Nanohybrid hydrogels designed for transbuccal anesthesia

Introduction

One of the most expected innovations in dentistry is the development of an effective topical anesthetic formulation. This is a relevant concern due to the patient fear to the injection and local anesthetic (LA) administration. Currently, “needle phobia” is the cause of treatment nonadherence, aggravating the dental problems. Moreover, there is a lack of efficient noninvasive pain relief formulations.¹ The most desirable marketed topical anesthetic cream is composed of the eutectic mixture of lidocaine and prilocaine (LDC-PLC) 5% w/w (EMLA^®). However, this formulation has been designed for dermatological purposes, and it causes ulceration when applied at the oral mucosa and does not minimize the palatal anesthesia pain, in humans.^2,3 Furthermore, systemic toxicity symptoms, such as fever after the eutectic mixture of LDC-PLC cream buccal application, were also reported.⁴

The nanoencapsulation of LA is a versatile approach, which has been successfully found in protecting the drug against degradation, providing nanostructured drug delivery systems (DDS) with physicochemical stability, biocompatibility, and optimized efficacy.⁵ Nanostructured lipid carriers (NLC) are a DDS formed by a lipid blend inner core coated with surfactants, and they provide efficient loading of hydrophobic molecules.⁶ In an attempt to develop an efficient pre-anesthetic for transbuccal application, we have previously described an optimized NLC/LDC-PLC (5%) formulation, selected from factorial design, with excellent structural properties, stability, and in vitro sustained release profile for both LAs.⁷ Despite the excellent properties of that DDS, the fluidness and low adhesion⁸ inherent to most of the colloidal formulations prevented its application as a pre-anesthetic in dentistry.

Hydrogels are macroscopic and water-soluble pharmaceutical forms formed by a tridimensional polymeric network, widely used for topical administration of several classes of drugs.⁹ Hydrogels can be processed from synthetic or natural polymers.^10,11 Processing hydrogels from biopolymeric matrices is especially interesting due to their biocompatibility and biodegradability properties, abundance, low cost, and absence of organic solvents or weak acids in most of the preparation methods.¹² Xanthan gum (XAN) is an anionic biopolymer synthesized from strains of Xanthomonas campestris that is broadly used in pharmaceutical and food industries.¹³ Its interest for use as hydrogel matrices for oral mucosa is also given by the free carboxylic acid available groups, which form hydrogen bonds with the mucus layer, improving the specificity of drug-release profile and efficacy.^14,15

The hybridization process of materials is an ancient practice, reported from the antique Egyptians.¹⁶ In the DDS field, these advanced hybrid materials combine structural, physicochemical, mechanical, and therapeutic properties of each excipient in a single final form. Hybridization enables the development of smart formulations or pharmaceutical forms that are able to specifically interact with biological barriers,¹⁷ such as the mucosal tissues and skin. There are some reports of lipid-biopolymer hydrogels for the topical sustained release of ibuprofen,¹⁸ ketoprofen,¹⁹ ofloxacin,²⁰ Resina draconis,²¹ clobetasol,²² and LAs,^23–25 which exhibited optimized properties in comparison to their lipid-related DDS.

In this sense, the development of lipid-biopolymer hydrogels based on NLC/LDC-PLC (5%) formulation was described,⁷ incorporated in XAN, alginate (ALG), or chitosan (CHT) matrices. The resultant hybrid hydrogels combined the sustained release of the LA provided by the NLC, with the desirable consistency, viscosity, and adhesion afforded by the biopolymer matrix. The NLC decreased the hydrophilic character of the biopolymers, improving the overall formulation affinity for the encapsulated anesthetics. The results obtained with the optimized (XAN-NLC) bio-hybrid hydrogel strongly support its future application for transbuccal anesthesia.

Materials and methods

Materials

LDC and PLC were donated by Cristália Prod. Quim. Farm. Ltda (Itapira, Brazil). Pluronic^® 68 (P68), ALG, XAN, and CHT were supplied by Sigma (St Louis, MO, USA). Cetyl palmitate (CP) was provided by Dhaymers Química Fina (Taboao Da Serra, Brazil) and capric/caprylic triglycerides (GC) were from Lipo do Brasil Ltda (São Bernardo do Campo, Brazil). High-performance liquid chromatography (HPLC)-grade acetonitrile was from J.T. Baker, Phillipsburg, NJ, USA. Deionized water (18 MΩ) was obtained from an Elga USF Maxima Ultra-Pure water purifier (Elga LabWater, High Wycombe, UK).

