In vitro study of chitosan-based multi-responsive hydrogels as drug release vehicles: a preclinical study.

Systematic administration of painkillers and anti-inflammatory drugs is routinely employed to minimize pain and bodily disorders. Controlled drug delivery has the potential to improve the outcomes of disorders by providing sustained exposure to efficacious drug concentrations. Herein, we report the fabrication of multi-responsive hydrogels using reactive and functional polymers such as chitosan and polyvinyl pyrrolidone by varying the concentration of a cleavable crosslinker, tetraethyl orthosilicate. The swelling indices of the hydrogels were evaluated in distilled water, solutions with different pH values and different electrolytes. FTIR, WAXRD and TGA were conducted to investigate the structures, crystallinities and thermal stabilities of the prepared multi-responsive hydrogels, respectively. The ultimate tensile strength and elongations at break of the fabricated hydrogels were investigated to assess their mechanical stability. Optical microscopy, biodegradation, antimicrobial and cytotoxicity analyses were further carried out to verify the magnified crosslinked and porous structures, biodegradabilities, biocompatibilities and toxic behaviour of the as-prepared hydrogels, respectively. Drug release analysis was conducted to evaluate their release behaviour in PBS, SGF, SIF and electrolyte solutions. The overall results indicate the successful development of novel, non-toxic and sustained drug deliverable hydrogels, which can be considered as a paramount success towards the fabrication of controlled drug delivery systems. This journal is © The Royal Society of Chemistry.

Introduction

The notion of controlled drug release was initiated by the demand for effectual treatment of diseases.[1] Targeted controlled release systems proffer several distinguishing benefits over conventional drug delivery methods. These include targeted delivery of the drug to a specific part of the body, drug stability, pledge of treatment continuity in nocturnal phase, optimal drug absorption and less need of follow-up care. Controlled release systems have been reported over a range of pH domains in the body, e.g. for intestinal, gastric, oral and periodontal applications.[2-4] Several studies have been reported for the use of hydrogels as controlled release systems.[5]

Multi-responsive hydrogels (MRHs) are 3-D polymeric networks that swell in the presence of different stimuli, such as aqueous medium, physiological pH, temperature, and ionic solutions. Due to their high water content, hydrogels have potential biomedical applications, such as in contact lenses, wound healing, tissue substitutes and slow drug delivery systems; they have been proved to be biocompatible and to enhance tissue regeneration and cell growth.[6-10] Copolymer or multipolymer hydrogels are smart materials because a variety of physical and chemical properties for biomedical applications can be induced by joining multiple monomeric units.[11] Natural functional and reactive polymers such as chitosan (CS), chitin, guar gum and alginate are used for drug delivery systems because they can play vital role in healing procedures. However, the use of natural polymers is limited because of their poor mechanical properties and difficult processing. The combination of reactive synthetic and natural polymers can endow a drug delivery system with optimum properties.[12]

CS is a natural cationic biopolymer that is produced by N-deacetylation of chitin, the second most abundant natural polymer after cellulose. It is an interesting functional biomaterial due to its good biodegradability, biocompatibility, low cost and low toxicity.[13,14] CS has been broadly used for an extensive range of applications, such as wound-healing agent, drug carriers, tissue engineering, skin regeneration,[15] membrane filters for water treatment, chelating agents, and biodegradable films or coatings for foodstuff packaging.[16] Polyvinyl pyrrolidone (PVP) is a water-soluble, highly amorphous polymer. It is considered to be a “miracle” polymer because of its numerous distinctive applications. It is used in the fabrication of thromboresistant hydrophilic gels.[17] Due to the lubricating and viscous properties of PVP, it is useful for vitreous humor replacement.[18] Both polymers are frequently used in the field of biomaterials, especially for the development of next generation hydrogels.[19]

Because CS is soluble in acidic solvents, therefore its gels are frequently crosslinked to increase the stability of their structures. Dialdehyde, epoxy compounds, formaldehyde, glutaraldehyde, etc. are frequently used crosslinking agents. However, all these materials are chemically synthesized and can cause physiological toxicology.[20] However, tetraethylorthosilicate (TEOS) is a preferred crosslinker because it forms covalent bonds between inorganic regions and amorphous polymer chains. It has been successfully used in biomedical applications and is non-toxic, unlike typically reported crosslinkers such as tripolyphosphate, borate, and glutaraldehyde.[21,22] A critical review of the reported literature was carried out on MRHs, covering different aspects such as natural and synthetic polymers, types of crosslinker, and modes of fabrication. As per the findings of our extensive literature survey, this study is the first to propose the fabrication of MRHs comprising CS and PVP crosslinked with TEOS by a solution casting protocol for controlled drug release systems.

