|ORIGINAL RESEARCH ARTICLE
|Year : 2017 | Volume
| Issue : 4 | Page : 174-181
Aminopropyl groups of the functionalized Mobil Crystalline Material 41 as a carrier for controlled diclofenac sodium and piroxicam delivery
Elham Khodaverdi1, Mina Ahmadi1, Hossein Kamali1, Farzin Hadizadeh2
1 Targeted Drug Delivery Research Center, School of Pharmacy, Mashhad University of Medical Sciences, Mashhad, Iran
2 Biotechnology Research Center, Institute of Pharmaceutical Technology; Department of Medicinal Chemistry, School of Pharmacy, Mashhad University of Medical Sciences, Mashhad, Iran
|Date of Web Publication||6-Apr-2018|
Prof. Farzin Hadizadeh
Biotechnology Research Center, School of Pharmacy, Mashhad University of Medical Sciences, P. O. Box 9196773117, Mashhad
Source of Support: None, Conflict of Interest: None
Objective: Synthetic Mobil Crystalline Material 41 (MCM-41) as a mesoporous material and functionalized MCM-41 using aminopropyl groups were studied in order to investigate their ability to encapsulate and to control the release of diclofenac sodium and piroxicam.
Materials and Methods: MCM-41 was synthesized through sol–gel procedure and functionalized with aminopropyl groups. The physicochemical properties of MCM-41 were studied through particle size analysis, infrared spectroscopy, scanning electron microscopy, transmission electron microscopy, and carbon–hydrogen–nitrogen analysis. Diclofenac sodium and piroxicam were loaded into the MCM-41 matrix using the filtration and solvent evaporation methods. The drug-loading capacity was determined by ultraviolet, Fourier transform infrared, X-ray diffraction, and Brunauer–Emmett–Teller analysis.
Results: According to the results for pure drug release, >57% was released in the 1st h, but when these drugs were loaded into pure Mobil Crystalline Material 41 (MCM-41) and functionalized MCM-41, the release into the simulated gastrointestinal medium was less, continuous, and slower. The release of piroxicam from functionalized MCM-41 was slower than that from MCM-41 in the simulated intestinal medium because of the formation of electrostatic bonds between piroxicam and the aminopropyl groups of the functionalized MCM-41. However, in the case of diclofenac sodium, there was no significant difference between pure MCM-41 and functionalized MCM-41. The difference between piroxicam and diclofenac sodium was due to the high solubility of diclofenac sodium in the intestinal medium (pH 6.8), which caused more rapid release from the matrixes than for piroxicam.
Conclusion: Our findings indicate that, after functionalization of MCM-41, it could offer a good means of delivering controlled diclofenac sodium and piroxicam.
Keywords: Diclofenac, drug delivery, functionalized MCM-41, MCM-41, piroxicam
|How to cite this article:|
Khodaverdi E, Ahmadi M, Kamali H, Hadizadeh F. Aminopropyl groups of the functionalized Mobil Crystalline Material 41 as a carrier for controlled diclofenac sodium and piroxicam delivery. Int J Pharma Investig 2017;7:174-81
|How to cite this URL:|
Khodaverdi E, Ahmadi M, Kamali H, Hadizadeh F. Aminopropyl groups of the functionalized Mobil Crystalline Material 41 as a carrier for controlled diclofenac sodium and piroxicam delivery. Int J Pharma Investig [serial online] 2017 [cited 2018 Aug 20];7:174-81. Available from: http://www.jpionline.org/text.asp?2017/7/4/174/229436
| Introduction|| |
Mesoporous silica is a promising mineral material with a high pore volume, large surface area, nanometer pore diameter (2–50 nm), good biocompatibility, thermal/chemical stability, ease of preparation, ease of functionalization, and adjustable pore diameter, making it a good candidate for controlled/sustained drug delivery and in new biomedical applications, such as tissue engineering and biological imaging., Due to its tunable nature, MCM-41 can assume different morphologies, such as worm shapes, crescent-like shapes, gyroids, hexagonal plates, spheres, rods, discs, and particles, so it is the most suitable choice for drug delivery, sensing, adsorption/separation, and acts as a catalyst and optically active material, among the mesoporous materials.
The variable effects of different types of surfactant on MCM-41 have been employed to obtain different pore sizes to investigate ibuprofen delivery. The profiles of drug release illustrate that the method of drug loading is effective for release, but that the type of surfactant has no effect on it. Functionalization of MCM-41 with aminopropyl groups with two methods of functionalization has also been employed to control the ibuprofen release. In addition, the method of functionalization has been varied: MCM-41 is directly synthesized using aminopropyl groups (Method I), while in the Method II, in the first step it was calcined and then synthesized using aminopropyl group. The rate of drug delivery through Method II is slower than that through Method I.,In vitro assays of phosphorous functionalized MCM-41 showed a bioactive response after 13 days, but there was no evidence of bioactivity even after 2 months for pure MCM-41. Popova et al. have synthesized amino carboxylic MCM-41 in two steps. The MCM-41 was first reacted with 3-amino-propyltriethoxysilane and then modified by succinic anhydride in toluene.In vitro release of sulfadiazine illustrated that the rate of release from functionalized MCM-41 was slower than that from pure MCM-41. MCM-41-NH2 COOH had no cytotoxicity to the human colon carcinoma cell line (Caco-2). In another study on the Caco-2 cell line, Heikkilä et al. found that the effects of pure MCM-41 on carcinoma cells were diminished cell metabolism, increased apoptotic signaling, and weakened cell membrane integrity, and it was concluded that the use of an oral formulation must be avoided for the smallest microparticles. Vyskočilová et al. have functionalized MCM-41 through amino, chloro, and oxo groups and showed that the pure MCM-41 and functionalized MCM-41 with oxo groups have the slowest dissolution of acetylsalicylic acid in vitro release. Furthermore, pure MCM-41 and functionalized MCM-41 have been utilized as sustained and controlled delivery systems for ibuprofen,, aspirin, indomethacin, furosemide, cisplatin, mesalazine (5-aminosalicylic acid), acetylsalicylic acid, and 5-Fu and famotidine.
In the present research, MCM-41 was synthesized through sol–gel procedure and functionalized with aminopropyl groups. The physicochemical properties of MCM-41 were studied through particle size analysis (PSA), infrared spectroscopy (IR), transmission electron microscopy (TEM), scanning electron microscopy (SEM), and carbon–hydrogen–nitrogen (CHN) analysis. Diclofenac sodium and piroxicam, nonsteroidal anti-inflammatory drugs that also have analgesic and anti-fever effects, were loaded into the MCM-41 matrix, and a study of the in vitro release was performed in simulated gastrointestinal medium. Drug loading was performed using the filtration and solvent evaporation methods. Furthermore, the drug-loading capacity was determined by ultraviolet (UV) spectroscopy, IR, X-ray diffraction (XRD), and Brunauer–Emmett–Teller (BET) analysis.
| Materials and Methods|| |
Tetraethoxysilane, 3-aminopropyltrimethoxysilane, and hexadecyltrimethyl-ammonium bromide (CTAB) were supplied by Sigma-Aldrich (Darmstadt, Germany). Piroxicam and diclofenac sodium were provided by Sobhan Darou Co (Rasht, Iran). All other chemical materials were purchased from Merck (Darmstadt, Germany).
Preparation of Mobil Crystalline Material 41
MCM-41 was synthesized via sol–gel procedure as follows: at first, 2.5 ml tetraethoxysilane was added to the surfactant solution (0.5 g CTAB in 250 ml distilled water) containing 3.5 ml NaOH solution (2 M) and stirred for 30 min. The resulting gel was stirred for 24 h at 80°C. Next, 50 mL ethanol and 4 ml of HCl were added to the gel and stirred for 24 h at 70°C. Finally, the mixture was centrifuged at 8500 rpm (6785 relative centrifugal force) for 15 min. The precipitate was washed using deionized water in triplicate and dried at room temperature overnight. The particle sizes, zeta potential, and polydispersity index (PDI) were measured through PSA, and the particle size was also confirmed by TEM.
Amine-functionalized Mobil Crystalline Material 41 particles
The mixture of 2 g MCM-41, 70 ml toluene, and 0.35 ml 3-aminopropyl triethoxysilane was added into a stainless steel vessel and was refluxed at 20°C for 15 h. Finally, the aminopropyl-functionalized MCM-41 obtained was passed through the filter and washed with ethanol 96% and dried at 80°C for 8 h. The presence of the amino propyl in MCM-41 was confirmed by Fourier transform infrared (FTIR) and CHN tests.
Drug loading by filtration method (Method A)
For drug loading through Method A, 2.5 g matrixes (pure MCM-41 or functionalized MCM-41) containing 1 g diclofenac sodium or piroxicam powders were stirred in 300 ml acidic methanol (10% v/v) for 48 h at 600 rpm. After that, the resulting products were passed through 0.2-μm polyester filter, and the residual solvent was removed at vacuum condition at 30°C for 30 min using a rotary evaporator. The filtrates were maintained in dry place until use. The drug-loading content (LC) and loading efficiency (LE) of the matrixes were measured using the following formulas:,
Drug loading by solvent evaporation method (Method B)
In this method, the filtration stage was not carried out and the rest of the process was similar to Method A. The acidic methanol was evaporated using a hot plate stirrer at 55°C for 48 h.
FTIR and CHN analyses were used to ensure that the aminopropyl was placed on the surface of the matrixes. Furthermore, UV spectroscopy, XRD, BET, and FTIR analyses were used to ensure that the drug was loaded in the matrixes.
For FTIR, a 20-mg sample (drug, matrixes, and matrixes containing drugs) was blended with 40-mg KBr in a mortar and then PerkinElmer spectrometer (model 1000 (USA) was used for analysis.
CHN analysis was used to determine the carbon (C), hydrogen (H), and nitrogen (N) elemental concentrations in functionalized MCM-41. Functionalization with aminopropyl was assessed based on the amount of nitrogen in the matrix using a CHN analyzer (PerkinElmer 2400 Series II).
Siemens-D5000 (UK) consisting of a PW3710 diffractometer and a X-ray tube (30 mA and 40 KV) with a copper anode from 5°–40° (diffraction angle 2θ) at a step size of 0.02° and a scanning rate of 4°/min radiation was used to obtain the XRD of the diclofenac sodium alone, the matrixes alone, and the matrixes containing diclofenac sodium.
BET analysis through a Quantachrome Autosorb 1-MP using N2 adsorption was utilized to measure the surface area (m 2/g) of the matrixes alone and the matrixes containing drugs. The matrixes containing drugs were depleted at 60°C before analysis because the melting points of the drugs, namely diclofenac sodium and piroxicam were 283°C–285°C and 198°C–200°C, respectively.
The drug loading content through Method A within and on the surface of pure MCM-41 and functionalized MCM-41 was measured by UV spectroscopy. It was assumed that the drug loading content through Method B was 100% because the acidic methanol was evaporated and the entire content of the drug had been loaded into or onto the matrix. After filtration, the absorbance of the bottom solution was read. The absorption spectra of diclofenac sodium and piroxicam in the acidic methanol (10% v/v) were 302 and 332 nm, respectively, in terms of λmax. The different formulations' abbreviations are listed in [Table 1].
The particle sizes and size distributions of the matrixes were determined at a 90° scattering angle using a 4 mW He-Ne laser with 633 nm incident beam through dynamic light scattering (Malvern Zetasizer™ ZS, Malvern, UK).
TEM (Hitachi H-7000, Nissei Sangyo, USA) was used to determine the size of the matrixes. In practice, a dilute suspension of matrixes in distilled water (0.5 mg/mL) was prepared that was filtered and was observed at 80 kV. All measurements were performed in triplicate.
For the determination of the morphologies and sizes of pure MCM-41 and functionalized MCM-41 matrixes, the SEM (LEO 1450, Germany) was used. Prior to imaging, the matrix samples were gold plated in order to investigate the surface structure.
To investigate the release of diclofenac sodium and piroxicam from the matrixes into simulated gastrointestinal medium from matrixes, a dissolution test apparatus was applied. The simulated gastric juice and simulated intestinal fluid containing HCl solution (pH = 1.5) and phosphate buffer at 0.2 M (pH = 6.8), respectively, were agitated at 100 rpm at 37°C. To prepare 1 L of phosphate buffer with a pH of 6.8 and a buffering capacity of 10, which could simulate the intestinal medium, salts of NaH2 PO4.2H2O (0.838 g) and Na2 HPO4.12H2O (1.656 g) were used. After washing and tuning the apparatus, 1000-ml dissolution medium was poured into each flask, and the drugs and matrixes containing drugs were subsequently separately poured into the flasks.
Sampling was performed using a peristaltic pump (Alitea, Sweden) at 0, 15, 30, 45, 60, 75, 90, 105, 120, 135, and 150 min under nonsink condition. The spectrophotometer connected to a dissolution testing device (Shimadzu, Japan) was used to record the absorption of each sample at 332 nm for piroxicam and at 302 nm for diclofenac sodium in simulated gastric juice and at 276 nm for piroxicam and at 279 nm for diclofenac sodium in simulated intestinal fluid. All measurements were performed in triplicate.
The Food and Drug Administration Guidance for Industry Human Medicines Evaluation Unit of The European Agency for the Evaluation of Medicinal Products has recommended the difference factor (f1) and a similarity factor (f2) to assess the percentage similarity between two in vitro dissolution curves over all time points according to Eq (3) and Eq (4).,
Where Tt is the dissolution value of the test formulation at time t, Rtis the dissolution value of the reference formulation at time t, and n is the number of time points. The test and reference formulation curves could be equivalent when the f1 values were up to 15 (0–15) and f2 values were >50 (50–100).
| Results|| |
The results for the particle size (Z-average), zeta potential (mV), and PDI of MCM-41 were 94.7 nm, −12.2 mV, and 0.192, respectively. Furthermore, the particle size was confirmed by TEM [Figure 1]a and SEM [Figure 1]b.
|Figure 1: (a) Transmission electron microscopy of Mobil Crystalline Material 41 and (b) scanning electron microscopy of Mobil Crystalline Material 41|
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The aminopropyl group of functionalized MCM-41 was confirmed by FTIR analysis, as shown in [Figure 2]. Furthermore, the amino propyl loading on MCM-41 was confirmed by the small peak for nitrogen in the functionalized MCM-41, identified using CHN analysis as shown in [Figure 3].
|Figure 2: Fourier transform infrared analysis of the samples after amino functionalization (b, blue color) compared with before functionalization (a, black color)|
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|Figure 3: Carbon–hydrogen–nitrogen analysis of functionalized Mobil Crystalline Material 41|
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The drug loading content was measured using UV spectroscopy within and on the surface of the matrixes. The LC and LE results are tabulated in [Table 2]. According to the results of [Table 3], the empty spaces of the matrixes were occupied at approximately 61% when the drug was loaded into the matrixes. During the loading of drug into the matrixes, the smooth surface and polyhedral shape of the matrixes [Figure 1]b were converted into an uneven surface, as shown in [Figure 4]a and [Figure 4]b.