NLC preparation method

NLC/LDC-PLC was prepared through the emulsification–ultrasonication method. Briefly, a blend of CP (16%; w/v) and GC (3.8%; w/v) was heated in a water bath to 10.0°C above the melting point of CP (55°C). Then, a eutectic mixture of LDC-PLC (5%; w/v) was incorporated in the oily phase until complete dissolution.⁷ Next, an aqueous phase containing 3.5% P68 (w/v) and equally heated was added dropwise to the oily phase, under high-speed agitation (10,000 rpm) for 2 minutes, in an Ultra-Turrax blender (IKA WerkeStaufen, Staufen im Breisgau, Germany). The obtained microemulsion was ultrasonicated for 30 minutes at 500 W and 20 kHz, with intermittent 30 seconds (on/off) cycles in a Vibracell tip sonicator (Sonics & Mat. Inc., Danbury, CT, USA); the obtained samples were cooled to reach room temperature.

Biopolymer solution and hydrogel preparation

Aliquots of 2 g of ALG, XAN, and CHT were dispersed in 50 mL of deionized water or acetic acid 0.1% (only for CHT), under stirring and until complete homogenization. Then, LDC-PLC (5%) hydroalcoholic solutions were dispersed in ALG, XAN, and CHT suspensions and stirred for 2 hours at room temperature. For the hybrid hydrogel, NLC formulations replaced the water used for dissolution of XAN.²⁶ The proportion of NLC/LDC-PLC and XAN in the hydrogel was 1:1 (w/w). In all types of prepared hydrogels, the final concentration of LDC-PLC was 25 mg/g. Crosslinking of the ALG-based and CHT-based hydrogels was achieved, respectively, by dropwise addition of 1 mL of 2% (w/v) CaCl₂ solution or 1% (w/v) tripolyphosphate solution, under magnetic stirring for 1 hour. The prepared hydrogels were stabilized overnight at 4°C, and visually inspected prior to use.

In vitro LDC-PLC release from hydrogels

The release of LDC-PLC from the biopolymer-based or lipid-biopolymer hydrogels was studied using a Franz-cell system, composed of a donor compartment (400 μL) and an acceptor compartment (4 mL), filled with 5 mM Tween/PBS, pH 7.4. A membrane with 10,000 Da molecular exclusion pore size separated the compartments. The systems were maintained under sink condition. Aliquots were withdrawn from the acceptor compartment at periodic intervals for HPLC quantification (λ=220 nm), and the volume was maintained constant by replacement of buffer solution (200 μL). All measurements were performed in sextuplicate. The two peak areas in the chromatograms were used to determine the percentage of LDC and PLC released. The KinetDS 3.0 software (Aleksander Mendyk, Kraków, Poland) was employed to analyze the kinetic curves. Among the kinetic models tested, the Weibull model was the best fit considering the coefficient of determination (R²).

where: m is the amount of LDC-PLC released at the time t, b is the release exponent, and a is the time scale of release.

Accelerated stability of lipid-biopolymer hydrogels

The accelerated stability of the XAN-based hydrogels was performed in triplicate at predetermined times, 0, 3, and 6 months, in terms of pH changes, weight loss (<5%), and LA content (mg/g, quantified by HPLC). The hydrogels were stored in an adapted stability chamber at 40°C±3°C and 75%±3% relative humidity (ICH Expert Working Group, 2003).⁴⁹ Statistical analyses were carried out by unpaired Student’s t-test and one-way analysis of variance (ANOVA) and Tukey post hoc test (p<0.05).

Structural characterization

The XAN-based hydrogels viscosity (mPa s) was determined with a rheometer (Haake RheoStress 1, Thermo Fisher Scientific, Waltham, MA, USA), in a low amplitude oscillatory strain, from 0.1 to 10 Hz, at 37°C. The analysis time for ascending and descending curve was 170 seconds, and the shear gradient ranged from 0 [1/s] to 170 [1/s].

