Patent Application
20100022479
This invention relates to cellular composite products based on polymers incorporating fillers and/or fibres and the method to process them. Such composite structures may advantageously be used in tissue engineering, bone replacement, consumer goods, transportation or in any other suitable field.
Porous materials are numerous in nature (bone, wood, sponge . . . ) as well as in synthetic materials (foams, honeycomb for sandwich structures, . . . ). Bone structure for instance, has been optimised by nature during millions of years, offering performance in terms of lightness, stiffness, strength, shapes, porosity, healing performance etc. As bone is basically a composite of natural ceramic and polymer materials with different distribution of porosity and mechanical properties, it is of interest to mimic this material and structure.
Any synthetic composite offering the properties of natural bone or based on a similar microstructure will open new opportunities for the next generation of polymer composites such as for applications in the biomedical field where they can be used as optimised implant for example. Similar structures will as well offer novel opportunities in applications where lightness and strength are required.
In the present text the terms “porosity” and “pore density” are synonyms.
Polymer foams are widely used in various applications such as insulation panels, furniture, damping components, composite sandwich structures . . . . Mechanical properties of these cellular solids mainly depend on the morphology of the pores, the properties of the raw material and the density of the foam (Gibson and Ashby 1988). Several foaming processes have been developed according to the different polymer types (Klempner and Frisch 1991). Current research aims at a better understanding of the foaming mechanisms in order to better control distributions and gradients of pore sizes and density as well as their morphology development.
Polymer based composites have been developed for their design freedom, offering tailored mechanical properties via the combination of polymers with different fillers or fibres (Manson 2000). Composition, orientation and architecture of the reinforcement can be selected to provide desired final performance. Several processing methods have been developed with always the same objective, obtaining a composite with a minimum of porosity in order to ensure optimum performance. Indeed uncontrolled morphology of pores induces stress concentrations, reductions of stiffness and early failure.
The main feature of gradient material is that its properties change gradually with position. The property gradient in the material is caused by a position dependent chemical composition, microstructure or atomic order. An early example of a gradient material manufactured by mankind is polyurethane skin foams, which are fully dense at the surface and porous in the interior. They provide high impact strength at low weight and are thus used for instrument panels or head rests in cars (Piechota and Röhr 1975). Another criterion can be the geometry of the gradation (throughout the bulk or only a coating) or the gradation's function as it is the case for functionally graded materials (FGMs). For processing FGMs numerous techniques are available. For metallic and ceramic materials, traditional powder processing can be used if an additional gradation step is introduced before consolidation. Wet processing takes use of aqueous suspensions instead of powders.
In polymer based composites, the sheet-lamination (stacking of 2D-fabrics) is used to obtain products with a step-like gradient through the thickness. Sometimes the impregnation distances in such composites are quite long, what motivated for example the development of preimpregnated preforms and of commingled (hybrid) yarns (Bourban, Bernet et al. 2001). Furthermore in sheet-lamination one might be confronted with delamination between laminae, stress concentrations and distributions, occurrence of internal stresses (Sunderland, Yu et al. 2001) or deconsolidation (Wolfrath, Michaud et al. 2005) due to the elastic energy stored in the fibre reinforcement network of the composite. The deconsolidation phenomena can be used for fabrication of porosity gradients in thermoplastic materials. Hereby the attainable porosity gradients are directly linked to the porosity increase during deconsolidation. This technique allows only very specific and limited design of polymer-based gradient composites. Indeed to precisely mimic bone structure for example larger porosity volumes, control of pore size and distribution, precise control of fillers and fibres positions are required. Combination of porosity and reinforcement gradients is still to be developed.
Indeed, bone is a very good example of a tailored porous composite structure. It has a complex hierarchical organization at the micro- and nano-level, and is made of hydroxyapatite crystals, collagen molecules and water as elementary components. Furthermore it shows a continuous change in architecture and collagen concentration when passing from cortical to trabecular bone tissue. There is an interphase in which the porosity passes from closed to open porosity. In this meaning bones are considered as functionally graded materials. Bones are viscoelastic and anisotropic. The current invention proposes composite systems and processing methods to mimic these bone properties.
