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Communication

pH-Dependent Release of Insulin from Layer-by-Layer-Deposited Polyelectrolyte Microcapsules

by
Kentaro Yoshida
1,*,
Tetsuya Ono
1,
Yoshitomo Kashiwagi
1,
Shigehiro Takahashi
2,
Katsuhiko Sato
2 and
Jun-ichi Anzai
2
1
School of Pharmaceutical Sciences, Ohu University, 31-1 Misumido, Tomita-machi, Koriyama, Fukushima 963-8611, Japan
2
Graduate School of Pharmaceutical Sciences, Tohoku University, Aramaki, Aoba-ku, Sendai 980-8578, Japan
*
Author to whom correspondence should be addressed.
Polymers 2015, 7(7), 1269-1278; https://doi.org/10.3390/polym7071269
Submission received: 7 May 2015 / Revised: 24 June 2015 / Accepted: 3 July 2015 / Published: 13 July 2015
(This article belongs to the Special Issue Polymers and Polymeric Nanoparticles for Therapy and Imaging)
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Abstract

:
Insulin-containing microcapsules were prepared by a layer-by-layer (LbL) deposition of poly(allylamine hydrochloride) (PAH) and polyanions, such as poly(styrenesulfonate) (PSS), poly(vinyl sulfate) (PVS), and dextran sulfate (DS) on insulin-containing calcium carbonate (CaCO3) microparticles. The CaCO3 core was dissolved in diluted HCl solution to obtain insulin-containing hollow microcapsules. The microcapsules were characterized by scanning electron microscope (SEM) and atomic force microscope (AFM) images and ζ-potential. The release of insulin from the microcapsules was faster at pH 9.0 and 7.4 than in acidic solutions due to the different charge density of PAH. In addition, insulin release was suppressed when the microcapsules were constructed using PAH with a lower molecular weight, probably owing to a thicker shell of the microcapsules. The results suggested a potential use of the insulin-containing microcapsules for developing insulin delivery systems.

Graphical Abstract

1. Introduction

Polyelectrolyte layer-by-layer (LbL) films can be prepared by an alternate and repeated deposition of polymeric materials on a solid surface through electrostatic interactions [1,2], hydrogen binding [3,4], host-guest complexation [5,6], and biological affinity [7]. A recent review has summarized biocompatible LbL films for smart materials [8]. This diversity of methods has led to a variety of materials, including synthetic polymers [9], nanoparticles [10], proteins [11], cells [12], and polysaccharides [13], being used for constructing LbL films. LbL films have been used in sensors [14], separation and purification membranes [15], stimuli-sensitive devices [16,17], and drug delivery systems [18,19]. Hollow microcapsules have also been constructed by coating the surface of microspheres with LbL films followed by dissolution of core material [20,21,22,23,24]. A merit of LbL film-based microcapsules is that whole working process can be carried out in water under mild conditions (i.e., neutral pH at room temperature). Therefore, microcapsules containing unstable compounds, such as proteins and genes, can be successfully prepared [25,26,27].
In this context, we reported that insulin can be built into LbL films by an alternate deposition of polymers and insulin to enable pH-controlled release of insulin [28,29,30]. Biodegradable microspheres were also used as support for depositing insulin LbL films [31]. Insulin was released from the LbL films and microspheres at neutral pH while the release was suppressed at acidic pH, suggesting a possible use of them for developing oral administrations of insulin.
We report here the preparation of insulin-containing LbL microcapsules and their pH-dependent insulin release. The LbL microcapsules were prepared by coating insulin-containing CaCO3 particles with LbL films, followed by dissolution of CaCO3 core in acidic solution.

2. Experimental Section

2.1. Materials

Insulin (Human, recombinant) was purchased from Wako Pure Chemical Industry (Osaka, Japan). Poly(allylamine hydrochloride) (PAH, molecular weight (MW): 1000, 15,000, and 70,000) were acquired from Nittobo Co. (Tokyo, Japan) and used without further purification. Poly(styrene sulfate) (PSS, MW: 500,000), poly(vinyl sulfonate) (PVS, MW: 240,000), and dextran sulfate (DS, MW: 25,000) were obtained from Scientific Polymer Product, Inc. (New York, NY, USA), Nacalai Tesque Co. (Kyoto, Japan), and Tokyo Kasei Co. (Tokyo, Japan), respectively. Tetramethylrhodamine-5-isothiocyanate (TRITC) was obtained from Sigma-Aldrich Co. (St. Louis, MO, USA) and used for preparing TRITC-labeled insulin (TRITC-insulin). TRITC-insulin was synthesized by the coupling reaction of TRITC and insulin according to the reported procedure [32].

