The load and release characteristics on a strong cationic ion-exchange fiber: kinetics, thermodynamics, and influences
Authors Yuan J, Gao Y, Wang X, Liu H, Che X, Xu L, Yang Y, Wang Q, Wang Y, Li S
Received 21 March 2014
Accepted for publication 29 April 2014
Published 16 July 2014 Volume 2014:8 Pages 945—955
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Jing Yuan, Yanan Gao, Xinyu Wang, Hongzhuo Liu, Xin Che, Lu Xu, Yang Yang, Qifang Wang, Yan Wang, Sanming Li
School of Pharmacy, Shenyang Pharmaceutical University, Shenyang, People’s Republic of China
Abstract: Ion-exchange fibers were different from conventional ion-exchange resins in their non-cross-linked structure. The exchange was located on the surface of the framework, and the transport resistance reduced significantly, which might mean that the exchange is controlled by an ionic reaction instead of diffusion. Therefore, this work aimed to investigate the load and release characteristics of five model drugs with the strong cationic ion-exchange fiber ZB-1. Drugs were loaded using a batch process and released in United States Pharmacopoeia (USP) dissolution apparatus 2. Opposing exchange kinetics, suitable for the special structure of the fiber, were developed for describing the exchange process with the help of thermodynamics, which illustrated that the load was controlled by an ionic reaction. The molecular weight was the most important factor to influence the drug load and release rate. Strong alkalinity and rings in the molecular structures made the affinity between the drug and fiber strong, while logP did not cause any profound differences. The drug–fiber complexes exhibited sustained release. Different kinds and concentrations of counter ions or different amounts of drug–fiber complexes in the release medium affected the release behavior, while the pH value was independent of it. The groundwork for in-depth exploration and further application of ion-exchange fibers has been laid.
Keywords: ion-exchange fibers, ionic reaction, drug load and release, opposing exchange kinetics, thermodynamics, influences
There has been growing concern on the delivery of active compounds, such as chemicals, peptides, or proteins, in a controlled manner. Each novel type of high-performance material guides researchers to a brand new field, including ion-exchange materials. Since the first synthesis of an ion-exchanger – ion-exchange resins in 19351 – ion-exchange materials that manifest specific functions, such as drug release based on the ionic environment, bio/mucoadhesive, and taste-masking, have provided an approach to novel drug delivery through adjusting and sustaining the release and permeation of drugs; it has been studied in oral,2–5 transdermal,6–9 mucosa,10 and therapeutic embolic11 drug delivery systems. Some ion-exchange resin complexes administrated orally that are already on the market, such as Delsym® (Reckitt Benckiser, Slough, UK), have illustrated that ion-exchange materials have important practical significance and broad application prospects.12
Ion-exchange fibers, as a typical type of ion-exchange material, contain two components: a water insoluble structural component (framework) consisting of polymer chains, such as polyethylene, polypropylene, or viscose, and a functional component (exchange group) consisting of fixed negative (cationic exchanger) or positive (anionic exchanger) electric charges that are compensated by ions of the opposite charge, the so-called counter ions. The distinction between fibers and conventional resins is the non-cross-linked structure in the former.1,13,14 Unlike the exchange between drugs and resins that happens in the pores and channels of resin particles, the exchange between drugs and fibers is located on the surface of the nonporous framework (Figure 1), and the transport resistance is reduced significantly, meaning the exchange is inclined to be controlled by an ionic reaction process instead of a diffusion process. Thus, a much faster loading rate and larger loading amount are possible because of a lack of pores and channels. These characteristics facilitate the preparation of drug–fiber complexes and improve patient compliance by markedly reducing the dose of materials.
Figure 1 The distinction in structure between fiber (left) and resin (right).
