Patent Application
20170056550
This disclosure relates to freeze-dried polymer compositions for use in implantation in bleeding subchondral bone defects and/or bleeding meniscal trephination channels and/or and/or bleeding tendon insertion sites and/or bleeding rotator cuff repair sites, i) promoting residency of the coagulum and ii) stimulating therapeutic effects on bone marrow-derived articular cartilage repair and meniscal repair.
Trauma or repetitive damage to the articular cartilage layer may lead to degeneration of the non-calcified tissue and the development of a symptomatic focal cartilage lesion. To prevent or delay meniscal damage and global knee degeneration, Outerbridge Grade III and IV lesions that approach or violate the osteochondral junction are often treated by surgical cartilage repair therapy. Cartilage repair therapies begin with a debridement step, where all degenerated articular cartilage is removed from the lesion area with a curette or shaver, to expose the subchondral bone underlying the lesion. In cell-assisted therapies, the debrided lesion is then treated by applying autologous cells using a biomaterial scaffold or tissue flap to retain the cells in the lesion. By another approach, bone marrow stimulation therapies such as microfracture, involve the creation of bone holes ˜2 mm in diameter and 2 to 4 mm deep in the base of the debrided cartilage defect (Steadman J R, Rodkey W G, Singleton S B, Briggs K K: Microfracture technique for full-thickness chondral defects: technique and clinical results, Operative Techniques in Orthopaedics 1997, 7:300-304; Mithoefer K, Williams R J, 3rd, Warren R F, Potter H G, Spock C R, Jones E C, Wickiewicz T L, Marx R G: The microfracture technique for the treatment of articular cartilage lesions in the knee. A prospective cohort study, J Bone Joint Surg-Am Vol 2005, 87:1911-1920) to stimulate repair tissue formation by cells that migrate from the trabecular bone marrow into the cartilage lesion. However it has been reported that the repair tissues elicited by cell-assisted or microfracture therapies are most frequently fibrous tissue or fibrocartilage (Knutsen G, Engebretsen L, Ludvigsen T C, Drogset J O, Grontvedt T, Solheim E, Strand T, Roberts S, Isaksen V, Johansen C: Autologous chondrocyte implantation compared with microfracture in the knee—A randomized trial, J Bone Joint Surg-Am Vol 2004, 86A:455-464; Saris D B, Vanlauwe J, Victor J, Haspl M, Bohnsack M, Fortems Y, Vandekerckhove B, Almqvist K, et al: Characterized chondrocyte implantation results in better structural repair when treating symptomatic cartilage defects of the knee in a randomized controlled trial versus microfracture, Am J Sports Med 2008, 36:235-246), tissues with weak biomechanical properties and limited durability compared to hyaline articular cartilage. In two distinct randomized controlled clinical trials with 40 patients per treatment group, the clinical benefit of cell therapy was not superior to microfracture at 5 years post-surgery (Knutsen G, Engebretsen L, Ludvigsen T C, Drogset J O, Grontvedt T, Solheim E, Strand T, Roberts S, Isaksen V, Johansen C: Autologous chondrocyte implantation compared with microfracture in the knee—A randomized trial, J Bone Joint Surg-Am Vol 2004, 86A:455-464; Saris D B, Vanlauwe J, Victor J, Haspl M, Bohnsack M, Fortems Y, Vandekerckhove B, Almqvist K, et al.: Characterized chondrocyte implantation results in better structural repair when treating symptomatic cartilage defects of the knee in a randomized controlled trial versus microfracture, Am J Sports Med 2008, 36:235-246; Knutsen G, Drogset J O, Engebretsen L, Grontvedt T, Isaksen V, Ludvigsen T C, Roberts S, Solheim E, Strand T, Johansen O: A Randomized trial comparing autologous chondrocyte implantation with microfracture, J Bone Joint Surg-Am Vol 2007, 89A:2105-2112; Vanlauwe J, Saris D B F, Victor J, Almqvist K F, Bellemans J, Luyten F P, for the TA, Group EXTS: Five-Year Outcome of Characterized Chondrocyte Implantation Versus Microfracture for Symptomatic Cartilage Defects of the Knee: Early Treatment Matters, The American Journal of Sports Medicine 2011, 39 2566-2574). Microfracture, otherwise known as “bone marrow stimulation” therapy, offers a less expensive alternative to cell therapy in treating focal cartilage lesions, with a similar probability of a therapeutic response. It is known that skeletally aged knees have an attenuated cartilage repair response to marrow stimulation (Kreuz P C, Erggelet C, Steinwachs M R, Krause S J, Lahm A, Niemeyer P, Ghanem N, Uhl M, Sudkamp N: Microfracture of chondral defects in the knee associated with different results in patients aged 40 years or younger?, Arthroscopy-the Journal of Arthroscopic and Related Surgery 2006, 22:1180-1186). Adjunct treatments that improve the quality and durability of bone marrow-elicited repair tissue are therefore desired, especially for chronic lesions with evidence of subchondral bone sclerosis (Hoemann C D, Gosselin Y, Chen H, Sun J, Hurtig M, Carli A, Stanish W D: Characterization of initial microfracture defects in human condyles, Journal of Knee Surgery 2013; 26(5):347-55).
Liquid chitosan formulations have been developed that successfully stimulate a more hyaline articular cartilage repair in animal microfracture defects (Hoemann C D, Hurtig M, Rossomacha E, Sun J, Chevrier A, Shive M S, Buschmann M D: Chitosan-glycerol phosphate/blood implants improve hyaline cartilage repair in ovine microfracture defects, J Bone Joint Surg-Am Vol 2005, 87A:2671-2686) and generate increased repair tissue fill at 1 year post-operative in human compared to microfracture-alone (Stanish W D, McCormack R, Forriol C F, Mohtadi N, Pelet S, Desnoyers J, Restrepo A, Shive M S: Novel scaffold-based BST-CarGel® treatment results in superior cartilage repair in a randomized controlled trial compared to microfracture. Better structural repair at 12 months in terms of repair tissue quantity and quality. J. Bone Joint Surg-Am Vol 2013, 95(18):1640-50) however current formulations and methods are limited by several practical considerations.