Favourable materials such as stainless steel, titanium and its alloys, calcium phosphates and alumina ceramics, polyethylene (PE) and polyetheretherketone (PEEK), and composites of these materials have been used in orthopaedic surgery. At present biodegradable polymers are also being studied, and have had some clinical success, with the aim of avoiding a second operation after successful bone healing.
Polymer biomaterials have gained a significant importance in health care and well-being in our modern society (Chu 2000). Fibres and textile fabrics have found some applications in this field. Sutures in wound closure represent the first and major use of fibres in medicine. Textiles can have either external uses like bandages, or internal, like vascular grafts where they bring flexibility and porosity, or as reinforcement of polymer in hip prosthesis, where they can bring anisotropy and enable to better match bone properties. Textiles could also be used for scaffolds in tissue engineering (Hutmacher 2000). Competences in science and engineering are currently being gathered to develop functional tissue and organ replacements (Burg, Porter et al. 2000; Rose and Oreffo 2002). In scaffold applications, fibres have been used as non woven mesh, which provides high porosity and a large surface area for cell adhesion and proliferation. However this type of scaffold is highly deformable and has poor mechanical properties (Cima, Vacanti et al. 1991). Attempts have also been made to prepare scaffolds with 3D woven fabric, using Ultra High Molecular Weight Polyethylene (UHMWPE) fibres coated with Low Density Polyethylene (LDPE). This 3D textile has been tested in cartilage applications and has shown compatibility with surrounding tissues (Shikinami and Kawarada 1998). Wintermantel (Wintermantel, Mayer et al. 1996) also suggests that superstructures with knitted fibres could be used in tissue engineering: they are porous, deformable to obtain complex shapes, and stiffness can be increased by impregnation with a polymer. Research in tissue engineering is also conducted to provide synthetic tissue graft (Atala and Mooney 1997). Scaffolds for tissue engineering need to be highly porous to have a high specific surface area for cell adhesion and a high void volume to allow vascularisation, nutrient diffusion and cell proliferation and differentiation. The first idea for such a porous structure is open-cell foams. Four main techniques of foaming have been developed mainly for bioresorbable polymers, with their own advantages and drawbacks: solvent casting and particles leaching, gas foaming, emulsion freeze-drying and thermally induced phase separation. They can be adapted to thermoplastics, and more specifically to bioresorbable and biocompatible polymers. It is known that non medical grades of PE or PET foams, with closed cells, are used in packaging, sports, construction, and automotive. Biocompatible grades of these polymers and bioresorbable polymers will certainly be more extensively considered in future for biomedical applications when tailored open-cell structures can be produced.
It is to note that mechanical properties of polymer foams always appear to be low, in particular if intended use is hard tissue engineering. It could thus be interesting to prepare and evaluate three-dimensional open-cell foams, i.e. porous polymer, reinforced with fillers, fibres and/or textile fabrics. Furthermore, these reinforcements can bring anisotropy, gradient of properties and functions.
Despite bone grafts is a routine procedure in orthopaedic surgery, no satisfactory bone substitutes are currently available. The use of synthetic bone substitutes is increasing; however, in a review of clinically available bone substitutes in France, no polymer scaffold was available for orthopaedic applications (Mainard, Gouin et al. 2001). Most of the synthetic bone grafts used are made of ceramic such as calcium phosphates, which do not allow load-bearing application due to their low toughness and brittle mechanical behaviour. There is actually a need for new synthetic bone scaffolds which can be used in different surgical situations, especially for load-bearing applications. Scaffolds based on porous polymer composites represent then an attractive solution.