The foremost issue in typical drug delivery systems is that; normally the drug is not released in significant amount. Therefore, a small concentration is absorbed by the body and the remainder is excreted from the body without any change. When working with drugs which are not easily consumed by the body, it is required to adopt alternative approaches to maintain the drug dosage in the prescribed amount. To address this problem, hydrogels were introduced; they release drugs in a controlled manner with a suitable delivery timespan.[23,24] Lidocaine was the first modern local anaesthetic agent, and it was used as a model drug in this study. It was selected due to its clinical relevancy in broad spectrum therapy for burning, itching and pain from skin inflammation.[25]

In this study, CS/PVP MRHs were fabricated via a solution casting protocol in the presence of TEOS. The prepared hydrogels were characterized by swelling in distilled water, different pH media and electrolytes, gel fractions, Fourier transform infrared spectroscopy (FTIR), optical microscopy, X-ray diffraction spectroscopy, and thermogravimetric analysis to determine their thermal stability, cytotoxicity, antimicrobial analysis and drug release in phosphate buffer saline (PBS), simulated gastric fluid (SGF), simulated intestinal fluid (SIF) and electrolyte solutions.

Experimental details

Materials

CS (molecular weight 90 000 g mol−1; DDA 90%) was procured from Germany. PVP (molecular weight 40 000 g mol−1), formic acid (≥96%) and TEOS were purchased from Sigma Aldrich, USA. Boric acid, calcium chloride and sodium chloride were purchased from Riedel-deHaën, potassium chloride, potassium dihydrogen phosphate and sodium dihydrogen phosphate were purchased from Merck, Germany, and hydrochloric acid (37% pure) was obtained from Riedel-deHaën. All chemicals were of analytical grade and were used without any further purification.

Methods

Hydrogels were prepared by the economical solution casting technique. CS (60 wt%, i.e. 0.6 g) was dissolved in 2% formic acid (50 mL), and PVP (40 wt%, i.e. 0.4 g) was dissolved separately in distilled water (50 mL). The two solutions were mixed and blended for 2 h at 50 °C to 55 °C. TEOS (50 μL) was taken in 5 mL of ethanol and added dropwise to the prepared blend, and this mixture was vortexed for an additional 4 h at the same temperature. Later, the mixture was poured in a Petri dish and placed in a vacuum drying oven (LVO-2040, Lab Tech, Korea) at 40 °C until it completely dry; it was then stored at room temperature for further studies. Digital images of the hydrogel mixture before and after development are shown in Fig. 1.

Fig. 1

Digital pictures (a) before hydrogel fabrication; (b) after hydrogel fabrication.

Hydrogel samples with 100, 150, 200 and 250 μL TEOS concentrations were synthesized in the same way. Hydrogel samples without crosslinker were also prepared and were coded as MRH. The MRHs with TEOS concentrations of 50, 100, 150, 200 and 250 μL were coded as MRH-1, MRH-2, MRH-3, MRH-4 and MRH-5, respectively. The proposed interactions among the components of the prepared hydrogels are shown in Scheme 1.

Scheme 1

Proposed interactions among the components of the prepared MRHs.

Drug-loaded hydrogels

CS (0.6 g) was dissolved in 50 mL of 2% formic acid solution and PVP (0.4 g) was dissolved separately in 50 mL of distilled water at 50 °C, as discussed in Section 2.2. The two solutions were blended for 2 h at 50 °C to 55 °C. Then, 50 mg of model drug (lidocaine) was dissolved in distilled water and was added to the polymer blend; the mixture was stirred for 1 h. 150 μL of TEOS was dissolved in 5 mL of ethanol and was added dropwise to the drug-loaded blend. This blend was further stirred for 4 h at the same temperature. This solution was then poured in a Petri dish and dried in a vacuum drying oven (LVO-2040, Lab Tech, Korea) at 40 °C. After complete drying, each drug-loaded sample was peeled off the Petri dish and stored at room temperature for the drug release studies.

