Thermosetting neutralized chitosan composition forming a hydrogel, lyophilizate, and processes for producing the same

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THERMOSETTING NEUTRALIZED CHITOSAN COMPOSITION FORMING A HYDROGEL, LYOPHILIZATE, AND PROCESSES FOR PRODUCING THE SAME

Field of the invention

The present invention relates to an aqueous thermosetting neutralized chitosan composition forming a phosphate-free, transparent hydrogel at a temperature higher than 5°C, and to a process for producing the same.

Further, the present invention relates to a lyophilizate obtained by freeze-drying the thermosetting neutralized chitosan composition of the present invention and to a process for producing the same.

Background ofthe invention

Hydrogels are attractive for biomedical applications.

Further, hydrogels exhibiting the specific ability of increasing their viscosity with temperature, also called thermosensitive / thermoresponsive / pseudothermosetting / thermogelling hydrogels, were proved to have a facilitated application combined with an increased residence time at the site of application, and therefore may be advantageously used for drug delivery or tissue augmentation.

As known from O. Felt et al. in The Encyclopedia of Controlled Drug Delivery,

1999, said thermosensitive hydrogels may be based advantageously on polymers of natural origin, for example on chitosan which is a commercially available inexpensive polymer derived from chitin, the second most abundant polysaccharide after cellulose.

Chitosan is known as a chitin derivative obtained by partial to substantial alkaline N-deacetylation of chitin also named poly(N-acetyl-D-glucosamine), which is a naturally occurring biopolymer.

Chitosan contains free amine (-NH2) groups and may be characterized as to the proportion of N-acetyl-D-glucosamine units and D-glucosamine units, and such is expressed as the degree of deacetylation (DD) of the fully acetylated polymer chitin.

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Parameters of chitosan influencing important properties such as solubility and viscosity are the degree of deacetylation (DD) which may be understood as representing the percentage of deacetylated monomers, and the molecular weight (Mw).

Chitosan is known to be biodegradable, biocompatible, bioadhesive, bacteriostatic, and further to promote wound-healing, drug absorption, and tissue reconstruction.

Due to its above mentioned intrinsic properties, chitosan is known to have numerous cosmetic and pharmaceutical activities, and has been also widely explored for various applications through gels.

Therefore, considering the advantageous properties of chitosan, there is a continuous need to improve the properties of known thermosensitive chitosan hydrogels which are still considered as very promising for a wider range of biomedical applications.

WO-A-99/07416 (BIOSYNTHEC) discloses a pH-dependent temperature-controlled chitosan hydrogel which has thermosensitive properties at neutral pH such that it has low viscosity at low temperature but gels at body temperature.

This thermosensitive chitosan hydrogel is prepared by neutralizing a commercial chitosan having a deacetylation degree of about 80 % with mono-phosphate dibasic salts of polyols or sugars exemplified in particular by β-glycerophosphate (β-GP).

However, presence of β-GP in the hydrogel leads to the following disadvantages.

β-GP is a negatively charged entity that can react with a positively charged bioactive component, leading to its precipitation or to the disturbance of its liberation from the hydrogel.

Therefore, presence of β-GP renders chitosan^-GP hydrogels inappropriate for use with numerous drugs.

Further, the properties of this hydrogel, such as gelation time and viscosity, depend on the concentration of β-GP and are therefore limited by the solubility of β-GP.

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In particular, a high concentration of β-GP is required to have a low gelation time avoiding the rapid elimination ofthe hydrogel after its administration.

However, a high concentration of β-GP also decreases the mechanical properties of the hydrogel.

Therefore, the gelation time has to be balanced with the consistency of the hydrogel, and it is not possible to obtain gels that have both a low gelation time and a high viscosity, which would be a desirable combination of characteristics.

Also, a too high concentration of β-GP may induce the precipitation ofthe hydrogel at its administration site.

Further, said thermosensitive chitosan^-GP hydrogels were found to be turbid, thus rendering their use inappropriate for particular applications such as ocular or topical administrations.

In addition, phosphate-containing materials may be inappropriate in terms of biocompatibility (G. Molinaro et al., Biomaterials, 23:2717-2722 (2002)).

In order to overcome the disadvantages of chitosan^-GP hydrogels, it was proposed in WO-A-2005/097871 (UNIVERSITE DE GENEVE) a thermosetting neutralized chitosan composition forming a phosphate-free transparent hydrogel at a temperature higher than 5°C, said composition comprising an homogeneously reacetylated chitosan having a molecular weight of not smaller than 200 kDa, and a deacetylation degree of 30 - 60 %, neutralized with an hydroxylated base.