In one application, a chitosan solution was prepared with biodegradable medium-viscosity chitosan with 75% to 85% degree of deacetylation (DDA) and disodium glycerol phosphate. The chitosan solution was then mixed at a 1:3 v/v ratio with autologous whole blood and flooded over a cartilage lesion treated by bone marrow stimulation (Hoemann C D, Hurtig M, Rossomacha E, Sun J, Chevrier A, Shive M S, Buschmann M D: Chitosan-glycerol phosphate/blood implants improve hyaline cartilage repair in ovine microfracture defects, J Bone Joint Surg-Am Vol 2005, 87A:2671-2686). The implant solidified in situ through blood coagulation, fibrin polymerization, and by the transitioning of chitosan from soluble chains at pH 6, to microparticles at blood pH 7, during which chitosan chains form complexes with anionic blood proteins such as complement C3 (Marchand C, Rivard G E, Sun J, Hoemann C D: Solidification mechanisms of chitosan-glycerol phosphate/blood implant for articular cartilage repair, Osteoarthritis Cartilage 2009, 17:953-960; Marchand C, Bachand J, Perinet J, Baraghis E, Lamarre M, Rivard G E, De Crescenzo G, Hoemann C D: C3, C5, and factor B bind to chitosan without complement activation, Journal of Biomedical Materials Research Part A 2010, 93A:1429-1441). The in situ-solidified chitosan-blood implant transiently concentrates neutrophils, macrophages, alternatively activated arginase-1+ macrophages and osteoclasts near the top of the subchondral bone defect, which stimulates angiogenesis, bone remodeling, mesenchymal stromal cell migration towards the cartilage lesion, and formation of cartilage-regenerating chondrogenic foci near the articular surface (Hoemann C D, Chen G P, Marchand C, Sun J, Tran-Khanh N, Chevrier A, Thibault M, Fernandes M G J, et al. Scaffold-guided subchondral bone repair: implication of neutrophils and alternatively activated arginase-1+ macrophages. Am. J. Sports Med. 2010; 38(9): 1845-56; Chen G, Sun J, Lascau-Coman V, Chevrier A, Marchand C, Hoemann C D. Acute osteoclast activity following subchondral drilling is promoted by chitosan and associated with improved cartilage repair tissue integration. Cartilage, 2011: 2: 173-185; Chevrier A, Hoemann C D, Sun J, Buschmann M D. Chitosan-glycerol phosphate/blood implants increase cell recruitment, transient vascularization and subchondral bone remodeling in drilled cartilage defects. Osteoarthritis & Cartilage 2007 15:316-327). In human subjects, the liquid chitosan/blood mixture was prepared ex vivo, with a phlebotomy, then injected as a liquid mixture over the microfracture cartilage lesion through a mini-arthrotomy along with a 15 minute wait-time for in situ solidification (WO200200272-A, WO2011060553-A1; Shive M S, Hoemann C D, Restrepo A, Hurtig M B, Duval N, Ranger P, Stanish W, Buschmann M D: BST-CarGel: In Situ ChondroInduction for Cartilage Repair, Operative Techniques in Orthopaedics 2006, 16:271-278). During the wait time for in situ solidification, the cartilage was exposed to the air. Creation of an implant with the same therapeutic responses that does not require a phlebotomy, ex vivo manipulation and a 15 minute wait time during the arthrotomy for in situ solidification would be very advantageous.
In other prior art, liquid chitosan formulations were mixed with autologous whole blood and pre-solidified to form an elastic cylindrical blood clot implant containing highly dispersed chitosan microparticles (Hoemann C, Sun J, Hurtig M, Guzman-Morales J, Hubert-Lafantaisie C: Presolidified composition for use in repairing tissue of a patient, comprises a blood component, a salt and a polymer, the blood component, salt and polymer being mixed and solidified in a recipient before administration to the patient, WO2011060554-A1). The hybrid implant can be prepared in advance of the arthrotomy step, and therefore reduces arthrotomy time, and allows treatment of defects that are not horizontally positioned (WO2011060554-A1). In a rabbit osteochondral repair model, chitosan formulations with low molecular weight (10 kDa, 40 kDa) were shown to stimulate therapeutic osteochondral wound repair responses during 3 weeks post-operative in skeletally aged rabbits (Lafantaisie-Favreau C H, Guzman-Morales J, Sun J, Chen G P, Harris A, Smith T D, Carli A, Henderson J, Stanish W D, Hoemann C D: Subchondral pre-solidified chitosan/blood implants elicit reproducible early osteochondral wound-repair responses including neutrophil and stromal cell chemotaxis, bone resorption and repair, enhanced repair tissue integration and delayed matrix deposition, BMC Musculoskeletal Disorders 2013, 14:27), including chemotaxis of neutrophils, mesenchymal stromal cells and osteoclasts, inhibition of rapid fibrocartilage formation, and bone remodeling. However chitosan clearance kinetics can also influence repair because, in the rabbit, where high metabolism drives rapid wound repair, the 150 kDa chitosan formulation was cleared too slowly, leading to excessive apoptotic neutrophil accumulation and greater bone resorption, which is an undesired effect. Implantation of a pre-solidified implant created from an aqueous solution of 10 kDa chitosan dispersed in whole blood stimulated more bone remodeling and a more hyaline-like cartilage repair compared to drilling alone, at 70 days after press-fitting into rabbit osteochondral defects (Guzman-Morales J, Lafantaisie-Favreau C H, Chen G, Hoemann C D: Subchondral chitosan/blood implant-guided bone plate resorption and woven bone repair is coupled to hyaline cartilage regeneration from microdrill holes in aged rabbit knees, Osteoarthritis and Cartilage 2014, 22:323). It is known how to create a blood clot containing dispersed chitosan microparticles by combining liquid chitosan solution and blood. However knowledge of how to create a blood clot containing dispersed chitosan microparticles directly from a freeze-dried chitosan formulation is currently lacking.
Implants consisting of chitosan microparticles in blood coagulum are known to elicit neutrophils and alternatively activated macrophages to other sites including subcutaneous implants (Hoemann C D, Chen G, Marchand C, Sun J, Tran-Khanh N, Chevrier A, Thibault M, Fernandes M G J, Poubelle P E, Shive M S, Centola M, El-Gabalawy H: Scaffold-guided subchondral bone repair: implication of neutrophils and alternatively activated arginase-1+ macrophages, Am J Sports Med 2010, 38:1845-1856). Therefore implants generated from freeze-dried chitosan scaffolds that disperse as microparticles in blood or blood-derived fluids may be used to stimulate the revascularization and repair of other joint tissues including the meniscus (Chevrier A, Nelea M, Hurtig M B, Hoemann C D, Buschmann M D: Meniscus Structure in Human, Sheep, and Rabbit for Animal Models of Meniscus Repair, Journal of Orthopaedic Research 2009, 27:1197-1203).
Liquid chitosan formulations, according to the solution pH and osmolality, will precipitate, gel, or undergo spontaneous hydrolysis over time at room temperature (WO2011060553-A1). Low molecular mass chitosan solutions that form spontaneously by long-term storage of liquid chitosan can still be used to prepare a liquid chitosan-blood implant but lack in ease-of-use for in situ solidification of the resulting aqueous mixture, because a liquid low-viscosity polymer-blood mixture is difficult to retain in a cartilage defect, and because joint contours are curved. Given that hydrolysis alters the chitosan structure and biophysical behavior, a method for maintaining chitosan molecular weight during storage is needed. An off-the-shelf chitosan formulation that maintains polymer molecular weight during prolonged storage at room temperature, that can be used to create a hybrid polysaccharide-blood implant containing dispersed chitosan microparticles, that does not require a 15 minute wait time for implantation, has controlled mechanical properties and a specific shape (rigid with mechanical integrity, not flakes), and that can be delivered and retained in an osteochondral defect is desired. A chitosan device that avoids time-consuming intra-operative wait time for implant ex vivo preparation and does not require a 15 minute wait time for in situ solidification, that is easy to deliver to marrow stimulation defects, and that allows for long-term room temperature storage without any alteration in the chitosan molecular weight would be very advantageous.
