Molecular Recognition and Immobilization of Ligand-Conjugated

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Molecular Recognition and Immobilization of Ligand Conjugated Redox-Responsive Polymer Nanocontainers Wilke De Vries, Matthias Tesch, Armido Studer, and Bart Jan Ravoo ACS Appl. Mater. Interfaces, Just Accepted Manuscript • DOI: 10.1021/acsami.7b15516 • Publication Date (Web): 15 Nov 2017 Downloaded from http://pubs.acs.org on November 17, 2017

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ACS Applied Materials & Interfaces

Molecular Recognition and Immobilization of Ligand Conjugated Redox-Responsive Polymer Nanocontainers Wilke C. de Vries, Matthias Tesch, Armido Studer, and Bart Jan Ravoo* Organic Chemistry Institute and Center for Soft Nanoscience, Westfälische WilhelmsUniversität Münster, Corrensstr. 40, D-48149 Münster, Germany KEYWORDS: nanocontainer – self-assembly – molecular recognition – surface design – stimulus-responsive – immobilization

ABSTRACT: We present the preparation of ligand conjugated redox-responsive polymer nanocontainers by the supramolecular decoration of cyclodextrin vesicles with a thin redoxcleavable polymer shell that displays molecular recognition units on its surface. Two widely different recognition motifs (mannose–Concanavalin A and biotin–streptavidin) are compared and the impact of ligand density on the nanocontainer surface as well as an additional functionalization with non-adhesive poly(ethylene glycol) is studied. Aggregation assays, dynamic light scattering, and a fluorometric quantification reveal that the molecular recognition of ligand conjugated polymer nanocontainers by receptor proteins is strongly affected by the multivalency of interactions and the association strength of recognition motif. Finally, microcontact printing is used to prepare streptavidin-patterned surfaces and the specific

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immobilization of biotin conjugated nanocontainers is demonstrated. As a prototype of a nanosensor, these tethered nanocontainers can sense a reductive environment and react by releasing a payload.

Introduction The rational design of the surface decoration of nanoparticles allows a versatile modulation of interactions among nanoparticles and enables a tunable interaction with their environment. Such sophisticated nanostructures have found widespread applications including targeted delivery,1,2 sensing3 and imaging4. In general, two approaches can be used to engineer the surface decoration of nanoparticles: (1) Functional units can be included during synthesis of the nanomaterials as for example in the self-assembly of (endgroup-)functionalized copolymers.5,6 (2) The surface can be designed by post-synthetic approaches such as physical adsorption7–9 or by chemical conjugation10,11. Among the various motifs for surface decoration, the functionalization of nanoparticles with ligands facilitates the recognition by proteins via ligand-receptor binding and results in a highly specific interaction of the nanoparticles with their environment. In nature, for example the recognition and adhesion of cells as well as the infection of cells with viruses are mainly driven by carbohydrate-protein interactions. Proteins that bind to a densely arranged coating of polysaccharides on the cell surface (“glycocalix”) are termed lectins and typically bind in a multivalent fashion, whereby the association constant Ka for a single carbohydratelectin complex usually is 103-104 M-1.12,13 To mimic and study these multivalent interactions, the self-assembly

of

carbohydrate

conjugated

polymers,

so-called

glycopolymers,

into

nanostructures exhibiting multiple carbohydrate ligands on their surface and their multivalent interplay with lectins gained increasing interest in the past.14-16 Amongst others, these platforms have been utilized in drug delivery as a promising approach to target specific cells.9,17–19


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Considering surface modifications where a highly robust and selective conjugation is desired, the recognition of the small vitamin biotin by the tetrameric protein streptavidin (STA) constitutes a widely-used ligand-receptor pair.5,20 The very high association constant of Ka ~ 1015 M-1 represents the strongest noncovalent biological interaction known and has resulted in extensive use in the field of nanodevices and surface functionalized nanostructures.21–23 Recently,