WO-A-2005/097871 also disclose that said composition may further comprise 1,3-propanediol to modulate the viscoelastic properties ofthe hydrogel.

However, 1,3-propanediol is neither mentioned as generally recognized as safe (GRAS), nor recognized as an additive mentioned in US pharmacopoeia,

European pharmacopoeia or Japanese pharmacopoeia so that its use is limited in biomedical applications.

Further, thermosetting neutralized chitosan compositions containing

1,3-propanediol loose their thermoresponsive properties upon lyophilization.

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In view of the continuous need to provide improved thermosensitive chitosan hydrogels for biomedical applications, the present inventors have continued their researches to overcome the disadvantages of the known thermosensitive hydrogels.

An object of the present invention is to provide an aqueous thermosetting neutralized chitosan composition forming a phosphate-free transparent hydrogel having improved properties and being acceptable for biomedical applications.

Another object of the present invention is to provide an aqueous thermosetting neutralized chitosan composition which may be stored easily and which preserves its thermogelling properties after storage.

io Still another object of the present invention is to provide an aqueous thermosetting neutralized chitosan composition having a facilitated application, for example by injection using needles or minimally invasive techniques.

These objects are achieved by the present invention.

Summary of the invention

According to the first aspect, the present invention provides an aqueous thermosetting neutralized chitosan composition (herein, also called “composition of the present invention).

According to a second aspect, the present invention provides a lyophilizate of the aqueous thermosetting composition according to the first aspect.

According to a third aspect, the present invention provides a process for producing the aqueous thermosetting neutralized chitosan composition according to the first aspect. According to the fourth aspect, the present invention provides a process for producing the lyophilizate according to the second aspect.

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According to a fifth aspect, the present invention provides the use of the composition according to the first aspect, or lyophilizate according to the second aspect.

According to the present invention, adding a complexing agent selected from polyoses and polyols derived from polyoses to a specified chitosan composition allows advantageously to provide a phosphate-free transparent hydrogel having improved properties, which is acceptable for biomedical applications and which can be easily stored.

According to another aspect, the present invention provides an aqueous thermosetting neutralized chitosan composition forming a phosphate-free transparent hydrogel at a temperature higher than 5°C, said composition comprising 0.1 to 5.0 w/w %, based on the total composition, of a reacetylated chitosan having a molecular weight of not smaller than 100 kDa and a deacetylation degree of 40 to 70 %, neutralized with an hydroxylated base, and 1 to 30 w/w %, based on the total composition, of a complexing agent selected from polyoses and polyols derived from polyoses.

According to still another aspect, the present invention provides a lyophilizate obtained by freeze-drying the aqueous thermosetting neutralized chitosan composition as described herein, except the composition containing glycerol as the complexing agent.

According to yet another aspect, the present invention provides a process for producing the aqueous thermosetting neutralized chitosan composition as described herein, which comprises the steps of: solubilizing an appropriate amount of a reacetylated chitosan having a molecular weight of not smaller than 100 kDa and a deacetylation degree of 40-70 %, in an aqueous HCI medium and cooling said acidic chitosan solution to a temperature lower than 5°C; neutralizing the cooled chitosan solution obtained in step a) by adding an aqueous hydroxylated base previously cooled to a temperature lower than 5°C

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5a to the cooled chitosan solution until the cooled solution of chitosan exhibits a pH of 6.7-7.1 ; adding an appropriate amount of a complexing agent selected from polyoses and polyols derived from polyoses during or after the solubilization as described above or before, during or after the neutralization as described above, and optionally, freezing the obtained aqueous thermosetting neutralized chitosan composition.

According to a further aspect, the present invention provides a process for producing the lyophilizate as described herein, which comprises freeze-drying the aqueous thermosetting neutralized chitosan composition obtained by the process as described herein, with the proviso that the composition does not contain glycerol as the complexing agent.

io According to a further aspect, the present invention provides a use of the aqueous thermosetting neutralized chitosan composition as described herein, as a drug delivery system, for the preparation of an injectable formulation, for the preparation of a drug delivery system and for the preparation of an injectable formulation.

Other advantages of the present invention will appear in the following description.

The present invention will be now described in a more detailed manner.

Brief description of the Figures

Figure 1 shows a device for measuring the injectability of the composition of the present invention.

Figure 2 shows the evolution of the elastic modulus G’ (storage modulus) and of the viscous modulus G (loss modulus) of the transparent hydrogel containing trehalose obtained in Example 1, as compared with the same hydrogel without trehalose, as a function of time when the temperature increases from 4 to 37°C.

