Patent Application
20060153894
This invention relates generally to biocompatible devices for delivery of drugs and cells, and in particular to implantable biocompatible matrices suitable for delivery of therapeutic compounds in combination with organs, tissues, or cells.
Tissue engineering strategies have explored the use of biomaterials in combination with cells and/or growth factors to develop biological substitutes that ultimately can restore or improve tissue function. Scaffold materials have been extensively studied as tissue templates, conduits, barriers and reservoirs useful for tissue repair. In particular, synthetic and natural materials in the form of foams, sponges, gels, hydrogels, textiles and nonwovens have been used in vitro and in vivo to reconstruct or regenerate biological tissue, as well as deliver chemotactic agents for inducing tissue growth. See, for example, U.S. Pat. Nos. 5,770,417, 6,022,743, 5,567,612, 5,759,830, 6,626,950, 6,534,084, 6,306,424, 6,365,149, 6,599,323, 6,656,488, and 6,333,029.
It is desirable for a scaffold to possess some fundamental characteristics such as being biocompatible, having adequate mechanical strength to resist loads experienced during surgery; being pliable, being highly porous to allow cell invasion or growth, being able to allow increased retention of cells in the scaffold, being easily sterilized, being susceptible to remodeling by invading tissue, and being degradable as the new tissue is formed. It is also desirable for a scaffold to have the ability to deliver certain therapeutics with specific activities and desirable release kinetics, for example, to reduce inflammation at the transplant site, to down regulate invading immune cells, to enhance proliferation of transplanted cells, or to induce differentiation of transplanted cells into functional tissue. In other cases, a scaffold may carry more than one biological entity such as cells, cell clusters, or organoids, in which case the scaffold must possess variable characteristics to accommodate each entity. It is clear that the manufacture of scaffold as a replacement for diseased or damaged tissue requires flexible designs to accommodate the complexity and high specificity associated with various biological functions.
Tissue engineering may offer alternative, promising approaches for treating diabetes. Degradable or non-degradable matrices have been used to seed and culture islet cells for implantation in vivo. As islet survival depends on diffusion of oxygen and nutrients, establishing stable vascularization is critical to islet survival. It has been shown that a sustained release of angiogenic signals is required for establishing stable vascularization, which allows for the development of a permanent implant structure. Efforts have been made to encapsulate, with a non-degradable material, both islet cells and angiogenic factors suspended in a matrix material such as gelatin hydrogel. Scaffold constructs made of biodegradable materials have also been used for delivering islet cells into various anatomical sites in vivo. For example, nonwoven scaffolds are an ideal matrix for hosting islets, as they provide adequate support for islets to get entangled within the fibers and allow enough porosity for diffusion of oxygen and nutrients, which is essential especially for the preliminary stages of the transplantation process until the vasculature is established. On the other hand, incorporation of a therapeutic compound into a nonwoven scaffold is fairly inefficient, since nearly 90% of the nonwoven scaffold can be void air. To address this issue, composite scaffolds have been designed to incorporate a foam component which lowers the overall porosity of the scaffold, yet may compromise the ability of the scaffold to host islets.
Clearly, there is a need for scaffold constructs that permit efficient delivery of multiple, distinct biological entities, such as islet cells and a therapeutic compound.
The present invention is directed to a biocompatible, implantable, partially or fully biodegradable delivery device, which is composed of at least two compartments. The compartments are designed independently and processed separately to accommodate and effectively deliver two or more biologically relevant entities.
In one embodiment, at least two compartments of a device are fabricated separately for hosting a therapeutic compound and cells, respectively. The two compartments can be physically joined with each other such that the therapeutic compound released from one compartment provides a beneficial activity to the cells hosted by the other compartment.
In another embodiment, at least two compartments of a device are fabricated separately for hosting two types of cells. The two compartments can be physically joined with each other such that the cells in one compartment provide a beneficial effect on the cells hosted by the other compartment. For example, one compartment of a device can be loaded with cells that protect cells in the other compartment against a destructive immune response. Alternatively, one compartment of a device can be loaded with cells that produce and secrete a molecule that improves the survival and function of cells in the other compartment.
In a further embodiment of the present invention, the compartments of a device of the present invention have been loaded with two or more biological entities suitable for implantation.
The compartments of a device can be combined prior to or at the time of transplantation. The cell-loaded compartment can be maintained under suitable culture conditions before joining with another compartment to allow proliferation and differentiation of the cells, or extracellular matrix production from the cells.
