanol-water solvent may completely evaporate from the jet allowing the fibers to fully develop. When this phenomenon is observed, it seems as though sections of fibrous mat appear in "mid-air." The mat shown in Figure 12 is an example of this midair spinning. It was created by inserting two glass pipettes into the electric field. The pipettes were held in a parallel line that was peφendicular to direction of the flow of materials during electroprocessing such that the electroprocessed materials passed between them. As the fibrous media begins to form on and between the pipettes, the pipettes are moved slowly apart. The fibrous mat builds on itself as the pipettes are moved apart to form the mat shown.

EXAMPLE 12 Mechanical joint created from mid-air electrospinning.

The fusing of two 12 in. Pasteur pipettes end to end was accomplished by electrospinning EVOH fibers in the space that separated the two pipettes. The electrospinning set-up used a syringe and needle, a grounded stainless steel plate (20 cm X 40 cm) 45 cm from the needle, and a Spellman CZEIOOOR high voltage supply. A positive voltage (22.5 kV) was applied to the polymer solution. EVOH/2-propanol-water solutions were first warmed to about 40°C and electrospun within 2 to 3 h of cooling to room temperature. The Pasteur pipettes (not grounded) were held approximately 10-20 cm from the grounded electrode plate inside the electric field. After approximately 30-90 seconds a fibrous medium formed between the two pipettes joining them together.

In another experiment, twisting and turning the pipettes inside the field afforded a more uniform and stronger bond. If the two pipettes are pulled apart while in the electric field, fibers will collect to fill in gaps created from the pulling.

EXAMPLE 13 Electrospinning of Hydrolyzed PVA from Aqueous Solutions and PVA Stabilization with Alcohol Solutions of aqueous powder of fully hydrolyzed PVA were prepared by dissolving hydrolyzed PVA having an average molecular weight of 115,000 g/mol (Aldrich Chemical, Milwaukee, WI) in water at approximately 80-85 °C for at least 12 hours to make a 10 wt% PVA solution. The PVA solution was cooled at room temperature with constant stirring. A clear, viscous solution was obtained. For some solutions, a small amount of non-ionic surfactant, Triton X-100 (Sigma-Aldrich Coφ. St. Louis, MO), was added to the above solutions at varying concentrations in the range between 0.03 to 1.5 v/w % while stirring. Other solutions did not have Triton X-100 added. The solutions were then stirred for 10-15 minutes before electrospinning. For electrospinning, the solutions were transferred to a syringe with a flat-end metal needle, configured with a syringe pump for controlled feeding rates and a high voltage DC power supply (Spellman, CZE 1000R, Spellman High Voltage Electronics Coφ. Hauppauge, NY). A grounded cylindrical stainless steel mandrel was positioned approximately 10 cm from the tip of the needle. In a typical electrospinning run, PVA solution was transferred into a syringe and delivered to the tip of the syringe needle by the syringe pump at a constant feed rate (0.7 - 2.0 ml/hour). A 25 kV positive voltage was applied to the PVA solution via the stainless steel syringe needle. The subsequently ejected polymer fiber was collected on the stainless steel mandrel, which was rotated and moved longitudinally simultaneously during the electrospinning process. Electrospun PVA mats were obtained. Similar procedures were performed using solutions without any addition of the surfactant. Formation of electrospun fibers was very infrequent, with electrospraying of droplets being the typical result.

Some of the PVA mats were stabilized against disintegration in water by treatment with methanol for several hours (8 - 24 h; 24 h is typical). After treatment, methanol-treated PVA mats were dried in a ventilated hood at room temperature for 24 hours. Figure 13 is an SEM picture of an electrospun, 100% hydrolyzed PVA mat.

Contact angle measurements on hydrophobically-modified glass surfaces were used to monitor the efficacy of Triton X-100 to lower and so adjust the surface tension of 100% hydrolyzed PV A/water solutions. Contact angles of PVA solutions were measured on hydrophobically-modified microscope glass slides using a goniometer (NRL CA. Goniometer, Rame-Hart Inc, Mountain Lakes, NJ) to track changes in surface tension of 100% hydrolyzed PV A/Triton solutions as a function of surfactant concentration. The surfaces of microscope glass slides were modified using octadecyltrichlorsilane (OTS) to as follows. Glass slides were sequentially cleaned by ultrasonication in acetone (1 min.), isopropyl alcohol (1 min.) and 4:1:1 H₂O:NH₄OH:H₂O₂ (10 s) then immersed in a solution of 0.1 v/v % OTS in anhydrous toluene at 40 °C for 30 minutes. The slides were then, rinsed with dried toluene three times and dried at 110 °C for 20 minutes. In a contact angle measurement, a droplet of PVA solution was vertically placed on an OTS-modified glass slide from a fixed height, and the contact angle was directly measured from the focusing lens of the goniometer. Since OTS provided hydrophobic surfaces on the substrate, de-ionized water on the hydrophobic OTS surface has a relatively high contact angle (102°), and this angle was expected to decrease upon addition of surfactant.