The first step in bone and cartilage tissue engineering is to develop a scaffold with controlled high porosity for maximal loading with cells and tissue ingrowth. It should be able to support cell proliferation, differentiation, and function. For bone, the minimum pore diameter required for ingrowth of cells into the interior of the matrices is 100 μm (Laurencin, Attawia et al. 1996). Indeed, it has been suggested that the ideal pore-size range of 200-400 μm is preferred by osteoblasts because it provides the optimum compression and tension on the osteoblast's mechanoreceptor (Boyan, Hummert et al. 1996). One of the key aspects of size porosity is to avoid occlusion of pores by cells. Interconnected porosity is also important for bone ingrowth (Baksh and Davies 2000). However, diffusion does not seem related to pore sizes as for osteocytes, canaliculi of the micrometer sizes allowed nutrients to reach these cells. As bone formation needs vascular support, the scaffold should also allow a rapid development of vascularization.
From a biomechanics point of view, properties of the scaffold should be close to the ones of bone if load-bearing applications are planned. In the slow regeneration of skeletal tissues, the mechanical stress should be engineered to be low during early phases, although it should increase during the late differentiation phase to properly align and mature the mechanical functioning of the repair tissue. A high initial stiffness will allow primary union followed by gradual resorption and reduction in stiffness corresponding to simultaneous bone healing to take-up load-bearing functions.
Furthermore, the material should be easily processed into complex shaped components (U.S. Pat. No. 0,054,372A1) even when bioresorbable constituents are used.
So far, in thermoplastic polymer foams mainly micro-sized, and more recently, nano-sized, fillers were used to reinforce foams and/or tailor foam morphology and properties. They were produced through various routes, such as reactive foaming of polyurethanes, solvent-phase processing, and gas foaming. The latter technique was in particular applied to a bioresorbable calcium phosphate-poly(L-lactic acid) (PLA) system, showing improved compression resistance and improved biocompatibility with bone cells (Mathieu, Montjovent et al. 2005; Mathieu, Bourban et al. 2006; Mathieu, Mueller et al. 2006). The observed increase in mechanical properties is related to an increase in foam density. These authors describe the preparation of porous composites based first on the homogeneous dispersion of fillers in the polymer matrix, which implies that the composition of pore walls does not vary across the foam. The only gradient present in these cellular composites is induced by the foaming process: due to different cooling rates in the core and on the outside of a sample, a higher pore density with smaller pores is obtained on the latter than in the middle. This porosity gradient mimics in particular the bone structure, and these biocomposites were shown to be biocompatible allowing cell proliferation and differentiation (Montjovent et al, 2005). Reactive foaming and solvent-based processes cited previously were used to obtain fibre-reinforced foams. However, particles and short fibres do not reinforce the polymeric foams sufficiently. Polyurethane (PUR) foams have already been reinforced with glass fibres, jute or woven flax (Bledzki A. K. 2001). However, to our knowledge no continuous fibres have been introduced into thermoplastic foams and an interconnected and micro-sized porosity obtained. Moreover no gradients in fibre volumes have yet been considered in the case of porous or cellular structures. The addition of continuous fibres, possibly combined with short fibres/particles in the matrix, allows further reinforcement even if the porosity is kept constant. By combining reinforcement volume and porosity gradients, structures can be tailored which are similar to the natural bone architecture, having an interface between trabecular and cortical bone, without having discontinuities in structure and concentration. The interest in the use of long, continuous reinforcing fibres in foams lies in the fact that the critical fibre length increases with the porosity and thus the mechanical foam properties (modulus, rupture resistance) can be increased.
Ideally the material should be easily processed into complex shaped components. A material exhibiting the viscoleastic and anisotropic properties of natural tissue will be preferred as it will integrate better into the body and transmit load in an optimised way reducing stress concentration or stiffness mismatches for instance.
Current ceramic implants have an intrinsic low toughness and can not easily be shaped or screwed; that is why they are not considered as ideal. There is also risk of inflammation induced by micro movements between implant and bone, because of modulus mismatch.
