THE INFLAMMATION-ASSOCIATED PROTEIN TSG-6 CROSS-LINKS HYALURONAN VIA HYALURONAN-INDUCED TSG-6 OLIGOMERS

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1 Supplemental Data THE INFLMMTION-SSOCITED PROTEIN TSG- CROSS-LINKS HYLURONN VI HYLURONN-INDUCED TSG- OLIGOMERS Natalia S. aranova 1, Erik Nilebäck 3,, F. Michael Haller 5, David C. riggs, Sofia Svedhem 3, nthony J. Day and Ralf P. Richter 1, From the 1 iosurfaces Unit, CIC biomagune, Paseo Miramon 1, 9 Donostia-San Sebastian, Spain, the Max-Planck-Institute for Metals Research, Stuttgart, Heisenbergstraße 3, 759 Stuttgart, Germany, the 3 Department of pplied Physics, Chalmers University of Technology, 19 Göteborg, Sweden, Q-Sense, Hängpilsgatan 7, 77 Västra Frölunda, Sweden, 5 Hyalose, L.L.C., 55 Research Parkway, Suite 55, Oklahoma City, OK 731, US, the Wellcome Trust Centre for Cell Matrix Research, Faculty of Life Sciences, University of Manchester, Oxford Road, Manchester M13 9PT, UK Running head. TSG- induced hyaluronan cross-linking ddress correspondence to: Ralf Richter, iosurfaces Unit, CIC biomagune, Paseo Miramon 1, 9 Donostia-San Sebastian, Spain. Phone: ; Fax: ; rrichter@cicbiomagune.es. nthony Day, Wellcome Trust Centre for Cell Matrix Research, Faculty of Life Sciences, University of Manchester, Oxford Road, Manchester M13 9PT, UK. Phone: ; Fax: ; anthony.day@manchester.ac.uk S1

