Mechanical stimuli profoundly alter cell fate, yet the mechanisms underlying mechanotransduction remain obscure because of a lack of methods for molecular force imaging. Here to address this need, we develop a new class of molecular tension probes that function as a switch to generate a 20- to 30-fold increase in fluorescence upon experiencing a threshold piconewton force. The probes employ immobilized DNA hairpins with tunable force response thresholds, ligands and fluorescence reporters. Quantitative imaging reveals that integrin tension is highly dynamic and increases with an increasing integrin density during adhesion formation. Mixtures of fluorophore-encoded probes show integrin mechanical preference for cyclized RGD over linear RGD peptides. Multiplexed probes with variable guanine-cytosine content within their hairpins reveal integrin preference for the more stable probes at the leading tip of growing adhesions near the cell edge. DNA-based tension probes are among the most sensitive optical force reporters to date, overcoming the force and spatial resolution limitations of traction force microscopy.
The integrin family of transmembrane proteins constitutes one of the major force-transducing receptors in cells1. These receptors provide a mechanical bridge linking the extracellular matrix (ECM) to the cytoskeleton. After binding their ligands, groups of integrin receptors often nucleate the formation of focal adhesions (FAs), which are multimicron-scale structures comprised of hundreds of different adaptor and signalling proteins, such as talin, vinculin and paxillin, that take part in mechanosensing2. Given that the majority of integrin functions, including ligand recognition, are force modulated, it is imperative to develop approaches to report the molecular forces experienced by integrin receptors within FA assemblies3. Accordingly, cellular traction forces are typically imaged at the scale of FAs by using techniques that track substrate deformation, such as traction force microscopy and microfabricated post array detectors4,5,6,7. These methods underpin our current understanding of FA mechanobiology, demonstrating the existence of force oscillations and revealing the mechanotransducing role of adaptor proteins, such as vinculin8. However, deformable substrates alter cell biology, are either computationally intensive to use or challenging to fabricate, and ultimately hinder high-resolution imaging9,10. Moreover, the forces experienced by individual integrins are three-orders of magnitude smaller than the force sensitivity and spatial resolution of traction force microscopy and microfabricated post array detectors11,12, thus hampering more detailed elucidation of the molecular mechanisms of mechanotransduction. Genetically encoded protein tension sensors have also been developed to study the mechanoresponse of vinculin, E-cadherin and platelet endothelial cell adhesion molecule (PECAM-1)13,14,15,16. Although successful in these applications, protein engineering requires careful screening of insertion sites to ensure that localization and biological function are maintained as many proteins may not tolerate insertion of a ~500 amino-acid sequence. In addition, the optical response of genetically encoded probes is fixed to forces ranging from ~2 to ~6 pN, which is limiting given that biological forces have been estimated to exceed ~50 pN in certain processes17.
To address these unmet needs, we invented molecular tension-based fluorescence microscopy (MTFM) to visualize pN-forces exerted by cell surface receptors, including integrin receptors18,19,20,21. In MTFM, we typically use a flexible polyethylene glycol (PEG) entropic spring that is flanked by a fluorophore-quencher pair to report cellular forces that stretch the polymer. Because the PEG-based tension probes provide a graded ‘analogue’ response from an ensemble of molecules, it is difficult to obtain the absolute magnitude of tension per receptor and to decouple this from the density of mechanically strained receptors. Dunn and colleagues tried to address this issue by using single-molecule imaging of sparsely labelled integrin tension probes (~0.5 probes per μm2)22. Unfortunately, single-molecule imaging requires the combination of oxygen-scavengers and triplet state quenchers, which are deleterious to cells23,24. Also, the FA contains thousands of integrin receptors that dynamically transmit mechanical signals, and thus the sparse density of reporters is limiting. Wang and Ha developed tension gauge tethers, DNA duplexes that shear under sufficient force, which elegantly report minimum forces needed for receptor activation, but cannot describe the spatial and temporal dynamics of receptor activation17. For example, it is not clear whether the mechanical load increases per integrin molecule within the nascent adhesion, or whether the load per integrin molecule is fixed as the density of integrins increases. Ultimately, mechanical tension needs to be visualized at the level of single-integrin molecules, across a wide dynamic range of force magnitudes, and within a dynamic FA containing hundreds to thousands of receptors.
To this end, we report a new class of molecular tension probes that employs a DNA hairpin as a ‘switch’ element, thus unfolding at a threshold force and reporting tension in a digital rather than analogue manner (Fig. 1a). DNA is ideally suited for this purpose because an oligonucleotide’s nucleobase sequence can be used to rationally tune its force-response function. Probes were designed to be highly adaptable, consisting of three oligonucleotides assembled through hybridization of 21-mer handles (Fig. 1b): a stem-loop DNA hairpin that is unmodified (black), a peptide-displaying ligand strand conjugated to a fluorophore (green) and a surface-anchor strand that is tagged with a quencher (blue). The apposing termini of the ligand and anchor oligonucleotides were modified with a fluorophore-quencher pair, such that a sufficient force leads to hairpin unfolding accompanied by a drastic increase in fluorescence intensity.
Because each probe engages only a single receptor, the signal intensity from an ensemble of digital tension reporters is linearly proportional to the number of integrin molecules exceeding a threshold force. This relationship overcomes the challenges of inferring single-receptor forces from an ensemble fluorescence measurement; that is, de-convoluting the relationship between probe density and the magnitude of tension per probe. Therefore, these reversible DNA-based probes obviate the need for estimating the average minimum force per receptor18,19,20,21 or conducting single-molecule measurements22.
