1. Preparation of Hydrogel-associated Solutions and Aliquots
2. Hydrogel Preparation (Refer to Figure 1)
3. Multiwell Plate Assembly, Collagen Coating, and Sterilization
4. Cell Seeding on PA Stiffness Assay
NOTE: Although typical for common mammalian cell lines, the protocol outlined in this section is specifically used with the breast cancer MDA-MB-231 cell line (see Figures 4 and 5).
5. Imaging of Cells Seeded onto PA Stiffness Assay
Polyacrylamide (PA) hydrogels are widely used to test stiffness-dependent cell responses.17,24 By mixing various concentrations of acrylamide (A) and bis-acrylamide (B) one can make PA gels that span the stiffness range of most soft tissues in the body — 0.3 – 300 kPa Young’s modulus.1 However, preparation of polyacrylamide gels is tedious and time consuming, often limiting their usefulness in “high-throughput” applications such as for example drug screening.12 Here, a simple and rapid method for assembling PA gels in multi-well plates or any other desirable tissue culture vessel is presented (Figure 1). Figure 2A shows the Young’s modulus as a function of several A and B concentrations (also summarized in Table 1). The moduli of additional A and B combinations are reported in the literature.17,25,26 The gel stiffness of fully swollen gels was measured by rheology (AR 2000ex rheometer, TA Instruments) with a 20 mm upper parallel geometry, oscillatory frequency sweep test 1 – 10 Hz, and 2% constant strain. As anticipated, it was demonstrated that both storage modulus, G’, and loss modulus, G”, are independent of frequency (Figure 2B). It was also confirmed that drying and then re-hydrating the gels, did not affect their Young’s modulus (Figure 2C). Young’s modulus was related to the storage modulus by the following equation:
where E is Young’s modulus and v is the Poisson’s ratio which was approximated to 0.5 for PA gels.27 Note that the reported values are for hydrogels prepared with TEMED. PA hydrogels could also be prepared by UV crosslinking when exposure time and UV intensity are optimized (Table 2). Overall, it is our experience that measuring stiffness of the hydrogels regularly and especially when first establishing the protocols is very important as variations due to operator technique are not uncommon. While rheology is the best established technique for measuring bulk stiffness of hydrogels,27 other methods such as atomic force microscopy5,7 are also appropriate. Polyacrylamide hydrogels alone are inert; thus, to elicit cell attachment extracellular matrix molecules must be added separately. Collagen Type I was chosen for hydrogel coating, but the same method could be used to coat any other extracellular matrix (ECM) protein of choice. Figure 3 demonstrates that by using the crosslinker sulfo-SANPAH, a uniform collagen coating on hydrogels of any stiffness can be achieved.5
Further, it was demonstrated that cells seeded on hydrogels of different stiffness exhibited different morphology. For this experiment, breast cancer MDA-MB-231 cells were seeded on top of the PA gels for 24 – 72 hr. Cells were cultured in RPMI medium supplemented with 10% fetal bovine serum and 1% penicillin/streptomycin in a humidified incubator at 37 °C and 5% CO2. Cells were seeded at 1 x 105 cells/ml or 1 x 104 cells/well for a 96-well plate. This is a typical cell seeding density — 4-fold lower than the confluency cell density, where confluency for a mammalian cell line is reached at ~1 x 105 cells/cm2. Images were taken on inverted fluorescent microscope and analyzed on ImageJ via the Shape Descriptor and Area software plug-ins. It was observed that when seeded on PA gels for 24 hr, breast cancer MDA-MB-231 cells remained round on the soft 0.5 and 1 kPa gels, but were able to spread and elongate on the stiff 100 kPa gel (Figure 4). Figure 4 also showcases the fact that hydrogels made on top of the flexible plastic support are transparent and allow for easy visualization and microscopy. Furthermore, the flexible plastic support does not autofluoresce and thus does not interfere with the imaging of fluorescently labeled cells. Cell morphology was further quantified in terms of overall cell spreading area and cell shape factor — circularity (Figure 5). Cell spreading area was measured by creating a mask to trace the perimeter of each cell. Cell shape (circularity) was then calculated from the following relationship:
Circularity is measured on a scale of 0 – 1, where 0.6 – 1 were taken to designate rounded cells and 0 – 0.5 were taken to designate elongated cells. Approximately three hundred cells from at least three independent experiments were analyzed for each data point. Statistical differences were calculated based on single factor analysis of variance (ANOVA) where data sets were considered significantly different when p < 0.05.