A few kinetic theories based on diffusion have been developed for ion-exchange resins.15,16 However, they are not suitable for fibers. Few studies have focused on the kinetics of drug loading into ion-exchange fibers. Chen et al17 studied fibers that are composed of an inert hard core and a shell of ion-exchange material. The behavior of drugs diffusing into the inner film was the same as when they penetrated through the pores of resins. The mathematical treatment of ion-exchange processes in the fiber shell is similar to that in the conventional spherical resin, that is, the diffusion is the rate-determining process. Besides, precedents exist in the use of ionic reaction mechanisms to interpret the exchange processes of ion-exchange resins, particularly to those happening in ion-exchange columns.1 However, because of the complex exchange processes and the cross-linked structure of resins, ionic reaction kinetics have obvious shortcomings.18 But these kinetics might be a good choice for fibers because the exchanges happening on the surface of the non-cross-linked structure.
In this study, a novel type of kinetics based on the ionic reaction mechanism, named “opposing exchange kinetics”, was developed to understand the nature and strength of interactions between drugs and fibers with the help of thermodynamics. The load and release behavior (rate and extent) of five model drugs in a strong cationic ion-exchange fiber (ZB-1) was investigated to learn how molecular weight, pKa (acid dissociation constant), logP, drug structure, and some other external conditions influence the load and release process.
Materials and methods
The strong cationic ion-exchange fiber ZB-1 used in this study was obtained from Guilin Zhenghan Co, Ltd, (Guangxi, People’s Republic of China), with a maximum ion-exchange capacity of about 3.03 mmol/g and a diameter of 30–50 μm. The non-cross-linked framework of the fiber was polypropylene chain grafted with styrene side chains, and the strong cation-exchange group was sulfonic. Atenolol, diltiazem hydrochloride, sinomenine hydrochloride, tramadol hydrochloride, and venlafaxine hydrochloride were obtained from Wuhan Yuancheng Science and Technology Development Co, Ltd, (Hubei, People’s Republic of China), Chengdu Geleixiya Chemical Technology Co, Ltd, (Sichuan, People’s Republic of China), Shanghai Boshikai Chemical Science Co, Ltd, (Shanghai, People’s Republic of China), Wuhan Yuancheng Science and Technology Development Co, Ltd., (Hubei, People’s Republic of China), and Kerui-Dekaihua Pharmacy Co, Ltd, (Sichuan, People’s Republic of China), respectively. The structures, molecular weights, and physicochemical data of the model drugs are presented in Table 1. All the other chemicals were of analytical grade and were used without further purification. Self-prepared deionized water with a resistivity of more than 18 MΩ/cm was used to prepare all the solutions.
Table 1 The structures, molecular weights, and physicochemical data of the model drugs
Pretreatment of the ion-exchange fibers
The fibers in staple form were washed consecutively by 95% ethanol and deionized water to remove impurities until the washing solution became colorless, and were then activated by recycling them between the basic and acidic forms with 0.01 M NaOH and 0.01 M HCl solutions, respectively, until the pH value of the washing solutions was stable at about 12 or 2. After washing with deionized water until neutral, fibers were immersed in 1 M NaCl solution several times in order to pre-load them with sodium ions. When the pH of the fiber pulp was nearly neutral, fibers were immersed in 1 M NaCl solution several times in order to pre-load them with sodium ions until the pH of the fiber pulp was nearly neutral, meaning that hydrogen ions bound on the fibers were replaced thoroughly by sodium ions. Finally surplus ions were washed away before the fibers were dried.5 Before use, the fibers were cut into small units fine enough to pass through an 80-mesh screen.
Drug-loaded ion-exchange fibers
The drugs were loaded into the fibers using a batch process, whereby the previously purified fiber powders (100 mg dry weight) were immersed in a 3.5 mM solution of the drug (100 mL). Equimolar HCl was added into atenolol solution beforehand in order to ensure the drug remained in its cationic form. All the experiments were performed at a predetermined temperature in glass containers with a suitable volume placed in a thermostat water bath with continuous stirring at 500 rpm using a magnetic stirrer. Samples were collected through a 400-mesh filter screen from the drug–fiber system at designated time points, and then the same volume of water was added back into the system in order to maintain a constant volume. The amount of drug loaded onto the fibers was determined as the difference between the amount of drug in the initial loading solutions and samples. Each experiment was performed at least in triplicate.