The present invention is also directed towards methods of treating disease, particularly diabetes, in a mammal utilizing a delivery device of the invention.
The present invention provides biocompatible delivery devices that are uniquely designed to utilize at least two, i.e., two or more, separately prepared compartments to host multiple biological entities. A principal feature of the devices of the present invention is the flexibility in the design, fabrication and loading of the compartments separately. A compartment can be designed and fabricated to address the specific need of a biological entity to be hosted by that compartment. Another desirable feature of the devices of the present invention is the ability to combine the compartments at the time of transplantation to permit interactions between the biological entities in separate compartments.
To illustrate the features of the present invention, an example of a device of the present invention is depicted in
The term “biological entity” is used herein as a general term and refers to any biologically active material suitable for use in implantation, including but not limited to compounds and cells, either cells in a single-cell suspension or cells in a cell cluster.
One or more compartments of a device of the present invention can host cells (“cellular compartment”). A cellular compartment is designed to optimize cell survival and function in a transplanted graft. An important characteristic of a cellular compartment is its overall porosity. The term “porosity” refers to the ratio of the volume of all the pores within a compartment to the total volume of the compartment. Appropriate porosity allows diffusion of nutrients and oxygen, which is necessary for cell survival, especially in the initial stage after transplantation. Appropriate porosity and pore size also allow tissue infiltration to establish a permanent vasculature network. The porosity and pore size of a cellular compartment may vary depending on the type of cells being transplanted and the dimensions of their clusters. Generally speaking, a compartment suitable for hosting cells has an average pore diameter in the range of from about 50 to about 1,000 microns, preferably, from about 50 to about 500 microns; and has a porosity in the range of 70% to 95%, preferably about 90%.
A cellular component of a device of the present invention can host mammalian cells, including but not limited to, bone marrow cells, smooth muscle cells, stromal cells partially or fully differentiated glucose responsive insulin secreting cells, stem cells, mesenchymal stem cells, synovial derived stem cells, embryonic stem cells, blood vessel cells, chondrocytes, osteoblasts, precursor cells derived from adipose tissue, bone marrow derived progenitor cells, kidney cells, intestinal cells, islets, beta cells, Sertoli cells, peripheral blood progenitor cells, ductal cells, acinar cells, fibroblasts, glomus cells, keratinocytes, nucleus pulposus cells, annulus fibrosus cells, fibrochondrocytes, stem cells derived from placenta, amniotic epithelium, amniotic fluid, umbilical cord, chorion, villus, cord or cord blood, stem cells isolated from adult tissue, oval cells, neuronal stem cells, glial cells, macrophages and genetically transformed cells, or combinations of the above.
In one embodiment, the cells loaded into one cellular compartment produce a factor or a group of factors that are beneficial to cells of a different type loaded into another cellular compartment of the same device so as to improve the survival, proliferation, differentiation, or function of such cells in such other compartment.
Cells are loaded into a cellular compartment using methods known to those skilled in the art. See, e.g., U.S. Pat. 6,132,463, Journal of Biomedical Materials Research (2001) 55(3): 379-386; Biotech. Bioeng. (2003) 82(4): 403-414; Biomaterials (2004) 25(14): 2799-805. The cells can be maintained in the compartment for a short period of time (<1 day) prior to implantation, or cultured for a longer time period (>1 day) to allow for cell proliferation and extracellular matrix synthesis within the compartment prior to implantation.
In one embodiment, a cellular compartment is treated, typically prior to loading cells, with factors that facilitate cell seeding and enhance cell attachment, for example, fibronectin, collagen, laminin and other extracellular matrices.
In another embodiment, a compartment loaded with cells is maintained in vitro using appropriate culturing techniques to allow the cells sufficient time to anchor, proliferate, or differentiate into functional cells prior to transplantation.
Although a cellular compartment is primarily designed and fabricated to host cells, such compartment can also include a bioactive compound so long as the inclusion of the compound does not interfere with the attachment, survival and function of the cells. However, it is desirable to incorporate the compound(s) into a separate compartment, which is independently designed to achieve optimum incorporation and release kinetics of the compound(s).
Accordingly, one or more compartments of a device of the present invention are designed and prepared as a compound compartment, primarily to achieve optimum incorporation and release kinetics of a compound(s). The characteristics of a compound compartment and the technique for loading a compound may vary depending on the physical nature of the compound, its mechanism of action, and desired release kinetics.
The term “bioactive compound” refers to small molecules, peptides, proteins, growth factors, differentiation factors, or combinations thereof. Bioactive compounds include any biological or synthetic factor that promotes attachment, proliferation, differentiation, and extracellular matrix synthesis of targeted cell types. Bioactive compounds also include, but are not limited to, anti-rejection agents, analgesics, antioxidants, anti-apoptotic agents such as erythropoietin, anti-inflammatory agents such as anti-tumor necrosis factor alpha, anti-CD44, anti-CD3, anti-CD154, p38 kinase inhibitor, JAK-STAT inhibitors, anti-CD28, acetoaminophen, cytostatic agents such as rapamycin, anti-IL2 agents, and combinations thereof.
In one embodiment, the compound is a small molecule that can be loaded during the fabrication process of the compound compartment. In another embodiment, the compound is a large biological factor that is sensitive to the fabrication process, and can be loaded at a later stage via adsorption, coating or a variety of other loading techniques known to those skilled in the art.
Examples of large biological factors that can be loaded into a compound compartment include growth factors, extracellular matrix proteins, and biologically relevant peptide fragments such as, but not limited to, members of the TGF-β family including TGF-β1, 2, and 3, bone morphogenic proteins (BMP-2, -4, 6, -12, and -13), fibroblast growth factors-1 and -2, platelet-derived growth factor-AA, and -BB, platelet rich plasma, insulin growth factor (IGF-I, II), growth differentiation factor (GDF-5, -6, -8, -10) vascular endothelial cell-derived growth factor (VEGF), exendin 4, (monocyte chemoattractant protein-1) (MCP1), pleiotrophin, endothelin, nicotinamide, glucagon like peptide-I and II, parathyroid hormone, tenascin-C, tropoelastin, thrombin- derived peptides, laminin, biological peptides containing cell- and heparin-binding domains of adhesive extracellular matrix proteins such as fibronectin and vitronectin, and combinations thereof.
The compartments of the present devices are made of biocompatible materials. By “biocompatible” is meant that the device of the present invention does not substantially adversely affect any desired characteristics of the biological entity to be seeded or incorporated within the device, or the cells or tissues in the area of a living subject where the device is to be implanted, or any other areas of the living subject.
By “a living subject” is meant to include any mammalian subject, including a primate, porcine, canine or murine subject, and particularly a human subject.
A compartment can be fully or partially biodegradable, and one or all the compartments of a device can be made biodegradable or non-biodegradable depending on the application. By “biodegradable” or “bioabsorbable” is meant that after the device is delivered inside the body of a living subject, the device will be gradually degraded or absorbed by the body, or passed from the body.
Those skilled in the art will appreciate that the selection of a suitable material for forming a particular compartment of the devices of the present invention depends on a number of factors. The more relevant factors in the selection of the appropriate material include bioabsorption (or biodegradation) kinetics; in vivo mechanical performance; cell response to the material in terms of cell attachment, proliferation, migration, differentiation, and biocompatibility. Other relevant factors, which to some extent dictate the in vitro and in vivo behavior of the material, include the chemical composition, the spatial distribution of the constituents, the molecular weight, the degree of crystallinity, and the monomer content (i.e., the ratio of the remaining monomer within the bulk of a polymer after the polymerization process) in the case of polymeric materials.
Suitable materials for making the compartments of the present devices include biocompatible metals such as stainless steel, cobalt chrome, titanium and titanium alloys; or of bio-inert ceramics such as alumina, zirconia and calcium sulfate; biodegradable glasses or ceramics containing calcium phosphates.
Other materials suitable for making the compartments include non-biodegradable synthetic polymers, including but not limited to polyethylene, polymethylmethacrylte (PMMA), silicone, polyethylene oxide (PEO), polyethylene glycol (PEG), and polyurethanes.