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5b

Figure 3 shows the evolution of the elastic modulus G’ (storage modulus) and of the viscous modules G” (loss modulus) of the transparent hydrogel containing trehalose obtained in Example 1, after preparation (A) and after thawing (B), as a function of time when the temperature increases from 4 to 37°C.

Figure 4 shows the evolution of the elastic modulus G’ (storage modulus) and of the viscous modulus G (loss modulus) of the transparent hydrogel containing trehalose obtained in Example 1, after freeze-drying and reconstitution, as compared with the same hydrogel without trehalose, as a function of time when the temperature increases from 4 to 37°C.

io Figure 5 shows the evolution of the elastic modulus G’ (storage modulus) and of the viscous modulus G” (loss modulus) of the transparent hydrogel containing

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PCT/EP2005/013980 trehalose obtained in Example 4, as compared with the same hydrogel without trehalose, as a function of time when temperature increases from 4 to 37°C.

Figure 6 shows the evolution of the elastic modulus G' (storage modulus) and of the viscous modulus G (loss modulus) ofthe transparent hydrogel containing 1,3-propanediol obtained in Example 5 (Comparative), after preparation (A) and after freeze-drying and reconstitution (B), as a function of time when the temperature increases from 4 to 37°C.

Figure 7 shows the evolution ofthe elastic modulus G' (storage modulus) and of the viscous modulus G (loss modulus) of the transparent hydrogel containing mannitol obtained in Example 6, after freeze-drying and reconstitution, as a function of time when the temperature increases from 4 to 37°C.

Figure 8 shows the evolution ofthe elastic modulus G' (storage modulus) and of the viscous modulus G (loss modulus) ofthe transparent hydrogel containing glycerol obtained in Example 7, as a function of time when the temperature increases from 4 to 37°C.

Detailed description of the present invention

It is to be noted that in the present description and claims, the expression thermosetting in connection with the composition of the present invention means that temperature does not induce the gelation ofthe composition but acts rather as a catalyst which dramatically shortens the gelation time when risen.

It is also to be noted that in the present description, the expression hydrogel or hydrogel ofthe present invention is used instead of composition ofthe present invention when appropriate.

It is still to be noted that in the present description and claims, the term neutralized means a pH of 6.7-7.1.

According to the present invention, the aqueous thermosetting neutralized chitosan composition forming a phosphate-free transparent hydrogel at a temperature higher than 5°C comprises a reacetylated chitosan neutralized with an hydroxylated base and a complexing agent selected from polyoses and polyols derived from polyoses.

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The average molecular weight (Mw) of the reacetylated chitosan comprised in the composition of the present invention is typically not lower than 100 kDa.

Molecular weight of chitosan may be determined by asymmetrical flow field-flow fractionation (AFFF) coupled to multiangle light scattering (MALS) as reported for example by B. Wittgren and K.-G. Wahlund in Journal of Chromatography A 760:205-215(1997).

Reacetylated chitosan having a Mw typically not lower than 100 KDa is particularly appropriate for use in the present invention because it allows the formation of a thermosetting composition forming a firm hydrogel.

Preferably, the reacetylated chitosan used in the present invention has a Mw not lower than 200 kDa.

The upper limit of the Mw of the reacetylated chitosan used in the present invention depends on the amount of the reacetylated chitosan comprised in the composition of the present invention and is determined by the ease of administration, which depends on the chosen application.

Reacetylated chitosan used in the present invention must have a deacetylation degree of 40 - 70 % which means that the chitosan comprises 40 to 70 % of D-glucosamine units and 60 to 30 % of neutral N-acetyl-D-glycosamine units, respectively.

The deacetylation degree of chitosan may be determined by Nuclear Magnetic Resonance such as described in the literature by Lavertu et al., Journal of Pharmaceutical and Biomedical Analysis 32: 1149-1158 (2003).

If deacetylation degree of the reacetylated chitosan is lower than 40 %, the reacetylated chitosan becomes a polymer close to chitin that is insoluble in acidic conditions and consequently not usable in the present invention.

If deacetylation degree of the reacetylated chitosan is higher than 70 %, the reacetylated chitosan does not allow the preparation of a composition forming a phosphate-free transparent hydrogel.

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Preferably, the deacetylation degree of the reacetylated chitosan comprised in the composition of the present invention is from 45 to 65 %.

A reacetylated chitosan having a molecular weight typically not smaller than 100 kDa and a deacetylation degree of 40 - 70 % for use in the present invention may be prepared for example according to the process disclosed in WO-A-2005/097871 or may be obtained from Novamatrix (Oslo, Norway).

