# Inulin-Grafted Stearate (In-g-St) as the Effective Self-Assembling Polymeric Micelle: Synthesis and Evaluation for the Delivery of Betamethasone

Authors: Gholamabbas Chehardoli; Parham Norouzian; Farzin Firozian
Journal: Journal of Nanomaterials
 (2020)

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## Abstract

Background. Betamethasone as a corticosteroid drug is commonly used for the treatment of rheumatoid arthritis. Unfortunately, betamethasone is a low water-soluble drug and its efficacy is low. So an attractive strategy is the targeted delivery of betamethasone to the damaged joint using polymeric micelle-based carriers. Methods. Inulin-grafted stearate (In-g-St) was synthesized via the reaction of stearoyl chloride and inulin, then characterized by FT-IR and H-NMR. In-g-St forms micelles in the presence of betamethasone. The prepared polymeric micelles were characterized for size, zeta potential, drug loading, particles’ morphology, critical micelle concentration (CMC), and encapsulation efficiency. So sustained release polymeric micelles of betamethasone were developed by employing In-g-St. Results. The measurement of particle size showed a mean diameter of 60 and 130 nm for 10% and 20% drug-loaded micelles, respectively, and SEM showed that the particle’s morphologies are spherical. Zeta potential measurement for the drug-containing micelles showed a value of -11.8 mV. Drug loading efficiency and the encapsulation efficiency were 6.36% and 63.6%, as well as 18.97% and 94.88% for 10% and 20%, respectively. 20% drug-loaded polymer showed a small burst release of betamethasone at the first 3 h which was followed by sustained release in the next 24 h. Furthermore, the formula with 10% exhibited good sustained release properties except for the minor initial burst release. Conclusion. Data from the zeta potential, CMC, drug loading capacity, and in vitro drug release studies indicated that In-g-St polymeric micelles can be suitable candidates for the efficient delivery of hydrophobic drugs like betamethasone.


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## Body

## 1. Introduction

Rheumatoid arthritis (RA), as one of the autoimmune and chronic inflammatory diseases, has affected approximately 1% of the world’s population [1]. This disease arises more commonly in the elderly people primarily determined by the pain and swelling in the small joints and wrist of the hands and feet, which in severe cases can lead to the progressive disability and premature death [2]. Currently, early diagnosis and treatment strategies that are based on glucocorticoids and nonsteroidal anti-inflammatory drugs could improve the RA patient’s quality of life [3]. Glucocorticoids or corticosteroids such as prednisone prednisolone, dexamethasone, and betamethasone as synthetic compounds similar to cortisol hormone can help to reduce the inflammation, stiffness, and pain of the swollen joints [4]. While there is currently no promising cure for RA, different pharmacologic therapy strategies are aimed at increasing the efficacy of existing drugs and attenuating disease progression and decrease and/or delay deformity of joints [5]. Therefore, even though long-term disease remission is not yet achieved for many patients and also the increasing number of various drugs and treatment regimes, novel strategies for drug delivery and new therapeutic options are required [5, 6].Betamethasone as one of the effective synthetic corticosteroid drugs is commonly used for the treatment of RA by attenuating inflammation and slowing joint damage [7]. However, these kinds of drugs also face some limitations, of which the most important ones are their toxicity especially with long-term use, low solubility, frequent administrations, and side effects on other tissues [8]. To overcome these problems, some strategies were introduced such as reducing toxicity by intra-articular administration of the drug and minimizing exposure of the drug to other tissues, but in RA, this requires repeated joint needling into a large number of joints, which faces treatment with other complications [9]. Therefore, an attractive strategy is the targeted delivery of betamethasone to the damaged joint using liposomes and polymeric micelle-based carriers. Over recent decades, there has been considerable interest in liposomes, polymeric micelles, and other nanoparticles as pharmaceutical nanocarriers for encapsulating various drugs and an effective option for their delivery to the target tissue [10–14]. In this regard, liposome-encapsulated betamethasone has been proven to be very effective for increasing the uptake and stability of the drug in the synovial cavity of damaged joints [15–17]. Besides liposomes, polymer micelles as drug carriers can also be targeted at the damaged site [18, 19]. The advantage of these nanoparticles is their low leakage, light stability, cheap industrial production, and their ease of use compared to liposomes [5, 20]. Besides, by formulating insoluble drugs in the form of lyophilized polymeric micelles, it can be considered as an injectable and stable dosage form candidate for the treatment of the condition by the medical community [14].Inulin, which is found as a group of natural polysaccharides [21–23] in various plants, with hydrophobic groups can form polymeric micelles in the aqueous solutions. Unique physicochemical properties (nontoxicity, biocompatibility, and water solubility), low-cost production, and their efficiency have introduced inulin as the attractive starting material to develop new drug carriers [24–27].In continuation of our studies on the polymer manipulation [28] specially grafting [29], in the present study, inulin-grafted stearate (In-g-St) would be synthesized for the formation of polymeric micelles as suitable carriers of betamethasone. Also, the release profile of betamethasone from the polymeric micelles has been studied.