Morphology of ion-exchange fibers
The surface characteristic of ion-exchange fibers was evaluated by scanning electron microscopy (SURA 35; Carl Zeiss AG, Jena, Germany). Samples were gold-plated using double-sided adhesive tape prior to imaging at 15.00 kV.
Drug release from ion-exchange fibers
The drug–fiber complexes (equivalent to 100 mg of atenolol, 100 mg of tramadol hydrochloride, 75 mg of venlafaxine hydrochloride, 60 mg of sinomenine hydrochloride, and 30 mg of diltiazem hydrochloride, respectively) were transferred to 900 mL of dissolution medium pH 1.2 HCl solution and pH 6.8 phosphate buffer in United States Pharmacopoeia (USP) dissolution apparatus 2 (RC-6 dissolution tester, Tianjin Optical Instrument Factory, Tianjin, People’s Republic of China). The temperature of the medium was maintained at 37.0°C±0.5°C. The paddle was rotated at 50 rpm. All experiments were performed in triplicate.
Analysis of drug concentrations
The content of drug in the solutions was measured with a UV-Vis (ultraviolet-visible) spectrophotometer (UV-9100; Beijing Ruili, Beijing, People’s Republic of China) at wavelengths of 273 nm, 271 nm, 273 nm, 265 nm, and 237 nm for atenolol, tramadol hydrochloride, venlafaxine hydrochloride, sinomenine hydrochloride, and diltiazem hydrochloride, respectively.
One-way analysis of variance was used to determine the significance among groups, after which post hoc tests with the least significant difference were used for comparison between individual groups. P<0.05 was considered as statistically significant.
Opposing exchange kinetics has been developed to describe the reversible ionic reaction that ion-exchange fibers undergo when placed in contact with a solution of ions. The load and release are simultaneous and the equilibrium will be reached when the positive and negative reaction rates are equal.
This type of ion-exchange reaction can be represented as follow:
where R and D stand for the ion-exchange fiber and the drug, respectively; k1 and k2 are the load and release rate constants. Here, NaCl is also considered to be a product due to its imperative role in the negative reaction, which is usually overlooked.19,20
The calculated rate of drug load at time t, as described by Equation 1, is given by:
where Q0 is the initial concentration (mmol/L) of the drug solution, Qm is the maximum loading capacity (mmol/g) of the fiber, and Qt is the loading amount (mmol/g) at time t. For an ion-exchange reaction, the positive and negative reaction rates are usually both proportional to one power of the concentrations of their reactants; therefore, the values of α, β, γ, and δ are 1:
Among k1, k2, and the equilibrium constant K, there is a relationship:
where Qe refers to the equilibrium loading amount (mmol/g). In Equation 3, k2 is substituted by k1:
Here, the ion exchange closely resembled the monomolecular layer adsorption in reversibility, which leads to a similarity in shape between the loading curve and the Langmuir adsorption isotherm curve. Therefore, an equation analogous to the Langmuir adsorption isotherm equation is used to get re, the measured reaction rate at time t, by fitting the points of Qt versus t received from experiments:
where b is the exchange coefficient.
Finally, k1 is determined by the least squares method according to Equation 8:
In particular, the first and the last time points were not included in the calculation of the reaction rate since the end points of a bounded function are non-derivable.