Biocompatible and bioresorbable polymers present instead ductile properties. For example, bioresorbable poly(L-lactic acid) (PLA) is a very good candidate for implants and bone replacing material. Fibres and/or fillers can be added to improve not only the mechanical behaviour but also other properties of the PLA such as dimensional or thermal stability, barrier properties, and biological functionalities. (U.S. Pat. No. 5,108,755) discloses composites comprising Poly-ε-caprolactone matrix reinforced with certain biodegradable fibres for improved retention of yield strength and Young's modulus with time under degrading conditions. (U.S. Pat. No. 4,655,777) is disclosing matrix reinforced with biodegradable fibres for increased strength of bone fixation plates in which no significant porosity, such as it would be the case for bone replacement implants, is present. The composite is prepared using conventional processing routes. As in the case of bulk composites, a similar extension of properties range can be obtained with porous composite structures.
In summary, mechanical performance of current scaffolds needs to be improved, and scaffolds should also be processable during surgery to correctly fit the bone defect. Polymer based composites have the potential to mimic bone microstructure, to provide range of mechanical properties and offer design freedom.
There is therefore a need for a new technique which enables the fabrication of composites with a thermoplastic matrix and reinforcing elements such as fillers, short or long or continuous fibres and having at the same time reinforcement volume and porosity gradients. The challenge is to combine fibre-volume and porosity gradients into composite structures which can be tailored to be similar to the natural bone architecture, having an interface between trabecular and cortical bone, without having discontinuities in structure and stress concentration. Similar structures can as well be found in other natural materials such us of the vegetable kingdom for instance.
A porous and reinforced polymer composite product is proposed, preferably obtained through a solvent-free process comprising the precise placement of fibres and/or fillers followed by the gas foaming of the composite preform. The composite product has a controlled cellular structure based on polymers with fillers, short, long or continuous fibres and combination of them. Gradients of fibre volumes (when fibres are used) are controlled through the placement of filaments, yarns or commingled yarns; fibre contents up to 65 vol % can be reached locally. Porosity can be varied from 0 up to 90% in volume and porosity gradients are achieved by varying the gas foaming parameters. The process can combine different types of gradients in order to prepare polymer foams with tailored variations of filler/fibre volumes and of porosity in several directions of the product. Fibres improve the mechanical modulus and strength of the porous composite while providing desired anisotropy and functional properties.
The invention will be better understood below with a detailed description including examples illustrated by the following figures:
The present invention relates to a porous or cellular composite product also named composite foam which will be described in terms of unique microstructure, macrostructure, morphology and characteristics. The process to obtain such product is then presented with its own specifics.
As depicted in
Porosity is defined in terms of relative volume of pores and of pore size distributions. When pores size and/or porosity volume change from one location to the other of the structure, a gradient of porosity is obtained. Different distribution functions can be used according to the variations of porosity volume desired in the different directions of the structure. Porosity can be closed and/or open when the pores are interconnected. The control of pore sizes is important for applications where liquids or biological media are injected or where growth of living cells occurs into the porous composite.
Distribution of fillers can be uniform through the structure, but a variation in the volume fraction along at least one direction (
Fibres can be of different aspect ratios between their lengths and their diameters. With the increase of the aspect ratio various type of fibres are usually considered, from short fibres to long fibres and to continuous fibres. For the latter the length of the fibres is close to or larger than the length of the elements or the structure considered.
A precise placement of fibres is required to induce gradients of fibre content or volume and thus gradients of properties or gradients of functions when functional fibres are added. Several gradient types are obtained depending of the relative positions of the fibres.
The process described below will offer different gradient types in terms of linear or non linear variations of composition, volume fractions and properties in one direction at least, in terms of variations in several space directions and in terms of combination of gradients. For example a variation of porosity from high porosity in the center of a part to a low porosity in the outside skin of the part can be combined with low fibre content in the center and high fibre content in the outside region of the part.
The method of this invention to process the mentioned porous composites comprises two main steps: a) preparation and precise placement of the reinforcement or functional material, and b) in situ creation of porosity.
Described fillers and fibres are placed properly in a way that after the next processing step creating porosity, they will still be in the desired position to ensure gradient properties into the final cellular composite.