The moφhology of PVA mats was characterized using scanning electron microscopy (SEM) (JEOL JSM-820, JEOL (U.S.A.), Inc., Peabody, MA) and polarized light microscope (Leica DM IRBE, Leica Microsystems AG, Wetzlar, Germany). For optical microscopy, PVA fibers were collected on a microscope glass slide during electrospinning process. The slide was soaked in methanol for 1 hour and then dried in air. A few drops of water were placed on top of the fibers (both untreated and treated) and examined simultaneously under light microscope before the water evaporated. Differential scanning calorimetry (DSC) (Perkin-Elmer Pyris DSC 1, PerkinElmer

Instmments, Shelton, CT) was used to characterize the thermal properties of the electrospun PVA mats. A piece of PVA mat (5 - 10 mg) was placed in an aluminum sample pan and heated from 30 to 250 °C at 5 °C/min under N₂. A melting peak was observed at approximately 230 °C for all samples (Table 2). The degree of crystallinity was calculated by dividing ΔH by the heat required for melting a 100% crystalline PVA sample (ΔH_C = 138.6 J/g). (According to Peppas, N. A.; Merrill, E. W. J. Appl. Polym. Sci. 1976, 20:1457).

82

ATLLIB02 127045 1 Table 2. DSC Results on Electrospun PVA Mats Before and After Methanol Treatment

Electrospun mat Electrospun mat Electrospun mat Sample without methanol soaked in soaked in soaking methanol for 8h. methanol for 24 h.

T_m (°C) 229 232 231

ΔH (J/g) 72.4 ± 1.0 82.7 ± 2.1 81.6 ± 1.0

Degree of 52.2 ± 0.7 59.7 ± 1.5 58.8 ± 0.8 crystallinity (%)

The mechanical properties of the electrospun PVA mats were characterized using dynamic mechanical analysis (DMA) instrument (Rheometrics RSA fl^", Rheometric Scientific Inc, Piscataway, NJ). For DMA tests, the specimens were cut into a rectangular bar with a typical geometry of 6 mm wide, 21 mm long (between the grips) and 0.08 mm thick. The elastic modulus (E') and loss modulus (E") were obtained during a frequency sweep (1 - 100 rad/s) in tension at room temperature. The DMA tests were performed on the dry mats before and after methanol treatment under ambient conditions. A methanol-treated (24 h), water-swollen (over 10 days) mat was also studied, and water was constantly sprayed on the mat during the measurements to prevent dehydration of the sample.

The contact angle of 10 wt% of 100% hydrolyzed PVA water solution without Triton X- 100 was as high as pure deionized water, 101.2 ± 0.4°. As the degree of hydrolysis decreases, the contact angle of the PVA solutions (10 wt%) decreases. The contact angles of 96% hydrolyzed PVA and 87-88% hydrolyzed PVA solution on OTS-modified glass were 82.5 ± 0.5° and 72.7 ± 0.3°, respectively. By addition of a small amount of surfactant, the contact angle of the 100% hydrolyzed PVA solution was significantly lowered (Figure 14). The contact angle of the aqueous 10wt%, 100% hydrolyzed PVA solution decreased dramatically with an increase of Triton X-100 concentration and then leveled off when the surfactant concentration was about 0.3 v/w %, yielding a contact angle of about 60°. Further addition of surfactant has little effect on the contact angle of the polymer solution. The electrospinning feasibility of 100% hydrolyzed PV A/Triton solutions was examined at 2.5 kV/cm. When the surfactant to PVA concentration was below 0.06 v/w %, corresponding to a contact angle of about 86°, electrospraying of small droplets was dominant. Electrospraying resulted in the formation of combinations of isolated droplets and small pieces of PVA film, the latter presumably due to coalescence of wet droplets followed by evaporation of water. When the surfactant to PVA was between 0.1 to 0.2 v/w %, corresponding to 77 - 65°, electrospraying was accompanied with some electrospinning of fibers. Electrospinning began to dominate when the surfactant concentration was about 0.3 v/w %. The 100% hydrolyzed PVA solution electrospun particularly well when its contact angle was about 54 - 60°, resulting in PVA fibers of about 100 - 200 nm in diameter as shown by the scanning electron microscopy (SEM) in Figure 13. The diameters of the resulting PVA fibers ranged from 200 to 700 nm with the majority in the 300 - 500 nm range as observed using SEM as shown in Figure 15(a). As the degree of hydrolysis decreases, the contact angle of the PVA solutions (10 wt%) decreases. The contact angles of 96% hydrolyzed PVA and 87-88% hydrolyzed PVA solution on OTS-modified glass were 82.5 ± 0.5° and 72.7 ± 0.3°, respectively.