Several lyophilized chitosan-acetic acid formulations with distinct degree of deacetylation and molecular mass were implanted into osteochondral defects in a rabbit model, and shown to have detrimental effects on bone and cartilage repair (Abarrategi A, Lopiz-Morales Y, Ramos V, Civantos A, Lopez-Duran L, Marco F, Lopez-Lacomba J L: Chitosan scaffolds for osteochondral tissue regeneration, Journal of Biomedical Materials Research Part A 2010, 95A:1132-1141). In the study by Abarrategi et al 2010, defects were created in the medial femoral condyle of N=3 rabbits with 3.0 to 3.4 kg body mass, which is skeletally immature according to data published by Masoud et al 1986 (Masoud I, Shapiro F, Kent R, Moses A: A longitudinal study of the growth of the New Zealand white rabbit: Cumulative and biweekly incremental growth rates for body length, body weight, femoral length, and tibial length, Journal of Orthopaedic Research 1986, 4:221-231). Treatment of an osteochondral rabbit defect with chitosan-acetic acid lyophilized scaffold (80% DDA-500 kDa, 90% DDA-500 kDa, 90% DDA-9 kDa) failed to improve or reduced the histological cartilage repair tissue scores compared to untreated osteochondral defects. It was reported that overall histological scores were improved in N=3 defects treated by 10 kDa chitosan 83% DDA with or without 18% w/w calcium carbonate mineral content, compared to untreated defects at 3 months post-operative (Abarrategi A, Lopiz-Morales Y, Ramos V, Civantos A, Lopez-Duran L, Marco F, Lopez-Lacomba J L: Chitosan scaffolds for osteochondral tissue regeneration, Journal of Biomedical Materials Research Part A 2010, 95A:1132-1141). However, high overall histology scores for 10 kDa 83% DDA chitosan-treated defects, were contradicted by accompanying histology images showing glycosaminoglycan-depleted extracellular matrix and poor structural integrity of the repair tissue (Abarrategi A, Lopiz-Morales Y, Ramos V, Civantos A, Lopez-Duran L, Marco F, Lopez-Lacomba J L: Chitosan scaffolds for osteochondral tissue regeneration, Journal of Biomedical Materials Research Part A 2010, 95A:1132-1141). Moreover, given the high spontaneous repair potential of immature rabbit osteochondral defects (Shapiro F, Koide S, Glimcher M J: Cell Origin and Differentiation in the Repair of Full-Thickness Defects of Articular Cartilage, J Bone Joint Surg-Am Vol 1993, 75A:532-553; Wei X C, Messner K: Maturation-dependent durability of spontaneous cartilage repair in rabbit knee joint, J Biomed Mater Res 1999, 46:539-548) and given the lack of evidence that the implants were retained in vivo in the treated defects, results of this study could be explained by failure of the implant to reside in the treated defect. Another freeze-dried chitosan scaffold has been patented for hemostatic activity, but the formulation includes a non-porous collagen phase to allow high mechanical properties that are incompatible with microparticle dispersion in a coagulum (Mehta R D: Accelerated wound healing systems and their production method. Edited by MEHTA R D (MEHT-Individual), IN200701721-I3). Another freeze-dried chitosan sponge was previously conceived but the scaffold was intended to remain a solid after implanting to allow prolonged drug delivery (Moon H, Byung J A: Porous drug delivery type functional scaffolds preparing method, involves controlling pore size by dissolving chitin/chitosan in solution of lactic and acetic acid or hydrochloric acid, and pouring solution into scaffold-forming mold. Edited by BYUNG J A (BYUN-Individual) MOON H (MOON-Individual) UNIV EULJI IND COOP (UYEU-Non-standard) WELLBEING CO LTD (WELL-Non-standard), KR2008016216-A).
Other polymer implants have been previously developed with ease-of-use for implanting in a bleeding osteochondral defect, but show inconsistent cartilage repair efficacy and frequently inhibit bone repair. Solid hydrogels, sponges, cross-linked polymers or cylinders of synthetic polyglycolic acid (PGLA)/tri-polyphosphate (TruFit®, Smith & Nephew), degrade slowly in the subchondral bone defect, inhibit subchondral bone regeneration and show inconsistent articular cartilage repair (Hoemann C D, Sun J, Legare A, McKee M D, Buschmann M D: Tissue engineering of cartilage using an injectable and adhesive chitosan-based cell-delivery vehicle, Osteoarthritis Cartilage 2005, 13:318-329; Streitparth F, Schoettle P, Schlichting K, Schell H, Fischbach F, Denecke T, Duda G N, Schroeder R J: Osteochondral Defect Repair after Implantation of Biodegradable Scaffolds: Indirect Magnetic Resonance Arthrography and Histopathologic Correlation, Acta Radiologica 2009, 50:765-774; Carmont M R, Carey-Smith R, Saithna A, Dhillon M, Thompson P, Spalding T: Delayed Incorporation of a TruFit Plug: Perseverance Is Recommended, Arthroscopy: The Journal of Arthroscopic & Related Surgery 2009, 25:810-814; Barber F A, Dockery W D: A Computed Tomography Scan Assessment of Synthetic Multiphase Polymer Scaffolds Used for Osteochondral Defect Repair, Arthroscopy-the Journal of Arthroscopic and Related Surgery 2010, 27:60-64). The TruFit PGLA scaffold that was shown to inhibit bone repair also has toxic degradation products (PGLA degrades to lactic acid and glycolic acid). In another approach, a solid membrane implant of porcine collagen type I and collagen type III (Chondro-Gide®, Geislich) was implanted over a full-thickness cartilage defect treated by microfracture, but proof-of-efficacy in eliciting cartilage repair as a cell-free scaffold is absent (Bartlett W, Skinner J A, Gooding C R, Carrington R W J, Flanagan A M, Briggs T W R, Bentley G: Autologous chondrocyte implantation versus matrix-induced autologous chondrocyte implantation for osteochondral defects of the knee, J Bone Joint Surg-Br Vol 2005, 87B:640-645). Polymers that biodegrade with a kinetics that is paralleled by granulation tissue formation are therefore desired because they have the potential to amplify natural wound repair responses, without physically interfering with cell migration into the bone lesion, and have the potential to stimulate wound repair responses that restore an osteochondral tissue with better biomechanical properties compared to implants that lead to soft tissue repair instead of mineralized bone repair of the subchondral bone plate, or large tissue voids in the subchondral bone space.
In designing an implant for augmented microfracture repair, there is a balance to strike between rigid polymers that degrade slowly and block subchondral bone regeneration, and collagen membranes that have low intrinsic wound repair bioactivity. The key property of a therapeutic implant applied to bleeding bone is chemotactic activity—the ability of the implant to attract cells, and the appropriate cell types, to the microfractured bone channels. Homogeneously dispersed chitosan microparticle in the initial blood clot, and appropriate in situ degradation kinetics by leukocytes, were shown to stimulate angiogenesis in subchondral bone defects (Mathieu C, Chevrier A, Lascau-Coman V, Rivard G E, Hoemann C D: Stereological analysis of subchondral angiogenesis induced by chitosan and coagulation factors in microdrilled articular cartilage defects, Osteoarthritis Cartilage 2013, 21:849-859) and transient resorption and repair of the subchondral bone plate (Bell A D, Lascau-Coman V, Sun J, Chen G, Lowerison M W, Hurtig M B, Hoemann C D: Bone-Induced Chondroinduction in Sheep Jamshidi Biopsy Defects with and without Treatment by Subchondral Chitosan-Blood Implant: 1-Day, 3-Week, and 3-Month Repair, Cartilage 2013, 4:131-143; Lafantaisie-Favreau C H, Guzman-Morales J, Sun J, Chen G P, Harris A, Smith T D, Carli A, Henderson J, Stanish W D, Hoemann C D: Subchondral pre-solidified chitosan/blood implants elicit reproducible early osteochondral wound-repair responses including neutrophil and stromal cell chemotaxis, bone resorption and repair, enhanced repair tissue integration and delayed matrix deposition, BMC Musculoskeletal Disorders 2013, 14; Guzman-Morales J, Lafantaisie-Favreau C H, Chen G, Hoemann C D: Subchondral chitosan/blood implant-guided bone plate resorption and woven bone repair is coupled to hyaline cartilage regeneration from microdrill holes in aged rabbit knees, Osteoarthritis and Cartilage 2014, 22:323), which can lead to chondroinduction at the base of the articular cartilage lesion and cartilage regeneration (WO2011060554-A1).
A solid polysaccharide implant formulation that can be shaped into a form that permits delivery to a bleeding defect, that reproducibly rehydrates and disperses in blood, and forms microparticles that reside in the defect, that attract macrophages and induce angiogenesis and local bone remodeling and osteochondral repair is desired.
Given the current state of the art, a chitosan implant is needed that responds to at least one of the following criteria:
As used herein, the term “controlled rehydration agent” refers to a substance whose composition or formulation controls the rate of rehydration of a lyophilized material.
In one aspect, there is provided a lyophilized scaffold composition comprising at least one polysaccharide, wherein said scaffold is substantially solid and capable of being formed into a desired shape; wherein the at least one polysaccharide has a protonation level resulting in controlled rehydration of said scaffold, such that when said scaffold is contacted with at least one of a neutral aqueous solution, blood, blood derived fluid and combinations thereof, said scaffold:
In another aspect, there is provided a process for preparing a lyophilized scaffold composition comprising at least one polysaccharide and optionally at least one controlled rehydration agent, wherein the at least one polysaccharide has a protonation level resulting in controlled rehydration and microparticle dispersion when contacted with at least one of a neutral aqueous solution, blood, blood derived fluid and combinations thereof; comprising the steps of
In one aspect there is provided a lyophilized scaffold composition comprising at least one polysaccharide, wherein said composition rehydrates in a controlled manner. In one embodiment, said composition further comprises at least one controlled rehydration agent. Preferably the polysaccharide is selected from chitosan, dextran and combinations thereof. Preferably the chitosan has a molecular weight of from about 5,000 Daltons (Da) to about 400,000 Da, more preferably from about 8,000 Da to about 350,000 Da and most preferably from about 10,000 Da to about 300,000 Da. If present in the formulation, the at least one controlled rehydration agent is preferably selected from the group consisting of low molecular mass chitosan, ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine and N-acetyl glucosamine. In a preferred embodiment, the lyophilized polysaccharide is in the form of a scaffold. In another preferred embodiment the lyophilized polysaccharide is porous, preferably highly porous, more preferably very highly porous, most preferably ultraporous.
In another aspect, there is provided the use of a lyophilized scaffold composition comprising at least one polysaccharide and optionally at least one controlled rehydration agent, wherein the at least one polysaccharide has a protonation level resulting in controlled rehydration and microparticle dispersion when contacted with at least one of a neutral aqueous solution, blood, blood derived fluid and combinations thereof, to modify a blood coagulum and promote wound repair in a mammal.
In another embodiment, the at least one controlled rehydration agent is selected from an acid. The acid is selected to provide an optimal level of polysaccharide protonation state. More preferably the acid is a pharmaceutically acceptable acid. Most preferably the acid is selected from the group consisting of hydrochloric acid, lactic acid, acetic acid and combinations thereof. In one embodiment, when chitosan is the at least one polysaccharide, the at least one controlled rehydration agent comprises an acid which generates a protonation state between 70% and 100% protonation of free amine groups, preferably between 80% and 98% protonation. In one embodiment, for a chitosan having a molecular weight no more than about 10,000 Da, said protonation state is preferably between 80% and 100% protonation. In another embodiment, for a chitosan having a molecular weight greater than 10,000 Da, said protonation state is preferably between 90% and 100%.
In another embodiment, the lyophilized polysaccharide is in the form of a pharmaceutically acceptable acid salt.
In another embodiment, the lyophilized polysaccharide composition further comprises at least one mineral selected from the group consisting of calcium carbonate, calcium phosphate, polytriphosphate, hydroxyapatite and combinations thereof.
In another aspect there is provided a lyophilized chitosan scaffold composition comprising chitosan and at least one controlled rehydration agent. Preferably the chitosan has a molecular weight from about 5,000 Da to about 400,000 Da, more preferably from about 8,000 Da to about 350,000 Da and most preferably from about 10,000 Da to about 300,000 Da. The at least one controlled rehydration agent is selected from the group consisting of ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine and N-acetyl glucosamine. In a preferred embodiment, the chitosan is in the form of a scaffold. In another preferred embodiment the chitosan is porous, preferably highly porous, more preferably very highly porous, most preferably ultraporous.
In another embodiment, the at least one controlled rehydration agent is selected from an acid. The acid is selected to provide an optimal level of chitosan protonation state. More preferably the acid is a pharmaceutically acceptable acid. Most preferably the acid is selected from the group consisting of hydrochloric acid, lactic acid, acetic acid and combinations thereof. The at least one controlled rehydration agent comprises an acid which generates a protonation state between 70% and 100% protonation of free amine groups, preferably between 80% and 98% protonation. In one embodiment, for a chitosan having a molecular weight no more than about 10,000 Da, said protonation state is preferably between 80% and 100% protonation. In another embodiment, for a chitosan having a molecular weight greater than 10,000 Da, said protonation state is preferably between 90% and 100%.
In another embodiment, the lyophilized chitosan scaffold composition further comprises at least one chitosan amino sugar selected from but not limited to glucosamine and N-acetyl glucosamine.
In another embodiment, the chitosan preferably has a degree of deacylation (DDA) of from about 50% to about 100%, more preferably from about 70% to about 90% and most preferably about 80%.
In another embodiment, the chitosan is in the form of a pharmaceutically acceptable acid salt. Preferably the acid is an inorganic acid, more preferably a hydrohalic acid. Most preferably the acid is hydrochloric acid. Preferably the inorganic acid is present from about 70% to about 110% molar ratio with free amino groups of the chitosan polymer, more preferably from about 75% to about 105% molar ratio and most preferably from about 80% to about 100% molar ratio. Preferably an 80% to 90% molar ratio is preferred for a chitosan of 10,000 Da or less and a 90% to 100% molar ratio is more preferred for a chitosan of above 10,000 Da.
