We developed an inclined dual fiber optical tweezers (DFOTs) for simultaneous force application and measurements in a 3D hydrogel matrix. The inclined DFOTs provide a potential solution for cell mechanics study in a three-dimensional matrix.
- fiber optics
- optical trapping and manipulation
- optical tweezers
- mechanical properties measurement
- cell mechanics study
Optical tweezers (OTs) have been widely used in manipulating micro- or nanoscale particles and measuring nanometer-scale displacements since Arthur Ashkin pioneered the field in the early 1970s . OTs have enabled significant advances in a range of applications in in biological and physical researches, such as the study of the motion of individual motor proteins [2, 3], rheology measurements of cell cytoskeleton response to external stimuli [4, 5], and mechanical properties of polymers . Conventional OTs rely on high-numerical-aperture objective lenses. The intrinsic limitations, such as being bulky, expensive, the lack of flexibility, and the requirement of substrate transparency, significantly hinder the application of conventional OTs in emerging biophysical topics such as cellular mechanics in a three-dimensional (3D) environment.
Both mechanical forces generated by cells  and external forces applied on cells  have been shown not only to determine cell behaviors, but also to regulate biological development such as proliferation  and differentiation . Currently, most of cellular force characterization has been carried out on deformable and homogeneous cell substrates [11, 12]. Cellular traction force can be backed out by measuring the local deformation of substrate. These techniques are also called traction force microscopy (TFM). Polyacrylamide gel is one of the most commonly used substrates for TFM. Its linear elastic properties lie in the range of deformation induced by single cells. Therefore, Polyacrylamide gel has been wildly used to measure cellular forces based on the substrate deformation during the cell attachment and migration , to investigate cell behaviors under various conditions of extracellular matrix (ECM) (e.g., by varying substrate stiffness) [13, 14], and to study traction forces of cells fully encapsulated in an elastic gel matrix .
In TFM, the mechanical properties of the substrate have to be pre-characterized in order to obtain the cell traction forces from the measured deformation field. Generally, local mechanical properties of the substrates, such as polyacrylamide gel, is measured by using atomic force microscopy (AFM) [16, 17]. However, the AFM based microrheology measurements require physical contact, and the resolution of lateral force measurements is limited. Micropost arrays  are an alternative substrate structure that has been used to replace polyacrylamide gel. However, these techniques cannot measure cellular forces in 3D compartments. Measurements of cellular traction forces in 3D compartments are important, since the behaviors of cells are different in a native environment, which is always inhomogeneous and 3D, compared to a 2D substrate . Legant et al. quantified traction forces of cells embedded in a 3D hydrogel matrices by tracking a large number of fluorescent beads around the cells . However, it is challenging to provide real-time measurements, since the post-process is time-consuming. In addition, a homogeneous elastic medium is required in order to back out the cellular forces for all the techniques mentioned above.
In this chapter, we demonstrate a versatile and flexible fiber optical trapping system, namely the inclined dual fiber optical tweezers (DFOTs) [20, 21], for measuring forces on and applying forces to particles embedded in a 3D compartment, without requiring any physical contact with the particles. It can reach anywhere in a liquid medium and does not require the substrate transparency. The trap can work with particles high above the substrate or those encapsulated inside a solid 3D compartment but close to the surface. Since the inclined DFOTs create traps without relying on the bulky objective lens, they have great potential to be miniaturized and integrated.
We demonstrate that the maximum force provided by the inclined DFOTs is comparable with that of conventional optical tweezers. For example, in our experiment with the inclined DFOTs, we obtained an optical force of ~20 pN on a 4.63 μm silica bead when an optical power at each fiber tip was 100 mW. By comparison, the maximum optical trapping forces provided by the conventional OTs is around 10 pN per 100 mW for micrometer-sized beads . Moreover, compared with conventional OTs, the inclined DFOTs could allow a higher optical trapping power before possible photodamage occurs to a trapped cell. This is due to the following two reasons. (1) The optical power is distributed over a large area of cell surfaces from both sides of the inclined DFOTs, and hence the intensity is lower on the cell. By comparison, conventional optical tweezers focusing all the power in a sub-micron spot, resulting in a higher intensity and likelihood of photodamage with the same power. (2) The optical beam size in the inclined DFOTs is around 30 μm at the trap position (beam intersection), so the effective trapping power illuminated on a 5 μm bead is much less than the power emitted from the fiber tip.
In this work, the calibration of the optical trapping spring constant was carried out on microscale silica beads in water as well as those embedded in 3D polyacrylamide gel compartments. In addition, the
2.1. System setup and working principles
In the optical trap, optical forces arise from the momentum transfer during the scattering or refraction of incident photons . When a dielectric particle, with a refractive index higher than the surrounding medium, is illuminated by a light beam, it will change the direction of light beam and in turn experience a force that is described as the sum of two components: a scattering force directed along the light beam and a gradient force pointing to the region of maximum light intensity. Traditionally, an optical trap is created by focusing a single laser beam with a high numerical aperture objective, which is called objective based OTs. Unlike objective based OTs, the inclined DFOTs create traps based on two inclined optical beams that can apply two sets of gradient forces and scattering forces, as shown Figure 1(a). Once the four optical forces balance with all other forces that the particle is subject to, such as viscous drag force and gravity, a 3D optical trap can be successfully created.
The setup of the inclined DFOTs was based on our previous work [20, 24, 25]. Briefly, we set up the inclined DFOTs on an inverted microscope platform. Each fiber was mounted on a common board and was aligned with respect to the other via a miniature 3D translational stage and a micro 1D rotational stage, as shown in Figure 1(a). The fiber inclination angle and fiber separation was also controlled by adjusting these stages. The position of the optical trap was then adjusted by manipulating the common board via another 3D translational stage.
The measurement setup is shown in Figure 1(b). Light from a 980 nm laser diode (AC 1405-0400-0974-SM-500, Eques) was split into two lensed fibers (Nanonics Imaging, Ltd) through a 3 dB coupler. The equalized optical power outputs from the two lensed fiber ends were ensured by attenuators. When a micro silica bead in water or in polyacrylamide gel was trapped, the light scattered by the bead was collected by an objective lens and detected by a position-sensitive detector (PSD) (DL100-7-PCBA3, First Sensor), which enabled precision measurements of bead displacements in the
2.2. Power spectrum calibration of optical spring constant
In this paper, calibration of the optical tweezers was accomplished by the power spectrum analysis method . In the power spectrum analysis, the motion of a particle was confined by the restoring “spring” forces provided by the optical trap as well as the surrounding medium (such as the polyacrylamide gel) and can be expressed by 
In our experiments, the motion of the trapped particle was detected by the PSD output signals that were recorded in a period of 5 seconds at a sampling rate of 50 kHz. Its power spectra were obtained by complex Fourier transform of the PSD signals . The sampling rate in the experiment was much larger than the measured corner frequency, which in our case is tens of Hz. The exponential distributed power spectrum data were then blocked and transformed to Gaussian distribution, which was used to follow the least square curve fitting. Being fitted to a Lorentzian in Eq. (1) with a frequency range of 10–800 Hz, the blocked power spectra provided the calibration results of the spring constants following Eq. (2). The calibration of the spring constant of the inclined DFOTs does not require excitation of particle motion at any specific frequencies. The calibration is passive and relies only on monitoring the confined Brownian motion of trapped particle. Therefore, the inclined DFOTs can be used for
2.3. Experimental measurements in water
We first investigated the dependence of the spring constant of the inclined DFOTs on the optical power in water, which allowed us to better characterize the inclined DFOTs. The results obtained in water set the base for polyacrylamide gel characterization that was described in Section 2.4. Silica beads (Bangs Laboratories, Inc.) with a density of 2.0 g/cm3 and a diameter of 4.63 μm were used in all experiments. A diluted silica bead solution, with a ratio of deionized (DI) water to original bead solution (10.2%, 0.5 g in weight) at 6000:1 was ultrasonicated in order to reverse bead aggregation. One drop of diluted bead solution (~0.2 ml) was added on a coverglass, where the trapping experiment was carried out. In order to reduce the sidewall effects, we accomplished the optical trap calibration with beads 3D trapped around 35 μm above the coverslip .
2.4. Experiment measurements in polyacrylamide gel
In this experiment, the inclined DFOTs were used to apply tunable forces on a bead embedded in the polyacrylamide gel without any physical contact. In the meantime, the resultant motion of the bead was monitored and measured by the PSD to enable spring constant calibration of both the optical trap and the polyacrylamide gel. By varying the optical power, the optical force provide by the inclined DFOTs was readily tuned, which enables the calibration of the effective spring constant of the hydrogel.