While an empirical correlation between a decrease in surface tension and the onset of electrospinning is observed, other factors may be relevant, including the possibility of localized gel formation in the solutions interfering with electrospinning but which may be suppressed by the addition of surfactant. Figure 16 shows a visual comparison of a wet, electrospun PVA mat prior to and after methanol treatment. Without methanol treatment, even though the PVA electrospun mat did not dissolve in water, it lost its mechanical integrity, forming a soft, gelatinous mass. In contrast, the water-swollen, methanol-treated PVA mat remained as such (see also Figure 15(d)) and was elastic. Methanol-treated (one hour) PVA fibers remained intact in contact with water after several days. Soaking the mat in either 95 % ethanol or rubbing alcohol, 70/30 v/v % isopropanol/water, also stabilized the mats. Such treatments did not appear to stabilize PVA with a lower degree of hydrolysis (e.g., 87%), presumably because crystallization was more difficult with acetate defects.

The degree of crystallinity for treated and untreated mats from DSC experiments was determined, the results of which are summarized in Table 2. The original, 100% hydrolyzed PVA mat was partially crystalline with degree of crystallinity about 52%. This is about 17 % higher than a PVA film cast from the same solution. Soaking in methanol afforded an approximately 7% additional crystallinity, or an increase of about 13% relative to the initial amount. There was little dependence of the degree of crystallinity on methanol soaking time beyond about 8 hours of immersion. Experiments on thin mats electrospun onto glass microscope slides indicated that 1 hour of treatment was effective. Additional experiments suggested that as little as 30 minutes, of treatment was sufficient. While not wanting to be bound to the following statement, it is believed that methanol treatment served to increase the degree of crystallinity, and hence the number of physical crosslinks in the electrospun PVA fibers. This may occur by removal of residual water within the fibers by the alcohol, allowing PVA-water hydrogen bonding to be replaced by intermolecular polymer hydrogen bonding resulting in additional crystallization. (Extraction of residual surfactant may also promote some local crystallization.)

The results of dynamic mechanical testing of PVA electrospun mats are shown in Figure 17. The frequency sweep from 1 to 100 rad/s indicated that, in all cases, the elastic (or storage) modulus, E', increased with frequency over the frequency range. This is a typical characteristic of the viscoelastic response of polymers. Note that data on wet PVA mats without methanol treatment are not available since these materials have essentially no mechanical integrity. Methanol treatment not only preserved fibrous stmcture of the PVA mat but also significantly increased the mechanical strength of the mat. The elastic modulus of the dry mats increased by a factor of 10 after methanol treatment (Table 3).

Table 3. Elastic Moduli of Electrospun PVA Mats at 1 Hz

Electrospun mat without Electrospun mat soaked

Sample methanol soaking in methanol for 20 h.

Dry Mat 93 ± 12 MPa 1331 ± 162 MPa

Wet Mat 6.7 ± 0.7 MPa

When immersed in water, methanol-treated PVA mats swelled significantly, thus softening the material yet affording the characteristics of a mechanically stable hydrogel. When immersed in water, methanol-treated PVA mats exhibited properties of a hydrogel. The water uptake of the methanol-treated PVA mat (24 h. methanol soaking) was about 250%. It is also worth noting that the loss modulus, E", of the wet, methanol-treated mat decreased with increasing frequency in contrast to the dry mats. Apparently, less energy per cycle could be dissipated by the methanol- treated, water-plasticized mats.