Fillers, short fibres, long fibres, extruded or preimpregnated compounds cut at desired lengths, are placed on a mould surface and distributed locally to generate variation of weight or volume fraction at different regions of the mould surface. Placement of fillers is made by hand or by using automated set-up (EP1184147A2). The preform is then moved to the next processing step to be transformed in a porous composite. Cellular composites of type A are based on this reinforcement placement and preform.
This processing step relates to a specific placement method to obtain cellular composites of type B and C.
For processing unidirectional type B composites a winding set-up (
This equipment allows creating unidirectional composites with a precise cross-sectional yarns or fibres distribution. Furthermore the ratio of reinforcing and polymer filaments is controlled. Any 2D fibre volume gradient of one or more fibre types is achievable. Either reinforcement fibres such as dry fibres, preimpregnated fibres, commingled fibres, coated fibres; or functional fibres such as foamable fibres, elastomeric fibres, fibres with any cross-sections, nano fillers based polymer fibres, optical fibres, metallic fibres or hybrid yarns of these fibres can be used. When the placed fibres are water sensitive, an appropriate drying step can be added. When filaments or fibre bundles are used, it is possible to build up commingled yarns directly on the mould.
To avoid any modification of the fibres position before the next consolidation or foaming step, the placed fibre bundles can be preconsolidated in a mould (
For processing composite foams comprising 3D fibre architecture (type C) the fibre holder depicted in
It is obvious that the holder can have more or less elements, can be of different sizes and that several of them can be combined. Furthermore, the holder can be used to maintain any types of fibre fabrics and textiles such as woven, knitted or braided preforms, dried or preimpregnated.
Together with this fibre holder, which guarantees that the reinforcement fibres stay stretched in place for the whole coming foaming step, the fibres may be dipped into a bath of liquid or molten matrix polymer for coating or pre-impregnation.
Afterwards the fibre holder and the fibres are put into a mould within the foaming chamber. When needed to complete desired polymer volume fraction, polymer powder or granulate is added to the mould to have enough matrix material.
In this way it is possible to process solvent-free thermoplastic foams, which are reinforced by oriented continuous fibres. Hereby the fibres orientation as well as the fibres distribution and fibres volume gradients can be chosen as one thinks best.
Porosity can be obtained by controlling the preconsolidation parameters of type B composite preform. By varying the heat transfer across the mould of
In the present invention a foaming process is proposed for the production of composite foams. The process avoids the use of any solvent or additional chemical foaming agent and allows the nucleation and growth of pores into a composite material while maintaining the position of the reinforcement. Subsequently, gradients of porosity and reinforcement content are obtained.
The prepared preforms based on the fillers or short fibres, as well as the preforms based on the continuous fibres are placed into a closed heated and pressurized vessel where the foaming process is induced. Supercritical CO2 is used to foam the composite preforms placed into a hosting mold. Parameters are indicated here for a poly(L-lactic acid) based system, but can obviously be adjusted for any type of thermoplastic based system. CO2 penetrates into the autoclave, and pressure is increased up to 50 to 300 bars, but more preferably between 100 and 250 bars. The gas saturation temperature Tsat and pressure Psat, will control gas diffusion and concentration into the materials. Depressurization is obtained by gas release at a controlled flow rate, between 1 and 20 bar/s, and more preferably between 3 and 15 bar/s. Pores are nucleated. The foaming chamber is simultaneously cooled down due to depressurization and by additional water cooling. Cooling rates are preferably between 0.5 and 7.0° C./s. Initial depressurisation rate dP/dt and maximum cooling rate dT/dt are significant parameters which influence pore expansion and stabilisation. The mentioned processing parameters are varied to control pore sizes and distributions in order to achieve different gradients of porosity. The presence of fibres influences the nucleation and growth of pores and thus requires specific foaming parameters. For example, higher saturation pressures and slower cooling rates are required to create interconnected porosity.
