Patent Grant
9040093
There has been a need for bone graft materials with improved osteogenic properties, i.e., bone graft materials that are capable of promoting bone formation. Ideally, the bone graft materials would serve as an osteoconductive scaffold that promotes the in-growth of new bone. As bone growth is promoted and increases, the bone graft material resorbs and is eventually replaced with new bone.
Chitin, the main constituent of the crustacean shells, is a naturally occurring linear polysaccharide composed of randomly distributed b-(1-4)-linked D-glucosamine (deacetylated unit) and N-acteyl-D-glucosamine (acetylated unit). Chitosan is synthetically produced by near complete deacetylation of the N-acteyl-D-glucosamine unit of chitin rendering it soluble in most acids. Chitin has been found to have an acceleratory effect on the wound healing process by increasing the rate of blood clotting at the wound site. Various forms of chitin including fibers, non-woven mats, sponges, and films have been used in wound healing products and show an increase in wound healing by over 30%. Chitosan has also been demonstrated to exhibit antimicrobial properties on various types of microorganisms.
However, there is a need for a bone graft material comprising chitosan which exhibits osteoconductive, hemostatic, and antibacterial properties without altering the structural integrity and/or handling characteristics of the bone graft material.
Described herein are bone graft materials with improved osteoconductive properties that also exhibit improved hemostasis as well as reducing the risk of infection at the surgical site. In one embodiment the bone graft material comprises calcium phosphate and a form of chitin, for example, chitosan. It has been discovered that chitin acts as an osteoconductive agent, increasing the rate of new calcium phosphate growth which is indicative of new bone formation. Without being bound by a particular theory, it is believed that bone and blood cell adhesion to the bone graft material is affected by the charge state of the chitin. A negative charge on the bone and blood cells causes them to adhere more readily to a positive charge on the chitin. In addition, the addition of chitin to the bone graft material can add this positive charge to the bone graft material without effecting the porosity of the material, allowing bone and blood cells to infiltrate. Furthermore, it has been discovered that chitin can be incorporated into the scaffold of bone graft materials without altering the structure (e.g., porosity) of the bone graft material while retaining optimal handling characteristics (e.g., flexibility, moldability).
In one embodiment, the bone graft material contains calcium phosphate and chitosan wherein the weight ratio of chitosan to calcium phosphate is about 20:80 to about 80:20.
In another embodiment the bone graft material further comprises collagen wherein the weight ratio of collagen is about 10% to about 30% of the total bone graft material composition.
The bone graft materials described herein can be used for increasing osteogenesis by placing in the bone, at a site to be restored or repaired, the biocompatible bone graft materials described herein. While the bone graft materials comprising chitosan exhibit increased osteogenic properties they also exhibit increased hemostasis as well as reduce the risk of infection at the surgical site.
Various methods for manufacturing the bone graft materials described herein are also contemplated. In one embodiment the method for preparing a biocompatible bone graft material comprising calcium phosphate and chitin includes making a solution of acid in water; adding chitosan to the acid solution to create a slurry; incubating the slurry; optionally, adjusting the pH of the slurry with a base to a neutral pH; adding calcium phosphate and optionally collagen to the slurry to create a mixture; incubating the mixture; drying the mixture; and, optionally washing the dried mixture to form a biocompatible bone graft material comprising calcium phosphate, chitosan, and optional collagen.
In one embodiment, the concentration of acid in water is about 1% to about 20% volume by volume. In another embodiment, the concentration of chitosan when added to the acid solution is about 0.5% to about 20% weight by volume. In yet another embodiment, the mixture of calcium phosphate and chitosan-acid slurry contains a ratio of calcium phosphate to chitosan slurry of about 0.01 grams calcium phosphate per about 1 ml of chitosan slurry to about 1 grams calcium phosphate per about 1 ml of chitosan slurry.
For embodiments in which the bone graft material also comprises collagen, the collagen can be added along with calcium phosphate to the chitosan-acid slurry or can be added after the calcium phosphate and chitosan mixture is dried.
The invention will be described in more detail below.
