**1. Introduction**

Cell encapsulation is a process that involves immune protection of the living cell by using different polymers. The polymers can be distinguished into two main groups: natural origin (i.e., polysaccharides, polynucleotides, polypeptides) [1] and synthetic polymers (i.e., polyethylene glycol, polyvinyl alcohol, polyurethane, etc.). Several attempts have been made by scientists to use natural, synthetic, and semi-synthetic polymers in the field of encapsulation. The first approach was made in 1933 by Bisceglie et al. and used enveloped membrane to demonstrate tumor cell survival in the abdominal cavity of guinea pigs [2]. In his report, the cells survived for 12 days by diffusion of the nutrients. However, at that time immunoisolation technology was not known or understood [3]. Later, in 1943 Algire et al. reported a transparent chamber for atherapeutic approach *in vivo* [4]. Since this report, therapeutic demands enhanced this encapsulation technology in a way that combines the polymer source (produced synthetically or isolated from natural sources) and their functionality by using its characterization.

Several advantages and disadvantages have been reported about synthetic polymers [5]. Mechanical specifications can be more easily engineered or modified with the desired characteristics and particularly can be produced with larger amounts [6–8]. The main deficit of synthetic polymers is that they require toxic substances during the capsulation process; therefore, cell viability is a true obstacle after encapsulation [8, 9]. In this regard, synthetic polymers are frequently used in combination with different devices such as macrocapsules. Before accommodation of the encapsules, first, synthetic polymers are manufactured in the absence of living tissue/cells, and second, tissue/cells are combined with the device to preserve direct contact of the toxic solvents [1]. The most common synthetic polymers are poly(ethylene glycol) [10], polyvinyl alcohol [11], polyurethane [12], poly(ether sulfone) [13], polypropylene [14], sodium polystyrene sulfate [15], polyacrylate [16], polyphosphazene [17], AN69 [18], and lastly polytetrafluoroethylene [19].

Natural polymers have been proposed for immunoisolation based on two distinct features. First, there is no interference with the functionality of cells/tissues and second, the stability of the structure they provide during encapsulation [1, 20]. Conventionally, the most frequently used polymers from natural sources are cellulose [21], chitosan [22], collagen [23], agarose [24], and alginate [25]. The experimental success mainly depends on the application and mimicry potential of the natural polymers. Among these, in this chapter, we mainly focused on the alginate-based encapsulation and its clinical application.

## **2. Alginates**

The most versatile biomaterials among natural polymers are alginates, which are used in a wide range of applications including diffusion systems, drug delivery, as a wound dressing, and for encapsulation when the transplantation has to be a substitute [25–27]. Alginates are hydrophilic compounds that are naturally found in the cell wall, extracellular matrix of brown algae and some species of bacteria, for example, *Pseudomonas aeruginosa* and *Azotobacter vinelandii* [26, 27]. The most common algae source is brown seaweed. During alginate extraction, alginic acid is generally obtained and converted to a form of salt [26]. Several forms of alginates are currently approved by the Food and Drug Administration (FDA) for use, particularly in the replacement of missing/nonfunctioning endocrine-related diseases [28].

#### **2.1 Gelling and ionic cross-linking of alginates**

Alginates are linear copolymers that include two hexuronic acid residues that become dimeric blocks, which are composed of -D-mannuronic (M) and -Lguluronic (G) acids for building the entire molecule [29]. These blocks are known as the building blocks of alginates. Mainly, the ratio of G and M blocks depends on the source of the algae type [9]. The important feature of these building blocks is the sensitivity to binding of multivalent cations. This is the starting point of this water-soluble polysaccharide, which allows alginate to form as hydrogels. This characteristic of the hydrogel equilibrates between the environment and the relatively physiologic internal environment [29]. The divalent cations and hydrogel feature depends on the divalent ion's affinity to alginate. Several studies reported high-rate ion affinity results in a stronger gel structure. In order to decrease the ion binding strength, divalent cations should be chosen from the following order: Pb2+>Cu2+>Cd2+>Ba2+>Sr2+>Ca2+>Co2+>Ni2+>Zn2+>Mn2+ [1, 29, 30] (**Figure 1**). Controlling cation addition to maintain a porous alginate structure is a critical step.