The amount of the reacetylated chitosan comprised in the composition of the present invention must be from 0.1 to 5.0 w/w %, based on the total composition.

An amount of reacetylated chitosan lower 0.1 w/w % does not allow the formation of a hydrogel and an amount of reacetylated chitosan higher than 5.0 w/w % induces the formation of a composition too difficult to inject.

The amount of reacetylated chitosan comprised in the composition of the present invention will be chosen depending on the Mw of the chitosan and on the aimed application.

Preferably, the amount of the reacetylated chitosan comprised in the composition of the present invention is from 0.5 to 3.0 w/w %, based on the total composition.

The amount of the complexing agent comprised in the composition of the present invention must be from 1 to 30 w/w %, based on the total composition, and will depend on the concentration and molecular weight of the reacetylated chitosan as well as on the required gelation time and degree of consistency of the hydrogel.

The amount of the complexing agent comprised in the composition of the present invention is preferably from 5 to 15 w/w %, based on the total composition.

Said complexing agent selected from polyoses and polyols derived from polyoses comprised in the composition of the present invention allows to modulate the properties of the hydrogel, such as gelation time and viscosity of the hydrogel.

In one prefered embodiment of the present invention, the complexing agent which may be used in the present invention is a polyose, more preferably a polyose selected from monosaccharides and disaccharides.

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As prefered examples of monosaccharides which may be used in the present invention, there may be cited D-glucose (also called dextrose), fructose and tagatose, which are known as excipients for pharmaceutical compositions according to European, US or Japanese pharmacopoeias.

As prefered examples of disaccharides which may be used in the present invention, there may be cited trehalose, sucrose, maltose and lactose which are known as excipients for pharmaceutical compositions according to European,

US or Japanese pharmacopoeias, with trehalose being particularly prefered.

As other examples of polyoses which may be used in the present invention, there may be cited polysaccharides selected from polydextose and amylose which are known as excipients for pharmaceutical compositions.

In another prefered embodiment of the present invention, the complexing agent which may be used in the present invention is a polyol derived from polyose (also called sugar alcohol) selected from glycerol, mannitol, sorbitol, xylitol, erythritol, lactitol and maltitol, which are known as excipients for pharmaceutical compositions according to European, US or Japanese pharmacopoeias, with glycerol being particularly prefered.

The compositions of the present invention may be freezed for storage while preserving their thermogelling properties and have to be thawed at 4°C before their use.

Further, the compositions of the present invention, except those comprising glycerol as the complexing agent, may be advantageously freeze-dried to obtain a lyophilizate for facilitated storage and distribution, and reconstituted by the addition of cooled water to the lyophilizate under stirring at 4°C before their use, while preserving their thermogelling properties.

The composition of the present invention may be prepared according to a process forming part of the present invention.

in step a) of said process, the reacetylated chitosan having a molecular weight typically not smaller than 100 kDa, preferably not smaller than 200 kDa, a deacetylation degree of 40 - 70 %, preferably 45 - 65 %, is solubilized in an

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PCT/EP2005/013980 aqueous HCI medium and after complete dissolution of chitosan, the temperature of the chitosan solution is cooled down to a temperature lower than 5°C, for example in an ice bath.

Then, in step b) of said process, the pH of the cooled chitosan solution is neutralized until the pH 6.7-7.1, preferably pH 6.8, by adding dropwise, under stirring at a temperature lower than 5°C, the required amount of an aqueous solution containing a hydroxylated base previously cooled to a temperature lower than 5°C.

A higher pH is not appropriate since it would induce the precipitation of chitosan.

According to said process, the hydroxylated base used for neutralization is preferably NaOH.

Inadequate stirring or too fast addition of aqueous hydroxylated base induces the precipitation of the chitosan.

In step c) of said process, the complexing agent selected from polyoses and polyols derived from polyoses is added during or after the solubilization step a), or before, during or after the neutralization step b).

It is pointed out that the description referring to chitosan, complexing agent and amounts thereof in connection with the composition of the present invention also applies in connection with the process of the present invention.

The process for preparing the composition of the present invention may further comprise, if required, a step of sterilizing the reacetylated chitosan before the step a) of solubilization. To obtain a sterile hydrogel, the preparation is performed under aseptic conditions (e.g. under a laminar flow) and every added solution is previously filtered through a 0.22 pm filter or steam-sterilized.

