**Abstract**

Chitosan (CS) is a polymer obtained from chitin, being this, after the cellulose, the most abundant polysaccharide. The fact of (i) CS being obtained from renewable sources; (ii) CS to possess capability for doing interactions with different moieties being such capability dependent of pH; (iii) plenty of possibilities for chemical modification of CS; and (iv) tuning the final properties of CS derivatives makes this polymer very interesting in academic and technological points of view. In this way, hydrogels based on CS and on CS derivatives have been widely used for biomedical applications. Other important technological applications can be also cited, such as adsorbent of metals and dyes in wastewater from industrial effluents. In pharmaceutical field, hydrogels based on CS are often used as drugs' and proteins' carrier formulations due to the inherent characteristics such as the biocompatibility, nontoxicity, hydrophilicity, etc. This chapter is an attempt for updating and joining the plenty of available information regarding the preparation, characterization, and biomedical application of hydrogels based on chitosan and chitosan derivatives. More than 260 references are provided, being the majority of them published in the last 10 years.

**Keywords:** hydrogels, chitosan, chitosan derivatives, biomedical application, protein and drug delivery

### **1. Introduction**

Among the diverse types of polymeric materials, the biopolymers represent an important class. Extensive research has been conducted on biodegradable polymeric materials, mainly because they are, in a huge majority, from renewable sources. Some of them present wide availability in nature and can be obtained for a low price. Frequently, they exhibit characteristics such as controlled reactivity, low toxicity, biocompatibility, biodegradability, and filmogenic properties [1, 2]. These

materials have gained attention due to environmental issues such as the reuse of organic waste and/or its reduction, preservation of natural resources [3–5].

There are a number of diverse naturally occurring polymers, such as those belonging to the class of polyesters, those obtained from bacterial sources, polymers of animal origin, proteins, and polypeptides. They can be easily used to produce fibers or particles at micro- or nanoscale for diverse and interesting pharmaceutical applications [6, 7]. Polysaccharides, in general, have some abundance in nature and are also biodegradable and nontoxic [8], making them an active subject of study. Because it is a vast field, many other polymers can also be used, and the decision must be according to the sought-after application. Chitosan (CS) is one of most important examples.

Chitosan is obtained from chitin (CT) that is the most abundant polysaccharide after cellulose [8]. CT is a linear, natural, biodegradable, biocompatible, and nontoxic polymer that is insoluble in most solvents [8, 9]. Chitosan is applied in several fields: agriculture, waste treatment, food, textile, and pharmaceutical industries, cosmetics development, and biomaterials such as gels, films, polymer membranes, and nanofibers [8, 9]. The vast and numerous applications are due to the chitosan's interesting properties. In addition to those mentioned, healing, antimicrobial, antifungal, and chelating properties may be also included [10, 11]. Besides, different methodologies and strategies for chitosan applications have been proposed in the literature. Development of hydrogels is one of such methodologies that have gained much attention. Hydrogels are three-dimensional structures formed by hydrophilic polymers that can absorb water or biological fluids [12]. The absorption capacity is due to the presence of cross-linking points, which can be chemical or physical, making these structures insoluble, with the possibility of controlling the pore size in the hydrogels during the preparation method [13]. Because of these characteristics, they have been widely used in various fields of science, such as pharmacy, environmental chemistry, and biomedicine [8, 14].

Hydrogels based on chitosan have attracted lot of attention since this biopolymer is degraded in humans by lysozyme [15], making it highly attractive for the fabrication of dressings. The chitosan dressings can, for example, aid in the absorption of wound secretions and control the hydration of the affected region. Furthermore, for another application in biomedicine, that is, skin regeneration, the polysaccharide chitosan, in addition to exhibiting the aforementioned several characteristics of interest, reduces the healing time of lesions caused by compromises, stimulates cell proliferation, and confers excellent mechanical resistance on the biomaterials [16–18].

In this chapter, the focus was on hydrogels based on chitosan and its derivatives. The study sought to harness the properties of chitosan toward hydrogel applications and to investigate its extensive use in the field of biomedicine.

#### **1.1 Basic concepts and useful properties of hydrogels**

Hydrogels are defined as three-dimensional (3D) polymer networks formed by cross-linking hydrophilic homopolymers (or copolymers) that have the ability to absorb large amounts of water and/or biological fluids [19]. Plenty of materials, both natural and synthetic, or mixture of them, fit the definition of hydrogels.

The physical, chemical, and mechanical properties of hydrogels are dependent on intra- and intermolecular interactions among polymer groups or chain segments and solutes/solvents that may be present inside of 3D structure. The interest in this class of materials (hydrogels) has increased significantly in the academic and technological media due, mainly, to the inherent characteristics such as malleability, biocompatibility, nontoxicity, and swelling in the presence of water or biological fluids, without, however, dissolving [20]. The studies show that the most important

**61**

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

characteristic of hydrogels, the swelling, can be significantly altered through variation of external stimuli. Such change is accompanied by alteration in mechanical

Depending on the nature of the 3D network, hydrogels can be divided in two categories: (i) chemical hydrogels and (ii) physical hydrogels. The 3D matrix of chemical hydrogel has cross-links, which are formed by covalent bonds; in the other class, the 3D matrix is formed by physical interactions. Such physical interactions arise due to the presence of (i) groups with opposite electrical charges (electrostatic interactions, as in the case of polyelectrolyte complexes or PECs) and (ii) dipolar or hydrophobic groups (that works for physical hydrogel forming, as is the case of the hydrogels obtained by the process of freezing-thawing) [23, 24]. Thus, the use cross-linking agents is not needed for preparing physical hydrogels. Another characteristic that distinguishes physical hydrogels is the reversibility of cross-links, that is, the 3D matrix of a physical hydrogel can be destroyed by varying pH, temperature, ionic strength, etc. A typical example of physical hydrogel is that obtained by cross-linking alginate through complexation of carboxylic groups (existing in alginate chains) with calcium ions [19, 25]. A very widespread model known as egg box is used to explain this type of gelation [26]. The alginate/Ca2+ matrix may be broken down under acidic conditions and/or by the addition of EDTA [27]. In the case of physical hydrogels, polymer-ion (for example, alginate/Ca2+ matrix) or polymer-polymer interactions (for example, complexation between anionic and cationic polymers) should prevail in relation to the polymer-solvent interactions. Without such prevalence, the gelation process would be prevented

Several methods can be used for the production of chemical hydrogels. Those involve radiation polymerization by free radicals, for example, the polyacrylamide hydrogel made by acrylamide reaction (AAm) in the presence of methylenebisacrylamide (MBAAm); hydrogels can also be made by polycondensation such as the cross-linking of polysaccharides by reaction with dialdehyde that is very frequent in literature. Other important example of hydrogel by polycondensation is the obtainment of chitosan hydrogel by reaction with glutaraldehyde. The disadvantage of such methods is the need for using initiators and/or catalysts. Such a disadvantage ceases to exist if the polymerization/cross-linking is induced by irradiation, for example, gamma radiation, which produces pure, sterile, and residue-free hydrogels and, beyond this, no catalysts or additives are required to initiate the reaction [28]. Because of this, obtaining hydrogels is a very useful method in the preparation of hydrogels for medical applications, where even a small contamination is undesirable [29, 30]. In this case, the disadvantage is the use of high-cost and rigidly controlled equipment that makes this process of little

The history of hydrogels began in the 1950s when Wichterle and Lim synthesized hydrogels based on 2-hydroxyethyl methacrylate copolymer with ethylene dimethacrylate [31] and applied them as contact lenses. They were the first gelatinous contact lenses with proven biocompatibility. The great commercial success of gelatinous contact lenses stimulated enormous interest in this type of materials. Subsequently, a wide range of studies enabled the development of hydrogels with different chemical structures, morphologies, and properties through several methodologies. The state of the art in the area of hydrogels is the synthesis of "intelligent" or "smart" hydrogels that modifies their properties once exposed to change of external stimulus, such as pH, temperature, light, or electric field [32]. Hydrogels sensitive to pH and temperature have been played an important role in the control of the drug transport and the drug delivery systems, because temperature and pH

are important environmental factors in biomedical systems [33–35].

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

and morphological properties [21, 22].

from occurring.

accessibility in many research groups.

#### *Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

characteristic of hydrogels, the swelling, can be significantly altered through variation of external stimuli. Such change is accompanied by alteration in mechanical and morphological properties [21, 22].

Depending on the nature of the 3D network, hydrogels can be divided in two categories: (i) chemical hydrogels and (ii) physical hydrogels. The 3D matrix of chemical hydrogel has cross-links, which are formed by covalent bonds; in the other class, the 3D matrix is formed by physical interactions. Such physical interactions arise due to the presence of (i) groups with opposite electrical charges (electrostatic interactions, as in the case of polyelectrolyte complexes or PECs) and (ii) dipolar or hydrophobic groups (that works for physical hydrogel forming, as is the case of the hydrogels obtained by the process of freezing-thawing) [23, 24]. Thus, the use cross-linking agents is not needed for preparing physical hydrogels. Another characteristic that distinguishes physical hydrogels is the reversibility of cross-links, that is, the 3D matrix of a physical hydrogel can be destroyed by varying pH, temperature, ionic strength, etc. A typical example of physical hydrogel is that obtained by cross-linking alginate through complexation of carboxylic groups (existing in alginate chains) with calcium ions [19, 25]. A very widespread model known as egg box is used to explain this type of gelation [26]. The alginate/Ca2+ matrix may be broken down under acidic conditions and/or by the addition of EDTA [27].

In the case of physical hydrogels, polymer-ion (for example, alginate/Ca2+ matrix) or polymer-polymer interactions (for example, complexation between anionic and cationic polymers) should prevail in relation to the polymer-solvent interactions. Without such prevalence, the gelation process would be prevented from occurring.

Several methods can be used for the production of chemical hydrogels. Those involve radiation polymerization by free radicals, for example, the polyacrylamide hydrogel made by acrylamide reaction (AAm) in the presence of methylenebisacrylamide (MBAAm); hydrogels can also be made by polycondensation such as the cross-linking of polysaccharides by reaction with dialdehyde that is very frequent in literature. Other important example of hydrogel by polycondensation is the obtainment of chitosan hydrogel by reaction with glutaraldehyde. The disadvantage of such methods is the need for using initiators and/or catalysts. Such a disadvantage ceases to exist if the polymerization/cross-linking is induced by irradiation, for example, gamma radiation, which produces pure, sterile, and residue-free hydrogels and, beyond this, no catalysts or additives are required to initiate the reaction [28]. Because of this, obtaining hydrogels is a very useful method in the preparation of hydrogels for medical applications, where even a small contamination is undesirable [29, 30]. In this case, the disadvantage is the use of high-cost and rigidly controlled equipment that makes this process of little accessibility in many research groups.

The history of hydrogels began in the 1950s when Wichterle and Lim synthesized hydrogels based on 2-hydroxyethyl methacrylate copolymer with ethylene dimethacrylate [31] and applied them as contact lenses. They were the first gelatinous contact lenses with proven biocompatibility. The great commercial success of gelatinous contact lenses stimulated enormous interest in this type of materials. Subsequently, a wide range of studies enabled the development of hydrogels with different chemical structures, morphologies, and properties through several methodologies. The state of the art in the area of hydrogels is the synthesis of "intelligent" or "smart" hydrogels that modifies their properties once exposed to change of external stimulus, such as pH, temperature, light, or electric field [32]. Hydrogels sensitive to pH and temperature have been played an important role in the control of the drug transport and the drug delivery systems, because temperature and pH are important environmental factors in biomedical systems [33–35].

*Hydrogels - Smart Materials for Biomedical Applications*

mental chemistry, and biomedicine [8, 14].

important examples.

materials have gained attention due to environmental issues such as the reuse of organic waste and/or its reduction, preservation of natural resources [3–5]. There are a number of diverse naturally occurring polymers, such as those belonging to the class of polyesters, those obtained from bacterial sources, polymers of animal origin, proteins, and polypeptides. They can be easily used to produce fibers or particles at micro- or nanoscale for diverse and interesting pharmaceutical applications [6, 7]. Polysaccharides, in general, have some abundance in nature and are also biodegradable and nontoxic [8], making them an active subject of study. Because it is a vast field, many other polymers can also be used, and the decision must be according to the sought-after application. Chitosan (CS) is one of most

Chitosan is obtained from chitin (CT) that is the most abundant polysaccharide after cellulose [8]. CT is a linear, natural, biodegradable, biocompatible, and nontoxic polymer that is insoluble in most solvents [8, 9]. Chitosan is applied in several fields: agriculture, waste treatment, food, textile, and pharmaceutical industries, cosmetics development, and biomaterials such as gels, films, polymer membranes, and nanofibers [8, 9]. The vast and numerous applications are due to the chitosan's interesting properties. In addition to those mentioned, healing, antimicrobial, antifungal, and chelating properties may be also included [10, 11]. Besides, different methodologies and strategies for chitosan applications have been proposed in the literature. Development of hydrogels is one of such methodologies that have gained much attention. Hydrogels are three-dimensional structures formed by hydrophilic polymers that can absorb water or biological fluids [12]. The absorption capacity is due to the presence of cross-linking points, which can be chemical or physical, making these structures insoluble, with the possibility of controlling the pore size in the hydrogels during the preparation method [13]. Because of these characteristics, they have been widely used in various fields of science, such as pharmacy, environ-

Hydrogels based on chitosan have attracted lot of attention since this biopolymer is degraded in humans by lysozyme [15], making it highly attractive for the fabrication of dressings. The chitosan dressings can, for example, aid in the absorption of wound secretions and control the hydration of the affected region. Furthermore, for another application in biomedicine, that is, skin regeneration, the polysaccharide chitosan, in addition to exhibiting the aforementioned several characteristics of interest, reduces the healing time of lesions caused by compromises, stimulates cell proliferation, and confers excellent mechanical resistance on the biomaterials [16–18].

In this chapter, the focus was on hydrogels based on chitosan and its derivatives. The study sought to harness the properties of chitosan toward hydrogel applications

Hydrogels are defined as three-dimensional (3D) polymer networks formed by cross-linking hydrophilic homopolymers (or copolymers) that have the ability to absorb large amounts of water and/or biological fluids [19]. Plenty of materials, both natural and synthetic, or mixture of them, fit the definition of hydrogels. The physical, chemical, and mechanical properties of hydrogels are dependent on intra- and intermolecular interactions among polymer groups or chain segments and solutes/solvents that may be present inside of 3D structure. The interest in this class of materials (hydrogels) has increased significantly in the academic and technological media due, mainly, to the inherent characteristics such as malleability, biocompatibility, nontoxicity, and swelling in the presence of water or biological fluids, without, however, dissolving [20]. The studies show that the most important

and to investigate its extensive use in the field of biomedicine.

**1.1 Basic concepts and useful properties of hydrogels**

**60**

The use of natural polymers in the preparation of hydrogels has attracted the attention of many researchers both for their natural abundance and for their better biocompatibility when used as biomaterials, with chitosan being one of the most commonly used [36]. Hydrogels derived from natural sources are advantageous because of their inherent biological properties and are widely researched for tissue engineering applications. However, as with other naturally occurring materials, variation in batch composition represents an important disadvantage [37].

#### **1.2 Techniques often used for hydrogel characterization**

The analysis of morphology, molecular structure, mechanical properties, and sensitivity to pH and temperature can be done through a great number of qualitative and quantitative techniques. The capability of absorbing liquids (swelling) is the main property of hydrogels, which depends on the hydrophilicity of the hydrogel matrix. From this characteristic, another important aspect arises: the liquid retention capacity of the hydrogel matrix. Changes associated to the swelling (or the shrinking), are controlled by various parameters such as temperature, pH, salinity, and ionic strength of the medium [38]. Superabsorbent hydrogels have the ability to absorb and retain large amount of liquid (*S* ≥ 100) [39]. They are prepared using highly hydrophilic moieties (polymers or monomers) and have important technological applications, for instance, in environment (as ion and/or dye absorbent) [40] and agriculture (as soil conditioner or nutrient carriers) [41].

The absorbability of the liquid or the swelling (*S*) capability of the hydrogels is generally calculated by the following equation [39].

$$\mathbf{S} = \left(\mathbf{W}\_t - \mathbf{W}\_d\right) / \mathbf{W}\_d \tag{1}$$

**63**

monly performed [59].

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

that allows to correlate the necessary force (stress) to induce deformation of these soft materials during compressive tests (for example, strain-stress measurements of compression). In addition, rheological measurements should be cited here [52]. Very important parameters, such as the size of pore and the porous distribution of hydrogel and hydrogel composites, as well as the dispersion of the loads inside the matrix, can be obtained from the images obtained from sample under stress using microscopies techniques. Atomic force microscopy (AFM) in its different modalities is often used to evaluate the surface morphology and topography of hydrogel and hydrogel composites [53, 54]. Finally, scanning electron microscopy (SEM) and transmission electron microscopy (TEM) [54] are also very often techniques for analyzing the structure of hydrogels. In this way, lyophilization of swollen hydrogels and further fracture are important strategies for analysis of pore

Chitosan is a β-(1→4)-d-glucosamine copolymer obtained from chitin [55]. The main sources for chitin extraction and production are crustaceous shells, mollusks, insects, silkworm chrysalides, and microorganisms [56]. Chitin is commonly synthesized in six steps: (i) pretreatment, (ii) demineralization, (iii) deproteinization, (iv) bleaching, (v) deodorizing, and (vi) drying [57]. In the pretreatment processes, washes of the specific chitin source are carried with distilled water, aiming to remove vegetal compounds, organic tissues, contaminants, clays, and soil residues [58]. Demineralization process is carried out using diluted hydrochloric acid solutions under heating, aiming to decrease ash and mineral residues as calcium and magnesium. Other common reagents that may be used for the demineralization of chitin sources are nitric, sulfur, and acetic acids. The deproteinization process is performed using diluted sodium hydroxide solution for the removal of proteins. This process must be performed after the demineralization process. Reagents often employed in the deproteinization processes include sodium carbonate, potassium hydroxide, sodium phosphate, and calcium hydroxide [58]. Bleaching and deodorizing processes are responsible for removing color pigments and improving the taste of the prepared polysaccharide, respectively. Both processes can be performed by using diluted sodium hypochlorite solution [55]. Mixture containing sodium hypochlorite and hydrochloric acid needs sometimes to be used [55]. After each process, subsequent washes with distilled water must be performed, aiming to neutralize the final polysaccharide. Drying processes either by lyophilization under −60.0°C or in an oven at temperatures ranging from 60.0 to 80.0 ± 1.0°C are com-

Chitosan is widely prepared from the chitin deacetylation using concentrated sodium hydroxide solution containing sodium borohydride with the aim of avoiding the polysaccharide degradation [60]. Many primary amino groups are removed from the chitosan molecule during hydrolyze reaction, resulting in polysaccharide chains with different sizes [61]. In this case, the molar mass distribution is influenced for parameters such as extraction time, temperature, reagent concentration, and atmospheric conditions. So, chitosan molecules can have different molar masses as compared to parent chitin. Beyond this, deacetylation degrees and viscosities are influenced by deacetylation process that may significantly affect the performance of the final polysaccharide [62]. Some important parameters that are monitored during the obtainment of chitosan with high deacetylation degree are temperature [63], concentration of sodium hydroxide, and step numbers evolved on chitin modification reaction [64]. Enzymatic deacetylation of chitin for the

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

size and its distribution within the 3D matrix.

**2. Chitosan obtainment through chitin deacetylation**

where *Ws* is the weight of the swollen hydrogel and *Wd* is the weight of the dry hydrogel. Thus, this ratio relates the amount of the mass of liquid absorbed to the mass of dry hydrogel. The parameter *S* can be evaluated aiming to determine the maximum mass of fluid that a giving hydrogel is capable of absorbing (steady state) or can be evaluated at different time intervals to determine the kinetic swelling up to the equilibrium has been reached.

Evaluation of parameters related to swelling kinetics is important for hydrogel characterization during swelling. The swelling process is controlled by diffusion and/or relaxation. Different models for predicting the release behavior of hydrogel matrices dipped in pure solvent, solvent mixture, or solute-solvent solution have been developed. Brazel and Peppas [42, 43] developed a semiempirical equation that is widely used, even if it fits only for the initial 60% of the absorbed consumer liquid. In this way, other mathematical models have been proposed to fit the swelling profile in the whole time scale [44].

Aspects such as the type of functional groups present at polymer chains, the network type, the cross-link density, etc., as well as the intermolecular interactions (e.g., H-bond, ionic interactions, etc.), define the physical and chemical properties of hydrogels. They have been thoroughly investigated by infrared (FTIR) techniques [45, 46], X-ray photoelectron spectroscopy (XPS) [47], nuclear magnetic resonance (NMR), and Mossbauer spectroscopies [48]. Differential scanning calorimetry (DSC) and thermogravimetry (TGA) have been used for analysis of thermal behavior [49], while the crystallinity of the hydrogels have been evaluated mainly by small and wide X-ray diffraction measurements (SAXS and WAXS) [49–51]. Different methods have been effectively used for evaluating mechanical properties of the hydrogels and hydrogel composites. For example, the elastic modulus (*E*) can be evaluated using data collected on a texturometer equipment

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

that allows to correlate the necessary force (stress) to induce deformation of these soft materials during compressive tests (for example, strain-stress measurements of compression). In addition, rheological measurements should be cited here [52].

Very important parameters, such as the size of pore and the porous distribution of hydrogel and hydrogel composites, as well as the dispersion of the loads inside the matrix, can be obtained from the images obtained from sample under stress using microscopies techniques. Atomic force microscopy (AFM) in its different modalities is often used to evaluate the surface morphology and topography of hydrogel and hydrogel composites [53, 54]. Finally, scanning electron microscopy (SEM) and transmission electron microscopy (TEM) [54] are also very often techniques for analyzing the structure of hydrogels. In this way, lyophilization of swollen hydrogels and further fracture are important strategies for analysis of pore size and its distribution within the 3D matrix.

#### **2. Chitosan obtainment through chitin deacetylation**

Chitosan is a β-(1→4)-d-glucosamine copolymer obtained from chitin [55]. The main sources for chitin extraction and production are crustaceous shells, mollusks, insects, silkworm chrysalides, and microorganisms [56]. Chitin is commonly synthesized in six steps: (i) pretreatment, (ii) demineralization, (iii) deproteinization, (iv) bleaching, (v) deodorizing, and (vi) drying [57]. In the pretreatment processes, washes of the specific chitin source are carried with distilled water, aiming to remove vegetal compounds, organic tissues, contaminants, clays, and soil residues [58]. Demineralization process is carried out using diluted hydrochloric acid solutions under heating, aiming to decrease ash and mineral residues as calcium and magnesium. Other common reagents that may be used for the demineralization of chitin sources are nitric, sulfur, and acetic acids. The deproteinization process is performed using diluted sodium hydroxide solution for the removal of proteins. This process must be performed after the demineralization process. Reagents often employed in the deproteinization processes include sodium carbonate, potassium hydroxide, sodium phosphate, and calcium hydroxide [58]. Bleaching and deodorizing processes are responsible for removing color pigments and improving the taste of the prepared polysaccharide, respectively. Both processes can be performed by using diluted sodium hypochlorite solution [55]. Mixture containing sodium hypochlorite and hydrochloric acid needs sometimes to be used [55]. After each process, subsequent washes with distilled water must be performed, aiming to neutralize the final polysaccharide. Drying processes either by lyophilization under −60.0°C or in an oven at temperatures ranging from 60.0 to 80.0 ± 1.0°C are commonly performed [59].

Chitosan is widely prepared from the chitin deacetylation using concentrated sodium hydroxide solution containing sodium borohydride with the aim of avoiding the polysaccharide degradation [60]. Many primary amino groups are removed from the chitosan molecule during hydrolyze reaction, resulting in polysaccharide chains with different sizes [61]. In this case, the molar mass distribution is influenced for parameters such as extraction time, temperature, reagent concentration, and atmospheric conditions. So, chitosan molecules can have different molar masses as compared to parent chitin. Beyond this, deacetylation degrees and viscosities are influenced by deacetylation process that may significantly affect the performance of the final polysaccharide [62]. Some important parameters that are monitored during the obtainment of chitosan with high deacetylation degree are temperature [63], concentration of sodium hydroxide, and step numbers evolved on chitin modification reaction [64]. Enzymatic deacetylation of chitin for the

*Hydrogels - Smart Materials for Biomedical Applications*

**1.2 Techniques often used for hydrogel characterization**

[40] and agriculture (as soil conditioner or nutrient carriers) [41].

generally calculated by the following equation [39].

to the equilibrium has been reached.

ing profile in the whole time scale [44].

The use of natural polymers in the preparation of hydrogels has attracted the attention of many researchers both for their natural abundance and for their better biocompatibility when used as biomaterials, with chitosan being one of the most commonly used [36]. Hydrogels derived from natural sources are advantageous because of their inherent biological properties and are widely researched for tissue engineering applications. However, as with other naturally occurring materials, variation in batch composition represents an important disadvantage [37].