2.4.1. Polyacrylamide gel sample preparation
Polyacrylamide gels were fabricated on 25 × 25 mm2 coverslips. In all the experiments, we prepared the polyacrylamide gel solution with the desired concentration of 5% acrylamide and 0.04% bisacrylamide in a pH 8.2 HEPES buffer. By adding 3 μl tetramethylethylenediamine (TEMED) and 10 μl of 10% ammonium persulfate (APS) solution for each 1 ml of polyacrylamide gel solution, we can initiate the polymerization process. The polyacrylamide gel solution was then quickly transferred to a glutaraldehyde-activated coverslip and covered by a second plasma-cleaned coverslip, on which dried silica beads with a diameter of 4.63 μm were attached previously. A polymerized polyacrylamide gel with a desired thickness of ~ 50 μm was achieved by controlling the volume of polyacrylamide gel solution on each coverslip to be 30 μl. The gelation was complete after curing the gel solution for 15 minutes at the room temperature. We obtained the polyacrylamide gel sample with silica beads embedded on the its top after peeling off the second coverslip. Due to the deformation of the polyacrylamide gel during the polymerization process, not all the beads are on the polyacrylamide gel surface. Beads close to the surface of the polyacrylamide gel were selected for the optical trapping experiments.
2.4.2. Optical trapping experiment of polyacrylamide gel calibration
The optical trapping experiment of polyacrylamide gel calibration was carried out by analyzing the confined motion of the bead, which resulted from the confinement effects of both the optical trap and the polyacrylamide gel. A bead close to the polyacrylamide gel top surface was first identified, and the inclined DFOTs were moved to this pre-identified location so that the bead was in the optical trap. The power spectrum measurements enabled the calibration of an effective spring constant. The tunable optical spring constant was achieved by varying the optical power, which allowed the polyacrylamide gel stiffness to be calibrated.
2.4.3. AFM measurements of polyacrylamide gel moduli
In this work, AFM [16, 17] was used to characterize local viscoelastic properties of polyacrylamide gel around the bead that was studied in the inclined DFOTs. An Asylum Research MFP3D-BIO AFM (Asylum Research, CA) was used for the measurements. Briefly, The AFM cantilever was first moved to the location above the polyacrylamide gel top surface around the selected bead that was studied by the inclined DFOTs. The cantilever was then lowered down to create an approximate 2 μm indentation in the gel. A small oscillating indentation at the tip was generated by driving the cantilever sinusoidally with an amplitude of 25 nm and a frequency
3. Experimental results and discussion
3.1. Experimental results in DI water and discussion
In this section, we will demonstrate the capability of the inclined DFOTS to apply and measure 3D forces in aqueous environments.
3.1.1. 3D trapping of yeast cells in DI water
3D trapping of silica beads with the inclined DFOTs was demonstrated in our previous work [20, 24, 25]. Here, we show that the inclined DFOTs are also applicable to 3D trapping of biological samples. In this experiment, the inclined DFOTs were used to trap and manipulate a living yeast cell in all three dimensions in DI water, as shown in Figure 2. The trapped yeast cell was moved via controlling the aluminum board (see yellow block in Figure 1(a)) by a single 3D stage (not shown in Figure 1(a)). The maximum moving speed of the trapped cells was dependent on the optical power. For example, the maximum moving speed was measured to be around 20 μm/s before the yeast cells escaped from the trap, when the optical power is 6.8 mW from each fiber. Manipulating the 3D positions of living cells bestows on the inclined DFOTs the capability of relocation and assembly of living biological particles with micrometer size.
3.1.2. Optical trapping spring constant calibration in water
Silica beads with the size of 4.63 μm were used to carry out the calibration of the trapping spring constant. The uniformity in shape and material properties allows silica beads to serve as appropriate samples for evaluating the capability of the inclined DFOTs.
The optical trapping spring constant can be measured by the bead displacement power spectrum when a silica bead is trapped in three dimensions in water. Figure 3(a) and (c) show the typical power spectrum data of a bead trapped in water in the
It is noted that the optical force can be calculated by multiplying optical trapping spring constant by the bead displacement. The results in Figure 3(b) and (d) indicate that the inclined DFOTs can provide forces ranging from sub-pN to tens of pN. It implies that the inclined DFOTs can be used to measure cellular forces, since various cellular forces lie in this range, such as those generated by neural growth cone  and by a single actin filament . Compared with the force sensing range of AFM, which is in the range of 10 pN to 100 nN , the force range of inclined DFOTs may extend the range of the biological applications and measurable quantities that may be challenging for AFM.
