# Screening of Most Effective Variables for Development of Gastroretentive Mucoadhesive Nanoparticles by Taguchi Design

Authors: Ankit Anand Kharia; Akhlesh Kumar Singhai
Journal: ISRN Nanomaterials
 (2013)

---

## Abstract

The objective of this study was the selection of the most influential variable for the preparation of gastroretentive mucoadhesive nanoparticles of acyclovir. Nanoparticles were prepared by one-step desolvation method; effect of formulation and processing variables on various response variables were studied by a Taguchi standard orthogonal array L8 design. Independent variables studied were the amount of gelatin, amount of glutaraldehyde, amount of Pluronic F-68, acetone addition rate, pH, stirring time, and stirring speed. The dependent variables studied were the particle size, polydispersity index, amount of drug released in 6 h, time required to release 60% of drug, entrapment efficiency, loading efficiency, and mucoadhesiveness. The size of all nanoparticulate formulations prepared as per the experimental design (Taguchi screening design) varied between 165 and 1610 nm, PDI between 0.360 and 1.00, bioadhesiveness between 3.959 and 11.02 g, cumulative percent drug release in 24 h between 40.74 and 72.48, entrapment efficiency between 15.70 and 83.12, and loading efficiency between 39.72 and 80.49. Pareto ranking analyses showed that the two most important factors affecting the selected responses were amount of gelatin and amount of Pluronic F-68 (P<0.05).


---

## Body

## 1. Introduction

Acyclovir is a cyclic analogue of the natural nucleoside 2-deoxyguanosine, clinically used in the treatment ofHerpes simplex, Varicella zoster, Cytomegalovirus, and Epstein barr virus infections [1]. It is currently marketed as capsules (200 mg), tablets (200, 400 and 800 mg), and suspension for oral administration, topical ointment, and intravenous injection. Oral acyclovir is mostly used as 200 mg tablets, five times a day [2]. Absorption of orally administered acyclovir is slow, variable, and incomplete, with a bioavailability of 15%–30% and the elimination half-life of acyclovir is approximately 3 h [3]. It has narrow absorption window and is primarily absorbed from stomach and upper part of the small intestine [4–6]. Reduced bioavailability of acyclovir may be because of transportation of dosage form from the region of absorption window to site where it is less absorbed. Therefore there was a need to increase the gastroretention time of dosage form so that drug would be available at the site of absorption and results in improved bioavailability.Several attempts are being made to increase the gastric retention of drugs, like intragastric floating systems, hydrodynamically balanced systems, extendable or expandable, microporous compartment system, microballoons, bio/mucoadhesive systems, high-density systems, and superporous biodegradable hydro gel systems [7]. After oral administration, such a dosage form would be retained in the stomach for several hours and would release the drug there in a controlled and prolonged manner, so that the drug could be supplied continuously to its absorption sites in the upper gastrointestinal tract [8]. Prolonged gastric retention improves bioavailability, reduces drug waste, and improves solubility of drugs that are less soluble in a high pH environment. It is also suitable for local drug delivery to the stomach and proximal small intestine [9]. Gastroretention helps to provide better availability of new products with suitable therapeutic activity and substantial benefits for patients.The traditional approach of optimizing a formulation or process involves studying the influence of one variable at time (OVAT), while keeping others as constant. Using this OVAT approach, the solution of a specific problematic property can be achieved somehow, but attainment of the true optimum composition or process is never assured [10]. This may be due to presence of interactions, that is, the influence of one or more factors on others. The ultimate product may be satisfactory but mostly suboptimal, as a better formulation might still exist for the studied conditions. The conventional OVAT approach of drug formulation development suffers from several pitfalls, like being strenuous, uneconomical, and inept to reveal interactions. Further, the OVAT methodology results only in “just satisfactory” solutions, as a detailed study of all variables is not possible. As one cannot establish “cause-and-effect” relationships using OVAT, it becomes ineffective when all variables are changed simultaneously. Recently, the systematic optimization approaches are being widely practiced to alleviate such inconsistencies. This holistic approach encompassing the application of appropriate experimental designs coupled with the generation of mathematical equations and graphic outcomes and depicting a complete picture of variation of the response(s) as a function of the factor(s) is termed as design of experiments (DoE). DoE techniques are thus far more beneficial, as they overcome most shortcomings inherent to the traditional OVAT approach [11, 12].Further, the screening techniques employed as a part of DoE help in finding the “important” and “unimportant” input variables. One can simulate the product or process behavior using model equation(s) and thus save a significant amount of resources, namely, time, effort, materials, and cost. The remarkable feature of DoE is that it can predict the performance of formulations even without preparing them and detect and estimate the possible interactions and synergies among variables. Recently, DoE optimization techniques are becoming a regular practice globally, not only in the design and development of an assortment of new dosage forms but also for modifying the existing ones. Whether it is a drug industry, institutional drug delivery resource, or federal compliance with USFDA, ICH, NIH, or ISO, DoE is being frequently sought after in drug discovery and development. The faster emerging area of quality by design (QbD) also requires the implementation of DoE precepts during different stages of product/process transformation. By and large, low-resolution designs like FDs (full or fractional), Plackett Burman design, or Taguchi designs are enough for the purpose of simpler screening of a large number of experimental parameters [10].Taguchi methods or an orthogonal array have been widely used to optimize the reaction variables by formulating a minimum number of experiments. This approach helps to identify the influence of individual factors and establish the relationship between variables and operational conditions [13]. It is a method of designing experiments that usually requires only a fraction of the full factorial combinations. An orthogonal array means the design is balanced so that factor levels are weighted equally. Because of this, each factor can be evaluated independently of all the other factors, so the effect of one factor does not influence the estimation of another factor.The aim of the present study was to screen most influential factors which effect formulation of mucoadhesive gastroretentive nanoparticles of acyclovir by Taguchi approach. Gelatin was selected as a mucoadhesive polymer to prepare gastroretentive nanoparticles as they strengthen the contact between dosage form and the site of absorption, thereby reducing the luminal diffusion pathway of the drug and lead to significant improvements in oral drug delivery [14, 15]. These mucoadhesive polymeric nanoparticles in the stomach will offer diverse advantages such as (a) longer residence time of the dosage form on gastric mucosa which will improve absorption of the drug and increase the bioavailability, (b) higher drug concentration at the site of adhesion absorption, which will create a driving force for the paracellular passive uptake, and (c) immediate absorption from the bioadhesive drug delivery system without previous dilution and probable degradation in the luminal fluids [16].