Design and synthesis of DNA-based tension probes
We synthesized a small library of hairpin sensors with different GC contents, stem lengths and loop sizes to tune their stability and their F1/2, the force at which 50% of hairpins unfold (Fig. 1c, Methods, Supplementary Figs 1 and 2, Supplementary Tables 1 and 2, Supplementary Note I). The value of F1/2 was initially estimated using the free energy of hairpin unfolding at zero force, as well as the free energy required to stretch single-strand DNA (ssDNA) based on the worm-like chain model (Methods, Supplementary Table 3, Supplementary Note II)25,26. The 22 and 100% GC content probes were further calibrated by using the biomembrane force probe (BFP), which is a single-molecule force spectroscopy technique based on optically monitoring the displacement of the interface between a microparticle and a red blood cell (RBC)27. Using a loading rate of 500 pN s−1, we found that the experimental F1/2 of the 22 and 100% GC probes was 4.7±1.7 pN (n=36 unfolding events) and 13.1±2.4 pN (n=63 unfolding events), respectively (Methods and Supplementary Fig. 3). Note that although the calculated and experimentally determined F1/2 values generally agree, there is a greater difference for the larger sized hairpins. Also, broadening of the unfolding probability compared with the expected Boltzmann distribution is likely due to thermal noise and the heterogeneity in the orientations of the molecules probed.
To identify the most sensitive fluorescent reporters, a series of probes with different fluorophore-quencher pairs were synthesized and characterized to determine the quenching efficiency (QE) at 37 °C in PBS. We found that Cy3B-BHQ1, Atto647N-QSY21 and Cy5-QSY21 showed the greatest QEs (~95%) among the dye-quencher pairs tested, and fully recover their fluorescence upon opening the hairpin with a complementary DNA strand (Fig. 1c, Methods, Supplementary Fig. 4, Supplementary Table 4). Importantly, these QE values (95–97%) are greater than those reported for any molecular tension probe, yielding a 20- to 30-fold increase in signal over background, which represents a two- to threefold improvement over PEG-based entropic spring reporters (Fig. 1a)18,19,20,21.
Visualizing integrin tension
The DNA surface density on glass coverslips was empirically tuned (~400 molecules per μm2, Methods and Supplementary Fig. 5) to support cell adhesion while limiting the background fluorescence. Breast cancer cells (HCC1143) were plated onto the 22% GC (F1/2=4.7 pN) hairpin probe surface displaying cyclic Arg-Gly-Asp-D-Phe-Lys (cRGDfK) and then timelapse videos were acquired as cells initiated spreading and adhesion (Fig. 2 and Supplementary Movie 1). Initially, the tension signal was diffuse and included puncta of higher intensity. Within minutes, the tension signal localized to the cell edges and rapidly increased in intensity (up to 9% of probes were unfolded), which indicated that a larger density of hairpins were ruptured at those regions (force ≥4.7 pN). We determined the percentage of unfolded tension probes by calculating the fluorescence intensity of de-quenched dye corresponding to a fully opened hairpin probe, and assuming a linear relationship between the fraction of hairpins unfolded and the fluorescence intensity (Methods, Supplementary Figs 6 and 7, Supplementary Tables 5–9). Linescan analysis shows the progression of cellular forces across three nascent adhesions over a 5-min time period (Fig. 2). This timelapse sequence shows that cell adhesion forces are highly dynamic, heterogeneous and rapidly exceed the estimated 4.7 pN F1/2 during initial cell spreading.
To confirm that hairpin unfolding is mechanically mediated through integrin receptors, we plated rat embryonic fibroblasts expressing GFP-β3-integrin on 22% GC probe surface (Fig. 3a). Timelapse total internal reflection fluorescence microscopy showed tension signal co-localization with GFP, confirming that forces were primarily exerted through the β3 integrin receptors28,29, and that tension increases following recruitment of β3-integrin. Treatment of cells with latrunculin B, an inhibitor of actin polymerization, led to complete and rapid (1–3 min) decay of the tension signal, confirming that the signal is reversible and F-actin dependent (Supplementary Movie 2). In contrast, myosin II inhibition using blebbistatin or the ROCK inhibitor, Y27632, did not abolish integrin tension, but led to a lower density of unfolded probes (Fig. 3b). Control experiments in which cells were seeded onto RGD-lacking DNA probes, either with or without the hairpin structure, did not show any cell attachment or sensor activation (Supplementary Fig. 8a,b). Importantly, cells plated on a binary mixture of DNA sensors, one that lacked the RGD peptide, whereas the second lacking the dye-quencher pair, showed that the cells spread but failed to generate a fluorescence response (Supplementary Fig. 8c). Together, these results unambiguously demonstrate that hairpin probes report integrin-specific and cytoskeletal-mediated forces.
At later time points (~40 min) following cell seeding, we found that the fluorescence intensity under cells decreased to levels below that of the quenched sensor background, for both cyclic and linear RGD ligand (Supplementary Fig. 9). This loss in fluorescence was mainly due to force-induced dissociation of the ligand strand (Supplementary Fig. 10), rather than nuclease activity, or biotin-streptavidin dissociation, as observed with PEG-based MTFM probes20. Shearing of the fluorescent ligand-presenting strand is in agreement with recent results obtained using tension gauge tethers17. Although ligand strand shearing at later time points simply reduces fluorescence and does not lead to false positive signal, the current probe design is better suited for imaging early FA mechanics, and for imaging weaker receptor-mediated forces such epidermal growth factor endocytosis and Notch activation17,18,30.