we have introduced novel redox-responsive nanocontainers applying a

supramolecular stabilization of vesicles by the self-assembly of a redox-responsive polymer shell around the vesicle templates. These disulfide crosslinked polymer shelled vesicles (PSVSS) can recognize a reducing microenvironment and react by releasing hydrophilic payloads, for example inside the reductive intracellular environment.24 Given the potential and significance of surface functionalized responsive materials, we herein introduce a method for the surface functionalization of PSVSS. Importantly, PSVSS represent an ideal scaffold for the conjugation of bioactive ligands since their thin and flexible polymer shell is easily accessible. To this end, we carefully design the surface properties of PSVSS by decorating them with carbohydrate or biotin ligands as well as with short poly(ethylene glycol) (PEG) chains to further stabilize them. These nanocontainers should be specifically recognized by corresponding proteins and the effect of the different recognition motifs and ligand densities is investigated. Finally, the surface functionalized nanocontainers are assembled into structured redox-responsive surface coatings, which can release a payload upon applying a reductive trigger.

Experimental Section Materials Synthesis. The synthesis and characterization of adamantane-terminated poly(acrylic acid) (Ad-PAA, degree of polymerization ≈ 119, Mw/Mn = 1.2), amphiphilic


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β-cyclodextrin and amine functionalized ligands (biotin-NH2, mannose-NH2) is described in detail the supporting information (SI). Preparation of Cyclodextrin Vesicles (CDV). Unilamellar bilayer CDV were prepared by hydration of a thin film and extrusion. Briefly, a 2 mM stock solution of amphiphilic β-cyclodextrin in chloroform was added in a round bottom flask and the solvent was evaporated in a stream of argon to obtain a thin film. Residual solvent was removed under high vacuum. The film was hydrated by addition of 4-(2-Hydroxyethyl)piperazine-1-ethanesulfonic acid (HEPES) buffered saline (HBS, 20 mM HEPES, 150 mM NaCl, pH 7.4) and vigorous stirring for at least 2 h. This solution was sonicated for 15 s and repetitively passed through a polycarbonate membrane with 100 nm pore size in a Liposofast manual extruder (AVESTIN) to yield CDV. Preparation of Surface Functionalized PSVSSLigand. To a buffered solution of CDV (100 µM amphiphilic β-cyclodextrin in HBS) 25.0 µM Ad-PAA (50% coverage of total β-cyclodextrin cavities at the outward surface of vesicles) was added and this mixture was gently stirred for 30 min to obtain polymer decorated vesicles (PDV). For crosslinking and functionalization of the polymer

shell

9.00 mM

1-ethyl-3-(3-dimethylaminopropyl)carbodiimide

hydrochloride

(EDC·HCl, corresponding to 3.0 eq. of total carboxylic acid groups at the PDV surface) was added. After 20 min, 600 µM cystamine (corresponding to 0.20 eq. of total carboxylic acid groups at the PDV surface) and for ligand conjugated PSVSSLigand 30-120 µM ligand-NH2 (biotin-NH2 or mannose-NH2, corresponding to 0.01-0.04 eq. of total carboxylic acid groups at the PDV surface) were added. For a PEG functionalization 1.20 mM PEG-NH2 (0.40 eq. of total carboxylic acid groups at the PDV surface) was added 2 h after the addition of cystamine and ligands. The colloid was stirred slowly overnight, and the byproducts were removed by dialysis


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(Spectra/Por regenerated cellulose (RC) dialysis membranes, MWCO 6–8 kDa) against HBS (3 × buffer exchange within 48 h) to yield PSVSSLigand (app. 0.75 mg/mL). Aggregation Assay. Aggregation assays were performed by the measurement of optical density at λ = 600 nm (OD600) collecting every 5 s one data point and DLS measurements before and after each experiment. The measurement procedure was as follows. The OD600 of 700 µL PSVSSLigand (synthesized from 100 µM β-cyclodextrin amphiphiles in HBS) was measured for 5 min before 35 µL of streptavidin (2 mg mL-1, Sigma Aldrich) or Concanavalin A (ConA, 2 mg mL-1, Sigma Aldrich) were added to make a resulting protein concentration of 0.1 mg mL-1 and the measurement was continued for at least 30 min. For experiments with ConA the HBS buffer medium was supplemented with 1 mM CaCl2 and 1 mM MnCl2. Fluorescence Titration of Biotin. The quantification of biotin conjugated to the surface of PSVSSBiotin was performed following a method introduced by Parce and coworkers.25 Briefly, a solution of 8 mg L-1 streptavidin (STA) in HBS was prepared. For calibration to 1.5 mL of this STA solution biotin (2.5 µM) was added in 5 µL increments and fluorescence of STA (λex = 300 nm, λem = 340 nm) was measured. The break point of this titration gives the number of biotin binding sites in 1.5 mL STA solution. For the quantification of biotin at the surface of PSVSSBiotin 15µL of a tenfold diluted nanocontainer solution were added to 1.5 mL of STA solution. Titration curves of this mixtures with biotin (2.5 µM) are depicted in the SI in Figure S5. Here, the break point gives the number of free biotin biding sites after the addition of the functionalized nanocontainers to the STA solution. By comparison of this value with the number of biotin binding sites in the calibration measurement the concentration of biotin at surface of PSVSSBiotin was calculated.