Figure 1. Schematic representation of polyacrylamide gel preparation on flexible plastic support. The figure represents the various steps involved in the preparation of PA gels on flexible plastic support. After the gel dries completely, it can be cut or punched into any desirable shape. A whole punch (~6 mm diameter) is most convenient when preparing gels for a 96-well plate, while a heavy-duty paper cutter can be used for square or rectangular shapes. The figure also highlights the edges of the wells, both with and without a gel, to demonstrate that complete well bottom coverage can be achieved with this method. Please click here to view a larger version of this figure.
Figure 2. Stiffness of PA hydrogels as measured by rheology. (A) Representative Young’s modulus for five different A&B concentrations (refer to Table 1 for acronyms); (B) storage and loss modulus as a function of frequency as measured by rheology; (C) gels exhibit the same Young’s modulus initially (Initial) and after they have been dried and re-hydrated (Re-hydrated) independent of polymer precursor concentration. All gels for the rheology measurements were prepared as slabs of 20 mm diameter and 1 – 1.5 mm height (upon complete swelling).
Figure 3. Collagen coating on PA gels. The collagen coating (green) is efficiently distributed and retained onto the PA gel (red) surface independent of hydrogel stiffness Young’s modulus). Collagen labeled with Cy5 was used for this data. Red-fluorescent beads were embedded into the PA hydrogel to aid visualization. Cross-sectional images were taken on a confocal microscope (scale bar = 100 μm). Image adapted from Zustiak et. al.5 Please click here to view a larger version of this figure.
Figure 4. Phase contract (top row) and fluorescent (bottom row) images of MDA-MB-231 cells seeded on PA gels for 24 hr. MDA-MB-231 cells remain round on soft gels (Young’s modulus of 0.5 and 1 kPa) but elongate on stiff PA gels (Young’s modulus of 100 kPa). The cells were seeded on the gels for 24 hr, fixed in ethanol and stained with acridine orange (AO — green) to visualize the cell cytoplasm and DAPI (blue) to visualize cell nucleus; scale bar = 100 μm. Please click here to view a larger version of this figure.
Figure 5. Cell spreading area and circularity are affected by the stiffness of the underlying substrate. (a) MDA-MB-231 cell spreading area is significantly increased on the 100 kPa as opposed to the 0.5 kPa gels. (b) Cell circularity decreases with increase in PA gel stiffness. Asterisks designate significant differences; p < 0.05.
Figure 6. Schematic representation of an alternative polyacrylamide gel preparation on flexible plastic support. The figure represents the various steps involved in the preparation of PA gels on flexible plastic support. Here the flexible plastic support is initially pre-cut into plastic “coverslips” of a desired shape and size. This technique works best for soft hydrogels. Please click here to view a larger version of this figure.
Acronym | Acrylamide % | Bis-acrylamide % | Acrylamide from 40% stock solution (ml) | Bis-acrylamide from 2% stock solution (ml) | Water (ml) | G' ± SD (kPa) | E ± SD (kPa) |
PA1 | 5 | 0.025 | 625 | 62.5 | 4312.5 | 0.62 ± 0.19 | 1.85 ± 0.57 |
PA2 | 5 | 0.1 | 625 | 250 | 4125 | 3.55 ± 0.12 | 10.64 ± 0.36 |
PA3 | 8 | 0.1 | 1,000 | 250 | 3750 | 9.71 ± 0.64 | 29.14 ± 1.93 |
PA4 | 8 | 0.25 | 1,000 | 625 | 3375 | 22.00 ± 2.10 | 66.01 ± 6.31 |
PA5 | 12 | 0.25 | 1,500 | 625 | 2875 | 37.42 ± 2.68 | 112.25 ± 8.03 |
Table 1. Concentrations of acrylamide (A) and crosslinker bis-acrylamide (B) and the resultant PA gel stiffness. Stiffness, represented here by G’ and E, was measured by rheology. G’ is the storage modulus at 1 Hz frequency. Young’s modulus, E, was calculated from Eq. 1. Standard deviation (SD) was calculated based on three independent experiments with 3-5 samples measured per experiment. The acronyms in the table correspond to the acronyms used in Figure 2A.