## 2. Material and Methods

### 2.1. Synthesis of Inulin-Grafted Stearate Polymeric Micelles

Under the N2 atmosphere, 2 g of inulin was mixed with 4 g lithium chloride in 20 mL of dimethylformamide (DMF) at 120°C. The mixture was stirred while reaching a clear and colorless solution. After decreasing the temperature to 80°C, 360 mg dimethylaminopyridine and 840 μL stearoyl chloride were added to the solution and refluxed for 24 hours. Then, the reaction mixture was dialyzed in 1 L ethanol by dialysis tubing with cutoff 2000 Da. After 12 hours, the dialysis tubing was transferred to 1 L water and the proses were continued up to 24 hours. Ultimately, by freeze-drying of the final solution, the lyophilized modified polymer was achieved.


### 2.2. Critical Micelle Concentration (CMC) Assay

The critical micelle concentration (CMC) of the In-g-St polymer was determined by studying the fluorescence spectra of pyrene as a hydrophobic fluorescent probe. Using the phosphate-buffered solution (PBS,pH=7.4), the different concentrations of polymer solutions from 1.55 μg/mL to 200 μg/mL were prepared and then mixed with 1 mL of pyrene solution 6×10−6mol/L in acetone while being stirred overnight to give the final concentration of pyrene (6×10−7mol/L).The fluorescence emission spectra of the solutions and pure pyrene solution in the PBS were obtained at a fixed emission wavelength (λem) of 390 nm. Based on the survey done on these spectrum fluorescence intensities of the samples at λex=335nm and 338 nm as determined using a fluorescence spectrophotometer, FP-6000.The changes in the ratio of fluorescence intensityλex=338nm to 335 nm (I335/I337) of pyrene were plotted against the log concentration of the In-g-St polymer for finding the CMC.


### 2.3. Loading of Betamethasone onto Polymeric Micelles and Drug Loading Efficiency

A dialysis method was used for the preparation of betamethasone-loaded micelles (10% and 20%). Briefly, 20 and 40 mg of betamethasone were added to 160 and 180 mg of (In-g-St), respectively, and the mixture was dissolved in 5 mL dimethyl sulfoxide (DMSO) and stirred for 1 hour at room temperature. To remove the unloaded drug and DMSO, the mixture was poured into a dialysis tube (Molecular cut off 2000 Da) and dialyzed against 1 L water for 1 hour; then, the dialysis solution was exchanged with the same amount of freshwater and the press was continued up to 24 hours. Thereafter, by freeze-drying, the lyophilized powder was obtained. In order to determine the percentage of betamethasone encapsulated in nanoparticles, a high-performance liquid chromatography (HPLC) analysis method was used. Briefly, 4 mg of each drug-loaded polymer (10% and 20%) dissolved in 10 mL DMSO; then, 1 mL of this solution was mixed with acetonitrile to make 10 mL volume of the final solution. After that, betamethasone concentration was determined by HPLC with ultraviolet detection at 240 nm using a Shimadzu apparatus (Shimadzu Corp., Model LC-20AD XR, Japan) equipped with an autosampler. Betamethasone loading efficiency (%) and loading content (%) of the prepared formulation were calculated as follows:(1)EncapsulationefficiencyEE%=MassofbetamethasonewithinthenanoparticleMassofbetamethasoneinitiallyused×100,DrugloadingDL%=MassofbetamethasonewithinthenanoparticleMassofnanoparticle×100.


### 2.4. Particle Size Distribution Measurements

Particle size, surface charge, and particle size distribution of betamethasone-loaded In-g-St nanoparticles were determined using a nanosizer apparatus (Nano-ZS; Malvern Instruments, United Kingdom).One mL of betamethasone-loaded micelle was diluted in deionized water, and the micelle size was determined by Zetasizer Nano ZS instrument at a wavelength of 633 nm at 25°C with a detection angle of 90°.


### 2.5. Characterization of Particle Morphology

Transmission electron microscopy (TEM) and scanning electron microscopy (SEM) techniques are used to evaluate the morphology of nanoparticles [30–33]. In this study, we used the SEM technique. SEM assay is performed at the central laboratory of Shahid Chamran University of Ahvaz by using a scanning electron microscope apparatus (Model 1455 VP manufactured by DME).


### 2.6. In Vitro Drug Release Evaluation

The evaluation of betamethasone release profile from micelle formulation was performed by the dialysis method. In brief, 25 mg of betamethasone-loaded micelle powder was dispersed in 2 mL of phosphate-buffered saline (pH 7.4), then added into the dialysis tubes (cut off 12000 Da). The tube was placed in a 100 mL bottle of phosphate-buffered saline (pH 7.4). Then, the capped bottles were incubated at 150 RPM spinning in 37°C shaker incubator. The samples were withdrawn at 1, 3, 6, 12, and 24 hours; then, the concentration of the drug in the samples was evaluated by the HPLC method.


## 2.1. Synthesis of Inulin-Grafted Stearate Polymeric Micelles

Under the N2 atmosphere, 2 g of inulin was mixed with 4 g lithium chloride in 20 mL of dimethylformamide (DMF) at 120°C. The mixture was stirred while reaching a clear and colorless solution. After decreasing the temperature to 80°C, 360 mg dimethylaminopyridine and 840 μL stearoyl chloride were added to the solution and refluxed for 24 hours. Then, the reaction mixture was dialyzed in 1 L ethanol by dialysis tubing with cutoff 2000 Da. After 12 hours, the dialysis tubing was transferred to 1 L water and the proses were continued up to 24 hours. Ultimately, by freeze-drying of the final solution, the lyophilized modified polymer was achieved.


## 2.2. Critical Micelle Concentration (CMC) Assay

The critical micelle concentration (CMC) of the In-g-St polymer was determined by studying the fluorescence spectra of pyrene as a hydrophobic fluorescent probe. Using the phosphate-buffered solution (PBS,pH=7.4), the different concentrations of polymer solutions from 1.55 μg/mL to 200 μg/mL were prepared and then mixed with 1 mL of pyrene solution 6×10−6mol/L in acetone while being stirred overnight to give the final concentration of pyrene (6×10−7mol/L).The fluorescence emission spectra of the solutions and pure pyrene solution in the PBS were obtained at a fixed emission wavelength (λem) of 390 nm. Based on the survey done on these spectrum fluorescence intensities of the samples at λex=335nm and 338 nm as determined using a fluorescence spectrophotometer, FP-6000.The changes in the ratio of fluorescence intensityλex=338nm to 335 nm (I335/I337) of pyrene were plotted against the log concentration of the In-g-St polymer for finding the CMC.


## 2.3. Loading of Betamethasone onto Polymeric Micelles and Drug Loading Efficiency

A dialysis method was used for the preparation of betamethasone-loaded micelles (10% and 20%). Briefly, 20 and 40 mg of betamethasone were added to 160 and 180 mg of (In-g-St), respectively, and the mixture was dissolved in 5 mL dimethyl sulfoxide (DMSO) and stirred for 1 hour at room temperature. To remove the unloaded drug and DMSO, the mixture was poured into a dialysis tube (Molecular cut off 2000 Da) and dialyzed against 1 L water for 1 hour; then, the dialysis solution was exchanged with the same amount of freshwater and the press was continued up to 24 hours. Thereafter, by freeze-drying, the lyophilized powder was obtained. In order to determine the percentage of betamethasone encapsulated in nanoparticles, a high-performance liquid chromatography (HPLC) analysis method was used. Briefly, 4 mg of each drug-loaded polymer (10% and 20%) dissolved in 10 mL DMSO; then, 1 mL of this solution was mixed with acetonitrile to make 10 mL volume of the final solution. After that, betamethasone concentration was determined by HPLC with ultraviolet detection at 240 nm using a Shimadzu apparatus (Shimadzu Corp., Model LC-20AD XR, Japan) equipped with an autosampler. Betamethasone loading efficiency (%) and loading content (%) of the prepared formulation were calculated as follows:(1)EncapsulationefficiencyEE%=MassofbetamethasonewithinthenanoparticleMassofbetamethasoneinitiallyused×100,DrugloadingDL%=MassofbetamethasonewithinthenanoparticleMassofnanoparticle×100.


## 2.4. Particle Size Distribution Measurements

Particle size, surface charge, and particle size distribution of betamethasone-loaded In-g-St nanoparticles were determined using a nanosizer apparatus (Nano-ZS; Malvern Instruments, United Kingdom).One mL of betamethasone-loaded micelle was diluted in deionized water, and the micelle size was determined by Zetasizer Nano ZS instrument at a wavelength of 633 nm at 25°C with a detection angle of 90°.