For example, sterilization may be performed by radiation or ideally by steam sterilization of reacetylated chitosan suspended in water, as described by Yen (Yen S.F. et al., 1998, US-A-5,773,608).

The process for preparing the composition of the present invention may further comprise, if required a step of freezing said composition for facilited storage.

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In this case, the freezed composition has to be thawed at 4°C before its use.

In a particularly prefered embodiment, the process according to the present invention may be completed by further freeze-drying the composition of the present invention, except the composition ofthe present invention containing glycerol as the complexing agent, to obtain a lyophilizate forming part ofthe present invention.

Said lyophilizate may be conveniently stored and distributed for medical use, and may be reconstituted by the addition of cold water under stirring at 4°C.

When the temperature of the thermosetting neutralized chitosan composition of the present invention is increased, for example after administration, thermogelation occurs leading to the formation of a phosphate-free, transparent firm hydrogel. The higher is the temperature, the shorter is the gelation time.

According to the present invention, the composition ofthe present invention may be advantageously used as a drug delivery system and in view of its specific properties, may be advantageously used for the preparation of an injectable formulation.

Further, since the lyophilizate ofthe present invention preserves its thermogelling properties after reconstitution, it may be advantageously used for the preparation of a drug delivery system and for the preparation of an injectable formulation.

In order to demonstrate the improved elastic properties ofthe phosphate-free transparent chitosan hydrogels ofthe present invention, rheological measurements of various hydrogels according to the present invention and comparative hydrogels were performed according to the following method, unless otherwise indicated.

Viscoelastic properties of hydrogels were determined immediately after preparation ofthe hydrogels using a Rheostress 1 (Haake, Karlsruhe, Germany) using a cone/plate device (diameter 60mm, angle 4°). Temperature was controlled with a thermostatic bath Haake DC 30 and a cooling device Haake K10 (Haake, Karlsruhe, Germany) coupled with the rheometer. Hydrogels were placed between the cone and plate (cooled down at 4°C) and measured after 10 minutes. All measurements were performed in the linear viscoelastic range and G' (storage modulus) and G (loss modulus) were determined under a constant deformation

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PCT/EP2005/013980 (γ = 0.05) at 1 .OOHz for 180 minutes. The temperature was increased from 4 to 37°C at 6.6°C/min over the first 5 minutes, and maintained at 37°C over the following 175 minutes. Evaporation of water leading to drying of hydrogels was minimized by use of a cover surrounding the cone/plate device.

The following hydrogels have been tested :

(1) the hydrogel of the present invention obtained in Example 1, containing 2 w/w % of chitosan (DD=47 %) obtained from Novamatrix and 8 w/w % trehalose, and the comparative hydrogel without trehalose (see Figure 2);

(2) the hydrogel of the present invention obtained in Example 1, containing 2 w/w % of chitosan (DD=47 %) obtained from Novamatrix and 8 w/w % trehalose, after preparation and after freezing-thawing according to Exemple 2 (see Figures 3A and 3B);

(3) the hydrogel of the present invention obtained in Example 1, containing 2 w/w % of chitosan (DD=47 %) obtained from Novamatrix and 8 w/w % trehalose, after freeze-drying and reconstitution according to Example 3, and the comparative hydrogel without trehalose (see Figure 4);

(4) the hydrogel of the present invention obtained in Example 4, containing 0.9 % w/w of chitosan (DD=61 %) obtained according to Preparation Example 1, and 5 w/w % trehalose, and the comparative hydrogel without trehalose (see Figure 5);

(5) a comparative hydrogel obtained in Example 5 (Comparative), containing w/w % chitosan (DD 47 %) obtained according to Preparation Example 2 and 10 w/w % 1,3-propanediol, after preparation and after freeze-drying and reconstitution (see Figures 6A and 6B);

(6) the hydrogel of the present invention obtained in Example 6, containing 0.9 w/w % chitosan (DD=61 %) obtained according to Preparation Example 1, and 5 w/w % mannitol, after freeze-drying and reconstitution (see Figure 7);

(7) the hydrogel of the present invention obtained in Example 7, containing w/w % chitosan (DD 47 %) obtained from Novamatrix and 10 % glycerol, and the comparative hydrogel without glycerol (see Figure 8).

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Figures 2-8 show the evolution of the elastic modulus G' (storage modulus) and of the viscous modulus G (loss modulus) of the tested hydrogels as a function of time when temperature increases from 4 to 37°C. The onset of incipient formation of the gel network, which defines the gelation time, is given by the time of crossover of G' and G.

As shown in Figure 2, addition of a polyose such as trehalose according to the present invention increases the G' and G values of the hydrogel as compared with the same hydrogel without trehalose.