Characterizations

Fourier transform infrared spectroscopy

The functional group confirmations and the interactions between all the components of the prepared hydrogels were evaluated by FTIR spectroscopy (Shimadzu, IR Prestige-21, Japan) in attenuated total reflectance (ATR) mode. The analysis was performed in the wavenumber range of 4000 to 400 cm−1 at a scan rate of 60 scans per sample, and the resolution was set as 4 cm−1. The air background was taken before each sample run.

Swelling experiments

Swelling index in distilled water

The swelling indices of the prepared MRHs were determined gravimetrically in distilled water. A small piece of sample was taken and weighed. Then, it was placed in distilled water in a Petri dish and was allowed to swell. After 10 min, the water was removed from the Petri dish, and the sample was cleaned properly with tissue paper and weighed again. This procedure was repeated until the weight of the sample began to decrease or become stable. The swelling indices of the samples were determined using eqn (1):where Ws and Wd are the weights of the swollen and dried samples, respectively. The swelling index of each hydrogel was calculated three times, and the average was taken to note the final reading.

Gel fraction

To determine the gel fractions, pre-weighed samples were taken in Petri dishes and immersed in sufficient amounts of distilled water for 10 h. After a specific time duration, the water was removed and the hydrogel samples were dried in a vacuum oven at 40 °C until the weight become constant. The gel fractions were measured by eqn (2):where M′ refers to the weight of the crosslinked sample after oven drying and Mo is the initial weight of the sample.

Swelling index in buffer solutions

Buffer solutions with different pH values (2, 4, 6, 8 and 10) were prepared by the standard method. Each hydrogel sample was weighed and immersed in buffer solutions till equilibrium time of each sample. All the samples were tested in triplicate. The swelling indices of the hydrogels was measured by the same equation as in Section 3.1.1.

Swelling index in electrolyte solutions

Electrolyte solutions, i.e. NaCl and CaCl2, with different concentrations (0.1, 0.3, 0.5, 0.7 and 0.9 M) were prepared using the standard method. The swelling indices of the prepared hydrogels in electrolyte solutions were measured by the same procedure as described in Section 3.1.1.

Thermogravimetric analysis

A TGA/STA 409C instrument (NETZSCH, Germany) was used to examine the thermal behaviour of the prepared MRHs. The samples were analyzed from ambient temperature to 650 °C, and the temperature ramp was maintained at 10 °C min−1. The samples were tested in flowing argon gas at a flow rate of 15 mL min−1.

Wide-angle X-ray diffraction analysis

Wide-angle X-ray diffraction analysis (WAXRD) was carried out to characterize the polymorphic forms of the prepared hydrogels by a Siemens D500 X-ray diffractometer, Germany, equipped with a cobalt source. WAXRD data were collected using an Fe-filtered Co-Kα radiation source in the 2θ range of 5 to 80° at a scan rate of 0.02° s−1. The accelerating current and voltage were set at 40 mA and 40 kV, respectively.

Mechanical properties

The mechanical properties of the prepared MRHs were evaluated using a Lloyd LRX material testing machine, UK, equipped with a 200 N load cell. Samples with dimensions of 2.5 × 0.5 inches were used to evaluate the ultimate tensile strength (UTS) and elongation at break (E%) using the ASTM D882-02 at 20 mm min−1 cross head speed of the machine with a gauge length of 1.5 inch at room temperature. These experiments were conducted in triplicate, and the average value of the three samples was calculated to evaluate the mechanical properties.

Optical microscopy

To examine the crosslinking and swelling behaviour of the surface of the MRHs, a research grade polarising microscope (GXM XPL33230; GT Vision, Haverhill, UK) with transmitted and incident polarized light was used. The hydrogel samples were illuminated with monochromatic light to minimize the chromatic deviation, and the images were captured at 20× magnification.

In vitro biodegradation

To evaluate the in vitro biodegradation of the prepared MRHs, PBS solution was prepared by standard method. Degradation studies were conducted after 1, 3, 5 and 7 days. Pre-weighed hydrogel samples were immersed in excess amount of PBS solution. After the predetermined time points, the PBS solution was removed carefully and the weight of the degraded sample was measured. The biodegradation of the hydrogel samples was determined by eqn (3).where Wi is the initial weight of the hydrogel and Wd is the degraded weight of the hydrogel.

