Peptide-directed assembly of functional supramolecular polymers for biomedical applications: electroactive molecular tongue-twisters (oligoalanine–oligoaniline–oligoalanine) for electrochemically enhanced drug delivery

We report the preparation and characterization of films of electroactive supramolecular polymers based on non-electroactive oligoalanines and electroactive oligoanilines. Fibroblasts adhered to and proliferated on the films, and the delivery of the clinically relevant anti-inflammatory drug dexamethasone phosphate could be enhanced upon the application of an electrical stimulus. Technologies that enable precise control of the amount of drugs in the blood stream or specific tissues facilitate the maintenance of the amount of drug within the therapeutic window, and controlling the chronopharmacology of a drug is particularly useful for the treatment of diseases with specific chronobiologies (e.g. cancers, infectious diseases, pain). 1-3 Drug delivery systems that respond to chemical (e.g. enzymes, pH) or physical (e.g. electric/magnetic fields, light, pH, temperature) stimuli are potentially applicable for the treatment of such conditions. 2,3 Here we report the application of electroactive polymers (EAPs) that allow drug delivery enhanced by the application of an electrical stimulus. EAPs have interesting electronic and optical properties and are currently investigated for use in electronic 4 and biomedical 5-8 industries. Polyaniline, polypyrrole and polythiophene derivatives are the EAPs most commonly investigated for biomedical applications. 9,10 In recent years block copolymers incorporating electroactive blocks (frequently oligoaniline-based polymers doped with camphorsulfonic acid, CSA, Fig. 1) have been investigated for use as electroactive tissue scaffolds

We report the preparation and characterization of films of electroactive supramolecular polymers based on nonelectroactive oligoalanines and electroactive oligoanilines. Fibroblasts adhered to and proliferated on the films, and the delivery of the clinically relevant anti-inflammatory drug dexamethasone phosphate could be enhanced upon the application of an electrical stimulus.
Technologies that enable precise control of the amount of drugs in the blood stream or specific tissues facilitate the maintenance of the amount of drug within the therapeutic window, and controlling the chronopharmacology of a drug is particularly useful for the treatment of diseases with specific chronobiologies (e.g. cancers, infectious diseases, pain). [1][2][3] Drug delivery systems that respond to chemical (e.g. enzymes, pH) or physical (e.g. electric/magnetic fields, light, pH, temperature) stimuli are potentially applicable for the treatment of such conditions. 2,3 Here we report the application of electroactive polymers (EAPs) that allow drug delivery enhanced by the application of an electrical stimulus. EAPs have interesting electronic and optical properties and are currently investigated for use in electronic 4 and biomedical [5][6][7][8] industries. Polyaniline, polypyrrole and polythiophene derivatives are the EAPs most commonly investigated for biomedical applications. 9,10 In recent years block copolymers incorporating electroactive blocks (frequently oligoaniline-based polymers doped with camphorsulfonic acid, CSA, Fig. 1) have been investigated for use as electroactive tissue scaffolds capable of the electrical stimulation of the cells inhabiting them, 11 and as materials for electrochemicallytriggered drug delivery. 12 Polyaniline-and polypyrrole-based systems have been used to deliver a variety of drugs, including; adenosine triphosphate, dexamethasone phosphate (DMP, Fig. 1), DNA, dopamine, nerve growth factor and N-methylphenothiazine, as discussed in greater depth in reviews by Garg and co-workers 13 and Ndesendo and coworkers. 14 Here we report the application of electroactive molecular tongue-twisters (MTTs) based on electroactive oligoanilines and nonelectroactive oligoalanines (i.e. oligoalanine-oligoanilineoligoalanine) for the delivery of dexamethasone phosphate. The MTTs are solution processable and assemble into hierarchically structured supramolecular polymers 15-21 because of hydrogen bonding interactions between the oligoalanines in the solid state. Such supramolecular polymers have prospects for the preparation of conformal electroactive coatings for implantable biomaterials. The electrochemically responsive blocks of oligoaniline were terminated with amines which enabled the initiation of ring-opening polymerization of α-amino acid N-carboxyanhydrides, 22 in this case alanine N-carboxyanhydride (Ala-NCA). The oligoanilines (tetraaniline and hexaaniline) were prepared using the methodology described in the literature (Scheme S1), 23,24 as was Ala-NCA (Scheme S2), 25 and they were polymerized at room temperature in anhydrous DMF, precipitated in diethyl ether and dried under vacuum (Scheme 1). The hexafluoroisopropanol (HFIP)-soluble fraction was extracted and dried under vacuum, yielding off-white solids that were used without further purification; tetraaniline-based molecular tongue-twister 1 (MTT1, oligoalanine-tetraaniline-oligoalanine) and hexaaniline-based molecular tongue-twister 2 (MTT2, oligoalanine-hexaaanilineoligoalanine), that are depicted in Scheme 1. The success of the polymerizations was confirmed spectroscopically. The presence of characteristic peaks in the IR spectra ( Fig. S1) for amides and oligoanilines (shoulders at ca. 1541 cm -1 (C=N and C=C stretches) and 1496 cm -1 (C-C stretching)). 26 NMR in deuterated HFIP suggested that MTT1 incorporated ca. 10 alanine units per tetraaniline (in line with the synthesis), whereas MTT2 incorporated 26 alanine units per hexaaniline, suggesting that polymers based on the less soluble hexaaniline required a greater number of alanines for the resulting polymer to be soluble. Yet their low solubility hampered determination of the molecular weight distributions via standard techniques such as GPC/SEC, light scattering or MALDI-TOF mass spectrometry.