In another embodiment, the lyophilized chitosan scaffold composition further comprises at least one biological therapeutic protein or other factors that stimulate acute innate immune wound repair responses, preferably said at least one biological therapeutic protein or other factors includes but is not limited to cationic amphiphilic anti-microbial peptides or biomimetic peptides that activate cell migration, including but not limited to polypeptides or subfragments of SDF-1/CXCL12, chemokines, CXCL10/IP-10, IL-1 receptor antagonist, G-CSF, GM-CSF, M-CSF, interferon beta, interferon alpha, IL-4, IL-13, IL-10, and peptides, bioactive lipids such as LTB4 or PGE2, or factors that activate neutrophil chemotaxis without inducing degranulation.
In another embodiment, the lyophilized chitosan scaffold composition further comprises at least one biological therapeutic factor that stimulate angiogenesis including but not limited to recombinant factor VIIa (rhFVIIa), thrombin, Tissue Factor, VEGF, tryptase, MMP-13, IL-8, MCP-1.
In another aspect there is provided a process for preparing a lyophilized polysaccharide scaffold composition described herein, comprising the steps of contacting at least one polysaccharide and at least one controlled rehydration agent with water in the presence of an acid under sterile conditions to form an aqueous mixture and lyophilizing the mixture to give the lyophilized polysaccharide scaffold composition. Preferably the at least one polysaccharide is selected the group consisting of chitosan, chitosan amino sugar, dextran and combinations thereof. The chitosan preferably has a molecular weight from about 5,000 Da to about 400,000 Da, more preferably from about 8,000 Da to about 350,000 Da and most preferably from about 10,000 Da to about 300,000 Da. Preferably the at least one controlled rehydration agent is selected from the group consisting of ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine and N-acetyl glucosamine.
In another embodiment of the process, the at least one controlled rehydration agent is selected from an acid. The acid is selected to provide an optimal level of chitosan protonation state. More preferably the acid is a pharmaceutically acceptable acid. Most preferably the acid is selected from the group consisting of hydrochloric acid, lactic acid, acetic acid and combinations thereof. In one embodiment, the at least one controlled rehydration agent comprises an acid which generates a protonation state between 70% and 100% protonation of free amine groups, preferably between 80% and 98% protonation. In one embodiment, for a chitosan having a molecular weight no more than about 10,000 Da, said protonation state is preferably between 80% and 100% protonation. In another embodiment, for a chitosan having a molecular weight greater than 10,000 Da, said protonation state is preferably between 90% and 100%.
In another embodiment of the process, the chitosan preferably has a degree of deacylation (DDA) of from about 50% to about 100%, more preferably from about 70% to about 90% and most preferably about 80%.
The at least one polysaccharide is preferably present in the aqueous mixture in an amount of about 0.2 to about 7% weight by volume (w/v), more preferably about 0.3 to about 5% w/v and most preferably about 0.5 to about 3% w/v. In a preferred embodiment, when the at least one controlled rehydration agent comprising a chitosan monomer or a short-chain chitosan polymer is preferably present in the aqueous mixture in an amount of about 0.2 to about 10% w/v, more preferably about 0.3 to about 7% w/v and most preferably about 0.5 to about 5% w/v.
In a preferred embodiment, when the at least one controlled rehydration agent comprises an acid, the pH of the aqueous mixture is from about 2 to about 6 to provide a chitosan amine protonation state of 100% to about 80%, most preferably from about 2 to about 5.5 to provide a chitosan amine protonation state of 100% to about 90%. In a preferred embodiment, the osmolality of the aqueous mixture is from about 5 to about 200 mOsm.
In another preferred embodiment, the lyophilizing step is carried out under aseptic conditions by controlled cooling the aqueous mixture from about room temperature to about −40° C. to freeze the solution and then drying the mixture. Preferably the cooling rate is about 1° C. per minute. Preferably the drying steps take place under a vacuum, preferably under a vacuum of about 100 m Torr. In one embodiment, the primary drying step may last from about 36 hours to about 54 hours, most preferably about 48 hours. Preferably the secondary drying step is carried out by warming at a rate of 0.05° C. to 0.2° C., more preferably 0.1° C. per minute, preferably from about −40° C. to about 30° C., for a period of time between 6 and 24 hours, preferably 12 hours, and followed by another step of maintaining isothermal temperature at about 30° C. for about 6 hours prior to removing the vacuum.
In another aspect there is provided a process for preparing a lyophilized chitosan scaffold composition comprising the steps of contacting chitosan and at least one controlled rehydration agent with water under sterile conditions in the presence of an acid to form an aqueous mixture, and lyophilizing the mixture to give the lyophilized chitosan scaffold composition. Preferably the composition further comprises a chitosan amino sugar. The chitosan preferably has a molecular weight from about 5,000 Da to about 400,000 Da, more preferably from about 8,000 Da to about 350,000 Da and most preferably from about 10,000 Da to about 300,000 Da. Preferably the at least one controlled rehydration agent is selected from the group consisting of ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine and N-acetyl glucosamine.
In another embodiment of the process, the at least one controlled rehydration agent is selected from an acid. The acid is selected to provide an optimal level of chitosan protonation state. More preferably the acid is a pharmaceutically acceptable acid. Most preferably the acid is selected from the group consisting of hydrochloric acid, lactic acid, acetic acid and combinations thereof.
In another embodiment of the process, the chitosan preferably has a degree of deacylation (DDA) of from about 50% to about 100%, more preferably from about 70% to about 90% and most preferably about 80%.
The chitosan of the process is preferably present in the aqueous mixture in an amount of about 0.2 to about 7% weight by volume (w/v), more preferably about 0.3 to about 5% w/v and most preferably about 0.5 to about 3% w/v. The at least one controlled rehydration agent is preferably present in the aqueous mixture in an amount of about 0.2 to about 10% w/v, more preferably about 0.3 to about 7% w/v and most preferably about 0.5 to about 5% w/v.
In a preferred embodiment of the process, the pH of the aqueous mixture is from about 2 to about 6 to provide a chitosan amine protonation state of 100% to about 80%, most preferably from about 2 to about 5.5 to provide a chitosan amine protonation state of 100% to about 90%. In a preferred embodiment, the osmolality of the aqueous mixture is from about 5 to about 200 mOsm.
In another preferred embodiment of the process, the lyophilizing step is carried out by cooling the aqueous mixture from about room temperature to about −40° C. and drying the mixture. Preferably the cooling is carried out at a cooling rate of about 1° C. per minute. Preferably the drying steps take place under vacuum, preferably a vacuum of about 100 m Torr. The primary drying step can last from about 36 hours to about 54 hours, most preferably about 48 hours. Preferably the secondary drying step is carried out by warming at a rate of 0.05° C. to 0.2° C., more preferably 0.1° C. per minute, preferably from about −40° C. to about 30° C., for a period of time between 6 and 24 hours, preferably 12 hours, and followed by another step of maintaining isothermal temperature at about 30° C. for about 6 hours prior to removing the vacuum.