## 2. Materials and Methods

### 2.1. Materials

Acyclovir was obtained as a gift sample from M/s Modern Laboratories Pvt., Ltd., Indore, India. Dialysis tubing (cut-off 12 kDa) was purchased from Sigma (USA). Gelatin (type B) and Pluronic F-68 were purchased from HiMedia Laboratories Pvt., Ltd., Mumbai, India. All other ingredients used throughout the study were of analytical grade and were used as received.


### 2.2. Preparation of Nanoparticles

Gelatin nanoparticles were prepared by desolvation method as previously described [17] with slight modification. Briefly gelatin was dissolved in 25 mL of distilled water at 37°C under magnetic stirring (400 rpm) until a clear solution was obtained; 200 mg acyclovir was dispersed in 50 mL of distilled water. Drug dispersion was then added to the polymeric solution followed by addition of Pluronic F-68 as a stabilizer under continuous stirring by using magnetic stirrer and the pH of solution was adjusted (by 1 mol/L HCl or NaOH). Then 50 mL of acetone was added at specified addition rate, after 10 min of acetone addition glutaraldehyde was added to the reaction vessel to cross-link the nanoparticles. Finally after stirring for 6 h, the particles were purified by threefold centrifugation (16000 g for 20 min at 4°C) and redispersion in 10 mL mixture of acetone: water (3 : 7 v/v). The supernatant was removed and the pellets were resuspended in distilled water, and finally, the nanoparticles were freeze-dried using 5% glucose solution as a cryoprotector and powder was stored in vials.


### 2.3. Evaluation of Formulations

#### 2.3.1. Particle Size and Particle Size Distribution

Average particle size and polydispersity index (PDI) which is a range of measurement of the particle sizes within measured samples were determined using the zeta sizer (Zetasizer-ZEN 2600 Malvern Instrument, Ltd., Worchestershire, UK) equipped with the Malvern PCS software. For analysis nanosuspensions were diluted five times with filtered (0.45μ) bidistilled water [18].


#### 2.3.2. Entrapment Efficiency

For determination of drug entrapment, the amount of drug present in the clear supernatant after centrifugation was determined (w) by UV spectrophotometer at 254 nm (UV-1700 Spectrophotometer, Shimadzu Scientific Instruments, Inc., Maryland, USA). A standard calibration curve of drug was plotted for this purpose. The amount of drug in supernatant was then subtracted from the total amount of drug added during the preparation (W). Effectively, (W-w) will give the amount of drug entrapped in the particles [19].Then percentage entrapment of a drug is obtained by using the following equation:(1)%DrugEntrapment=(W-w)×100W.


#### 2.3.3. Drug Loading

The acyclovir content in the nanoparticles was determined by pulverizing the acyclovir loaded nanoparticles (10 mg) followed by immersing them in 100 mL simulated gastric fluid (SGF, pH 1.2, without enzymes) with agitating at room temperature for 12 h. After filtration through a 0.45μ membrane filter (Millipore), the drug concentration was determined spectrophotometrically at the wavelength of 254 nm. The filtered solution from the empty nanoparticles (without acyclovir) was taken as blank. All samples were analyzed in triplicate and the drug loading (DL) was calculated according to the following equation [20]:
(2)DL(%)=WDWT×100,
where DL is the drug loading; WD is the weight of the drug loaded in the nanoparticles; WT is the total weight of the nanoparticles.


#### 2.3.4. Drug Release Study

The in vitro drug release studies were performed by dialysis membrane diffusion technique using glass tube of 10 cm length open at its both ends having 2.5 cm diameter. The dialysis membrane of 12,000 Mwco (Spectra por, Sigma, USA) was used for release study because it retains nanoparticles and allows free drug to diffuse in the release media. The lower end of the glass tube was covered with the pretreated membrane to keep the nanoparticulate formulation on the donor side. The nanoparticles (equivalent to 10 mg of acyclovir) were placed in donor compartment by dispersing in 3 mL of SGF (pH 1.2) where the drug was allowed to freely diffuse over the receptor compartment containing 100 mL of SGF (pH 1.2). The entire system was kept at37±0.5°C with continuous magnetic stirring at 100 rpm. Samples of 5 mL were withdrawn at predetermined time intervals (0.5, 1, 2, 3, 4, 5, 6, 12, and 24 h) and replaced with fresh SGF [18, 21]. The withdrawn samples were suitably diluted to carry out UV Spectrophotometric analysis at 254 nm.