The error bars in Figure 3(b) and (d) are the 95% confidence interval ranges of the Lorentzian curve fitting. It can be seen that there is a linear relationship between the spring constant and the optical power in both
There are data points in Figure 3(b) and (d) scattering around the fitted linear curve. This may be that the
3.2. Experimental measurements of polyacrylamide gel and discussion
3.2.1. Experimental results measured by inclined DFOTs
In the experiments, the effective spring constant was changed by tuning the optical power. We obtained the dependence of effective spring constant on power in the
Since the calibration of the material equivalent spring constant is accomplished by monitoring the bead confined Brownian motion, the inclined DFOTs can used to measure the stiffness of nonlinear materials. We estimate that the effective root-mean-square displacement of the Brownian motion is around 0.6 nm for a bead embedded in a material with an equivalent spring constant of 0.012 N/m at the room temperature. Most of the materials can be considered to be linear and uniform in such a small range as 0.6 nm, so the material equivalent spring constant can be calibrated
In addition, unlike traditional AFM measurements which require physical contact, no physical contact is needed for the inclined DFOTs. This enables the inclined DFOTs to work with particles embedded in 3D matrices. Although the traction force microscopy has been demonstrated in a homogenous 3D medium, it is still challenging to realize real-time measurements due to the requirement of tracking large numbers of fluorescent beads . By comparison, the inclined DFOTs have a potential to provide a real-time, versatile, and non-invasive way to measure the material properties inside a 3D heterogeneous and nonlinear medium.
It is noted that laser illumination can affect the mechanical properties of polyacrylamide gel in the experiment. For example, under laser illumination, local temperature changes originating from optical absorption of the trapped particle can change the surrounding medium viscosity . The polyacrylamide gel stiffness has also been observed to change under localized laser illumination [31, 32]. Moreover, polyacrylamide gel mechanical integrity can also be changed  due to the nature of polyacrylamide gel swelling. In addition, the effective polyacrylamide gel property may be influenced due to the imperfect contact condition at the interface between bead and surrounding polyacrylamide gel. In our experiments, we noticed differences in data obtained in water and polyacrylamide gel, mainly in the slope of spring constant-power curve, shown in Figures 3(b), (d), and 4(b). Although we do not fully understand how the polyacrylamide gel has been changed by laser illumination, we observed the linear dependence of corner frequencies on optical power, because the spring constant-power data in polyacrylamide gel can be well fitted by linear functions. According to the repeatability of our optical trapping measurements of the polyacrylamide gel stiffness, we believe the laser-induced polyacrylamide gel changes are reversible. As a result, the capability of the inclined DFOTs to measure the intrinsic polyacrylamide gel stiffness will not be influenced by the laser induced polyacrylamide gel changes, since the measurement of the intrinsic polyacrylamide gel stiffness with the inclined DFOTs is determined by the intersect of the linear fitting curve on the vertical axis.
3.2.2. Experimental results measured by AFM
AFM based microrheology measurements [16, 17] were also used to characterize the local viscoelasticity of polyacrylamide gel. In this work, AFM was used to serve as a reference to verify the inclined DFOTs measurements. To ensure the statistical measurements, we characterized the viscoelastic properties of polyacrylamide gel at 19 different locations around the bead of interest. The typical AFM force and indentation curves, shown in Figure 5(a), can be fitted by sinusoidal function to remove noise. Figure 5(b) plots the force as a function of indentation. Its raw data and the corresponding fitted data is shown as the blue and red curves, respectively. The hysteresis in Figure 5(b) indicates the viscoelasticity of polyacrylamide gel, which can be used to back out the elastic and viscous moduli. Following the analysis method in Ref. , the elastic and viscous moduli of the polyacrylamide gel can be calculated and obtained to be 1469.9 ± 555.9 Pa and 533.2 ± 243.4 Pa, respectively. The mean values and standard deviations of the moduli were determined by 19 independent measurements. As a result, based on the viscous moduli of the polyacrylamide gel, we obtained its viscosity to be 8.5 ± 3.9 Pa ⋅ s.