## 2.5. Characterization of Particle Morphology

Transmission electron microscopy (TEM) and scanning electron microscopy (SEM) techniques are used to evaluate the morphology of nanoparticles [30–33]. In this study, we used the SEM technique. SEM assay is performed at the central laboratory of Shahid Chamran University of Ahvaz by using a scanning electron microscope apparatus (Model 1455 VP manufactured by DME).


## 2.6. In Vitro Drug Release Evaluation

The evaluation of betamethasone release profile from micelle formulation was performed by the dialysis method. In brief, 25 mg of betamethasone-loaded micelle powder was dispersed in 2 mL of phosphate-buffered saline (pH 7.4), then added into the dialysis tubes (cut off 12000 Da). The tube was placed in a 100 mL bottle of phosphate-buffered saline (pH 7.4). Then, the capped bottles were incubated at 150 RPM spinning in 37°C shaker incubator. The samples were withdrawn at 1, 3, 6, 12, and 24 hours; then, the concentration of the drug in the samples was evaluated by the HPLC method.


## 3. Results and Discussion

### 3.1. Characterization of the Synthesized Polymer (In-g-St)

#### 3.1.1. FT-IR Study

The FT-IR spectra of inulin (a) and inulin-grafted stearate (b) are presented in Figure1. The strong and broad-band peak between 3000 and 3600 cm-1 was assigned to O–H stretching vibrations. Two peaks which appeared in 2919 and 2850 cm-1 indicate the stretching vibrations of aliphatic C–H of the stearate group. Compared to the inulin spectrum, a new weak band in 1737 cm-1 (highlighted as a green curve) was assigned to the carbonyl group of an ester, which confirmed the grafting of the stearate group to the inulin via an esterification reaction. While only a few monomers of the polysaccharide are substituted with stearate groups, the esoteric peak is seen as a shoulder. This phenomenon has been observed in previous studies that have been conducted at the chemical modification of polysaccharides [29, 34–36].Figure 1
The FT-IR spectrum of inulin (a) and inulin-grafted stearate (b).


#### 3.1.2.1H-NMR Study

Another confirmation of the grafting reaction is the1H-NMR spectrum of the In-g-St (Figure 2). The absorption peak at δ=0.850ppm was assigned to the terminal methyl group of the stearate. Methylene groups of the St appeared in δ=1.230 and 1.495 ppm. The region of the stearate peaks in our polymer is consistent with the reported paper [36]. The peaks appear in regions 3.495, 3.797, 4.058, 4.629, 4.737, and 5.176 related to the inulin backbone [37].Figure 2
1H-NMR spectrum of the In-g-St in DMSO-d6.


#### 3.1.3. Degree of Substitution

Degree of substitution of In-g-St was achieved in the manner reported by Mandracchia et al. [26]. It was calculated as the ratio between the integral of the peak at 0.85 ppm belonging to the terminal methyl group of the stearate and the integral of the peak at 5.176 ppm belonging to the anomeric proton of fructose unit of inulin [37]. The degree of substitution is 16.1%.


### 3.2. Characterization of Betamethasone-Loaded Polymeric Micelles

#### 3.2.1. Scanning Electron Microscopy (SEM)

Polymeric micelles comprise a hydrophobic core enclosed by a hydrophilic shell, and they are generally synthesized from an amphiphilic copolymer with self-assembling properties in water. This structure causes reducing systemic side-effects and improving therapeutic efficiency, especially for poorly soluble drugs such as betamethasone [20].The morphology of the micelles is determined by SEM. SEM micrograph of micelles containing betamethasone-loaded In-g-St shows the round homogenously dispersed particles with a regular spherical shape (Figure3) which is an important factor for articular delivery [38]. Regarding the homogenous spherical shape of In-g-St particles, in a study by Mandracchia et al. [26], SEM pictures also represented homogenously dispersed round particles of inulin-based micelle loaded with hydrophobic drugs.Figure 3
SEM micrograph of betamethasone-loaded polymeric micelle.


#### 3.2.2. Zeta Potential

Zeta potential is commonly used to determine the surface charge of NPs and is an important factor that directly affects the stability of NPs [39]. Zeta potential for betamethasone-loaded In-g-St was measured which showed the surface charge of −13.4 mV. This negative charge is due to the presence of stearate moieties in inulin structure which is present on the surface of the NPs [40]. Though the surface charge is negative to some extent, betamethasone-loaded In-g-St NPs have enough repulsive force to prevent aggregation during long-term storage [41, 42]. In accordance with our results, Kim et al. have shown negative results for zeta potential of phthalyl inulin NPs ranged from −21.29 to −27.91 mV [43]. The very small size and the negative surface charges allow this system to pass through the cell membranes.