EXAMPLE 14 Two-Phase Electrospinning of Internal Phase of Aqueous Solution in External Phase of EVA/CH₂Cl₂

Poly(ethylene-co-vinyl acetate) (EVA) (Elvax 40, 40% vinyl acetate, DuPont) pellets were washed in ethanol while stirring for several days to remove antioxidants. All solvents were analytical grade and were used as received. A 13% wt/wt solution of EVA in CH₂C1₂ (Aldrich Chemical, Milwaukee, WI) was prepared using lOg of EVA and 47.75 ml of CH₂C1₂, and stirred with a magnetic stir bar until all beads had dissolved.

Solutions of various dyes (Bromphenol Blue, Blue Dextran, Evans Blue) were made in deionized water with typical concentrations of 0.1 grams per milliliter (g/ml) (high concentration), 0.05 g/ml (medium concentration), and 0.025 g/ml (low concentration). For each aqueous dye solution at each concentration, 10 ml of 13% EVA in CH₂C1 and 0.2 ml of the aqueous dye solution were added in a scintillation vial, and agitated for several minutes on a shaker (Vortex- Genie 2, Scientific Industries, Inc., Bohemia, N.Y.) until the resulting suspension appeared uniform. The resulting liquid was immediately electrospun.

The electrospinning set-up consisted of a syringe with a blunted 18 gage needle, a rotating metal drum placed approximately 15 centimeters (cm) from the needle tip, a copper sheet (ground electrode) approximately. 30 cm from the needle tip, and a Spellman CZEIOOOR high voltage supply. A negative voltage (10 kV) was applied to the needle, and thus to the polymer liquid inside the syringe. The liquid was delivered via a syringe pump to control the mass flow rate at 10 ml/h. The resulting electrically charged fibers were collected on the rotating drum to produce a sheet of non-woven fabric.

Electrospun liquids consisting of a 50:1 ratio of EVA/CH2C12 to aqueous dye were electrospun for each of the three dyes at different dye concentrations. The collected electrospun matrices were used for studying the release of the dyes from EVA. The matrices were wetted with ethanol, then rinsed with deionized water. The matrices were then placed in deionized water. Release rate into the deionized water was measured by determining the change in concentration in the deionized water over time. A representative graph of the release is shown in Figure 18. The letter "L," "M," and "H" accompanying the abbreviation for the substance name in the figure refer to low, medium, and high concentrations, respectively.

EXAMPLE 15

Incorporation of Aqueous Phase Containing Protein into EVA/ CH₂CI₂

A 13% solution of EVA in CH₂C1 was prepared as described in Example 14. Three different aqueous solutions containing 2 ml of phosphate buffered saline (pH 7.4) and differing amounts of bovine serum albumin (BSA) (ICN Biomedicals, Inc., Aurora, OH) were gently agitated on a shaker (Vortex-Genie 2, Scientific Industries, Inc., Bohemia, N.Y.) until the BSA was in solution.

For each of the three samples, 1.33 ml of the BSA solution and 40 ml of the EVA solution were placed in a scintillation vial, then capped tightly, and agitated on the shaker until the liquid became homogenous. Due to the differing BSA concentrations in the BSA solutions, the resulting liquids had total BSA contents of 0.0958, 0.0479, and 0.0239 grams of BSA per gram EVA.

The resulting liquids were immediately electrospun as described in Example 14, and the electrospun mats were used for studying the release of the BSA from EVA. The fabrics were wetted with ethanol, then rinsed with deionized water. The fabrics were then placed in phosphate buffered saline solution (PBS). Release rate into the PBS was measured by determining the change in concentration in the PBS over time. Absorbance measurements taken of the PBS over time were compared with absorbances of known BSA concentrations to determine concentration, and, ultimately, mass of BSA released. A representative graph of the release profile is shown in Figure 19.

EXAMPLE 16 Incorporation of Aqueous Phase Containing Fluorescent Labeled Protein into EVA/ CH2CI2

A 13% solution of EVA in CH₂C1₂ was prepared as described as described in Example 14.

A solution of fluorescent labeled BSA was prepared using a Alexafluor™ 350 protein labeling kit (Molecular Probes, Eugene, OR). The resulting solution had a BSA molarity of 1.379 e-7 moles per liter. A solution was prepared using 0.5 ml of the solution containing labeled BSA, 0.5 ml

PBS with 2 millimoles NaN₃ and 0.55 g unlabeled BSA. This solution was agitated on a shaker

(Vortex-Genie 2, Scientific Industries, Inc., Bohemia, N.Y.) until all the BSA was in solution.