2 Preparation of biotinylated oh Preparation of H oligomers with a hydrazide functionality at their reducing end..3 µm H N 1 (i.e. a decasaccharide with D-glucuronic acid () at the nonreducing terminus and N-acetyl-D-glucosamine (N) at the reducing terminus) was stirred at room temperature with.17 mm adipic acid dihydrazide in 1 M sodium phosphate buffer (prepared from Na HPO and NaH PO ), ph 5.5 overnight. NaH 3 CN was added to 1 mm, and the reaction mixture was heated at C overnight. The reaction mixture was desalted in the fume hood over a column of Toyopearl HW-F resin with 1 mm sodium phosphate buffer, ph 7. as eluent. The Hcontaining fractions were diluted -fold with water, and passed through a Strata SX tube. The resin was washed thoroughly with 5 mm ammonium hydrogen carbonate, and the H oligomer eluted with 5 mm ammonium hydrogen carbonate. The material was repeatedly freeze-dried to remove all volatile salts. Preparation of H oligomers with a biotin functionality at their reducing end. The hydrazide-functionalized oligomers were biotinylated by incubating. μm hydrazide-h 9 with 5. μm sulfo-nhs-lc-lc-biotin (Pierce) in 5 mm sodium phosphate buffer, ph 5.5 overnight with constant agitation. The ph was then adjusted to ph 3. with acetic acid, and passed through a Strata C-1E column. fter washing with 5 mm acetic acid, followed by a water rinse, the conjugate was eluted with 5% aqueous methanol and lyophilized. iotin-h 9 was further purified by size exclusion chromatography on a D-salt polyacrylamide desalting column with MWCO ~ 1 Da (Pierce) equilibrated and run in 1 mm HEPES, 5 mm NaCl at ph 7.. The purified sample was stored at C for no longer than 3 months before use. Preparation of surfaces Substrate preparation. Silica-coated QCM-D sensors (QSX33; Q-Sense, Västra Frölunda, Sweden), silicon wafers with a native oxide layer of about nm thickness (University Wafers, South oston, M, US) and glass cover slips (#1, mm ; Menzel-Gläser, Thermo Scientific, Germany) were used as substrates for QCM-D, ellipsometric and RICM measurements, respectively, on H films on supported lipid bilayers (SLs). efore each use, the QCM-D sensors and the silicon wafers were cleaned in an aqueous solution of % sodium dodecyl sulfate (15 min), rinsed with ultrapure water, blow-dried in N and treated with UV/ozone (ioforce Nanoscience, mes, I, US) for 3 min. Glass cover slips were immersed in freshly prepared piranya solution, i.e. a 1:1 (v/v) mixture of 5% H O and concentrated H SO for 1 h, rinsed with ultrapure water, blow-dried with N and stored under N atmosphere. Cleaned substrates were exposed to UV/ozone (3 min) prior to use. Gold-coated QCM-D sensors (QSX31; Q-Sense ), silicon wafers with a 1 nm gold coating and glass cover slips with a 5 nm gold coating (both from G. lbert PVD eschichtungen, Silz, Germany) were used as substrates to create H films on oligoethylene glycol (OEG) layers for QCM-D, ellipsometric and RICM measurements, respectively. The surfaces were cleaned by exposure to UV/ozone (3 min) prior to use. Preparation of vesicles, and formation of supported lipid bilayers (SLs) on silica or glass surfaces. 1, dioleoyl-sn-glycero-3-phosphocholine (DOPC) and 1,-dioleoyl-sn-glycero-3-phosphoethanolamine-N-(cap biotinyl) (DOPE-CP-biotin) were purchased from vanti Polar Lipids (labaster, L, US). mixture of DOPC/DOPE-CP-biotin (9:1 molar ratio) was dissolved in chloroform, dried, re-suspended in Hepes buffer (as defined in the main text) without added calcium and homogenized as described earlier (1). Small unilamellar vesicles (SUVs) were formed by sonication (). 5 μg/ml biotinylated SUVs were exposed to cleaned silica or glass surfaces for 3 min, leading to the formation of an SL (Fig. S1). OEG-functionalization of gold surfaces. Clean gold surfaces were functionalized by overnight incubation in a solution of 1 mol % of a biotinylated oligo(ethylene glycol) disulfide (SS-OEG-biotin; M W = 15 Da) and 99 mol % of a plain OEG disulfide (SS-OEG; 771 Da) (both Polypure, Oslo, Norway) with a total thiol concentration of.5 mm in spectroscopy grade ethanol (3), rinsed and sonicated (15 min) in ethanol, blow-dried in N, and stored in the dark under N atmosphere at C for no longer than one week before being used. This procedure leads to the formation of a dense OEG monolayer with a few nanometres in thickness (). S