**171**

**Figure 2.**

*(CC-BY 4.0).*

manner [35].

**Figure 1.**

occur [36].

the spheres.

*Microencapsulation for Clinical Applications and Transplantation by Using Different Alginates*

Successful formation of alginate spheres for delivery purposes requires suitable and selective methods. In 2006, Darrabie et al. identified gelling-cation stability by determining swelling, which contributes to colloid osmotic pressure. They suggested that Ca2+ is more hygroscopic and less prominent swelling occurs when compared with Ba2+ [32]. Protecting the conformational polymer blocks during preparation of the alginate gels for microencapsulation has been reported using different methods including conjugation of long alkyl chains [33] or dodecylamine [34], temperature (up to 60°C ± 1°C) [35, 36], emulsification by cationic agent [37], and ionotropic gelation of alginate layers [38], etc. Slow gelation utilizes the alginate solution in a more uniform structure in a gradual

*article distributed under the terms of the creative commons by attribution 4.0 (CC-BY 4.0).*

*Representative image for the formation of egg-box ionic cross-links between guluronic acid-rich monomer units (box) and the divalent cations (eggs). Reprinted from Baumberger and Ronsin (2009) [31], an open access* 

In the latter case, Lee et al. reported a degree of cross-linking of the alginate can influence a low dose of drug entrapment and unsuitable pore sizes for transplantation. In addition, the efficiency of the microcapsule size or content was found irrelevant, although the preparation step of the water-soluble alginate itself appears to be responsible for the arrangement of the polymer blocks [37]. Crosslinking capacity of the alginates can be modifiable and flexible (**Figure 2**). There are more than 200 types of biocompatible alginates manufactured so far [25, 26]. Moreover, due to the different cross-linking degree of various alginate types, switch in homogenous distribution of the graft/drug during the encapsulation process may

Both features of alginates promote several advantages over other polymers such as the stability of the building blocks (-G and/or/both -M repetitively); elasticity of the alginate hydrogel; surface roughness, which is related to elasticity as well, approximately 1% of the alginate can entrap a hundred times more water than its weight; and lastly permitting the ability of oxygen and nutrient permeation inside

*Representative image of alginate gelation process by continued calcium cations. Reprinted from Dumitru et al. [39], an open access article distributed under the terms of the creative commons by attribution 4.0* 

*DOI: http://dx.doi.org/10.5772/intechopen.92134*

*Microencapsulation for Clinical Applications and Transplantation by Using Different Alginates DOI: http://dx.doi.org/10.5772/intechopen.92134*

**Figure 1.**

*Nano- and Microencapsulation - Techniques and Applications*

alginate-based encapsulation and its clinical application.

Several advantages and disadvantages have been reported about synthetic polymers [5]. Mechanical specifications can be more easily engineered or modified with the desired characteristics and particularly can be produced with larger amounts [6–8]. The main deficit of synthetic polymers is that they require toxic substances during the capsulation process; therefore, cell viability is a true obstacle after encapsulation [8, 9]. In this regard, synthetic polymers are frequently used in combination with different devices such as macrocapsules. Before accommodation of the encapsules, first, synthetic polymers are manufactured in the absence of living tissue/cells, and second, tissue/cells are combined with the device to preserve direct contact of the toxic solvents [1]. The most common synthetic polymers are poly(ethylene glycol) [10], polyvinyl alcohol [11], polyurethane [12], poly(ether sulfone) [13], polypropylene [14], sodium polystyrene sulfate [15], polyacrylate [16], polyphosphazene [17], AN69 [18], and lastly polytetrafluoroethylene [19]. Natural polymers have been proposed for immunoisolation based on two distinct features. First, there is no interference with the functionality of cells/tissues and second, the stability of the structure they provide during encapsulation [1, 20]. Conventionally, the most frequently used polymers from natural sources are cellulose [21], chitosan [22], collagen [23], agarose [24], and alginate [25]. The experimental success mainly depends on the application and mimicry potential of the natural polymers. Among these, in this chapter, we mainly focused on the