While the specification concludes with the claims particularly pointing out and distinctly claiming the invention, it is believed that the invention described herein will be better understood from the following description. All temperatures are in degrees Celsius unless specified otherwise. The invention described herein can comprise (open ended) or consist essentially of the components of the invention described herein as well as other ingredients or elements described herein. As used herein, “comprising” means the elements recited, or their equivalent in structure or function, plus any other element or elements which are not recited. The terms “having,” “including,” and “comprised of” are also to be construed as open ended unless the context suggests otherwise. As used herein, “consisting essentially of” means that the invention may include ingredients in addition to those recited in the claim, but only if the additional ingredients do not materially alter the basic and novel characteristics of the claimed invention. Generally, such additives may not be present at all or only in trace amounts. However, it may be possible to include up to about 10% by weight of materials that could materially alter the basic and novel characteristics of the invention as long as the utility of the compounds (as opposed to the degree of utility) is maintained. All ranges recited herein include the endpoints, including those that recite a range “between” two values. Terms such as “about,” “generally,” “substantially,” and the like are to be construed as modifying a term or value such that it is not an absolute. Such terms will be defined by the circumstances and the terms that they modify as those terms are understood by those of skill in the art. This includes, at very least, the degree of expected experimental error, technique error and instrument error for a given technique used to measure a value.
It should be further understood that a description in range format is merely for convenience and brevity and should not be construed as an inflexible limitation on the scope of the invention. Accordingly, the description of a range should be considered to have specifically disclosed all the possible sub-ranges as well as individual numerical values within that range. For example, description of a range such as from 1 to 6 should be considered to have specifically disclosed sub-ranges such as from 1 to 3, from 1 to 4, from 1 to 5, from 2 to 4, from 2 to 6, from 3 to 6 etc., as well as individual numbers within that range, for example, 1, 2, 2.3, 3, 4, 5, 5.7 and 6. This applies regardless of the breadth of the range.
Bone Graft Materials Containing Calcium Phosphate and Chitosan
Described herein are biocompatible bone graft materials for use in restoring or repairing a defect at a bony site that exhibits increased osteogenic properties, increased hemostasis, and reduced the risk of infection at the surgical site. In one embodiment, the biocompatible bone graft materials described herein comprise a calcium salt and a form of chitin.
It has been discovered that chitin acts as an osteoconductive agent, increasing the rate of new calcium phosphate growth which is indicative of new bone formation. Without being bound by a particular theory, it is believed that bone and blood cell adhesion to the bone graft material is affected by the charge state of the chitin. A negative charge on the bone and blood cells causes them to adhere more readily to a positive charge on the chitin. In addition, the addition of chitin to the bone graft material can add this positive charge to the bone graft material without effecting the porosity of the material, allowing bone and blood cells to infiltrate. In addition, the bone graft materials described herein containing chitin also exhibit increased hemostasis as well as antimicrobial properties.
Various forms of chitin are contemplated and include, for example, deacetylated chitin, e.g., chitosan, as well as other linear polysaccharides. Also contemplated are alpha, beta, and gamma forms of chitin. However, for the sake of brevity, “chitosan” includes any form of chitin known to those skilled in the art.
Various calcium salts are contemplated and include, for example, calcium phosphates such as tricalcium phosphate, β-tricalcium phosphate (β-TCP), α-tricalcium phosphate (α-TCP), and apatites such as hydroxyapatite. However, for the sake of brevity, “calcium phosphate” includes any calcium salt known to those skilled in the art. The preparation of various forms of calcium phosphate for use in the present invention is described in U.S. Pat. Nos. 6,383,519 and 6,521,246, assigned to the assignee of the present invention and incorporated herein by references in their entireties. An exemplary calcium phosphate product is Vitoss® Bone Graft Substitute (Orthovita, Inc., Malvern, Pa.).
In one embodiment the calcium phosphate is β-TCP. In typical embodiments the calcium phosphate is porous. In another embodiment, the calcium phosphate contains micro-, meso-, and macroporosity. In yet another embodiment the porosity of the calcium phosphate is interconnected. Macroporosity is characterized by pore diameters greater than about 100 μm and, in some embodiments, up to about 1000 μm to 2000 μm. Mesoporosity is characterized by pore diameters between about 100 μm and 10 μm, while microporosity occurs when pores have diameters below about 10 μm. It is preferred that macro-, meso-, and microporosity occur simultaneously and are interconnected in products of the invention. It is not necessary to quantify each type of porosity to a high degree. Rather, persons skilled in the art can easily determine whether a material has each type of porosity through examination, such as through the preferred methods of mercury intrusion porosimetry, helium pycnometry and scanning electron microscopy. While it is certainly true that more than one or a few pores within the requisite size range are needed in order to characterize a sample as having a substantial degree of that particular form of porosity, no specific number or percentage is called for. Rather, a qualitative evaluation by persons skilled in the art shall be used to determine macro-, meso-, and microporosity.