|Table 2: The loading efficiency and content results for drugs in formulations created using Method A|
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|Figure 4: (a) Scanning electron microscopy images (×10,000) of D.F.A and (b) P.F.A|
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The maximum release values of diclofenac sodium and piroxicam (control) in the simulated gastric juice were 57.31% and 74.11%, respectively. After 150 min, the release values for matrixes containing diclofenac sodium and piroxicam were 0% and 10%, as shown in [Figure 5]a and [Figure 5]b. The pure diclofenac sodium and piroxicam can be dissolved within 50 min, while for drugs with matrixes, drug was not released in this media. The maximum release value of both drugs from pure MCM-41 and functionalized MCM-41 after 150 min was 10%. Comparison between the dissolution profiles of formulations in the stomach-like medium was performed by computing the difference (f1) and similarity (f2) factors. All profiles of two drugs were different mutually except certain dissolution profiles for diclofenac sodium, including D.M.A versus D.M.B, D.M.A versus D.F.B, and D.M.B versus D.F.B, which were similar.
|Figure 5: (a) The profile of diclofenac sodium release in stomach-like media, (b) the profile of piroxicam release in stomach-like media, (c) the profile of diclofenac sodium release in small intestine-like media, (d) the profile of piroxicam release in small intestine-like media|
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The maximum release values of diclofenac sodium and piroxicam (control) in the simulated intestinal fluid were 99.3% and 99.45%, respectively, after 30 min; while these values for matrixes containing diclofenac sodium and piroxicam were approximately 76% after 300 min [Figure 5]c and [Figure 5]d. The dissolution curves of the formulations in the small intestine-like medium were compared by computing the difference (f1) and similarity (f2) factors. The curves for diclofenac sodium release, including D.F.A versus D.M.B; D.F.A versus D.F.B; D.F.A versus D.M.A; D.M.A versus D.F.B; D.M.A versus D.M.B; and D.M.B versus D.F.B, and the curves for piroxicam release, including P.M.A versus P.M.B; P.M.A versus P.F.B; and P.M.B versus P.F.B, were found to be similar.
| Discussion|| |
MCM-41 and functionalized MCM-41 as a mesoporous material were studied to verify their ability to encapsulate and release a nonsteroidal anti-inflammatory drug as diclofenac sodium and piroxicam. The results of TEM and SEM confirm that the method of synthesis was suitable because the PDI (0.15–0.4) showed that the nanomatrix (60–100 nm) had a suitable size distribution and a negative zeta potential due to the stability of MCM-41. The result of FTIR determined that the bands of Si–O–Si asymmetric stretching vibration and symmetric stretching vibration have been demonstrated at approximately 1100 and 800 cm −1, respectively. The deformation modes of Si–O–Si were also detected at approximately 460 cm −1. The Si–OH bending was indicated at 970 cm −1 obviously. The stretching vibrational modes of the silanol groups present on the surface of the mesoporous material were illustrated in adsorption bands at approximately 3740 cm −1–3000 cm −1. Furthermore, absorption bands at 3380 cm −1–3310 cm −1 could be presented at the NH stretching bands. In addition, the band for -NH2 overlaps with that of O–H stretching vibration that makes difficult to identify the NH2 connected to the mesoporous material surfaces.
The parameters such as pore size, pore volume, surface area, and surface properties of the carrier materials can influence the drug-loading capacity. The results showed that the loading capacity of MCM-41-NH2 was higher than the pure matrixes due to the presence of hydrogen bonds of silanol groups on the mesoporous wall with the carboxylic groups of drugs. The powder XRD patterns of pure MCM-41 and functionalized MCM-41 before and after diclofenac sodium loading through Method A were done. A slight decline in the crystallinity was attributed to the drug absorption on matrix, with an overall decline in the intensity of the peak. The spawning peaks in the curve were probably related to diclofenac sodium. The C = O groups in the molecule were indicated by FTIR that could be proved by the existence of diclofenac and piroxicam and their interactions in the matrixes. The stretching vibrational frequency of the silanol groups caused adsorption bands in the range of 3750 cm −1–3000 cm −1. A strong stretching band for the carbonyl group (C = O peak) in the infrared spectrum relating to the diclofenac sodium powder and the piroxicam was observed at a wave number of approximately 1700 cm −1. This carbonyl peak is one of the most useful infrared spectra and is often regarded as the first studied peak. The diclofenac sodium peak for C = O at wave numbers of 1696 and 1722 cm −1 proves the presence of diclofenac sodium in the functionalized MCM-41 generated through Method A and Method B. In addition, the piroxicam peak for carbonyl at wave numbers of 1653 and 1652 cm −1 proves the presence of piroxicam in the functionalized MCM-41 generated through Method A and Method B. The BET analysis indicating a significant decrease of surface area from matrix containing drugs was observed. The pores of matrixes have entrapped a huge amount of drug, rather than on the surface according to the results of TEM and SEM. This conclusion was confirmed by dissolution studies.