Selective mechanical response toward linear and cyclic RGD
Given the molecular specificity of these probes, we next wondered whether integrin receptors would display mechanical selectivity when presented with a mixture of ligands. This is an important question because the ECM is comprised of nanoscale fibrillar protein assemblies that are chemically heterogeneous. For example, conventional techniques such as traction force microscopy report the average nN force from micrometre-sized elements, thus obscuring molecular specificity of tension in a complex mixture of ECM ligands4. We generated cRGDfK- and linear GRGDS-modified tension probes that were spectrally encoded by Cy3B-BHQ1 and Cy5-QSY21 reporters, respectively (Fig. 4). Both ligand strands were hybridized to the 77% GC content sensors and anchored to a substrate in 1:1 molar ratio. Cells plated onto this multiplexed surface generated signals that were highly localized at the lamella in the two fluorescence channels (Fig. 4b). However, the intensity of the linear peptide channel was significantly weaker, and showed at least a twofold smaller number of unfolded hairpins when compared with cRGDfK ligands and also when compared with the signal generated by surfaces exclusively presenting the linear GRGDS 77% GC content sensor (Supplementary Fig. 11). To exclude the possibility that this difference was due to fluorophore photophysics and other artefacts (Supplementary Figs 12–14), we swapped the dye-quenchers pair encoding and observed the same trend (Fig. 4c). These results show that integrin-ligand mechanical selectivity acts at the individual ligand level, whereby RGD ligand variants experience differential magnitudes of tension regardless of their spatial proximity. The mechanism for this selectively is likely due to lower integrin affinity for linear RGD ligands when compared with cyclic RGD peptides28. These results demonstrate how integrin receptors would mechanically respond when presented with chemically heterogeneous ECM ligands in more physiologically relevant settings.
F1/2-encoded probes to analyze force distribution within FAs
To analyze the spatial distribution of forces within individual growing adhesions, we spectrally encoded a binary mixture of cRGDfK tension probes with the 100 and 22% GC hairpins using the Atto647N and Cy3B dyes (Fig. 5a). As expected, cells attached and spread onto this 1:1 ratio multiplexed sensor surface, generating similar signals in both fluorescence channels (Fig. 5a and Supplementary Movie 3). Timelapse imaging showed that both probes displayed similar dynamics, spatial localization and intensities (unfolding percentage per unit area) during cell spreading and FA formation (Fig. 5a–c). This trend was maintained when the encoding was swapped (Supplementary Movie 4) or when both channels were encoded using the same 100% GC content probe. This general agreement between the two channels indicates that most engaged integrin receptors exerted tension that was greater than or equal to 13.1 pN.
Upon closer inspection of the data, we noted two additional features. The first was that a subset of FAs appeared larger and more intense in the 22% GC probe channel than the 100% GC probe channel (Fig. 5b). To quantify this observation, we measured the ratio of the signal intensity when the 100 and 22% GC content probes were encoded with Atto647N and Cy3B, respectively, and compared this to experiments with reversed encoding as well as control experiments where both probes used the 100% GC hairpin (Fig. 5d, n=15 cells; Supplementary Fig. 15). This confirms that a subset of integrins exert tension that is lower than 13.1 pN but greater than 4.7 pN. The existence of such a subpopulation is expected, as the tension must gradually rise per integrin during FA maturation.
The second observation was that a subset of FAs near the cell edge preferentially triggered the 100% GC probe over the 22% GC probe specifically at the tips of these adhesions (Fig 5c and e). To verify the statistical significance of this observation, we measured the offset between the start positions of tension signal in the two fluorescence channels when each channel encoded different hairpins and when each channel encoded the same 100% GC hairpin (as a control). Histogram analysis of 221 adhesions from 17 cells indicated that there is a subset of FAs where the 100% GC hairpin probe was triggered ~0.5 μm ahead of the 22% GC probe (Fig. 5e, and Supplementary Figs 16 and 17). This small population of FAs with an offset is not observed in the control experiment and is counterintuitive, as both probes are chemically identical and the 22% GC probes mechanically denature at significantly lower forces than the 100% GC probes. Thus, one would expect to observe the opposite phenomenon, that is, the 22% GC probe should be triggered closer to the cell edge because the integrin-ligand association rates are identical for both probes and initial adhesions likely exert lower magnitude forces that may not be sufficient to trigger the 100% GC content probes. Therefore, the offset in the start position of tension indicates that there is a small differential preference for integrins to remain bound to the more rigid 100% GC probes that can support higher forces before yielding, thus suggesting a molecular basis for cellular rigidity sensing of the substrate. Although further work is needed to fully elucidate the molecular underpinnings of the observed preference, the results obtained from multiplexed sensors highlight the unique capabilities of DNA-tension probes, providing a new approach to investigate differential integrin forces in a manner dependent on chemomechanical properties of individual ligand molecules.
DNA-based tension probes confer several advantages. First, the predictable secondary structure places the fluorophore-quencher pair in a well-defined position, thus lowering background signal and increasing the signal-to-noise ratio (~20- to 30-fold over background). This design strategy is widely used by molecular beacon-based assays31. Accordingly, the F1/2 is highly tailorable, and the hairpin can be precisely tuned to generate a clear binary response at a desired threshold tension (~1–20 pN)25. Second, by employing a three-strand system, we circumvent chemical modification of the hairpin oligonucleotide, and therefore, existing models can be used to estimate the F1/2. The three-strand design is also advantageous because it allows one to tune libraries of F1/2 values while avoiding re-synthesis of the anchor and ligand strands. In principle, the anchoring strand (and DNA-probes) can be attached to virtually any type of material, including three-dimensional matrices that better mimic the ECM, which is of great interest to the community. The caveat of the three-strand design pertains to force-induced shearing of the probe from the surface, which is a unique problem associated with the large mechanical loads in integrin-based mechanotransduction processes. Third, although an ensemble of DNA tension probes are engaged and activated within each diffraction limited region, which is necessary to support cell adhesion, we extract molecular details because each sensor functions as a digital switch for well-defined thresholds of force. Finally, the growing availability of inexpensive and rapid oligonucleotide synthesis allows one to easily generate and systematically test libraries of tension probes with tunable force sensitivity, thus ensuring the broad dissemination of this method.
DNA-based tension probes
All oligonucleotides were custom synthesized and purified by Integrated DNA Technologies, unless otherwise noted. This design consisted of a ssDNA hairpin hybridized through two 21-mer DNA handles to the ligand and anchor strands (Supplementary Table 1). Poly(T) was used for the hairpin loop sequence to avoid secondary structures and base stacking. The 3′ terminus of the anchor strand was modified with a biotin group to immobilize the oligonucleotide to a streptavidin surface. The alkyne group at the 5′ terminus of the ligand strand was used in a 1′,3′ dipolar cycloaddition click reaction to couple the appropriate RGD peptides. To generate multiplexed tension probe surfaces, each hairpin sensor was folded separately and then mixed at 1:1 ratio and added to the streptavidin surface.
F1/2 calculation for DNA hairpin
The following F1/2 calculation was primarily based on the assumptions and measurements used by Woodside et al.25 The total free energy of the hairpin can be described as follows:
where ΔGfold is the free energy of unfolding the hairpin at F=0, F is the externally exerted force, x is the hairpin extension and ΔGstretch is the free energy of stretching the ssDNA from F=0 to F=F1/2, and can be calculated from worm-like chain model as follows25:
where Lp is the persistence length of ssDNA (~1.3 nm), L0 is the contour length of ssDNA (~0.63 nm per nucleotide), x is the hairpin extension from equilibrium and was calculated by using (0.44 × (n-1)) nm, and kB is the Boltzmann constant and T is temperature.
To use these equations and estimate the F1/2 for each hairpin probe, we determined the sum of ΔGfold and ΔGstretch, and estimated the hairpin displacement needed for unfolding, Δx, by using ((0.44 × (n-1))-2) nm, where n represents the number of bases comprising the hairpin. Note that we subtract a distance of 2 nm because this corresponds to the initial separation between the hairpin termini, which is set by the diameter of the hairpin stem duplex (effective helix width)25. When F=F1/2, then the free energy of the transition equals zero and the F1/2 can be rearranged as follows:
In our calculations, ΔGstretch was determined using Supplementary Equation 2 without modification. ΔGfold was determined using nearest neighbour free energy parameters obtained from the IDT oligoanalyzer 3.1, which uses the UNAfold software package, and will now be referred to as ΔGIDT.
Equation (3) was used to infer the F1/2 for tension probes at experimental conditions (37 °C, 140.5 mM Na+ and 0.4 mM Mg2+), and these data are summarized in Supplementary Table 3.
Force probes calibration by BFP
The BFP measurement was based on previous work, which has been described in detail elsewhere27. In the BFP setup, a biotinylated RBC was first aspirated by a micropipette. A streptavidinylated glass bead was then attached to the apex of the RBC to form an ultra-sensitive force probe. On the opposite side, a bead coated with our DNA force probe was aspirated by a target micropipette. A piezoelectric translator (Physical Instrument) drove the target pipette with sub-nanometer precision via a capacitive sensor feedback control. The beads were assembled in a cell chamber filled with L15 media supplemented with 5 mM HEPES and 1% BSA and observed under an inverted microscope (Nikon TiE, Nikon) through two cameras. One camera (GC1290, Procilica) captured real-time images at 30 frames per second (f.p.s.), whereas the other (GE680, Proscilica) recorded at 1,600 f.p.s. as the region of interest was confined to the contact interface between the RBC and the bead. A customized LabView (National Instrument) programme analyzed the image and tracked in real time the position of the bead with a 3-nm displacement precision32. The BFP spring constant was set to ~0.3 pN nm−1, and it was determined from the suction pressure inside the probe pipette that held the RBC, the radius of the probe pipette, the diameter of the spherical portion of the RBC outside of the pipette and the contact area between the RBC and the probe bead32,33.
Briefly, in a measurement cycle, a DNA-coated 5-μm silica bead was brought into contact with the probe bead with a 20-pN impingement force for 0.1 s to allow bond formation. The target pipette was then retracted at 500 pN s−1 until it reached a 20-pN force level before dropping the force level to ~0 pN by bringing the two beads into close proximity again. The biotin-streptavidin bond was ruptured after 1 s, and the target bead was returned to the original position to start the next cycle. To ensure that most adhesion events were due to single bonds, adhesion frequency (number of adhesions divided by total number of contacts) was controlled to be ≤20% by adjusting the coating density of the DNA force probe34.
An unfolding event was identified by a dip in force level in the force-ascending phase (Supplementary Fig. 3a), because of the lengthening of the DNA upon hairpin opening. Similarly, a folding event was identified by a rise in force level in the force-descending phase. The force at which each unfolding event occurred was recorded and the cumulative histogram was plotted in Supplementary Fig. 3 to determine the F½.
QE measurement for different reporter pairs
To identify the optimal fluorophore-quencher pairs for the DNA-based MTFM probes, we synthesized a series of probes with different reporters and measured their QE (Supplementary Table 4). MTFM probes were anchored to supported lipid membrane, to minimize nonspecific binding and ensure a homogeneous and reproducible DNA density across all the tested pairs. Fluorophore labelling was performed as described in Supplementary Note 1 and associated text.
For all these measurements, a 45-mer hairpin (H45, ~15.38 nm, Supplementary Table 1) was used to ensure that the donor was completely dequenched upon hybridization. The fluorescence intensity of the hairpin sensor, IDA, was measured with the closed H45 in triplicate (Supplementary Fig. 4). To measure the donor only intensity, ID, H45 was hybridized to a complementary strand (tenfold molar excess), and then assembled with the DNA handles and anchored to the surface. Based on these measurements, we selected the Cy5-QSY21, Atto647N-QSY21 and Cy3B-BHQ1 pairs given their superior QE when compared with other fluorophore quencher combinations.
Calibration curve and determination of F factor and sensor density
This protocol has been adapted from Galush et al.35, and is briefly described in this section. To calibrate the fluorescence intensity, 1,2-dioleoyl-sn-glycero-3-phosphocholine (DOPC)-supported lipid membranes were doped with TRITC-DHPE lipids with concentrations ranging from 0 to 0.08 mol% and imaged under the same conditions used in live cell imaging (Supplementary Fig. 5). The number of fluorophore molecules per unit area was estimated from the footprint of DOPC, which was reported at 0.72 nm2. To use the calibration curve, the intensity of the ligand molecules was compared with the lipid-fluorophore standards to obtain the F factor. The F factor is defined as: , where Ibulk(sensor) and Ibulk(TRITC-DHPE) are the intensity of the ligand or lipid molecules in solution after being normalized for concentration. This value was measured on the fluorescence microscope by moving the focal plane (~200 μm) into the centre of the sample.
Measurement of QE (1- IDA/ID) on glass substrate
To determine the QE as a function of the hairpin used in DNA-based tension probes, we recorded the fluorescence intensity of the closed hairpin, IDA, on glass substrates at experimental conditions (37 °C, cell media; Supplementary Fig. 6a, c). To measure the donor only intensity, ID, tension probes were hybridized to their complementary strands (tenfold molar excess) and DNA handles (Supplementary Fig. 6b, d). Note that these QE value were in general agreement with the values obtained on supported lipid membranes in 1 × PBS at room temperature.
Conversion of IDA/ID to calculate the fraction of unfolded hairpins
To calculate the fraction of hairpins that are unfolded from any given cell experiment, we assumed that the fluorescence intensity of immobilized tension probes at resting (F=0 pN) corresponded to a monolayer of fully folded hairpins (0% unfolded, IDA). As hairpins that were hybridized with a tenfold excess of complementary stands are completely dequenched (Supplementary Fig. 4), the fluorescence intensity from this surface corresponds to hairpins that are 100% unfolded. Therefore, the fluorescence intensity of the 100% unfolded hairpins corresponds to ID. Given that there is a linear relationship between the fraction of unfolded hairpins and the QE, we used the ratio of IDA/ID to obtain this linear function (Supplementary Fig. 6e). This linear relationship was then used to convert the fluorescence intensity from the cell experiment to the fraction of unfolded hairpins (% unfolded).
Supplementary Tables 5–9 summarize all the imaging parameters used in our experiments. Sensors with GC content of 22% and 77% GC have the same length (25mer); therefore, these two sensors share the same values for QE, IDA/ID and conversion function, which were determined from the 77% GC probe surface. We assumed that the QE for each probe remained the same regardless of whether it was displayed in single-channel experiment or if it was included as part of a multiplexed surface with hairpins of different F1/2.
The glass substrates were covalently functionalized with biotin and modified with streptavidin by using previously published literature procedures18. Briefly, glass coverslips (number 2, 25-mm diameter; VWR) were sonicated in Nanopure water for 10 min and then etched in piranha (a 3:1 mixture of sulfuric acid (Avantor Performance Materials) and hydrogen peroxide (Sigma)) for 10 min (please take caution: piranha is extremely corrosive and may explode if exposed to organics). The glass coverslips were then washed six times in a beaker of Nanopure water (18.2 mω) and placed into three successive wash beakers containing EtOH (Decon Labs) and left in a final fourth beaker containing 1% (3-aminopropyl)triethoxysilane (Sigma) in EtOH for 1 h. The substrates were then immersed in the EtOH three times and subsequently rinsed with EtOH and dried under nitrogen. Substrates were then baked in an oven (~100 °C) for 10 min. After cooling, the samples were incubated with NHS-biotin (Thermo Fisher) at 2 mg ml−1 in dimethyl sulfoxide (Sigma) overnight. Subsequently, the substrates were washed with EtOH and dried under nitrogen. The substrates were then washed with 1 × PBS (3 × 5 ml) and incubated with BSA (EMD Chemicals, 100 μg μl−1, 30 min) and washed again with 1 × PBS (3 × 5 ml). Streptavidin was then added (1 μg ml−1 45 min, room temperature) followed by washing with 1 × PBS (3 × 5 ml). The chambers were then incubated with the DNA-based tension sensor (10 nM) for 1 h and rinsed before conducting cell experiments and imaging.