The analysis of morphology, molecular structure, mechanical properties, and sensitivity to pH and temperature can be done through a great number of qualitative and quantitative techniques. The capability of absorbing liquids (swelling) is the main property of hydrogels, which depends on the hydrophilicity of the hydrogel matrix. From this characteristic, another important aspect arises: the liquid retention capacity of the hydrogel matrix. Changes associated to the swelling (or the shrinking), are controlled by various parameters such as temperature, pH, salinity, and ionic strength of the medium [38]. Superabsorbent hydrogels have the ability to absorb and retain large amount of liquid (*S* ≥ 100) [39]. They are prepared using highly hydrophilic moieties (polymers or monomers) and have important technological applications, for instance, in environment (as ion and/or dye absorbent)

The absorbability of the liquid or the swelling (*S*) capability of the hydrogels is

*S* = (*Ws*–*Wd*)/*Wd* (1)

where *Ws* is the weight of the swollen hydrogel and *Wd* is the weight of the dry hydrogel. Thus, this ratio relates the amount of the mass of liquid absorbed to the mass of dry hydrogel. The parameter *S* can be evaluated aiming to determine the maximum mass of fluid that a giving hydrogel is capable of absorbing (steady state) or can be evaluated at different time intervals to determine the kinetic swelling up

Evaluation of parameters related to swelling kinetics is important for hydrogel characterization during swelling. The swelling process is controlled by diffusion and/or relaxation. Different models for predicting the release behavior of hydrogel matrices dipped in pure solvent, solvent mixture, or solute-solvent solution have been developed. Brazel and Peppas [42, 43] developed a semiempirical equation that is widely used, even if it fits only for the initial 60% of the absorbed consumer liquid. In this way, other mathematical models have been proposed to fit the swell-

Aspects such as the type of functional groups present at polymer chains, the network type, the cross-link density, etc., as well as the intermolecular interactions (e.g., H-bond, ionic interactions, etc.), define the physical and chemical properties of hydrogels. They have been thoroughly investigated by infrared (FTIR) techniques [45, 46], X-ray photoelectron spectroscopy (XPS) [47], nuclear magnetic resonance (NMR), and Mossbauer spectroscopies [48]. Differential scanning calorimetry (DSC) and thermogravimetry (TGA) have been used for analysis of thermal behavior [49], while the crystallinity of the hydrogels have been evaluated mainly by small and wide X-ray diffraction measurements (SAXS and WAXS) [49–51]. Different methods have been effectively used for evaluating mechanical properties of the hydrogels and hydrogel composites. For example, the elastic modulus (*E*) can be evaluated using data collected on a texturometer equipment

**62**

production of chitosan is an excellent alternative to offset some disadvantages of the chemical deacetylation process such as high energy consumption, generation of acid and alkaline residues, and environmental concerns [59]. Currently, 1 ton billion of chitin and chitosan are annually produced, around the world, by biological processes. The chitin and chitosan production is industrially important, as these polysaccharides are not found in high amounts in the natural environment due to their high biodegradability. Hydrolytic enzymes such as lysozyme, chitinase, chitin deacetylase, and chitosanase are commonly present in body tissue of animals, plants, and soil, avoiding the bioaccumulation of chitin and chitosan in the natural environment. It is estimated that approximately 50,000 tons per year of chitin is worldly produced with 30,000 ton per year from crustaceous shells, excluding the Krill that has potential to produce 56,000 tons per year of chitin. Depending on the extraction method of chitin and production of chitosan, it is possible to recovery proteins, astaxanthin and carotenoid [65].

The main source of chitosan production is from chitin. For producing 1 kg of chitosan from shrimp shells with 70% deacetylation degree, 6.3 kg of hydrochloric acid, 1.8 kg of sodium hydroxide, and 1400 L of water are necessary. The yield for producing chitin from insects, shrimp shells, and silkworm chrysalides ranges from 1.4 to 2.0, 10 to 15, and 6 to 10%, respectively [55]. Commercial chitosan has deacetylation degree ranging from 70 to 95% and molar mass from 1.0 × 104 to 1.0 × 106 g mol<sup>−</sup><sup>1</sup> [59]. The acetylation reaction can be used for obtaining chitosan with deacetylation degree around 50% and high solubility in water [66]. Chitin and chitosan are commercially produced in India, Japan, Poland, Norway, Australia, and China with costs that are dependent on the physical and chemical properties and desired application [55].

Chitin is extracted from different sources in α-chitin, β-chitin, or γ-chitin forms as indicated in **Figure 1a–c**. The α-chitin is the most abundant form of chitin that is commonly found in crab, shrimp, and lobster shells. It is rarely found in insects and fungi. β-Chitin is a rare form that can be also found in insects, chrysalides, crustaceous, and fungi. However, β-chitin is commonly found in squids. Finally, γ-chitin is found in cocoons of insects [55]. The α-chitin, β-chitin, and γ-chitin are identified by the position of acetyl groups in the molecular structure. The α-chitin is formed by repeating polymer units containing acetyl groups in opposite sides, alternating their position to each monomer (**Figure 1a**). The β-chitin has acetyl groups alternating to each two monomers (**Figure 1b**), while the γ-chitin has two acetyl groups in the same side of two monomers, followed by one acetyl group of the opposite side in the third monomer (**Figure 1c**) [67].

#### **2.1 Properties of chitosan**

CS is a nontoxic (DL50 of 16 g kg<sup>−</sup><sup>1</sup> , studies *in vivo* using rats), biodegradable, biocompatible, antiallergenic, anticoagulant, antifungal, and antimicrobial polysaccharide. These properties are important to apply CS as a biomaterial in medicine, pharmacy, and so forth [68]. Many biomaterials are developed by using CS as solid support due to its feasible biological properties. For instance, capsules of controlled drug release and adhesive films have been registered by the US Food and Drug Administration (FDA) for human applications. Moreover, CS-based biomaterials can be employed in controlled drug release systems, wound healing, filtration membranes, and so forth [66]. CS has been studied for the synthesis of medical biomaterial [69] due to its alkaline characteristic. As CS can be a zwitterionic polysaccharide that contains cationic/anionic groups in its molecular structure, it is efficient for the controlled drug release systems [69], water and wastewater treatment [70], and immobilization of enzymes [71]. The amino groups in the CS

**65**

**Figure 1.**

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

molecules have pKa values of approximately 6.5, which are deprotonated in higher pHs. Thus, the charge density depends on the pH value and deacetylation degree [55]. CS/silver zeolite composite films can be used for producing burn dressings [72], CS-hydroxyapatite composites can be used for hard tissue regeneration [73], and composite of CS/montmorillonite can be used as matrix for prolonged delivery of some nitric oxide donor compounds [74]. The application of CS as support for the synthesis of composite biomaterials depends on its physiochemical properties such as deacetylation degree and molar mass [75]. Composite materials based on polysaccharides are generally formed by blending either inorganic or organic species to polymer molecules. These composites may be synthesized by electrospray [76], sol-gel process [77], thermomechanical process [78], solvothermal method [79], precipitation and coprecipitation methods [80], solvent casting and evaporation process [81], simple mixing and heating method [75], biomimetic method [82], alternate soaking method [83], and so forth. Composite materials have physiochemical properties different from those ones of initially individual materials and depend on the type of the formed product. For instance, CS-magnetite composite has biodegradability, biocompatibility, mechanical resistance, and magnetic sensibility [84], and the CS-hydroxyapatite composite is pH-sensitive

*(a–c) Molecular structures of α-chitin (a), β-chitin (b), and γ-chitin (c).*

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

**Figure 1.** *(a–c) Molecular structures of α-chitin (a), β-chitin (b), and γ-chitin (c).*

molecules have pKa values of approximately 6.5, which are deprotonated in higher pHs. Thus, the charge density depends on the pH value and deacetylation degree [55]. CS/silver zeolite composite films can be used for producing burn dressings [72], CS-hydroxyapatite composites can be used for hard tissue regeneration [73], and composite of CS/montmorillonite can be used as matrix for prolonged delivery of some nitric oxide donor compounds [74]. The application of CS as support for the synthesis of composite biomaterials depends on its physiochemical properties such as deacetylation degree and molar mass [75]. Composite materials based on polysaccharides are generally formed by blending either inorganic or organic species to polymer molecules. These composites may be synthesized by electrospray [76], sol-gel process [77], thermomechanical process [78], solvothermal method [79], precipitation and coprecipitation methods [80], solvent casting and evaporation process [81], simple mixing and heating method [75], biomimetic method [82], alternate soaking method [83], and so forth. Composite materials have physiochemical properties different from those ones of initially individual materials and depend on the type of the formed product. For instance, CS-magnetite composite has biodegradability, biocompatibility, mechanical resistance, and magnetic sensibility [84], and the CS-hydroxyapatite composite is pH-sensitive

*Hydrogels - Smart Materials for Biomedical Applications*

proteins, astaxanthin and carotenoid [65].

g mol<sup>−</sup><sup>1</sup>

properties and desired application [55].

the third monomer (**Figure 1c**) [67].

CS is a nontoxic (DL50 of 16 g kg<sup>−</sup><sup>1</sup>

**2.1 Properties of chitosan**

production of chitosan is an excellent alternative to offset some disadvantages of the chemical deacetylation process such as high energy consumption, generation of acid and alkaline residues, and environmental concerns [59]. Currently, 1 ton billion of chitin and chitosan are annually produced, around the world, by biological processes. The chitin and chitosan production is industrially important, as these polysaccharides are not found in high amounts in the natural environment due to their high biodegradability. Hydrolytic enzymes such as lysozyme, chitinase, chitin deacetylase, and chitosanase are commonly present in body tissue of animals, plants, and soil, avoiding the bioaccumulation of chitin and chitosan in the natural environment. It is estimated that approximately 50,000 tons per year of chitin is worldly produced with 30,000 ton per year from crustaceous shells, excluding the Krill that has potential to produce 56,000 tons per year of chitin. Depending on the extraction method of chitin and production of chitosan, it is possible to recovery

The main source of chitosan production is from chitin. For producing 1 kg of chitosan from shrimp shells with 70% deacetylation degree, 6.3 kg of hydrochloric acid, 1.8 kg of sodium hydroxide, and 1400 L of water are necessary. The yield for producing chitin from insects, shrimp shells, and silkworm chrysalides ranges from 1.4 to 2.0, 10 to 15, and 6 to 10%, respectively [55]. Commercial chitosan has deacetylation degree ranging from 70 to 95% and molar mass from 1.0 ×

chitosan with deacetylation degree around 50% and high solubility in water [66]. Chitin and chitosan are commercially produced in India, Japan, Poland, Norway, Australia, and China with costs that are dependent on the physical and chemical

Chitin is extracted from different sources in α-chitin, β-chitin, or γ-chitin forms as indicated in **Figure 1a–c**. The α-chitin is the most abundant form of chitin that is commonly found in crab, shrimp, and lobster shells. It is rarely found in insects and fungi. β-Chitin is a rare form that can be also found in insects, chrysalides, crustaceous, and fungi. However, β-chitin is commonly found in squids. Finally, γ-chitin is found in cocoons of insects [55]. The α-chitin, β-chitin, and γ-chitin are identified by the position of acetyl groups in the molecular structure. The α-chitin is formed by repeating polymer units containing acetyl groups in opposite sides, alternating their position to each monomer (**Figure 1a**). The β-chitin has acetyl groups alternating to each two monomers (**Figure 1b**), while the γ-chitin has two acetyl groups in the same side of two monomers, followed by one acetyl group of the opposite side in

biocompatible, antiallergenic, anticoagulant, antifungal, and antimicrobial polysaccharide. These properties are important to apply CS as a biomaterial in medicine, pharmacy, and so forth [68]. Many biomaterials are developed by using CS as solid support due to its feasible biological properties. For instance, capsules of controlled drug release and adhesive films have been registered by the US Food and Drug Administration (FDA) for human applications. Moreover, CS-based biomaterials can be employed in controlled drug release systems, wound healing, filtration membranes, and so forth [66]. CS has been studied for the synthesis of medical biomaterial [69] due to its alkaline characteristic. As CS can be a zwitterionic polysaccharide that contains cationic/anionic groups in its molecular structure, it is efficient for the controlled drug release systems [69], water and wastewater treatment [70], and immobilization of enzymes [71]. The amino groups in the CS

[59]. The acetylation reaction can be used for obtaining

, studies *in vivo* using rats), biodegradable,

**64**

104

to 1.0 × 106

[85]. CS-iron (III) chloride composite membrane has excellent permeability for different fluids [86]. CS-carbon nanotube composite is mechanically resistant [87]. Carboxymethylated-CS composite protected with ruthenium nanoparticles was synthesized with good thermal stability [88]. Graphene oxide-CS nanocomposite films are formed with excellent mechanical and thermal properties [89], and montmorillonite-CS nanocomposites are produced with excellent biocompatibility and antimicrobial properties [89]. Moreover, CS-based composites were synthesized to be used as microcapsules in drug release systems [90], CS-porous-silica [91] and nanohydroxyapatite-CT derivative composites for bone regeneration [92], CS-zirconium composite as precursor of zirconium carbide [93], CS-barium sulfate composite fibers for endovascular prosthesis, fibrous embolic agent, bone substitution, and X-ray marker [89], CS composite reinforced with carbon nanotubes for biomedicine [78], and CS-hydroxyapatite-glycopolymer/cloisite composite for biomedical applications [94].