The most versatile biomaterials among natural polymers are alginates, which are used in a wide range of applications including diffusion systems, drug delivery, as a wound dressing, and for encapsulation when the transplantation has to be a substitute [25–27]. Alginates are hydrophilic compounds that are naturally found in the cell wall, extracellular matrix of brown algae and some species of bacteria, for example, *Pseudomonas aeruginosa* and *Azotobacter vinelandii* [26, 27]. The most common algae source is brown seaweed. During alginate extraction, alginic acid is generally obtained and converted to a form of salt [26]. Several forms of alginates are currently approved by the Food and Drug Administration (FDA) for use, particularly in the replacement of missing/nonfunctioning endo-

Alginates are linear copolymers that include two hexuronic acid residues that become dimeric blocks, which are composed of -D-mannuronic (M) and -Lguluronic (G) acids for building the entire molecule [29]. These blocks are known as the building blocks of alginates. Mainly, the ratio of G and M blocks depends on the source of the algae type [9]. The important feature of these building blocks is the sensitivity to binding of multivalent cations. This is the starting point of this water-soluble polysaccharide, which allows alginate to form as hydrogels. This characteristic of the hydrogel equilibrates between the environment and the relatively physiologic internal environment [29]. The divalent cations and hydrogel feature depends on the divalent ion's affinity to alginate. Several studies reported high-rate ion affinity results in a stronger gel structure. In order to decrease the ion binding strength, divalent cations should be chosen from the following order: Pb2+>Cu2+>Cd2+>Ba2+>Sr2+>Ca2+>Co2+>Ni2+>Zn2+>Mn2+ [1, 29, 30] (**Figure 1**). Controlling cation addition to maintain a porous alginate structure is a critical step.

**170**

**2. Alginates**

crine-related diseases [28].

**2.1 Gelling and ionic cross-linking of alginates**

*Representative image for the formation of egg-box ionic cross-links between guluronic acid-rich monomer units (box) and the divalent cations (eggs). Reprinted from Baumberger and Ronsin (2009) [31], an open access article distributed under the terms of the creative commons by attribution 4.0 (CC-BY 4.0).*

Successful formation of alginate spheres for delivery purposes requires suitable and selective methods. In 2006, Darrabie et al. identified gelling-cation stability by determining swelling, which contributes to colloid osmotic pressure. They suggested that Ca2+ is more hygroscopic and less prominent swelling occurs when compared with Ba2+ [32]. Protecting the conformational polymer blocks during preparation of the alginate gels for microencapsulation has been reported using different methods including conjugation of long alkyl chains [33] or dodecylamine [34], temperature (up to 60°C ± 1°C) [35, 36], emulsification by cationic agent [37], and ionotropic gelation of alginate layers [38], etc. Slow gelation utilizes the alginate solution in a more uniform structure in a gradual manner [35].

In the latter case, Lee et al. reported a degree of cross-linking of the alginate can influence a low dose of drug entrapment and unsuitable pore sizes for transplantation. In addition, the efficiency of the microcapsule size or content was found irrelevant, although the preparation step of the water-soluble alginate itself appears to be responsible for the arrangement of the polymer blocks [37]. Crosslinking capacity of the alginates can be modifiable and flexible (**Figure 2**). There are more than 200 types of biocompatible alginates manufactured so far [25, 26]. Moreover, due to the different cross-linking degree of various alginate types, switch in homogenous distribution of the graft/drug during the encapsulation process may occur [36].

