Patent Application
20220409778
The following invention relates to novel fiber reinforced polymeric compositions and processing methods suitable for medical devices. Particularly compositions from polymeric fibers incorporated into a resorbable matrix, which can be injection molded. The fibers greatly enhance the mechanical properties of the composite, and can be resorbable, non-resorbable, natural, metallic and from water soluble polymers. Also disclosed is the addition of inorganic additives to the matrix and/or the reinforcing fibers, which results in additional increase in mechanical properties while providing secondary effects such as osteoconductivity.
Tormala et. al. describes in U.S. Pat. Nos. 4,743,257 and 4,968,317 resorbable polymer compositions where the matrix and the reinforcing fiber are the same. Such self-reinforcement creates higher strength by drawing the material to produce highly aligned fibrils within the polymer thus increasing the mechanical properties of the material along the axis of alignment.
WO 90/12605 describes fiber reinforced bioerodible polymer compositions which include inorganic additives as well as oriented polymer fibers as a reinforcing component with the distinction that if the matrix is other than a poly(ortho ester), such as poly(lactic acid) the reinforcing additive must contain calcium-sodium metaphosphate, and when the reinforcement is other than calcium-sodium metaphosphate the matrix must include a poly(ortho ester).
WO 96/00592 describes a biodegradable reinforcement material that includes a pharmacological active ingredient with a biodegradable polymer layer, and a biodegradable reinforcing structure dispersed within the polymer layer. Such composition was described as having layers of reinforcement stacked with layers of polymer pressed together to incorporate the reinforcing layer into the polymer. A similar composition with layers of aligned fibers is described in US 20170246356A1.
In U.S. Pat. No. 7,541,049, fiber reinforced formulations are described where a bioceramic, or bioactive particles of size between 60 to 150 microns are dispersed into a resorbable matrix, and a resorbable polymer fibers are incorporated into said composite matrix as well. However, their processing method requires compression molding of fiber and powder to form an article, which is not as scalable as other methods such as injection molding.
Although widely used in the medical field, the currently used resorbable polymers for implantable medical devices have for the most part limitations on their mechanical properties. Highly elastic and ductile materials such as poly(dioxanone) (PDO), poly(caprolactone) (PCL), and poly (trimethylene carbonate) (PTMC) can only achieve tensile strengths of 20 to 30 MPa, whereas high strength polymers such as poly(lactides) (PLA) and poly(glycolides) (PGA) are much stronger, but also highly brittle. These limitations have excluded these materials from a large segment of medical device applications where load bearing capacity is paramount. Their current use is mostly in sports medicine with devices, such as suture anchors, interference screws, as well as non-load bearing resorbable plating systems for cranio-maxillofacial applications. Still the promise of resorbable plating systems for internal fracture fixation is desirable, since the material would restore normal function to the bone after fixation compared to plating systems, which would require a second surgery to remove the metallic plates and screws. Upper extremity periarticular plating systems are among the first in line candidates for such materials, especially given the prevalence of fractures of the distal radius and proximal humerus.
The present invention describes compositions of materials, which are suitable for these kinds of load bearing applications, wherein fibers are incorporated into a resorbable polymer matrix through an impregnation process, which requires a polymer with low viscosity and with a melting temperature sufficiently lower than that of the fibers to allow the fibers to be fully impregnated or wetted by the polymer without affecting their strength or melting them.