#### 3.2.3. Encapsulation Efficiency (EE) and Drug Loading (DL) Capacity

The high encapsulation efficiency is owing to high affinity of drug and the modified polymer in the same media (organic or aqueous phase) [44]. Encapsulation efficiency and drug loading of the betamethasone-loaded In-g-St NPs were found to be 63.38% and 6.36% for 10% polymer and 92.54% and 18.50%, for 20% polymer, respectively (Table 1).Table 1
Physical characteristics of In-g-St polymeric micelles.
FormulationSize (nm)DL% (w/w)EE% (w/w)Zeta potential (mv)10% formula127.1±5.66.36%±0.0263.6%±0.22-12.7±0.920% formula57.5±2.618.50%±0.5894.89%±2.91-13.4±4.2The In-g-St nanoparticles in comparison with dextran stearate polymeric micelles show that the inulin-derived particle was significantly smaller, which could be due to the lack of branching in the In-g-St polymer. In addition, it is much easier and less costly to produce low molecular weight of inulin than other polysaccharides [34, 35].


#### 3.2.4. CMC of In-g-St Polymer

CMC is defined as the minimum polymer concentration required for the micelle formation; therefore, it is an important parameter for the characterization of micelle stability. The lower CMC values cause the more thermodynamic stability of the polymeric micelles [45].The CMC of the In-g-St was evaluated via a shift of the intensity ratio of the pyrene fluorescence bands due to the passage of the hydrophobic pyrene from a hydrophilic to a hydrophobic environment. The ratio of fluorescence intensity of the third energy inλex=338nm (I338) which is higher in the molecule placed in the hydrophobic microenvironment and λex=335nm which is higher in the polar environment can be used as the index of the polarity of its microenvironment (Figure 4).Figure 4
Fluorescence emission spectra of pyrene in the presence of decreasing concentrations of In-g-St at pH 7.4.The CMC was determined from the intersection of the straight line and the horizontal lines at the low and high concentration ranges, respectively, which was 6.2μg/mL (Figure 5). Therefore, In-g-St copolymers can form a more thermodynamically stable micelle under high-dilution conditions.Figure 5
Plot for calculation of CMC of In-g-St using pyrene as the fluorescent probe.


#### 3.2.5. In Vitro Drug Release

In order to determine the drug release behaviors of drug-loaded In-g-St polymer, release experiments were performed in phosphate buffered saline (PBS,pH=7.4) by HPLC analysis technique. The calibration curve and plot of % cumulative drug release are represented in Figures 6 and 7. As seen in Figure 7, 20% drug-loaded polymer showed a small burst release of betamethasone at the first 3 h of the experiment which was followed by sustain release in the next 24 h. The burst release is related to the more concentrations of drug molecules which were presented in the surfaces of the micelles. Furthermore, the formula with 10% drug exhibited good sustained release properties except for the minor initial burst release. The sustained release of betamethasone from In-g-St micelle is the result of interaction between these hydrophobic drug molecules and the lipophilic core of the micelles that acts as a reservoir of the drug which released drug molecules slowly. In the literature, similar inulin-based drug delivery systems show similar release behaviors. For example, Mandracchia et al. have shown the sustained and sensitive release of celecoxib from inulin-d-alpha-tocopherol succinate (INVITE) nanomicelles [46].Figure 6
Calibration curve of betamethasone.Figure 7
In vitro betamethasone release from betamethasone-loaded In-g-St micelles for two formulations.


## 3.1. Characterization of the Synthesized Polymer (In-g-St)

### 3.1.1. FT-IR Study

The FT-IR spectra of inulin (a) and inulin-grafted stearate (b) are presented in Figure1. The strong and broad-band peak between 3000 and 3600 cm-1 was assigned to O–H stretching vibrations. Two peaks which appeared in 2919 and 2850 cm-1 indicate the stretching vibrations of aliphatic C–H of the stearate group. Compared to the inulin spectrum, a new weak band in 1737 cm-1 (highlighted as a green curve) was assigned to the carbonyl group of an ester, which confirmed the grafting of the stearate group to the inulin via an esterification reaction. While only a few monomers of the polysaccharide are substituted with stearate groups, the esoteric peak is seen as a shoulder. This phenomenon has been observed in previous studies that have been conducted at the chemical modification of polysaccharides [29, 34–36].Figure 1
The FT-IR spectrum of inulin (a) and inulin-grafted stearate (b).


