Badri Narayanan
Narasimhan
ab,
Gerrit Sjoerd
Deijs
ab,
Sesha
Manuguri‡
ab,
Matthew Sheng Hao
Ting
ab,
M. A. K.
Williams
bc and
Jenny
Malmström
*ab
aDepartment of Chemical and Materials Engineering, University of Auckland, Auckland, New Zealand. E-mail: j.malmstrom@auckland.ac.nz
bMacDiarmid Institute for Advanced Materials and Nanotechnology, 6140 Wellington, New Zealand
cSchool of Fundamental Sciences, Massey University, PN461, