Patent Application
20100184720
The invention relates to a sterile, injectable aqueous formulation in gel form that consists of hyaluronic acid (or one of its salts) with or without other polysaccharides of natural origin and one or more polyol(s). This injectable formulation is used in intra-articular spaces in the treatment of articular degeneration.
A joint is a junction that makes it possible to connect two bones and to give them mobility relative to one another.
Synovial joints are the most numerous joints, in particular in the limbs. In these joints, the bones are joined via a cavity that is filled with fluid that is both viscous and elastic and that is called synovial fluid.
The sinovial fluid is responsible for the good operation and the protection of joints. It consists in particular of a polysaccharide, hyaluronic acid, which imparts to the synovial fluid viscoelasticity properties that make possible, based on imposed constraints, a lubrication of the joint or an absorption of impacts.
In the case of articular degeneration such as osteoarthritis of the knee (degeneration due in particular to factors such as obesity, heredity, traumas, . . . ), the synovial fluid degrades (reduction of the concentration and the molecular weight of the hyaluronic acid), and this degradation reduces the capacity of the synovial fluid to lubricate the joint and to absorb the impacts.
Treatment by viscosupplementation consists in injecting a gel into the joint so as to replace the deficient synovial fluid. The viscosupplementation can lessen or stop the pain and contribute to restoring the mobility of the joint.
The viscosupplementation products that are currently on the market are gels that contain hyaluronic acid. These gels can be based on hyaluronic acid of animal or non-animal origin and can be cross-linked (the case of Synvisc®, Durolane®) or non-cross-linked (the case of Synocrom®, Arthrum®, Lubravisc®, Structovial®).
It is well known to one skilled in the art that the persistence of a hyaluronic-acid-based gel is low in a joint (from several hours to several days). According to Laurent, “The Chemistry, Biology and Medical Applications of Hyaluronan and its Derivatives, Wenner-Gren International Series, Volume 72,” the half-life in a rabbit's joint of a 1% hyaluronan solution is 12 hours, and that of a 0.5% Hylan B gel is 9 days.
This low persistence (kinetics of rapid resorption of gel within the joint) is explained by a degradation (by depolymerization) of the hyaluronic acid. The primary factors of degradation of the hyaluronic acid in the joint are radical degradation, thermal degradation at 37° C., and mechanical degradation (enzymatic degradation is not a significant factor of degradation in the joint). Although the therapeutic effectiveness of the viscosupplement is of longer duration than its dwell time in the joint, the persistence of a gel based on hyaluronic acid in the joint is a prominent parameter that governs the effectiveness of the product. Thus, the longer the dwell time of the hyaluronic-acid-based gel in the joint, the more effective the viscosupplementation treatment (reduction of pain, gain in mobility). Consequently, the increase of dwell time (persistence) of a gel within the joint is a capital point for increasing the effectiveness of a treatment by viscosupplementation using a hyaluronic-acid-based gel.
It is well known by one skilled in the art that the increase in the concentration of hyaluronic acid, the use of high molecular weights of hyaluronic acid and the cross-linking/grafting techniques of the hyaluronic acid make it possible to improve the persistence of a hyaluronic-acid-based gel. However, the optimization of the various parameters listed above does not seem sufficient to allow the persistence of a hyaluronic-acid-based gel to increase significantly in intra-articular spaces (the half-life, within the joint, of current viscosupplementation gels that are on the market is only several days at most).
In a development that was absolutely unexpected and surprising, it was demonstrated that:
This invention therefore consists of a sterile, injectable aqueous formulation in gel form that consists of hyaluronic acid (or one of its salts) with or without other polysaccharides of natural origin and of one or more polyol(s). This formulation, used in the treatment of articular degeneration, in some cases (see Examples 1 and 3) presents a rheology that is close to that of synovial fluid and always an increased resistance to degradation.
Example 4 shows the best resistance of a hyaluronic-acid-based gel and a polyol when the latter is subjected to a radical, thermal and mechanical degradation test. This best resistance of the gel to degradation allows a longer persistence of the gel that is injected into intra-articular spaces.
Example 5 shows the best resistance of a hyaluronic-acid-based gel and a polyol to thermal degradation. This best resistance of the gel to thermal degradation makes possible a longer persistence of the gel that is injected into intra-articular spaces and a better stability of the formulation during storage of the product before use (important point for the expiration period of the product).
Example 8 demonstrates the strong affinity between the hyaluronic acid and a polyol. Injected into the joint, the strong affinity between the hyaluronic acid and the polyol allows a better long-term resistance of the gel to degradation by a synergetic action. Actually, in the case of an injection of a polyol solution into the joint, the natural washing will quickly eliminate the molecule (=polyol) from the joint. In the case of a hyaluronic-acid-based gel with polyol, the strong affinity between the hyaluronic acid and the polyol will prevent the quick release of polyol outside of the gel (and therefore its quick elimination outside of the joint) and will thus make possible effective long-term protection of the gel by polyol against degradation.
Examples 1 and 3 show a rheology of a hyaluronic-acid-based gel and a polyol that is close to that of the synovial fluid.