In another aspect there is provided the use of a lyophilized polysaccharide scaffold composition to promote blood coagulation and wound repair in a mammal. The composition comprises at least one polysaccharide and at least one controlled rehydration agent. Preferably the at least one polysaccharide is selected from chitosan. Preferable the chitosan has a molecular weight of from about 5,000 Daltons (Da) to about 400,000 Da, more preferably from about 8,000 Da to about 350,000 Da and most preferably from about 10,000 Da to about 300,000 Da. Preferably the at least one controlled rehydration agent is selected from the group consisting of ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine and N-acetyl glucosamine. In another embodiment the at least one controlled rehydration agent is selected from the group consisting of dextran of about 2,000 Da to 20,000 Da and most preferably from about 3,000 to 8,000 Da. In a preferred embodiment, the lyophilized composition is in the form of a scaffold. In another preferred embodiment the lyophilized composition may be porous, preferably highly porous, more preferably very highly porous, most preferably ultraporous.
In another embodiment of the use, the at least one controlled rehydration agent is selected from an acid. The acid is selected to provide an optimal level of chitosan protonation state. More preferably the acid is a pharmaceutically acceptable acid. Most preferably the acid is selected from the group consisting of hydrochloric acid, lactic acid, acetic acid and combinations thereof.
In another embodiment, the lyophilized polysaccharide is in the form of a pharmaceutically acceptable acid salt. Preferably the acid is an inorganic acid, more preferably a hydrohalic acid. Most preferably the acid is hydrochloric acid. When the at least one controlled rehydration agent comprises an acid, it generates a protonation state between 70% and 100% protonation of free amine groups, preferably between 80% and 98% protonation. In one embodiment, for a chitosan having a molecular weight no more than about 10,000 Da, said protonation state is preferably between 80% and 100% protonation. In another embodiment, for a chitosan having a molecular weight greater than 10,000 Da, said protonation state is preferably between 90% and 100%.
In one embodiment, wound repair includes, but not be limited to, the processes of angiogenesis, cell chemotaxis, tissue remodeling, viscoelastic extracellular matrix deposition for joint repair, fracture repair, meniscal repair, rotator cuff repair, suppression of fibrosis, revascularization and anabolic tissue regeneration. In another embodiment, the composition is administered in a solid form to the wound site.
In another aspect there is provided a kit for wound repair in a mammal comprising a lyophilized scaffold composition comprising at least one polysaccharide and at least one controlled rehydration agent, a cutting tool, an injection tool, a microdrill or micropick and a shaping tool.
In another aspect, a lyophilized polysaccharide scaffold composition may be combined with whole blood or blood elements, preferably in vivo or in vitro followed by in vivo delivery either following combining with whole blood or blood elements, or after fibrin fiber formation, in order to introduce the composition to a bleeding channel, bleeding wound, or a bleeding surface. Preferably the bleeding channel may be created by a diverse array of surgical tools selected from the group consisting of a drill bit, a burr, an awl, a trephination needle, a K-wire, a hollow tube, a Jamshidi needle and combinations thereof. Preferably the bleeding wound is created by accidental trauma or by surgical manipulation. Preferably the bleeding surface may be generated by a tool selected from the group consisting of a shaver, a curette, a scalpel, a scraper, a knife. In a preferred embodiment, the lyophilized polysaccharide scaffold may be used to treat a bleeding wound selected from the group consisting of subchondral bone, bone, periodontal bone, meniscus, tendon insertion site, rotator cuff, tendon insertion site, skin and combinations thereof, and organs, where anabolic wound repair processes such as neutrophil and macrophage chemotaxis, stem cell chemotaxis, angiogenesis, and tissue remodeling are desired.
Further and other embodiments will become apparent to those skilled in the art.
In one aspect, there is provided a lyophilized polysaccharide scaffold composition, preferably a lyophilized chitosan scaffold composition, that spontaneously forms a hydrated microparticle dispersion after contact with blood or blood-derived fluids and stimulate anabolic wound repair processes including, but not limited to, neutrophil and macrophage migration, stem cell migration, angiogenesis, cell chemotaxis, tissue remodeling, bone resorption, woven bone repair, suppression of fibrosis, and viscoelastic extracellular matrix deposition for joint repair.
In a preferred embodiment, there is provided a solid lyophilized ultraporous chitosan scaffold which slowly rehydrates in blood, blood plasma, platelet-rich plasma, fibrin glue, or in situ in a bleeding defect, to spontaneously form a resident chitosan microparticle dispersion in the coagulum, in order to stimulate local anabolic processes including recruitment of neutrophils and macrophages, promote angiogenesis, bone remodeling, and enhance cartilage repair tissue volume when directly delivered to bleeding subchondral bone, or to promote angiogenesis in repairing meniscal tears.
The composition may be useful for local delivery of dispersed chitosan microparticles in a fibrin clot, promoting hemostasis for promoting wound remodeling, revascularization, anabolic tissue regeneration. In a further aspect, the composition forms an implant by rehydrating the solid freeze-dried scaffold ex vivo in fibrinogen-containing fluids that are subsequently made to coagulate through thrombin activation and spontaneous fibrin clot formation.
The solid chitosan scaffold composition may be administered more easily to bleeding surgical defects compared to a liquid solution or powder or flakes. The composition dissolves over time post-delivery which permits more control over the location of delivery compared to formulations that dissolve instantly or within a few seconds upon contact with blood. The composition allows for direct administration of the chitosan scaffold to an accessible surgical site which improves ease-of-use and reduces the amount of time to carry out the treatment compared to other methods that require ex-vivo manipulation. In one example, the composition permits control over the mass of scaffold administered to a bleeding surgical site compared to a liquid formulation that can spill out of the lesion site. In one aspect, the composition undergoes delayed rehydration and microparticle dispersion throughout the blood or blood-derived fluid allowing for the chitosan scaffold to become dispersed in the coagulum for efficient retention of the chitosan scaffold at the surgical site. This delayed rehydration being achieved through the use of at least one controlled rehydration agent selected from the group consisting of low molecular mass chitosan, ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine, N-acetyl glucosamine, at least one acid preferably selected from the group consisting of hydrochloric acid, lactic acid and acetic acid.
Improved control over in vivo biodegradation kinetics has unexpectedly been achieved with the composition, compared to prior art aggregated chitosan polymer implants or solid chitosan scaffold formulations that are unable to spontaneously form a microparticle dispersion after contact with blood or blood-derived fluids. Furthermore, the solid and dry chitosan scaffold composition may be kept at room temperature for an extended period of time as would be understood by a person skilled in the art without resulting in modification of the chitosan polymer chain by hydrolytic degradation.
In another aspect there is provided a process for preparing a solid polysaccharide scaffold composition comprising lyophilizing an aqueous mixture of a polymeric cation, preferably comprising chitosan, where water is a porogen occupying ≧80%, preferably ≧90% and most preferably ≧95% of the initial mass of the solution, to give a lyophilized polysaccharide scaffold with a high porosity. In a preferred embodiment, the pH of the aqueous mixture is from about 2 to about 6, most preferably from about 2 to about 5.5. The lyophilization is preferably carried out in at least 3 steps, which include at least a freezing, a primary drying, and a secondary drying step. The freezing step can be carried out by cooling the aqueous mixture under a slight vacuum, at about 600 Torr to about 400 Torr, more preferably 500 Torr, preferably from about room temperature to about −40° C. Preferably the cooling is carried out at a cooling rate of about 1° C. per minute. Preferably, the primary drying step takes place under a vacuum, preferably of about 100 mTorr. Preferably, the primary drying step takes place at constant shelf temperature, preferably at about −40° C. The primary drying step may last from about 36 hours to about 54 hours, most preferably about 48 hours. Preferably the secondary drying step is carried out by warming at a rate of 0.05° C. to 0.2° C., more preferably 0.1° C. per minute, preferably from about −40° C. to about 30° C., for a period of time between 6 and 24 hours, preferably 12 hours, and followed by another step of maintaining isothermal temperature at about 30° C. for about 6 hours prior to removing the vacuum. The vials are preferably brought to room pressure by purging with argon followed by storage at 4° C. to 25° C. The resulting lyophilized polysaccharide scaffold composition has sufficient mechanical resiliency to be shaped with a razor or biopsy punch or Jamshidi needle.