The compartments of the present devices can also be made of biogradable synthetic polymers such as, without limitation, aliphatic polyesters, polyalkylene oxalates, polyamides, polycarbonates, polyorthoesters, polyoxaesters, polyamidoesters, polyanhydrides and polyphosphazenes. Aliphatic polyesters can be homopolymers or copolymers (random, block, segmented, tapered blocks, graft, triblock, etc.) having a linear, branched or star structure. Suitable monomers for making aliphatic homopolymers and copolymers may be selected from the group consisting of, but are not limited to, lactic acid, lactide (including L-, D-, meso and L,D mixtures), gl ycolic acid, glycolide, ε-caprolactone, ρ-dioxanone, trimethylene carbonate, δ-valerolactone, β-butyrolactone, ε-decalactone, 2, 5-diketomorpholine, pivalolactone, α, α-diethylpropiolactone, ethylene carbonate, ethylene oxalate, 3-methyl-1,4-dioxane-2,5-dione, 3,3-diethyl-1,4-dioxan-2,5-dione, γ-butyrolactone, 1,4-dioxepan-2-one, 1,5-dioxepan-2-one, 6,6-dimethyl-dioxepan-2-one and 6,8-dioxabicycloctane-7-one.
Preferred polymers include polylactic acid (PLA), polyglycolic acid (PGA), polycaprolactone (PCL), polydioxanone (PDO), trimethylene carbonate (TMC), polyvinyl alcohol (PVA), copolymers, or blends thereof.
Biodegradable, biocompatible elastomers are also particularly useful materials for making the devices of the present invention. Suitable elastomeric polymers include, but are not limited to, elastomeric copolymers of ε-caprolactone and glycolide with a mole ratio of ε-caprolactone to glycolide of from about 35/65 to about 65/35, more preferably from 35/65 to 45/55; elastomeric copolymers of ε-caprolactone and lactide where the mole ratio of ε-caprolactone to lactide is from about 35/65 to about 65/35 and more preferably from 35/65 to 45/55; elastomeric copolymers of lactide and glycolide where the mole ratio of lactide to glycolide is from about 95/5 to about 85/15; elastomeric copolymers of ρ-dioxanone and lactide where the mole ratio of ρ-dioxanone to lactide is from about 40/60 to about 60/40; elastomeric copolymers of ε-caprolactone and ρ-dioxanone where the mole ratio of ε-caprolactone to ρ-dioxanone is from about from 30/70 to about 70/30; elastomeric copolymers of ρ-dioxanone and trimethylene carbonate where the mole ratio of ρ-dioxanone to trimethylene carbonate is from about 30/70 to about 70/30; elastomeric copolymers of trimethylene carbonate and glycolide where the mole ratio of trimethylene carbonate to glycolide is from about 30/70 to about 70/30; elastomeric copolymers of trimethylene carbonate and lactide where the mole ratio of trimethylene carbonate to lactide is from about 30/70 to about 70/30, or blends thereof.
The compartments of the present devices can also be made of biodegradable biopolymers that are naturally occurring biological materials or derivatives thereof. Such biopolymers include, e.g., small intestine submucosa (SIS), hyaluronic acid, collagen, alginates, chondroitin sulfate, chitosan, and blends thereof.
In one embodiment, one or more compartments of a device are made of a fibrous scaffold, which is prepared from biocompatible metals, biodegradable glasses or ceramics, non-biodegradable or biodegradable polymers, as described herein above, or combinations thereof. The fibrous scaffold can be prepared by weaving, knitting, warped knitting (i.e., lace-like), dry laying, wet laying or braiding, and can be organized in a form selected from threads, yarns, nets, laces, felts or nonwoven mats.
In another embodiment, one or more compartments of a device is made of a porous, polymeric matrix prepared by conventional polymer processing techniques such as extrusion, cast molding, injection molding, and blow molding. In a specific embodiment, the porous matrix is in the form of a polymeric foam, which can be fabricated by a variety of techniques such as, for example, lyophilization, supercritical solvent foaming, gas injection extrusion, gas injection molding or casting with an extractable material (e.g., salts, sugar or similar suitable materials).
In still another embodiment, one or more compartments of a device are fabricated in the form of a composite of a polymeric matrix and a fibrous scaffold where the percentage of the polymeric matrix determines the overall porosity of the composite.
In accordance with the present invention, the materials and fabrication techniques are selected and tailored to produce a compartment that accommodates the specific biological entity or entities to be delivered by such compartment.
