The therapeutic agent (naproxen, ibuprofen or aspirin) containing gel was prepared by dispersion of naproxen powder 0.4 gm in glycerol (5% w/w) using a mortar and a pestle following the earlier reported generic protocol [27] . Ten milliliters of glacial acetic acid (3% w/w) was then added with continuous mixing and finally chitosan:vitamin C polymer was spread on the surface of the dispersion and mixed well to form the required gel. The strength of the prepared gel (10 gm) is 0.4 g (naproxen, ibuprofen or aspirin) in each gram of the base. The

summary of the newly prepared materials was presented in Table 1.

Bioadhesion studies were done using chatillon apparatus for force measurement [22] . This method determines the maximum force and work needed to separate two surfaces in intimate contact [22] . The hydrogels (0.1 g) were homogeneously spread on a 1 cm² glass disk and then the disks were fixed to the support of the tensile strength tester using double side adhesive. The gel was brought into contact with the commercially available band aid, in order to simulate the skin attachment or the contact with slice of dentin was established in order to imitate adhesion of the gel to the tooth structure, after a preset contact time (1 min) under contact strength (0.5 N) the 2 surfaces were separated at a constant rate of displacement (1 mm/s). The strength was recorded as a function of the displacement, which allowed to determine the maximal detachment force, Fmax, and the work of adhesion, W, which was calculated from the area under the strength-displacement curve.

The procedure for the investigation was adapted from the literature [23] . Flavonoids in propolis hydroalcoholic extracts were expressed as quercetine equivalent. Quercetine (Sigma, Germany) was used to make the calibration curve (standard solutions of 6.25, 12.5, 25.0, 50.0, 80.0 and 100.0 g·mL⁻¹ in 80% ethanol (V/V)). 0.5 mL of a product (ethanolic solutions of propolis) was mixed with 1.5 mL 95% ethanol (V/V), 0.1 mL 10% aluminum chloride (m/V), 0.1 mL of 1 mol·L⁻¹ potassium acetate and 2.8 mL water. A volume of 10% (m/V) aluminum chloride was substituted by the same volume of distilled water in blank. After incubation at room temperature for 30 min, the absorbance of the reaction mixture was measured at 415 nm.

One gram of the prepared gels was accurately weighed and dispersed in 10 mL of purified water. The pH of the dispersions was measured using a pH meter (HANNA instruments, HI8417, Portugal).

The release study was carried out with USP dissolution apparatus type 1, Copley UK, slightly modified in order to overcome the small volume of the dissolution medium, by using 100 mL beakers instead of the jars. The basket of the dissolution apparatus (2.5 cm in diameter) was filled with 1 gm of asprin gel on a filter paper. The basket was immersed to about 1 cm of its surface in 50 mL of phosphate buffer pH 6.8, at 37˚C ± 0.5 and 100 rpm [24] . Samples (2 mL) were collected at 0.25 - 24 hours hours [25] and were analyzed spectro-photometri- cally by U.V. Spectrophotometer (Cintra 5, GBC Scientific equipment, Australia) at λ max 275 nm (aspirin), λ max 264 nm (for ibuprofen), and λ max 260 nm (for naproxen) [26] . Each sample was replaced by the same volume of phosphate buffer pH 6.8 to maintain its constant volume and sink condition [27] .

Where P is propolis additive, A is aspirin additive, N is the naproxen, I is ibuprofen. Hydrogels containing chitosan:vitamin C (5:1) (5%) are synthesized and characterized.

The samples were prepared by freezing in liquid nitrogen for 10 min, and then were freeze-dried for 24 h. The prepared samples were fractured in liquid nitrogen using a razor blade. The fractured samples were attached to metal stubs, and sputter coated with gold under vacuum for SEM. The interior and the surface morphology were observed in scanning electron microscope (SEM, Hitachi S4800, Japan).

Stability of the gel formulations was also investigated. The organoleptic properties (color, odor), pH, drug content, and release profiles of the gels stored at 20˚C were examined on days (0, 15, 30 and 178) [27] .

A known weight functionalized chitosan containing dry gels were immersed in pH 4.0, pH 9.0 buffer solutions, respectively, and kept at 25˚C for 48 h until equilibrium of swelling had been reached as previously described [27] . The swollen gels were taken out and immediately weighed with microbalance after the excess of water lying on the surfaces was absorbed with a filter paper. The equilibrium swelling ratio (SR) was calculated using the following equation:

where W_s and W_d are the weights of the gels at the equilibrium swelling state and at the dry state, respectively [28] . Experiments were repeated in triplicate for each gel specimen and the mean value calculated.