UV Intensity = 15 mW/cm2 | Exposure time = 300 sec | ||
Time (s) | E (kPa) ± SD | Intensity (mW/cm2) | E (kPa) ± SD |
75 | 0.14 ± 0.03 | 15 | 28.05 ± 2.62 |
100 | 6.98 ± 2.34 | 26 | 21.13 ± 3.01 |
125 | 19.11 ± 2.29 | 37 | 20.01 ± 2.38 |
300 | 28.05 ± 2.62 | 66 | 19.35 ± 2.86 |
Table 2. UV polymerization is an alternative and a quicker method for PA gel preparation when gelation conditions are optimized; PA3 (refer to Table 1) gel is depicted. The table summarizes the resultant Young’s modulus when either exposure time (left two columns) or UV intensity (right two columns) are varied for the same solution. Based on the results from the table, it appears that 300 sec exposure time and 15 mW/cm2 UV intensity give the highest PA gel stiffness, which is comparable to the stiffness of the traditionally polymerized gel as reported in Table 1.
Reagents | |||
40% Acrylamide | Bio-Rad | 161-0140 | |
2% Bis-acrylamide | Bio-Rad | 161-0142 | |
Ammonium Persulfate | Bio-Rad | 161-07000 | |
TEMED | Sigma Aldrich | T9281 | |
Sulfo-SANPAH | Thermo Scientific | 22589 | |
Collagen Type 1, from Rat tail, 3.68 mg/mL | BD Biosciences | 354236 | |
Dimethyl sulfoxide (DMSO) | Fisher Scientific | BP231-100 | |
Hydrophobic solution – Repel Silane | GE Healthcare Bio-Sciences | 17-1332-01 | |
PBS (1x), pH 7.4 | HyClone | SH30256.01 | |
Polydimehylsiloxane (PDMS) [Slygard 182 Elastomer Kit] | Elsworth Adhesives | 3097358-1004 | |
Tyrpsin/EDTA (10x) | Sigma Aldrich | 44174 | |
RPMI-1640 Medium (1x) | HyClone | SH30027-02 | |
Fetal Bovine Serum | HyClone | SH30073-03 | |
Penicillin Streptomycin | MP Biomedicals | 1670046 | |
Detergent – Triton-X | Sigma Aldrich | T8787 | |
Formaldehyde 37% Solution | Sigma Aldrich | F1635 | |
Bovine Serum Albumin (BSA) | Sigma Aldrich | A2153 | |
BSA-based cell adhesion blocking kit – ECM Cell Adhesion Array Kit | Chemicon International | ECM540 | |
Disposable lab equipment | |||
flexible plastic support – GelBond PAG Film for Polyacrylamide Gels | GE Healthcare Bio-Sciences | 309819 | |
Glass Plates | Slumpys | GBS4100SFSL | |
50 mL Conicals | Fisher Scinetific | 3181345107 | |
15 mL Conicals | FALCON | 352097 | |
Micro centrifuge tubes | Fisher Scinetific | 2 mL: 02681258 | |
96-well plate (flat bottom) | Fisher Scinetific | 12565501 | |
Disposable Pipettes (1 mL, 2mL, 5mL, 10mL, 25 mL, 50mL) | Fisher Scinetific | 1 mL: 13-678-11B, 2mL: 05214038, 5mL(FALCON): 357529, 10mL: 13-678-11E, 25mL: 13-678-11, 50mL: 13-678-11F | |
Glass Transfer Pipettes | Fisher Scinetific | 5 3/4": 1367820A, 9":136786B | |
Pipette Tips (1-200uL, 101-1000uL) | Fisher Scinetific | 2707509 | |
Plastic Standard Disposable Transfer Pipettes | Fisher Scientific | 13-711-9D | |
Parafilm | PARAFILM | PM992 | |
Powder Free Examination Gloves | Quest | 92897 | |
Silicone spacers – Silicone sheet, 0.5 mm thick/13 cm x 18 cm | Grace Bio-Labs | JTR-S-0.5 | |
Large/non-disposable lab equipment | |||
Light and Flourescent Microscope (Axiovert 200M) | Zeiss | 3820005619 | |
Microscope Software | Zeiss | AxioVision Rel. 4.8.2 | |
UV oven | UVITRON | UV1080 | |
Vacuum chamber/degasser | BelArt | 999320237 | |
Vacuum pump for degasser | KNF Lab | 5097482 | |
Tissue Culture Hood | NUAIRE | NU-425-600 | |
Chemical Fume Hood | KEWAUNEE | 99151 | |
Inverted Microscope (Axiovert 25) | Zeiss | 663526 | |
Incubator | NUAIRE | NU-8500 | |
Pipette Aid | Drummond Scientific Co. | P-76864 | |
Hemacytometer | Bright-Line | 383684 |