### **2.2 Main chitosan derivatives of technological interest**

Considering the vast number of functional groups available on the CS chains and the myriad of chemical compounds that can react with such groups, it is consensual that a plenty of possibilities regarding the use of CS derivatives as precursor materials for the synthesis of hydrogels applicable in drug delivery. There are some methodologies that allow these modifications to occur in CS, such as carboxymethylation, acetylation, and alkylation [7]. In this way, CS derivatives may appear, which seek to improve some properties of this polymer. Among them, the improvement in water solubility is often investigated [6, 95].

From the carboxymethylation reaction, a water-soluble CS derivative can be obtained over a wide pH range [95], and among those obtained so far, carboxymethyl CS stands out because it contains ether groups, and the -COOH and -NH2 groups [95]. Similarly to CS, the carboxymethylated-CS, also stands out because it exhibits interesting characteristics, such as antifungal activity, low toxicity, and membrane properties, which allows its application for drug release [96].

Quaternized CS through successive methylation in -NH2 groups [97] has been proposed using different methodologies, methacrylated glycol CS [98] and sulfated CS [99].

The methylation in -NH2 groups is a very interesting strategy allowing the N atoms be permanently charged with positive charges as -N(CH3)3 + . Such increase in positive charges allows the material (N,N,N-trimethylchitosan, TMC) be soluble in water in the whole range of pH [100]. Beyond this, the positive charges help for the occurrence of interactions of TMC and the membrane of gram-negative bacteria. So, the TMC has pronounced antibacterial activity [101]. There are several methodologies for synthesis of TMC [101–103]. The following methodology is often used for quaternization of CS: the dispersion of CS in N-methylpyrrolidone containing sodium iodide/methyl iodide in the presence of sodium hydroxide. At final, the iodide counterions of the reaction product are exchanged with chloride for obtaining a more stable salt. Some reviews of CS chemistry are recently published [101–103].

#### **2.3 Methodologies used for obtaining chitosan derivatives aiming at biomedical applications as hydrogels**

**67**

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

structural changes, in principle, lead to completely new properties as well as a significant improvement in water solubility [6, 95]. From the carboxymethylation reaction, a water-soluble CS derivative can be obtained over a wide pH range [95], and among those obtained thus far, carboxymethyl CS stands out because it contains ether, -COOH, and -NH2 groups [95]. Similar to CS, the carboxymethyl CS derivative also stands out because it exhibits interesting characteristics such as antifungal activity, low toxicity, and membrane properties, which allow its application in drug delivery systems [96]. In general, it is well known that a high degree of deacetylation and a narrow polymer molecular weight distribution are critical parameters for controlling the particle size distribution [107]. Evidently, the size of the particles has significant influence on the biomedical applicability of CS-based

It is well known that the hydrogel matrix structure is generally created from the hydrophilic groups (or domains) present in a natural or synthetic polymeric network upon hydration in an entirely aqueous environment [112]. On the other hand, it is also well known that the various properties exhibited by hydrogels (such as self-healing, biodegradability, swelling degree, mechanical resistance, and so on) are intrinsically related to the physical or chemical cross-linking methods [113, 114]. Hence, the physical cross-linking of hydrogels leads to the formation of a nonpermanent network due to noncovalent interactions (e.g., hydrogen or electrostatic bonds and physical entanglements) [22, 115–117]. Consequently, physically crosslinked hydrogels can be formed via ionic interactions of charges, that is, by utilizing the graft copolymers, crystallization, as well as the formation of different stereocomplex forms [117, 118]. Notably, CS can be self-cross-linked when the initial polymer concentration is beyond the critical concentration (C\*) for chain entanglement. In this condition, a precise balance between the hydrophilic and hydrophobic interactions is reached [114]. These values may be achieved after decreasing the apparent charge density by solvent evaporation or changing the dielectric constant of the medium [119]. Phosphate-bearing molecules such as polyacrylic acid, sodium alginate, heparin, and polyglutamic acid are the common anions used for physically cross-linked CS [120]. Sarmento et al. have reported the preparation of alginate/CS nanoparticle hydrogels by ionotropic pregelation of an alginate core followed by CS

polyelectrolyte complexation, for biomedical applications [121].

On the other hand, it is well known that chemical cross-linking methods, including free-radical polymerization, condensation reactions, and addition reactions, provide good mechanical strength while preserving the hydrogel properties [114, 122–125]. Particularly, chemically cross-linked hydrogels have more uniform properties as compared with those of physically cross-linked hydrogels. For biomedical applications, immense attention must be paid to the cleavage of the cross-linker (which can be done either by chemical or enzymatic methods) to avoid the release of toxic compounds [114]. However, the concentration of the cross-linking agent and the cross-linking reaction time are the main factors that could affect such an approach [126]. For example, the photopolymerization process is started by free radicals produced by radiation (e.g., UV, visible light irradiation, gamma irradiation, or electron beam) that, in turn, promote attacks on the double bonds of monomers and propagate the radical attack, creating a chemically cross-linked polymer network [114, 127–129]. Furthermore, the cross-linking reactions can occur more efficiently on the surface than in the polymer center, probably due to the steric effects [130]. However, the principal disadvantage of using CS-based hydrogels, mainly with regard to their biomedical applicability, is probably the poor reproducibility of the particles formed [106]. Hence, it is believed that a deeper understanding of these methods as well as the development of new strategies is fundamentally necessary and represents

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

hydrogels [106, 108–111].

A large variety of synthetic methods have been utilized for the fabrication of hydrogels based on CS and CS derivatives. The degree of acetylation and/or polymerization of CS-based materials have been widely considered as the critical parameters for controlling their outstanding properties [104–106]. These

#### *Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

structural changes, in principle, lead to completely new properties as well as a significant improvement in water solubility [6, 95]. From the carboxymethylation reaction, a water-soluble CS derivative can be obtained over a wide pH range [95], and among those obtained thus far, carboxymethyl CS stands out because it contains ether, -COOH, and -NH2 groups [95]. Similar to CS, the carboxymethyl CS derivative also stands out because it exhibits interesting characteristics such as antifungal activity, low toxicity, and membrane properties, which allow its application in drug delivery systems [96]. In general, it is well known that a high degree of deacetylation and a narrow polymer molecular weight distribution are critical parameters for controlling the particle size distribution [107]. Evidently, the size of the particles has significant influence on the biomedical applicability of CS-based hydrogels [106, 108–111].

It is well known that the hydrogel matrix structure is generally created from the hydrophilic groups (or domains) present in a natural or synthetic polymeric network upon hydration in an entirely aqueous environment [112]. On the other hand, it is also well known that the various properties exhibited by hydrogels (such as self-healing, biodegradability, swelling degree, mechanical resistance, and so on) are intrinsically related to the physical or chemical cross-linking methods [113, 114].

Hence, the physical cross-linking of hydrogels leads to the formation of a nonpermanent network due to noncovalent interactions (e.g., hydrogen or electrostatic bonds and physical entanglements) [22, 115–117]. Consequently, physically crosslinked hydrogels can be formed via ionic interactions of charges, that is, by utilizing the graft copolymers, crystallization, as well as the formation of different stereocomplex forms [117, 118]. Notably, CS can be self-cross-linked when the initial polymer concentration is beyond the critical concentration (C\*) for chain entanglement. In this condition, a precise balance between the hydrophilic and hydrophobic interactions is reached [114]. These values may be achieved after decreasing the apparent charge density by solvent evaporation or changing the dielectric constant of the medium [119]. Phosphate-bearing molecules such as polyacrylic acid, sodium alginate, heparin, and polyglutamic acid are the common anions used for physically cross-linked CS [120]. Sarmento et al. have reported the preparation of alginate/CS nanoparticle hydrogels by ionotropic pregelation of an alginate core followed by CS polyelectrolyte complexation, for biomedical applications [121].

On the other hand, it is well known that chemical cross-linking methods, including free-radical polymerization, condensation reactions, and addition reactions, provide good mechanical strength while preserving the hydrogel properties [114, 122–125]. Particularly, chemically cross-linked hydrogels have more uniform properties as compared with those of physically cross-linked hydrogels. For biomedical applications, immense attention must be paid to the cleavage of the cross-linker (which can be done either by chemical or enzymatic methods) to avoid the release of toxic compounds [114]. However, the concentration of the cross-linking agent and the cross-linking reaction time are the main factors that could affect such an approach [126]. For example, the photopolymerization process is started by free radicals produced by radiation (e.g., UV, visible light irradiation, gamma irradiation, or electron beam) that, in turn, promote attacks on the double bonds of monomers and propagate the radical attack, creating a chemically cross-linked polymer network [114, 127–129]. Furthermore, the cross-linking reactions can occur more efficiently on the surface than in the polymer center, probably due to the steric effects [130]. However, the principal disadvantage of using CS-based hydrogels, mainly with regard to their biomedical applicability, is probably the poor reproducibility of the particles formed [106]. Hence, it is believed that a deeper understanding of these methods as well as the development of new strategies is fundamentally necessary and represents

*Hydrogels - Smart Materials for Biomedical Applications*

**2.2 Main chitosan derivatives of technological interest**

ment in water solubility is often investigated [6, 95].

biomedical applications [94].

[85]. CS-iron (III) chloride composite membrane has excellent permeability for different fluids [86]. CS-carbon nanotube composite is mechanically resistant [87]. Carboxymethylated-CS composite protected with ruthenium nanoparticles was synthesized with good thermal stability [88]. Graphene oxide-CS nanocomposite films are formed with excellent mechanical and thermal properties [89], and montmorillonite-CS nanocomposites are produced with excellent biocompatibility and antimicrobial properties [89]. Moreover, CS-based composites were synthesized to be used as microcapsules in drug release systems [90], CS-porous-silica [91] and nanohydroxyapatite-CT derivative composites for bone regeneration [92], CS-zirconium composite as precursor of zirconium carbide [93], CS-barium sulfate composite fibers for endovascular prosthesis, fibrous embolic agent, bone substitution, and X-ray marker [89], CS composite reinforced with carbon nanotubes for biomedicine [78], and CS-hydroxyapatite-glycopolymer/cloisite composite for

Considering the vast number of functional groups available on the CS chains and the myriad of chemical compounds that can react with such groups, it is consensual that a plenty of possibilities regarding the use of CS derivatives as precursor materials for the synthesis of hydrogels applicable in drug delivery. There are some methodologies that allow these modifications to occur in CS, such as carboxymethylation, acetylation, and alkylation [7]. In this way, CS derivatives may appear, which seek to improve some properties of this polymer. Among them, the improve-

From the carboxymethylation reaction, a water-soluble CS derivative can be obtained over a wide pH range [95], and among those obtained so far, carboxymethyl CS stands out because it contains ether groups, and the -COOH and -NH2 groups [95]. Similarly to CS, the carboxymethylated-CS, also stands out because it exhibits interesting characteristics, such as antifungal activity, low toxicity, and

Quaternized CS through successive methylation in -NH2 groups [97] has been proposed using different methodologies, methacrylated glycol CS [98] and sulfated

The methylation in -NH2 groups is a very interesting strategy allowing the N

positive charges allows the material (N,N,N-trimethylchitosan, TMC) be soluble in water in the whole range of pH [100]. Beyond this, the positive charges help for the occurrence of interactions of TMC and the membrane of gram-negative bacteria. So, the TMC has pronounced antibacterial activity [101]. There are several methodologies for synthesis of TMC [101–103]. The following methodology is often used for quaternization of CS: the dispersion of CS in N-methylpyrrolidone containing sodium iodide/methyl iodide in the presence of sodium hydroxide. At final, the iodide counterions of the reaction product are exchanged with chloride for obtaining a more stable salt. Some reviews of CS chemistry are recently published [101–103].

**2.3 Methodologies used for obtaining chitosan derivatives aiming at biomedical** 

A large variety of synthetic methods have been utilized for the fabrication of hydrogels based on CS and CS derivatives. The degree of acetylation and/or polymerization of CS-based materials have been widely considered as the critical parameters for controlling their outstanding properties [104–106]. These

+

. Such increase in

membrane properties, which allows its application for drug release [96].

atoms be permanently charged with positive charges as -N(CH3)3

**66**

**applications as hydrogels**

CS [99].

a prerequisite to obtaining optimized CS-based hydrogels with entirely new functionality and properties for a broad variety of applications in emerging biomedical technologies.

## **3. Uses of hydrogels based on chitosan and chitosan derivatives**

The well-known and attractive properties of CS rank this polysaccharide as a safe choice to engineer novel materials applicable as biomaterials. Proof of this is the great volume of studies and review papers published in the literature dealing with this subject [131–133]. As noticed, various research groups are focused on the development of materials based on CS or CS derivatives, aiming their use in the most varied areas and subareas of pharmacy, medicine, and biochemistry [134–136]. In particular, hydrogels synthesized from CS or CS derivatives have been extensively utilized as delivery systems (for drugs, gene factors, and/or protein delivery), dressing devices, and scaffolds for cell/tissue culture [134–137]. Considering these applications, some notable finds and characteristics related to CS and CS-derivative-based hydrogels will be discussed below.