#### 2.3.5. Measurement of Mucoadhesive Strength

The method is based on the measurement of shear stress required to break the adhesive bond between a mucosal membrane and the formulation. The formulation is sandwiched between two mucosal membranes fixed on flexible supports in the assemblies for a sufficient period of time. After the adhesive bond has formed, the force (weight) required to separate the bond was recorded as mucoadhesive strength.Mucoadhesive properties of acyclovir nanoparticles were evaluated by Texture analyzer (M/s TA. XT. Plus, Stable Microsystem, UK) using porcine gastric mucosa. Stomach of pig was obtained immediately after slaughter at local slaughterhouse. The stomach was washed with fresh water to remove nondigested food from stomach, then placed in SGF at 4°C (used within 6 h). The membrane was then attached both on the base of texture analyzer and to the stainless steel probe (using two-side adhesive tape); probe is then fixed to the mobile arm of the texture analyzer. The 10 mg of nanoparticulate formulation was placed on the membrane placed on lower surface moistened with 1 mL of SGF. The mobile arm (with attached membrane) was lowered at a rate of 0.5 mm s−1 until contact with the formulation was made. A contact force of 10 g was maintained for 500 s, after which the probe was withdrawn from the membrane. After the adhesive bond has formed, the force of detachment (g) required to separate the bond was recorded as mucoadhesive strength [22]. This parameter was used to compare mucoadhesive property of various formulations.


### 2.4. Screening of Influential Variables

A number of formulation and processing variables influence the overall performance of nanoparticles. Thus it becomes extremely difficult to study the effect of each variable and interaction among them through the conventional approach. In current studies, screening of various process and formulation variables, potentially influencing nanoparticulate formulation development, was performed employing Taguchi design for seven factors at two levels each as given in Table1. The number of experiments during screening was kept as small as possible, to limit the volume of work carried out during initial stages. This was conducted to identify the potential factors for further systematic DoE optimization studies, as the nature of influence of such variables is not widely known from prior literature reports.Table 1
List of variables employed in Taguchi L8 orthogonal array experiment.
Factors
Levels
Low (−1)
High (+1)
Amount of gelatin (mg)
200
1000
Amount of glutaraldehyde (mL)
0.1
0.5
Amount of pluronic F-68 (mg)
50
250
Acetone addition rate (mL/min)
1
5
pH
2
4
Stirring time (h)
1
5
Stirring speed (rpm)
200
1000A standard orthogonal array L8 was used to examine this system where L and subscript 8 denote the latin square and the number of the experimental runs, respectively. Design-Expert (Stat-Ease Inc., USA) was used as software for the DoE modeling. Table2 depicts the orthogonal array L8 for the seven factors at two levels by Taguchi design was adopted in the studies. Particle size, polydispersity index (PDI), amount of drug released in 6 h (Q6), time required to release 60% of drug (T60%), entrapment efficiency, loading efficiency, and mucoadhesiveness were the key response variables investigated thoroughly for selecting the significant formulation and response factors. A run involved the corresponding combination of levels to which the factors in the experiment were set as shown in Table 3. All experiments were done in triplicate. The effects of the proposed experiments on the responses were then analyzed by the Design Expert software to obtain independently the main effects of these factors, followed by the analysis of variance (ANOVA) to determine which factors were statistically significant. Series of Pareto charts were constructed to demonstrate the influence of each parameter on the responses (Figure 3). The most influential factor among the seven factors will be derived by selecting factors which are showing maximum standardized effect for most of the responses in Pareto charts.Table 2
L8 array layout as per 7 factors, 2 levels Taguchi screening design.
Formulation code
Amount of gelatin (mg)
Amount of Glutaraldehyde (mL)
Amount of Pluronic  F-68 (mg)
Acetone addition rate (mL/min)
pH
Stirring time (h)
Stirring speed (rpm)
F1
-
1
-
1
-
1
-
1
-
1
-
1
-
1
F2
-
1
+
1
-
1
+
1
+
1
+
1
-
1
F3
+
1
+
1
-
1
-
1
-
1
+
1
+
1
F4
+
1
-
1
-
1
+
1
+
1
-
1
+
1
F5
+
1
-
1
+
1
+
1
-
1
+
1
-
1
F6
+
1
+
1
+
1
-
1
+
1
-
1
-
1
F7
-
1
+
1
+
1
+
1
-
1
-
1
+
1
F8
-
1
-
1
+
1
-
1
+
1
+
1
+
1Table 3
Preparation of nanoparticles on the basis of Taguchi screening design.
Formulation
Amount of gelatin (mg)
Amount of Glutaraldehyde (mL)
Amount of Pluronic  F-68 (mg)
Acetone addition rate (mL/min)
pH
Stirring time (h)
Stirring speed (rpm)
F1
200
0.1
50
1
2.0
1
200
F2
200
0.5
50
5
4.0
5
200
F3
1000
0.5
50
1
2.0
5
1000
F4
1000
0.1
50
5
4.0
1
1000
F5
1000
0.1
250
5
2.0
5
200
F6
1000
0.5
250
1
4.0
1
200
F7
200
0.5
250
5
2.0
1
1000
F8
200
0.1
250
1
4.0
5
1000
Drug amount was kept constant at 200 mg.


## 2.1. Materials

Acyclovir was obtained as a gift sample from M/s Modern Laboratories Pvt., Ltd., Indore, India. Dialysis tubing (cut-off 12 kDa) was purchased from Sigma (USA). Gelatin (type B) and Pluronic F-68 were purchased from HiMedia Laboratories Pvt., Ltd., Mumbai, India. All other ingredients used throughout the study were of analytical grade and were used as received.


## 2.2. Preparation of Nanoparticles

Gelatin nanoparticles were prepared by desolvation method as previously described [17] with slight modification. Briefly gelatin was dissolved in 25 mL of distilled water at 37°C under magnetic stirring (400 rpm) until a clear solution was obtained; 200 mg acyclovir was dispersed in 50 mL of distilled water. Drug dispersion was then added to the polymeric solution followed by addition of Pluronic F-68 as a stabilizer under continuous stirring by using magnetic stirrer and the pH of solution was adjusted (by 1 mol/L HCl or NaOH). Then 50 mL of acetone was added at specified addition rate, after 10 min of acetone addition glutaraldehyde was added to the reaction vessel to cross-link the nanoparticles. Finally after stirring for 6 h, the particles were purified by threefold centrifugation (16000 g for 20 min at 4°C) and redispersion in 10 mL mixture of acetone: water (3 : 7 v/v). The supernatant was removed and the pellets were resuspended in distilled water, and finally, the nanoparticles were freeze-dried using 5% glucose solution as a cryoprotector and powder was stored in vials.


## 2.3. Evaluation of Formulations

### 2.3.1. Particle Size and Particle Size Distribution

Average particle size and polydispersity index (PDI) which is a range of measurement of the particle sizes within measured samples were determined using the zeta sizer (Zetasizer-ZEN 2600 Malvern Instrument, Ltd., Worchestershire, UK) equipped with the Malvern PCS software. For analysis nanosuspensions were diluted five times with filtered (0.45μ) bidistilled water [18].


### 2.3.2. Entrapment Efficiency

For determination of drug entrapment, the amount of drug present in the clear supernatant after centrifugation was determined (w) by UV spectrophotometer at 254 nm (UV-1700 Spectrophotometer, Shimadzu Scientific Instruments, Inc., Maryland, USA). A standard calibration curve of drug was plotted for this purpose. The amount of drug in supernatant was then subtracted from the total amount of drug added during the preparation (W). Effectively, (W-w) will give the amount of drug entrapped in the particles [19].Then percentage entrapment of a drug is obtained by using the following equation:(1)%DrugEntrapment=(W-w)×100W.


### 2.3.3. Drug Loading

The acyclovir content in the nanoparticles was determined by pulverizing the acyclovir loaded nanoparticles (10 mg) followed by immersing them in 100 mL simulated gastric fluid (SGF, pH 1.2, without enzymes) with agitating at room temperature for 12 h. After filtration through a 0.45μ membrane filter (Millipore), the drug concentration was determined spectrophotometrically at the wavelength of 254 nm. The filtered solution from the empty nanoparticles (without acyclovir) was taken as blank. All samples were analyzed in triplicate and the drug loading (DL) was calculated according to the following equation [20]:
(2)DL(%)=WDWT×100,
where DL is the drug loading; WD is the weight of the drug loaded in the nanoparticles; WT is the total weight of the nanoparticles.


### 2.3.4. Drug Release Study

The in vitro drug release studies were performed by dialysis membrane diffusion technique using glass tube of 10 cm length open at its both ends having 2.5 cm diameter. The dialysis membrane of 12,000 Mwco (Spectra por, Sigma, USA) was used for release study because it retains nanoparticles and allows free drug to diffuse in the release media. The lower end of the glass tube was covered with the pretreated membrane to keep the nanoparticulate formulation on the donor side. The nanoparticles (equivalent to 10 mg of acyclovir) were placed in donor compartment by dispersing in 3 mL of SGF (pH 1.2) where the drug was allowed to freely diffuse over the receptor compartment containing 100 mL of SGF (pH 1.2). The entire system was kept at37±0.5°C with continuous magnetic stirring at 100 rpm. Samples of 5 mL were withdrawn at predetermined time intervals (0.5, 1, 2, 3, 4, 5, 6, 12, and 24 h) and replaced with fresh SGF [18, 21]. The withdrawn samples were suitably diluted to carry out UV Spectrophotometric analysis at 254 nm.


### 2.3.5. Measurement of Mucoadhesive Strength

The method is based on the measurement of shear stress required to break the adhesive bond between a mucosal membrane and the formulation. The formulation is sandwiched between two mucosal membranes fixed on flexible supports in the assemblies for a sufficient period of time. After the adhesive bond has formed, the force (weight) required to separate the bond was recorded as mucoadhesive strength.Mucoadhesive properties of acyclovir nanoparticles were evaluated by Texture analyzer (M/s TA. XT. Plus, Stable Microsystem, UK) using porcine gastric mucosa. Stomach of pig was obtained immediately after slaughter at local slaughterhouse. The stomach was washed with fresh water to remove nondigested food from stomach, then placed in SGF at 4°C (used within 6 h). The membrane was then attached both on the base of texture analyzer and to the stainless steel probe (using two-side adhesive tape); probe is then fixed to the mobile arm of the texture analyzer. The 10 mg of nanoparticulate formulation was placed on the membrane placed on lower surface moistened with 1 mL of SGF. The mobile arm (with attached membrane) was lowered at a rate of 0.5 mm s−1 until contact with the formulation was made. A contact force of 10 g was maintained for 500 s, after which the probe was withdrawn from the membrane. After the adhesive bond has formed, the force of detachment (g) required to separate the bond was recorded as mucoadhesive strength [22]. This parameter was used to compare mucoadhesive property of various formulations.


## 2.3.1. Particle Size and Particle Size Distribution

Average particle size and polydispersity index (PDI) which is a range of measurement of the particle sizes within measured samples were determined using the zeta sizer (Zetasizer-ZEN 2600 Malvern Instrument, Ltd., Worchestershire, UK) equipped with the Malvern PCS software. For analysis nanosuspensions were diluted five times with filtered (0.45μ) bidistilled water [18].


## 2.3.2. Entrapment Efficiency

For determination of drug entrapment, the amount of drug present in the clear supernatant after centrifugation was determined (w) by UV spectrophotometer at 254 nm (UV-1700 Spectrophotometer, Shimadzu Scientific Instruments, Inc., Maryland, USA). A standard calibration curve of drug was plotted for this purpose. The amount of drug in supernatant was then subtracted from the total amount of drug added during the preparation (W). Effectively, (W-w) will give the amount of drug entrapped in the particles [19].Then percentage entrapment of a drug is obtained by using the following equation:(1)%DrugEntrapment=(W-w)×100W.