ATR-FTIR spectra were recorded with an infrared spectrometer equipped with ATR (Bruker IFS, Bruker, Billerica, MA, USA), in the range of 4500–500 cm⁻¹.

DSC measurements were carried out in a TA Q20 calorimeter (TA Instruments, New Castle, DE, USA) equipped with a cooling system. The samples (5 mg) were placed in aluminum pans and the thermal profiles were obtained from 0°C to 250°C, at 10°C/min heating rate, under a flow of nitrogen.

FE-SEM equipment (FEI-NOVA NanoSEM 230, Sydney, NSW, Australia) was used to elucidate the textural properties of the hydrogels. The samples were adhered on a carbon tape and subjected to a gold conducive coating on the surface.

Bioassays

In vitro cell viability

The cytotoxicity of XAN-based hydrogels was determined by MTT assay, in cultures of Balb/c 3T3 fibroblasts, immortalized human keratinocytes cells (HaCat), and monkey kidney fibroblasts (VERO). All the cell lines were commercially purchased from the Laboratório BCRJ, Universidade Federal do Rio de Janeiro, UFRJ, Brazil. Briefly, the cells were seeded in 96-well culture plates and incubated for 2 hours (37°C, 5% CO₂). The Roswell Park Memorial Institute culture medium was replaced by 200 μL of fresh medium, with different concentrations of hydrogels. After the exposure period (2 hours), the medium was removed, and the plate was washed with PBS (pH 7.4). Then, 200 μL of medium (without serum) containing 0.5 mg/mL of MTT reagent was added to each well and incubated for 2 hours at 37°C. After that, the MTT solution was removed and 200 μL of ethanol was added to each well, dissolving the formed formazan crystals. The formazan absorbance was quantified in a microplate reader (570 nm). Results were expressed as the mean viability percentage ± standard error means (SEM) (n=3). The statistical analysis was carried out by two-way ANOVA and Tukey post hoc test.

Tail-flick test

Male adult Swiss mice (25–30 g) were obtained from the Centro Multidisciplinar para Investigação Biológica na área de Ciência em Animais de Laboratório (CEMIB-UNICAMP, Campinas, Brazil). The protocol was approved by the UNICAMP Institutional Animal Care and Use Committee (4468-1/2017), and the methodologies following the recommendations of the Guide for the Care and Use of Laboratory Animals. The animals were maintained (5/cage) with free access to food and water and were placed in a restraint over an analgesimeter, with a portion of the tail (5 cm from its top) exposed to heat from a projector lamp (55°C±1°C). Thirty seconds cut-off time was used to avoid thermal injury and the baseline (normal response to the noxious stimulus) was noted. For the blockage of the caudal nerve, hydrogels (0.025 g) containing 5% LDC-PLC were applied on the back of the mice tail, and occluded. The analysis started 30 minutes after hydrogel administration and the data were recorded every 30 minutes during the first 1 hour, and every 60 minutes up to the end of the experiment (8 hours). Data were expressed as percentage of maximum effect (%MPE), and the areas under the curves were calculated. The statistical analyses were performed by two-way ANOVA plus Tukey post hoc, n=5.

Results

Visual inspection of lipid-biopolymer hydrogels

Different hybrid hydrogels were prepared by blending the lipid (NLC/LDC-PLC) and biopolymer (CHT, ALG, and XAN) phases, ionically crosslinked when necessary. The most successful hybrid hydrogel composition was prepared with NLC and XAN (XAN-NLC/LDC-PLC) excipients, which showed homogenous aspect and suitable consistency (Figure 1). The ALG-based hydrogels presented heterogeneous aspect, with dispersed microgranules in the final form. Regarding the CHT hydrogel matrix, separation was observed immediately after the preparation. Therefore, the XAN-based NLC hydrogel was selected for further in vitro and in vivo tests.