Antimicrobial profile

The antimicrobial profiles of the MRHs were determined against Escherichia coli (E. coli). Growth of the bacterial strain was checked in sterile Luria–Bertani (LB) medium which was prepared by taking 10 g Tryptone, 5 g yeast and 10 g NaCl in 800 mL distilled water. The pH of the solution was maintained at 7. The solution volume was marked up to 1000 mL and was sterilized in an autoclave for 1 h. For the control sample, 20 μL of E. coli strain and 20 mL of LB medium were taken in a vessel and incubated for 24 h at 37 °C. For sample preparation, 20 μL E. coli strain and 20 mL LB media were mixed; a hydrogel sample (5 × 5 mm) was added to the mixture, and the above procedure was repeated. The antimicrobial activity was measured by taking the optical densities of the control and samples with a spectrophotometer (Double beam, PerkinElmer, Model Lambda25, USA) at 600 nm.

In vitro cytotoxicity analysis

In vitro cytotoxicity analysis was performed by the brine shrimp lethality assay protocol, which is a fundamental toxicity screening procedure. Brine shrimps were hatched using brine shrimp eggs in a vessel containing sterile sea water with constant aeration for 48 h at ambient temperature. After proper hatching, active nauplii were separated from the brighter portion of the hatching vessel and taken for the assay in a deep well microtitre plate with a well depth of 2 cm and a well diameter of 1.8 cm filled with 0.2 mL salt water. The immature larvae were counted, and hydrogel samples were placed in triplicate in the active nauplii wells. The well plate was kept in the dark at room temperature. Surviving nauplii were observed using a microscope (GXM, XPL33230; GT Vision, Haverhill, UK) and were counted to calculate the mortality using eqn (4):M = percent of dead larvae after 24 h, A = number of dead larvae after 24 h, B = average number of dead larvae in the blind samples after 24 h, N = number of dead larvae before starting the test, G = total number of larvae.

Drug release profile

The drug release profiles were evaluated by submerging the above-prepared drug-loaded hydrogel samples in 100 mL of PBS solution at physiological conditions (pH 7.4 and 37 °C). This release medium was selected to simulate intestinal fluids and to maintain the pH of the colon.[26] After every 10 min, a 5 mL aliquot of this PBS solution was collected in a vial to check the drug release concentration, and 5 mL of fresh PBS was added to maintain the constant volume of solution. This process was repeated for 3 h, and the drug release concentration was quantified by measuring the absorbance of the collected sample by UV-Vis analysis (UV-Vis spectrophotometer, double beam, model Lambda 25, PerkinElmer, USA) at 263 nm.

The same procedure was repeated to check the drug release in simulated gastric fluid (SGF; pH 1.2) and simulated intestinal fluid (SIF; pH 6.8) solutions as well as in electrolyte solutions, i.e. NaCl and CaCl2.

Results and discussion

FTIR is a very useful technique to evaluate chemical changes at the molecular level. The intensity and position of the spectral bands are sensitive to chemical changes and provide confirmation of the formation of macromolecules.[27] This analysis confirms the functional groups present in ingredients and shows intermolecular hydrogen bonding between components because particular interactions influence the local electron density and corresponding frequency shifts. Fig. 2 shows the FTIR spectra of the prepared hydrogel samples. All spectra showed absorption bands in the region of 3500 to 3200 cm−1 corresponded to the –NH group of CS, which are masked by the absorption bands of the –OH groups present in CS. The bands at 2925 and 2855 cm−1 are assigned to asymmetric and symmetric vibrations of –CH bonds, respectively.[19] The existence of hydrogen bonding between components is inferred by the shift of the sharp band at 1653 cm−1 towards a lower wave number (1646 cm−1). This hydrogen bonding may occur between the carbonyl groups of PVP and the hydroxyl groups of CS,[28] as shown in Scheme 1. The new Si–N bonds which develop due to the interactions between CS and TEOS are shown in the spectra at 1152 cm−1. The bands at 1288 and 1028 cm−1 are ascribed to the –C–O–C acyclic and cyclic linkages of CS, respectively. The band at 455 cm−1 is ascribed to the Si–O–Si linkages of TEOS, which develops hydrogen bonds between CS and PVP.[29]

Fig. 2

FTIR spectra of the as-prepared MRHs.