Materials having a resorbable matrix with a resorbable synthetic fiber have been extensively described, most recently in U.S. Pat. No. 7,541,049 and US 2017/0246356. A limiting factor for such compositions is the difference in melting temperatures of the matrix polymer and the reinforcing fiber, which make them unsuitable for injection molding. One of the most common examples of this are compositions of a PLA matrix reinforced with highly oriented PGA fibers. The melting point of PLA is approximately 180°, whereas the melting point of PGA is approximately 215° C. measured by differential scanning calorimetry DSC. Such composition can easily be compression molded at 180°−185° C., however injection molding requires good flowability of the material to be able to pass through the mold gate and cavity, additionally the higher the fiber concentration the higher the need for good flowability of the matrix material. To injection mold these compositions, the material needs to be heated above 200° C. At this temperature, the fibers significantly soften, and lose most of their strength due to loss of molecule orientation, or flat out melt if the injection molding temperature exceeds the melting point of the PGA. It is because of this limitation that the field only focuses on compression molded compositions of a resorbable synthetic matrix and a resorbable synthetic fiber, but injection molding compositions do not exist in the field. To provide a fiber reinforced resorbable material that can be injection molded, companies are turning their focus to the use of non-synthetic fibers such as bioglass. Materials that incorporate these fibers can be processed with ease at high temperatures without the fibers weakening or melting. Bioglass can be made into strong fibers, but once implanted the fiber reinforced material loses strength rapidly due to the material's fast degradation and pH change under bodily fluid conditions. Bioglass fibers are also radiopaque, which limits the surgeon's ability to monitor the placement of implants under fluoroscopy in order to assess the bone fusion. The use of polymeric fibers however, do not have that restriction since they are radiolucent.
The disclosed compositions differ from the prior art in this regard in two key aspects, processing method and selection of matrix/fiber. The prior art describes their fiber impregnation methods as solvent mixing, melt mixing using a twin-screw extruder and powder mixing. These methods are either not scalable (due to no being cost effective), as is the case for solvent and powder mixing, or are ineffective due to their inability to produce material with sufficiently long fibers in the case of mixing the fibers with the matrix polymer inside a twin-screw extruder. The current invention also describes a method called long fiber resorbable thermoplastic (LFRT). The advantage of LFRT is its ability to incorporate fibers into a base polymer with improved impregnation while limiting the time that the fiber is exposed to heat, as well as maintaining tension on the fiber while processing. These two aspects prevent polymer fibers from melting or shrinking to the point that they lose their strength due to polymer chain relaxation. Having thoroughly wetted fibers with minimal loss in strength makes the process particularly suitable for making pre-pegs (pellets with fibers pre impregnated with matrix polymer), which can be injection molded. Poorly wetted fibers agglomerate during injection molding, and as a result, the material does not possess good flowability, which makes it difficult to injection mold, leading to injection molded parts with poor strength and quality.
The present invention is directed to compositions that increase the mechanical properties of the base polymer by using reinforcing fibers dispersed into a resorbable matrix. The matrix described is made from a group of polymers, which resorb inside the body after implantation. The reinforcing fibers or woven textiles can be resorbable, non-resorbable, natural, or metallic. Additives can be incorporated into the matrix material or fibers to provide a secondary effect. These additives can be bioceramics or bioactive glass to produce an osteoconductive effect, antimicrobial particles such as silver, coloring agents, and radiopaque additives to make the implants visible under fluoroscopy. The incorporation of submicron sized additive particles into the matrix or into the fiber themselves result in an increase in tensile strength attributed to an increase in the interfacial bonding between the matrix and the fiber due to increased roughness, as well as increased heat transfer during molding between the fiber and the matrix. The disclosed compositions can be processed via both injection molding and compression molding. This is a key distinction between other compositions that rely on only compression molding methods due to the limited difference between the melting points of that of the fiber and the matrix.
The above and other objects, features and advantages of the present invention will be more clearly understood from the following detailed description taken in conjunction with the accompanying drawing, in which:
For the purpose of promoting a thorough understanding of the presently disclosed invention and not as a limitation of potential future embodiments of the herein disclosed invention, below are given examples of potential embodiments of the herein disclosed invention with reference made to specific embodiments with specific language being used to describe the same. It is therefore to be understood that no limitation of the scope of the herein disclosed invention shall be read into the preferred embodiment examples herein described or further modifications of the disclosed invention, with such further modifications and/or applications being those which would occur normally to one skilled in the art of the herein disclosed invention and related fields of study.
Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art. In case of conflict, the present document, including definitions, will control. Preferred methods and materials are described below, although methods and materials similar or equivalent to those described herein can be used in practice or testing of the present invention. All publications, patent applications, patents and other references mentioned herein are incorporated by reference in their entirety. The materials, methods, and examples disclosed herein are illustrative only and not intended to be limiting.