## 2.3.3. Drug Loading

The acyclovir content in the nanoparticles was determined by pulverizing the acyclovir loaded nanoparticles (10 mg) followed by immersing them in 100 mL simulated gastric fluid (SGF, pH 1.2, without enzymes) with agitating at room temperature for 12 h. After filtration through a 0.45μ membrane filter (Millipore), the drug concentration was determined spectrophotometrically at the wavelength of 254 nm. The filtered solution from the empty nanoparticles (without acyclovir) was taken as blank. All samples were analyzed in triplicate and the drug loading (DL) was calculated according to the following equation [20]:
(2)DL(%)=WDWT×100,
where DL is the drug loading; WD is the weight of the drug loaded in the nanoparticles; WT is the total weight of the nanoparticles.


## 2.3.4. Drug Release Study

The in vitro drug release studies were performed by dialysis membrane diffusion technique using glass tube of 10 cm length open at its both ends having 2.5 cm diameter. The dialysis membrane of 12,000 Mwco (Spectra por, Sigma, USA) was used for release study because it retains nanoparticles and allows free drug to diffuse in the release media. The lower end of the glass tube was covered with the pretreated membrane to keep the nanoparticulate formulation on the donor side. The nanoparticles (equivalent to 10 mg of acyclovir) were placed in donor compartment by dispersing in 3 mL of SGF (pH 1.2) where the drug was allowed to freely diffuse over the receptor compartment containing 100 mL of SGF (pH 1.2). The entire system was kept at37±0.5°C with continuous magnetic stirring at 100 rpm. Samples of 5 mL were withdrawn at predetermined time intervals (0.5, 1, 2, 3, 4, 5, 6, 12, and 24 h) and replaced with fresh SGF [18, 21]. The withdrawn samples were suitably diluted to carry out UV Spectrophotometric analysis at 254 nm.


## 2.3.5. Measurement of Mucoadhesive Strength

The method is based on the measurement of shear stress required to break the adhesive bond between a mucosal membrane and the formulation. The formulation is sandwiched between two mucosal membranes fixed on flexible supports in the assemblies for a sufficient period of time. After the adhesive bond has formed, the force (weight) required to separate the bond was recorded as mucoadhesive strength.Mucoadhesive properties of acyclovir nanoparticles were evaluated by Texture analyzer (M/s TA. XT. Plus, Stable Microsystem, UK) using porcine gastric mucosa. Stomach of pig was obtained immediately after slaughter at local slaughterhouse. The stomach was washed with fresh water to remove nondigested food from stomach, then placed in SGF at 4°C (used within 6 h). The membrane was then attached both on the base of texture analyzer and to the stainless steel probe (using two-side adhesive tape); probe is then fixed to the mobile arm of the texture analyzer. The 10 mg of nanoparticulate formulation was placed on the membrane placed on lower surface moistened with 1 mL of SGF. The mobile arm (with attached membrane) was lowered at a rate of 0.5 mm s−1 until contact with the formulation was made. A contact force of 10 g was maintained for 500 s, after which the probe was withdrawn from the membrane. After the adhesive bond has formed, the force of detachment (g) required to separate the bond was recorded as mucoadhesive strength [22]. This parameter was used to compare mucoadhesive property of various formulations.


## 2.4. Screening of Influential Variables

A number of formulation and processing variables influence the overall performance of nanoparticles. Thus it becomes extremely difficult to study the effect of each variable and interaction among them through the conventional approach. In current studies, screening of various process and formulation variables, potentially influencing nanoparticulate formulation development, was performed employing Taguchi design for seven factors at two levels each as given in Table1. The number of experiments during screening was kept as small as possible, to limit the volume of work carried out during initial stages. This was conducted to identify the potential factors for further systematic DoE optimization studies, as the nature of influence of such variables is not widely known from prior literature reports.Table 1
List of variables employed in Taguchi L8 orthogonal array experiment.
Factors
Levels
Low (−1)
High (+1)
Amount of gelatin (mg)
200
1000
Amount of glutaraldehyde (mL)
0.1
0.5
Amount of pluronic F-68 (mg)
50
250
Acetone addition rate (mL/min)
1
5
pH
2
4
Stirring time (h)
1
5
Stirring speed (rpm)
200
1000A standard orthogonal array L8 was used to examine this system where L and subscript 8 denote the latin square and the number of the experimental runs, respectively. Design-Expert (Stat-Ease Inc., USA) was used as software for the DoE modeling. Table2 depicts the orthogonal array L8 for the seven factors at two levels by Taguchi design was adopted in the studies. Particle size, polydispersity index (PDI), amount of drug released in 6 h (Q6), time required to release 60% of drug (T60%), entrapment efficiency, loading efficiency, and mucoadhesiveness were the key response variables investigated thoroughly for selecting the significant formulation and response factors. A run involved the corresponding combination of levels to which the factors in the experiment were set as shown in Table 3. All experiments were done in triplicate. The effects of the proposed experiments on the responses were then analyzed by the Design Expert software to obtain independently the main effects of these factors, followed by the analysis of variance (ANOVA) to determine which factors were statistically significant. Series of Pareto charts were constructed to demonstrate the influence of each parameter on the responses (Figure 3). The most influential factor among the seven factors will be derived by selecting factors which are showing maximum standardized effect for most of the responses in Pareto charts.Table 2
L8 array layout as per 7 factors, 2 levels Taguchi screening design.
Formulation code
Amount of gelatin (mg)
Amount of Glutaraldehyde (mL)
Amount of Pluronic  F-68 (mg)
Acetone addition rate (mL/min)
pH
Stirring time (h)
Stirring speed (rpm)
F1
-
1
-
1
-
1
-
1
-
1
-
1
-
1
F2
-
1
+
1
-
1
+
1
+
1
+
1
-
1
F3
+
1
+
1
-
1
-
1
-
1
+
1
+
1
F4
+
1
-
1
-
1
+
1
+
1
-
1
+
1
F5
+
1
-
1
+
1
+
1
-
1
+
1
-
1
F6
+
1
+
1
+
1
-
1
+
1
-
1
-
1
F7
-
1
+
1
+
1
+
1
-
1
-
1
+
1
F8
-
1
-
1
+
1
-
1
+
1
+
1
+
1Table 3
Preparation of nanoparticles on the basis of Taguchi screening design.
Formulation
Amount of gelatin (mg)
Amount of Glutaraldehyde (mL)
Amount of Pluronic  F-68 (mg)
Acetone addition rate (mL/min)
pH
Stirring time (h)
Stirring speed (rpm)
F1
200
0.1
50
1
2.0
1
200
F2
200
0.5
50
5
4.0
5
200
F3
1000
0.5
50
1
2.0
5
1000
F4
1000
0.1
50
5
4.0
1
1000
F5
1000
0.1
250
5
2.0
5
200
F6
1000
0.5
250
1
4.0
1
200
F7
200
0.5
250
5
2.0
1
1000
F8
200
0.1
250
1
4.0
5
1000
Drug amount was kept constant at 200 mg.