Casting dilute solutions of the MTTs in HFIP allowed the preparation of water insoluble films of a few µm in thickness with µm scale roughness (Ra) or root mean square roughness (Rq) as determined by profilometry (Table 1). Undoped films were blue, whereas films doped with CSA (10 wt %) were green.
[Note to editors, please insert Table 1 near here. Title: Table 1 Surface and physicochemical properties of the polymer films. Footnote: a As determined by XRD. b Not applicable.] IR spectra of the films recorded in attenuated total reflectance (ATR) mode revealed subtle differences in the hierarchical supramolecular assembly of the polymers, with evidence of both α-helices and βsheets in all spectra (Fig. S1), [27][28][29] with the α-helices induced by HFIP and the intermolecular β-sheets being partially responsible for the insolubility of the polymers in water (also observed in oligoalanine-rich proteins). [30][31][32] The oligoalanine blocks in undoped films of MTT1 assembled into both α-helices (amide I, 1649 cm -1 ) and β-sheets (amide I, 1692 cm -1 ; amide II, 1530 and 1517 cm -1 ). Doping MTT1 with CSA altered the assembly of the MTTs, yet both α-helices (amide I, 1649 cm -1 ; amide II, 1543 cm -1 ) and β-sheets (amide I, 1690 cm -1 ; amide II, 1530 and 1514 cm -1 ) were present, although the β-sheet content was clearly reduced. The oligoalanine blocks in undoped films of MTT2 were predominantly amorphous (amide I, 1646 cm -1 ; amide II, 1533 cm -1 ) with some β-sheets (amide I, 1629 cm -1 ; amide II, 1518 cm -1 ). Doping MTT2 with CSA reduced the β-sheet content (weak amide I, 1690 cm -1 ; weak amide II, 1530 and 1514 cm -1 ), and the chains were predominantly amorphous (amide I, 1646 cm -1 ; amide II, 1535 cm -1 ). [27][28][29] Wide angle XRD patterns for the films (Fig. S2) 33 and were clearly more crystalline (higher Xc) than those of CSA-doped MTT1 ( Fig. S2 and Table 1) because the presence of the bulky CSA anions interfered with the assembly of the oligoaniline blocks. 12,34 Films of MTT2 were amorphous in both the undoped or CSA-doped state. The conductance of films of the MTTs were measured as previously reported. 12 Undoped films of tetraaniline-based MTT1 had a conductivity of ca. 1.6 x 10 -8 S cm -1 , that was moderately increased by doping with CSA to ca. 2.5 x 10 -8 S cm -1 (Table 1). Undoped films of hexaaniline-based MTT2 had a conductivity of ca. 7.3 x 10 -8 S cm -1 , that was moderately increased by doping with CSA to ca. 8.6 x 10 -8 S cm -1 ( Table 1). The higher conductivity of MTT2-based films was because of the greater level of conjugation in the backbone of hexaaniline than in tetraaniline. These conductivities are lower than those of mammalian tissues (typically ≥ 10 -4 S cm -1 ) 35-37 that should enable the controlled delivery of a drug upon the application of an electrical potential to the EAPs. We studied the release profiles of the anti-inflammatory drug DMP from MTT films into phosphate buffered saline (PBS) in the absence or presence of an electrical stimulus using the experimental setup depicted in Fig. S3. Cyclic voltammograms (Fig. S4) of the DMPdoped films of MTT1 presented a redox process at ca. 0.26 V (leucoemeraldine to emeraldine 1 transition), whereas those for MTT2 presented a process at 0.42 V (emeraldine 1 to emeraldine 2 transition), confirming the greater conjugation in the backbone of the longer oligomers (potentials are reported vs. a Ag/AgCl reference electrode calibrated with ferrocenemethanol). We monitored the release of DMP at specific time points spectroscopically, using its characteristic UV absorption at 242 nm. DMP loadings in the films were at 10 wt%. Passive release from films of MTT1 (Fig. 2, grey checked bars) and MTT2 (Fig. 2, black checked bars) was observed, however, release was moderately enhanced by the application of an electrical stimulus ( Fig. 2; MTT1 grey bars, MTT2 black bars), typically by 10 to 20% for the first five rounds of stimulation, after which the profiles for MTT1 in the absence/presence of stimulation was observed to be equal which suggests that it is more prone to spontaneous de-doping than the more highly conjugated MTT2. We believe that the release profiles could be improved by tuning both the length of the electroactive oligoaniline, the ratio of electroactive to non-electroactive peptide blocks, and the identity of the non-electroactive peptide (i.e. composition and sequence of amino acids). Analogous electroactive block copolymers incorporating CSA-doped oligoalanines have been shown to support the adhesion of a variety of cells including fibroblasts, keratinocytes, osteoblasts, PC12 cells and Schwann cells. 