The positive and negative reaction activation energies, Ea1 and Ea2, respectively, can be calculated by the differential form of the “Arrhenius equation”:
The thermodynamic parameters: standard free energy change (ΔG0), enthalpy change (ΔH0), and entropy change (ΔS0) were evaluated to test the feasibility, heat effect, and mechanism of the loading process.21 All of them were related to the equilibrium constant K by the following equations:
Results and discussion
Drug-loaded ion-exchange fibers
Kinetics and thermodynamics
Figure 2 shows two types of curves of model drugs loading into the ion-exchange fibers at 25°C. Type one exhibited a very fast loading rate – 30 minutes was enough to reach equilibrium, while the loading amount was small, and the drugs included atenolol, tramadol, and venlafaxine; type two exhibited a slow loading rate – several days were needed to reach equilibrium, while the loading amount was larger, and the drugs included sinomenine and diltiazem. Opposing exchange kinetics captured the characteristics of the loading curves of atenolol and sinomenine, at three different temperatures, quite successfully (Figure 3), illustrating that the model could interpret the loading behaviors. Table 2 depicts the comparison between the experimental results (Qt) and the theoretical predictions (Qp) for atenolol at varying temperatures. The residual variations were small between the rates of ion-exchange and ionic reaction, suggesting that the ionic reaction was the rate-determining step for the loading process of ion-exchange fibers. However, for type two drugs at low temperature, the calculated values were somewhat higher than the observed ones, illustrating that there were other factors influencing the exchange rate under some conditions.
Figure 2 The loading curves of model drugs into ZB-1 at 25°C.
Table 2 Estimation of fitting accuracy of atenolol load at three temperatures
Theoretical considerations indicate that the rate constant should depend on the concentration of the reactants, with the exception of reactions between ions. By far the most dramatic effect on rate constants is caused by temperature changes.22 The calculated rate constants of all the drug loads were increased as the temperature rose (Table 3) and did not depend on the initial concentrations of reactants at a certain temperature (results not shown). These results were in agreement with the general principles of kinetic theory.
Table 3 Kinetics parameters calculated by opposing exchange kinetics for model drug loading experiments
The absolute of ΔG0 shown in Table 4 was small, which meant that the direction of spontaneous reaction could not be determined, and the difference between the Ea1 and Ea2 of one drug shown in Table 3 was small. Both of them were characteristic of reversible reactions.
Table 4 Thermodynamic parameters of model drug loading experiments
The results of ΔS0 could provide some information on the ion-exchange mechanism. This value should be positive in an ionic reaction because the randomness in the (solid + liquid) interface is increased, attributed to the release of sodium and chlorine ions, which have a smaller radius; meanwhile, the value of the adsorption process should be negative due to the decrease in the particle number. In Table 4, the ΔS0 for atenolol was negative, while that for the other four hydrochlorides was positive, which might suggest that the exchange of atenolol in ion-exchange fibers is apt to physical adsorption, while the others are more apt to ion reactions. High linearity is shown in Figure 4, in which the positive and negative reaction activation energies were calculated from the slope of lnk versus 1/T. Wang et al pointed out that the value of Ea depicted the type of adsorption: when its value is between 8 and 16 kJ/mol, it is a chemisorption, while it is a physisorption process when Ea is lower than −40 kJ/mol.23 Nollet et al also reported that low activation energies (5–40 kJ/mol) are characteristic for physisorption, while higher activation energies (40–800 kJ/mol) suggest chemisorptions.24 The Ea1 of atenolol was below 8 kJ/mol, while the Ea1 for the other drugs were all above it. The positive center of atenolol is a secondary amine while the others are tertiary amines. The secondary amine is much harder to ionize in solutions than the tertiary amine, so a coordination complex might be formed between it and hydrochloric acid instead of the ionic compound, resulting in atenolol being absorbed in the molecular form. Similarly, Borodkin et al25 reported that greater affinity existed between the resin and tertiary amines than with secondary amines.
Figure 4 lnk1 (A) and lnk2 (B) versus 1/T for estimating the positive reaction and negative reaction.