2.2. Preparation of LbL Microcapsules

Ten milliliters of 0.2 M CaCl2 (Wako Pure Chemical Industry, Osaka, Japan) solution containing 5 mg of insulin or TRITC-insulin was mixed with 10 mL of 0.2 M (NH3)2CO3 (Wako Pure Chemical Industry, Osaka, Japan) solution containing 40 mg PSS under stirring. The mixture was stirred for 30 min, and the precipitated particles were collected by centrifugation and washed with distilled water. The surface of CaCO3 particles was coated with LbL film by immersing the CaCO3 particles alternately in 0.5 mg mL−1 PAH and 0.5 mg mL−1 polyanion (PSS, PVS, and DS) in 10 mM Tris-HCl buffer (Nacalai Tesque Inc., Kyoto, Japan) containing 150 mM NaCl (Wako Pure Chemical Industry, Osaka, Japan) (pH 7.4) for 15 min. After each deposition, the CaCO3 particles were collected by centrifugation and rinsed in the working buffer for 5 min. Then, LbL film-coated particles were dispersed in excess amount of 0.1 M HCl solution to dissolve the CaCO3 core, and the resulting hollow microcapsules were thoroughly rinsed in 10 mM acetate buffer (pH 3.0) containing 150 mM NaCl. The whole process was carried out at room temperature. The amounts of TRITC-insulin loaded in the microcapsules were found to be 0.23 ± 0.01, 0.13 ± 0.03, and 0.20 ± 0.08 mg in 1 mg of lyophilized (PAH/PSS)5, (PAH/PVS)5 and (PAH/DS)5 microcapsules, respectively.

2.3. AFM and SEM Images of CaCO3 Particles and Microcapsules

A suspension of CaCO3 particles with and without film coating or LbL microcapsules was dispersed on a glass slide, which had been cleaned using chromic acid/sulfuric acid mixture, and then dried in a desiccator for scanning electron microscope (SEM) (S-3200N, Hitachi Co., Tokyo, Japan) and atomic force microscope (AFM) (SPM-9600, Shimadzu, Japan) observation. The SEM samples were sputtered with platinum. AFM images were taken in contact mode using a microcantilever (OMCL-TR800PSA-1 (Olympus, Tokyo, Japan) at room temperature in air.

2.4. ζ-Potential of LbL Film-Coated CaCO3 Particles

The ζ-potential of LbL film-coated CaCO3 particles was recorded using a ζ-potential analyzer (Zeecom/ZC-2000, Microtec Co., Funabashi, Japan) at pH 7.0.

2.5. Evaluation of Insulin Release from Microcapsules

The release of insulin was evaluated in 10 mM acetate buffer at pH 1.4–6.0 or in 10 mM Tris buffer at pH 7.0–9.0 (all buffer solutions contained 150 mM NaCl). TRITC-insulin-containing microcapsules were suspended in the buffer solutions under gentle stirring. The dispersion was centrifuged occasionally and the fluorescence intensity of the supernatant was recorded at 530 nm (excitation: 488 nm) to estimate the concentration of TRITC-insulin released from the microcapsules.