As they are mainly based on polymer, the moulded composite foam samples can be cut, machined or screwed for the specific requirements of given applications.
In conclusion, the invention relates to a process integrating the steps of placement and preparation of fillers or fibres preceding the step of foaming the composite preforms and thus obtaining porous composite structures with tailored gradients.
With the above mentioned methods and combinations of them porosity gradients with variations ranging between 0 to 90% porosity in volume are achievable. At the same time, the fibre volume fraction, which is defined to be the fibre fraction within the solid material only can be tailored locally between 0 to 65% to get different gradient types.
Thus depending on local porosity level and fibre volume fraction the mechanical properties such as the elastic modulus, can vary on a large range. Examples will provide values for specific material systems.
Thermoplastic polymers in general can be used, such as polyethylene terephtalate (PET), polyethylene (PE), polyurethanes (PUR), etc. They can be reinforced with standard fillers or fibres using the mentioned processing steps.
Biocompatible and biodegradable polymers, fibres and particles already used in the biomedical field can be considered to prepare respectively biocompatible and biodegradable porous products to be used as scaffolds for example. Some examples of suitable polymers are α-polyhydroxy acids, such as poly(glycolic acid) (PGA), poly(lactic acid) (PLA, L or D,L enantiomers), poly(ε-caprolacton) (PCL), poly(trimethylene carbonate), poly(ethylene oxide) (PEO), poly(β-hydroxylbutyrate) (PHB), poly(β-hydroxyvalerate), poly(p-dioxanone) (PDS), poly(ortho esters), polypeptides, and copolymers of the above.
For the foaming process, polymers or compounds should have an intrinsic viscosity preferably higher than 0.8 dL/g, and more preferably higher than 1.0 dL/g. They must preferably be dried before processing, in order to prevent polymer hydrolysis.
Reinforcing elements can have the shape of particulate fillers, short, long or continuous fibres. They can be dry, preimpregnated with resins, coated or the result of a compounding process. Some suitable examples of ceramic particles are calcium phosphates, such as hydroxyapatite (HAp), β-tricalcium phosphate (β-TCP), calcium carbonate (CC), calcium dihydrogenphosphate (CDHP), calcium hydrogenphosphate (CHP), or mixtures of above, and bioactive glasses, such as Bioglass®, phosphate based glasses . . . . Fillers and fibers based on natural and renewable resources such as cellulose, starch, etc can be used as well. Filler volume fraction is preferably comprised between 0 and 15 vol %. Composites of type A can also contain fillers, particles or fibres in the nanometric range such as nanofillers or nanotubes made of various materials.
Long and continuous fibres can be made of traditional materials such as glass, carbon, of resorbable glass, such as Bioglass® and phosphate based glasses. Polymer and composite fibres are also used. For example cellulosic or wood fibres are used for processing cellular composite made of renewable resources. Polymer fibres containing fillers or other reinforcement material are envisaged as well. In opposite to filler material which increases the polymer's viscosity, the volume fraction of long/continuous fibres can go up to 65%. The polymer's capacity for foaming is maintained even for such high fibre volume fractions because the polymer's viscosity is not changed. The polymer (eventually charged with a low fraction of fillers) will simply foam around the continuous fibres. Nevertheless the size and distribution of porosity is affected by fibre presence and distribution.
With the described method, combination of different fillers and fibre types is possible. For example, hybrid fibre systems, polymer fibres, biodegradable fibres, metallic fibres, optical fibres, functional fibres can be integrated into porous composite structures using the method of this invention. Functionally graded composites can thus be processed. Degradable, foamable, coated or hollow fibres can bring additional porosity and additional ways to distribute pores into the final composite.
The composite foams obtained can be tailored in terms of porosity. Obviously they can thus be infiltrated and filled with any media, liquid or gel bringing additional function to the structure. For example bioactive or rheoactive fluids are of interest for tissue engineering applications and damping materials respectively. Another example is the use of catabolic or anabolic drugs, proteins such as growth factors, or any chemical agents influencing the bone metabolism liquid or dissolved in a liquid, which can thus be deposited at the surface of the pores.