After agitation, 0.2 ml of the resulting solution and 4 ml of the EVA solution were placed in a scintillation vial, then capped tightly, and agitated on the shaker until the liquid became homogenous.

The resulting liquid was immediately electrospun with two glass slides secured to a rotating metal target to collect the fibers. Microscopy using both visible and ultraviolet light revealed that the BSA was incoφorated into the fibers. Controls using EVA fibers without an aqueous phase and EVA with an aqueous phase containing PBS and no protein in the same aqueous to non-polar ratios as above, did not show significant fluorescence. Fibers whose aqueous phases contained labeled BSA showed significant fluorescence.

EXAMPLE 17 Incorporation of Yeast Cells into EVA/ CH2CI₂

A 13% solution of EVA in CH₂C1₂ was prepared as described in Example 14. A solution containing Kluyveromyces lactis yeast in an aqueous buffer was donated by Dr. Rachel Chen at

Virginia Commonwealth University. 0.2 ml of the yeast cell solution and 4 ml of the EVA solution were placed in a scintillation vial, then capped tightly, and agitated on a shaker (Vortex- Genie 2, Scientific Industries, Inc., Bohemia, N.Y.) until the liquid became homogenous.

The resulting liquid was immediately electrospun from a 5 ml syringe with a 14.5 gauge stainless steel cut needle, an applied voltage of 11 kV at a rate of 1 ml per hour. Two glass slides secured to a rotating metal target were used to collect the fibers. Fibers were collected and studied under a light microscope. The fibers were sprayed once with a 70% solution of isopropyl alcohol and allowed to soak for 24 hours, then soaked for 24 hours in deionized water. After soaking, Light microscopy revealed the presence of yeast cells in the fibers as shown in Figure 20.

EXAMPLE 18 Electrospun EVA with BSA and the effect of water soaking on fiber morphology

A bi-phase EVA spinning solution was prepared. A thirteen percent EVA solution (by mass) was made by dissolving 9.0246 grams of washed EVA in 43 ml of dichloromethane. The

EVA solution was allowed to stir with a magnetic stir bar overnight. An aqueous phase solution was made by dissolving 1.1083 g of BSA in 2 ml of PBS containing 2 millimoles of sodium azide, an anti-microbial. To 4 ml of EVA solution was added 0.2 ml of BSA/aqueous solution.

The mixture was agitated for approximately two minutes to obtain a homogeneous suspension. The suspension was electrospun from a 5 ml syringe with a 14.5 gauge stainless steel cut needle and an applied voltage of 9 kV at a rate of 1ml per hour. An adapter was used that allowed glass microscope slides to be the grounded target instead of the mandrel. Samples were labeled and observed under a light microscope. One slide was marked so that one fiber could be easily found and isolated after soaking experimentation. Photographs were taken of the selected fiber at different focuses for an idea of the dimensionality of the fiber. The glass slide was immersed in water for approximately one hour. The fiber was reexamined and pictures were taken at different focuses to determine changes in the dimensionality of the fiber. Figure 10 shows a fiber before immersion in water. Figure 11 shows a fiber after immersion in water.

EXAMPLE 19

Electrospun EVA with a mixture offluoro-labeled and unlabeled BSA

An Alexa Fluor 350 Protein Labeling Kit was used to attach a fluorescent tag to BSA. A 1 molar solution of sodium bicarbonate was prepared by adding 1 ml of deionized water to a vial of sodium bicarbonate. The solution was agitated on a shaker (Vortex-Genie 2, Scientific Industries, Inc., Bohemia, N.Y.) until the sodium bicarbonate was fully dissolved. A BSA solution was prepared by dissolving 0.2 grams of BSA in 100 ml of PBS with 2 millimoles of sodium azide. To 0.5 ml of the BSA solution was added 50 microliters of the sodium bicarbonate solution. A vial of fluorescent dye was allowed to warm to room temperature. The protein/sodium bicarbonate solution was added to the fluorescent dye and stirred on a magnetic stir plate for approximately two hours. A purification column was assembled. An elution buffer was prepared by diluting 1 ml of PBS with 2 mM sodium azide with 9ml of deionized water. The purification resin that accompanied the column was stirred thoroughly until its contents appeared homogeneous. The resin was pipeted into the column and excess buffer was allowed to drain. The column was packed with resin up to approximately 3 cm from the top of the column. The reaction mixture was carefully loaded into the packed column and was allowed to enter the column. The reaction vial was rinsed with a small amount of elution buffer and this too was loaded. Small amounts of elution buffer were slowly added to the column and the column was illuminated with a UV light approximately every five minutes. Two fluorescent bands were visible. The bottom band contained the labeled BSA and was collected (approximately 1 ml) and stored in a dark container at 4° Celsius until it was ready to be used, upon which time the fraction was centrifuged for two minutes at 5 X lOOOmin ^_1. The sample was then diluted with 1ml of PBS with 2 mM sodium azide. The degree of labeling and concentration of protein in the sample were calculated according to the Molecular Probes handbook on Alexa Fluor 350, labeling kit.