3.2.3. Comparison of the inclined DFOTs and AFM results
In the experiments, the optical trapping experiments measure the effective spring constants (with a unit of N/m) on a silica bead, which is dependent on bead size, the bead location, and the elastic modulus of polyacrylamide gel. However, AFM measures the elastic modulus (with a unit of Pa). To compare them, we used the commercial finite element analysis software (COMSOL) to calculate the spring constant on a bead embedded in the top surface of polyacrylamide gel using the elastic modulus measured from the AFM experiments. We then compared the spring constant obtained by the inclined DFOTs measurements with that calculated from COMSOL.
We use the Kelvin-Voigt model to describe the viscoelasticity of polyacrylamide gel in the simulation. By applying a 20 nN static body force applied parallel to the polyacrylamide gel surface, we obtain the displacement of a silica bead embedded in the polyacrylamide. The polyacrylamide gel stiffness is then calculated based on the resultant bead displacement and the applied force.
According to the procedures of polyacrylamide gel preparation, the beads selected for optical trapping measurements were always close to the top surface of polyacrylamide gel. However, due to the polyacrylamide gel deformation during the polymerization process, it was challenging to determine the precise position of the bead with respect to the polyacrylamide gel top surface. Therefore, it was important to investigate the influence of the polyacrylamide gel stiffness on the depth of the bead in the simulation. In the simulation, we obtain the polyacrylamide gel stiffness shown in Figure 6(a)–(c) to be 0.0154 N/m, 0.0177 N/m, and 0.0206 N/m, respectively. It is noted that the deeper the bead, the larger the stiffness. In addition, due to the weaker polyacrylamide gels surface effects, the rate of change of the stiffness is smaller with deeper bead positions. The polyacrylamide gel displacement field is not influenced much by the surface when the bead is far away from the polyacrylamide gel surface, as shown in Figure 6(c). When the bead is deeper than 10 μm from the surface, the stiffness variation becomes small, as shown in Figure 6(d).
According to the simulation results shown in Figure 6(d), we can see that the optical trapping measurement of polyacrylamide gel stiffness agrees with the simulation results based on AFM measurements when the bead top surface is in the range from −1 to 2 μm above the polyacrylamide gel surface. This proves that the inclined DFOTs can be a reliable tool to realize
The ability of simultaneously applying and measuring forces enables the inclined DFOTs to be a potential tool for cell mechanics study in 3D compartments. The spring constant measurements bestows upon the inclined DFOTs capable of directly measuring forces on the bead if the displacement is monitored.
In this chapter, we show the inclined dual fiber optical tweezers (DFOTs) can be used for simultaneous applications and measurements of optical forces on particles in water and those in a 3D polyacrylamide gel compartment. Moreover, we demonstrate
This research is supported by the National Science Foundation under Grant No. CBET-1403257.
Ashkin A. Acceleration and trapping of particles by radiation pressure. Physical Review Letters. 1970; 24:156
Svoboda K, Schmidt CF, Schnapp BJ, Block SM. Direct observation of kinesin stepping by optical trapping interferometry. Nature. 1993; 365:721-727
Finer JT, Simmons RM, Spudich JA. Single myosin molecule mechanics: Piconewton forces and nanometre steps. Nature. 1994; 368:113-119
Fabry B, Maksym GN, Butler JP, Glogauer M, Navajas D, Fredberg JJ. Scaling the microrheology of living cells. Physical Review Letters. 2001; 87:148102
Fredberg J, Fabry B. The cytoskeleton as a soft glassy material. In: Mofrad MRK, Kamm RD, editors. Cytoskeletal Mechanics: Models and Measurements. Cambridge, NY: Cambridge University Press; 2006
Grier DG. Optical tweezers in colloid and interface science. Current Opinion in Colloid & Interface Science. 1997; 2:264-270
Dembo M, Wang Y-L. Stresses at the cell-to-substrate interface during locomotion of fibroblasts. Biophysical Journal. 1999; 76:2307-2316