The publication of MAZZUCCO, D. et al., “Rheology of Joint Fluid in Total Knee Arthroplasty Patients”; Journal of Orthopedic Research, 1157-1163, 2002, indicates that the frequency of crossover between the elastic modulus G′ and the viscous modulus G″ is equal to 0.41±0.12 Hz for an uncontaminated (non-osteoarthritic) synovial fluid of the knee. The value of this crossover frequency is confirmed by the publication of Fam et al., “Rheological Properties of Synovial Fluids,” Biorheology, 44, 59-74, 2007. In this publication, a figure has the crossover frequency between the moduli G′ and G″ of between 0 and 10 Hz for a synovial fluid that belongs to a young or old individual or else for an osteoarthritic synovial fluid.
According to one aspect of this invention, the gel that consists of an aqueous solution of hyaluronic acid (or one of its salts) with or without other polysaccharides of natural origin and one or more polyol(s) has, after sterilization, a crossover frequency fc between the elastic modulus G′ and the viscous modulus G″ that is close to 0.41 Hz. Thus, the gel has viscoelastic properties that are close to that of the synovial fluid.
As a result, according to one aspect of this invention:
According to one aspect of this invention, the crossover frequency is between 0 and 10 Hz, preferably 0.41±0.41 Hz. This kind of rheology is therefore appropriate to the mechanical constraints of joints and in particular of the knee, the hip or small joints. Consequently, it has a great advantage in the treatment of osteoarthritis by viscosupplementation of the knee or other joints.
The invention therefore relates to the use of a sterile, injectable aqueous formulation in gel form that consists of hyaluronic acid (or one of its salts) at 1-100 mg/ml with or without other polysaccharide(s) of natural origin and one or more polyol(s) at 0.0001-100 mg/ml. This injectable formulation in used in intra-articular spaces in the treatment of articular degeneration.
The hyaluronic acid is preferably obtained by biofermentation but it can also be of animal origin. Its molecular weight is 0.1 to 10×106 Da and preferably 2 to 3×106 Da.
The concentration of hyaluronic acid is between 1 and 100 mg/ml and preferably between 10 and 25 mg/ml.
The polysaccharide(s) of natural origin that can be used in combination with the hyaluronic acid is selected from among, for example, chondroitin sulfate, keratan, keratan sulfate, heparin, heparin sulfate, cellulose and its derivatives, chitosan, xanthans, alginates, and all of their respective salts.
Hyaluronic acid, just like the polysaccharide(s) of natural origin, can be cross-linked or non-cross-linked, grafted or non-grafted according to the cross-linking/grafting techniques described in the prior art.
The polyol(s) is/are selected from among, for example, glycerol, propylene glycol, sorbitol, mannitol, erythritol, xylitol, lactitol, maltitol or else cyclic oses such as glucose.
The polyol concentration is between 0.0001 and 100 mg/ml and preferably between 15 and 45 mg/ml.
The aqueous solution that is used is preferably a buffered solution. The composition of this buffer solution is selected so as to have the desired physico-chemical (pH, osmolarity) and rheological properties.
Preferably, the buffer solution that is selected is a phosphate buffer solution.
According to this invention, the formulation is sterilized by the techniques that are well known to one skilled in the art and preferably with the autoclave.
The formulation according to this invention is used by injection into the joint, and the dose that is injected can be between 0.1 and 20 ml based on the nature of the treated joint.
By way of illustration, two viscoelastic gel formulations that can be prepared according to this invention are provided below:
Examples are proposed so as to illustrate the invention but are in no way limiting of said invention. The formulations that are prepared in the following examples are gels based on sodium hyaluronate (NaHA) that are non-cross-linked or cross-linked with polyol.
The preparation of non-cross-linked or cross-linked gels is carried out according to the techniques that are well known by one skilled in the art. The sodium hyaluronate that is used to produce these gels has a molecular weight that is equal to 2.5×106 Da. In the case of the cross-linked gels, the cross-linking agent that is used is BDDE, and the definition of the cross-linking level that is used is: weight (BDDE)/weight (dry NaHA).
The incorporation of polyol in the gel is carried out by adding the necessary amount of polyol in the non-cross-linked or cross-linked gel and by mixing it with the spatula for 10 minutes (per 100 g of final gel).
The prepared gels are filled into glass syringes and then sterilized with moist heat (T=121° C.).
The rheometer that is used to carry out the rheological measurements is an AR1000 (TA Instruments) with a flat geometry of 40 mm, a gap of 1000 microns, and an analytical temperature of 37° C.
The metering of the polyols is carried out by an HPLC Ultimate 3000 (Dionex) and an ion exchange column.
Formulation A: Gel based on non-cross-linked NaHA with glycerol
The formulations A, B, C, D, E and F are isotonic and have a neutral pH.
The viscoelastic properties of the formulations A, B, C, D and E are characterized by measuring the evolution of the viscous modulus (G″) and the elastic modulus (G′) based on frequency (see
For these 5 formulations, it is noted that the crossover frequency of the modulus G′ and the modulus G″ is close to that of the uncontaminated synovial fluid.