Extracted non-carious, intact, human molars stored in water containing a few crystals of thymol at 4˚C were used within two months using protocol previously described by us [27] .

80 teeth samples (each containing 2 studs) prepared and divided into 10 groups of 8 each, A-N (Table 2) and stored in a solution of artificial saliva. These groups were then treated as outlined in Table 2. After 24 hours one stud of each tooth was tested for shear bond strength and the other one after 3 months. An Instron Universal Testing Machine at a crosshead speed of 0.5 mm/minute was used to test the de-bonding strength. All data tests were analyzed using the non-parametric ANOVA test.

On the basis of calibration curve for standard flavonoids, the concentration of these bioactive compounds in the hydroalcoholic extracts of the propolis sample used in the study was assessed. The content of flavonoids of the

propolis was 1.23% ± 0.35%, which is consistent with the previously reported values for a hydroalcoholic extracts of the propolis in the literature [28] . The flavonoid content of the propolis extracts is the major contributing factor in biological activity of the propolis. The biological effects of flavonoids can be subdivided into 4 categories: a) binding affinity to biological polymers, b) binding of heavy metal ions, c) catalyst of electron transport and d) ability to scavenge free radicals [29] . The proposed mechanism of the propolis and its ability to mediate the inflammatory response in vivo have been previously explored in some details and suggested that the healing properties of propolis can be directly correlated with anti-oxidant potential as well as anti-inflammatory properties of flavonoids [30] . The work is currently on the way in our laboratories to evaluate the mechanism in vitro and in vivo in great details.

The SEM images were obtained to characterize the microstructure of the freeze-dried naproxen composite gels and are presented in Figure 1. It was thought that the micro-porous structure of the gels could lead to high internal surface areas with low diffusional resistance in the gels. The surfaces of the gels were also presented (Figure 1). The “skin” of the gels can be seen, and the collapse of the surface pores may be due to freeze-drying process.

The hydrogels remain in the cylindrical form after swelling. Compared with dry state hydrogels, the swollen state hydrogel volume displays significant increases and are summarized in Figure 2.

Equilibrium swelling ratio (SR) of hydrogels exerts an influence on their release rates. The reduction in equilibrium swelling capacity is due to the formation of a tight network structure in high content. Environmental pH value has a large effect on the swelling behavior of these gels. From Figure 2, it is clear that the SR value increases with the increase of pH. Such pH dependent properties of the hydrogels come from the polyelectrolyte nature of chitosan segments in the hydrogel network. Namely, when the pH value of the buffer solution (pH 9.0) was far higher than the isoelectric point (PI) of the hydrogels prepared, the carboxyl groups were de-protonized to carry negative charges, which made molecular chains repulsed to each other. The network became looser and it was easy for the water molecules to diffuse into the cross-linked network. Additionally chitosan:vitamin C host:guest complex represents the additional benefit of the expanding the functionality of these materials and the in depth investigation of the mechanism is currently under investigation in our laboratories and will be reported in due cause.

Figure 3 gives the shear bond strength values (MPa) after 24 hours.

Mean shear bond strength values and difference between the groups are summarized in Figure 3 for bonding to dentin after 24 hours and in Figure 4 for bonding after 3 month. In general there was an increase in bond strength of the dentin treated with the antioxidant (chitosan:vit C complex) containing hydrogels compared to the bond strength of the conventionally bonded teeth. An increase in the shear bond strength was also previously reported [31] for chitosan-vit C, chitosan/vit C-aspirin, chitosan-vit C-aspirin-propolis, chitosan-vit C-naproxen, chitosan-vit C-naproxen-propolis, chitosan-vit C-ibuprofen and chitosan:vit C:ibuprofen:propolis. Interestingly the increase in bond strength was also observed in the groups of hydrogen peroxide exposed samples suggesting that there additional benefits associated with chitosan:antioxidant system are in need of further investigations [31] .