## 3. Results and Discussion

The current study was undertaken to screen most influential factors in optimization of a nanoparticulate system suitable for mucoadhesion along with low particle size, low PDI, sustained release, high entrapment, and loading efficiency. The results for evaluation of gastroretentive mucoadhesive nanoparticles are given in Table4.Table 4
Evaluation of formulations of Taguchi screening design.
Formulation
Particle Size (nm)
PDI
Q
6
* (%)
T
60
%
* (h)
Entrapment efficiency* (%)
Drug loading* (%)
Mucoadhesion study* (g)
F1
165.3
0.906
15.00
±
0.26
26.8
±
0.351
20.26
±
1.98
39.72
±
1.03
6.021
±
0.094
F2
256.7
1.000
14.34
±
0.74
24.4
±
0.861
30.82
±
1.45
53.04
±
1.14
4.494
±
0.058
F3
478.3
0.832
34.93
±
0.86
21.2
±
0.984
15.70
±
2.16
47.25
±
2.01
11.02
±
0.846
F4
1610
0.360
7.31
±
0.64
37.6
±
0.654
51.69
±
2.48
55.07
±
2.48
8.347
±
0.989
F5
552.8
0.532
12.77
±
0.26
21.2
±
1.48
31.57
±
1.61
78.63
±
1.98
5.992
±
0.114
F6
345.9
1.000
7.59
±
1.29
37.2
±
2.03
49.30
±
3.04
80.49
±
2.85
5.029
±
0.0742
F7
319.3
0.656
11.89
±
2.35
24
±
0.987
83.12
±
2.45
59.04
±
1.64
3.959
±
0.056
F8
1300
0.809
15.42
±
0.35
19.2
±
0.494
67.79
±
1.47
71.23
±
1.03
5.029
±
0.081
*Mean ± SD (n=3); (P<0.05).
Q
6 is amount of drug released in 6 h; T60%* (h) is time required for 60% cumulative drug release.


### 3.1. Evaluation of Formulations

#### 3.1.1. Influence of Various Factors on Particle Size

It has been shown that particle size and size distribution are the most important characteristics of nanoparticles systems. Many studies have demonstrated that nanoparticles of submicron size have a number of advantages over microparticles as a drug delivery system. It was found that increasing the quantity of Pluronic F-68 results in reduction in size of the formulation because it decreases the surface tension between organic and aqueous phase and leads to the formation of smaller solvent droplets, which in turn causes decrease in particle size. It also stabilizes newly generated surfaces and prevents aggregation of the particles which is similar to the previous studies [23]. It was also observed that increase in stirring speed and amount of cross-linking agent results in reduction in particle size which may be due to stabilization of the surface and thereby preventing aggregation in later case. Lower value of pH favors nanoparticles with small size because of maximum solubility of gelatin at pH values far from its isoelectric point (pH 4.7–5.2 for gelatin type B).


#### 3.1.2. Influence of Various Factors on Particle Size Distribution

It was found that on increasing pH (close to isoelectric point of gelatin) and amount of glutaraldehyde PDI was increased, while high stirring speed and amount of polymer resulted in lowering of PDI. Considering that the PDI is calculated from the square of the standard deviation/mean diameter, less value of polydispersity index indicates enhanced homogeneity of the nanoparticles.


#### 3.1.3. Influence of Various Factors on Loading and Entrapment Efficiency

Loading efficiency of the formulation increases with increasing the amount of polymer. Maximum loading and entrapment efficiency was obtained when drug is loaded at or near its isoelectric point when it has minimum solubility and maximum adsorption. Loading and entrapment efficiencies were more on increasing the acetone addition rate and Pluronic F-68. On increasing stirring speed loading efficiency reduces which may be because of leaching of drug from the formulation before cross-linking step. It is probable that the entrapment of acyclovir molecule to gelatin nanoparticles is due to noncovalent interactions since gelatin (type B, isoelectric point between pH 4.7–5.2) remains charged at a pH away from isoelectric point. Noncovalent interactions unlike covalent types proceed more slowly and go to completion over time results in increased loading efficiency with increase in stirring time.


#### 3.1.4. Influence of Various Factors on Drug Release

The results of drug release study for various formulations are shown in Figure1. Drug release was found to decrease with increase in the polymer ratio. This can be attributed to the release retarding effect of polymer which reduces the release of drug from the nanoparticulate formulation. Release rate was also reduced with increase in amount of cross-linking agent which may be due to rigidization of surface of nanoparticles.Figure 1
Drug release study of formulations of Taguchi screening design.