The table below provides crossover frequency values fc for each formulation and for uncontaminated synovial fluid.
As described in this invention:
To show that the presence of a polyol in an NaHA-based gel makes it possible to reduce the degradation of the gel by a radical, thermal and mechanical action, the resistance to the degradation of NaHA-based gels with polyol (formulations of Example 1) and the resistance to the degradation of NaHA-based gels without polyol (=reference gels) were compared.
For the formulations B, C, D and E of Example 1, the NaHA-based reference gel without polyol is a non-cross-linked NaHA-based gel with 20 mg/ml of NaHA (MM=2.5×106 D, in the phosphate buffer)—formulation G.
For the formulation F of Example 1, the NaHA-based reference gel without polyol is a cross-linked NaHA-based gel with 18 mg/ml of NaHA (MM=2.5×106 D before cross-linking, in the phosphate buffer) that has a cross-linking level of 6%—formulation H.
The degradation test is carried out by adding an oxidizing agent to the gel to be tested, by homogenizing the mixture with the spatula for 1 minute, by being brought to the temperature of 37° C., and by imposing a deformation of 0.3%. The value of the parameter tan δ=G″/G′ at 0.7 Hz (characteristic parameter of the viscoelastic properties of the gel) is measured over time.
It is noted that this parameter increases over time, synonymous with a gradual breakdown of the gel. The values that are measured at t=0 and t=15 minutes for the formulations B, C, D, E, F, G and H are provided in the table below.
As described in this invention, each formulation B, C, D and E has a resistance to degradation that is significantly higher than that of the gel without polyol (formulations G). Likewise, the formulation F has a resistance to degradation that is significantly higher than that of the corresponding gel without polyol (formulations H).
Consequently, the polyols protect the gel effectively against degradation.
Two formulations are subjected to accelerated furnace aging at 40° C.:
A measurement of zero viscosity (zero-shear viscosity) and a determination of the crossover frequency fc between the elastic modulus G′ and the viscous modulus G″ is carried out at 3 times (t=0, 7 days, 26 days)
The results that are obtained are provided in the table below:
It is noted that during the accelerated aging, the loss of zero viscosity and the offsetting of the crossover frequency fc are less in the case of the formulation B (formulation according to this invention) than in the case of the formulation without polyol (formulation G).
The tested products are as follows:
For the 5 gels tested,
It is noted that only the gel according to Example 1 has a crossover frequency (0.50 Hz) that is close to that of the uncontaminated synovial fluid (0.41 Hz).
The table below combines the values of the crossover frequencies fc for the products P1 to P4 and for the formulation A of Example 1.
It is known that according to the publication of Mazzucco, D. et al. (cited above), the crossover frequency of the uncontaminated synovial fluid (0.41 Hz) is below the frequencies that are observed in the knee during walking (0.7 Hz) and running (3 Hz).
For the products P1 to P3, the crossover frequency is higher than 3 Hz, and, consequently, the products do not have strong elasticity allowing the absorption of impacts when the knee is moving.
The product P4 has a very low crossover frequency; the elastic modulus is higher than the viscous modulus over the entire frequency range of 0.1-10 Hz. Consequently, the elasticity is high when the knee is moving, but the lubrication of the joint is not very effective when the patient is at rest.
The tested products are as follows:
The degradation test is carried out according to the method that is described in Example 4.
The value of the parameter G′ at 0.7 Hz is tracked over time.
The thus obtained rheology curves are provided in
It is noted that the gel according to this invention becomes significantly degraded less quickly than the 3 commercial products tested.
So as to demonstrate the strong affinity between the hyaluronic acid and the polyol and therefore the long-term protection of the gel by the polyol, a follow-up study of the release of a polyol by dialysis has been carried out.
5 g of the formulation E (gel based on 20 mg/ml of non-cross-linked NaHA and 40 mg/ml of sorbitol—Example 1) was introduced into a dialysis membrane (No. 1) (Spectra/Pore®, MWCO: 12-14,000).
5 g of a phosphate buffer solution that contains 40 mg/ml of sorbitol was introduced into a 2nd dialysis membrane (No. 2) (Spectra/Pore®, MWCO: 12-14,000)—same dimension as the membrane No. 1.
These membranes were placed in respective bottles containing 50 g of purified water (=dialysis bath) while being stirred magnetically. Measurements of sorbitol concentration by HPLC were carried out in the dialysis baths at different times so as to track the kinetics for release of sorbitol outside of the membrane with gel or a buffer solution.
The tracking curves of the sorbitol concentration over time are provided in
The kinetics for release of sorbitol into a gel is significantly slower than in a buffer solution.
This study promotes the synergy between the hyaluronic acid and the polyol that is present in the gel: the strong hyaluronic acid/polyol affinity makes it possible for the polyol to be present within the gel over a long period, and the protection capacity of the polyol with regard to the gel makes it possible to have a strong long-term resistance of the gel against degradation.
| Number | Date | Country | Kind |
|---|---|---|---|
| 0704772 | Jul 2007 | FR | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/FR08/00948 | 7/2/2008 | WO | 00 | 3/30/2010 |