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Preparation of Biotin Structured Surfaces by Microcontact Printing (µCP). Biotin structured surfaces were prepared following a recently published procedure.22 Briefly, silicon or glass substrates were cleaned by sonication in pentane, acetone and ultrapure water. The cleaned substrates were immersed in a freshly prepared piranha solution (concentrated H2SO4/H2O2 (30%) = 3/1 (vol/vol)) for 30 min and extensively washed with ultrapure water and EtOH and dried in a stream of argon. These oxidized substrates were used to prepare an alken SAM by incubation in a solution of 7-octenyltrichlorosilane (0.1 vol.-%) in toluene for 40 min. The substrates were washed with DCM and EtOH, dried and used for µCP of biotin-SH. Therefore, PDMS stamps were prepared by casting a 10:1 (vol/vol) mixture of poly(dimethylsiloxane) (Dow Corning) and curing agent (Sylgards 184, Dow Corning) on a patterned silicon master. After curing at 80°C for 24 h stamps were cut out and directly prior to use put into an UV ozonizer for 55 min. The stamps were incubated with biotin-SH ink (10 mM biotin-SH, 20 mM 2,2dimethoxy-2-phenylacetophenone (DMPA) in MeOH) for 30 s before excess ink was removed in a stream of argon and the stamps were carefully placed on the alken modified substrates. After the thiol-ene reaction was initiated photochemically using a high-power UV-LED, which was placed approximately 2 cm above the stamp for 5 min, the stamp was removed, and the substrate was rinsed with EtOH and dried. Finally, unreacted alkenes were saturated with mercaptoethanol by applying a solution of 3 wt.-% DMPA in mercaptoethanol to the substrate, which was then covered with a microscopy cover slide and irradiated by using the high-power UV-LED for 10 min. Upon washing with EtOH and drying biotin patterned surfaces were obtained. Immobilization of PSVSSBiotin: Biotin patterned substrates were blocked with 3 wt.-% bovine serum albumin (BSA) in HBS for 30 min and washed with HBS afterwards (2 × 5 min). Incubation with STA (50 µg mL-1) for 15 min and careful rinsing with HBS yielded STA


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patterned surfaces. STA patterned surfaces were incubated with PSVSSBiotin for 15 min and subsequently carefully and repeatedly washed with HBS. PSVSSBiotin with a maximum functionalization of 1% of the carboxylic acid groups by biotin-NH2 and a concentration of 20 µM β-cyclodextrin amphiphiles in HBS were used in the immobilization procedure. For rhodamine B labelled PSVSSBiotin 5 mol-% of amphiphilic β-cyclodextrin were replaced by rhodamine B labelled amphiphilic β-cyclodextrin. For carboxyfluorescein (CF) loaded PSVSSBiotin the preparation of the nanocontainers was performed in HBS containing 100 µM CF. Payload Encapsulation and Release: CDV (100 µM amphiphilic β-cyclodextrin) were prepared in a buffered solution of the payload (self-quenching solution of 5 mM CF in HBS) and PSVSSBiotin were prepared by the above described procedure. After crosslinking of the polymer shell, non-encapsulated dye and byproducts were removed by Sephadex G50 size exclusion chromatography with HBS as eluent. A fraction of ~5.0 mL was collected and used for the immobilization on a small glass slide (8 mm × 15 mm surface area) by the above described procedure (instead of the µCP step the surface was completely functionalized by applying 20 µL of biotin ink capped by a microscopy cover slide). The glass slide with immobilized PSVSSBiotin was placed in a cuvette with 10 mm path length and 1.5 mL HBS were added to cover the immobilized PSVSSBiotin. The HBS was replaced 4 times to remove any residual not-immobilized material. The time dependent measurement of CF fluorescence (λex = 480 nm, λem = 520 nm) in the supernatant solution was started and 400 µM tris(2-carboxyethyl)phosphine (TCEP) was added when indicated. Release at time t was calculated by dividing the fluorescence intensity at time t by the intensity after a complete release.