Both features of alginates promote several advantages over other polymers such as the stability of the building blocks (-G and/or/both -M repetitively); elasticity of the alginate hydrogel; surface roughness, which is related to elasticity as well, approximately 1% of the alginate can entrap a hundred times more water than its weight; and lastly permitting the ability of oxygen and nutrient permeation inside the spheres.

#### **Figure 2.**

*Representative image of alginate gelation process by continued calcium cations. Reprinted from Dumitru et al. [39], an open access article distributed under the terms of the creative commons by attribution 4.0 (CC-BY 4.0).*

#### **2.2 Biotolerability over biocompatibility**

Source-dependent impurities may have detrimental effects. Safe and effective delivery of the therapeutic graft/drug with the alginate carrier is frequently mentioned as biocompatible. This naturally derived product provides immunoprotection and most of the studies reported purity of its building block structure preventing a host response when transplanted. Therefore, this makes alginate the most common material for microencapsulation. Higher water-carrying capability of alginates has been shown to directly maintain diffusion and this shows immune-safe characteristics [3]. A decade ago, Kendall et al. focused on the various components of alginate blocks and compared their purity and sphere sizes depending on the cationic agent. They reported that higher purification of alginate prevents imperfections and size/ shape properties would affect immunogenicity [40]. Several other reports also demonstrated that -G and -M blocks of the alginate gel need a balance whereas the distribution of these proportions indicates the biocompatibility of the purified alginate is influenced by its viscosity [41–43]. One of the most obvious results from the studies that explains the difference between the building block's balance in alginate gels is higher -M blocks mainly stimulate and induce an immune response [41, 44–46].

There are many immunogenic substances such as endotoxins, proteins, and polyphenols in natural polymers including alginates. Those molecules may diffuse the outer surface from the capsules and then induce an unwanted immune response against the capsules [3]. There are highly conserved molecular motifs that are present in nature and pathogens known as pathogen-associated molecular patterns (PAMPs). PAMPs provoke pattern recognition receptors (PRRs) to enhance inflammatory response [47]. The presence of PAMPs in natural products and alginate as well is not a direct threat; however, complement activation has been reported for encapsulated islets [48]. Therefore, complement activation has a more destructive effect than the inflammatory response; it may activate and produce large quantities of cytokines to induce a stronger response.

Immunoprotective properties still require the exact characterization and preparation of the material to be used as a delivery agent. Despite giving most of the efforts to optimize the encapsulation process, the applicability of this technology has still resulted in an insufficient investigation of graft/drug delivery. In 2014, Rokstad et al. described the duration and the type of host responses and divided the whole process into three categories: acute inflammation, chronic inflammation, and the long-lasting granulation tissue phase [48]. Based on the publications from islet transplantation studies, it was reported that the granulation phase mainly refers to the "vascularized fibrous tissue containing a moderate epithelial histiocytic response" [49–52]. Solely, it is important to observe these responses and that leads to the question: Why do alginate microencapsules contribute to these chain of events even when their purity, stability, and biocompatibility are comparable to most other polymers? Immunocompatibility of the alginate microencapsules should not be determined only by the features of alginate and its preparation process, but should also be evaluated for its protein absorption capability as well.

A profound impact might be introduced with the biotolerability term. Biotolerability is a term for a strategy of making biocompatible encapsulations to induce none/minimal host response. A seemingly minimal cellular overgrowth for graft provides the free diffusion of nutrients, oxygen, and some therapeutic proteins, and controlled drug release from the microcapsules. We should emphasize that the alginate microspheres are not meant to prevent an immune response yet to protect the carrier against an immune response. Therefore, the biocompatibility term not clear enough to explain the biotolerability of the carrier system.

**173**

in **Table 1**.