UV-Vis measurements were taken to determine absorbance of the sample at 280 nm and 346 nm and found to be 0.0727 and 0.0880, respectively. Protein concentration was calculated to be 1.379 X 10^"7 M and the degree of labeling was calculated to be 16.79 moles of dye per mol of BSA. To 1ml of the labeled protein solution was added 0.5544 g of unlabeled protein. The mixture was agitated on a shaker (Vortex-Genie 2, Scientific Industries, Inc., Bohemia, N.Y.) until the mixture appeared homogeneous. A bi-phase EVA spinning suspension was prepared by adding 0.2 ml of the labeled protein solution to 4 ml of the aforementioned 13 percent EVA solution. An adapter replaced the mandrel in the electrospinning apparatus that allowed glass microscope slides to be the grounded target instead of the mandrel. Electrospinning was performed from a 5ml syringe with a 14.5 gauge stainless steel cut needle, an applied voltage of 9 kV at a rate of 1 ml per hour. Control fibers were prepared from a thirteen percent washed EVA solution (by mass) made by dissolving 5.7706 g of washed EVA in 27 ml of dichloromethane. The EVA solution was allowed to stir with a magnetic stir bar overnight.

Samples of the following liquids were obtained on glass slides in the same manner as previously mentioned: 13 % EVA solution with no aqueous phase; 13 % EVA solution with PBS/2 mM sodium azide aqueous phase; 13 % EVA solution with unlabeled BSA in PBS solution aqueous phase. These controls were taken in order to determine if any background fluorescence was caused by EVA, PBS or BSA. All solutions were prepared by adding 0.2 ml of aqueous phase to 4 ml of 13 % washed EVA solution. Samples were labeled and observed under a light microscope with a fluorescent light and a DAPI filter. Micrographs were taken with both white and UV light settings. In the case of the fluorescent labeled fibers, one slide was marked so that a

89

ATLUB02 127045 1 few fibers could be easily found and isolated after soaking experimentation. Micrographs were taken of the selected fiber at different focuses for an idea of the dimensionality of the fiber. The slide was soaked in deionized water for approximately one hour and reexamined.

In all cases, aqueous phase channels in the center of EVA fibers were observed. In many cases, the tubular channels appeared to be breaking into tiny beads, suggestive of Rayleigh instability. Location of BSA within the fiber was determined by studying fibers containing fluorescent-labeled BSA with fluorescent microscopy, and found to be primarily within the central aqueous channels within the fibers.