Supported lipid membrane preparation
The supported lipid bilayers were prepared by mixing 99.9% DOPC and 0.1% 1,2-dioleoyl-sn-glycero-3-phosphoethanolamine-N-(cap biotinyl) (sodium salt) (DPPE-biotin). The solution was dried with a rotary evaporator and placed under a stream of N2 to ensure complete evaporation of the solvent. These lipid samples were then resuspended in Nanopure water and subjected to three freeze/thaw cycles by alternating immersions in an acetone and dry ice bath and a warm water bath (40 °C). To obtain small unilamellar vesicles, lipids were extruded through a high-pressure extruder with a 200-nm nanopore membrane (Whatman). Supported lipid bilayers were assembled by adding small unilamellar vesicle’s to 1 M NaOH-etched 96-well plates with glass-bottomed wells. After blocking with 0.1% BSA for 30 min, bilayer surfaces were incubated with streptavidin (1 μg per 400 μl) for 1 h. Wells were rinsed three times with 5 ml of 1 × PBS, then incubated with the appropriate DNA hairpin sensors duplex (50 nM) for 1 h and rinsed 3 × with 5 ml of 1 × PBS before imaging.
High-performance liquid chromatography
All DNA conjugates were purified by using a C18 column (diameter: 4.6 mm; length: 250 mm) in a reverse phase binary pump high-performance liquid chromatography that was coupled to a diode array detector (Agilent 1100). The flow rate was generally set to 1 ml min−1 with a linear gradient of 10–60% B over 50 min (A: aqueous 0.1 M triethylammonium acetate buffer; B:acetonitrile (LC-MS Chromasolv, ≥99.9%; Fluka)). Unless otherwise noted, this elution gradient was followed by a second gradient of 60–100% B over 10 min to collect the more hydrophobic fractions.
Matrix-assisted laser desorption/ionization (MALDI)-time-of-flight mass spectroscopy
The matrix was prepared by dissolving 20 mg 3-hydroxypicolinic acid into 1 ml of matrix solvent (50% acetonitrile, 0.1% trifluoroacetic acid and 10% of a solution of 50 mg ml−1 ammonium citrate). 2 μl of this mixture was added to each well on the MALDI plate. After allowing the solution to dry for 20 min, the sample was analyzed by a high-performance MALDI time-of-flight mass spectrometer (Voyager STR).
Live cells were imaged in standard cell media at 37 °C, and fixed cells were imaged in 1% BSA in 1 × PBS at room temperature. During imaging, physiological temperature was maintained with a warming apparatus consisting of a sample warmer and an objective warmer (Warner Instruments, 641674D and 640375). The microscope was a Nikon Eclipse Ti driven by the Elements software package. The microscope features an Evolve electron multiplying charge-coupled device (Photometrics), an Intensilight epifluorescence source (Nikon), a CFI Apo × 100 (numerical aperture=1.49) objective (Nikon) and a TIRF launcher with two laser lines: 488 nm (10 mW) and 638 nm (20 mW). This microscope also includes the Nikon Perfect Focus System, an interferometry-based focus lock that allowed the capture of multipoint and time-lapse images without loss of focus. The microscope was equipped with the following Chroma filter cubes: TIRF 488, TRITC, Epi 640 and reflection interference contrast microscopy (RICM).
All DNA oligonucleotides were allowed to fold into their hairpin secondary structure in 50 μl PBS at a concentration of 100 nM in a 0.2-ml Thermowell Tube. All oligonucleotides were first denatured at 75 °C for 5 min. This was followed by a renaturation step in which the temperature was allowed to return to room temperature at a rate of 1.3 °C min−1.
HCC1143 human breast carcinoma cells were cultured in RPMI 1640 medium (Mediatech) supplemented with 10% FBS (Mediatech), HEPES (9.9 mM, Sigma), sodium pyruvate (1 mM, Sigma), L-glutamine (2.5 mM, Mediatech), penicillin G (100 IU ml−1, Mediatech) and streptomycin (100 μg ml−1, Mediatech) and were incubated at 37 °C with 5% CO2. Cells were passaged at 90% confluency and plated at a density of 50% and media renewed every 3 days. NIH 3T3 mouse embryonic fibroblasts and rat embryonic fibroblasts expressing GFP-β3-integrin cells were cultured in DMEM (Mediatech) supplemented with 10% Calf Serum (Mediatech), L-glutamine (2.5 mM, Mediatech), penicillin G (100 IU ml−1, Mediatech) and streptomycin (100 μg ml−1, Mediatech) at 37 °C with 5% CO2. Cells were passaged at 80% confluency and plated at a density of 4 × 103 cells per cm2 (100 × 103 cells per flask) and media renewed every 3 days.