The amount of release for diclofenac sodium and piroxicam was low because they have acidic pKa values and exist primarily in the unionized form in the stomach environment. Furthermore, uncharged MCM-41 can remain bound to these drugs in the simulated gastric media through hydrophobic interaction. It was concluded that these formulations can resist the release of drug from matrixes in the simulated gastric media, which supported our findings. It is worth mentioning that the rate of drug release was faster and more extensive for the formulations prepared by Method B in two release media (stomach-like and small intestine-like media) than prepared by Method A because the drug was placed on the surface of the matrixes through Method B. The drug release of matrixes was slow and continuous likely when compared to pure drug since the negatively charged surface of MCM-41 repelled the negatively charged drug in the simulated intestinal environment.
Rimoli et al. and Khodaverdi et al. have confirmed the results of drug release in the gastrointestinal media. Rimoli et al. showed that release of ketoprofen loaded into a carrier matrix is low in the stomach, whereas the drug can be dissolved in and released into the intestinal environment. Khodaverdi et al. indicated that ibuprofen and indomethacin cannot be released from a matrix in the stomach-like media, whereas these drugs can be released slowly and continuously in the small intestine-like media. The release of piroxicam from functionalized MCM-41 was slower than the release from pure MCM-41 in intestine-like medium because of the formation of electrostatic bonds between piroxicam and the amino propyl groups of the functionalized MCM-41. However, in the case of diclofenac sodium, there was no significant difference between pure MCM-41 and functionalized MCM-41. The difference between piroxicam and diclofenac sodium was due to the high solubility of diclofenac sodium in the simulated intestinal medium (pH 6.8) which caused more rapid release from the matrixes than for piroxicam.
| Conclusion|| |
MCM-41 was synthesized through sol–gel procedure and functionalized with aminopropyl groups and was investigated as a matrix for controlled release. Diclofenac sodium and piroxicam were loaded into pure MCM-41 and functionalized MCM-41 matrixes, and a study of the in vitro release was performed in simulated gastrointestinal medium. Drug loading was performed using the filtration and solvent evaporation methods. Drug loading by the filtration method (Method A) is less than that by the solvent evaporation method (Method B), whereas the drug release of matrixes prepared through Method A is slightly slower than the matrix through Method B. According to the dissolution tests of pure drugs (control sample) and matrix containing pure drugs (formulations), the pure diclofenac sodium and piroxicam were released more quickly than the drugs in the formulations in the simulated gastrointestinal environment. The release of piroxicam from functionalized matrixes was slower than release from matrixes in the simulated intestinal medium because of the formation of electrostatic bonds between piroxicam and the amine groups of the functionalized matrix. However, in the case of diclofenac sodium, there was no significant difference between the functionalized matrix and the pure matrix. The difference between piroxicam and diclofenac sodium was due to the high solubility of diclofenac sodium in the simulated intestinal medium (pH 6.8), which caused more rapid release from the matrixes than for piroxicam.
This article is the result of a Pharm.D. thesis of Dr. Mina Ahmadi; we sincerely thank the Research Council of Mashhad University of Medical Sciences for providing the fund of this study.
Financial support and sponsorship
Conflicts of interest
There are no conflicts of interest.
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[Figure 1], [Figure 2], [Figure 3], [Figure 4], [Figure 5]
[Table 1], [Table 2], [Table 3]