For example, a cellular compartment should be made such that the pore size and porosity of the compartment are optimal for uniform distribution of the cells in the compartment, for diffusion of nutrients and oxygen, and for ingrowth of cells to establish stable vasculature. Porosity and pore size can be controlled by a variety of means, including manipulating the density of the fibers in the fibrous component, the concentration or amount of the polymer solution used in forming the compartment. Additionally, a compartment, e.g., a fibrous scaffold, can be treated, after the fabrication of the scaffold, with factors that facilitate cell seeding and enhance cell attachment, for example, fibronectin, collagen, laminin and other extracellular matrices.
A compound compartment, on the other hand, should be made to have desired release kinetics of the compound. A variety of techniques have been developed to incorporate a compound into a polymeric porous device. The compound can be impregnated within the entire device via an injection technique disclosed in U.S. Pat. No. 5,770,417. A device can also be submerged in a solution containing the compound such that the compound fills the interstices within the device. Alternatively, a scaffold device can be immersed in a solution containing the compound, and the solvent allowed to evaporate, thereby precipitating the compound on the surface of the scaffold, as disclosed in U.S. Pat. Nos. 5,980,551 and 5,876,452. Additionally, a compound can be adhered to a scaffold by surface modification of the scaffold to allow better attachment, as achieved using techniques such as plasma irradiation (Kwok et al., J. Controlled Release 62: 301-311,1999). Another common technique is freeze drying, wherein the compound or a solution containing the compound is added to a polymer solution, and the solvent is sublimed leaving behind a polymer scaffold with the compound dispersed within. Organic solvents, such as an alcohol or ether with a relatively high melting point, can be used to facilitate the infiltration of soluble compounds into the porous matrix of a scaffold.
Although cellular compartments and compound compartments are typically designed and fabricated separately, certain compartments (e.g., a composite device) may be suitable for loading both cells and one or more bioactive compounds.
In one embodiment, the present invention provides a device composed of at least two compartments. The two compartments can be made in any geometrical shape and can be adjoined snugly with each other such that the biological entity in one compartment provides a beneficial effect to the biological entity in the other compartment.
In a specific embodiment, one compartment of the device is a cellular compartment and another compartment is a compound compartment, and the two compartments can be adjoined snugly with each other to permit the interactions between the compound released from the compound compartment and the cells in the cellular compartment.
In another preferred embodiment, the device is comprised of an inner compartment that has a disk-like geometry and an outer compartment that has a ring-like geometry. A particularly preferred device is shown in
In a specific embodiment (
In another specific embodiment (
In yet another specific embodiment (
In still another embodiment, the device includes at least two cellular compartments prepared separately for loading two different types of cells, where the two compartments can be joined snugly with each other such that the cells in one compartment provides beneficial effect to the cells in the other compartment.
In a specific embodiment, the device is comprised of an inner compartment that has a disk-like geometry and an outer compartment that has a ring-like geometry, where the inner compartment is loaded with islets of Langerhans and the outer compartment is loaded with Sertoli cells. The Sertoli cells can improve the survival of the islets and prevent or reduce an immune response upon implantation.
In another specific embodiment, one compartment of a device is loaded with cells that produce and secrete a molecule that improves the survival and function of cells in another compartment. For example, one compartment is loaded with islets of Langerhans and another compartment of the same device is loaded with genetically modified cells that have been transfected with a vector coding for VEGF-121. Once the two compartments are combined and transplanted, the transfected cells can start producing VEGF-121, a powerful angiogenic agent, which accelerates the neo-vasculature process, which in turn enhances the survival of the transplanted islets.
The compartments of a device can be combined prior to implantation and maintained under suitable conditions for a period of time prior to implantation. Alternatively, the compartments are combined and are implanted shortly thereafter. Additionally, one or more compartments can be implanted first, and the remaining compartment(s) can be implanted at a later time.
The multi-compartment devices of the present invention are particularly useful for delivering islets or insulin-producing cells or precursors thereof in combination with one or more bioactive compounds. As islet survival depends on adequate diffusion of oxygen and nutrients, it is desirable to load the delivery devices with molecules that are beneficial for establishing stable vascularization. The devices of the present invention, which combine compartments designed and fabricated separately to accommodate cells and a bioactive compound(s), respectively, permit effective delivery and optimal activities of both islets or insulin producing cells and the bioactive compound(s).
Accordingly, in a further aspect of the present invention, a device as described hereinabove is utilized for the treatment of diabetes mellitus.
Those skilled in the art will realize that a key feature of the current invention lies the ability to assemble a device with compartments prepared to address the specific requirements of the biological entities to be delivered. The devices of the present invention allow for the incorporation of a variety of therapeutic compounds, each with distinct release profiles, without compromising the porosity necessary for the survival and function of transplanted cells.