### 3.1.2.1H-NMR Study

Another confirmation of the grafting reaction is the1H-NMR spectrum of the In-g-St (Figure 2). The absorption peak at δ=0.850ppm was assigned to the terminal methyl group of the stearate. Methylene groups of the St appeared in δ=1.230 and 1.495 ppm. The region of the stearate peaks in our polymer is consistent with the reported paper [36]. The peaks appear in regions 3.495, 3.797, 4.058, 4.629, 4.737, and 5.176 related to the inulin backbone [37].Figure 2
1H-NMR spectrum of the In-g-St in DMSO-d6.


### 3.1.3. Degree of Substitution

Degree of substitution of In-g-St was achieved in the manner reported by Mandracchia et al. [26]. It was calculated as the ratio between the integral of the peak at 0.85 ppm belonging to the terminal methyl group of the stearate and the integral of the peak at 5.176 ppm belonging to the anomeric proton of fructose unit of inulin [37]. The degree of substitution is 16.1%.


## 3.1.1. FT-IR Study

The FT-IR spectra of inulin (a) and inulin-grafted stearate (b) are presented in Figure1. The strong and broad-band peak between 3000 and 3600 cm-1 was assigned to O–H stretching vibrations. Two peaks which appeared in 2919 and 2850 cm-1 indicate the stretching vibrations of aliphatic C–H of the stearate group. Compared to the inulin spectrum, a new weak band in 1737 cm-1 (highlighted as a green curve) was assigned to the carbonyl group of an ester, which confirmed the grafting of the stearate group to the inulin via an esterification reaction. While only a few monomers of the polysaccharide are substituted with stearate groups, the esoteric peak is seen as a shoulder. This phenomenon has been observed in previous studies that have been conducted at the chemical modification of polysaccharides [29, 34–36].Figure 1
The FT-IR spectrum of inulin (a) and inulin-grafted stearate (b).


## 3.1.2.1H-NMR Study

Another confirmation of the grafting reaction is the1H-NMR spectrum of the In-g-St (Figure 2). The absorption peak at δ=0.850ppm was assigned to the terminal methyl group of the stearate. Methylene groups of the St appeared in δ=1.230 and 1.495 ppm. The region of the stearate peaks in our polymer is consistent with the reported paper [36]. The peaks appear in regions 3.495, 3.797, 4.058, 4.629, 4.737, and 5.176 related to the inulin backbone [37].Figure 2
1H-NMR spectrum of the In-g-St in DMSO-d6.


## 3.1.3. Degree of Substitution

Degree of substitution of In-g-St was achieved in the manner reported by Mandracchia et al. [26]. It was calculated as the ratio between the integral of the peak at 0.85 ppm belonging to the terminal methyl group of the stearate and the integral of the peak at 5.176 ppm belonging to the anomeric proton of fructose unit of inulin [37]. The degree of substitution is 16.1%.


## 3.2. Characterization of Betamethasone-Loaded Polymeric Micelles

### 3.2.1. Scanning Electron Microscopy (SEM)

Polymeric micelles comprise a hydrophobic core enclosed by a hydrophilic shell, and they are generally synthesized from an amphiphilic copolymer with self-assembling properties in water. This structure causes reducing systemic side-effects and improving therapeutic efficiency, especially for poorly soluble drugs such as betamethasone [20].The morphology of the micelles is determined by SEM. SEM micrograph of micelles containing betamethasone-loaded In-g-St shows the round homogenously dispersed particles with a regular spherical shape (Figure3) which is an important factor for articular delivery [38]. Regarding the homogenous spherical shape of In-g-St particles, in a study by Mandracchia et al. [26], SEM pictures also represented homogenously dispersed round particles of inulin-based micelle loaded with hydrophobic drugs.Figure 3
SEM micrograph of betamethasone-loaded polymeric micelle.


### 3.2.2. Zeta Potential

Zeta potential is commonly used to determine the surface charge of NPs and is an important factor that directly affects the stability of NPs [39]. Zeta potential for betamethasone-loaded In-g-St was measured which showed the surface charge of −13.4 mV. This negative charge is due to the presence of stearate moieties in inulin structure which is present on the surface of the NPs [40]. Though the surface charge is negative to some extent, betamethasone-loaded In-g-St NPs have enough repulsive force to prevent aggregation during long-term storage [41, 42]. In accordance with our results, Kim et al. have shown negative results for zeta potential of phthalyl inulin NPs ranged from −21.29 to −27.91 mV [43]. The very small size and the negative surface charges allow this system to pass through the cell membranes.