In one embodiment, the calcium phosphate is in the form of particles or morsels and may contain a porous structure as described herein.
It will be appreciated that in some embodiments of materials prepared in accordance with this invention the overall porosity will be high. This characteristic is measured by pore volume, expressed as a percentage. Zero percent pore volume refers to a fully dense material, which, perforce, has no pores at all. One hundred percent pore volume cannot meaningfully exist since the same would refer to “all pores” or air. Persons skilled in the art understand the concept of pore volume, however and can easily calculate and apply it. For example, pore volume may be determined in accordance with Kingery, W. D., Introduction to Ceramics, Wiley Series on the Science and Technology of Materials, 1st Ed., Hollowman, J. H., et al. (Eds.), Wiley & Sons, 1960, p. 409-417, who provides a formula for determination of porosity. Expressing porosity as a percentage yields pore volume. The formula is: Pore Volume=(1−fp) 100%, where fp is fraction of theoretical density achieved.
Porosity can be measured by Helium Pycnometry. This procedure determines the density and true volume of a sample by measuring the pressure change of helium in a calibrated volume. A sample of known weight and dimensions is placed in the pycnometer, which determines density and volume. From the sample's mass, the pycnometer determines true density and volume. From measured dimensions, apparent density and volume can be determined. Porosity of the sample is then calculated using (apparent volume-measured volume)/apparent volume. Porosity and pore size distribution may also be measured by mercury intrusion porosimetry.
Pore volumes in excess of about 30% may be achieved in accordance with this invention while materials having pore volumes in excess of 50% or 60% may also be routinely attainable. Some embodiments of the invention may have pore volumes of at least about 70%. Some embodiments that may be preferred have pore volumes in excess of about 75%, with 80% being still more preferred. Pore volumes greater than about 90% are possible as are volumes greater than about 92%. In some preferred cases, such high pore volumes are attained while also attaining the presence of macro- meso-, and microporosity as well as physical stability of the materials produced. It is believed to be a great advantage to prepare graft materials having macro-, meso-, and microporosity simultaneously with high pore volumes that also retain some compression resistance and flexibility when wetted.
In one embodiment, the bone graft material comprises porous calcium phosphate morsels at a size greater than about 0.25 mm. The morsels of calcium phosphate may be, for example, about 1-2 mm in size for some embodiments or about 0.25 mm to about 1 mm or to about 2 mm for other embodiments of the present invention. For flowable compositions, it will be appreciated that the morsel size will be selected considering the desired delivery apparatus. For example, for delivery of a flowable composition using a standard syringe, it will be necessary to select a morsel size that fits through the syringe orifice.
Due to the high porosity and broad pore size distribution (1 μm to 1000 μm) of the present invention graft, the implant is not only able to wick/soak/imbibe materials very quickly, but is also capable of retaining them. A variety of fluids could be used with the present invention including blood, bone marrow aspirate, saline, antibiotics and proteins such as bone morphogenetic proteins (BMPs). Materials of the present invention can also be imbibed with cells (e.g., fibroblasts, mesenchymal, stromal, marrow and stem cells), platelet rich plasma, other biological fluids, and any combination of the above. Bone grafts of the present invention actually hold, maintain, and/or retain fluids once they are imbibed, allowing for contained, localized delivery of imbibed fluids. This capability has utility in cell-seeding, drug delivery, and delivery of biologic molecules as well as in the application of bone tissue engineering, orthopaedics, and carriers of pharmaceuticals.
Wettability determines the amount of fluid taken up by sample material and if the material absorbs an appropriate amount of fluid within a specified time. Pieces of the material are randomly selected, weighed, and placed in a container of fluid for 120 seconds. If the samples adequately take up fluid, they are then weighed again to determine the percentage of mass increase from fluid absorption. Some embodiments exhibit a wettability wherein bone graft material becomes fully saturated within 120 seconds with at least a 100% mass increase. In some embodiments, the graft material experiences a 150% mass increase and yet, in others, an approximate 200%-300% mass increase. Fluids that may be used in the present invention may be bone marrow aspirate, blood, saline, antibiotics and proteins such as bone morphogenetic proteins (BMPs) and the like.