#### **3.1 As carriers of drug**

Drug delivery systems that make use of carriers based on CS are of particular interest because this polysaccharide exhibits three paramount features: a mucoadhesive nature, ability to transiently open epithelial tight junctions, and biodegradability [138]. The mucoadhesion ability can be assigned to different interactions (electrostatic attraction, hydrogen bonding, and hydrophobic effects) that take place between CS and mucosa [139]. Biodegradability property is attributed to CS because it is degraded by the two naturally produced enzymes: lysozyme (present in various mucosal surfaces) and chitinase (present in the intestinal flora) [117]. Due to this, CS-based carriers are able to deliver drugs across various well-organized epithelia (e.g., ocular, nasal, buccal, pulmonary, and intestinal) in a controlled manner [140].

In light of this, carrier systems based on CS have been formulated in different forms (tablets, particles, films, membranes, gels, and so forth) using a vast number of protocols [141, 142]. CS hydrogels can be prepared via physical and/ or chemical cross-linking processes, and its functional groups allow grafting synthetic monomers on its backbone [143, 144]. Generally, the association of CS with other synthetic polymer or its grafting with vinylic monomers (acrylic acid, acrylamide, etc.) is architected in order to increase the liquid uptake capacity and to enhance the mechanical properties of the hydrogel [117, 145]. Of course, the cross-linking process has a direct relationship with the final properties of the hydrogel, which allows, for example, tailoring hydrogel properties according to the application. Furthermore, CS hydrogels usually show responsive properties, mainly pH-dependent properties [146]. In acidic condition, CS hydrogels show high liquid uptake capacity favoring the drug release by diffusional processes [147]. On the other hand, hydrogels synthesized from the polyelectrolyte complexation of CS (polycationic) with polyanionic polymers (e.g., alginate, pectin, chondroitin sulfate, among others) or anionic salts (e.g., potassium tripolyphosphate) can be disrupted by changing the pH of the release medium [148–150]. In this case, the drug loaded into the hydrogel is released owing to erosion/disruption process. This pH-sensitive is useful to modulate the drug release profile, which prevents unwanted side effects such as burst or time lag release, and to promote targeted drug release.

**69**

others) [164].

**3.2 As wound healing**

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

loading and delivery of hydrophobic drugs from CS-based hydrogels [58].

Currently, various studies report the synthesis of hydrogels from water-soluble CS derivatives, such as carboxymethyl CS, quaternized CS, (such as TMC) zwitterionic CS, oligomerized CS, and so on, and their use as drug delivery systems [155, 156]. The chemical modification of the CS backbone without modification of its initial backbone (to preserve the original properties) is a reliable strategy to overcome the shortcomings related to the use of raw CS. For instance, owing to their properties, CS derivative hydrogels can offer prolongation of the contact time between the drug and the absorptive sites in the mucosa and slow and continuous drug release [157]. Furthermore, the grafting of specific chemical modifiers on CS makes possible new cross-linking routes (click reactions, self-assembling, etc.) allowing, for example, the synthesis of *in situ* hydrogels [158, 159]. The use of CS derivatives to synthesize hydrogels may impart new properties to this material (antioxidant or bactericidal properties, for instance), which enlarge the field of the potential applications of such materials, especially as carriers for drug delivery [160, 161].

Any internal or external stimulus that damages the anatomy of a tissue and compromises its function generates a wound [162]. In general, the healing process of a wound can be described in four phases named vascular response, inflammatory response, proliferation, and maturation [163]. Therefore, a proper wound dressing should present specific features to act in each abovementioned phase to promote a satisfactory healing process. Such features include blood clotting, inflammation fluids absorption, barrier against infection, protection against friction, support for

cell attachment and growth, hydration, air permeability, and others [164]. CT, CS, and CS derivatives have been studied in several preparations for treatment of wounds and in tissue regeneration especially due to their biological properties including hemostatic, antibacterial, antifungal, biocompatibility, biodegradability, lack of toxicity, adhesive, and more [165, 166], all those required by a proper dressing. Currently, distinct manufacturers make available wound dressings based on CT and its derivatives under many trade names (Syvek-Patch®, Beschitin®, Tegaderm®, Chitodine®, Trauma DEX®, and Talymed®, among several

CT/CS-based wound dressings have been reported in a variety of forms, for example, membranes, sponges, scaffold, fibers, and so on. However, hydrogels are probably the most promising materials for wound dressing because of their similarity and physical chemical properties to the extracellular matrix, which allows cell

CS hydrogels also show versatility regarding the drug loading process because drugs can be encapsulated *in situ* during the hydrogel synthesis procedure (this increases the loading efficiency) or they can be loaded in the hydrogel by sorption processes. Generally, drugs adsorbed in the hydrogel are easily released due to the weak interaction forces between the drug and the hydrogel matrix [151]. More recently, the incorporation of filler materials (e.g., clays, metallic particles, graphene, etc.) within the CS matrix has been investigated, aiming to increase the drug encapsulation efficiency (mainly for hydrophobic drugs) and a better control of the release profile [114, 152, 153]. Another strategy adopted by several researchers to enhance the encapsulation efficiency and to improve the release profile is the synthesis of hydrogels using CS derivatives. In general lines, CS derivatives have been synthesized in order to solve some issues related to the use of raw CS in the design of delivery systems. For example, CS shows poor solubility under neutral conditions, which limit its processability and reactivity in biological solutions (pH 7.4) [154]. Moreover, CS is insoluble in the most part of organic solvents hindering the

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

#### *Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

CS hydrogels also show versatility regarding the drug loading process because drugs can be encapsulated *in situ* during the hydrogel synthesis procedure (this increases the loading efficiency) or they can be loaded in the hydrogel by sorption processes. Generally, drugs adsorbed in the hydrogel are easily released due to the weak interaction forces between the drug and the hydrogel matrix [151]. More recently, the incorporation of filler materials (e.g., clays, metallic particles, graphene, etc.) within the CS matrix has been investigated, aiming to increase the drug encapsulation efficiency (mainly for hydrophobic drugs) and a better control of the release profile [114, 152, 153]. Another strategy adopted by several researchers to enhance the encapsulation efficiency and to improve the release profile is the synthesis of hydrogels using CS derivatives. In general lines, CS derivatives have been synthesized in order to solve some issues related to the use of raw CS in the design of delivery systems. For example, CS shows poor solubility under neutral conditions, which limit its processability and reactivity in biological solutions (pH 7.4) [154]. Moreover, CS is insoluble in the most part of organic solvents hindering the loading and delivery of hydrophobic drugs from CS-based hydrogels [58].

Currently, various studies report the synthesis of hydrogels from water-soluble CS derivatives, such as carboxymethyl CS, quaternized CS, (such as TMC) zwitterionic CS, oligomerized CS, and so on, and their use as drug delivery systems [155, 156]. The chemical modification of the CS backbone without modification of its initial backbone (to preserve the original properties) is a reliable strategy to overcome the shortcomings related to the use of raw CS. For instance, owing to their properties, CS derivative hydrogels can offer prolongation of the contact time between the drug and the absorptive sites in the mucosa and slow and continuous drug release [157]. Furthermore, the grafting of specific chemical modifiers on CS makes possible new cross-linking routes (click reactions, self-assembling, etc.) allowing, for example, the synthesis of *in situ* hydrogels [158, 159]. The use of CS derivatives to synthesize hydrogels may impart new properties to this material (antioxidant or bactericidal properties, for instance), which enlarge the field of the potential applications of such materials, especially as carriers for drug delivery [160, 161].

#### **3.2 As wound healing**

*Hydrogels - Smart Materials for Biomedical Applications*

biomedical technologies.

**3.1 As carriers of drug**

manner [140].

a prerequisite to obtaining optimized CS-based hydrogels with entirely new functionality and properties for a broad variety of applications in emerging

The well-known and attractive properties of CS rank this polysaccharide as a safe choice to engineer novel materials applicable as biomaterials. Proof of this is the great volume of studies and review papers published in the literature dealing with this subject [131–133]. As noticed, various research groups are focused on the development of materials based on CS or CS derivatives, aiming their use in the most varied areas and subareas of pharmacy, medicine, and biochemistry [134–136]. In particular, hydrogels synthesized from CS or CS derivatives have been extensively utilized as delivery systems (for drugs, gene factors, and/or protein delivery), dressing devices, and scaffolds for cell/tissue culture [134–137]. Considering these applications, some notable finds and characteristics related to CS

Drug delivery systems that make use of carriers based on CS are of particular interest because this polysaccharide exhibits three paramount features: a mucoadhesive nature, ability to transiently open epithelial tight junctions, and biodegradability [138]. The mucoadhesion ability can be assigned to different interactions (electrostatic attraction, hydrogen bonding, and hydrophobic effects) that take place between CS and mucosa [139]. Biodegradability property is attributed to CS because it is degraded by the two naturally produced enzymes: lysozyme (present in various mucosal surfaces) and chitinase (present in the intestinal flora) [117]. Due to this, CS-based carriers are able to deliver drugs across various well-organized epithelia (e.g., ocular, nasal, buccal, pulmonary, and intestinal) in a controlled

In light of this, carrier systems based on CS have been formulated in different forms (tablets, particles, films, membranes, gels, and so forth) using a vast number of protocols [141, 142]. CS hydrogels can be prepared via physical and/ or chemical cross-linking processes, and its functional groups allow grafting synthetic monomers on its backbone [143, 144]. Generally, the association of CS with other synthetic polymer or its grafting with vinylic monomers (acrylic acid, acrylamide, etc.) is architected in order to increase the liquid uptake capacity and to enhance the mechanical properties of the hydrogel [117, 145]. Of course, the cross-linking process has a direct relationship with the final properties of the hydrogel, which allows, for example, tailoring hydrogel properties according to the application. Furthermore, CS hydrogels usually show responsive properties, mainly pH-dependent properties [146]. In acidic condition, CS hydrogels show high liquid uptake capacity favoring the drug release by diffusional processes [147]. On the other hand, hydrogels synthesized from the polyelectrolyte complexation of CS (polycationic) with polyanionic polymers (e.g., alginate, pectin, chondroitin sulfate, among others) or anionic salts (e.g., potassium tripolyphosphate) can be disrupted by changing the pH of the release medium [148–150]. In this case, the drug loaded into the hydrogel is released owing to erosion/disruption process. This pH-sensitive is useful to modulate the drug release profile, which prevents unwanted side effects such as burst or time lag release, and to

**3. Uses of hydrogels based on chitosan and chitosan derivatives**

and CS-derivative-based hydrogels will be discussed below.

**68**

promote targeted drug release.

Any internal or external stimulus that damages the anatomy of a tissue and compromises its function generates a wound [162]. In general, the healing process of a wound can be described in four phases named vascular response, inflammatory response, proliferation, and maturation [163]. Therefore, a proper wound dressing should present specific features to act in each abovementioned phase to promote a satisfactory healing process. Such features include blood clotting, inflammation fluids absorption, barrier against infection, protection against friction, support for cell attachment and growth, hydration, air permeability, and others [164].

CT, CS, and CS derivatives have been studied in several preparations for treatment of wounds and in tissue regeneration especially due to their biological properties including hemostatic, antibacterial, antifungal, biocompatibility, biodegradability, lack of toxicity, adhesive, and more [165, 166], all those required by a proper dressing. Currently, distinct manufacturers make available wound dressings based on CT and its derivatives under many trade names (Syvek-Patch®, Beschitin®, Tegaderm®, Chitodine®, Trauma DEX®, and Talymed®, among several others) [164].

CT/CS-based wound dressings have been reported in a variety of forms, for example, membranes, sponges, scaffold, fibers, and so on. However, hydrogels are probably the most promising materials for wound dressing because of their similarity and physical chemical properties to the extracellular matrix, which allows cell

diffusion and proliferation. Either chemically or physically, hydrogels can be readily prepared from CS, as extensively reported [167–169].

Zhang et al. demonstrated the wound dressing based on CS loaded with superoxide dismutase (SOD) enzyme could effectively improve the healing process in chronic wounds in rat models [170]. Hydrogels based on electrostatic interaction of the cationic CS and the anionic heparin and poly(γ-glutamic acid) were successfully prepared and characterized. The best composition was loaded with SOD and applied to the wounds. The continuous release of SOD prevented cell oxidative damage due to excess of O2 <sup>−</sup> and improved the healing process.

Hydrogels based on CS and Ag nanoparticles were proved to be efficient restructuration of epithelium and collagen deposition, effectively accelerating the wound healing [171]. CS hydrogel was prepared by the freeze-thawing process using the system LiOH:KOH:urea:H2O as solvent. In this case, the Ag nanoparticles worked as both fillers for improving the mechanical properties of the hydrogel and antimicrobial agent. The mechanism of bactericidal activity was a combination of cell membrane disruption and DNA binding, preventing bacteria replication.

