C O M M U N I C A T I O N S
Figure 2. SEM image of microparticles synthesized by polymerization of
acrylamide (I) with the bisacrylamide acetal cross-linker (II).
Figure 1. pH-dependent release of FITC-Albumin from acid-degradable
hydrogels (data points are an average of three experiments).
shown in Figure 2; the particle size varies between 1 and 10 µm,
and the particles are therefore of a size appropriate for their
phagocytosis by antigen presenting cells.
The protein-loaded hydrogels and microgels based on acid
cleavable acetal cross-linkers are expected to release their contents
under the mild acidic conditions found in lysosomes, tumors, and
sites of inflammation. As a result, such cross-linkers should find
applications as lysosomal escape promoters and more generally in
the areas of tumor drug delivery, biomaterial coatings, and in the
development of vaccine and DNA delivery systems.
Protein-loaded hydrogels were prepared using II, acrylamide (I),
and a fluorescently labeled protein (FITC-Bovine Serum Albumin
(BSA)). Encapsulation was carried out by copolymerizing II (60
mg/mL) with I (200 mg/mL) in the presence of FITC-BSA (1 mg/
mL) in PBS buffer. This hydrogel was washed with PBS (pH 8.5)
buffer; analysis of the washing solution demonstrated essentially
quantitative gel entrapment of the FITC-BSA, suggesting that the
pore size of this gel, at this cross-linking ratio, is smaller than 3.48
nm (the Stokes radius of bovine albumin).2c As expected from the
molecular design of the gel, the rate of protein release was found
to be pH dependent. At pH 5.0, the acetal cross-links hydrolyze,
rapidly transforming the gel into a soluble polymer, and the
encapsulated protein is completely released within 2 h (see Figure
1). Gel electrophoresis of the released protein confirmed that it was
not significantly modified by either the encapsulation or the
hydrolysis procedures (see Supporting Information). At pH 7.4,
release of the entrapped protein is significantly slower as only 5%
of the encapsulated protein is released after 2 h, and 96 h was
required for the hydrogel to completely release its contents (Figure
1). The equilibrium water content, at this cross-linking ratio, is 5.1
mL of water per gram of gel.
The bisacrylamide acetal cross-linker was also used to synthesize
acid-degradable micron-sized hydrogels (microgels). Micron-sized
materials that decompose under acidic conditions are of great
interest because they can induce a colloid osmotic disruption of
phagosomes and deliver macromolecules into the cytoplasm of
antigen presenting cells.7
Microgel particles were prepared by inverse microemulsion
polymerization using I and II as co-monomers. Given the unusual
combination of monomers, several different polymerization pro-
cedures involving different combinations of organic phases and
blends of surfactant had to be tried.2a,8 Inverse emulsion polymer-
izations with toluene/chloroform as the continuous phase and
pluronic F-68 as the surfactant were unsuccessful, likely due to
the high solubility of II in toluene/chloroform. However, particles
could be obtained using hexane (4.0 g) as the continuous phase,
dioctyl sulfosuccinate (0.506 g) and Brij 30 (0.16 g) as the
surfactants, and an aqueous phase (5 mL, pH 8.4, 100 mM
phosphate buffer) containing 40 mg (0.5 mmol) of acrylamide and
22 mg (0.061 mmol) of II. An SEM image of these particles is
Acknowledgment. The Center for New Directions in Organic
Synthesis is supported by Bristol-Myers Squibb as Sponsoring
Member and Novartis as a Supporting Member. Financial support
of this research by the Biomolecular Program of the E. O. Lawrence
Berkeley National Laboratory (Department of Energy, Basic Energy
Sciences) is acknowledged with thanks. We would also like to thank
Dr. Thomas Rohr for help with SEM images and Amish Patel for
help with the protein gels.
Supporting Information Available: Experimental details of the
synthesis of II, hydrogel synthesis, and protein release studies (PDF).
This material is available free of charge via the Internet at http://
pubs.acs.org.
References
(1) Park, K.; Shalaby, W. S.; Park, H. Biodegradable Hydrogels for Drug
DeliVery; Technomic Publishing Co.: Lancaster, PA, 1993.
(2) (a) Ekman, B.; Lofter, C.; Sjoholm, I. Biochemistry 1976, 15, 5115-
5120. (b) Sawhney, A.; Pathak, C.; Hubbell, J. Macromolecules 1993,
26, 581-587. (c) Sanxia, L.; Anseth, K. S. Macromolecules 2000, 33,
2509-2515. (d) Dijk-Wolthius, W. N. E.; et al. Macromolecules 1997,
30, 4639-4645.
(3) (a) Helmlinger, G.; Sckell, A.; Dellian, M.; Forbes, N. S.; Rakesh, K.
Jain. Clin. Cancer Res. 2002, 8, 1284-1291. (b) Trevani, S.; Andonegui,
G.; Giordano, M.; Lopez, D.; Gamberale, R.; Minucci, F.; Geffner, J. R.
J. Immunol. 1999, 162, 4849-57.
(4) Park, T. G. Biomaterials 1999, 20, 517-521. Kim, I. Y.; et al. J. Appl.
Polym. Sci. 2002, 85, 2661-2666.
(5) Sassi, A. P.; Shaw, A. J.; Han, S. M.; Blanch, H. W.; Prausnitz, J. M.
Polymer 1996, 11, 2151-2164.
(6) Fife, T.; Jao, L. J. Org. Chem. 1965, 30, 1492-1495.
(7) Lynn, D. M.; Mansoor, A.; Langer, R. Angew. Chem., Int Ed. 2001, 40,
1707-1710.
(8) Daubreese, C.; Grandfils, R.; Jerome, P. H.; Teyssie, P.; Goethals, P.;
Schacht, E. J. Pharm. Pharmacol. 1993, 45, 1018-1023.
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