#### 3.1.5. Influence of Various Factors on Mucoadhesion

Mucoadhesion studies were performed by using texture analyzer and representative graph showing force of detachment is given in Figure2. Point F represents the force at which the breaking of the adhesive bond starts (i.e., the force of detachment). It was found that increase in polymer ratio increases the mucoadhesiveness of the formulation due to bioadhesive nature of the polymer, while increase in concentration of Pluronic F-68 and glutaraldehyde results in lowering of mucoadhesiveness which may be due to surfactant effect of Pluronic F-68 and greater cross-linking of mucoadhesive polymer due to glutaraldehyde.Figure 2
Graph showing force of detachment. Point F represents the force at which the breaking of adhesive bond starts (the force of detachment).Figure 3
Pareto chart of the standardized effects of various formulation and process factors on selected responses.


### 3.2. Screening of Influential Formulation and Process Variables

Taguchi has developed a method based on “orthogonal array” experiments which gives much reduced “variance” for the experiment with “optimum settings” of control parameters. Seven formulation and process variables including amount of gelatin (mg), amount of glutaraldehyde (mL), amount of Pluronic F-68 (mg), acetone addition rate (mL/min), pH, stirring time (h), and stirring speed were studied each in two levels.Implementation of the L8 array design helps in identifying the most significant factors for further detailed investigation with minimum experimentation thus saving considerable time, efforts, and resources. Data obtained after the evaluation of the prepared formulation was subjected to ANOVA by using Design Expert Software which provides the coefficient values for the selected responses. These coefficient values were used as standardized effect and plotted against various responses to construct Pareto charts. The “standardized effect” determines each factor’s relative strength; the higher the absolute value the greater the effect of that factor on the response. A positive effect value indicates an effect that favors the response, and a negative value represents an inverse relationship between the response and the factor. Pareto ranking analyses showed that the most significant factors were amount of gelatin and amount of Pluronic F-68 (P<0.05) relative to other factors influencing the studied response variables including particle size, PDI, Q6, T60%, entrapment efficiency, loading efficiency, and mucoadhesiveness.Based on the results of Taguchi screening further experimental design such as central composite design is suggested to generate polynomial equations for various responses, feasibility followed by intensive grid search, and overlay plot method for selection of optimized formulation. The criteria for selection of suitable feasible region will be based upon the best possible values of particle size, PDI,Q6, T60%, entrapment efficiency, loading efficiency, and mucoadhesiveness. Validated formulations will be evaluated for their performance and the results will be critically compared with those predicted using RSM.


## 3.1. Evaluation of Formulations

### 3.1.1. Influence of Various Factors on Particle Size

It has been shown that particle size and size distribution are the most important characteristics of nanoparticles systems. Many studies have demonstrated that nanoparticles of submicron size have a number of advantages over microparticles as a drug delivery system. It was found that increasing the quantity of Pluronic F-68 results in reduction in size of the formulation because it decreases the surface tension between organic and aqueous phase and leads to the formation of smaller solvent droplets, which in turn causes decrease in particle size. It also stabilizes newly generated surfaces and prevents aggregation of the particles which is similar to the previous studies [23]. It was also observed that increase in stirring speed and amount of cross-linking agent results in reduction in particle size which may be due to stabilization of the surface and thereby preventing aggregation in later case. Lower value of pH favors nanoparticles with small size because of maximum solubility of gelatin at pH values far from its isoelectric point (pH 4.7–5.2 for gelatin type B).


### 3.1.2. Influence of Various Factors on Particle Size Distribution

It was found that on increasing pH (close to isoelectric point of gelatin) and amount of glutaraldehyde PDI was increased, while high stirring speed and amount of polymer resulted in lowering of PDI. Considering that the PDI is calculated from the square of the standard deviation/mean diameter, less value of polydispersity index indicates enhanced homogeneity of the nanoparticles.


### 3.1.3. Influence of Various Factors on Loading and Entrapment Efficiency

Loading efficiency of the formulation increases with increasing the amount of polymer. Maximum loading and entrapment efficiency was obtained when drug is loaded at or near its isoelectric point when it has minimum solubility and maximum adsorption. Loading and entrapment efficiencies were more on increasing the acetone addition rate and Pluronic F-68. On increasing stirring speed loading efficiency reduces which may be because of leaching of drug from the formulation before cross-linking step. It is probable that the entrapment of acyclovir molecule to gelatin nanoparticles is due to noncovalent interactions since gelatin (type B, isoelectric point between pH 4.7–5.2) remains charged at a pH away from isoelectric point. Noncovalent interactions unlike covalent types proceed more slowly and go to completion over time results in increased loading efficiency with increase in stirring time.


### 3.1.4. Influence of Various Factors on Drug Release

The results of drug release study for various formulations are shown in Figure1. Drug release was found to decrease with increase in the polymer ratio. This can be attributed to the release retarding effect of polymer which reduces the release of drug from the nanoparticulate formulation. Release rate was also reduced with increase in amount of cross-linking agent which may be due to rigidization of surface of nanoparticles.Figure 1
Drug release study of formulations of Taguchi screening design.


### 3.1.5. Influence of Various Factors on Mucoadhesion

Mucoadhesion studies were performed by using texture analyzer and representative graph showing force of detachment is given in Figure2. Point F represents the force at which the breaking of the adhesive bond starts (i.e., the force of detachment). It was found that increase in polymer ratio increases the mucoadhesiveness of the formulation due to bioadhesive nature of the polymer, while increase in concentration of Pluronic F-68 and glutaraldehyde results in lowering of mucoadhesiveness which may be due to surfactant effect of Pluronic F-68 and greater cross-linking of mucoadhesive polymer due to glutaraldehyde.Figure 2
Graph showing force of detachment. Point F represents the force at which the breaking of adhesive bond starts (the force of detachment).Figure 3
Pareto chart of the standardized effects of various formulation and process factors on selected responses.