Currently, most of the in vitro cell research is performed on rigid tissue culture polystyrene (~1 GPa), while most cells in the body are attached to a matrix that is elastic and much softer (0.1 – 100 kPa). Since such stiffness mismatch greatly affects cell responses, there is a strong interest in developing hydrogel materials that span a wide range of stiffness to serve as cell substrates. Polyacrylamide gels, which are inexpensive and cover the stiffness range of all soft tissues in the body, are the hydrogel of choice for many research groups. However, polyacrylamide gel preparation is lengthy, tedious, and only suitable for small batches. Here, we describe an assay which by utilizing a permanent flexible plastic film as a structural support for the gels, enables the preparation of polyacrylamide gels in a multiwell plate format. The technique is faster, more efficient, and less costly than current methods and permits the preparation of gels of custom sizes not otherwise available. As it doesn’t require any specialized equipment, the method could be easily adopted by any research laboratory and would be particularly useful in research focused on understanding stiffness-dependent cell responses.
Currently, most of the in vitro cell research is performed on rigid tissue culture polystyrene (~1 GPa), while most cells in the body are attached to a matrix that is elastic and much softer (0.1 – 100 kPa). Since such stiffness mismatch greatly affects cell responses, there is a strong interest in developing hydrogel materials that span a wide range of stiffness to serve as cell substrates. Polyacrylamide gels, which are inexpensive and cover the stiffness range of all soft tissues in the body, are the hydrogel of choice for many research groups. However, polyacrylamide gel preparation is lengthy, tedious, and only suitable for small batches. Here, we describe an assay which by utilizing a permanent flexible plastic film as a structural support for the gels, enables the preparation of polyacrylamide gels in a multiwell plate format. The technique is faster, more efficient, and less costly than current methods and permits the preparation of gels of custom sizes not otherwise available. As it doesn’t require any specialized equipment, the method could be easily adopted by any research laboratory and would be particularly useful in research focused on understanding stiffness-dependent cell responses.
Currently, most of the in vitro cell research is performed on rigid tissue culture polystyrene (~1 GPa), while most cells in the body are attached to a matrix that is elastic and much softer (0.1 – 100 kPa). Since such stiffness mismatch greatly affects cell responses, there is a strong interest in developing hydrogel materials that span a wide range of stiffness to serve as cell substrates. Polyacrylamide gels, which are inexpensive and cover the stiffness range of all soft tissues in the body, are the hydrogel of choice for many research groups. However, polyacrylamide gel preparation is lengthy, tedious, and only suitable for small batches. Here, we describe an assay which by utilizing a permanent flexible plastic film as a structural support for the gels, enables the preparation of polyacrylamide gels in a multiwell plate format. The technique is faster, more efficient, and less costly than current methods and permits the preparation of gels of custom sizes not otherwise available. As it doesn’t require any specialized equipment, the method could be easily adopted by any research laboratory and would be particularly useful in research focused on understanding stiffness-dependent cell responses.