It is preferred that flexible grafts of the present invention will be able to wick and hold fluids, even under compression. It is preferred that moldable embodiments will be able to wick and hold fluids, even in a wet environment. For example, if a wetted, flexible graft is placed on mesh suspended above a weigh boat and is challenged with a 500 g weight, it is preferred that the graft maintain a mass of fluid at least about 95% of the mass of the graft or about equivalent to the mass of the graft. If a wetted, moldable graft of the invention is placed in fluid, it is preferred that the graft maintains as a continuous object and does not swell substantially larger in size than its original dimensions. In some instances, the graft does not swell in size greater than about 50% more than its original dimensions, by qualititative assessment. If a wetted, moldable graft of the invention is compressed, it is preferred that the graft maintain a mass of fluid at least about 85% of the mass of the graft or about equivalent to the mass of the graft. Bone graft materials of the present invention have osteoconductive and osteostimulatory properties. In certain embodiments, the addition of bioactive glass in the present invention enhances the ability of the product to foster bone growth. The bone graft materials of the present invention may also have osteoinductive properties.
In one embodiment, the bone graft material comprises calcium phosphate and chitosan. The weight ratio of chitosan to calcium phosphate is not limited. In one embodiment, the weight ratio of chitosan to calcium phosphate is about 20:80 to about 80:20. In another embodiment, the weight ratio of chitosan to calcium phosphate is about 40:60 to about 70:30. In yet another embodiment, the weight ratio of chitosan to calcium phosphate is about 55:45 to about 67:33.
In one embodiment, the bone graft material comprises calcium phosphate and chitosan but does not contain collagen. Chitin, including chitosan, increases the viscosity of the calcium phosphate upon mixing without the need for adding a viscosity modifying agent, such as collagen. Unlike typical bone graft materials in the art that require the addition of collagen, gelatin, or other similar polymers to create a putty-like or moldable bone graft, the bone graft materials described herein containing calcium phosphate and chitosan without collagen exhibit a putty-like substance that is moldable, moderately flexible, and easily compressed.
It is also contemplated that the various forms of chitin described herein can be used to coat or can be combined with other materials known in the art for preparing bone graft materials or bone implants. Such materials include, for example, collagen, metals including titanium, stainless steel and cobalt, polymers including polymethylmethacrylate (PMMA), and other similar hardenable bone cement and bone augmentation materials, including those sold under the trademark Cortoss® (Orthovita, Malvern, Pa.).
In one embodiment, the bone graft material contains calcium phosphate, chitosan, and collagen. Collagen is added in order to provide a bone graft material with a more cohesive mass, such as, for example, a sponge-like material. In one embodiment the biocompatible bone graft material comprises a homogenous blend of calcium phosphate and collagen. In another embodiment the bone graft material comprises collagen wherein the weight ratio collagen is about 10% to about 30% of the total bone graft material composition. In yet another embodiment the bone graft material comprises collagen wherein the weight ratio collagen is about 15% to about 25% of the total bone graft material composition.
Collagens suitable for use in the present invention may consist of non-crosslinked collagen pellet, lyophilized non-cross-linked collagen, and cross-linked collagen. Suitable collagens are described, for example, in U.S. Pat. No. 7,189,263, which is herein incorporated by reference in its entirety. Some embodiments of the present invention contain collagen that comprises up to 100% Type I collagen. In other embodiments, the collagens used may be predominantly, or up to about 90%, of Type I collagen with up to about 5% of Type III collagen or up to about 5% of other types of collagen. Suitable Type I collagens include native fibrous insoluble human, bovine, porcine, or synthetic collagen, soluble collagen, reconstituted collagen, and microfibrillar forms of collagen as described, for example, in U.S. Pat. Nos. 6,096,309 and 6,280,727, which are herein incorporated by reference in its entirety. The various types of collagens can be used alone or in combination.
In one embodiment the collagen is cross-linked with one selected from the group consisting of N-(3-dimethylaminopropyl-N′-ethylcarbodiimide hydrochloride and N-hydroxysuccinimde; and gluteraldehyde.
Methods of Using the Bone Graft Materials
The bone graft materials described herein may be used to increases osteogenesis, while also increasing hemostasis and reducing the rate of infection at the surgical site. These methods include, for example, placing in the bone, at a site to be restored or repaired, the biocompatible bone graft materials described herein. In one embodiment the bone graft material is wetted with a fluid prior to placement in the bony site. In another embodiment, the wetted bone graft material is flexible, moldable or flowable.