The results of ΔH0 are also shown in Table 4. The exchanges for atenolol and tramadol are exothermic, which makes their load easier and K went down as the temperature increased; high temperatures benefit the negative reaction to obtain a smaller amount. For other endothermic reactions, K increased as the temperature rose; high temperatures benefit the positive reaction to obtain a larger loading amount. However, the effect of temperature on the loading amount was not statistically significant for atenolol and sinomenine (P>0.05), and statistically significant for tramadol, venlafaxine, and diltiazem (P<0.05).
Influences on loading drugs
The effect of model drug loading into ion-exchange fibers was investigated under the same initial molar concentration of reactants. The differences among the five drugs were tested in terms of four factors: molecular weight, pKa, logP, and the structural framework of the drug.
The relationships of lnk1 or Ea1 versus molecular weight are exhibited in Figure 5. The activation energy increased and loading rate decreased with increasing molecular weight. Good linearity adequately proved that molecular weight was the most important influence on drug load. The surface of the fibers where the ionic reactions occurred was limited unlike homogeneous reactions; thus, steric hindrance appeared to be a noticeable factor in affecting the loading process. While some parts of the drug ions bonded quickly with the ion-exchange groups, other parts needed more time to rearrange into an appropriate position for the exchange, typically for drug ions with larger molecule weights, which move more slowly. This is why the observed values of the exchange rate were somewhat lower than the predicted rates for sinomenine at lower temperatures. When the load occurred at a higher temperature, the time was shorter because of the acceleration of molecular thermal motion; the loading curve was similar to that of type one (Figure 2B).
Figure 5 lnk1 versus molecular weight at 25°C, plotted with the molecular weight of model drugs loading.
As an ionic reaction in nature, since the negative electric charges of the exchange groups were definite, the charge density of the model drugs might impact on loading behavior,26 that is, drug alkalinity. The molecular weight of tramadol and atenolol were nearly the same, but the pKa of the former was larger, which enhanced the affinity between the drug and the fiber, that made the load faster.
The differences of logP among the drugs did not cause any profound differences in the load amount. In a previous study, Hänninen et al13 also found similar results in the Smopex® DS-218v fiber (Johnson Matthey, Royston, UK).
Framework of drug structure
Helfferich noted that, “The ion exchanger prefers counter ions with organic groups which resemble the components of the matrix. For example, resins usually prefer counter ions with aromatic groups to those with aliphatic groups”.1,27 Here, more attention was paid on the framework of the drug structures, not on logP. The loading amounts in this study were increased notably (P<0.05) as the ring number increased. At 25°C, the loading amount for atenolol, with one ring in its structure, was the lowest (2.17 mmol/g), while that for sinomenine, which comprises four rings, was the highest (2.90 mmol/g). Rings in molecular structures strengthen the affinity between the drug and the fiber.
Morphology of ion-exchange fibers
The scanning electron micrographs of the ion-exchange fibers are shown in Figure 6. The surface of ZB-1 was composed of countless etched bulges. After being loaded, firstly, the crystals of the drug disappeared, ie, the drug in the fiber was in the amorphous state; secondly, the fiber surface became smoother due to the drug film covering it.
Figure 6 Scanning electron micrographs of ZB-1 (A, B) and Atenolol-fiber complexes (C, D) with different amplified times.
Drug release from ion-exchange fibers
The in vitro release of the five drugs from the ion-exchange fibers was studied by carrying out their dissolution in USP dissolution apparatus 2. The drug–fiber complexes were initially floated onto the surface of water due to their hydrophobicity and gradually sank after more than 6 hours. The floating ability could prolong the gastric retention time of complexes. The influences on drug release were investigated from two aspects: physicochemical properties and external conditions.