3. Results and Discussion

3.1. Preparation of Insulin-Containing Microcapsules

Insulin-containing microcapsules were prepared by depositing LbL films on the surface of insulin-loaded CaCO3 particles followed by dissolution of CaCO3 core, as illustrated in Figure 1. In this protocol, insulin is encapsulated in the cavity in the form of insulin-PSS aggregates created through electrostatic interactions because the microcapsules were prepared by using CaCO3 particles containing PSS and insulin. The preparation of microcapsules was evaluated by measuring ζ-potential of CaCO3 particles coated with LbL film, as well as SEM and AFM images.
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Figure 1. A schematic illustration of the preparation of insulin-containing microcapsule.
Figure 1. A schematic illustration of the preparation of insulin-containing microcapsule.
Polymers 07 01269 g001
Figure 2 shows plots of typical ζ-potential of CaCO3 particles coated with PAH/PSS, PAH/PAA, and PAH/DS films. Positive values were obtained when the outermost layer was PAH, while the ζ-potentials were negative when the outermost was PSS, PAA, or DS. These results show that electric charges on the surface of the CaCO3 particles coated with LbL films alternated between positive to negative according to the type of the outermost material, which demonstrates successful deposition of LbL films on the CaCO3 particles.
Polymers 07 01269 g002 1024
Figure 2. Typical ζ-potential of CaCO3 particles coated with PAH/PSS (●), PAH/PVS (▲), and PAH/DS (♦) films. The outermost is PSS, PVS, or DS when the number of bilayers is an integer.
Figure 2. Typical ζ-potential of CaCO3 particles coated with PAH/PSS (●), PAH/PVS (▲), and PAH/DS (♦) films. The outermost is PSS, PVS, or DS when the number of bilayers is an integer.
Polymers 07 01269 g002
Figure 3 shows SEM images of CaCO3 microparticles, (PAH/PSS)5 film-coated CaCO3 particles, and (PAH/PSS)5 hollow microcapsules. Spherical CaCO3 particles 3–6 μm in diameter are clearly seen in Figure 3A. Figure 3B is a SEM image of (PAH/PSS)5 film-coated CaCO3 particles. The (PAH/PSS)5 film-coated CaCO3 particles exhibited a slightly smooth surface compared to uncoated CaCO3 particles, suggesting a successful deposition of (PAH/PSS)5 film on CaCO3 particles. The (PAH/PSS)5 film-coated CaCO3 particles were dispersed in 0.1 M HCl solution to dissolve the CaCO3 core and rinsed in a buffer solution of pH 3.0. Figure 3C shows a SEM image of dried hollow (PAH/PSS)5 microcapsules thus prepared. The dried microcapsules are spreading onto the substrate with typical folds. Similar SEM images for dried LbL microcapsules have often been reported [33,34].
Polymers 07 01269 g003 1024
Figure 3. SEM images of CaCO3 particles containing insulin and PSS (A), (PAH-PSS)5 film-coated CaCO3 particles (B); and dried (PAH/PSS)5 microcapsules (C).
Figure 3. SEM images of CaCO3 particles containing insulin and PSS (A), (PAH-PSS)5 film-coated CaCO3 particles (B); and dried (PAH/PSS)5 microcapsules (C).
Polymers 07 01269 g003
To further verify the microcapsule preparation, AFM images of dried (PAH/PVS)5 microcapsules with and without insulin loading were recorded (Figure 4). The vertical sectional profile of the empty microcapsule and the insulin-loaded ones were different from each other. The shell thickness of the empty microcapsule was estimated to be approximately 30 nm at its thinnest portion (Figure 4A). Interestingly, on the other hand, the dried insulin-containing microcapsule was thicker due to insulin-PSS aggregates loaded in the capsule (Figure 4B). Thus, the SEM and AFM images ensure successful preparation of (PAH/PSS)5 microcapsules containing insulin.
Polymers 07 01269 g004 1024
Figure 4. AFM images of dried (PAH/PVS)5 microcapsule without insulin loaded (A) and microcapsules containing insulin-PSS aggregates (B). The sectional profiles a–b and c–d show thickness of the dried microcapsules.
Figure 4. AFM images of dried (PAH/PVS)5 microcapsule without insulin loaded (A) and microcapsules containing insulin-PSS aggregates (B). The sectional profiles a–b and c–d show thickness of the dried microcapsules.
Polymers 07 01269 g004