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Results and Discussion The preparation of surface functionalized nanocontainers starting from the supramolecular building blocks adamantane-terminated poly(acrylic acid) (Ad-PAA) and cyclodextrin vesicles (CDV) is depicted in Scheme 1. An important advantage of CDV in contrast to conventional liposomes is the fact that these dynamic platforms can selectively bind hydrophobic guest molecules, considerably simplifying the preparation of polymer nanocontainers.26 In a first step, Ad-PAA was self-assembled on the surface of bare CDV (hydrodynamic diameter dH = 120 150 nm) templates via highly efficient host-guest recognition of β-cyclodextrin and adamantane conjugated polymers (Ka ~ 103 M-1)27 delivering polymer decorated vesicles (PDV). The subsequent 1-ethyl-3-(3-dimethylaminopropyl)carbodiimide (EDC) mediated crosslinking of the poly(acrylic acid) shell with cystamine linkers results in stable PSVSS and simultaneously allows for a facile decoration of the polymer shell with primary amine functionalized small molecules via amide bond formation. The ratio of diamine linker versus functionalized amine used for amide formation will allow for varying the density of the functionalities in the polymer layer. In comparison with physical methods to adsorb ligands on nanocarrier surfaces, this covalent functionalization approach allows for a more robust and irreversible attachment of the ligands.10 Applying this single-step procedure, nanocontainers were covalently functionalized with biotin-NH2 (PSVSSBiotin), mannose-NH2 (PSVSSMan), PEG-NH2 (Mn ≈ 750 g mol-1) (PSVSSPEG) or combinations thereof (PSVSSBiotin,PEG and PSVSSMan,PEG).


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Scheme 1. Schematic representation of the preparation of ligand functionalized PSVSSLigand and molecular structures of amine-functionalized ligands.

Dynamic light scattering (DLS) measurements show that the self-assembly of the thin polymer shell increases the hydrodynamic diameter slightly by ca. 10 nm, but during the crosslinking and ligand conjugation no change in particle diameter was observed. This clearly indicates that no interparticle crosslinking occurred which is most probably a consequence of high local concentration of preorganized carboxylic acid groups at the vesicle surface reacting with free amine groups of the crosslinker in combination with the steric and electrostatic stabilization resulting from the polymer shell (Figure 1a, Table S1). To assess the surface properties of the nanocontainers, ζ-potential measurements were performed (Figure 1b, Table S1). At pH 7.4 the poly(acrylic acid) shell of PDV creates a strongly decreased ζ-potential of -21.3 mV for PDV.


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The crosslinking and attachment of biotin-NH2 or mannose-NH2 increases the ζ-potential by ca. 6 mV as a consequence of amide bond formation. Since only a small number of ligands was added in the amide formation step to limit a functionalization of carboxylic acid groups with ligands to a stoichiometric maximum of 2%, the ζ-potential of PSVSS, PSVSSBiotin and PSVSSMan does not differ significantly. PEG-NH2 was added in higher concentration to achieve a maximum functionalization of 40% of carboxylic acid groups. In this case a ζ-potential of -8.2 mV was observed, which is typical for PEG-coated nanoparticles and indicates a successful functionalization. As a protective layer of PEG is a common method to sterically stabilize nanoparticles in biological media and to prevent unspecific protein absorption (stealth effect),8,28,29 we tested the colloidal stability in buffered saline containing 10% fetal bovine serum (FBS). It can be seen from DLS data that the average hydrodynamic diameter of both, PSVSS and PSVSSPEG did not change over 4 days and no aggregation could be observed (Figure S1), documenting a remarkable colloidal stability of the polymer nanocontainers in a biological environment.