Many of the embodiments disclosed herein are to fill bony voids and defects. It will be appreciated that applications for the embodiments of the present invention include, but are not limited to, filling interbody fusion devices/cages (ring cages, cylindrical cages), placement adjacent to cages (i.e., in front cages), placement in the posterolateral gutters in posterolateral fusion (PLF) procedures, backfilling the iliac crest, acetabular reconstruction and revision hips and knees, large tumor voids, use in high tibial osteotomy, burr hole filling, and use in other cranial defects. The bone graft material strips may be suited for use in posterolateral fusion (PLF) by placement in the posterolateral gutters, and in onlay fusion grafting. Additional uses may include craniofacial and trauma procedures that require covering or wrapping of the injured/void site. The bone graft material cylinders may be suited to fill spinal cages and large bone voids, and for placement along the posterolateral gutters in the spine.
Methods of Manufacturing Bone Graft Materials
Described herein are methods for manufacturing the biocompatible bone graft materials described herein. One exemplary embodiment for preparing a bone graft material comprising calcium phosphate and chitosan includes making a solution of acid in water; adding chitosan to the acid solution to create a slurry; incubating the slurry; optionally, adjusting the pH of the slurry with a base to a neutral pH; adding calcium phosphate and, optionally, collagen to the slurry to create a mixture; incubating the mixture; drying the mixture; and optionally, washing the lyophilized material to form a biocompatible bone graft material.
Any acid can be used to make the solution of acid in water. Exemplary acids include acetic acid, acrylic acid, citric acid, formic acid, hydrochloric acid, lactic acid, and tartaric acid. There is no limit to the concentration of acid in the aqueous solution. In one embodiment, the concentration of acid in water is about 1% to about 99% volume by volume. In another embodiment, the concentration of acid in water is about 1% to about 20% volume by volume. In yet another embodiment, the concentration of acid in water is about 1% to about 10% volume by volume. In still another embodiment, the concentration of acid in water is about 1% to about 5% volume by volume.
The amount of chitosan mixed with the acid solution is not limited, so long as the temperature does not degrade or chemically modify the chitosan. In one embodiment, the concentration of chitosan in the acid solution is about 0.5% to about 20% weight by volume. In another embodiment, the concentration of chitosan in the acid solution is about 0.5% to about 10% weight by volume. In yet another embodiment, the concentration of chitosan in the acid solution is about 1% to about 5% weight by volume.
Upon addition of chitosan to the acid solution to form a slurry, the slurry of chitosan and calcium phosphate is incubated. During incubation, the slurry can be shaken, mixed, or both. The length of the incubation step is not limited. In one embodiment, incubation is about 0.5 hour to about 5 days. In another embodiment the slurry is incubated for about 4 hours to about 3 days. In yet another embodiment the slurry is incubated for about 4 hours to about 24 hours.
The temperature of the slurry during incubation is not limited so long as the components are not degraded or chemically altered. In one embodiment, the temperature of the slurry during incubation is about room temperature to about 70° C. In another embodiment, the temperature of the slurry during incubation is about 37° C. to about 50° C.
After incubating the chitosan-acid slurry, the pH of the slurry can optionally be adjusted to a neutral pH with any base. A neutral pH is a pH of at least about 4 to about 8. Adjusting the pH to a neutral pH may help to maintain the biocompatibility of the bone graft material. Any base known to those skilled in the art can be used to adjust the pH of the slurry including, for example, sodium hydroxide (NaOH). In one embodiment, the pH is adjusted to about pH 4 to about pH 5. In certain embodiments, the pH is not adjusted with a base after incubating the chitosan-acid slurry, because upon the subsequent addition of calcium phosphate to the chitosan-acid slurry, the pH may be naturally adjusted to a neutral pH.
After incubating the slurry, or optionally adjusting the pH of the slurry, calcium phosphate is added to the slurry to create a mixture of chitosan and calcium phosphate. The ratio of chitosan to calcium phosphate is not limited. In one embodiment, the ratio of calcium phosphate to chitosan-acid slurry is about 0.01 grams per ml to about 1 gram per ml. In another embodiment, the ratio of calcium phosphate to chitosan-acid slurry is about 0.01 grams per ml to about 0.5 grams per ml. In yet another embodiment, the ratio of calcium phosphate to chitosan-acid slurry is about 0.025 grams per ml to about 0.25 grams per ml.
During incubation of the mixture of chitosan-acid slurry and calcium phosphate, the mixture can be shaken, mixed, or both. The length of the incubation is step not limited. In one embodiment, incubation is about 1 hour to about 24 hours. In another embodiment, incubation is about 1 hour to about 5 hours. The temperature at which incubation is performed is not limit so long as the components are not degraded or chemically altered. In one embodiment incubation is performed at about room temperature to about 37° C.