11 We found that cell viability for the HDFs cultured on the films of MTTs was comparable, and indeed somewhat better than TCP controls (Fig. 3A). However, the adhesion of human dermal fibroblasts (HDFs) to films of undoped or CSA-doped MTT1 was poor by comparison with commercially available Corning Costar® tissue culture plate (TCP) controls as determined using the AlamarBlue® assay (Fig. 3B), and cells had relatively rounded morphologies indicative of poor cell adhesion (Fig. 4 A and B), particularly by comparison with TCP controls (Fig. S5). Interestingly, HDF adhesion to films of undoped or CSA-doped MTT2 was moderately better, with cells more likely to adopt a spread morphology (Fig. 4 C and D). For certain applications, non celladhesive biomaterials are interesting candidates, such as for the manufacture of anti-adhesion membranes; 38 however, for other applications (e.g. tissue scaffolds) cell adhesion is beneficial. We believe that cell adhesion could be improved by incorporating cell adhesive peptides (e.g. the ubiquitous RGD) 10,16,[39][40][41] in the backbone of such EAPs.

Conclusions
Herein we described electrically-triggered drug release from electroactive molecular tongue-twisters (i.e. oligoalanineoligoaniline-oligoalanine). The electroactive ABA block copolymers based on A) non-electroactive oligoalanines, and B) electroactive blocks of oligoanilines, represents a novel platform for drug delivery. The physicochemical properties of the films were characterized by various techniques, and we found that hexaaniline-based MTT2 was more conductive and appeared to be more electrochemically stable towards de-doping than tetraaniline-based MTT1. While HDFs cultured on the surfaces of such films adhered weakly, this could be improved by incorporating cell-adhesive moieties. [39][40][41] While imperfect, such EAPs represent valuable lead structures for the development of materials that enable us to deliver drugs with clinically relevant chronopharmacologies, and facilitate the treatment of conditions with specific chronobiologies (e.g. infectious diseases, pain). We believe that it should be possible to rationally control the release profiles and cell-biomaterial interactions by tuning the length of the electroactive oligoaniline, the ratio of electroactive to non-electroactive peptide blocks, and the identity of the non-electroactive peptide (i.e. composition and sequence of amino acids). Specifically, increasing the length of the oligoalanine segments should render them more conductive and electrochemically stable (i.e. less likely to be spontaneously de-doped in biological milieu). The composition and sequence of amino acids in the non-electroactive peptide dictate the charge and hydrophobicity of the materials, which play roles in the self-assembly of the peptides (i.e. hydrogen bonding interactions, electrostatic interactions) and protein deposition on their surfaces which may be important for cell adhesion. Cell-biomaterial interactions could be controlled through the inclusion of cell-adhesive peptides (e.g. RGD, YIGSR, KQAGDV, KHIFSDDSSE, KRSR), [39][40][41] and protease-labile domains (APGL, VRN, or indeed oligoalanines such as those in the backbone of MTT1 and MTT2 that are degraded by elastase), 40 potentially facilitate their degradation in vivo. Furthermore, molecules with higher ratios of electroactive to non-electroactive peptide blocks should be more conductive, and the inclusion of charged amino acids may facilitate the inclusion of cationic drugs (antibacterials, antiarrhythmics, etc.). 42