The terms “comprise(s),” “include(s),” “having,” “has,” “can,” “contain(s),” and variants thereof, as used herein, are intended to be open-ended transitional phrases, terms, or words that do not preclude the possibility of additional acts or structures. The singular forms “a,” “an” and “the” include plural references unless the context clearly dictates otherwise. The present disclosure also contemplates other embodiments “comprising,” “consisting of” and “consisting essentially of,” the embodiments or elements presented herein, whether explicitly set forth or not.
The conjunctive term “or” includes any and all combinations of one or more listed elements associated by the conjunctive term. For example, the phrase “an apparatus comprising A or B” may refer to an apparatus including A where B is not present, an apparatus including B where A is not present, or an apparatus where both A and B are present. The phrases “at least one of A, B, . . . and N” or “at least one of A, B, . . . N, or combinations thereof” are defined in the broadest sense to mean one or more elements selected from the group comprising A, B, . . . and N, that is to say, any combination of one or more of the elements A, B, . . . or N including any one element alone or in combination with one or more of the other elements which may also include, in combination, additional elements not listed.
The modifier “about” used in connection with a quantity is inclusive of the stated value and has the meaning dictated by the context (for example, it includes at least the degree of error associated with the measurement of the particular quantity). The modifier “about” should also be considered as disclosing the range defined by the absolute values of the two endpoints. For example, the expression “from about 2 to about 4” also discloses the range “from 2 to 4.” The term “about” may refer to plus or minus 10% of the indicated number. For example, “about 10%” may indicate a range of 9% to 11%, and “about 1” may mean from 0.9-1.1. Other meanings of “about” may be apparent from the context, such as rounding off, so, for example “about 1” may also mean from 0.5 to 1.4.
The term “wt. %” means weight percent.
The term “w/w” means weight per weight.
For the purposes of the present invention, the term “biodegradable” refers to polymers that dissolve or degrade in vivo within a period of time that is acceptable in a particular therapeutic situation. Such dissolved or degraded product may include a smaller chemical species. Degradation can result, for example, by enzymatic, chemical and/or physical processes. Biodegradation takes typically less than five years and usually less than one year after exposure to a physiological pH and temperature, such as a pH ranging from 6 to 9 and a temperature ranging from 22° C. to 40° C.
For the purposes of the present invention, the term “radiopacity” means being visualized by x-ray.
For the purposes of the present invention, the term “tensile strength” refers to the maximum stress of a material to break under tension.
For the purposes of the present invention, the term “e-modulus” refers to the modulus of elasticity of the material under tension. It is the slope of the stress-strain curve of the material in the elastic region.
For the purposes of the present invention, the term “e-break” refers to the elongation at break. It is the ratio between the increase in length of a material subject to an axial load necessary for breaking the specimen and the initial length of the material.
For the purposes of the present invention, the term “injection molding” refers to the manufacturing method of producing parts where the melted plastic material is injected into a mold.
For the purposes of the present invention, the term “compression molding” refers to the manufacturing method of producing parts by placing the plastic material, sometimes preheated, in a mold, which is then subject to heat and pressure.
For the purposes of the present invention, the term “drawn fiber process” refers to the common practice of making polymeric fibers, where the fibers are melted, routed through a die, cooled off, and subsequently pulled by controlling their temperature and rate of pull to produce strong fibers with high molecular orientation.
For the purposes of the present invention, the term “thermoforming” refers to a manufacturing process where a plastic sheet is heated to soften the material to form it over a mold.
For the purposes of the present invention, the term “computer numerical control machining” refers to the common practice of forming a component or part from a stock shape by removing material using machining tools such as mills, drills, lathes where the movement of the tool is automated using a computer.
The present invention is directed to fiber reinforced compositions and fabrication methods suitable for medical implantable devices having a resorbable matrix phase and one or more reinforcing phases. In one embodiment, the fiber reinforced compositions contain additives incorporated into the matrix phase. In one embodiment, the fiber reinforced compositions contain additives incorporated into the fiber phase. In one embodiment, the fiber reinforced compositions contain additives in both the matrix phase and the fiber phase.