Figure 3A shows the viscoelastic properties of the hydrogel just after its preparation (as reported in Figure 2) while Figure 3B shows the viscoelastic properties of the same hydrogel after freezing and thawing.

As shown in Figure 3B, thermogelling properties of the composition of the present invention are maintained after freezing and thawing.

Figure 4 shows the viscoelastic properties of the hydrogel reported in Figure 2 after freeze-drying and reconstitution.

As shown in Figure 4, thermogelling properties of the composition of the present invention are maintained after freeze-drying and reconstitution.

As shown in Figure 5, the composition of the present invention containing trehalose shows a gélification point of 30 minutes, whereas the same formulation containing no trehalose forms a gel after 150 minutes.

As shown in Figures 6A and 6B, the comparative composition containing 1,3-propanediol forms an hydrogel when the viscoelastic properties are measured after its preparation (Figure 6A) but does not preserve its thermogelling properties after lyophilization and reconstitution as indicated by the absence of a gélification point in Figure 6B.

As shown in Figure 7, the composition of the present invention containing mannitol preserves its thermogelling properties after lyophilization and reconstitution, as indicated by the presence of a gélification point.

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As shown in Figure 8, the composition ofthe present invention containing glycerol forms an hydrogel, as indicated by the presence of a gélification point whereas the same formulation containing no glycerol shows no gélification point after 180 minutes.

The following examples are intended to illustrate the present invention. However, they cannot be considered in any case as limiting the scope of the present invention.

EXAMPLES

In the following examples, the deacetylation degree of chitosans was determined by Nuclear Magnetic Resonance (NMR) such as described in the literature by Lavertu et al., Journal of Pharmaceutical and Biomedical Analysis 32: 1149-1158 (2003).

The molecular weight of chitosans was determined by asymmetrical flow field-flow fractionation (AFFF) coupled to multiangle light scattering (MALS), as follows :

Fractionation ofthe chitosan solution (2mg/ml in acetate buffer pH 4.5) was performed in a trapezoidal channel, 26.5 cm in length and 350 gm in height, connected to an Eclipse F system (Wyatt Technology Europe, Dernbach, Germany). The bottom of the channel was lined with a regenerated cellulose membrane with a 10 kDa cut-off (Microdyn-Nadir GmbH, Wiesbaden, Germany). The elution medium consisted of acetate buffer pH 4.5. The channel flow was set to 1 ml/min and the injection flow to 0.2 ml/min. The separation started with a focus flow of 1 ml/min for 3 minutes and was followed by a cross flow of 0.2 ml/min for 15 minutes.

A Dawn EOS multi-angle light scattering detector (Wyatt Technology, Santa Barbara, USA) and a refractive index (RI) detector (Waters differential refractometer, Milford, MA, USA) were coupled online with the field-flow fractionation channel. The light scattering detector was equipped with a GaAs laser (wavelength: 690 nm) and eighteen detectors. Scattered light was collected at angles comprised between 14 and 163 degrees. The RI detector was calibrated with sodium chloride. Data were collected and

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PCT/EP2005/013980 analysed with the Astra version 4.90.08 software, using a refractive index increment (dn/dc) of 0.153 ml/g.

In the following examples, injectability of some compositions was determined with a device composed of a vertical support for a 1.0 ml luer lock syringe filled with the hydrogel at 3°C and a pan resting on the piston of the syringe as shown in Figure 1. A 27G^1/2 x 0.5 inches needles was fixed on the syringe which was positioned in the support. A mass (500 gr or 1 kg) was placed on this pan and the time necessary for the composition to be expelled from the syringe was measured.

In the following Examples 1-3 and 7, the reacetylated chitosan used for the preparation of the hydrogel is a reacetylated chitosan obtained from Novamatrix (batch FU-507-03), with a DD of 47 % (measured by NMR) and an average molecular weight (Mw) of 3600 kDa (measured by AFFF-MALS).

In the following Examples 4 and 6, the reacetylated chitosans used for the preparation of the hydrogels are reacetylated chitosans prepared according to Preparation Example 1.

In the following Example 5, the reacetylated chitosan used for the preparation of the hydrogel is reactetylated chitosan prepared according to Preparation Example 2.

Preparation Example 1

Preparation of a reacetylated chitosan Fagal Lot 21 having a DD of 61 % according to the method disclosed in WO-A-2005/097871

25.5 gr of chitosan flakes (Sigma-aldrich, Saint Louis, Missouri, USA, product number 41,941-9, batch 14418LB) were dissolved in 1 liter of a solution of acetic acid 10% and methanol (50/50) for one hour under stirring. 550 ml of methanol were added. After 2 hours stirring, the mixture was filtered through a 100 pm filter to eliminate insoluble particles. The viscous solution was then dialyzed (Spectra/Por® 1 Dialysis Membranes 6,000 - 8,000 MWCO, n°132665, Spectrum Laboratories, Rancho Dominguez, USA) against deionized water for 72 hours, with daily change of the water. The solution was then filtered through a 5 pm filter.

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Under stirring, 400 ml of NH₄OH 0.2M/methanol (50/50) were added to induce precipitation. After 1 hour stirring, the suspension was filtered through a 100 pm filter. The precipitate was washed with methanol until neutral. The purified chitosan obtained was dried in the presence of Silicagel, under vacuum, at room temperature and protected from light.

g of this purified chitosan were dissolved in 500 ml acetic acid 10% / methanol (50/50). The mixture was stirred for 1 hour and allowed to stand overnight. 400 ml of methanol were added. The solution was stirred for several hours and allowed to stand overnight. 150 ml of methanol were added and the chitosan solution was cooled down to a temperature lower than 5°C using an ice bath. A solution made of 2.4 ml acetic anhydride and 200 ml methanol was cooled down to a temperature lower than 5°C and added dropwise to the chitosan solution, under vigorous mechanical stirring. This solution containing homogeneously reacetylated chitosan was kept under stirring at a temperature lower than 5°C for one hour to ensure complete reaction, and allowed to stand overnight at room temperature. To eliminate salts produced during reacetylation and to further eliminate insoluble particles, this viscous solution was dialyzed against deionized water for 12 days (same dialysis membranes as above) with daily change ofthe water. The chitosan viscous solution was then filtered through a 5 pm filter. 200 ml of NH4OH 0.2M / methanol (50/50) were added under stirring to induce chitosan precipitation. After 4 hours stirring, the chitosan was passed through a 100 pm filter and washed with methanol. Finally, the homogeneously reacetylated chitosan was dried in the presence of Silicagel, under vacuum, at room temperature and protected from light.

The obtained reacetylated chitosan had a DD of 61 % (measured by NMR) and an average molecular weight (Mw) of 7900 kDa (measured by AFFF-MALS).

Preparation Example 2

Preparation ofa reacetylated chitosan Fagal Lot 25 having a DD of 47 % according to the method disclosed in WQ-A-2005/097871

Chitosan flakes (Sigma-aldrich, Saint Louis, Missouri, USA, product number 41,941-9, batch 14418LB) were purified as in Preparation Example 1. Chitosan

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PCT/EP2005/013980 was then reacetylated with a solution made of 2.0 ml acetic anhydride and 200 ml methanol according to the same procedure as in Example Preparation 1 .

The obtained reacetylated chitosan had a DD of 47 % (measured by NMR).

Example 1

Preparation of a composition according to the present invention, containing % w/w of reacetylated chitosan (DD=47 % rmn) provided by Novamatrix and w/w % trehalose

700 mg of reacetylated chitosan provided by Novamatrix (batch FU-507-03), with a DD of 47% (measured by RMN) were autoclaved in suspension in water at a concentration of 4 % (w/w). 145 pi HCI were added and the suspension was kept under stirring for 18 h at room temperature to allow complete chitosan solubilization. 3.09 g of trehalose were solubilized in 6.5 mi NaOH 0.15M. This solution was cooled down in an ice bath and added dropwise under stirring to the cooled down chitosan solution. The pH ofthe gel was then adjusted to 6.8 by dropwise addition of cooled down diluted NaOH. Finally, cold water was added to obtain a total mass of 35 g. The transparent hydrogel obtained showed an increase of its viscoelastic behaviour following time at 37°C, as illustrated in Figure 2 and Figure 3A and had a gelation of time of 111 min. The injectability measurement gave 30 seconds with a kilogram mass.

Example 2

Freezing-thawing the hydrogel obtained in Example 1 gr of the preparation of Example 1 was frozen in liquid nitrogen and kept at -20°C. It was then thawed at 4°C before its rheological properties were determined. As shown in Figure 3B, the thermogelling properties were maintained.

Example 3

Freezing-drying the hydrogel obtained in Example 1 gr ofthe preparation of Example 1 was frozen in liquid nitrogen and kept at -20°C before being lyophilized for 24 hours with an Edwards Modulyo Freeze dryer (plate at -50°C, vacuum of 10'¹ mbar). The lyophilizate obtained was reconstituted by the addition of cold water under stirring, at 4°C. As shown in Figure 4, the thermogelling properties were maintained.