3.2. pH-Dependent Release of Insulin from Microcapsules

The release of insulin from the LbL microcapsules was studied by means of fluorescence spectroscopy using microcapsules containing TRITC-insulin. The time course of TRITC-insulin release from (PAH/PSS)5, (PAH/PVS)5 and (PAH/DS)5 microcapsules is shown in Figure 5. The release of TRITC-insulin from the microcapsules significantly depended on pH of the medium. The TRITC-insulin release was suppressed in acidic media (pH 1.4–3.0) for all microcapsules tested. The formation of TRITC-insulin-PSS aggregates in the microcapsules may be responsible for the suppressed release in the acidic media. TRITC-insulin and the anionic PSS should form aggregates through electrostatic interactions at pH 5.0 or lower because insulin contains a net positive charge (the isoelectric point of insulin is 5.4 [35]). In fact, we have previously found that insulin binds to anionic polymers to form aggregates in acidic media [28,29]. It is plausible that the high-molecular-weight aggregates could not be transported across the shell of the microcapsules.
Polymers 07 01269 g005 1024
Figure 5. TRITC-Insulin release from (PAH/PSS)5 (A); (PAH/PVS)5 (B) and (PAH/DS)5 (C) microcapsules in the media with different pH. The solution pH was pH 1.4 (▲), pH 3.0 (△), pH 5.0 (■), pH 7.4 (○), and pH 9.0 (●).
Figure 5. TRITC-Insulin release from (PAH/PSS)5 (A); (PAH/PVS)5 (B) and (PAH/DS)5 (C) microcapsules in the media with different pH. The solution pH was pH 1.4 (▲), pH 3.0 (△), pH 5.0 (■), pH 7.4 (○), and pH 9.0 (●).
Polymers 07 01269 g005
In contrast, TRITC-insulin released rapidly from (PAH/PVS)5 and (PAH/DS)5 microcapsules at pH 7.4 and 9.0, while the release was slower for (PAH/PSS)5 microcapsules. The enhanced release at neutral and basic pHs results from dissociation of TRITC-insulin-PSS aggregates in the neutral and basic media, in which insulin is negatively charged. It is reasonable that TRITC-insulin molecules can be transported out of the capsules more effectively than the aggregates. The release of TRITC-insulin was higher in pH 9.0 medium than in pH 7.4 solution. It is likely that, at pH 7.4, a part of TRITC-insulin was electrostatically adsorbed into the PAH layer at the inner surface of the microcapsule shell. The electrostatic interactions between TRITC-insulin and PAH at pH 9.0 may be weaker than those at pH 7.4 owing to reduced positive charges of PAH. It should be noted here that Bäumler and coworkers reported that LbL microcapsules consisting of PAH and PSS exhibited no pH dependent permeability for macromolecules such as human albumin [36]. In addition, Mauser and coworkers reported that PAH-poly(methacrylic acid) microcapsules exhibited pH-independent swelling in the pH range from 2.7 to 11.5 [37]. These findings strongly suggest that pH-dependent release of TRITC-insulin from the microcapsules should be attributed mainly to pH-dependent formation/decomposition of TRITC-insulin/PSS aggregates in the microcapsules, as illustrated in Figure 1. A similar pH-dependent insulin release from LbL microcapsules composed of alginic acid and chitosan has been reported by Ye and coworkers [38]. The amount of TRITC-insulin released from (PAH/PSS)5 microcapsules was smaller than those released from (PAH/PVS)5 and (PAH/DS)5 microcapsules. This may originate from different porosity of the microcapsule shell, i.e., the aromatic ring in PSS may result in tighter binding to PAH in the microcapsule shell.
Figure 6 shows release profiles of TRITC-insulin from (PAH/PSS)5 microcapsules constructed with PAHs of different molecular weights. The release of TRITC-insulin was accelerated at pH 7.4 as compared to that in acidic media irrespective of molecular weights of PAH. Interestingly, TRITC-insulin release from the microcapsules constructed from low-molecular-weight PAH (MW: 1000) was slightly slower than those from the microcapsules composed of higher-molecular-weight PAHs. These results show that permeability or porosity of the microcapsule shell depends on the molecular weight of PAH used. In this context, it has been reported that LbL films fabricated using low-molecular-weight polymers are thicker than those constructed using higher-molecular-weight ones [39,40]. The (PAH/PSS)5 microcapsules constructed with PAH of lower molecular weight may consist of thicker shell, resulting in slower release of TRITC-insulin.
Polymers 07 01269 g006 1024
Figure 6. The effect of molecular weight of PAH on the release of TRITC-Insulin from (PAH/PSS)5 microcapsules. The average molecular weight of PAH used was 1000 (A), 15,000 (B), and 70,000 (C).
Figure 6. The effect of molecular weight of PAH on the release of TRITC-Insulin from (PAH/PSS)5 microcapsules. The average molecular weight of PAH used was 1000 (A), 15,000 (B), and 70,000 (C).
Polymers 07 01269 g006

4. Conclusions

We have prepared polyelectrolyte microcapsules containing insulin by coating insulin-containing CaCO3 particles with LbL films followed by CaCO3 dissolution. The release of insulin from the prepared microcapsules was accelerated at pH 7.4 and 9.0 while suppressed at pH 1.4–5.0, as a result of formation of insulin-PSS aggregates in the microcapsules. In addition, insulin release from (PAH-PSS)5 microcapsules constructed using PAH of lower molecular weight was slower than that from high-molecular-weight PAH-based microcapsules. Insulin-containing polyelectrolyte microcapsules prepared in this study may be useful in the development of insulin delivery systems.

Acknowledgments

This work was partially supported by the Japan Society for the Promotion of Science Grants-in-Aid for Scientific Research (grant numbers 26860111 and 24390006). The authors thank Toshinori Ito (Ohu University) for his help in manuscript preparation.

Author Contributions

All authors were involved in the experimental works and the manuscript was prepared by Kentaro Yoshida and Jun-ichi Anzai.

Conflicts of Interest

The authors declare no conflict of interest.

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Yoshida, K.; Ono, T.; Kashiwagi, Y.; Takahashi, S.; Sato, K.; Anzai, J.-i. pH-Dependent Release of Insulin from Layer-by-Layer-Deposited Polyelectrolyte Microcapsules. Polymers 2015, 7, 1269-1278. https://doi.org/10.3390/polym7071269

AMA Style

Yoshida K, Ono T, Kashiwagi Y, Takahashi S, Sato K, Anzai J-i. pH-Dependent Release of Insulin from Layer-by-Layer-Deposited Polyelectrolyte Microcapsules. Polymers. 2015; 7(7):1269-1278. https://doi.org/10.3390/polym7071269

Chicago/Turabian Style

Yoshida, Kentaro, Tetsuya Ono, Yoshitomo Kashiwagi, Shigehiro Takahashi, Katsuhiko Sato, and Jun-ichi Anzai. 2015. "pH-Dependent Release of Insulin from Layer-by-Layer-Deposited Polyelectrolyte Microcapsules" Polymers 7, no. 7: 1269-1278. https://doi.org/10.3390/polym7071269

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