The fluorescent dye Cy5 NHS ester (Cat. # 23020) was purchased from Lumiprobe corporation. The fluorescent dye Cy3B NHS ester (Product code: PA63101) was purchased from GE Healthcare Life Science. Quencher QSY21 succinimidyl ester (Cat. # Q-20132) was purchased from Life Technologies. The fluorescent dye Atto 647N NHS ester was purchased from Sigma-Aldrich. Cyclo [Arg-Gly-Asp-d-Phe-Lys(PEG-PEG)] (Product code: PCI-3696-PI, c(RGDfK(PEG-PEG)), PEG=8-amino-3,6-dioxaoctanoic acid) was acquired from Peptides International. Gly-Arg-Gly-Asp-Ser (Cat. # G4391) was purchased from Sigma-Aldrich. Glass coverslips (number 2, 25 mm diameter) were acquired from VWR. The heterobifunctional linkers NHS-azide (#88902) and NHS-biotin (#20217) were purchased from Thermo Fisher Scientific. Ascorbic acid (>99.0%) and 96-well plates were purchased from Fisher Chemical & Scientific. Dimethylformamide (DMF) (>99.5%), dimethyl sulfoxide (99.5%) and sodium bicarbonate (99.0%) were acquired from EMD chemicals. Sulfuric acid was acquired from Avantor Performance Materials. Ethyl alcohol (EtOH) (200 proof) was purchased from Decon Labs. 3-Aminopropyltriethoxysilane and CH3(CH2CH2O)9-12(CH2)3Si(OCH3)3 (mPEG) were acquired from Gelest. Unless otherwise stated, all the other starting materials and reagents were purchased from Sigma-Aldrich and used without further purification. All buffers were made with Nanopure water (18.2 MΩ) and passed through a 0.2 μm filtration system.
How to cite this article: Zhang, Y. et al. DNA-based digital tension probes reveal integrin forces during early cell adhesion. Nat. Commun. 5:5167 doi: 10.1038/ncomms6167 (2014).
Burridge, K., Fath, K., Kelly, T., Nuckolls, G. & Turner, C. Focal adhesions—Transmembrane junctions between the extracellular-matrix and the cytoskeleton. Annu. Rev. Cell Biol. 4, 487–525 (1988).
Kanchanawong, P. et al. Nanoscale architecture of integrin-based cell adhesions. Nature 468, 580–584 (2010).
Schoen, I., Pruitt, B. L. & Vogel, V. The Yin-Yang of Rigidity Sensing: how forces and mechanical properties regulate the cellular response to materials. Annu. Rev. Mater. Res. 43, 589–618 (2013).
Plotnikov, S. V., Pasapera, A. M., Sabass, B. & Waterman, C. M. force fluctuations within focal adhesions mediate ECM-rigidity sensing to guide directed cell migration. Cell 151, 1513–1527 (2012).
Sabass, B., Gardel, M. L., Waterman, C. M. & Schwarz, U. S. High resolution traction force microscopy based on experimental and computational advances. Biophys. J. 94, 207–220 (2008).
Tan, J. L. et al. Cells lying on a bed of microneedles: an approach to isolate mechanical force. Proc. Natl Acad. Sci. USA 100, 1484–1489 (2003).
Lemmon, C. A. et al. Shear force at the cell-matrix interface: enhanced analysis for microfabricated post array detectors. Mech. Chem. Biosyst 2, 1–16 (2005).
Dumbauld, D. W. et al. How vinculin regulates force transmission. Proc. Natl Acad. Sci. USA 110, 9788–9793 (2013).
Discher, D. E., Janmey, P. & Wang, Y. L. Tissue cells feel and respond to the stiffness of their substrate. Science 310, 1139–1143 (2005).
Ghassemi, S. et al. Cells test substrate rigidity by local contractions on submicrometer pillars. Proc. Natl Acad. Sci. USA 109, 5328–5333 (2012).
Schwarz, U. S. et al. Calculation of forces at focal adhesions from elastic substrate data: The effect of localized force and the need for regularization. Biophys. J. 83, 1380–1394 (2002).
Wiseman, P. W. et al. Spatial mapping of integrin interactions and dynamics during cell migration by Image Correlation Microscopy. J. Cell Sci. 117, 5521–5534 (2004).
Grashoff, C. et al. Measuring mechanical tension across vinculin reveals regulation of focal adhesion dynamics. Nature 466, 263–266 (2010).
Cai, D. F. et al. Mechanical feedback through E-cadherin promotes direction sensing during collective cell migration. Cell 157, 1146–1159 (2014).
Conway, D. E. et al. Fluid shear stress on endothelial cells modulates mechanical tension across VE-cadherin and PECAM-1. Curr. Biol. 23, 1024–1030 (2013).
Borghi, N. et al. E-cadherin is under constitutive actomyosin-generated tension that is increased at cell-cell contacts upon externally applied stretch. Proc. Natl Acad. Sci. USA 109, 19034–19034 (2012).
Wang, X. & Ha, T. Defining single molecular forces required to activate integrin and notch signaling. Science 340, 991–994 (2013).
Stabley, D. R., Jurchenko, C., Marshall, S. S. & Salaita, K. S. Visualizing mechanical tension across membrane receptors with a fluorescent sensor. Nat. Methods 9, 64–67 (2012).
Liu, Y., Yehl, K., Narui, Y. & Salaita, K. Tension sensing nanoparticles for mechano-imaging at the living/nonliving interface. J. Am. Chem. Soc. 135, 5320–5323 (2013).
Jurchenko, C., Chang, Y., Narui, Y., Zhang, Y. & Salaita, K. S. Integrin generated forces lead to streptavidin-biotin unbinding in cellular adhesions. Biophys. J. 106, 1436–1446 (2014).
Liu, Y. et al. Nanoparticle tension probes patterned at the nanoscale: impact of integrin clustering on force transmission. Nano Lett doi:10.1021/nl501912g (2014).
Morimatsu, M., Mekhdjian, A. H., Adhikari, A. S. & Dunn, A. R. Molecular tension sensors report forces generated by single integrin molecules in living cells. Nano Lett. 13, 3985–3989 (2013).
Xia, T., Li, N. & Fang, X. Single-molecule fluorescence imaging in living cells. Annu. Rev. Phys. Chem. 64, 459–480 (2013).