CA 02634479 2008-06-20

WO 2007/073749

PCT/EP2005/013980

Example 4

Preparation of a composition according to the present invention, containing

0.9 % w/w of reacetylated chitosan Fagal lot 21 (DD=61 % _RMn) obtained according to the Preparation Example 1 and 5 w/w % trehalose

270 mg of reacetylated chitosan prepared according to Preparation Example 1 and having a DD of 61% (measured by RMN) were solubilized in 15 ml HCI 0.1 N under stirring for 18 hours at room temperature. 1.66 g of trehalose dihydrate were solubilized in 8 ml NaOH 0.15M. This solution was cooled down in an ice bath and added dropwise under stirring, to the cooled down chitosan solution. The pH of the gel was then adjusted to 6.8 by dropwise addition of cooled down diluted NaOH. Finally, cold water was added to obtain a total mass of 30 g. The transparent hydrogel obtained showed an increase of its viscoelastic behaviour following time at 37°C, as illustrated in Figure 5. The formulation containing trehalose showed a gélification point after 30 minutes, whereas the formulation containing no trehalose formed a gel after 150 minutes. The injectability measurement gave 30 seconds with a 500 gr mass.

Example 5 (Comparative)

Preparation of a comparative composition containing 1 % w/w of reacetylated chitosan Fagal lot 25 (DD=47 % rmn) obtained according to the Preparation

Example 2 and 10 w/w % 1,3-propanediol

200 mg of reacetylated chitosan prepared according to Preparation Example 2 and having a DD of 47% (measured by RMN) were solubilized in 10 ml HCI 0.1 N under stirring for 18 hours at room temperature. 2 g of cooled down 1,3-propanediol were added to the solubilized chitosan. The pH of the gel was then adjusted to 6.8 by dropwise addition of cooled down diluted NaOH. Finally, cold water was added to obtain a total mass of 20g. The transparent hydrogel obtained showed an increase of its viscoelastic behaviour following time at 37°C, as illustrated in Figure 6A.

When frozen (at -80°C), lyophilized (for 24 hours) and reconstituted with cold water under stirring at 4°C, the preparation obtained was not any longer injectable (27G^1/2, a kilogram mass) in the injectability measurement test. Moreover, it did not present any thermogelling properties, as shown in Figure 6B.

CA 02634479 2008-06-20

WO 2007/073749

PCT/EP2005/013980

Example 6

Preparation of a composition according to the present invention, containing

0.9 % w/w of reacetylated chitosan Fagal lot 21 (DD=61 % _RMn) obtained according to the Preparation Example 1 and 5 w/w % mannitol

630 mg of the reacetylated chitosan obtained according to Preparation Example 1 were solubilized in 35 ml HCI 0.1 N under stirring for 18 hours at room temperature. This chitosan solution was cooled down to around 5°C before adding 3.5 g of mannitol. The pH of the gel was then adjusted to 6.8 by dropwise addition of cooled down diluted NaOH. Finally, cold water was added to obtain a total mass of 70 g. 10 g of this preparation were frozen in liquid nitrogen and kept at -20°C before being lyophilized for 24 hours with an Edwards Modulyo Freeze dryer (plate at -50°C, vacuum of 10'¹ mbar). The lyophilizate obtained was reconstituted by the addition of cold water under stirring, at 4°C. The transparent hydrogel obtained showed an increase of its viscoelastic behaviour following time at 37°C, with a gelation time of 1 hour, as illustrated in Figure 7.

Example 7

Preparation of a composition according to the present invention, containing % w/w of reacetylated chitosan (DD=47 % _RMn) provided by Novamatrix and w/w % of glycerol

700 mg of reacetylated chitosan obtained from Novamatrix were autoclaved in suspension in water at a concentration of 4 % (w/w). After cooling down the suspension at room temperature, 145 μΙ HCI were added and the mixture was kept under stirring for 18 h to allow complete chitosan solubilization. The chitosan solution was cooled down to around 5°C using an ice bath and 3.5 g of cooled down glycerol were added. The pH of the gel was then adjusted to 6.8 by dropwise addition of cooled down diluted NaOH. Finally, cold water was added to obtain a total mass of 35 g. The transparent hydrogel containing glycerol showed an increase of its viscoelastic behaviour following time at 37°C with a gelation time of 135 minutes, as illustrated in Figure 8, whereas the formulation containing no glycerol showed no gélification point after 180 minutes.