The present invention is directed to compositions of materials which are suitable for load bearing applications. In one embodiment, fibers are incorporated into a resorbable polymer matrix through an impregnation process. In one embodiment, the impregnation process requires a polymer with low viscosity and with a melting temperature sufficiently lower than that of the fibers. This allows the fibers to be fully wetted by the polymer without affecting their strength or melting them. Materials ready to be post processed using molding methods, such as injection or compression molding are often referred to as “pre-pegs” alluding to the pre-impregnation process. In one embodiment, pre-impregnated forms can be pellets suitable for injection molding or compression molding. In one embodiment, pre-impregnated forms can be sheets that can be compression molded or thermoformed. In one embodiment, pre-impregnated forms can be rods and bars which can be machined.
Impregnated or wetted defines a measure of the fibers to be thoroughly coated by the matrix polymer. When there is good impregnation most of the fibers are coated by the polymer, which allows them to disperse better when injection molding. The result of this is an injection molded article that has uniform properties and better strength. In contrast, when there is bad impregnation the matrix polymer forms a “jacket” around the fibers without thoroughly wetting them. When these pre-pegs are injection molded into fibers, they don't disperse and instead tend to agglomerate.
In one embodiment, the present invention uses a method called long fiber resorbable thermoplastic (LFRT). LFRT is a modification of the common long fiber thermoplastic (LFT) processing method. During LFT processing the matrix material is melted using a single or twin screw into a fiber impregnation die. The die pools the melted polymer into a vat and fiber is forced to go through the vat via a series of high pressure zones. Although the method works extremely well for some polymers especially resins and non-degradable thermoplastics, it presents serious challenges when processing materials highly susceptible to thermal degradation such as PLA in that the melted pool of polymer will degrade the material much more and with more variability. In contrast, the LFRT method relies on continuous flow of matrix material, and does not use a pool of material for the impregnation process. The polymer is melted and directed through a die, where it meets the fiber. The two phases are combined by pulling the fibers with the polymer through a flat portion of the die with rollers or high-pressure zones, which force the melt into the fiber. This way the polymer material is continually flowing through the die and no pooling occurs. One of the advantages of using this method is its versatility to produce fiber reinforced composites, which can be tape, strand or ribbons with continuous fibers suitable for compression molding sheets. If pelletized, upon injection molding the parts can be short or long fiber thermoplastics depending on the length of cut of the pellet.
The present invention uses polymers with low melting temperature, which include but are not limited to PCL, PDO, PTMC and their copolymers with polylactides and polyglycolides and blends thereof at low molecular weight coupled with fibers with high melting points. The use of these materials allows for improved flowability at lower temperatures, which in turn improves the impregnation and injection moldability. Good impregnation requires a matrix polymer with a low enough viscosity, which can be adjusted by controlling the matrix polymer temperature. However, the matrix polymer processing temperature cannot be high enough as to melt the reinforcing fiber. Empirical data suggests that the processing temperature of the matrix polymer must not exceed the glass transition temperature of the reinforcing fibers plus 132° C. (Tg+132° C.).
T
p
<T
g(Fiber)+132° C.
Different polymers have different flow properties and characteristics depending on their class (thermoplastics, thermosets, and elastomers), degree of crystallinity, molecular weight, moisture, etc., and the processing temperature described above will be largely influenced by those factors. Multiple methods can be used to define the processing temperature such as rheology, melt flow analysis, or DSC, which gives the melting temperature of the polymer (assuming it has one).
In one of the examples presented, the processing temperature is defined as the minimum temperature necessary such that the matrix polymer will have a complex viscosity of no higher than 12,000 Pa*s as measured by parallel plate rheology. This temperature would provide low enough viscosity such that the matrix polymer would flow through the LFRT extrusion head. Using this definition for the processing temperature yields a selection criterion for determining the processability of matrix/fiber combinations as follows:
T(Matrix Polymer)@12 kPa·s<Tg(Fiber)+132° C.
Table 1 depicted below provides examples of fiber matrix compositions applying the relationship stated above. The complex viscosity of the base polymer is obtained via rheology methods.