3 Implementation of surface-sensitive characterization techniques Quartz crystal microbalance with dissipation monitoring. Measurements were performed with a Q-Sense E system (Q-Sense ), in flow mode () with flow speeds between 5 and μl/min and at a working temperature of 3 C. To avoid depletion of sample by adsorption to tubings or chamber walls, these were passivated by exposure to a 1% (w/v) solution of bovine serum albumin (S; Sigma) in Hepes buffer (3 min), rinsed with ultrapure water and blow-dried with N prior to each measurement. QCM-D data were collected at six overtones (n = 3, 5, 7, 9, 11, 13, corresponding to resonance frequencies of ~15, 5, 35, 5, 55, 5 MHz). Changes in dissipation and normalized frequency, Δf = Δf n /n, of the fifth overtone (n = 5) are presented. For homogeneous and sufficiently rigid layers, the film thickness can be estimated, to within an error of typically < %, from d = Δm/ρ = -C/ρ Δf, where Δm, ρ = 1. g/cm 3 and C = 1. ng/cm /Hz are, respectively, the adsorbed mass (including coupled water), the density of the bulk solution, and the mass sensitivity constant for a sensor with a fundamental resonance frequency of.95 MHz (5). For soft films (exhibiting high dissipation) this equation is not valid. To determine the film thickness of H films, colloidal probe reflection interference contrast microscopy was used instead. In situ ellipsometry. Measurements were performed with a spectroscopic rotating compensator ellipsometer (MV, Woollam, NE, US), as described earlier (). purpose-designed open glass cuvette with a total volume of approximately 15 µl was employed, the walls of which were passivated with S as described above. Samples were injected directly into the cuvette and excess sample was removed by repeatedly diluting the cuvette content in buffer. ound masses were determined by numerically fitting of the ellipsometric data, as described earlier (). Colloidal probe reflection interference contrast microscopy. The thickness of surface-bound H films was determined by triple wavelength colloidal probe RICM, as described previously (,7). Naked polystyrene microspheres of ~5 μm diameter (Polysciences, Eppelheim, Germany) were used as colloidal probes. The H films were assembled on bare or gold-coated glass cover slips, using custom-built liquid flow cells with an internal volume of a few μl. Protein solutions at desired concentrations were injected with a flow rate of μl/min until equilibrium was reached (typically within 5 to min). t the end of each titration step, colloidal probes were mixed into the protein solution and applied at a flow rate of 5 μl/min. Presented thickness values correspond to the increase in the total measured film thickness upon the addition of H, or of H and TSG-. From the analysis of the microspheres lateral mobility, we estimate that interactions between the microspheres and the H films did not perturb the samples appreciably (7). S3

4 SUVs b Sv ph b (5kDa) SUVs b Sv oh b (H 9 ) D (1 - ) D (1 - ) SiO Figure S1. uild up of H films on supported lipid bilayers (SLs), monitored by QCM-D. The start and duration of the incubation with different samples and buffer is indicated (solid arrows and dashed arrows, respectively). The two-phase behavior in the frequency ( f; blue curves with open triangles) and dissipation ( D; red curves) shifts upon incubation of small unilamellar vesicles (SUVs; containing 1 mol-% of biotinylated lipids (DOPE-CP-biotin) and 9 mol-% inert lipids (DOPC)) is characteristic for the process of SL formation in which vesicles first adsorb intact and then rupture and spread. Final values of f = - ± 1 Hz and D < indicate the formation of an SL of good quality (). n additional frequency shift of - ± 1 Hz together with a small dissipation shift of (.5±.1) 1 - upon exposure of the SL to streptavidin (Sv) are characteristic for the formation of a thin and densely packed protein monolayer (9). iotinylated ph (5 kda; ), incubated at 1 µg/ml, assembles into a thick, soft and highly hydrated film, as shown by the pronounced increase in dissipation of (9.5 ±.5) 1 - (). iotinylated oh (H 9 ; ), incubated at approximately 1 µg/ml, forms a much thinner and more densely packed layer. Schematic presentations of the design of the model systems are also shown (right). The size of the proteins, the thickness of the SL, and the length of the oh are drawn to scale; the thickness of the ph films is compressed by about one order of magnitude. SiO DOPE CP biotin DOPC Sv biotin(+linker) H S