## 3.1.1. Influence of Various Factors on Particle Size

It has been shown that particle size and size distribution are the most important characteristics of nanoparticles systems. Many studies have demonstrated that nanoparticles of submicron size have a number of advantages over microparticles as a drug delivery system. It was found that increasing the quantity of Pluronic F-68 results in reduction in size of the formulation because it decreases the surface tension between organic and aqueous phase and leads to the formation of smaller solvent droplets, which in turn causes decrease in particle size. It also stabilizes newly generated surfaces and prevents aggregation of the particles which is similar to the previous studies [23]. It was also observed that increase in stirring speed and amount of cross-linking agent results in reduction in particle size which may be due to stabilization of the surface and thereby preventing aggregation in later case. Lower value of pH favors nanoparticles with small size because of maximum solubility of gelatin at pH values far from its isoelectric point (pH 4.7–5.2 for gelatin type B).


## 3.1.2. Influence of Various Factors on Particle Size Distribution

It was found that on increasing pH (close to isoelectric point of gelatin) and amount of glutaraldehyde PDI was increased, while high stirring speed and amount of polymer resulted in lowering of PDI. Considering that the PDI is calculated from the square of the standard deviation/mean diameter, less value of polydispersity index indicates enhanced homogeneity of the nanoparticles.


## 3.1.3. Influence of Various Factors on Loading and Entrapment Efficiency

Loading efficiency of the formulation increases with increasing the amount of polymer. Maximum loading and entrapment efficiency was obtained when drug is loaded at or near its isoelectric point when it has minimum solubility and maximum adsorption. Loading and entrapment efficiencies were more on increasing the acetone addition rate and Pluronic F-68. On increasing stirring speed loading efficiency reduces which may be because of leaching of drug from the formulation before cross-linking step. It is probable that the entrapment of acyclovir molecule to gelatin nanoparticles is due to noncovalent interactions since gelatin (type B, isoelectric point between pH 4.7–5.2) remains charged at a pH away from isoelectric point. Noncovalent interactions unlike covalent types proceed more slowly and go to completion over time results in increased loading efficiency with increase in stirring time.


## 3.1.4. Influence of Various Factors on Drug Release

The results of drug release study for various formulations are shown in Figure1. Drug release was found to decrease with increase in the polymer ratio. This can be attributed to the release retarding effect of polymer which reduces the release of drug from the nanoparticulate formulation. Release rate was also reduced with increase in amount of cross-linking agent which may be due to rigidization of surface of nanoparticles.Figure 1
Drug release study of formulations of Taguchi screening design.


## 3.1.5. Influence of Various Factors on Mucoadhesion

Mucoadhesion studies were performed by using texture analyzer and representative graph showing force of detachment is given in Figure2. Point F represents the force at which the breaking of the adhesive bond starts (i.e., the force of detachment). It was found that increase in polymer ratio increases the mucoadhesiveness of the formulation due to bioadhesive nature of the polymer, while increase in concentration of Pluronic F-68 and glutaraldehyde results in lowering of mucoadhesiveness which may be due to surfactant effect of Pluronic F-68 and greater cross-linking of mucoadhesive polymer due to glutaraldehyde.Figure 2
Graph showing force of detachment. Point F represents the force at which the breaking of adhesive bond starts (the force of detachment).Figure 3
Pareto chart of the standardized effects of various formulation and process factors on selected responses.


## 3.2. Screening of Influential Formulation and Process Variables

Taguchi has developed a method based on “orthogonal array” experiments which gives much reduced “variance” for the experiment with “optimum settings” of control parameters. Seven formulation and process variables including amount of gelatin (mg), amount of glutaraldehyde (mL), amount of Pluronic F-68 (mg), acetone addition rate (mL/min), pH, stirring time (h), and stirring speed were studied each in two levels.Implementation of the L8 array design helps in identifying the most significant factors for further detailed investigation with minimum experimentation thus saving considerable time, efforts, and resources. Data obtained after the evaluation of the prepared formulation was subjected to ANOVA by using Design Expert Software which provides the coefficient values for the selected responses. These coefficient values were used as standardized effect and plotted against various responses to construct Pareto charts. The “standardized effect” determines each factor’s relative strength; the higher the absolute value the greater the effect of that factor on the response. A positive effect value indicates an effect that favors the response, and a negative value represents an inverse relationship between the response and the factor. Pareto ranking analyses showed that the most significant factors were amount of gelatin and amount of Pluronic F-68 (P<0.05) relative to other factors influencing the studied response variables including particle size, PDI, Q6, T60%, entrapment efficiency, loading efficiency, and mucoadhesiveness.Based on the results of Taguchi screening further experimental design such as central composite design is suggested to generate polynomial equations for various responses, feasibility followed by intensive grid search, and overlay plot method for selection of optimized formulation. The criteria for selection of suitable feasible region will be based upon the best possible values of particle size, PDI,Q6, T60%, entrapment efficiency, loading efficiency, and mucoadhesiveness. Validated formulations will be evaluated for their performance and the results will be critically compared with those predicted using RSM.


## 4. Conclusion

A Taguchi design was performed to screen the effect of formulation and processing variables on the response variables by applying computer optimization technique. Screening studies showed that the most influential independent variables were amount of gelatin and amount of Pluronic F-68 which influences the studied response variables for development of gastroretentive mucoadhesive nanoparticles. Based on the results of optimization studies it was concluded that further experimental designs are required to study the main interaction, quadratic effects of these variables on the responses and obtain the optimized formulation.



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*Source: 348095-2013-08-07.xml*