With the processing methods described above, a wide array of fibers can be impregnated with a resorbable matrix polymer, co-polymer, or blend. Currently in the field, synthetic PLA and poly(lactide-co-glycolide) PLGA resorbable fibers is utilized and more recently bioglass fibers. However, fibers from other biomaterials can be used as well. In one embodiment, fibers are poly(vinyl alcohol) (PVA). PVA is highly biocompatible and widely used in pharmaceutical and tissue engineering applications. Fibers with very high tenacity can be manufactured from PVA and incorporated into a resorbable matrix.
In one embodiment, PVA is fully hydrolyzed and therefore non-soluble or partially hydrolyzed with varying degrees of solubility. In one embodiment, fibers are non-resorbable materials, which include but are not limited to polyaryletherketone (PAEK), poly(ethylene terephthalate) (PET), and poly(butylene terephthalate) (PBT). The inclusion of these fiber materials is particularly useful in the case of patients suffering from osteoporosis, where bone loss is expected and having bone scaffolds with a degradable and non-degradable component creates a permanent fiber scaffold to promote continued bone growth long after the resorbable portion has gone.
In one embodiment, fibers are natural fibers, which include but are not limited to silk, collagen, keratin, and chitosan. These fibers depend more on enzymatic degradation and some are useful for the bone healing process such as collagen. In one embodiment, fibers are metallic fibers. Metallic fibers include but are not limited to magnesium, zinc, iron, or any other metal or metal alloys which are well tolerated by the body. Unlike polymers which degrade when implanted these metals undergo surface corrosion as their method for absorption.
Some of the embodiments presented in this invention use additives to provide a secondary effect. In one embodiment, the additives are added to the matrix. In one embodiment, the additives are added to the fibers. In one embodiment, the additives are added to both the matrix and the fibers.
In one embodiment, the additives are inorganic additives, which include but are not limited to beta-tricalcium phosphate (β-TCP), hydroxyapatite (HA), and biphasic calcium phosphate (BCP). Inorganic additives can provide an osteoconductive effect.
The inclusion of additives to the matrix has been covered in U.S. Pat. No. 4,743,257 along with two fiber phases, one synthetic and one bioactive or bioceramics. The incorporation of the synthetic fibers in that work was to promote bonding between the bioceramics fiber phase and the matrix phase. Unlike the prior art, the supporting examples for this invention demonstrate that sub-micron sized particles of beta-tri-calcium phosphate improve the interfacial bonding between the matrix and the fiber by improving the surface roughness of such interface, which results in an increase in tensile strength of the composite material over the same material without the inorganic additive. Furthermore, the supporting examples demonstrate this strengthening effect when the additive is added to the matrix as well as to the fiber, that is synthetic drawn fibers made from a resorbable polymer composite containing inorganic sub-micron sized particles.
The following examples are put forth to provide those of ordinary skill in the art with a complete disclosure and description of how the compositions, articles, and/or methods claimed herein are made and evaluated and are intended to be purely exemplary of the invention and are not intended to limit the scope of what the inventors regard as their invention. Efforts have been made to ensure accuracy with respect to numbers (e.g., amounts, temperature, etc.), but some errors and deviations should be accounted for. Unless indicated otherwise, parts are parts by weight, temperature is in ° C. or is at ambient temperature, and pressure is at or near atmospheric. All tensile specimens in this disclosure follow ISO 527 testing protocol “Plastics—Determination of tensile properties” under the following conditions:
1. Test speed from 0% to 0.3% strain: 0.2 mm/min
2. Test speed above 0.3% strain: 5 mm/min
3. Determination of modulus of elasticity strain range: 0.05% to 0.025%
4. Injection Molded Specimen Type: ISO 527-2 5A
5. Compression Molded Specimen Type: ISO 527-2 1BA
PCL material (RESOMERO C209 commercially available from Evonik) was melted on a twin-screw extruder (commercially available from Thermo Scientific) and combined with a bundle of aligned continuous synthetic fibers introduced to the extrusion melt via a Long Fiber Thermoplastic Extrusion custom made die. One experiment used commercially available PVA fibers with a denier of 1.8 dpf and a subsequent experiment used commercially available PGA fibers with a denier of 2.5 dpf. Each of the extrudates, with PGA and PVA fibers, had 40 wt % incorporated fibers. The material was cut to 14 mm length and injection molded to ISO 527-2 5A specimens. Injection molding temperature was 120° C. The resulting specimens were aged for two days at room temperature. Specimens were also manufactured this same way using only PCL material with no reinforcing fibers. Table 2 depicts the tensile strength, e-modulus, and e-break data of the specimens. Modulus of elasticity for the unreinforced specimens was 631 MPa compared to the PVA reinforced specimens' value of 5939 MPa and 3087 MPa for PGA fiber reinforcement. Tensile Strength was 22.1 MPa for the PCL specimens, 79.7 MPa for PVA and 90.7 MPa for PGA reinforced specimens. Elongation at break was 277%, 11.3% and 13.8 for PCL, PCL with 40 wt % PVA fibers and PCL with 40 wt % PGA fibers respectively.