Molecular weight and pKa
The release profiles of each drug from the drug–fiber complexes in pH 1.2 HCl solution and pH 6.8 phosphate buffer are shown in Figure 7. The rate of drug release from the fiber was determined by extrapolating the time when 50% (t50%) and 80% (t80%) of the drug in the fiber was released into the dissolution medium (Table 5). Generally, the release rate decreased with increasing molecular weight. Atenolol was released very quickly from the fiber complexes, and the release rate was approximately the same as that of drug powder in pH 1.2 solution, and even faster than that of drug powder in pH 6.8 buffer. Atenolol-fiber complexes preformed an ability of rapid release. The reason for this is that the dissolving rate of atenolol powder is slow due to its strong surface hydrophobicity and comparatively low solubility; however, the highly dispersed state of the drug in the fiber accelerated the release. The other drug–fiber complexes exhibited sustained release, and the extent of this release increased as the molecular weight increased. Steric hindrance made it difficult for the extraction ions to approach the ionic bonds between the small ion-exchange groups and the much larger drug. Meantime, the release rate of tramadol was slower than that of atenolol, illustrating that the stronger affinity caused by higher charge density and ring structure between tramadol and the fiber made it harder to release. In oral administration, additional release control through another method, such as coating, is needed for ion-exchange resins.
Table 5 The time after which 50% or 80% of the drug had been released from the fiber
The release profiles for venlafaxine hydrochloride from the fiber complexes under various external conditions are shown in Figure 8. Different kinds and concentrations of counter ions in the release medium affect the release behavior, while the pH value is independent of it once the concentrations of counter ions in solutions are adjusted by NaCl. The order of the extent of release for the five extraction ions was Ca2+ > Mg2+ > K+ > Na+ > H+. Although each kind of ion has its own special affinity for the ion-exchange fibers, the ability of the divalent ions is about one time greater than that for the monovalent ions, illustrating that the ion exchange is a stoichiometric reaction. When the molar amount of sodium ions was equal, ten-fold, or hundred-fold as compared to the drug ions in the fiber, the release percentages of the drug from the fiber were 17%, 46%, and 81%, respectively. The reason for this is that the increase in the molar amount of counter ions shifts the equilibrium toward drug release. Similarly, the release extent could also become higher as the solution volume increases. Prabhu et al28 reported that the release of diltiazem hydrochloride from resinates is about 40% in pH 1.2 solution in the same apparatus. In comparison, in our work, the release of the drugs from the complexes was more than 80%. The drug dose used was different in the two experiments (30 mg in this work and 120 mg in the previous report). Figure 9 shows the dissolution tests of three doses of diltiazem–fiber complexes. The drug release is irrelevant to the structure; the drug release is determined by the ionic reaction. The release of drug is also not due to the dissolution of drug powder. Once the ionic reaction equilibrium was established between the drugs in fibers and that in release medium, the release was not continued though a good sink condition was maintained in release medium. As the dose decreased, the relative concentration of the extraction solution increased so as to shift the reaction toward drug release and make the release extent higher. Therefore, this dissolution method is more suitable for the release of small doses of drugs from ion-exchange fibers.
Figure 8 The release curves of venlafaxine-fiber complexes in different dissolution mediums.
Figure 9 The release curves of diltiazem-fiber complexes in pH 1.2 solution with different doses (weighed equivalent to 30, 60 and 120 mg diltiazem hydrochloride).
The load and release characteristics of model drugs with ion-exchange fibers was investigated in the present study to lay the groundwork for the application of ion-exchange fibers. Through the development of opposing exchange kinetics, ionic reaction was proved to be the rate-determining step for the loading process. Molecular weight was the most important influential factor for both drug load and release rate. Both of these decreased with increasing molecular weight, ie, a drug that loads quickly is released quickly too. pKa and the ring structure of drugs strengthened the affinity between the drug and fiber, while logP did not cause any profound differences. Different types and concentrations of counter ions or different amounts of complexes in the dissolution medium affect the release behavior, while pH is independent of it. These results could be very useful for predicting the load and release behavior of other drugs with ion-exchange fibers.
Financial support of the National Natural Science Foundation of China (No 81072603) is gratefully acknowledged.
The authors report no conflicts of interest in this work.
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