Figure 1 (A) Digital photo of XAN/LDC-PLC (left) and XAN-NLC/LDC-PLC (right) hydrogels; (B) schematic representation of the lipid-biopolymer hydrogel internal organization. Abbreviations: LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

In vitro LDC-PLC release test

The in vitro LDC-PLC release test was carried out in a Franz-type vertical diffusion cell for 24 hours, and quantified by HPLC. Control hydrogels, containing only the biopolymer and the anesthetics (XAN-LDC and XAN-PLC), reached 100% release of both LA after 4–5 hours of experiment (Figure 2). The hybrid (lipid-biopolymer) XAN-NLC hydrogels exhibited a sustained bimodal release profile: after 3 and 24 hours of study, 35% and 57% of lidocaine and 43% and 81% of prilocaine were released, respectively.

Figure 2 In vitro release profile of LDC (left) and PLC (right) up to 24 hours of experiment from xanthan (XAN/LDC; XAN/PLC) hydrogels as controls and their respective lipid-biopolymer hydrogels. Note: LDC-PLC =5%, n=6 at 37°C. Abbreviations: LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

The KinetD 3.0 software was used to fit the release curves in Figure 2, using several mathematical models.²⁷ The best fit (higher R² values) for LDC and PLC release from the hydrogels were found with the Weibull model (Table S1). In all curves, the b coefficient (Weibull model) that determines the release mechanism, ranged from 0.03 to 0.14, denoting Fickian diffusion.²⁸

Accelerated stability test

In the accelerated stability test (conducted under critical stress condition) of semisolid formulations, the physicochemical parameters that are followed over time anticipate processes such as drug degradation and physicochemical changes, that can compromise the formulation performance.²⁹ Therefore, the XAN-based hydrogel was followed during 6 months at 40°C and 75% relative humidity, in terms of pH, weight loss, and LA content (Figure 3).²⁹ No significant changes (p>0.05) in any of the analyzed parameters were detected for the XAN-NLC/LDC-PLC hydrogel that preserved its pH (~7.4), initial weight (loss <2%), and LDC-PLC content (~25 mg/g) for 6 months. However, for the control hydrogel prepared without the lipid nanoparticles (XAN/LDC-PLC), the stability was only kept up to 3 months. After that (6 months) the formulation exhibited a significant increase in weight loss (>5%) and a decrease in pH (p<0.05) and content of both anesthetics (p<0.05).

Figure 3 Accelerated stability tests of XAN-based hydrogels (XAN-NLC/LDC-PLC and its control XAN/LDC-PLC) in terms of pH (A), weight loss (B), and LA content (C), followed for 6 months at 40°C and 75% RH. Notes: Statistical analyses were carried out by Student’s t-test and one-way ANOVA and Tukey post hoc test, p<0.05; mean ± SD; n=3. Abbreviations: ANOVA, analysis of variance; LA, local anesthetic; LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

Structural characterization

For the selected formulation, the interactions between the polymer and NLC/LDC-PLC excipients were assessed by rheology, FE-SEM, FTIR-ATR, and DSC analyses, providing information about the molecular organization of the novel nanohybrid system.

Figure 4A shows rheological properties of XAN-based hydrogels, given by the viscosity vs frequency (37°C) curve, which is currently required for any potential topical formulation.³⁰ A pseudoplastic behavior was observed for all the analyzed XAN hydrogels, where the increase in frequency was followed by a decrease in viscosity.³¹ Indeed, all XAN-based hydrogels presented the rheological profiles of the pristine material.

Figure 4 Physicochemical and morphological characterization of the hydrogels and excipients. Notes: Rheological profile: viscosity vs frequency curves, at 37°C (A), FE-SEM images in two different magnifications (B), FTIR-ATR (4000–500 cm−1) spectra (C) and DSC thermogram (D) for XAN-based hydrogels (XAN-NLC/LDC-PLC and its control: XAN/LDC-PLC) and components (LDC, PLC, XAN). Abbreviations: LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

The FE-SEM (Figure 4B) images were used to compare the textural properties of XAN/LDC-PLC (control) and XAN-NLC/LDC-PLC hydrogels. The microscopy of control hydrogel showed the typical XAN flake-like architecture. The hybrid (XAN-NLC/LDC-PLC) hydrogel exhibited rougher surfaces, plus evident XAN-coated nanoparticles, with a completely different texture than the control.

The observed FTIR-ATR bands and assignment are provided in Figure 4C and Table S2, respectively. The infrared spectroscopic profile of the lipid nanoparticles (NLC/LDC-PLC) and their excipients has been previously determined.⁷ Figure 4C shows typical XAN polysaccharides bands, observed in the 1100–920 and 3250–2885 cm⁻¹ regions of the spectra. The bands centered at 1021 and 1061 cm⁻¹ are noticed in XAN and XAN-NLC/LDC-PLC spectra, respectively, and can be attributed to the ν_C=O vibrations of XAN glucose residues. The bands comprised in the wide (3250–2885 cm⁻¹) region in the XAN spectrum, and those bands shifted to higher wavenumber in the XAN-NLC/LDC-PLC spectrum (3310 cm⁻¹), correspond to XAN structural ν_OH.³² As expected, in the hybrid-polymer spectrum, bands centered at 2917 and 2851 cm⁻¹, consistent with C-H and O-CH₂ stretching vibrations of the NLC structural lipid (CP), were observed.³³ Interestingly, the set of bands in the 3303–2800 cm⁻¹ region, assigned to the LA, was not observed in the hybrid hydrogel spectrum.

Finally, the thermodynamic features of the excipients and XAN-based hydrogels were assessed by DSC analysis (Figure 4D). The thermogram of pure LDC and PLC evidenced endothermic peaks centered at 69°C and 43°C, respectively, related to the respective melting points of the LA.⁷ The calorimetric behavior of pristine XAN showed a wide endothermic peak at 115°C, due to evaporation of the water physically adsorbed in the biopolymer.³⁴ In the XAN/LDC-PLC thermogram, the endothermic peaks of both LA were less intense and shifted to lower temperatures. Finally, in the hybrid (XAN-NLC/LDC-PLC) sample, a single endothermic peak was noticed at 115°C, assigned to the evaporation of physically adsorbed -water of the XAN biopolymer.

Once the structural properties of XAN-NLC/LDC-PLC were elucidated, this hybrid hydrogel could be evaluated in terms of cytotoxicity and biological activity.

Bioassays

The MTT-cell viability assay was conducted using 3T3, HaCat, and VERO cultured cells, for 2 hours. Since pure XAN hydrogel is widely known as noncytotoxic, even after 21 days of analysis,³⁵ it was used as a control. None of the concentrations tested affected the cell viability of the three cultured cell lines (p>0.05), in any of tested hydrogel concentrations (up to 250 mg/mL) (Figure 5). The concentration-dependent decrease in cell viability of the three cell lines observed in Figure 5 exclusively for XAN/LDC-PLC samples is a result of the well-known intrinsic cytotoxicity of LA.³⁶

Figure 5 Cell viability (MTT) tests in Balb/c 3T3, HaCaT and VERO cells treated with XAN, XAN/LDC-PLC, and XAN-NLC/LDC-PLC for 2 hours. Notes: Results are expressed as mean ± SD (n=3). Statistical analyses were carried out by two-way ANOVA, p<0.05; n=3. Abbreviations: ANOVA, analysis of variance; LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

Last but not least, the anesthetic effect of the XAN-based hydrogels was assessed by the tail-flick test in mice (n=5). Figure 6 shows the %MPE and total anesthesia, given by the area under the curve for XAN-NLC/LDC-PLC (~505), XAN/LDC-PLC (~238) hydrogels and the eutectic mixture of LDC-PLC cream (~76). In both the %MPE and area under the curve parameters, the hybrid hydrogel exhibited an anesthetic effect almost twice and four times higher than control hydrogel and the eutectic mixture of LDC-PLC cream, respectively. The caudal nerve block lasted for 2, 4, and 8 hours, in the animals treated with the commercial cream, XAN/LDC-PLC, and XAN-NLC/LDC-PLC, respectively.