5 Sv ph b (5kDa) Sv oh b (H 9 ) D (1 - ) D (1 - ) S S S S SSS S S S S S S S S S S S S Figure S. uild up of H films on OEG layers, monitored by QCM-D. The biotin-oeg layer was formed ex situ prior to the QCM-D measurement. The start and duration of the incubation with different samples and buffer is indicated (solid arrows and dashed arrows, respectively). Frequency shifts (blue curves with open triangles) of f = - ± Hz and small dissipation shifts (red curves) of D = (.3±.15) 1 - upon exposure of the OEG film to Sv indicate formation of a protein monolayer that is less dense than the Sv monolayer on SLs (see Fig. S1). inding curves for ph (5 kda; ) and oh (H 9 ; ) are similar to those obtained on SLs. The frequency shifts for oh on the OEG layer (-7 ± 1 Hz) is slightly smaller than on the SL (- ± Hz), indicating somewhat lower coverage. y ellipsometry, we found typical oh surface coverages of 3 ± 5 ng/cm on SLs and around 1 ± 5 ng/cm on OEG layers (data not shown), corresponding to a mean spacing between adjacent anchor points of 5.1±. nm and 5.±. nm, respectively. y ellipsometry, we found also that 1. to. biotin-binding sites per Sv molecule were on average occupied with oh (data not shown). Schematic presentations of the design of the model systems are also shown (right). The size of the proteins, the thickness of the OEG layer, and the length of the oh are drawn to scale; the thickness of the ph films is compressed by about one order of magnitude. u S S S S SSS S S S S S S S S S S S S u S OEG biotin S OEG Sv biotin(+linker) H S5

6 surface density (ng/cm ) C 1 1 surface density (ng/cm ) Figure S3. Quantification of ph surface densities for QCM-D (5 kda) and RICM (1 kda) measurements. (-C) Correlation between the hyaluronan surface mass density and the QCM-D frequency shifts upon binding of 5 kda ph, from a simultaneous measurement by QCM-D and ellipsometry on the same surface (7,1). () Surface mass densities upon incubation of ph as determined by ellipsometry. () Corresponding QCM-D frequency shifts. t min, ph was injected at a concentration of 7.5 μg/ml; a second injection of equal concentration after 5 min led to renewed H binding, indicating some depletion of H in the solution phase. (C) Parametric plot of the frequency shifts vs. surface density for the data from () and (). With the aid of this calibration curve, the surface density of ph can be quantified from QCM-D frequency shifts for arbitrary coverages (7,9,1). The dependence is linear over the entire range of densities investigated, with a slope of -. Hz/(ng/cm ). The QCM-D measurements in this study were performed with 5 kda ph, with a frequency shift of f = -3± Hz, corresponding to 5±5ng/cm. (D) Surface mass densities upon incubation of 5 μg/ml 1 kda ph as determined by ellipsometry. The adsorption rate is very slow beyond one hour of incubation, consistent with the kinetic limitations that are associated with the densification of a polyelectrolyte brush in the grafting-to method (). maximal adsorbed amount of 35 ng/cm is obtained after one hour of incubation, which is similar to, yet slightly below, a previously reported value (). The RICM measurements in this study were performed with 1 kda ph, under similar incubation conditions as shown here. surface density (ng/cm ) 1 D D (1 - ) Figure S. The nature of the passivation layer does not affect the morphology of the H films. Parametric plot of ΔD vs. Δf for the QCM-D data that corresponds to the formation of ph (5 kda; ) and oh (H 9 ; ) films in Figs. S1 and S. The plot provides insight into the evolution of the viscoelastic properties as the H film grows. In this presentation, the curves for the respective H films on the SL (black lines with open triangles) and on the OEG layer (orange lines with open circles) are very similar, indicating that the film morphology is the same on both immobilization platforms. D (1 - ) S

7 .3μM rhtsg surface density (ng/cm ) μM rhtsg ph(kda) ph(kda) Figure S5. Controls for the binding of rhtsg- to Sv-covered OEG layers. () Ellipsometric data for the exposure of.3 μm rhtsg- to a Sv-covered OEG layer that was formed as described in Fig. S. The start and duration of the incubation with different samples and buffer is indicated (solid arrows and dashed arrows, respectively). The bound amount is very small (<1 ng/cm ). () QCM-D responses, Δf (blue curves with open triangles) and ΔD (red curves) are shown for the sequential exposure of.3 μm rhtsg- and 5 µg/ml biotinfree polymeric H ( kda) to a Sv-covered OEG layer. Exposure to rhtsg- induces a small frequency response of - Hz, indicating minor unspecific binding. Non-specifically bound rhtsg- does not have detectable ph binding activity. (C) QCM-D responses for the exposure of 5 µg/ml biotin-free polymeric H ( kda) to a Sv-covered OEG layer that had been incubated with biotinylated oh; no binding was observed. C D (1 - ) S7