Other study reported hydrogels based on freeze-thawing of solution of CS with poly(vinyl alcohol) PVA, sodium alginate (SA) or Pluronic F68 [172]. The dressings based on CS and Pluronic were more effective in the healing probably due to its porous morphology and the level of moisture based on comparative histology of healing effects of hydrogels after 15 days of inflicted wounds. Chemically crosslinked hydrogel based on glycol CS and glycidyl methacrylate was obtained via visible light radiation [173]. The endothelial and fibroblast growth factors-loaded hydrogel accelerated the wound healing *in vivo* models. In general lines, several reports have demonstrated the CS-based hydrogels either unloaded or loaded (bactericidal agents, growth factors, etc.) played an important role in the wound by direct acting in different phases of the healing process. The authors also refer to the following review papers focusing on CT/CS hydrogels as wound dressing for further reading [162, 174, 175].

#### **3.3 As protein delivering**

Mucoadhesive systems such as CS-based matrix are used in order to increase the protein residence time at the activity site [176]. However, CS can be dissolved in the stomach due its solubility at low pH condition (pKa 6.5) [177], causing release and denaturation of protein [178]. Therefore, the solubility of CS can be prevented by its association with anionic polymers including alginate [179], pectin [180], gelatin [181], and carrageenan [182] to create hydrogels as oral protein delivery carriers.

When proteins are physically incorporated in CS-based hydrogels, their release can occur by diffusion, erosion/degradation, swelling, or a combination of these mechanisms [183]. In order to slow down the degradation rate of hydrogels and prevent burst protein release, polycaprolactone can be incorporated in CS-based hydrogels. Shamloo et al. [181] developed poly(vinyl alcohol)/CS/gelatin hydrogel incorporating polycaprolactone microspheres for delivery of basic fibroblast growth factor (bFGF). Poly(vinyl alcohol) and gelatin were used to improve mechanical properties and increase cell adhesion, respectively. The bFGF release accelerated the wound healing process with polycaprolactone incorporation into hydrogel [181].

The control protein release can also be enhanced with use of mineralized inorganic compounds combined with CS-based hydrogel network [184]. Salama et al. [184] reported the synthesis of CS-g-poly(3-sulfopropyl methacrylate) hydrogel mineralized with calcium phosphate for bovine serum albumin (BSA) release. The mineralization decreased the permeability of the loaded protein and controlled the release proteins [184].

**71**

rhBMP-2 [99].

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

Hydrogels prepared from polysaccharides containing -COOH groups such as carboxymethyl CS may undergo shrinking in acidic condition (e.g., gastric juice) and swelled in neutral or alkaline environment (e.g., intestinal juice) due to electrostatic repulsion between the ionized acid groups present on polysaccharides chains [185]. Therefore, carboxymethyl CS-based pH-sensitive hydrogels can be used to direct protein release, including BSA and insulin (INS), into intestinal region [178]. Zhang et al. [185] synthesized carboxymethyl CS-g-polyacrylic acid for insulin delivery. The results showed that 16.3 and 93.2% of insulin was released at pH 1.2

Carboxymethyl CS can also be associated with xanthan to prepare hydrogel to fluorescein-isothiocyanate-labeled bovine serum albumin (FITC-BSA) release [186]. Huang et al. [186] developed aldehyde xanthan/carboxymethyl CS hydrogel to FITC-BSA release. Moreover, a signaling protein, endothelial growth factor (VEGF), was loaded to accelerate abdominal wall reconstruction. The BSA-FITC release was stable within 10 h. After VEGF incorporation, the abdominal wall

Besides carboxymethyl CS, other CS derivatives such as quaternized CS [97], methacrylated glycol CS [98], and sulfated CS [99] have been used as oral protein delivery carriers. Quaternized CS has been used in hydrogel preparation for protein delivering due to its several properties such as absorption enhanced across intestinal epithelial for hydrophilic drug delivery [187], low toxicity [188], capacity to open the junctions between epithelial cells, which allow greater transport of hydrophilic compounds [187], better mucoadhesive [189], and antibacterial activity [190] than CS. Wu et al. [97] developed hydrogel-based N-[(2-hydroxy-3 trimethylammonium)propyl]chitosan chloride (HTCC) and poly(ethylene glycol) (PEG) for insulin release. Hydrogen bonds among amino groups present in insulin and hydroxyl groups present in PEG or HTCC allowed slowed drug release. The results showed that the hydrogel can be used as nasal delivery carrier for protein or

The controlled protein release from heparin-based hydrogels has also been studied due to its strong binding capacity, which attenuates the burst protein release such as rhBMP2 [191]. Therefore, some CS derivatives have been used to mimic heparin to protein delivery, including sulfonated molecules incorporated into methacrylated glycol CS hydrogels [98] and sulfated CS hydrogels [99]. Kim and Chung [98] developed methacrylated glycol CS (MeGC) hydrogel used to mimic heparin to stabilize bone morphogenetic protein-2 (BMP-2) and to enhance osteogenesis by the addition of poly-4-styrenesulfonic acid (PSS) or poly-vinylsulfonic acid (PVSA) into hydrogel. The addition of PSS or PVSA reduced the initial burst and increased the recombinant human BMP-2-induced osteogenesis differentiation, indicating

However, sulfated CS, 2-N,6-O-sulfated CS, besides to mimic heparin, has been shown to enhance BMP-2 bioactivity than heparin [192]. In this context, Cao et al. developed rhBMP-2-loaded 2-N,6-O-sulfated CS nanoparticles and hydrogel photopolymerizable incorporating rhBMP-2-loaded 2-N,6-O-sulfated CS nanoparticles. The composite gel system showed gradual and more release than nanoparticle

system. The use of 2-N,6-O-sulfated CS enhanced the bioactivity of released

The protein residence time at activity can also be improved by thiolation of CS due to the covalent bond formation between subdomains with high cysteine content in the mucus glycoproteins and thiol groups [193]. Liu et al. [194] developed thiolated CS-TBA/hydroxyapatite(HA)/beta-glycerophosphate (β-GP) hydrogel. The BSA protein residence time at activity using such hydrogel was higher than unmodi-

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

and 7.4, respectively [185].

peptide drugs [97].

efficient protein delivery [98].

fied CS system CS/HA/β-GP [194].

reconstruction was accelerated [186].

#### *Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

Hydrogels prepared from polysaccharides containing -COOH groups such as carboxymethyl CS may undergo shrinking in acidic condition (e.g., gastric juice) and swelled in neutral or alkaline environment (e.g., intestinal juice) due to electrostatic repulsion between the ionized acid groups present on polysaccharides chains [185]. Therefore, carboxymethyl CS-based pH-sensitive hydrogels can be used to direct protein release, including BSA and insulin (INS), into intestinal region [178]. Zhang et al. [185] synthesized carboxymethyl CS-g-polyacrylic acid for insulin delivery. The results showed that 16.3 and 93.2% of insulin was released at pH 1.2 and 7.4, respectively [185].

Carboxymethyl CS can also be associated with xanthan to prepare hydrogel to fluorescein-isothiocyanate-labeled bovine serum albumin (FITC-BSA) release [186]. Huang et al. [186] developed aldehyde xanthan/carboxymethyl CS hydrogel to FITC-BSA release. Moreover, a signaling protein, endothelial growth factor (VEGF), was loaded to accelerate abdominal wall reconstruction. The BSA-FITC release was stable within 10 h. After VEGF incorporation, the abdominal wall reconstruction was accelerated [186].

Besides carboxymethyl CS, other CS derivatives such as quaternized CS [97], methacrylated glycol CS [98], and sulfated CS [99] have been used as oral protein delivery carriers. Quaternized CS has been used in hydrogel preparation for protein delivering due to its several properties such as absorption enhanced across intestinal epithelial for hydrophilic drug delivery [187], low toxicity [188], capacity to open the junctions between epithelial cells, which allow greater transport of hydrophilic compounds [187], better mucoadhesive [189], and antibacterial activity [190] than CS. Wu et al. [97] developed hydrogel-based N-[(2-hydroxy-3 trimethylammonium)propyl]chitosan chloride (HTCC) and poly(ethylene glycol) (PEG) for insulin release. Hydrogen bonds among amino groups present in insulin and hydroxyl groups present in PEG or HTCC allowed slowed drug release. The results showed that the hydrogel can be used as nasal delivery carrier for protein or peptide drugs [97].

The controlled protein release from heparin-based hydrogels has also been studied due to its strong binding capacity, which attenuates the burst protein release such as rhBMP2 [191]. Therefore, some CS derivatives have been used to mimic heparin to protein delivery, including sulfonated molecules incorporated into methacrylated glycol CS hydrogels [98] and sulfated CS hydrogels [99]. Kim and Chung [98] developed methacrylated glycol CS (MeGC) hydrogel used to mimic heparin to stabilize bone morphogenetic protein-2 (BMP-2) and to enhance osteogenesis by the addition of poly-4-styrenesulfonic acid (PSS) or poly-vinylsulfonic acid (PVSA) into hydrogel. The addition of PSS or PVSA reduced the initial burst and increased the recombinant human BMP-2-induced osteogenesis differentiation, indicating efficient protein delivery [98].

However, sulfated CS, 2-N,6-O-sulfated CS, besides to mimic heparin, has been shown to enhance BMP-2 bioactivity than heparin [192]. In this context, Cao et al. developed rhBMP-2-loaded 2-N,6-O-sulfated CS nanoparticles and hydrogel photopolymerizable incorporating rhBMP-2-loaded 2-N,6-O-sulfated CS nanoparticles. The composite gel system showed gradual and more release than nanoparticle system. The use of 2-N,6-O-sulfated CS enhanced the bioactivity of released rhBMP-2 [99].

The protein residence time at activity can also be improved by thiolation of CS due to the covalent bond formation between subdomains with high cysteine content in the mucus glycoproteins and thiol groups [193]. Liu et al. [194] developed thiolated CS-TBA/hydroxyapatite(HA)/beta-glycerophosphate (β-GP) hydrogel. The BSA protein residence time at activity using such hydrogel was higher than unmodified CS system CS/HA/β-GP [194].

*Hydrogels - Smart Materials for Biomedical Applications*

damage due to excess of O2

reading [162, 174, 175].

**3.3 As protein delivering**

prepared from CS, as extensively reported [167–169].

diffusion and proliferation. Either chemically or physically, hydrogels can be readily

Zhang et al. demonstrated the wound dressing based on CS loaded with superoxide dismutase (SOD) enzyme could effectively improve the healing process in chronic wounds in rat models [170]. Hydrogels based on electrostatic interaction of the cationic CS and the anionic heparin and poly(γ-glutamic acid) were successfully prepared and characterized. The best composition was loaded with SOD and applied to the wounds. The continuous release of SOD prevented cell oxidative

<sup>−</sup> and improved the healing process. Hydrogels based on CS and Ag nanoparticles were proved to be efficient restructuration of epithelium and collagen deposition, effectively accelerating the wound healing [171]. CS hydrogel was prepared by the freeze-thawing process using the system LiOH:KOH:urea:H2O as solvent. In this case, the Ag nanoparticles worked as both fillers for improving the mechanical properties of the hydrogel and antimicrobial agent. The mechanism of bactericidal activity was a combination of cell

Other study reported hydrogels based on freeze-thawing of solution of CS with poly(vinyl alcohol) PVA, sodium alginate (SA) or Pluronic F68 [172]. The dressings based on CS and Pluronic were more effective in the healing probably due to its porous morphology and the level of moisture based on comparative histology of healing effects of hydrogels after 15 days of inflicted wounds. Chemically crosslinked hydrogel based on glycol CS and glycidyl methacrylate was obtained via visible light radiation [173]. The endothelial and fibroblast growth factors-loaded hydrogel accelerated the wound healing *in vivo* models. In general lines, several reports have demonstrated the CS-based hydrogels either unloaded or loaded (bactericidal agents, growth factors, etc.) played an important role in the wound by direct acting in different phases of the healing process. The authors also refer to the following review papers focusing on CT/CS hydrogels as wound dressing for further

Mucoadhesive systems such as CS-based matrix are used in order to increase the protein residence time at the activity site [176]. However, CS can be dissolved in the stomach due its solubility at low pH condition (pKa 6.5) [177], causing release and denaturation of protein [178]. Therefore, the solubility of CS can be prevented by its association with anionic polymers including alginate [179], pectin [180], gelatin [181], and carrageenan [182] to create hydrogels as oral protein delivery carriers. When proteins are physically incorporated in CS-based hydrogels, their release can occur by diffusion, erosion/degradation, swelling, or a combination of these mechanisms [183]. In order to slow down the degradation rate of hydrogels and prevent burst protein release, polycaprolactone can be incorporated in CS-based hydrogels. Shamloo et al. [181] developed poly(vinyl alcohol)/CS/gelatin hydrogel incorporating polycaprolactone microspheres for delivery of basic fibroblast growth factor (bFGF). Poly(vinyl alcohol) and gelatin were used to improve mechanical properties and increase cell adhesion, respectively. The bFGF release accelerated the wound healing process with polycaprolactone incorporation into hydrogel [181]. The control protein release can also be enhanced with use of mineralized inorganic compounds combined with CS-based hydrogel network [184]. Salama et al. [184] reported the synthesis of CS-g-poly(3-sulfopropyl methacrylate) hydrogel mineralized with calcium phosphate for bovine serum albumin (BSA) release. The mineralization decreased the permeability of the loaded protein and controlled the

membrane disruption and DNA binding, preventing bacteria replication.