*Microencapsulation for Clinical Applications and Transplantation by Using Different Alginates*

The vascularization process of the microencapsules is another requirement to increase the survival of the transplanted graft. Sufficient vascularization may be achieved by improving the physical features of the spheres such as the size of the spheres or micropores and the amount/density of the graft/cells. The main argument against vascularization is hypoxia and oxidative stress whereby it develops inside the microspheres [53]. Insufficient oxygenation and nutrition occur particularly in the absence of ideal vascularization. A prerequisite is that the functional performance of the microencapsules often depends on the surface-to-volume ratio. This implies that free diffusion of nutrients and oxygen is necessary and this

The majority of researchers developed different strategies to allow a fast exchange of nutrition and demonstrated several boundaries to ensure a low or no inflammatory response while supplying oxygen-nutrients inside [29, 53]. Currently, the accepted limitations of the islet transplantation are defined with three main strategies: first, the cell-to-volume ratio should not exceed 10% even if a large number of cells are required to reach curative treatment. Second, microencapsules should be kept <1 mm, once they reach the spheres they do not maintain their biphasic effect (releasing insulin after a glucose challenge) and also an immune response may be triggered. Third, direct vascular access of the microencapsules to the optimal transplantation site, for instance, glucose must pass and be observed in the transplantation site and then islets release insulin to diffuse through circulation. The whole process requires time and larger amounts to reach an effective dose

A broad range of clinical applications of the microencapsulation process have shown promising results despite encountering some biotolerability issues. Multiple disciplines have been using this alginate encapsulation technology including chemistry, protein science, and cell therapy (mostly transplantation and immunology field). The most studied and reported diseases include Type 1 diabetic patients (T1DM) [55], permanent hypoparathyroidism patients [56], scaffold systems for tissue engineering [57], bone regeneration [58, 59], leukemia (an *in vivo* study that uses alginate to encapsulate specialized hybridoma cells) [60], and even neurodegenerative diseases [61]. Some of the clinical studies about cell therapy are compiled

Based on the current experience with alginate, most of the studies have already performed transplantation of beta-cells (islets). The first and well-known clinical trial with islet transplantation was performed in 1994 by Soon-Shiong et al. They reported 9 months of survival of the microencapsules, which were prepared with high guluronic acid containing alginate [49]. Another case reported how islet transplantation was prepared with alginate- poly-l-ornithine and that the patient's need for insulin decreased after transplantation [62]. Following two case reports, Tuch et al. used barium alginate to encapsulate islets and transplanted these into four recipients. In their report, grafts showed various survival rates and did not restore insulin requirements [51]. Considering the last case reports, several companies took the stage and initiated clinical trials to overcome T1DM by using macro- and microencapsulation with alginate and other polymers. In 2014, Scharp and Marchetti evaluated the outcomes of islet encapsulation from companies with larger clinical studies, respectively. The increased interest in islet transplantation reached its most

*DOI: http://dx.doi.org/10.5772/intechopen.92134*

directly interferes with vascularization.

to lower glucose [1, 53, 54].

**3. Clinical applications**

**2.3 Vascularization**

*Microencapsulation for Clinical Applications and Transplantation by Using Different Alginates DOI: http://dx.doi.org/10.5772/intechopen.92134*