### 3.2.3. Encapsulation Efficiency (EE) and Drug Loading (DL) Capacity

The high encapsulation efficiency is owing to high affinity of drug and the modified polymer in the same media (organic or aqueous phase) [44]. Encapsulation efficiency and drug loading of the betamethasone-loaded In-g-St NPs were found to be 63.38% and 6.36% for 10% polymer and 92.54% and 18.50%, for 20% polymer, respectively (Table 1).Table 1
Physical characteristics of In-g-St polymeric micelles.
FormulationSize (nm)DL% (w/w)EE% (w/w)Zeta potential (mv)10% formula127.1±5.66.36%±0.0263.6%±0.22-12.7±0.920% formula57.5±2.618.50%±0.5894.89%±2.91-13.4±4.2The In-g-St nanoparticles in comparison with dextran stearate polymeric micelles show that the inulin-derived particle was significantly smaller, which could be due to the lack of branching in the In-g-St polymer. In addition, it is much easier and less costly to produce low molecular weight of inulin than other polysaccharides [34, 35].


### 3.2.4. CMC of In-g-St Polymer

CMC is defined as the minimum polymer concentration required for the micelle formation; therefore, it is an important parameter for the characterization of micelle stability. The lower CMC values cause the more thermodynamic stability of the polymeric micelles [45].The CMC of the In-g-St was evaluated via a shift of the intensity ratio of the pyrene fluorescence bands due to the passage of the hydrophobic pyrene from a hydrophilic to a hydrophobic environment. The ratio of fluorescence intensity of the third energy inλex=338nm (I338) which is higher in the molecule placed in the hydrophobic microenvironment and λex=335nm which is higher in the polar environment can be used as the index of the polarity of its microenvironment (Figure 4).Figure 4
Fluorescence emission spectra of pyrene in the presence of decreasing concentrations of In-g-St at pH 7.4.The CMC was determined from the intersection of the straight line and the horizontal lines at the low and high concentration ranges, respectively, which was 6.2μg/mL (Figure 5). Therefore, In-g-St copolymers can form a more thermodynamically stable micelle under high-dilution conditions.Figure 5
Plot for calculation of CMC of In-g-St using pyrene as the fluorescent probe.


### 3.2.5. In Vitro Drug Release

In order to determine the drug release behaviors of drug-loaded In-g-St polymer, release experiments were performed in phosphate buffered saline (PBS,pH=7.4) by HPLC analysis technique. The calibration curve and plot of % cumulative drug release are represented in Figures 6 and 7. As seen in Figure 7, 20% drug-loaded polymer showed a small burst release of betamethasone at the first 3 h of the experiment which was followed by sustain release in the next 24 h. The burst release is related to the more concentrations of drug molecules which were presented in the surfaces of the micelles. Furthermore, the formula with 10% drug exhibited good sustained release properties except for the minor initial burst release. The sustained release of betamethasone from In-g-St micelle is the result of interaction between these hydrophobic drug molecules and the lipophilic core of the micelles that acts as a reservoir of the drug which released drug molecules slowly. In the literature, similar inulin-based drug delivery systems show similar release behaviors. For example, Mandracchia et al. have shown the sustained and sensitive release of celecoxib from inulin-d-alpha-tocopherol succinate (INVITE) nanomicelles [46].Figure 6
Calibration curve of betamethasone.Figure 7
In vitro betamethasone release from betamethasone-loaded In-g-St micelles for two formulations.


## 3.2.1. Scanning Electron Microscopy (SEM)

Polymeric micelles comprise a hydrophobic core enclosed by a hydrophilic shell, and they are generally synthesized from an amphiphilic copolymer with self-assembling properties in water. This structure causes reducing systemic side-effects and improving therapeutic efficiency, especially for poorly soluble drugs such as betamethasone [20].The morphology of the micelles is determined by SEM. SEM micrograph of micelles containing betamethasone-loaded In-g-St shows the round homogenously dispersed particles with a regular spherical shape (Figure3) which is an important factor for articular delivery [38]. Regarding the homogenous spherical shape of In-g-St particles, in a study by Mandracchia et al. [26], SEM pictures also represented homogenously dispersed round particles of inulin-based micelle loaded with hydrophobic drugs.Figure 3
SEM micrograph of betamethasone-loaded polymeric micelle.