**70**

release proteins [184].

In order to increase protein half-life and to improve the biocompatibility of CS, polyethylene glycol (PEG) can be used to prepare chemically modified CS hydrogels [195, 196]. Farahani et al. [197] developed semi-interpenetrating polymer network CS-PEG-acrylamide hydrogels for closed-loop insulin delivery. Moreover, catalase and glucose oxidase were loaded into hydrogel to make an intelligent protein carrier. The increasing of PEG increased the swelling ratio, protein loading capacity, and entrapment efficiency. The increase in insulin release was observed with increase in the glucose level, indicating that the hydrogel has a good responsiveness to the glucose concentration [197].

#### **3.4 As scaffolds for cell growth in tissue engineering**

Scaffolds provide an intermediary template for neotissue/organ formation as well as temporary artificial extracellular matrices [198, 199]. Scaffolds-based extracellular matrices are characterized by pore volume fraction of typically 0.90–0.95 or higher and pore diameter in the range of 5–500 μm [199]. Generally, the use of scaffolds in tissue engineering should have several properties, such as biocompatibility, cell proliferation, controlled swelling, antimicrobial, biomineralization, biodegradability, stability, porosity, adhesion, and protein absorption [200–202].

#### *3.4.1 Chitosan hydrogels in bone tissue engineering*

CS has been widely used for bone tissue engineering due to its capacity in providing growth and deposition of matrix with high mineral content by osteoblast cell culture [203]. As already mentioned in this chapter, CS can be associated with anionic polymers, such as pectin to create physical hydrogels [204]. Moreover, metallic nanoparticles (NPs) coupled to hydrogels can be used to induce cell growth [205, 206]. Tentor et al. related scaffolds-based CS/pectin/gold nanoparticles for bone tissue engineering [204]. The hydrogels were cytocompatible with several cell types, such as normal kidney epithelial cell, HPV-16-positive human cervical tumor cells, epithelial colorectal adenocarcinoma cells, and murine macrophage cells. Regarding the cell viability assay, such hydrogels possess potential for applications in the bone tissue engineering to promote proliferation and growth of bone cells (e.g., MC3T3-E1).

Hydroxyapatite (HA) is the major inorganic component of bone [207]. So, nanohydroxyapatite (n-HA) has been used in bone tissue engineering due to its osteoconductivity and bioactivity [208]. However, n-HA has poor shape ability [208]. Mechanical property of HA can be improved by its association with hyaluronic acid [209] and glycol CS [210], for fabricating scaffold hydrogels to apply in bone tissue engineering. Huang et al. [210] developed n-HA/glycol CS/hyaluronic acid hydrogel composite as scaffold for bone tissue engineering. The porosity of hydrogel increased with increase in the HA concentration. *In vitro* cytocompatibility tests were carried out using MC-3T3-E1 cells. After 7 days co-incubation, cells were attached, and spreading on scaffolds and increasing in cell aggregation were observed. The scaffolds were cytocompatible and nontoxic, so these results are suitable for bone tissue engineering application [210].

#### *3.4.2 Cardiac and nerve tissue engineering*

CS and CS associated with biopolymers [211], including gelatin [212], collagen [213], and alginate [214], have been used in developing hydrogel scaffolds for cardiac tissue engineering applications [215]. Gelatin scaffolds are susceptible to fast degradation, while gelatin/CS composite scaffolds are structurally stable in cell

**73**

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

tion of neonatal rat ventricular myocytes (NRVMs) was observed [216].

culture media [212]. However, these polymers may be associated with polycaprolactone (PCL), to provide sufficient tensile strength to work in the ventricular wall [216]. Pok et al. [216] developed 3D scaffolds composed of self-assembled PCL sandwiched in a gelatin-CS hydrogel for reconstruction of congenital heart defects. The compressive modulus of the hydrogel was similar to native tissue, and migra-

Quaternized CS can also be used in tissue engineering due to its enhanced antibacterial activity and more solubility than CS [217]. Similar to CS, quaternized CS possesses properties of biocompatibility, low toxicity, biocompatibility, and biodegradability [188]. Zhao et al. [218] developed antibacterial conductive hydrogel scaffolds using quaternized CS-grafted polyaniline with oxidized dextran as cross-linker. The use of polyaniline into quaternized CS copolymer decreased the cytotoxicity, enhanced the antibacterial activity, and stimulated proliferation of C2C12 myoblast cells, by a synergistic effect, as compared with quaternized CS hydrogel. These scaffold showed great potential as scaffold for muscle, nerve, and

The cartilage tissue engineering can involve the seeding chondrogenic cells in scaffolds for cartilage repair [136]. Glycosaminoglycans and type II collagen are components commonly found in the cartilage-specific extracellular matrix, which may stimulate the chondrogenesis [219, 220]. CS has structural characteristics similar to glycosaminoglycans and can mimic their functional behavior [221]. Several polymers, such as alginate [222], glycosaminoglycans [223], collagen [224], and carrageenan [225], have been associated with CS for cartilage engineering tissue applications. Hong et al. [224] developed an injectable composite scaffold obtained from collagen-coated polylactide microcarriers/CS hydrogel. Collagen-coated polylactide microcarriers enhanced the mechanical properties of the scaffold. The cell metabolic activity increased rapidly before 9 days of *in vitro* chondrocytes growth within the scaffold. After 9–12 days, confluent cell layers were formed. The composite scaffolds showed great potential for tissue engineering applications, particularly in orthopedics [224]. Liang et al. [225] developed rubbery CS/carrageenan hydrogels prepared by electroneutrality system as cartilage scaffold. The results showed pH- and salt-responsiveness, hierarchically porous architecture, and great mechanical properties. The hydrogels enhanced the viability and the adhesion

Mechanical properties and biological activities may be altered by chemical modification of CS. *N*-succinyl CS possess biocompatibility and long-term retention *in vivo* [226]. Kamoun [227] developed *N*-succinyl CS-dialdehyde starch hydrogels for cartilage repair. The hydrogel was relatively stable, and the hydrolysis rate was limited with a high N-succinyl hydrogel composition without any by-products in physiological conditions. The adhered human gingival fibroblast cell number on hydrogel surface was improved by *N*-succinyl CS content in hybrid hydrogels. This hydrogel showed great potential to be used as injectable scaffold for cartilage repair [227]. *N*-succinyl CS can also be associated with other polysaccharides such as hyaluronic acid to prepare hydrogels, as an injectable scaffold, to improve biocom-

Regarding skin tissue engineering, CS has been used in the preparation of scaffold hydrogel due to its biocompatibility [229], biodegradability [230], antibacterial properties [231], and hemostatic activity [232], stimulating fibroblast growth and accelerating tissue regeneration [233]. Franco et al. [234] developed CS/gelatin hydrogel scaffolds for skin engineering. The hydrogel showed a high porosity and

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

cardiovascular repair [218].

of TDC5 cells [225].

patibility and biodegradation [228].

*3.4.3 Cartilage and skin tissue engineering*

#### *Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

culture media [212]. However, these polymers may be associated with polycaprolactone (PCL), to provide sufficient tensile strength to work in the ventricular wall [216]. Pok et al. [216] developed 3D scaffolds composed of self-assembled PCL sandwiched in a gelatin-CS hydrogel for reconstruction of congenital heart defects. The compressive modulus of the hydrogel was similar to native tissue, and migration of neonatal rat ventricular myocytes (NRVMs) was observed [216].

Quaternized CS can also be used in tissue engineering due to its enhanced antibacterial activity and more solubility than CS [217]. Similar to CS, quaternized CS possesses properties of biocompatibility, low toxicity, biocompatibility, and biodegradability [188]. Zhao et al. [218] developed antibacterial conductive hydrogel scaffolds using quaternized CS-grafted polyaniline with oxidized dextran as cross-linker. The use of polyaniline into quaternized CS copolymer decreased the cytotoxicity, enhanced the antibacterial activity, and stimulated proliferation of C2C12 myoblast cells, by a synergistic effect, as compared with quaternized CS hydrogel. These scaffold showed great potential as scaffold for muscle, nerve, and cardiovascular repair [218].

#### *3.4.3 Cartilage and skin tissue engineering*

*Hydrogels - Smart Materials for Biomedical Applications*

**3.4 As scaffolds for cell growth in tissue engineering**

*3.4.1 Chitosan hydrogels in bone tissue engineering*

suitable for bone tissue engineering application [210].

*3.4.2 Cardiac and nerve tissue engineering*

glucose concentration [197].

(e.g., MC3T3-E1).

In order to increase protein half-life and to improve the biocompatibility of CS, polyethylene glycol (PEG) can be used to prepare chemically modified CS hydrogels [195, 196]. Farahani et al. [197] developed semi-interpenetrating polymer network CS-PEG-acrylamide hydrogels for closed-loop insulin delivery. Moreover, catalase and glucose oxidase were loaded into hydrogel to make an intelligent protein carrier. The increasing of PEG increased the swelling ratio, protein loading capacity, and entrapment efficiency. The increase in insulin release was observed with increase in the glucose level, indicating that the hydrogel has a good responsiveness to the

Scaffolds provide an intermediary template for neotissue/organ formation as well as temporary artificial extracellular matrices [198, 199]. Scaffolds-based extracellular matrices are characterized by pore volume fraction of typically 0.90–0.95 or higher and pore diameter in the range of 5–500 μm [199]. Generally, the use of scaffolds in tissue engineering should have several properties, such as biocompatibility, cell proliferation, controlled swelling, antimicrobial, biomineralization, biodegradability, stability, porosity, adhesion, and protein absorption [200–202].

CS has been widely used for bone tissue engineering due to its capacity in providing growth and deposition of matrix with high mineral content by osteoblast cell culture [203]. As already mentioned in this chapter, CS can be associated with anionic polymers, such as pectin to create physical hydrogels [204]. Moreover, metallic nanoparticles (NPs) coupled to hydrogels can be used to induce cell growth [205, 206]. Tentor et al. related scaffolds-based CS/pectin/gold nanoparticles for bone tissue engineering [204]. The hydrogels were cytocompatible with several cell types, such as normal kidney epithelial cell, HPV-16-positive human cervical tumor cells, epithelial colorectal adenocarcinoma cells, and murine macrophage cells. Regarding the cell viability assay, such hydrogels possess potential for applications in the bone tissue engineering to promote proliferation and growth of bone cells

Hydroxyapatite (HA) is the major inorganic component of bone [207]. So, nanohydroxyapatite (n-HA) has been used in bone tissue engineering due to its osteoconductivity and bioactivity [208]. However, n-HA has poor shape ability [208]. Mechanical property of HA can be improved by its association with hyaluronic acid [209] and glycol CS [210], for fabricating scaffold hydrogels to apply in bone tissue engineering. Huang et al. [210] developed n-HA/glycol CS/hyaluronic acid hydrogel composite as scaffold for bone tissue engineering. The porosity of hydrogel increased with increase in the HA concentration. *In vitro* cytocompatibility tests were carried out using MC-3T3-E1 cells. After 7 days co-incubation, cells were attached, and spreading on scaffolds and increasing in cell aggregation were observed. The scaffolds were cytocompatible and nontoxic, so these results are

CS and CS associated with biopolymers [211], including gelatin [212], collagen

[213], and alginate [214], have been used in developing hydrogel scaffolds for cardiac tissue engineering applications [215]. Gelatin scaffolds are susceptible to fast degradation, while gelatin/CS composite scaffolds are structurally stable in cell

**72**

The cartilage tissue engineering can involve the seeding chondrogenic cells in scaffolds for cartilage repair [136]. Glycosaminoglycans and type II collagen are components commonly found in the cartilage-specific extracellular matrix, which may stimulate the chondrogenesis [219, 220]. CS has structural characteristics similar to glycosaminoglycans and can mimic their functional behavior [221]. Several polymers, such as alginate [222], glycosaminoglycans [223], collagen [224], and carrageenan [225], have been associated with CS for cartilage engineering tissue applications. Hong et al. [224] developed an injectable composite scaffold obtained from collagen-coated polylactide microcarriers/CS hydrogel. Collagen-coated polylactide microcarriers enhanced the mechanical properties of the scaffold. The cell metabolic activity increased rapidly before 9 days of *in vitro* chondrocytes growth within the scaffold. After 9–12 days, confluent cell layers were formed. The composite scaffolds showed great potential for tissue engineering applications, particularly in orthopedics [224]. Liang et al. [225] developed rubbery CS/carrageenan hydrogels prepared by electroneutrality system as cartilage scaffold. The results showed pH- and salt-responsiveness, hierarchically porous architecture, and great mechanical properties. The hydrogels enhanced the viability and the adhesion of TDC5 cells [225].