### **2.3 Vascularization**

*Nano- and Microencapsulation - Techniques and Applications*

Source-dependent impurities may have detrimental effects. Safe and effective delivery of the therapeutic graft/drug with the alginate carrier is frequently mentioned as biocompatible. This naturally derived product provides immunoprotection and most of the studies reported purity of its building block structure preventing a host response when transplanted. Therefore, this makes alginate the most common material for microencapsulation. Higher water-carrying capability of alginates has been shown to directly maintain diffusion and this shows immune-safe characteristics [3]. A decade ago, Kendall et al. focused on the various components of alginate blocks and compared their purity and sphere sizes depending on the cationic agent. They reported that higher purification of alginate prevents imperfections and size/ shape properties would affect immunogenicity [40]. Several other reports also demonstrated that -G and -M blocks of the alginate gel need a balance whereas the distribution of these proportions indicates the biocompatibility of the purified alginate is influenced by its viscosity [41–43]. One of the most obvious results from the studies that explains the difference between the building block's balance in alginate gels is higher -M blocks mainly stimulate and induce an immune response [41, 44–46]. There are many immunogenic substances such as endotoxins, proteins, and polyphenols in natural polymers including alginates. Those molecules may diffuse the outer surface from the capsules and then induce an unwanted immune response against the capsules [3]. There are highly conserved molecular motifs that are present in nature and pathogens known as pathogen-associated molecular patterns (PAMPs). PAMPs provoke pattern recognition receptors (PRRs) to enhance inflammatory response [47]. The presence of PAMPs in natural products and alginate as well is not a direct threat; however, complement activation has been reported for encapsulated islets [48]. Therefore, complement activation has a more destructive effect than the inflammatory response; it may activate and produce large quantities

Immunoprotective properties still require the exact characterization and preparation of the material to be used as a delivery agent. Despite giving most of the efforts to optimize the encapsulation process, the applicability of this technology has still resulted in an insufficient investigation of graft/drug delivery. In 2014, Rokstad et al. described the duration and the type of host responses and divided the whole process into three categories: acute inflammation, chronic inflammation, and the long-lasting granulation tissue phase [48]. Based on the publications from islet transplantation studies, it was reported that the granulation phase mainly refers to the "vascularized fibrous tissue containing a moderate epithelial histiocytic response" [49–52]. Solely, it is important to observe these responses and that leads to the question: Why do alginate microencapsules contribute to these chain of events even when their purity, stability, and biocompatibility are comparable to most other polymers? Immunocompatibility of the alginate microencapsules should not be determined only by the features of alginate and its preparation process, but should also be evaluated for its protein absorption

A profound impact might be introduced with the biotolerability term. Biotolerability is a term for a strategy of making biocompatible encapsulations to induce none/minimal host response. A seemingly minimal cellular overgrowth for graft provides the free diffusion of nutrients, oxygen, and some therapeutic proteins, and controlled drug release from the microcapsules. We should emphasize that the alginate microspheres are not meant to prevent an immune response yet to protect the carrier against an immune response. Therefore, the biocompatibility

term not clear enough to explain the biotolerability of the carrier system.

**2.2 Biotolerability over biocompatibility**

of cytokines to induce a stronger response.

**172**

capability as well.

The vascularization process of the microencapsules is another requirement to increase the survival of the transplanted graft. Sufficient vascularization may be achieved by improving the physical features of the spheres such as the size of the spheres or micropores and the amount/density of the graft/cells. The main argument against vascularization is hypoxia and oxidative stress whereby it develops inside the microspheres [53]. Insufficient oxygenation and nutrition occur particularly in the absence of ideal vascularization. A prerequisite is that the functional performance of the microencapsules often depends on the surface-to-volume ratio. This implies that free diffusion of nutrients and oxygen is necessary and this directly interferes with vascularization.

The majority of researchers developed different strategies to allow a fast exchange of nutrition and demonstrated several boundaries to ensure a low or no inflammatory response while supplying oxygen-nutrients inside [29, 53]. Currently, the accepted limitations of the islet transplantation are defined with three main strategies: first, the cell-to-volume ratio should not exceed 10% even if a large number of cells are required to reach curative treatment. Second, microencapsules should be kept <1 mm, once they reach the spheres they do not maintain their biphasic effect (releasing insulin after a glucose challenge) and also an immune response may be triggered. Third, direct vascular access of the microencapsules to the optimal transplantation site, for instance, glucose must pass and be observed in the transplantation site and then islets release insulin to diffuse through circulation. The whole process requires time and larger amounts to reach an effective dose to lower glucose [1, 53, 54].