The same setup, LFRT process and PGA fiber as EXAMPLE 1 was used, and the matrix material was changed to a poly(l-lactide-co-glycolide) (PLLA-co-PGA) ternary blend including 30 wt % poly(L-lactide-co-trimethylene carbonate) (PLLA-co-TMC) and 15 wt % poly(L-lactide-co-caprolactone) PLLA-co-PCL. Processing of these materials was not feasible due to the high viscosity of the matrix material. Processing at low temperature resulted in poorly impregnated fibers where the matrix polymer simply surrounded the fiber bundle without wetting it. Processing at high temperature resulted in the fiber bundle breaking during processing due to high temperature. Following selection criteria previously shown it can be easily corroborated that such combination would not be suitable for this process. The glass transition temperature of PGA is 38° C. and adding 132° C. to it gives us a maximum processing temperature of 170° C. The rheology results in
Compositions of fiber reinforced PCL (RESOMERO C209 commercially available from Evonik) were made by melting the matrix polymer using a twin-screw extruder and incorporating aligned continuous fibers into the polymer by means of a long fiber resorbable thermoplastic extrusion die. The inorganic additive was β-TCP with a particle size distribution D50 of 500 to 700 nanometers. The fibers used were PVA and PGA with deniers of 1.8 and 2.5 denier per filament (dpf) respectively.
Tensile specimens were made from these compositions using injection and compression molding methods. Injection molded specimens used ISO 527-2 5A specimen geometry, whereas compression molded specimens used ISO 527-2 1BA specimen geometry. The resulting specimens were aged for two days at room temperature. Table 3 depicts the tensile strength, e-modulus, and e-break data of the specimens.
Compositions of PGA fiber reinforced PCL (RESOMERO C209 commercially available from Evonik) with β-TCP were made using the same methods described in example 3. The PGA fibers had a denier of 2.1 dpf and the β-TCP had a particle size distribution D50 of 500 to 700 nanometers. Tensile specimens were made from these compositions using injection and compression molding methods. Injection molded specimens used ISO 527-2 5A specimen geometry, whereas compression molded specimens used ISO 527-2 1BA specimen geometry. The resulting specimens were aged for two days at room temperature. Table 3 depicts the tensile strength, e-modulus, and e-break data of the specimens.
Monofilament fibers with a diameter of 30 microns were made out compositions 4A and 4B shown in Table 5.
Fiber Compositions 4A and 4B were each separately combined with monofilament fibers of PDO (RESOMERO X206S) to a weight ratio of 70:30 (PDO:Fiber) and mixed using an air mixer. The mixtures were then fed into an injection molding machine and injection molded into a tensile specimen (ISO 527-2 5A) The specimens where molded at a temperature of 120° C. The resulting specimens were aged for two days at room temperature. Table 6 depicts the tensile strength, e-modulus, and e-break data of the specimens. The tensile strength of the fiber reinforced specimens with added inorganic ceramic inside the fiber exhibited an increase of 8.5% over the specimens without the additive (57.4 MPa to 62.3 MPa).