The objective of this example is to illustrate how to obtain a composite porous structure of type A (
First 5 g of PLA+5% β-TCP (PLA-5TCP), and 5 g of PLA+10% β-TCP (PLA-10TCP) are extruded under an inert atmosphere, using a micro-extruder (Micro5, DSM; the Netherlands). The following parameters are used: screw rotation speed 100 rpm, residence time 4 min and set temperature 200° C. Extruded compounds are then dried and cut into 1 cm long rods. Into a 50 mm diameter cylinder mould, a paper cylinder of 35 mm diameter is placed inside. Inside this cylinder, the 5 g of PLA-5TCP are placed, and on the outside the 5 g of PLA-10TCP are added. The paper cylinder is then removed, leading to a gradient of β-TCP concentration in the composite.
In a second step, foaming is carried out. The mould prepared as previously described is put into the autoclave. After tightly closing, pressure is increased up to 200 bar, and temperature up to 195° C. After 10 min saturation, pressure is released at a maximum rate of 4.5 bar/s, and cooling simultaneously occurs. Controlling the processing parameters, a porous composite structure with two gradients is achieved (
Processing steps and microstructure of type B composites with fibre volume gradients is described. The winding set-up is used to place polyamide (PA12) fibre bundles here with 32 monofilaments and carbon fibres (CF), in this case bundles of 250 monofilaments, around the mould (8) (
The main challenge is here to combine fibre volume and porosity gradients, and more specifically, to preserve the initial fibre volume gradient when applying the gas foaming process to the system. The final fibre-reinforced foams have porosities ranging from 0% or more up to 90%.
The example is based on a bioresorbable polymer, Poly(L-lactic acid) (PLA) reinforced with glass fibres, but the method is not restricted to this material system.
Continuous conventional E glass fibres are winded progressively around the holder (
Depending on local porosity level and fibre volume fraction the mechanical properties such as the compression elastic modulus E can vary on a large range and in different gradient types. For the material system PLA and E glass fibres an overview of the achievable property range is given in
In the examples discussed previously the processing of foams reinforced with fillers, short or long or continuous fibres and the resulting structures are demonstrated on an application in the medical field but the processing techniques allow also fabrication of such cellular gradient composites for other applications.
Drug delivery systems are of major interest in the control of bone metabolism. There is then an important potential to combine the developed composite with catabolic or anabolic bone drugs, proteins such as growth factors or any chemical agents having an effect on bone metabolism. The mixing of the above enumarated agents combined with the composite is also possible. The combination of the composite with bisphosphonates is interesting. The composite is soaked in solutions containing different concentrations of bisphosphonate for some times to allow the composite to be impregnated and the pore surfaces to be coated with the drug solution. A possible process is to soak the composite in an aqueous solution containing 10 to 500 mM bisphosphonate, preferably 20 to 200 mM for one hour, preferably between 15 to 30 minutes. The obtained composite containing the drug is then be conserved in a freezer, preferably between −10° C. to −30° C. until the surgery is performed. As example, an animal study is performed where the composite containing a bisphosphonate (Zoledronate) is inserted in a bone defect of a rat condyle. The composite loaded with the bisphosphonate induces an important bone formation (anabolic activity), which is unexpected as the bisphosphonate is a drug designed to decrease the catabolic activity of the bone but not to increase bone anabolic activity. This increased anabolic activity of the bone with the combination of the composite and the bisphosphonate can be due to this particular delivery system and is highly interesting from a therapeutical point of view.
The proof-of-concept is then established and the composite could be an effective carrier of catabolic or anabolic bone drugs, proteins such as growth factors or any chemical agents having an effect on bone metabolism, and especially bisphosphonates.
| Number | Date | Country | Kind |
|---|---|---|---|
| 06116882.9 | Jul 2006 | EP | regional |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/IB07/52705 | 7/9/2007 | WO | 00 | 7/2/2009 |