After mixing the calcium phosphate and optional collagen with the chitosan-acid slurry, the mixture is dried to produce a biocompatible bone graft material. Drying can occur, for example, by vacuum, by air drying, or by freezing and lyophilizing the mixture. In one embodiment, the mixture is dried by freezing and lyophilizing, wherein the freezing temperature is about −28° C. to about 0° C., and the lyophilization is performed to dryness. In another embodiment, lyophilization is performed for up to 5 days. In yet another embodiment, lyophilization is performed for up to 3 days.
Lastly, the dried bone graft material can optionally be washed with a solution, for example water, to remove any residual acid from the bone graft material. The optional washing step can occur any time subsequent to the drying step but prior to implantation into the bony site.
In one embodiment, the calcium phosphate added to the chitosan-acid slurry is in the form of particles or morsels. In one embodiment, the amount of chitosan-acid slurry added to the calcium phosphate particles or morsels, as well as incubation time, is sufficient to saturate and coat the entire surface of the calcium phosphate particles or morsels, including any porous surfaces that may exist in the calcium phosphate particles or morsels without disrupting, changing or blocking the pores of the porous surface of the particles or morsels.
For the embodiments in which the bone graft material contains collagen, the collagen can be added before drying of the mixture as described above. In another embodiment, the collagen can be added to the dried calcium phosphate and chitosan mixture to create a second mixture and incubated as described above. After incubation, the second mixture can optionally be dried a second time, as described above, to form a bone graft material comprising calcium phosphate, collagen, and chitosan.
In one embodiment, bone graft materials are contemplated that are prepared by the any of the methods described herein. For example, in one embodiment, a bone graft material comprising calcium phosphate and chitosan is prepared by making a solution of acid in water; adding chitosan to the acid solution to create a slurry; incubating the slurry; optionally, adjusting the pH of the slurry with a base to a neutral pH; combining the chitosan-acid slurry with calcium phosphate particles or morsels and, optionally, collagen to create a mixture; incubating the mixture; drying the mixture; and optionally, washing the dried material to form a biocompatible bone graft material, wherein the amount of chitosan-acid slurry added to the calcium phosphate particles or morsels, as well as incubation time, is sufficient to saturate and coat the entire surface of the calcium phosphate particles or morsels, including any porous surfaces that may exist in the calcium phosphate particles or morsels.
Several formulations of bone graft materials were prepared with varying amounts of chitosan and acid solutions: 5% chitosan in 5% acetic acid, 3% chitosan in 3% acetic acid, 3% chitosan in 4% acetic acid, and 5% chitosan in 3% acetic acid using the following method. First, the appropriate concentration of acid solution was prepared by diluting a stock solution of the acid in water. Chitosan was added to the acid solution to prepare a slurry to form the appropriate concentration of chitosan. The slurry was then mixed for at least 4 hours at room temperature. After mixing, 0.5 grams of calcium phosphate morsels were added to 20 ml of the slurry and mixed for 60 minutes at room temperature. The mixtures were then frozen and lyophilized to form a bone graft material. The resulting materials were putty-like, moderately flexible, and easily compressed.
In order to determine if the addition of chitosan to the calcium phosphate caused any chemical change to the structure of the calcium phosphate morsels, Fourier-Transform Infrared Spectroscopy (FTIR) was performed to analyze the bone graft materials. For controls, unmodified calcium phosphate and chitosan alone were also tested. The FTIR spectra results are summarized in
A bone graft material was prepared with 1% chitosan in 2% acetic acid. First, the appropriate concentration of acid solution was prepared by diluting a stock solution of the acid in water. Chitosan was added to the acid solution to prepare a slurry to form the appropriate concentration of chitosan. The pH was then adjusted with a base to pH 4.2. After adjusting the pH enough calcium phosphate particles were added to soak up the chitosan-acid slurry in order to saturate the calcium phosphate particles and allowed to air dry overnight to form a bone graft material. After drying, approximately 0.2 g of the bone graft material was added to approximately 1 mL of mammalian cell culture broth and incubated at 37 degrees Celsius for 24 hours. After incubation, the medium was extracted and added to a culture of MG63 osteoblast, cells and Saos-2 osteoblast cells. The cells were cultured for up to 8 months. Various enzymatic tests and microscopic images were taken during this time as described below.