Item 1 is a composition comprising:
Item 2 is the composition of item 1, wherein the resorbable matrix comprises a poly(lactic acid), poly(glycolic acid), poly(ε-caprolactone), poly(trimethylene carbonate), poly(dioxanone), poly (ethylene oxide), isomers, copolymers or blends thereof.
Item 3 is the composition of any of items 1 to 2, wherein the reinforcing fiber(s) is made from one or more materials, wherein the materials comprise resorbable materials, non-resorbable materials, natural materials, or metallic materials.
Item 4 is the composition of any of items 1 to 3, wherein the resorbable materials comprise poly(lactic acid), poly(glycolic acid), poly(lactide-co-glycolide), poly (lactide-co-ethylene glycol), poly (lactide-co-caprolactone), poly(lactide-co-trimethylene carbonate), poly(lactide-co-dioxanone), poly (glycolide-co-caprolactone), poly(glycolide-co-trimethylene carbonate), poly(glycolide-co-dioxanone), isomers, or blends thereof.
Item 5 is the composition of any of items 1 to 4, wherein the non-resorbable materials comprise poly(ethylene terephthalate), poly(butylene terephthalate), poly(arylene ether ketone), poly(vinyl alcohol), carbon fiber, or glass fiber.
Item 6 is the composition of any of items 1 to 5, wherein the natural materials comprise silk, collagen, keratin, chitin, chitosan, or elastin.
Item 7 is the composition of any of items 1 to 6, wherein the metallic materials comprise magnesium, iron, zinc, or alloys thereof.
Item 8 is the composition of any of items 1 to 7, wherein the additives comprise:
Item 9 is the composition of any of items 1 to 8, wherein the inorganic additives comprise apatites or calcium phosphates.
Item 10 is the composition of any of items 1 to 9, wherein the apatites comprise hydroxyapatites (HA).
Item 11 is the composition of any of items 1 to 10, wherein the calcium phosphates comprise β-tricalcium phosphate (β-TCP), or biphasic calcium phosphate (BCP).
Item 12 is the composition of any of items 1 to 11, wherein the dopant comprises Fluorine (F), Sulphur (S), Boron (B), Strontium (Sr), Magnesium (Mg), Silver (Ag), Barium (Ba), Zinc (Zn), Sodium (Na), Potassium (K), Aluminium (Al), Titanium (Ti), Silicon (Si), or Copper (Cu).
Item 13 is the composition of any of items 1 to 12, wherein the radiopaque materials comprise barium sulfate, bismuth compounds, tantalum, or tungsten.
Item 14 is the composition of any of items 1 to 13, wherein the coloring agents comprise monosodium salt of 2-[(9,10-dihydro-4-hydroxy-9,10-dioxo-1-anthracenyl) amino]-5-methyl-benzenesulfonic acid (D&C Violet NO. 2), D&C Blue NO. 6, or D&C Green NO. 6.
Item 15 is the composition of any of items 1 to 14, wherein the biologics comprise antibacterial agent, proteins, peptides, growth factors, or antibiotics.
Item 16 is the composition of any of items 1 to 15, wherein the reinforcing phase comprises multifilament or monofilament fibers which can be aligned continuous, chopped, woven or braided into strips, ribbons, strands, and other forms.
Item 17 is the compositions of any of items 1 to 16, wherein the inclusion of an inorganic additive into the matrix, the fiber or both, results in increased tensile strength compared to compositions without an inorganic additive.
Item 18 is the composition of any of items 1 to 17, wherein the average particle size of the additive is less than 50 microns, preferably less than 1 micron.
Item 19 is the composition of any of items 1 to 18, wherein the matrix phase polymer material is between 30 wt % to 90 wt %, the reinforcing phase fibers is between 10 wt % to 70 wt % by weight of the composition, and the additive(s) is between 1 wt % to 30 wt % by weight of the composition.