Swelling behaviour

Swelling in distilled water

The release response of MRHs is greatly dependent on the swelling index. In fact, the release mechanism of drugs is dependent upon the swelling ratio. The hydrogels started to absorb water when they came in contact with distilled water, and this degree of swelling increased up to a specific time. As shown in Fig. 3, inclusion of TEOS had a significant effect on the swelling response of the studied hydrogel samples. As the concentration of TEOS increased, the swelling response of the hydrogels showed an upward trend. However, this increasing behaviour was observed up to an optimum concentration of TEOS; beyond that, the swelling index was detected to decrease. The first increasing trend is due to the increase of hydrophilicity by increasing the TEOS content, which caused an increase in the number of hydroxyl groups.[30] The later decreasing behaviour is due to the fact that the high concentration of crosslinker restricted the movement of the CS and PVP chains by developing a compact network, thus hindering the absorption of water into the crosslinked network.[31]

Fig. 3

Swelling indices of the as-prepared MRHs in distilled water.

Water diffusion mechanism

Generally, the swelling of hydrogel materials depends upon the diffusion mechanism, i.e. the diffusion of water from the extracellular matrix to its structure. The diffusion mechanism can be described by eqn (5):where F is the fractional swelling determined by the swelling ratio of Wt and Weq (Wt is the weight at time t and Weq is the weight of the material at the equilibrium time (min), respectively), k is the rate constant and n is the swelling exponent. The swelling data of the MRHs were used to measure the values of n and k. The plots of ln(F) vs. ln(t) are shown in Fig. 4, and the values of the diffusion parameters are given in Table 1.

Fig. 4

ln(F) vs. ln(t) plots of the MRHs.

Diffusion parameters and gel fractions of the MRHs

Parameter	MRH-1	MRH-2	MRH-3	MRH-4	MRH-5
n	0.21	0.35	0.31	0.18	0.20
Intercept	−0.466	−0.741	−0.691	−0.406	−0.434
K	0.627	0.476	0.501	0.666	0.648
Regression (R%)	90	96	98	91	92
Gel fraction (%)	64.68	71.23	83.37	86.24	89.65

It can be observed that the value of n is less than 0.5, which corresponds to the Fickian transport mechanism; this indicates that the rate of diffusion was lower than the rate of relaxation.

The gel fraction of a hydrogel is the ratio of the dried crosslinked polymer network to the dried hydrogel sample before washing. It can be observed in Table 1 that the gel fractions of the MRHs increased with increasing concentration of crosslinker.

Swelling in pH solutions

Inspection of Fig. 5 reveals quantitatively different swelling behaviours at different pH values (2, 4, 6, 7, 8 and 10). It was observed that at lower pH, the prepared MRHs showed pronounced swelling compared to the swelling in neutral and alkaline conditions. Because PVP is not significantly sensitive to pH, the swelling changes are mainly due to CS in different pH solutions. At low pH, the amine groups of CS undergo protonation, which leads to repulsion of the NH3+–NH3+ groups in the polymer chains; this ultimately increases the osmotic pressure inside the network and dissociates secondary interactions such as H-bonding, allowing the absorption of more water into the polymer chains of the MRHs.[18,32] As the pH increases towards neutral and alkaline conditions, deprotonation of the amine functional groups takes place and the NH3+ groups change back to NH2 moieties; this causes the formation of H-bonds among amino groups, and shrinkage of the repulsion of the polymer chains eventually occurs.[33]

Fig. 5

Swelling indices of the as-prepared MRHs in buffer solutions.

The degrees of swelling of the MRHs depend upon the network structures of the hydrogels, which are determined by the amount of crosslinker. Beyond the optimum concentration of crosslinker, the networks of the MRHs become denser, which leads to a decrease in swelling.[34] Therefore, in different buffer solutions, MRH-3 showed the maximum swelling; after that concentration, due to the denser networks, the swelling showed a decreasing trend.