Figure 6 Anesthetic effect (tail-flick test) in mice treated with XAN-based hydrogels (XAN-NLC/LDC-PLC and XAN/LDC-PLC) containing 5% LDC-PLC (A). Results were expressed as %MPE vs time (hours). The areas under the curves (AUC), from 0 to 8 hours are also given (B). Statistical analyses were carried out by two-way ANOVA plus Tukey post hoc: a, XAN/LDC-PLC × commercial cream; b, XAN-NLC/LDC-PLC × commercial cream, *p<0.05, **p<0.01, ****p<0.0001; n=6, commercial cream = EMLA®. Abbreviations: %MPE, percentage of maximum possible effect; ANOVA, analysis of variance; LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

Discussion

As mentioned above, we have previously developed through factorial design an NLC/LDC-PLC formulation with optimized properties. However, the fluidity of that formulation was a serious limitation for its successful topical application.¹⁶ Aiming to accomplish major advances in transbuccal anesthesia, we hybridized this NLC formulation with ALG, XAN, or CHT hydrogels. In the hybridization approach, benefits from the nanostructured particles and polymers were combined into a single pharmaceutical form: the sustained release profile of NLC-encapsulated LA and the appropriate viscosity, consistency, and adhesion of the biopolymer matrix, to provide efficient topical anesthesia of the oral mucosa.¹⁷

Despite the best mucoadhesion of CHT,³⁷ its incompatibility with NLC formulations led to separation,³⁸ probably due to the tripolyphosphate ionic crosslinking. Moreover, the use of weak acid in the polymer preparation and its undesirable flavor³⁹ contraindicate CHT administration at the oral mucosa. ALG hydrogels were crosslinked with a cationic solution of CaCl₂⁴⁰ in order to attain the desirable viscosity. However, their final form was not homogeneous, probably due to the interaction of calcium ions with the NLC. Together, these findings supported the choice of XAN as the biopolymer counterpart for the hybrid formulations. XAN was also the cheapest biopolymer tested, and its polymerization only requires water, which is extremely suitable for industrial scale production.

The blending procedure (hybridization) seemed not to affect the structural organization of the NLC, since XAN-NLC/LDC-PLC exhibited a bimodal LA release profile – with an initial high burst effect followed by sustained release – decisive to achieve an optimized LA action.⁴¹ The release of LDC was longer sustained than that of PLC in the hybrid hydrogels, in a similar way to the release from NLC suspensions.⁷ The higher hydrophobic character and encapsulation efficiency by NLC could explain the differential release profile of LDC.

In addition, the presence of a biopolymer matrix in the formulation extended the release time of both anesthetics, probably due to the double physical barrier that the LA should overcome to be released. The time for total release of the anesthetics increased from 8 hours in suspensions of NLC⁷ to 18 hours in XAN-NLC/LDC-PLC. The continuous sustained release observed for hybrid formulation was also a result of the weak interactions between nonencapsulated LA molecules (in the aqueous of NLC) and XAN free hydroxyl groups.⁴² The kinetic of hydrogels was best fitted by the Weibull model, where Fickian diffusion describes the LA release from inside the nanoparticles through the swelled XAN chains. This result is also in agreement with the bimodal LDC-PLC release profile also observed in polyacrylate hydrogels.⁴³

A set of biophysical methods provided valuable molecular information, confirming that a novel topical formulation was produced, which was stable in critical conditions for 6 months, as required by regulatory issues. The final pH of lipid-biopolymer hydrogel (7.4) was the same as the oral mucosa, contrasting those of the control hydrogel (XAN/LDC-PLC, pH ~5) and commercial cream (pH ~9). Since the pH attained after topical administration is strictly related to the buccal mucosa’s susceptibility to injury, the pH of XAN-NLC/LDC-PLC is an outstanding advantage. Furthermore, the formulation showed a pseudoplastic behavior due to XAN, a natural improver of rheological properties in pharmaceuticals and food industries.⁴⁴ The pseudoplastic behavior assured: 1) the desirable viscosity prior to the hybrid hydrogel application (keeping it in the site of administration) and 2) a subsequent decrease in viscosity, favoring hydrogel spreadability and fixation in the oral mucosa.³¹

It is worth mentioning that the control (XAN/LDC-PLC) hydrogel, despite the pseudoplastic XAN-related behavior, was not found appropriate for transbuccal anesthesia, as revealed by the accelerated stability study and structural characterization tests. In fact, DSC analysis anticipated the lack of stability, by the presence of the two endothermic peaks related to pristine LA. Therefore, in XAN/LDC-PLC samples, the expected formation of drug–polymer conjugates was not observed, which could explain the lack of stability in all parameters evaluated over 6 months of storage and the less sustained LDC-PLC release profile. These facts reinforce the relevance of the material hybridization.