EXAMPLE 20

Use of Osmotic Swelling to Control Release of Aqueous Phase

It was observed that, upon immersion in water of some of the fibers prepared by processes similar to those disclose in Examples 14-19, the aqueous reservoirs would swell slightly. Without being bound to the following statement, it is believed that this swelling may be due to water diffusion through the thin fiber walls driven by the presence of BSA and salt in the reservoirs. In order to amplify this effect, EVA fibers were electrospun from dispersions in which the aqueous phase contained 1.28 M sucrose. When the resulting fibers exposed to a lower molarity solution, in this case lx PBS, (Typical formulation: 137mM NaCl, lOmM sodium phosphate buffer pH 7.4, 2.7mM KC1), the aqueous pockets swelled to several times their initial diameters (Figure 21(a)- (d)). Swelling of the individual pockets occurred at different rates. Without being bound to the following statement, it is believed that the difference in swelling rates may be due to non-uniform wall thicknesses in the pockets. Several of the swollen pockets, or blisters, were also observed to decrease in size (Figure 21(c), (d)) back to near their original volumes after they had reached a maximum inflation, suggesting that the blister walls had ruptured with concomitant leakage of the contents of the pockets. Some fibers show extensive strings of blisters while others have few or none (Figure 22). Electron micrographs of EVA fibers containing aqueous sucrose pockets which had burst indicate that the walls of the blisters ruptured with significant plastic deformation (Figure 23(a)). In one case, a hole almost a micron in diameter was left at the base of the bubble after mpture (Figure 23(b)). Stress (σ) in a thin walled spherical vessel is defined as σ = Pr/2t where P is pressure, r the inner radius of the vessel, and t the thickness of the blister. Solving for the osmotic pressure inside the blister (P) gives P = 2σ t r. The tensile stress of EVA is approximately. 900 psi for Elvax-40 (obtained from the manufacturer). Given blister diameters of approximately 20-40 μm (Figure 22) and assuming a blister wall thickness at mpture of about 1 μm, the values for the pressure at mpture are between about 45 and 90 psi. The osmotic pressure generated (calculated from the

90

ATLL1B02 127045 1 van't Hoff equation, π = cRT) by a 1.3 molar solute in water is approximately 460 psi, significantly larger than the pressure needed for mpture of an EVA membrane given our assumptions

The solutions and electrospinning procedures of this Example were duplicated except that a 0.1M solution of sodium ferrocyanide was added to the aqueous phase of the dispersion. The resulting electrospun fibers were immersed in an aqueous solution containing 0.035M ferric ammonium sulfate. Upon immersion of the fibers, swelling of several pockets was observed and blue regions characteristic of Pmssian Blue were seen outside of the mptured blisters. Pmssian Blue, or Fe₄[Fe(CN)₆] , is a product of the reaction of ferrocyanide and the ferric ammonium sulfate. The presence of Pmssian Blue outside the mptured blisters indicated osmotically triggered release of their contents.

All patents, publications and abstracts cited above are incoφorated herein by reference in their entirety. It should be understood that the foregoing relates only to preferred embodiments of the present invention and that numerous modifications or alterations can be made therein without departing from the spirit and the scope of the present invention as defined in the following claims.

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ATLLIB02 127045 1

Claims

WHAT IS CLAIMED IS

1. A composition comprising: an electroprocessed material comprising fibers having a diameter of about 20 microns or less; and, enclosures defining spaces within the fibers, wherein the spaces contain a substance that is immiscible with the fibers.

2. A composition comprising: an electroprocessed material comprising fibers; and, enclosures defining spaces within the fibers, wherein the spaces contain a substance that is immiscible with the fibers.

3. The composition of Claim 1 or Claim 2, wherein the substance comprises a molecule, a cell, an object, or a combination thereof.

4. The composition of any of the preceding claims, wherein the substance comprises a cell.

5. The composition of any of the preceding claims, wherein the spaces comprise one or more molecules that increase flow of a liquid surrounding the composition into the spaces.

6. The composition of any of the preceding claims, wherein the fiber comprises one or more molecules that facilitates flow of a liquid surrounding the fibers through the material and into the spaces.

7. A composition comprising the result of a process comprising: bonding a substance to a material; and, electroprocessing the material.

8. The composition of Claim 7, wherein the material is a synthetic polymei derivatized to allow formation of a bond between the material and the substance.

9. An electroprocessed material that has been treated with a compound, wherein the compound enhances the ability of the electroprocessed material to retain its moφhology in aqueous solutions.

10. A method of manufacturing the composition of any of the preceding claims, comprising: combining the substance with an electrically-charged solution; and, electroprocessing the solution into a location under conditions effective to form an electroprocessed material.

11. The method of Claim 10, wherein the solution is an emulsion, dispersion, or suspension comprising two or more immiscible liquid phases.

12. The method of Claim 10 or Claim 11, wherein the method further comprises combining a processing aid with the solution prior to electroprocessing.

15. The method of any of Claims 10-12, wherein the method further comprises heating one or more of the solutions prior to electroprocessing and allowing the solution to cool, whereby the ability of the material to be electrodeposited from the solution is enhanced.

16. Use of any of the electroprocessed compositions of Claims 1-9 for delivery of a substance or an electroprocessed material.

17. Use of any of the electroprocessed compositions of Claims 1-9 for preparation of a medicament useful for delivery of a substance or an electroprocessed material.