8 15mM NaCl.1 Link_TSG in bulk solution(µm) mM NaCl surface density (ng/cm ) 5 3 M GuHCl mM NaCl 1μM Link_TSG 5mM NaCl 5mM NaCl 1μM Link_TSG 5mM NaCl Figure S. Controls for binding of Link_TSG to Sv-covered SLs. () Ellipsometric response for the titration of Link_TSG on a Sv-covered SL that was formed as described in Fig. S1. The start and duration of the incubation with different samples and buffer is indicated (solid arrows and dashed arrows, respectively). Minor but significant amounts of Link_TSG bind non-specifically in a concentration-dependent manner. ound Link_TSG could not be eluted in buffer, but in M GuHCl (GuHCl incubation period shaded in grey). (-C) QCM-D responses, Δf (blue curves with open triangles) and ΔD (red curves), for the exposure of Link_TSG to Sv-covered SLs in 5 mm NaCl. t 1 µm concentration, Link_TSG showed no detectable binding: Δf <.5 Hz and ΔD < (). small frequency shift of -3 Hz was detected at 1 µm concentration in 5 mm NaCl, indicating some minor unspecific binding (C). C D (1 - ) S

9 ph b (5kDa) M GuHCl D (1 - ) Figure S7. H films are stable against treatment with the dissociating agent GuHCl. () QCM-D response, Δf (blue curves with open triangles) and ΔD (red curves), for the exposure of M GuHCl to a film of ph (5 kda) on a Sv-coated SL. The start and duration of the incubation with different samples and buffer is indicated (solid arrows and dashed arrows, respectively). oth Δf and ΔD recover their original value after GuHCl treatment, indicating that M GuHCl do not irreversibly alter the morphology of the surface-bound film. Changes in Δf and ΔD from to 5 min are likely not to reflect any changes on the surface. Instead, they result predominantly from a change in the viscosity and/or density of the surrounding solution owing to the presence of GuHCl. () Ellipsometric response for the exposure of M GuHCl (incubation period shaded in grey) to a film of ph (5 kda) on a Sv-covered OEG layer. The surface density is identical before and after GuHCl treatment, indicating that the interaction between H and the surface is resistant to M GuHCl. surface density (ng/cm ) ph b (5kDa) M GuHCl References 1. Richter, R. P., Mukhopadhyay,., and risson,. (3) iophys. J. 5, Eisele, N.., Frey, S., Piehler, J., Görlich, D., and Richter, R. P. (1) EMO Rep. 11, Nilebäck, E., Westberg, F., Deinum, J., and Svedhem, S. (1) nal. Chem., Nilebäck, E., Uddenberg, H., Valiokas, R., and Svedhem, S. manuscript in preparation 5. Wolny, P. M., Spatz, J. P., and Richter, R. P. (1) Langmuir, Richter, R. P., Hock, K. K., urkhartsmeyer, J., oehm, H., ingen, P., Wang, G., Steinmetz, N. F., Evans, D. J., and Spatz, J. P. (7) J. m. Chem. Soc. 17, Wolny, P. M., anerji, S., Gounou, C., risson,. R., Day,. J., Jackson, D. G., and Richter, R. P. (1) J. iol. Chem. 5, Richter, R. P., érat, R., and risson,. R. () Langmuir, ingen, P., Wang, G., Steinmetz, N. F., Rodahl, M., and Richter, R. P. () nal. Chem., Carton, I., risson,. R., and Richter, R. P. (1) nal. Chem., S9

Supporting Information. Evaluating the Cell Membrane Penetration Potential of Lipid- Soluble Compounds using Supported Phospholipid Bilayers

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