Swelling in electrolyte solutions

Hydrogels do not show substantial swelling capacity in electrolyte solutions due to the imbalance of hydrophilic–hydrophobic ions in the network and the ex-osmosis phenomenon.[35] The swelling indices of the prepared hydrogels in NaCl and CaCl2 at different concentrations are shown in Fig. 6 and 7, respectively. It was observed that the swelling ratios of the hydrogel samples decreased with increasing concentration of the salt solutions. The shrinkage and swelling behaviour of hydrogels in salt solutions can be determined by ionic interactions between fixed charges and mobile ions, which develop osmotic pressure between the external solutions and the hydrogel samples. At higher concentrations of NaCl solution, the swelling in the hydrogels decreased due to the increase in osmotic pressure of the solution ions and the decrease in Donnan osmotic pressure. The different swelling behaviour with different crosslinker contents is attributed to changes in the crosslinking density in the hydrogel networks.[36,37]

Fig. 6

Swelling indices of the as-prepared MRHs in NaCl solutions.

Fig. 7

Swelling indices of the as-prepared MRHs in CaCl2 solutions.

Fig. 7 shows that the equilibrium swelling of the hydrogels was lower in CaCl2 compared to NaCl with increasing salt concentration. This result is attributed to the decrease in the osmotic pressure difference between the external solvent and the hydrogel. The charge shielding effect of cations is another parameter that affects the swelling in salt solutions. This effect decreases the anion–anion repulsive forces in the hydrogels.[38] The swelling of the hydrogels follows this order: Na+ > Ca2+. Another reason is the electrostatic interactions between the cationic salt ions and the anionic groups of the polymer chains; this results in an increase in ionic crosslinking, which increases the rigidity and causes deswelling of the hydrogels.[39]

The thermal stability of the MRHs was examined by TGA. This is considered to be the most reliable method to determine the thermal stability of materials. The thermograms of the MRHs showed multiple weight loss stages of the prepared hydrogels (Fig. 8). The first step weight loss from room temperature to 260 °C is due to the evaporation of moisture, bound water and H-bonded water due to the strongly absorbing nature of CS and PVP.[40] However, this degradation step was different for the different MRH samples due to the different water absorption capacities of each individual sample. The next stage of weight loss up to 400 °C is due to the scissoring of interactions between different ingredients and degradation of the ether linkages present in CS. The last stage of weight loss is corresponded to the degradation of the backbone chains of the polymers.[41] The broadening in the decomposition of all samples indicated the homogeneous blending of CS with PVP, which formed hydrogen bonds between the components.[42]

Fig. 8

TGA thermograms of the as-prepared MRHs.

These thermograms also demonstrated the effects of the crosslinker loading on the thermal stability of the prepared MRHs. It can be observed that the thermal stability of the samples increased dramatically with increasing concentration of TEOS up to MRH-3 (35.76% residue). When the concentration of TEOS was increased fourfold (200 μL), the thermal stability started to decrease (26.8% residue). A further increase in TEOS concentration caused a significant decrease in the thermal stability (21.17% residue). Hence, MRH-3 can be considered as a threshold towards maximum thermal stability of these materials.[34]

In order to evaluate the crystalline behaviour of the prepared MRHs, WAXRD was conducted. The WAXRD patterns of the MRHs are shown in Fig. 9. The crystalline peaks at 18.89° and 26.4° are due to the semi-crystalline nature of CS.[43,44] The peaks of PVP appear at approximately the same positions; therefore, both peaks overlap in the same region.[45] CS shows two crystalline peaks due to the hydroxyl and amino moieties of CS, which are more susceptible to forming strong hydrogen bonds and show crystalline behaviour. The small shifts and broadness of the diffraction peaks are due to the high miscibility and intermolecular interactions between the components.[46]

Fig. 9

WAXRD spectra of the as-prepared MRHs.

Mechanical integrity is an important property for in vitro and in vivo applications of hydrogels in controlled drug release systems. UTS and E% were evaluated to examine the mechanical properties of the MRHs, and the results are shown in Fig. 10. For in vivo applications, hydrogels should be pliable enough to endure surrounding tissues and have enough structural integrity to withstand subcutaneous and intraluminal pressure from surrounding structures.[47] It was observed that UTS and E% increased gradually up to a TEOS concentration of 150 μL; beyond that concentration, a decreasing trend was observed. The enhancement of these properties is due to increased interactions and crosslinking between CS, PVP and TEOS because various types of chemical and physical crosslinks exist in the system to develop the network structure. The decreases in the UTS and E% may be due to the development of more compact network structures, which increase the brittleness and ultimately decrease the mechanical properties of the samples. The improved fracture strain and toughness can enhance their performance in novel biomedical applications.[48]

Fig. 10

UTS and E% of the as-prepared MRHs.