The hybrid hydrogel combined advantages from the lipid and biopolymer components. FTIR-ATR data confirmed the interaction between them, by the coexistence of mutual bands in the XAN-NLC/LDC-PLC spectrum (eg, the C-H and O-CH₂ lipid vibrations and the shift of typical anhydrous glucose bands of xanthan to higher wavenumbers). DSC thermogram demonstrated that the XAN-NLC/LDC-PLC maintained the thermodynamic features of NLC (control), without any endothermic event related to pristine LA. FE-SEM images proved that a new assembly was formed, with a completely different texture than that of the control hydrogel, in which the excipients could not be distinguished. Based on the abovementioned information, it was suggested that the new hybrid material is able to protect LA against hydrolysis, corroborating the slower release profile and good stability exhibited by the XAN-NLC/LDC-PLC hydrogel.

Bioassays confirmed the safety of XAN hydrogels, even at the highest quantity (250 mg/mL), against different cell lines. This was possible due to the fact that XAN is a biocompatible matrix, currently applied as a thickener and gelling agent that only requires the addition of water to form a stable gel.⁴⁵ Moreover, in the XAN/LDC-PLC hydrogel, the biopolymer somehow neutralized the intrinsic toxicity of the anesthetics, probably due to available XAN-hydroxyl groups that interact with the dispersed free LA through hydrogen bonds, decreasing the potential toxicity of the anesthetics. Additionally, the safety behavior observed for XAN-NLC/LDC-PLC hydrogel was predictable, since NLC formulations were previously described as noncytotoxic for 3T3 and HaCat cells.^36,46–48

Finally, the anesthesia duration was determined through tail-flick assay in mice. XAN-NLC/LDC-PLC exhibited an anesthetic effect two times higher than the control hydrogel (XAN/LDC-PLC) and four times higher than the commercially available cream. The prolonged analgesia effect is a result of combined action of NLC plus the hydrophilic hydrogel matrix. The massive superficial contact area of NLC favors the anesthetic release from the lipid core to the swelled adhesive biopolymer network, toward the biological barrier. This promising lipid-biopolymer hydrogel will be tested for the minimization of pain (prior to LA injection) in humans, and thus can also be useful in the treatment of other oral painful conditions.

Concluding remarks

The high interest in the development of an effective preanesthetic formulation to be applied in dentistry has moved this current work. We have pointed out the preparation of a pre-anesthetic of complex molecular organization. The nanohybrid hydrogel for the delivery of LDC-PLC (5%) was composed of XAN as biopolymer and NLC/LDC-PLC as the lipid matrix, comprising the use of abundant, biocompatible, and cheap biomaterials. This strategy provided an advanced pharmaceutical form with excellent compatibility between the excipients, desirable rheological properties, and prolonged delivery profile. The hydrogel was stable (for 6 months on critical conditions), had suitable mechanical properties to be orally administered, was safe, and doubled and quadrupled, the anesthesia duration in comparison to a control hydrogel formulation (without the nanostructured lipid counterpart) and the commercial cream, respectively. The nanohybrid hydrogel should now be clinically evaluated to enable the formulation to reach the market.

Acknowledgment

The authors thank FAPESP (#14/25372-0, #14/14457-5) and Cristália Ind. Quim. Farm. Ltda, for kindly providing lidocaine and prilocaine.

Disclosure

The authors report no conflicts of interest in this work.

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Supplementary materials

Table S1 Mathematical modeling of LDC-PLC release profile, according to the Weibull model Notes: b, shape of the dissolution curve progression; k, release kinetic constant; R2, coefficient of determination. Abbreviations: LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.

Table S2 FTIR-ATR bands and assignment for the XAN-NLC/LDC-PLC sample Abbreviations: LDC-PLC, lidocaine–prilocaine; NLC, nanostructured lipid carrier; XAN, xanthan.