The following examples are illustrative of the principles and practice of the invention, although not limiting the scope of the invention. Numerous additional embodiments within the scope and spirit of the invention will become apparent to those skilled in the art.
In the examples, the polymers and monomers were characterized for chemical composition and purity (NMR, FTIR), thermal analysis (DSC) and molecular weight by conventional analytical techniques.
Inherent viscosities (I.V., dL/g) of the polymers and copolymers were measured using a 50 bore Cannon-Ubbelhode dilution viscometer immersed in a thermostatically controlled water bath at 30° C., utilizing chloroform or hexafluoroisopropanol (HFIP) as the solvent at a concentration of 0.1 g/dL.
Certain abbreviations are used. These include PCL to indicate polymerized ε-caprolactone; PGA to indicate polymerized glycolide and PLA to indicate polymerized (L) lactide. Additionally, the ratios in front of the copolymer identification indicate the respective mole percentages of each constituent.
The polymer used to manufacture the foam compartment was a 35/65 PCL/PGA copolymer produced by Birmingham Polymers Inc. (Birmingham, Ala.), with an I.V. of 1.45 dL/g. A 5/95 weight ratio of 35/65 PCL/PGA in 1,4-dioxane solvent was weighed out. The polymer and solvent were placed into a flask, which in turn was put into a water bath and stirred for 5 hours at 70oC to form a solution. The solution was then filtered using an extraction thimble (extra coarse porosity, type ASTM 170-220 (EC)) and stored in a flask at room temperature.
A laboratory scale lyophilizer, or freeze dryer, (Model Duradry, FTS Kinetics, Stone Ridge, N.Y.), was used to form the compartment. The polymer solution was added into a 4-inch by 4-inch aluminum mold to a height of 2 mm. The mold assembly was then placed on the shelf of the lyophilizer and the freeze dry sequence begun. The freeze drying sequence used in this example was: 1)−17° C. for 60 minutes, 2)−5° C. for 60 minutes under vacuum 100 mT, 3)5° C. for 60 minutes under vacuum 20 mT, and 4)20° C. for 60 minutes under vacuum 20 mT.
After the cycle was completed, the mold assembly was taken out of the freeze dryer and allowed to degas in a vacuum hood for 2 to 3 hours. A foam sheet was then removed from the mold and an 8 mm dermal biopsy punch (Miltex Inc. New York, N.Y.) was used to cut a disk from the foam sheet. Another dermal biopsy punch that is 5mm in diameter was used to cut a centric 5 mm disk in the previously cut 8 mm disk leaving behind a ring with an inner diameter of 5 mm and an outer diameter of 8 mm.
A needle-punched nonwoven mat (2 mm in thickness) composed of a 90/10 PGA/PLA (vicryl® Ethicon Inc.) fiber was made as described below. A copolymer of PGA/PLA (90/10) was melt-extruded into continuous multifilament yarn by conventional methods of making yarn and subsequently oriented in order to increase strength, elongation and energy required to rupture. The yarns comprised filaments of approximately 20 microns in diameter. These yarns were then cut and crimped into uniform 2-inch lengths to form 2-inch staple fibers.
A dry lay needle-punched nonwoven mat was then prepared utilizing the 90/10 PGA/PLA copolymer staple fibers. The staple fibers were opened and carded on standard nonwoven machinery. The resulting mat was in the form of webbed staple fibers. The webbed staple fibers were needle punched to form the dry lay needle-punched, fibrous nonwoven mat.
The mat was scoured with iso-propanol for 60 minutes, followed by drying under vacuum. A 5 mm biopsy punch was used to cut a disk from the fibrous mat.
The polymer used to manufacture the foam component was a 35/65 PCUPGA copolymer produced by Birmingham Polymers Inc. (Birmingham, Ala.), with an I.V. of 1.45 dL/g. A 0.5/99.5 weight ratio of 35/65 PCL/PGA in 1,4-dioxane solvent was weighed out. The polymer and solvent were placed into a flask, which in turn was put into a water bath and stirred for 5 hours at 70° C. to form a solution. The solution then was filtered using an extraction thimble (extra coarse porosity, type ASTM 170-220 (EC)) and stored in a flask.
A laboratory scale lyophilizer, or freeze dryer, (Model Duradry, FTS Kinetics, Stone Ridge, N.Y.), was used to form the composite sheet. Approximately 10 ml of the polymer solution was added into a 4-inch by 4-inch aluminum mold to cover uniformly the mold surface. The needle-punched fibrous mat prepared in Example 2 was immersed into the beaker containing the rest of the solution until fully soaked and was then placed in the aluminum mold. The remaining polymer solution was poured into the mold so that the solution covered the nonwoven mat and reached a height of 2 mm in the mold. The mold assembly then was placed on the shelf of the lyophilizer and the freeze-drying sequence begun. The freeze drying sequence used in this example was: 1)−17° C. for 60 minutes, 2)−5° C. for 60 minutes under vacuum 100 mT, 3)5° C. for 60 minutes under vacuum 20 mT, and 4)20° C. for 60 minutes under vacuum 20 mT.
After the cycle was completed, the mold assembly was taken out of the freeze drier and allowed to degas in a vacuum hood for 2 to 3 hours. The composite sheet was then removed from the mold and a dermal biopsy punch was used to cut a 5 mm disk from the sheet.
Several composite inner compartments were fabricated as indicated above in Example 3. The compartments were then sterilized using EtO method of sterilization. A 0.5 mg/ml solution of VEGF-121 in a co-solvent system of PBS and tertiary butanol was prepared with the tertiary butanol to PBS ratio being 6%. An aliquot of 20 μl of this solution was pipetted onto each of three composite inner compartments. Within 10 seconds, VEGF solutions completely infiltrated the scaffolds, which were then frozen and the solvents sublimed. Similar procedure was used to load 3 other inner compartments with blank vehicles as controls.
Contracting collagen gels were made using type I rat tail collagen (3.69 mg/ml, BD Biosciences) and primary rat thoracic aorta endothelial cells (0.5×106/mL). Medium (Endothelial Growth Medium-2, Cambrex), collagen, neutralizing medium (medium containing 0.1N NaOH), and cells were mixed in a 4:2:1:1 ratio respectively. Six ml of the collagen/cell mixture was pipetted into each well of a 6-well low cluster plate (Costar) and allowed to solidify at 37° C., 5% CO2 for 2-4 hours prior to the addition of 3 ml medium. After two days, the gels had contracted by approximately 4 mm.
An 8 mm biopsy punch was used to remove the center of the gel from all samples. Each inner compartment (d=5 mm)(loaded either with VEGF-121 or a blank vehicle) was combined with an outer fibrous compartment (d=8 mm), fabricated essentially as described in Example 2. Finally each two-compartment device was inserted into the space prepared in the collagen gel (
Outer compartments were made from a composite matrix similar to the one prepared in Example 3. The compartments were loaded with three different amounts (10.99 ng, 109.9 ng, or 1099 ng) of p38 kinase inhibitor (JNJ 3026582, also known as RWJ 67657). The chemical structure of this compound (4-[4-(4-fluorophenyl)-1-(3-phenylpropyl)-5-44-pyridinyl)-1H-imidazol-2-yl]-3-butyn-1-ol) has been previously documented (Wadsworth et al., J. Pharm. Exp. Ther 291:680-687, 1999).
The inner compartments were prepared from a non-woven Vicryl® fibrous matrix fabricated as described in Example 2. Mononuclear cells were freshly isolated from human peripheral blood, counted and adjusted to a final cell number in RPMI-1640 (Invitrogen Life Technologies, Carlsbad, Calif.) with 1% fetal bovine serum (FBS, HyClone, Logan, UT). A total of 1×106 cells in a final volume of 50ul were seeded onto the inner compartments.
The two compartments were combined and pre-cultured for 1 hour in a 24-well plate with 0.5 ml culture medium. A stimulus of LPS (lipopolysaccharide) (10 ng/ml; Sigma, St. Louis, Mo.) was added to each well and incubated overnight at 37° C., 5%CO2. Supernatant from each well was collected and analyzed for TNF-α content using a standard commercial ELISA kit (R&D Systems, Minneapolis, Minn.). Control wells for assay were seeded with an identical number of cells and a titrated amount of drug in solution without the presence of the device (
This application claims priority from U. S. Provisional Application No. 60/584,343, filed on Jun. 30, 2004.
| Number | Date | Country | |
|---|---|---|---|
| 60584343 | Jun 2004 | US |