Hickory WB, Nanda R. Effect of tensile force magnitude on release of cranial suture cells into S phase. American Journal of Orthodontics & Dentofacial Orthopedics. 1987; 91:328-334
Chen CS, Mrksich M, Huang S, Whitesides GM, Ingber DE. Geometric control of cell life and death. Science. 1997; 276:1425-1428
Roskelley C, Desprez P, Bissell M. Extracellular matrix-dependent tissue-specific gene expression in mammary epithelial cells requires both physical and biochemical signal transduction. Proceedings of the National Academy of Sciences. 1994; 91:12378-12382
Harris AK, Wild P, Stopak D. Silicone rubber substrata: A new wrinkle in the study of cell locomotion. Science. 1980; 208:177-179
Schoen I, Pruitt BL, Vogel V. The yin-yang of rigidity sensing: How forces and mechanical properties regulate the cellular response to materials. Annual Review of Materials Research. 2013; 43:589-618
Pelham RJ, Wang Y-l. Cell locomotion and focal adhesions are regulated by substrate flexibility. Proceedings of the National Academy of Sciences. 1997; 94:13661-13665
Gray DS, Tien J, Chen CS. Repositioning of cells by mechanotaxis on surfaces with micropatterned Young’s modulus. Journal of Biomedical Materials Research Part A. 2003; 66:605-614
Legant WR, Miller JS, Blakely BL, Cohen DM, Genin GM, Chen CS. Measurement of mechanical tractions exerted by cells in three-dimensional matrices. Nature Methods. 2010; 7:969-971
Mahaffy R, Park S, Gerde E, Käs J, Shih C. Quantitative analysis of the viscoelastic properties of thin regions of fibroblasts using atomic force microscopy. Biophysical Journal. 2004; 86:1777-1793
Thomas G, Burnham NA, Camesano TA, Wen Q. Measuring the mechanical properties of living cells using atomic force microscopy. JoVE (Journal of Visualized Experiments). 2013; 76:e50497-e50497
Du Roure O, Saez A, Buguin A, Austin RH, Chavrier P, Siberzan P, Ladoux B. Force mapping in epithelial cell migration. Proceedings of the National Academy of Sciences of the United States of America. 2005; 102:2390-2395
Cukierman E, Pankov R, Stevens DR, Yamada KM. Taking cell-matrix adhesions to the third dimension. Science. 2001; 294:1708-1712
Liu Y, Yu M. Investigation of inclined dual-fiber optical tweezers for 3D manipulation and force sensing. Optics Express. 2009; 17:13624-13638
Liu Y, Yu M. Multiple traps created with an inclined dual-fiber system. Optics Express. 2009; 17:21680-21690
Neuman KC, Block SM. Optical trapping. Review of Scientific Instruments. 2004; 75:2787-2809
Svoboda K, Block SM. Biological applications of optical forces. Annual Review of Biophysics and Biomolecular Structure. 1994; 23:247-285
Ti C, Thomas GM, Wen Q, Liu Y. Fiber optical tweezers for simultaneous force exertion and measurements in a 3D hydrogel compartment. In: Lasers and Electro-Optics (CLEO). Washington, DC: Optical Society of America; 2015; 79:1-2. JW2A.79
Ti C, Thomas GM, Ren Y, Zhang R, Wen Q, Liu Y. Fiber based optical tweezers for simultaneous in situ force exertion and measurements in a 3D polyacrylamide gel compartment. Biomedical Optics Express. 2015; 6:2325-2336
Berg-Sørensen K, Flyvbjerg H. Power spectrum analysis for optical tweezers. Review of Scientific Instruments. 2004; 75:594-612
Hällström W, Lexholm M, Suyatin DB, Hammarin G, Hessman D, Samuelson L, Montelius L, Kanje M, Prinz CN. Fifteen-piconewton force detection from neural growth cones using nanowire arrays. Nano Letters. 2010; 10:782-787
Ananthakrishnan R, Ehrlicher A. The forces behind cell movement. International Journal of Biological Sciences. 2007; 3:303-317
Rodriguez ML. Review on cell mechanics: Experimental and modeling approaches. Applied Mechanics Reviews. 2013; 65:510-518
Seol Y, Carpenter AE, Perkins TT. Gold nanoparticles: Enhanced optical trapping and sensitivity coupled with significant heating. Optics Letters. 2006; 31:2429-2431
Chan BP. Biomedical applications of photochemistry. Tissue Engineering Part B: Reviews. 2010; 16:509-522
Mosiewicz KA, Kolb L, Van Der Vlies AJ, Lutolf MP. Microscale patterning of hydrogel stiffness through light-triggered uncaging of thiols. Biomaterials Science. 2014; 2:1640-1651