Mechanical properties and biological activities may be altered by chemical modification of CS. *N*-succinyl CS possess biocompatibility and long-term retention *in vivo* [226]. Kamoun [227] developed *N*-succinyl CS-dialdehyde starch hydrogels for cartilage repair. The hydrogel was relatively stable, and the hydrolysis rate was limited with a high N-succinyl hydrogel composition without any by-products in physiological conditions. The adhered human gingival fibroblast cell number on hydrogel surface was improved by *N*-succinyl CS content in hybrid hydrogels. This hydrogel showed great potential to be used as injectable scaffold for cartilage repair [227]. *N*-succinyl CS can also be associated with other polysaccharides such as hyaluronic acid to prepare hydrogels, as an injectable scaffold, to improve biocompatibility and biodegradation [228].

Regarding skin tissue engineering, CS has been used in the preparation of scaffold hydrogel due to its biocompatibility [229], biodegradability [230], antibacterial properties [231], and hemostatic activity [232], stimulating fibroblast growth and accelerating tissue regeneration [233]. Franco et al. [234] developed CS/gelatin hydrogel scaffolds for skin engineering. The hydrogel showed a high porosity and

supported fibroblast cell proliferation. Notably, the scaffold with lowest crosslinker content swelled more than 600% of its dry weight [234].

Carboxymethyl CS can also be used in skin tissue engineering. This polysaccharide is biodegradable, biocompatible, and more bioactive than the raw CS [235]. Jaikumar et al. [236] developed alginate/O-carboxymethyl CS composite hydrogel scaffolds for adipose tissue regeneration with incorporation of fibrin nanoparticles. The use of fibrin nanoparticles promoted adhesion and proliferation on hydrogel. Human adipose-derived stem cells cultured on this hydrogel scaffold supported cell growth [236].

#### **3.5 Other technological applications**

The main reasons to propose different applications of hydrogels is attributed to their considerable volume change capacity in response to little surrounding alterations, such as electric and magnetic fields, solvent, pH, ionic strength, and temperature. Specifically, in biomedical application, it is desirable that the hydrogels may mimic the performance of human organs in response to some alterations in the environmental conditions such as pH, temperature, enzymes, and electric field [237].

Beyond technological applications mentioned in this session, hydrogel and nanocomposites based on CS and their derivatives have been studied for other several applications, such as contact lenses [238, 239], enzyme and cell separations and immobilizations [71, 240–243], DNA delivering [244], cartilage and skin regenerations [245–249], biosensors [250–252], submucosal fluid or injections [253–257], tissue engineering [258–263], postoperative adhesion prevention [264–266], cancer treatment [267–270], orthopedic applications [271, 272], artificial muscles [273], and others. Important characteristics of some cited applications are discussed as follows.

Among the different areas that the hydrogels would be used, the chemotherapy treatment is one of the most important due to great side effects that chemotherapy treatment provokes for patients, such as highly toxic, poor specific drugs, insufficient availability of drugs to the tumor, and others. In this way, the usual chemotherapy treatments have been changed to controlled/localized drug release technology using polysaccharide hydrogel as carrier vehicles [274]. In that work, the authors concluded that the CS/polyvinyl alcohol hydrogels have great potential to be used for the treatment of cancer because these 3D matrices had an antiproliferative effect and great capacity of the inhibit angiogenesis. In the work described by Pattavarakorn et al. [273], the authors found that the electroactive performance of the polythiophene/CS/carboxymethyl CS (PTh/CS/CMCS) as conductive hydrogel is dependent of the hydrogel composition, and the hydrogel prepared with 3:2 CS:CMCS ratio exhibited highest electric field response sensitivity. According to Tan et al. [275], CS and its derivatives are one of the most appropriate materials for enzyme immobilization because of a high specific surface area (high enzyme loading), nontoxicity, and biocompatibility, improving their stability and reusability.

Ulutürk and Alemdar [252] reported that the electroconductive hydrogel has great applicability as biosensor because this material can overcome some disadvantages of the inherently electroconductive polymers like toxicity and can also contribute to decreasing the release of the conductive polymer to the body. As mentioned before, hydrogels have been used in the biomedical area such as contact lens due to the possibility of increase up to 50% of drug bioavailability, which contributes to minimizing the collateral effect that this drug would provoke in the patient. However, the main disadvantage is that these carrier vehicles presented burst release in the first or couple of hours after application. In this way, Åhlén et al. [238] observed that contact lenses based on CS-poly(acrylic acid) nanoparticles and poly(vinyl alcohol) (PVA) hydrogels had greater potential for extended release

**75**

toxicities.

suffer eminent lack.

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications*

during 28 h. Postoperative peritoneal adhesion is one of the serious damages after surgeries, reaching until 67–93% after general surgical abdominal procedures, and as consequence, the patient may have various complications like chronic pain, female infertility, bowel obstruction, and others. *In vivo* studies realized by Song et al. [276] showed that the injectable N,O-carboxymethyl CS-aldehyde hyaluronic acid hydrogel had significant antiadhesion efficacy in a rat repeated-injury model. They observed that after 14 days, the peritoneum is completely recovered without

CT, CS, and CS derivatives have been used for wide technological applications, from metallic ions and dye absorbents in environmental to drug carriers in biomedical field. Another important application of CS derivative, for example, the trimethyled CS, is due to its antibacterial properties [277] and, at same time, no toxicity for human and animals. Most of the derivatives are soluble in the whole range of pH, for instance, the trimethyled CS, CS sulfate, and others. So, the drawback related to solubility of chitosan that is limited to acidic conditions (due to the pKa ca. 6.5) is overcome. The use of CS and its derivatives as hydrogels is one very important issue. The fact of CS being easily cross-linked or doing complexes, forming chemical or physical 3D matrixes, induced plenty of researchers to target themself for producing new materials through different methodologies/strategies/formulations, aiming to intensify some desired properties improving new applications. This is also due mainly to the relatively low cost, abundance, renewability, and biodegradability, among other advantages for using CS and its derivatives. In the last two decades, important technologies have been developed mostly for chemically modifying CS enabling to the preparation of hydrogels with a wide range of desired properties. A lot of examples were given in this review, but a very large window in this issue remains opened [278]. Some highlights, among others, can be given as trends in this field:

• Studies show that functional properties of CS and its derivatives clearly depend on their molecular weight. So, many studies need to be performed to investigate this aspect, because the molecular weight of chitosan depends strongly on the methodology used for CS obtainment from CT or the one used

• Besides the chitosan and its derivatives are not toxic to human or animals, current matter of discussion is whether these biopolymers may have the potential to influence physiological functions or metabolism in the microorganisms [277]. So, huge enforces need to be done in this issue because the molecular weight of CS is dependent on the methodology used for CS obtainment from

• Another important issue is to evaluate if the mixture of chitosan and chitosan derivatives with other polymer (synthetic or natural) affects their low

• The future of materials based on CS and CS derivatives is still more promising due to the lack of petroleum. In this way, eco-friendly extraction methods need to be developed. It was mentioned in this review that 1400 L of water is used for extracting and purifying 1 kg of chitosan. So, in the future, water will also

*DOI: http://dx.doi.org/10.5772/intechopen.81811*

**4. Future trends and perspectives**

for preparing the CS derivatives.

CT or for CS derivative preparation from raw CS.

adhesion aspect.

*Hydrogels Based on Chitosan and Chitosan Derivatives for Biomedical Applications DOI: http://dx.doi.org/10.5772/intechopen.81811*

during 28 h. Postoperative peritoneal adhesion is one of the serious damages after surgeries, reaching until 67–93% after general surgical abdominal procedures, and as consequence, the patient may have various complications like chronic pain, female infertility, bowel obstruction, and others. *In vivo* studies realized by Song et al. [276] showed that the injectable N,O-carboxymethyl CS-aldehyde hyaluronic acid hydrogel had significant antiadhesion efficacy in a rat repeated-injury model. They observed that after 14 days, the peritoneum is completely recovered without adhesion aspect.

## **4. Future trends and perspectives**

*Hydrogels - Smart Materials for Biomedical Applications*

**3.5 Other technological applications**

growth [236].

supported fibroblast cell proliferation. Notably, the scaffold with lowest cross-

Carboxymethyl CS can also be used in skin tissue engineering. This polysaccharide is biodegradable, biocompatible, and more bioactive than the raw CS [235]. Jaikumar et al. [236] developed alginate/O-carboxymethyl CS composite hydrogel scaffolds for adipose tissue regeneration with incorporation of fibrin nanoparticles. The use of fibrin nanoparticles promoted adhesion and proliferation on hydrogel. Human adipose-derived stem cells cultured on this hydrogel scaffold supported cell

The main reasons to propose different applications of hydrogels is attributed to their considerable volume change capacity in response to little surrounding alterations, such as electric and magnetic fields, solvent, pH, ionic strength, and temperature. Specifically, in biomedical application, it is desirable that the hydrogels may mimic the performance of human organs in response to some alterations in the environmental conditions such as pH, temperature, enzymes, and electric field [237]. Beyond technological applications mentioned in this session, hydrogel and nanocomposites based on CS and their derivatives have been studied for other several applications, such as contact lenses [238, 239], enzyme and cell separations and immobilizations [71, 240–243], DNA delivering [244], cartilage and skin regenerations [245–249], biosensors [250–252], submucosal fluid or injections [253–257], tissue engineering [258–263], postoperative adhesion prevention [264–266], cancer treatment [267–270], orthopedic applications [271, 272], artificial muscles [273], and others. Important characteristics of some cited applications are discussed as follows. Among the different areas that the hydrogels would be used, the chemotherapy

treatment is one of the most important due to great side effects that chemotherapy treatment provokes for patients, such as highly toxic, poor specific drugs, insufficient availability of drugs to the tumor, and others. In this way, the usual chemotherapy treatments have been changed to controlled/localized drug release technology using polysaccharide hydrogel as carrier vehicles [274]. In that work, the authors concluded that the CS/polyvinyl alcohol hydrogels have great potential to be used for the treatment of cancer because these 3D matrices had an antiproliferative effect and great capacity of the inhibit angiogenesis. In the work described by Pattavarakorn et al. [273], the authors found that the electroactive performance of the polythiophene/CS/carboxymethyl CS (PTh/CS/CMCS) as conductive hydrogel is dependent of the hydrogel composition, and the hydrogel prepared with 3:2 CS:CMCS ratio exhibited highest electric field response sensitivity. According to Tan et al. [275], CS and its derivatives are one of the most appropriate materials for enzyme immobilization because of a high specific surface area (high enzyme loading), nontoxicity, and biocompatibility, improving their stability and reusability. Ulutürk and Alemdar [252] reported that the electroconductive hydrogel has great applicability as biosensor because this material can overcome some disadvantages of the inherently electroconductive polymers like toxicity and can also contribute to decreasing the release of the conductive polymer to the body. As mentioned before, hydrogels have been used in the biomedical area such as contact lens due to the possibility of increase up to 50% of drug bioavailability, which contributes to minimizing the collateral effect that this drug would provoke in the patient. However, the main disadvantage is that these carrier vehicles presented burst release in the first or couple of hours after application. In this way, Åhlén et al. [238] observed that contact lenses based on CS-poly(acrylic acid) nanoparticles and poly(vinyl alcohol) (PVA) hydrogels had greater potential for extended release

linker content swelled more than 600% of its dry weight [234].

**74**

CT, CS, and CS derivatives have been used for wide technological applications, from metallic ions and dye absorbents in environmental to drug carriers in biomedical field. Another important application of CS derivative, for example, the trimethyled CS, is due to its antibacterial properties [277] and, at same time, no toxicity for human and animals. Most of the derivatives are soluble in the whole range of pH, for instance, the trimethyled CS, CS sulfate, and others. So, the drawback related to solubility of chitosan that is limited to acidic conditions (due to the pKa ca. 6.5) is overcome.

The use of CS and its derivatives as hydrogels is one very important issue. The fact of CS being easily cross-linked or doing complexes, forming chemical or physical 3D matrixes, induced plenty of researchers to target themself for producing new materials through different methodologies/strategies/formulations, aiming to intensify some desired properties improving new applications. This is also due mainly to the relatively low cost, abundance, renewability, and biodegradability, among other advantages for using CS and its derivatives. In the last two decades, important technologies have been developed mostly for chemically modifying CS enabling to the preparation of hydrogels with a wide range of desired properties. A lot of examples were given in this review, but a very large window in this issue remains opened [278]. Some highlights, among others, can be given as trends in this field:


Of course, the understanding of structure-properties-applications relationship in application of CS and CS derivatives as hydrogels will be expanded with more comprehensive studies. Certainly, this will increase the significance of these important soft materials, considering their application.