The results of this study suggests that the optimum results for the strengthening of dentin can be achieved throughout the immediate treatment with antioxidant:chitosan:vitamin C “host:guest” complex with the increase of dentin bond strength. The additional advantage of the system may suggest that, antioxidant release from chitosan gel depends on the physical host:guest structure as well as pH properties and flexibilities of the material. Antioxidant release occurs through the pores of the low polymer concentration while chitosan concentration increment resulted in more cross-linking of the network structure; consequently slower antioxidant release from the gel base was achieved and there for weaker adhesive properties of the materials such as Gel 1 in case of groups [32] -[34] . The additional benefit of using chitosan:antioxidant system as a bonding/pre-bonding to

(a) (b)

Chit/Vit C/Ib/Propolis Chit/Vit C/Ib

(a) (b)

(c) (d)

Chit/Vit C/Nap/Propolis Chit/Vit C/Nap

(c) (d)

(e) (f)

Chit/Vit C/Asp/Propolis Chit/Vit C/Asp

(e) (f)

Figure 1. SEM photographs of interior morphology of the selected gels under investigation for (a) Gel 2, (b) Gel 3, (c) Gel 4, (d) Gel 5, (e) Gel 6, (f) Gel 7.

enamel and dentin system lies in its ability to show favorable immediate results in terms of bonding effectiveness as well as the durability of resin-dentin bonds for a prolonged time (up to 6 months) [27] [34] . It is well documented that the hydrostatic pulpal pressure, the dentinal fluid flow and the increased dentinal wetness in vital dentin can affect the intimate interaction of certain enamel and dentin adhesives with dentinal tissue [27] [34] [38] . Therefore the newly developed chitosan:antioxidant (combination of vitamin C and propolis) systems, are supporting our earlier reported results [27] be able to address the shortfalls affecting the long-term bonding performance of modern adhesives and addresses the current perspectives for improving bond durability of con- ventional adhesive systems.

The in vitro release of therapeutic agent such as (naproxen, ibuprofen and aspirin) from chitosan:vitamin C hydrogelsgels. The cumulative release studies as shown in Figures 5-7. Its becomes apparent that the influence of chemical structures of antioxidants such as vitamin C and propolis have significantly improved the release of naproxen, Ibuprofen and asprin from the hydrogels. The mechanism of this interaction is currently under investigations in our laboratories.

Stability of various conventional antioxidants in the newly designed drug delivery system during storage is an important factor to determine whether chitosan-coated nano-size delivery vehicle can protect various conventional antioxidants. So the stability of the microencapsulated antioxidants has been measured by UV absorbance. Stabilities of microencapsulated antioxidants have been compared and after 6 month of storage at 24˚C, the stability of antioxidant-molecular carrier vehicle was over 95%. This indicated that the antioxidant had been protected by the molecular carrier such as chitosan:vitamin C complex. Important to note that performance of the antioxidant was enhanced by the presence of the chitosan, which is a very interesting point in itself as the synergism in increased stability and lower concentration of the active antioxidant wit the same or even higher antioxidant capacity can lead to a development of broad range to novel functional drug delivery systems. Surfaces of the material were also examined and the SEM images are summarized in Figure 8.

The in-depth investigation of interaction between Fe³⁺/Fe²⁺ and functional chitosan biomaterials are currently on the way in our laboratory and will be reported in due course.

Higher adhesiveness of the gels is desired to maintain an intimate contact with skin or tooth structure and results are summarized in Table 3. Chitosan hydrogels showed the highest adhesive force and the work of adhesion this can be expected because of the well known intrinsic bioadhesive properties of chitosan [35] . The adequate water absorption capacity together with the cationic nature which promotes binding to the negative surface of skin or dentin structure can also interpret these results.

Chitosan hydrogels showed the highest adhesive force and the work of adhesion this can be expected because of the well known intrinsic bioadhesive properties of chitosan. The adequate water absorption capacity together

(a) (b)

Ch/Vit C/As exposed to peroxide Ch/Vit C/As/Propolis exposed to peroxide

(a) (b)

(c) (d)

Ch/Vit C/Nap exposed to peroxide Ch/Vit C/Nap/Krill exposed to peroxide

(c) (d)

(e) (f)

Ch/Vit C/Ib exposed to peroxide Ch/Vit C/Ib/Propolis exposed to peroxide

(e) (f)

Figure 8. SEM images of reactive surfaces of novel biomaterials after the exposure to peroxide and “in vitro model of free radical damage”.

The presented values are an average (n = 5).

with the cationic nature, which promotes binding to the negative surface of skin or dentin structure can also interpret this results. According to Caffaggi, hydration of the polymer causes mobilization of the polymer chains and hence influences polymeric adhesion [36] . Appropriate swelling is important to guarantee adhesivity; however, over hydration can form slippery non-adhesive hydrogels [37] . In addition the molecular arrangement of the polymeric chains, which are present in the new hydrogels, such as propolis, aspirin, ibuprofen and naproxen can further unable to interact further with the substrate. The correlation between the force and work of adhesion is noticeable for all. Further experiments are to be conducted on the skin samples to evaluate the bio-adhesive capacity of the designed hydrogels.