In the microscopy of hydrogels, it is imperative that the hydrogels are in a hydrated form to ensure accurate representation of their swollen structures. Commonly used microscopic techniques such as scanning electron microscopy and transmission electron microscopy result in changes in the microstructures and crystallinity of hydrogels due to drying during microscopic analysis.[49] To restrain the effects of drying, prepared MRHs in dry and swollen forms were analyzed by an optical microscope. The brown images in Fig. 11 show micrographs of the dried MRHs, while the respective black images show micrographs of the swollen samples. It can be observed that with increasing concentration of crosslinker, a more compacted network structure appears. In the swollen micrographs, the pockets or pore sizes increase up to the MRH-3 sample; however, beyond that concentration, a declining trend was observed. This behaviour of the MRHs is due to the decrease in the distance between the polymer chains, the increase in hydrogen bonding, and crystallite formation.[50] This result is in accordance with the behaviour noted for the swelling indices in water.

Fig. 11

Optical micrographs of (a) dried and (b) swollen MRHs.

In vitro biodegradation analysis

The degradability of a material determines its mode of application, and the degradation behaviour of the hydrogels was determined with respect to time by weight loss measurements. The MRHs showed downward trends with time (Fig. 12); this degradation is due to the fact that CS degrades in PBS solution at a slow rate. The connectivity of the CS-based hydrogel network is linked with CC bonds, which yield alkyl linkages. Hence, the degradation of the hydrogel samples is due to dissociation of the glycosidic bonds of the CS molecules.[51] The graph shows that the hydrogels degraded consistently with time (14.28% from MRH-1 to MRH-3; the degradation extent was lower at higher concentrations of crosslinker). This lower degradation extent at higher loadings of TEOS was ascribed to the higher crosslinking densities and the compact networks of the hydrogels. This increased compact network of the material is responsible for absorbing a lower amount of water, which can assist the degradation. These results are in agreement with those of McBath and Ship.[52]

Fig. 12

Biodegradation of the as-prepared MRHs in PBS solution.

Antimicrobial activity

The antibacterial activities of the MRHs were determined using E. coli by implementing the JIS L 1902-2002 test to evaluate the resistance of bacterial growth. The antibacterial activities of the prepared MRHs are shown in Fig. 13 in terms of optical density (OD). The OD of the control sample (without hydrogel sample) was observed as 1.287, while those of the other samples containing hydrogels were lower; this provides evidence of the antibacterial properties of the hydrogels against E. coli. The lowest OD value is that of MRH-3; after that optimum concentration of crosslinker, the OD values are slightly high. The inclusion of hydrophilic crosslinker moieties (silanol groups of TEOS) in the hydrogels allowed the formation of hydrophilic hydrogels with good swelling indices in aqueous and organic media and with greater positive charge densities. The CO and NH– moieties in PVP and CS present in the MRHs could be protonated and the net positive charge density was eventually strengthened, which led to better antibacterial activity.[53]

Fig. 13

Antibacterial activities of the as-prepared MRHs.

Cytotoxicity analysis

In vitro cytotoxicity analysis provides insight into potential issues with local tissue response. One method to determine cell and tissue response is to evaluate the cytotoxicity, or the level of toxicity to cells. Cytotoxicity can be determined by the inhibition of cell proliferation or cell lysis.[54]In vitro cytotoxicity analysis of the prepared hydrogel samples was performed by counting live and dead nauplii by light microscope and then applying the formula described in Section 3.7. Deaths of nauplii may be due to three reasons: cytotoxicity of chemicals, deficiency of dissolved oxygen in sea water and development of a viscous layer on the gills of the nauplii.[27] In this work, the possibility of the death of the nauplii due to toxicity is very low because the percent mortality is very low at lower concentrations of crosslinker (Table 2). Moreover, these hydrogel samples were prepared by CS, PVP and TEOS, and all these ingredients are biocompatible and approved by the FDA. The low percent mortality of the hydrogel samples may be due to the formation of viscous layers on the gills of the nauplii; this eventually inhibits the oxygen permeability and causes the deaths of nauplii and an increase in the percent mortality beyond the optimum concentration (150 μL) of TEOS.[55]