Figure 1. a) Size distribution according to DLS and b) ζ-Potential of CDV, PDV and PSVSSLigand functionalized with biotin-NH2, mannose-NH2 or PEG-NH2. CDV, PDV and PSVSSLigand concentrations correspond to 100 µM β-cyclodextrin amphiphiles in HBS (20 mM HEPES, 150 mM NaCl, pH 7.4) and measurements were performed at 25 °C. ζ-Potential represents mean ± SD (n = 5).


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An agglutination assay was performed to prove a functionalization of the polymer shell with biotin or mannose ligands. In this experiment STA was added to PSVSSBiotin, whereas the lectin Concanavalin A (ConA), which has a high affinity to derivatives of α-D-mannose (Ka ~ 104 M-1),12,13 was added to PSVSSMan. Each of these tetrameric proteins can bind four ligands and the specific and multivalent interaction of these proteins with the corresponding ligands conjugated to the surface of PSVSSBiotin or PSVSSMan should result in the formation of numerous non-covalent crosslinks between the nanocontainers, thereby causing aggregation and an increase of turbidity. Indeed, a spontaneous time-dependent increase of optical density at λ = 600 nm (OD600) was observed upon addition of the proteins to the biotin or mannose conjugated nanocontainers (Figure 2a). When PSVSS without surface functionalization were treated with STA or ConA, there was no change in OD600 verifying the specificity of multivalent interactions. The results of optical density measurements were corroborated by DLS measurements. Upon the addition of ConA to PSVSSMan the average hydrodynamic diameter increased drastically from about 135 nm to average aggregate sizes > 1000 nm, whereas the treatment of unfunctionalized PSVSS did not cause a change in size distributions (Figure 2b). Similarly, the aggregation of PSVSSBiotin in the presence of STA resulted in highly polydisperse samples with large aggregates (Figure S2). Furthermore, agglutination of PSVSSMan was immediately reversed by the addition of a large excess of mannose displaying the highly dynamic nature of the non-covalent recognition of mannose ligands at the nanocontainers surface (Figure 2b, S3). In contrast, the initial OD600 could not be recovered for aggregated PSVSSBiotin in the presence of an excess of biotin ligand. This can be explained by the remarkably strong binding and slow dissociation (half-life time of days to weeks)21 of biotin and STA inhibiting a dynamic ligand exchange and a redispersion of the aggregates.


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Figure 2. a) Time-dependent OD600 and b) DLS measurements monitoring the aggregation of PSVSSLigand in the presence of tetravalent binding proteins. In OD600 measurements ConA or STA was added at t = 5 min. Concentrations of PSVSSLigand (2% maximum functionalization of carboxylic acid groups by biotin-NH2 or mannose-NH2) correspond to 100 µM β-cyclodextrin amphiphiles in HBS (20 mM HEPES, 150 mM NaCl, pH 7.4) supplemented with 1 mM CaCl2 and 1 mM MnCl2 for ConA recognition experiments, [STA] = [ConA] = 0.1 mg/mL, measurements were performed at 25 °C.

To evaluate if a functionalization with PEG-NH2 still facilitates a recognition of surface conjugated ligands, we first prepared PSVSSBiotin,PEG functionalized with biotin-NH2 (2% stoichiometric maximum functionalization of carboxylic acid groups by biotin-NH2) and PEG-NH2 simultaneously. Interestingly, PSVSSBiotin,PEG in the presence of STA show a much slower aggregation and a lower OD600 compared to PSVSSBiotin and the size distribution according to DLS indicates the co-presence of aggregates with sizes of ca. 1000 nm and remaining, nonaggregated nanocontainers (Figure S4). For PSVSSMan,PEG functionalized with mannose-NH2 and PEG-NH2 agglutination with the weaker binding ConA was fully inhibited and OD600 remained low for a stoichiometric maximum of 2% functionalized carboxylic acid groups with mannose-NH2 (Figure S4). Again, these results imply that a functionalization with PEG groups sterically stabilizes the nanocontainer surface diminishing the recognition and aggregation process. However, the strong biotin-STA-binding still facilitates the interparticle crosslinking.