At 7 days, 14 days, and 21 days the MG63 cells were tested using an MTT assay which indicates continued cell proliferation of the MG63 cells. As a control, MG63 cells plated only with culture media was tested. The results of the MIT assay are summarized in
At 7 days, 14 days, and 21 days the MG63 cells were tested using an assay which is a bone differentiation marker. As a control, MG63 cells plated only with culture media were tested. The results of the ALP assay are summarized in
At 0 days, 28 days, 90 days, and 150 days, the cell proliferation and infiltration of the Saos-2 cells and new calcium phosphate formation with bone graft materials containing chitosan and calcium phosphate was observed using scanning electron microscopy images (SEM). As a control, the bone graft materials containing only calcium phosphate and not chitosan were evaluated. Selected SEM images are shown in
Hematoxylin and eosin (H&E) staining was performed on 90 day samples in order to determine the extent of protein matrix lining on the bone graft materials.
The results of the H&E study indicating faster osteoblast infiltration and new bone growth with bone graft materials described herein containing chitosan was confirmed by Energy dispersive X-ray spectroscopy (EDAX). EDAX spectra for bone graft materials with or without chitosan at 90 days are demonstrated in
Several formulations of bone graft materials were prepared with varying amounts of chitosan and acid solution: 3% chitosan in 3% acetic acid, 3% chitosan in 4% acetic acid, 5% chitosan in 3% acetic acid, 5% chitosan in 5% acetic acid and 5% chitosan in 3% acetic acid washed with ethanol using the method described in Example 1. The bone graft materials were added to Tryptic Soy Broth (TSB) at a ratio of 0.2 g of material per ml of broth. Staphylococcus aureus was added to the bone graft material/broth mixture at a target concentration of 1×106 cfu/ml and incubated at 37° C. for up to 8 days. An aliquot of each sample was taken at 0 hour, 24 hour and 5 days, and 8 days, serially diluted, and plated onto agar plates. Bacterial colonies were counted after 24 hours. A sample containing Staphylococcus aureas without bone graft material was used as a control.
Several different formulations of bone graft materials were prepared by adding each of the components into a dual syringe with a luer connector and using the plunger to push the contents back and forth until mixed well, generally at least 20 pushes. The various formulations prepared are listed in Table 2 below.
Each the formulations was tested for their hemostatic properties by simulating an injury to a blood vessel. To perform this test a cut was made in a tubing though which pigs blood was being pumped through. To test for hemostatic properties, each of the bone graft materials was applied to the cut in the tubing, while blood was pumping, to determine if the bone graft material could cause the blood to clot and prevent leakage of the blood out of the cut in the tubing. Observations regarding the clotting capabilities were made and summarized in Table 2 above.
Although the invention herein has been described with reference to particular embodiments, it is to be understood that these embodiments are merely illustrative of the principles and applications of the present invention. It is therefore to be understood that numerous modifications may be made to the illustrative embodiments and that other arrangements may be devised without departing from the spirit and scope of the present invention as defined by the appended claims.
| Number | Name | Date | Kind |
|---|---|---|---|
| 4326532 | Hammar | Apr 1982 | A |
| 4365050 | Ivani | Dec 1982 | A |
| 4447562 | Ivani | May 1984 | A |
| 5053212 | Constantz et al. | Oct 1991 | A |
| 5064653 | Sessions et al. | Nov 1991 | A |
| 5065752 | Sessions et al. | Nov 1991 | A |
| 5180426 | Sumita | Jan 1993 | A |