Percent mortality of A. salina after 24 h exposure to the MRHs

Type of hydrogel	Mortality (%)
MRH-1	2.35
MRH-2	2.44
MRH-3	2.05
MRH-4	2.34
MRH-5	2.67

Drug release profiles

Drug release profiles in PBS and SIF solutions

Based upon the mechanisms of drug release from the polymer network, drugs are released by four different mechanisms, which are stimulated release, degradation-controlled, solvent-controlled and diffusion-controlled. The solvent-controlled mechanism is further classified into osmotic pressure-controlled and swelling-controlled mechanisms.[56] The drug release behaviour of the prepared hydrogels is strongly linked to the swelling characteristics of the hydrogels, which is a key parameter of the structural design of hydrogels. When a hydrogel undergoes swelling, its mesh size increases, and drug release to the surface of the device occurs through the diffusion pathways.[57,58]

In vitro drug release of lidocaine from MRH-3 was evaluated in SGF, SIF and PBS solutions as a function of time, as shown in Fig. 14. In SGF solution, the lidocaine was completely released in less than 30 min; this is not in accordance with the standard pharmacopeia, according to which the release of a drug must not be greater than 10% in SGF solution. This release profile shows that 96.37% lidocaine was released in a controlled way in 110 min in PBS (pH 7.4) solution; whereas in SIF, 94.37% lidocaine was released in 110 min, which is in accord with the US pharmacopeia standard (USP XXIV).[59]

Fig. 14

Drug release profiles of MRH-3 in (a) PBS solution (pH 7.4) and (b) SIF solution (pH 6.8) at 37 °C.

At pH values close to neutral, such as 6.8 and 7.4, the amino groups of CS are not protonated, which causes development of the physical networks in the hydrogels. The resulting network is responsible for the controlled release of lidocaine in PBS solution.[62] The remaining amount of drug could not be easily determined because the hydrogel film was broken into tiny pieces. Butt et al. developed a hydrogel using CS and determined its drug release behaviour in PBS, SGF and SIF solutions.[60] The results indicated that the prepared hydrogel can be used for controlled drug delivery systems and other biomedical applications.

Drug release in electrolyte solutions

Generally, as the concentration of electrolyte solution increases, the polymer solubility decreases and, ultimately, the drug release rate slows. The amount of water available to hydrate the polymer, which ultimately releases the drug after swelling, will decrease because more water is required to maintain the ions in electrolyte solutions. The type of ion also affects the extent of polymer hydration.[61]

The in vitro drug release profiles of MRH-3 in NaCl and CaCl2 solutions as a function of time are shown in Fig. 15. It was observed that the lidocaine release was slower in CaCl2 solutions than in NaCl solutions at higher concentrations of the electrolytes. At a lower concentration (0.1 M) of electrolyte, the polymer chains swell and allow the drug to be released; whereas, at a higher concentration (0.5 M), less water is available to swell the polymer chains, and the rate of drug release was therefore more slow.

Fig. 15

Drug release profiles of MRH-3 in (a) NaCl and (b) CaCl2 solutions.

Conclusions

A novel multi-responsive series of hydrogels which are capable of prolonging the release of lidocaine were successfully devised in this study by a solution casting approach. These prepared hydrogels contain complex networks of CS, PVP and TEOS and have sufficient mechanical integrity, i.e. UTS of 78 MPa and E% of 48, to carry the drug through the body. The physical and chemical intermolecular interactions among all the components of the hydrogels were confirmed by FTIR spectroscopy. The prepared hydrogels showed the highest swelling indices (140.75 g g−1) in distilled water, at acidic pH (pH 4) and in electrolyte solutions at the optimum concentration (150 μL) of crosslinker. The hydrogel sample with the same concentration of TEOS showed the highest thermal stability (35%) as evaluated by TGA, and its crystalline behaviour was assessed by WXRD. Optical microscopy of dried and swollen MRH samples was also conducted to evaluate their porous and networked structures. On the basis of their biodegradability, antimicrobial activity and cytotoxicity analyses, we envision that our MRHs will find potential applications in drug delivery. To validate the significance of the prepared MRHs, controlled release (96.14 and 94.37%) of lidocaine-loaded MRH-3 was obtained in PBS and SIF solutions, respectively, over a period of 110 min; thus, this hydrogel is a potential candidate for use in in vivo drug release applications.

Conflicts of interest

There are no conflicts to declare.