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We next investigated if the ligand density at the nanocontainers surface can be varied and how this influences the multivalent recognition by proteins. Therefore, increasing concentrations of biotin-NH2 were added during the preparation of PSVSSBiotin resulting in a theoretical maximum biotinylation of 1%, 2%, 3% or 4% of carboxylic acid groups at the nanocontainer surface. After dialysis to remove free biotin-NH2, the biotin concentration was measured by a fluorometric method based on the quenching of the natural fluorescence of STA upon binding to biotin (see Materials and Methods section and Figure S5).25 Figure 3a shows that the measured biotin concentration correlates with the theoretical degree of functionalization, demonstrating that the concentration of surface attached ligands can easily be varied by adapting the stoichiometry during synthesis. Upon addition of STA to PSVSSBiotin with a low surface density of biotin (1% or 2% maximum biotinylation), a fast and extensive increase of OD600 was monitored. Interestingly, nanocontainers with higher biotin surface densities (3% and 4%) showed only a slow and moderate increase of OD600 in the presence of STA (Figure 3b). Similarly, DLS measurements show aggregated and non-aggregated nanocontainers for 3% and 4% functionalized nanocontainers, which indicates a strongly reduced interparticle crosslinking (Figure S6). This phenomenon most probably can be attributed to a starting saturation of STA binding sites with biotin ligands within a densely functionalized polymer shell reducing the number of free biotin binding sites and thereby the probability of interparticle crosslinking. This hypothesis is corroborated by a theoretical estimation on the number of biotin binding sites necessary to fully saturate a shell of STA on the surface of PSVSSBiotin (see SI). In this simple geometric consideration, we assumed that STA covers the volume of a thin shell around a spherical nanocontainer core. Based on this estimation, the biotin surface density for a starting saturation of STA is in the same order of magnitude as for 3-4% biotinylation, where a reduced


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interparticle crosslinking was observed. For PSVSSMan the mannose density on the surface was varied in the same manner. Here, the initial rate of increase in OD600 was almost 10-fold increased from 0.03 min-1 for 1% to 0.24 min-1 for 2% maximum functionalization. For samples with higher ligand densities only a slightly stronger agglutination was observed (Figure 3c). This experiment demonstrates two vital points: A fast and extensive agglutination is a result of high mannose density and a most likely multivalent recognition by ConA (i.e. cluster glycoside effect)30,31 and at high ligand densities the dynamic nature of interaction still allows for a dynamic exchange of ligands and interparticle crosslinking. In contrast, the slow dynamics of biotin-STA binding and saturation of binding sites reduce interparticle recognition at high biotin ligand densities.


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Figure 3. a) Fluorometric quantification of biotin in dispersions of PSVSSBiotin with varied stoichiometric maximum functionalization of carboxylic acid groups by biotin-NH2 (performed as duplicates). b) Time-dependent aggregation PSVssBiotin with different maximum functionalization by biotin-NH2 upon addition of STA at t = 5 min. c) Time-dependent aggregation PSVssMan with different maximum functionalization by mannose-NH2 upon addition of ConA at t = 5 min. d) Initial rates of aggregation of PSVSSMan + ConA or PSVSSBiotin + STA calculated by a linear approximation of the increase in OD600 within the first 60 s of aggregation. Concentrations of PSVSSLigand correspond to 100 µM β-cyclodextrin amphiphiles in HBS (20 mM HEPES, 150 mM NaCl, pH 7.4) supplemented with 1 mM CaCl2 and 1 mM MnCl2 for ConA recognition experiments, [STA] = [ConA] = 0.1 mg/mL, measurements were performed at 25 °C.

