Patent Application
20160346367
A sterile formulation for injectable collagenase which will have extended residence time for the drug at the therapeutic targeted area for the indication being treated, methods of use of such formulation and processes for its preparation.
At present a collagenase consisting of a 1:1 mixture of Aux I and Aux II collagenases derived from clostridium histolyticum has been approved for use as a prescription medicine in the United States under the trademark Xiaflex® and in the European Union under the trademark Xiapex®. Current approved indications are for the treatment of adults suffering from Dupuytren contraction and for adult men who have Peyronies disease. In addition, this product is under clinical and pre-clinical investigation for a number of collagen lesion based human and veterinary applications such as frozen shoulder, human lipoma, canine lipoma, cellulite and uterine fibroids.
All of the aforesaid applications require local (lesion site) injection of the collagenase product. It is highly desirable that to achieve optimum clinical benefit that the collagenase remain at the lesion site for an extended period to allow the enzyme to work to maximum extent. However, the current commercial formulation of collagenase for injection is a solution prepared by reconstituting the lyophilized collagenase powder with buffered saline for injection. Data from a pharmacokinetic study has shown that a significant amount of collagenase in the commercial formulation is found in patient urine as early as thirty minutes post injection. This indicates that the administered collagenase may be washed away easily from the injection site at the lesion or other therapeutic targeted area. It is evident that formulations which provide longer residence time at the injection site can improve the therapeutic effect of the collagenase treatment.
It is an object of the present invention to provide a formulation for injectable collagenase which will have extended residence time for the drug at the therapeutic targeted area for the indication being treated. It is a further object of the invention to provide a slow release formulation for collagenase which is compatible with the active ingredient and does not adversely affect its activity. Still a further object of the invention is to provide an injectable formulation for collagenase which can be effectively administered to a patient with a small size needle without exhibiting pregelation, which would interfere with the ability to deliver the required dose for treatment.
As used herein the term “collagenase” is meant to include one or more proteins exhibiting collagenase activity in a standard collagenase assay, preferably an Aux I and/or an Aux II collagenase derived from clostridium histolyticum, most preferably a 1:1 mixture of such Aux I and Aux II collagenases.
It has now been found and forms the basis of the present invention that a compatible, injectable formulation for providing a slow release of collagenase at the therapeutic targeted site can be prepared using specific reverse thermogeling hydrogels. Such hydrogels are fluid at room temperature but form a gel at the higher interbody temperature, which gel can entrap substantial amounts of the collagenase at the injection site in the body for extended release at the desired location.
Thermogelling hydrogels for delivery of therapeutic drugs is still a fairly new technology and there are still many problems to solve to achieve the desired objects of this invention. One problem is the injectability or syringeability problem which represents a critical issue for clinical usage. See for example, T. R. Hoare and D. S. Kohane, Polymer's 49 (2008) 1993-2007. High viscosity and premature gelation inside the needle are the two aspects of such injectability problem. It is common that the polymers solution comprising the hydrogel is viscous at a room temperature of about 24° C. The “thick” solution is a complication for the clinician who is administering the solution through a syringe. In order to improve patient acceptance of procedures involving multiple injections it is highly desired to use a small size needle in the syringe. However, when the scientific literature is reviewed it is interesting to observe that when hydrogels have been reported to have been injected into animals numerous citations indicate the use of large size syringes and needles. For example, ReGel®, a triblock copolymer has been used to inject drugs in humans using a 23 gauge needle (Anti-cancer Drugs,2007, vol 18, No 3).
Due to the thermoresponsive properties of the prior hydrogel compositions, gelation inside the needle can occur after penetration of the skin but prior to discharging the contents of the syringe thus plugging up the needle. Thus, in order to have acceptable injectability for a collagenase hydrogel formulation the formulation must demonstrate that: (1) the collagenase hydrogel solution can be handled comfortably with a 0.5 mL syringe fitted with a 28G½ needle at room temperature; and (2) the needle will not exhibit pregelation after the needle has penetrated through the skin for at least 30 seconds—thus allowing the content of the syringe to be administered under normal conditions of treatment with collagenase for injection.
It is desired that the in situ gelation of the thermosensitive hydrogel/collagenase formulation at the therapeutic targeted site will entrap at least about 70 wt % of the amount of the collegenase originally contained in the original solution in the syringe and most preferably at least 80 wt % of such collagenase. The amount of collagenase in an injectable dose for present approved indications is about 0.58 mg, although the formulation can be adapted to contain more or less collagenase for other indications which may be approved in the future. The non-entrapped portion of the administered o collagenase is available for immediate treatment of the target collagen lesion while the entrapped collagenase will be released over a period of time to allow for extended treatment from the single injection. Unlike conventional gel formulations for extended release of systemic therapeutic drugs which can have release times of several weeks or even months, the release period for the collagenase gels should not exceed a few days, preferable about two days from the time of injection. Such a regime may reduce the number of injections needed for effective treatment of the lesion with minimum risk of undesired side effects from exposure of normal tissue to collagenase thus resulting in a high level of patient acceptance of this modality of treatment.
Numerous thermosensitive hydrogels are known in the art and are commercially available. A preferred thermosensitive hydrogel for use in the formulation of the present invention is a triblock polymer of the structure PLGA-PEG-PLGA where PLGA represents poly (DL-lactic acid-co-glycolic acid) and PEG represents poly (ethylene glycol). A commercially available triblock polymer of these materials which has (Mn=1600-1500-1600) is obtainable from Daigang Bio of Jinan, China as well as from Akina, Inc. of West Lafayette, Ind. 47906, USA.
In a further preferred embodiment of the present invention thermosensitive hydrogel materials known in the art which do not meet the requirements of injectability or compatibility due to viscosity or acidic pH can be treated in solution to modify their properties by adding to their solutions a viscosity adjusting or pH adjusting amount of the compound tris (hydroxymethyl) amino methane. In this manner such hydrogel properties will be modified to allow injection through a 28G½ needle without jamming and at a neutral or slightly basic pH, will be compatible with collagenase.
A suitable collagenase formulation for non-clinical testing can be prepared by dissolving 1 mg collagenase and 1.7 mg of a polysaccharide carrier material such as lactose in 0.5 ml of 13%-15% triblock hydrogel solution, such as PLGA-PEG-PLGA with pH adjusted to a pH 8.5 by the addition of tris (hydroxymethyl) amino methane. Such resulting solution can be readily introduced into a insulin syringe through a 28G½ needle. The basic pH has been found to be a key to having an acceptable injectability. Collagenase has been found to be stable when maintained in gels formed from the recipe when held at 37° C. for at least 48 hours. Additionally, it has been found that released and entrapped collagenase from such gels have the same biological activity as the untreated collagenase.In certain embodiments where the hydrogel exhibits a sensitivity to basic conditions it is preferred that the tris (hydroxymethyl) amino methane can be added to the hydrogel solution just prior to mixing with the collagenase powder in order to minimize any risk of degradation.
In order to provide a formulation suitable for injection the hydrogel solution has to be sterilized. Any method not involving elevated temperatures or use of materials which might affect the integrity of the hydrogel may be employed. A preferred sterilization method involves filtering the hydrogel solution through a small pore filter such as, for example, a filter with pores of about 0.22 μm into a sterile, sealable container. The resulting sterile solution can be conveniently stored prior to use as a frozen stock solution. This stock solution can be thawed when needed and used as diluent to dissolve lyophilized collagenase provided before injection.
In a further embodiment of the invention the needed components for effecting treatment of a subject for a target indication can be conveniently provided to the medical professional in kit form. Such kit would contain a sterile vial containing the thermosensitive hydrogel stock solution in an amount sufficient to provide one or more injections, one or more vials each containing a therapeutic dose for the target indication of collagenase as a lyophilized powder and optionally a package insert approved by the drug regulatory authority in the jurisdiction where the kit is to be used in treating a patient. In embodiments where the hydrogel Is sensitive to extended exposure to base conditions, It Is preferable to provide the tris (hydroxymethyl) amino methane solution In a separate vial. Most preferably the vials will be store at refrigerator or frozen conditions before use.
The preparation and use of formulations of the present invention are further illustrated by reference to the Examples which follow. It should be understood that the scope and nature of the present invention are to be defined by the claims of this application and should be not limited in any way by such Examples.
Preparation of Polymer Stock Solution
A triblock polymer, poly (DL-lactic acid-co-glycolic acid)-poly (ethylene glycol)-poly(DL-lactic acid-co-glycolic acid), (PLGA-PEG-PLGA) (Mn=1600-1500-1600) was obtained from Daigang Bio., Jinan China. A 15% (w/v) polymer solution was prepared by mixing dry polymer and water at 2-8° C. The dissolution may take a few days under gentle agitation. The solution was then filtered through a 0.22 μm filter. The sterilized solution can be aliquoted and stored at −20° C. The frozen solution is preferred to be placed at refrigerator temperature overnight prior to preparing the collagenase-hydrogel solution.
Method of Polymer Dilution
The polymer solution is further diluted to 13% with water. This solution has a pH of 4. The solution is capable of forming a soft gel at 37° C. In addition to the acidic condition which causes collagenase denaturing , the13% polymer solution was also found to be viscous at room temperature. Many published results are in fact from using chilled polymer solution, normally 4° C. A temperature of 4° C. is less than ideal as a clinical working condition which normally prefers an ambient temperature. This viscosity makes it impossible to use in a syringe. Tris buffer of pH 7.5 was then used to dilute the polymer solution. The collagenase is now safe, but the polymer solution was still too thick to be handled in a syringe at room temperature. Adjusting to pH 8.5 was found to substantially reduce the viscosity of the polymer solution at room temperature. The pH 8.5 polymer solution was a clear, fluidic solution and can be handled by a syringe with a 28G½ needle.
Preparation of Collagenase/Hydrogel Solution
Collagenase/hydrogel solution may be prepared as follows: (A) add a calculated volume of sterile 0.75 M tris buffer, pH 8.5 into a sterile polymer solution (example 1); B. add a required volume of polymer solution to lyophilized collagenase powder. The final concentration of the polymer is 13% (w/v). The dissolved collagenase is preferred to be left in a refrigerator for 30 minutes prior to injection.
Many thermosensitive hydrogel solutions are viscous and pose a challenge for use in a syringe at room temperature : withdrawing, expelling air etc. especially when a small size of syringe and needle is needed. A syringe test may be performed using a small size of syringe and 28G½ needle. An acceptable polymer solution should be easily handled with a small size of syringe and 28G½ needle at room temperature. The current mode of injection of collagenase solution is by intra-lesion injection, which often requires a clinician to spend time doing needle placement before pushing the plunger. Since the needle has already entered the body, gelation may occur prior to discharging the contents of the syringe. Needle test can be performed by immersing the needle into buffer warmed to 37° C. for up to 40 seconds before pushing the plunger to release the hydrogel solution.
The syringe tests demonstrate that collagenase—hydrogel solution (0.25 mL) can be handled like collagenase-saline solution. The needle tests show that the collagenase/hydrogel can be discharged easily at body temperature.
Polymer solutions can be sterilized by filtration at 4° C. through a 0.22 μm filter.
Collagenase activity can be measured by a biological potency assay method—the SRC assay. This method uses soluble rat trail tendon collagen as a substrate. The assay is based on the method originally developed by Mallya (Mallya, S. K., et al. (1986) Anal. Biochem. 158: 334-345). The collagenase activity is measured by the amount of degraded collagen, (small peptide fragments) which is quantified by the Ninhydrin reaction. The optical density of the reaction solution (purple Ninhydrin) is measured with a spectrometer at 570 nm and compared with the ninhydrin reaction using a known amount of leucine (standard curve). The nmol peptide hydrolyzed is calculated into nmol leucine equivalent. The unit of collagenase activity was expressed as nmol leu equiv./min.
A 200 μl of collagenase/hydrogel solution was placed into a test tube with 1 mL Tris buffer (20 nM Tris(hydroxymethyl)amino methane/4 mM calcium acetate pH 7.4) pre-warmed at 37° C. The gelation occurred instantly. The test tubes were incubated for various times up to 48 hr. The collagenase potency of supernatant and gel were measured with the SRC assay. The result in Table I indicate that the collagenase is compatible with the polymer and gelation process. The results show that initially more than 80% of the collagenase is entrapped in the gel. The results also show that most of the collagenase is released from the gel in 48 hours. A SDS-PAGE test showed a similar entrapment rate and release pattern. In contrast to most slow release hydrogels, the release for the present formulation is much faster. This relative “fast” slow release is more desirable for clinical uses.
The hydrogel's compatibility is also verified with the second biological potency assay—GPA assay, a synthetic peptide substrate based assay. Carbobenzoxy-glycyl-L-prolyl-glycyl-glycyl-L-prolyl-L-alanine (zGPGGPA) is a synthetic substrate for Clostridial collagenase. This substrate is readily cleaved by Aux II collagenases (collagenase ABC II) into the two peptides; carbobenzolxy-glycyl-L-prolyl-glycine (zGPG) and glycyl-L-prolyl-L-alanine (GPA). The released free amino group on GPA is reacted with ninhydrin reagent. The optical density of purple ninhydrin reaction solution is measured with a spectrometer at 570 nm and compared with the ninhydrin reaction from to collagenase reference standard. The unit of collagenase activity was expressed as nmol leu equiv./min. This assay procedure was originally developed by W. Appel [in H. U. Bergmeyer, ed., Methods of Enzymatic Analysis; New York: Academic Press/Verlag Chemie, 1974].
A total of 0.353 mg of collagenase was mixed with 0.3 mL 13/2% triblock hydrogel solution, pH 8.5. 0.2 mL collagenase hydrogel solution was added to 1 mL 37° C. tris buffer in a test tube. The gelation occurred instantly. The test tube was placed on a rocker for 1 hr. at 37° C. . The collagenases which went through the gelation process was compared with a control collagenase using the GPA assay. The results of 51473 units/mg for the control collagenases and 51182 units/mg for the collagenase in the gel indicate that the collagenases were compatible with the polymer.
| Number | Date | Country | Kind |
|---|---|---|---|
| 201410018764.3 | Jan 2014 | CN | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US15/11296 | 1/14/2015 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 62063056 | Oct 2014 | US |