Henriques, R., Griffiths, C., Rego, E. H. & Mhlanga, M. M. PALM and STORM: unlocking live-cell super-resolution. Biopolymers 95, 322–331 (2011).
Woodside, M. T. et al. Nanomechanical measurements of the sequence-dependent folding landscapes of single nucleic acid hairpins. Proc. Natl Acad. Sci. USA 103, 6190–6195 (2006).
Liphardt, J., Onoa, B., Smith, S. B., Tinoco, I. Jr. & Bustamante, C. Reversible unfolding of single RNA molecules by mechanical force. Science 292, 733–737 (2001).
Liu, B., Chen, W., Evavold, B. D. & Zhu, C. Accumulation of dynamic catch bonds between TCR and agonist peptide-MHC triggers T cell signaling. Cell 157, 357–368 (2014).
Englund, E. A. et al. Programmable multivalent display of receptor ligands using peptide nucleic acid nanoscaffolds. Nat. Commun. 3, 614 (2012).
Liu, S. Radiolabeled cyclic RGD peptides as integrin alpha(v)beta(3)-targeted radiotracers: maximizing binding affinity via bivalency. Bioconjug. Chem. 20, 2199–2213 (2009).
Narui, Y. & Salaita, K. Membrane tethered delta activates notch and reveals a role for spatio-mechanical regulation of the signaling pathway. Biophys. J. 105, 2655–2665 (2013).
Tan, W., Wang, K. & Drake, T. J. Molecular beacons. Curr. Opin. Chem. Biol. 8, 547–553 (2004).
Chen, W., Evans, E. A., McEver, R. P. & Zhu, C. Monitoring receptor-ligand interactions between surfaces by thermal fluctuations. Biophys. J. 94, 694–701 (2008).
Evans, E., Ritchie, K. & Merkel, R. Sensitive force technique to probe molecular adhesion and structural linkages at biological interfaces. Biophys. J. 68, 2580–2587 (1995).
Chesla, S. E., Selvaraj, P. & Zhu, C. Measuring two-dimensional receptor-ligand binding kinetics by micropipette. Biophys. J. 75, 1553–1572 (1998).
Galush, W. J., Nye, J. A. & Groves, J. T. Quantitative fluorescence microscopy using supported lipid bilayer standards. Biophys. J. 95, 2512–2519 (2008).
We are grateful for support from the NIH (R01-GM097399), the Alfred P. Sloan Research Fellowship, the Camille-Dreyfus Teacher-Scholar Award and the NSF CAREER Award (1350829). We also thank Dr Jin-Tang Dong, Emory Department of Hematology and Medical Oncology, School of Medicine, for the HCC 1143 cells; Dr Jeremy Boss, Emory Microbiology and Immunology, School of Medicine, for the NIH 3T3 fibroblasts; Dr Ada Cavalcanti-Adam, Max-Planck-Institute and University of Heidelberg, and Dr Benjamin Geiger, Department of Molecular Cell Biology at Weizmann Institute, for rat embryonic fibroblast cells transfected with the GFP-β3-integrin.
The authors declare no competing financial interests.
Supplementary Figures 1-17, Supplementary Tables 1-9 and Supplementary Notes 1-2 (PDF 1709 kb)
Supplementary Movie 1 is a timelapse video showing the integrin tension dynamics of a cell attached to a surface. The left panel shows the reflection interference contrast microscopy (RICM) channel, the center panel shows the fluorescence signal resulting from integrin tension, and the right channel shows an overlay of both RICM and tension channels. A 22% GC content hairpin (4.7 pN) encoded using Cy3B was used for this experiment. The duration of the video was 8 min. Scale bar = 10 μm. (AVI 4374 kb)
Supplementary Movie 2 is a timelapse video that shows the effect of latrunculin B treatment on integrin tension. The left channel shows the RICM while the right channel shows the integrin tension. Latrunculin B was added at t = 0 when we started recording the video. The duration of the timelapse was 6 min. Scale bar = 10 μm. (AVI 6803 kb)
Supplementary Movie 3 is a timelapse video showing integrin tension dynamics recorded using two different types of force sensors reported in two fluorescence channels. The left channel shows the RICM signal, while the green and red channels represent integrin tension as reported through a 22% GC content (4.7 pN) and 100% GC content (13.1 pN) hairpin, respectively. The far right channel shows an overlay of the two integrin tension signals. The duration of the video is 31.5 min and we started recording the video upon the initial adhesion and spreading of a 3T3 fibroblast cell. This movie shows that both probes displayed similar dynamics, spatial localization, and intensities (unfolding percentage per unit area) during cell spreading and FA formation. Scale bar = 10 μm. (AVI 4394 kb)
Supplementary Movie 4 is a timelapse video of a 3T3 fibroblast cell spreading on a multiplexed sensor surface encoded using the Cy3B-100% GC hairpin and the Atto647N-22% GC hairpin (reversed encoding of supplementary Movie 3). Images were acquired for a duration of 9 min at 30 s intervals. The left channel was RICM and the green and red channels report tension through the 100% GC content, and 22% GC content hairpins, respectively. The far right channel shows an overlay of the two tension channels. Scale bar is 10 μm. (AVI 1039 kb)
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Zhang, Y., Ge, C., Zhu, C. et al. DNA-based digital tension probes reveal integrin forces during early cell adhesion. Nat Commun 5, 5167 (2014). https://doi.org/10.1038/ncomms6167
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