In another aspect, there is provided a lyophilized composition comprising a cationic polysaccharide, preferably chitosan, formulated with an appropriate protonation state and osmolality for spontaneous microparticle dispersion after rehydration in blood plasma. The composition is lyophilized from an aqueous mixture such that the water acts as a porogen to generate a semi-rigid mass with a very highly porous structure. The dispersion of polysaccharide as microparticles in blood or blood-derived liquids and subsequent blood coagulation is controlled by the molecular weight and protonation state of the polysaccharide solution at the time of lyophilization. Chitosan protonation is preferably from about 80% to about 100% for a chitosan of 10 kDa and less and at least about 90% to about 100% for a chitosan above 10 kDa. In one embodiment, the cationic polysaccharide is a polymeric cation, preferably chitosan, preferably present an amount of about 0.2 to about 7% weight by volume (w/v), more preferably about 0.3 to about 5% w/v and most preferably about 0.5 to about 3% w/v.
In another embodiment, the composition further comprises a variable proportion of at least one controlled rehydration agent preferably present in an amount of about 0.2 to about 10% w/v, more preferably about 0.3 to about 7% w/v and most preferably about 0.5 to about 5% w/v, the controlled rehydration agent being selected from the group consisting of a low molecular mass chitosan, ultra-low molecular mass chitosan, chitosan oligomers, monomeric glucosamine and N-acetyl glucosamine to control the delayed kinetics of in situ rehydration of polysaccharide in blood plasma. Upon rehydration the polysaccharide polymer chains spontaneously rehydrate and form dispersed microparticles at the pH and ionic strength of liquid blood or other body fluids. The composition being compatible with propagation of the intrinsic coagulation cascade and fibrin clot formation.
In a preferred embodiment, the polysaccharide is selected form chitosan having a molecular weight of from about 5,000 Daltons (Da) to about 400,000 Da, more preferably from about 8,000 Da to about 350,000 Da and most preferably from about 10,000 Da to about 300,000 Da. In a preferred embodiment, the chitosan composition may further comprise chitosan amino sugars (including but not limited to glucosamine or N-acetyl glucosamine) to permit further time-delayed rehydration of lyophilized chitosan in blood plasma or whole blood. In a preferred embodiment, if dextran is present in the composition, the dextran has a molecular weight of about 3,000 to 10,000 Da, and more preferable around 5,000 Da.
In another preferred embodiment, the composition further comprises a pharmaceutically acceptable acid salt. Preferably the acid is an inorganic acid, more preferably a hydrohalic acid. Most preferably the acid is hydrochloric acid. In one embodiment, the inorganic acid is present from about 70% to about 110% molar ratio, more preferably from about 75% to about 105% molar ratio and most preferably from about 80% to about 100% molar ratio. The preferred osmolality of the composition prior to lyophilization is between 5 and 200 mOsm.
Without being bound by theory, it is believed that the use of the composition ensures a more rapid hemostasis, and the attraction of higher numbers of wound repair cells that normally migrate to blood clots, including neutrophils and macrophages, for a longer period of time compared to a natural hematoma that degrades spontaneously within 1 to 2 weeks post-surgery. The use of the composition also indirectly promotes (1) recruitment of blood vessels and mesenchymal stem cells to wounds, (2) recruitment of osteoclasts and blood vessels to subchondral bone defects, (3) subchondral bone plate remodeling, (4) suppression of fibrosis and (5) bone-induced chondroinduction at the base of an articular cartilage lesion, key features of regenerating connective tissues, and endochondral articular cartilage regeneration. In addition, in vivo degradation kinetics are tunable by chitosan molecular mass which remains stable during storage, therefore allowing a novel and inventive way to control the degree of increased cell recruitment and post-implant time frame of blood clot amplification.
The following non-limiting examples are provided.
Sterile liquid chitosan formulations were prepared with chitosan dissolved in HCl pH 2 to 5.5 (10 kDa, 85 kDa, or 150 kDa, 80% DDA, or 10 kDa 90% DDA) with or without bulking agent or lyoprotectant (sucrose, trehalose, dextrose, sorbitol, glucosamine-HCl, N-acetyl glucosamine). Some formulations contained bulking agent-only. Other formulations contained different ratios of 10 kDa and 150 kDa chitosan. Some chitosan formulations were prepared at 80% protonation of free amine groups of glucosamine monomer and other formulations were prepared at 98% protonation of free amine groups prior to lyophilization. Some chitosan formulations contained trace rhodamine isothiocyanate (RITC) chitosan with matching molecular mass and DDA to permit tracking of chitosan particle dispersion in plasma and water. Solutions were lyophilized under aseptic conditions in glass or plastic vials using 2 distinct methods.
Lyophilization method (A): Sterile liquid formulations were lyophilized under aseptic conditions in glass vials by cooling at 1° C. per minute from 25° C. to −40° C. at about 500 Torr and then submitted to primary drying at −40° C., 100m Torr for 48 hours in a Laboratory Series PLC Freeze-Dryer (Millrock Technologies Inc), followed by a secondary drying cycle where they were gradually warmed from −40° C. to 30° C. at 100 mTorr during 12 hours then kept isothermal at 30° C. for 6 hours. The vials were then brought to room temperature and pressure, purged with argon and stored at 4° C.
Lyophilization method (B): Sterile liquid formulations at room temperature in glass vials or plastic tubes were flash-frozen or placed in a −80° C. freezer then transferred to a standard laboratory freeze-drier (Labconco FreeZone 2.5 liter freeze dry system), the condenser temperature was set to −80° C. and maximal vacuum (<0.133 mBar) for 72 hours, then the vaccum was broken and samples warmed to room temperature. Note that in a standard apparatus such as the Labconco instrument, the sample temperature cannot be controlled precisely at any step, because the sample typically has a different temperature (between 0° C. and −70° C.) than that of the condenser (−80° C.).