## 3.2.2. Zeta Potential

Zeta potential is commonly used to determine the surface charge of NPs and is an important factor that directly affects the stability of NPs [39]. Zeta potential for betamethasone-loaded In-g-St was measured which showed the surface charge of −13.4 mV. This negative charge is due to the presence of stearate moieties in inulin structure which is present on the surface of the NPs [40]. Though the surface charge is negative to some extent, betamethasone-loaded In-g-St NPs have enough repulsive force to prevent aggregation during long-term storage [41, 42]. In accordance with our results, Kim et al. have shown negative results for zeta potential of phthalyl inulin NPs ranged from −21.29 to −27.91 mV [43]. The very small size and the negative surface charges allow this system to pass through the cell membranes.


## 3.2.3. Encapsulation Efficiency (EE) and Drug Loading (DL) Capacity

The high encapsulation efficiency is owing to high affinity of drug and the modified polymer in the same media (organic or aqueous phase) [44]. Encapsulation efficiency and drug loading of the betamethasone-loaded In-g-St NPs were found to be 63.38% and 6.36% for 10% polymer and 92.54% and 18.50%, for 20% polymer, respectively (Table 1).Table 1
Physical characteristics of In-g-St polymeric micelles.
FormulationSize (nm)DL% (w/w)EE% (w/w)Zeta potential (mv)10% formula127.1±5.66.36%±0.0263.6%±0.22-12.7±0.920% formula57.5±2.618.50%±0.5894.89%±2.91-13.4±4.2The In-g-St nanoparticles in comparison with dextran stearate polymeric micelles show that the inulin-derived particle was significantly smaller, which could be due to the lack of branching in the In-g-St polymer. In addition, it is much easier and less costly to produce low molecular weight of inulin than other polysaccharides [34, 35].


## 3.2.4. CMC of In-g-St Polymer

CMC is defined as the minimum polymer concentration required for the micelle formation; therefore, it is an important parameter for the characterization of micelle stability. The lower CMC values cause the more thermodynamic stability of the polymeric micelles [45].The CMC of the In-g-St was evaluated via a shift of the intensity ratio of the pyrene fluorescence bands due to the passage of the hydrophobic pyrene from a hydrophilic to a hydrophobic environment. The ratio of fluorescence intensity of the third energy inλex=338nm (I338) which is higher in the molecule placed in the hydrophobic microenvironment and λex=335nm which is higher in the polar environment can be used as the index of the polarity of its microenvironment (Figure 4).Figure 4
Fluorescence emission spectra of pyrene in the presence of decreasing concentrations of In-g-St at pH 7.4.The CMC was determined from the intersection of the straight line and the horizontal lines at the low and high concentration ranges, respectively, which was 6.2μg/mL (Figure 5). Therefore, In-g-St copolymers can form a more thermodynamically stable micelle under high-dilution conditions.Figure 5
Plot for calculation of CMC of In-g-St using pyrene as the fluorescent probe.


## 3.2.5. In Vitro Drug Release

In order to determine the drug release behaviors of drug-loaded In-g-St polymer, release experiments were performed in phosphate buffered saline (PBS,pH=7.4) by HPLC analysis technique. The calibration curve and plot of % cumulative drug release are represented in Figures 6 and 7. As seen in Figure 7, 20% drug-loaded polymer showed a small burst release of betamethasone at the first 3 h of the experiment which was followed by sustain release in the next 24 h. The burst release is related to the more concentrations of drug molecules which were presented in the surfaces of the micelles. Furthermore, the formula with 10% drug exhibited good sustained release properties except for the minor initial burst release. The sustained release of betamethasone from In-g-St micelle is the result of interaction between these hydrophobic drug molecules and the lipophilic core of the micelles that acts as a reservoir of the drug which released drug molecules slowly. In the literature, similar inulin-based drug delivery systems show similar release behaviors. For example, Mandracchia et al. have shown the sustained and sensitive release of celecoxib from inulin-d-alpha-tocopherol succinate (INVITE) nanomicelles [46].Figure 6
Calibration curve of betamethasone.Figure 7
In vitro betamethasone release from betamethasone-loaded In-g-St micelles for two formulations.


## 4. Conclusion

In this study, we synthesized a novel derivative of inulin via the reaction of stearoyl chloride and inulin. FT-IR and H-NMR spectra confirmed the formation of the modified polysaccharide. Drug loading studies, particle size analysis, and the images of the electron microscope showed that betamethasone was efficiently loaded onto the modified polysaccharide and the micelles were formed successfully. The modified polymer low CMC level indicated that the micelles have acceptable stability. In-g-St polymeric micelles could be the suitable candidates to the controlled release of the lipophilic drugs such as betamethasone. In-g-St has two major advantages over dextran-g-St: first, it is cheaper, and second, it forms smaller micelles.



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*Source: 6579538-2020-05-26.xml*