Item 20 is a long fiber resorbable thermoplastic process of making the composition of any of items 1 to 19, wherein the process comprises of impregnating the materials in the reinforcing phase into the resorbable matrix phase by:
Item 21 is an injection moldable fiber reinforced material comprising the composition of any of items 1 to 19, wherein the resorbable matrix and the reinforcing fiber(s) comprises polymeric materials; wherein the polymeric materials are being selected in such a way that the processing temperature of the matrix polymer is less than the glass transition temperature of the fiber(s) plus 132° C.
Item 22 is the injection moldable fiber reinforced material of item 21, wherein the processing temperature of the matrix polymer has a minimum temperature that would yield a complex viscosity of 12 kPa*s or less as determined by rheology.
Item 23 is the injection moldable fiber reinforced material of any of items 21 to 22, wherein the resorbable matrix and the reinforcing fiber(s) comprises polymeric materials; wherein the polymeric materials are being selected in such a way that the difference between the melting points of the reinforcing phase polymer and the resorbable matrix phase polymer is not less than 50° C.
Item 24 is the injection moldable fiber reinforced material of any of items 21 to 23, wherein the resorbable matrix phase polymer or the reinforcing phase polymer are amorphous, wherein the melting point temperature is replaced by the melt flow temperature of the polymer that corresponds to a melt flow index of 10 g/10 min.
Item 25 is the composition of any of items 1 to 19, wherein the resorbable matrix has an inherent viscosity of not more than 2 dL/g.
Item 26 is the compositions of any of items 1 to 19 and 25, wherein the length of the fibers is no more than 20 mm; and wherein the diameter of the fibers is no more than 15 microns.
Item 27 is the composition of any of items 1 to 19 and 25 to 26, wherein the composition is formed into an injection moldable specimen; and wherein the tensile strength of the injection moldable specimen is more than 2 folds of the matrix material.
Item 28 is the process of item 20, wherein the process further comprises pelletizing the material for injection molding.
Item 29 is the composition of any of items 1 to 19, and 25 to 27, wherein composition is formed into a compression moldable specimen; and wherein the compression molded specimens have a tensile strength of no less than 4 times of the matrix materials.
Item 30 is the composition of any of items 1 to 19, 25 to 27 and 29, wherein the composition is formed into a compression moldable specimen, and wherein the tensile and the flexural strength of the compression molded specimens further increases when inorganic additive is included as compared with a similar composition without the inorganic additive.
Item 31 is the compositions of any of items 1 to 19, 25 to 27, and 29 to 30, wherein the composition is formed into an injection moldable specimen, and wherein the tensile and the flexural strength of the injection molded specimens further increases when inorganic additive is included as compared with a similar composition without the inorganic additive.
Item 32 is the composition of any of items 1 to 19, 25 to 27, and 29 to 31, wherein the average particle size of the bioceramic additive is less than 50 microns, and preferably less than 1 micron.
Item 33 is the composition of any of items 1 to 19, 25 to 27, and 29 to 32, wherein the concentration of additive is 1 to 30% wt % by weight of the composition, and preferably 1 to 5% wt % by weight of the composition.
Item 34 is the composition of any of items 1 to 19, 25 to 27, and 29 to 33, wherein the composition is formed into a semi-finished or finished medical device article.
Item 35 is the composition of any of items 1 to 19, 25 to 27, and 29 to 34, wherein the composition is processed into pellets, filaments, rods, or sheets.
Item 36 is the composition of any of items 1 to 19, 25 to 27, and 29 to 35, wherein the composition is processed by drawing into tubes or films.
Item 37 is the composition of any of items 1 to 19, 25 to 27, and 29 to 36, wherein the composition is used to form an article, and wherein the article is annealed.
Item 38 is the composition of any of items 1 to 19, 25 to 27, and 29 to 37, wherein the pellets are injection molded or compression molded into articles.
Item 39 is the composition of any of items 1 to 19, 25 to 27, and 29 to 38, wherein the sheets are formed into articles by means of thermoforming.
Item 40 is the composition of any of items 1 to 19, 25 to 27, and 29 to 39, wherein the sheets and rods are milled into articles using computer numerical control machining.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2020/081407 | 11/9/2020 | WO |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 16685786 | Nov 2019 | US |
| Child | 17777002 | US |