Physical handling test: Some scaffolds prepared by lyophilization method (A) were rigid and could be cored with a 1.5 mm inner diameter dermal biopsy punch, while others formed a dense matted scaffold with high entanglement, or fluffy consistency that could not be cored with a biopsy punch (
A clotting and chitosan particle dispersion test was carried out in a 96-well plate with 170 μL human citrated plasma (thawed from a frozen aliquot for 5 minutes at 37° C.), one 1.5 mm diameter scaffold cylinder cored or cut from a lyophilized scaffold, 10 μL 200 mM CaCl2 and 5 μL glass microbeads (10 μm Spherocell borosilicate glass beads at 10 mg/mL in ddH20). The samples were incubated for 20 minutes to 1 hour at 37° C. to permit coagulation via the contact pathway and fibrin polymerization to take place. Fluorescent images of the RITC-chitosan particles dispersed in the hybrid plasma clot were taken with an inverted fluorescent microscope. Results: All samples coagulated and formed fibrin clots (
The results of experiments 1 and 2 are shown in Tables 1 and 2, and are summarized as follows:
Formulations that passed the handling test (rigid cake, can be cored, Tables 1-3), rehydration test (category “R” in Tables 1-3) and microparticle dispersion test (category “D”, Tables 1-3) required lyophilization method (A), and included ultra-low molecular weight chitosan-HCl (10 kDa, pH 4.5 to pH 5.5) with 5 to 10 mg/mL chitosan-HCl, or 2.4 to 5 mg/mL chitosan and 10 to 50 mg/ml bulking agent, and samples with medium molecular mass chitosan-HCl (˜85 kDa, pH 2.5, <60 mOsm) at 10 or 20 mg/mL, and 85 kDa chitosan 5 mg/mL pH 4.5 with 10 mg/mL N-acetyl glucosamine bulking agent, or mixtures of 85 kDa and 10 kDa chitosan (1:1 v/v, pH 4.5).
Formulations that failed the handling test include all samples lyophilized by method (B), and samples lyophilized by method (A) with 10 kDa or 85 kDa chitosan-HCl (pH 2.5 to 5.5) at less than 5 mg/mL, 85 kDa or 150 kDa chitosan 2.5 to 10 mg/mL pH 4.5, and 85 kDa or 150 kDa chitosan 5 mg/mL with lyoprotectant (sucrose or glucosamine-HCl, 10 mg/mL).
In a pilot rabbit study (3 week endpoint to observe in situ angiogenesis and bone remodeling), sterile freeze-dried chitosan implants were created (Table 4), cored with a biopsy punch and directly implanted into 1.5 mm diameter, 2 mm deep drill holes created in a 4×5 mm full-thickness cartilage defect in the rabbit knee trochlea. Sterile chitosan scaffold cakes and lyoprotectant-only cakes were generated by controlled lyophilization method (A). Cylindrically-shaped implants were created intra-operatively using a biopsy punch to core 1.5 mm diameter cylinders from the solid cake (
Results: In vivo handling properties: It was discovered that some formulations dissolved too rapidly while other formulations dissolved in situ with desired slow and controlled kinetics. Chitosan+50 mg/mL sucrose, chitosan+50 mg/mL sorbitol, and chitosan+50 mg/mL trehalose dissolved instantly upon contact with blood and could not be deposited in a controlled fashion in the bleeding drill hole (see
Biological response: The chitosan implants were retained in the defects, as shown by the presence of residual rhodamine-chitosan tracer in the 3 week repair tissues (
Two of the freeze-dried chitosan formulations were identified with therapeutic angiogenic effects in a rabbit model using ultra-low molecular mass chitosan (formulations C5* and 010*, Table 5). However osteochondral repair in large animals is delayed compared to rabbit (Bell A D, Lascau-Coman V, Sun J, Chen G, Lowerison M W, Hurtig M B, Hoemann C D: Bone-Induced Chondroinduction in Sheep Jamshidi Biopsy Defects with and without Treatment by Subchondral Chitosan-Blood Implant: 1-Day, 3-Week, and 3-Month Repair, Cartilage 2013, 4:131-143; Bell A, Hurtig M, Rivard G E, Hoemann, CD. Effect of bone marrow surgical approach and rapidly degrading presolidified subchondral chitosan/blood implant on resurfacing of chondral defects in a sheep model. Transactions OARSI, April 2014, Paris), and requires a higher molecular weight chitosan to elicit chondrogenesis in sheep defects using presolidified chitosan-NaCl/blood implants (Bell A D, Lascau-Coman V, Sun J, Chen G, Lowerison M W, Hurtig M B, Hoemann C D: Bone-Induced Chondroinduction in Sheep Jamshidi Biopsy Defects with and without Treatment by Subchondral Chitosan-Blood Implant: 1-Day, 3-Week, and 3-Month Repair, Cartilage 2013, 4:131-143; Bell A, Hurtig M, Rivard G E, Hoemann, C D. Effect of bone marrow surgical approach and rapidly degrading presolidified subchondral chitosan/blood implant on resurfacing of chondral defects in a sheep model. Transactions OARSI, April 2014, Paris). These data suggested that an in vivo chitosan implant with a slower degradation rate is preferred for large animals to accommodate the slower osteochondral repair progression compared to small animals or to accommodate the denser subchondral bone requiring longer remodeling times. Therefore, 3 freeze-dried chitosan formulations were evaluated with higher molecular weight chitosan (85 kDa), at 3 different concentrations and 98% protonation prior to freeze-drying using Lyophilization method (A) (Table 5). Some implants were freeze-dried with rhodamine-chitosan tracer of matching molecular mass to document in vivo clearance. The study design used skeletally aged sheep, 9 years old, with N=2 sheep (day 1), N=5 sheep (3 months), and N=5 sheep (9 months). Using a small arthrotomy approach, one knee at a time, a medial femoral condyle full-thickness cartilage defect was created with a curette 10×10 mm, and then 3 vertical rows of ˜4 mm deep micro-drilled holes were created (1.5 mm drill burr diameter, 11 holes total). Each vertical row of drill holes in one knee was treated with one formulation of distinct chitosan concentration by inserting a cylinder of lyophilized implant, with a tweezers into each bleeding hole (
Results: Handling properties were found to be superior for 10 and 20 mg/m L freeze-dried scaffolds compared to 5 mg/mL chitosan scaffold as they were easily cored with a biopsy punch and retained a cylindrical shape. The 5 mg/mL scaffold was difficult to core with a biopsy punch and more difficult to implant in the bleeding osteochondral defect. Day 1 fluorescence images of treated drill holes show implant retention at day 1 for all 3 formulations, mainly at the edges of the holes (
Formulations targeted for therapeutic activity in human joints may show therapeutic effects using formulations covering those that were shown here to be effective in rabbit and sheep cartilage repair models. Formulations include a biodegradable chitosan (80% DDA, molecular weight 10 to 150 kDa) prepared as a solution at pH 2.5, 20 mg/mL and 45 to 68 mOsm, or 10 mg/mL and 25 mOsm or 5 mg/mL and 10 mOsm. The formulation may be adjusted to permit an in vivo clearance rate that is optimal for meniscal repair, rotator cuff repair, bone fracture repair, or other connective tissue repair, depending on the size of the lesion, and the physiological rate of granulation tissue formation and subsequent connective tissue formation. The formulation may also be adjusted to promote angiogenesis with only minor bone remodeling for applications involving tendon insertion site repair, and sinus bone augmentation procedures.
The scope of the claims should not be limited by preferred embodiments set forth in the examples, but should be given the broadest interpretation consistent with the description as a whole.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/CA2015/050130 | 2/20/2015 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 61942547 | Feb 2014 | US |