| 5254301 | Sessions et al. | Oct 1993 | A |
| 5281404 | Sumita | Jan 1994 | A |
| 5326350 | Li | Jul 1994 | A |
| 5462990 | Hubbell et al. | Oct 1995 | A |
| 5571181 | Li | Nov 1996 | A |
| 5573934 | Hubbell et al. | Nov 1996 | A |
| 5773577 | Cappello | Jun 1998 | A |
| 5817303 | Stedronsky et al. | Oct 1998 | A |
| 5858746 | Hubbell et al. | Jan 1999 | A |
| 5916928 | Sessions et al. | Jun 1999 | A |
| 5944754 | Vacanti | Aug 1999 | A |
| 5968542 | Tipton | Oct 1999 | A |
| 6033654 | Stedronsky et al. | Mar 2000 | A |
| 6054122 | MacPhee et al. | Apr 2000 | A |
| 6056970 | Greenawalt et al. | May 2000 | A |
| 6096309 | Prior et al. | Aug 2000 | A |
| 6117425 | MacPhee et al. | Sep 2000 | A |
| 6156305 | Brauker et al. | Dec 2000 | A |
| 6162241 | Coury et al. | Dec 2000 | A |
| 6197325 | MacPhee et al. | Mar 2001 | B1 |
| 6214048 | Ito et al. | Apr 2001 | B1 |
| 6280727 | Prior et al. | Aug 2001 | B1 |
| 6383519 | Sapieszko et al. | May 2002 | B1 |
| 6413539 | Shalaby | Jul 2002 | B1 |
| 6423333 | Stedronsky et al. | Jul 2002 | B1 |
| 6447802 | Sessions et al. | Sep 2002 | B2 |
| 6451301 | Sessions et al. | Sep 2002 | B1 |
| 6458889 | Trollsas et al. | Oct 2002 | B1 |
| 6465001 | Hubbell et al. | Oct 2002 | B1 |
| 6495127 | Wallace et al. | Dec 2002 | B1 |
| 6503527 | Whitmore et al. | Jan 2003 | B1 |
| 6521246 | Sapieszko et al. | Feb 2003 | B2 |
| 6536448 | McDevitt et al. | Mar 2003 | B2 |
| 6559119 | Burgess et al. | May 2003 | B1 |
| 6568398 | Cohen | May 2003 | B2 |
| 6632446 | Hubbell et al. | Oct 2003 | B1 |
| 6699484 | Whitmore et al. | Mar 2004 | B2 |
| 6833408 | Sehl et al. | Dec 2004 | B2 |
| 7008392 | Beaudry | Mar 2006 | B2 |
| 7019191 | Looney et al. | Mar 2006 | B2 |
| RE39192 | MacPhee et al. | Jul 2006 | E |
| 7078055 | Sessions et al. | Jul 2006 | B2 |
| 7078056 | Sessions et al. | Jul 2006 | B2 |
| RE39298 | MacPhee et al. | Sep 2006 | E |
| 7109163 | Pendharkar et al. | Sep 2006 | B2 |
| RE39321 | MacPhee et al. | Oct 2006 | E |
| 7153519 | Hubbell et al. | Dec 2006 | B2 |
| 7166570 | Hunter et al. | Jan 2007 | B2 |
| 7186684 | Pendharkar et al. | Mar 2007 | B2 |
| 7189263 | Erbe et al. | Mar 2007 | B2 |
| 7189410 | Drohan et al. | Mar 2007 | B1 |
| 7196054 | Drohan et al. | Mar 2007 | B1 |
| 7208179 | Drohan et al. | Apr 2007 | B1 |
| 7229959 | Drohan et al. | Jun 2007 | B1 |
| 7252837 | Guo et al. | Aug 2007 | B2 |
| 7279177 | Looney et al. | Oct 2007 | B2 |
| 7294334 | Michal et al. | Nov 2007 | B1 |
| 7300663 | Stedronsky et al. | Nov 2007 | B2 |
| 7371403 | McCarthy et al. | May 2008 | B2 |
| 7482503 | Gregory et al. | Jan 2009 | B2 |
| 7595043 | Hedrick et al. | Sep 2009 | B2 |
| 7615373 | Simpson et al. | Nov 2009 | B2 |
| 7622437 | Morrissey et al. | Nov 2009 | B2 |
| 7625585 | Sessions et al. | Dec 2009 | B2 |
| 7641643 | Michal et al. | Jan 2010 | B2 |
| 7709005 | Sessions et al. | May 2010 | B2 |
| 7718412 | Pendharkar et al. | May 2010 | B2 |
| 7744913 | Noyes | Jun 2010 | B2 |
| 7820872 | Gregory et al. | Oct 2010 | B2 |
| 20110118850 | Govil et al. | May 2011 | A1 |
| Entry |
|---|
| Moreau, Jennifer L., Michael D. Weir, and Hockin HK Xu. “Self- setting collagen—calcium phosphate bone cement: Mechanical and cellular properties.”Journal of Biomedical Materials Research Part A 91.2 (2009): 605-613. |
| Ito, M. “In vitro properties of a chitosan-bonded hydroxyapatite bone-filling paste.” Biomaterials 12.1 (1991): 41-45. |
| Leffler et al., “Influence of the acid type on the physical and drug liberation properties of chitosan—gelatin sponges”, International Journal of Pharmaceutics, 194, pp. 229-237, 2000. |
| Kingery, W. D., Introduction to Ceramics, Wiley Series on the Science and Technology of Materials, 1st Ed., Hollowman, J. H., et al. (Eds.), Wiley & Sons, 1960, p. 409-417. |
| Number | Date | Country | |
|---|---|---|---|
| 20140271914 A1 | Sep 2014 | US |