Finally, we applied the rational surface design of the redox-responsive nanocontainers to immobilize them on solid substrates, creating a surface coating that can release its cargo upon a reductive trigger. We decided to exploit the biotin-STA receptor-ligand pair to immobilize PSVSSBiotin (Figure 4a) due to its high association constant, which should inhibit a dynamic dissociation of the PSVSSBiotin from the surface.22 Applying a recently published procedure22 the


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surface of silicon substrates was structured by microcontact printing (µCP)32 of a thiol functionalized biotin derivative (biotin-SH) reacting with a silicon-supported self-assembled monolayer (SAM) of alkenes. To generate a hydrophilic surface with a static contact angle of 39.5° (Figure S7) unreacted alkenes were saturated with mercaptoethanol and to minimize unspecific protein adsorption the surfaces were blocked with bovine serum albumin (BSA) prior to application of STA. Finally, these patterned substrates were incubated with PSVSSBiotin, which were fluorescently labelled by including rhodamine B conjugated amphiphilic β-cyclodextrin33 in the template vesicles. Fluorescence microscopy analysis clearly shows the specific immobilization of PSVSSBiotin since the signal of rhodamine B resembles the printed patterns of 10 µm dots that are spaced by 10 µm (Figure 4b). To show that PSVSSBiotin remained intact upon immobilization, they were loaded with the hydrophilic fluorescent dye carboxyfluorescein (CF) before immobilization.24 Here, the immobilization in a stripe pattern nicely demonstrates the recognition of intact CF loaded PSVSSBiotin (Figure 4c). In negative control experiments, dye loaded or rhodamine B labelled PSVSS without biotin functionalization were incubated with STA patterned surfaces. No immobilization was observed, verifying the specific deposition of nanocontainers on the surface (Figure S8). In previous studies, we demonstrated the redox-responsive release of hydrophilic payloads from PSVSS in solution.24 To investigate the influence of surface immobilization on the redoxresponsive release of a payload from PSVSS, we immobilized PSVSSBiotin loaded with CF and measured fluorescence of the supernatant solution. In the absence of a reducing agent only a moderate increase of fluorescence intensity was monitored, indicating a slow passive release of CF from the aqueous lumen of the immobilized nanocontainers. Strikingly, upon addition of the reducing agent TCEP a highly accelerated release of cargo was monitored (Figure 4d, S9). Taken


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together, the immobilization experiments indicate that the PSVSSBiotin stay intact and maintain their redox-responsive release properties upon attachment to a solid substrate.

Figure 4. a) Illustration of the biotin-STA binding motif for the immobilization of PSVSSBiotin. Fluorescence microscopy images of b) rhodamin-B labelled and c) CF loaded PSVSSBiotin immobilized on STA-patterned surfaces. d) Time-dependent release of CF from immobilized redox-responsive PSVSSBiotin.

Conclusions In summary, we have introduced the rational surface design of self-assembled polymer shelled vesicles and employed this methodology for their immobilization in a non-covalent biomimetic fashion. The conjugation of biotin or mannose ligands to the polymer shell proved to be appropriate for the recognition and binding of biological macromolecules and indicates that this complex process can be controlled by the variation of ligand densities on the nanocontainer surface and a proper choice of the ligand-receptor pair. Moreover, the structured immobilization


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of these redox-responsive polymer nanocontainers provides a new strategy to construct tethered nanocapsules, which can release their payload upon a reductive trigger. Such materials may have promise for use in targeted drug delivery applications and may be considered in the design of microarrays for sensing applications. ASSOCIATED CONTENT Supporting Information. Experimental details, synthesis of Ad-PAA, amphiphilic β-cyclodextrin and ligands, DLS, OD600 and contact angle data, release profiles, fluorescence microscopy images, control experiments and calculations (PDF). AUTHOR INFORMATION Corresponding Author *Bart Jan Ravoo ([email protected]). Notes The authors declare no competing financial interest. ACKNOWLEDGMENT W.C.V acknowledges a fellowship of the Fonds der Chemischen Industrie. We sincerely thank the Deutsche Forschungsgemeinschaft (DFG SFB858 and EXC 1003) for funding. The authors thank Dr. Christian Wendeln for providing mannose-NH2 and Dr. Oliver Roling for supplying biotin-SH. REFERENCES (1)

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SYNOPSIS

For Table of Contents Only


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Molecular Recognition and Immobilization of Ligand-Conjugated

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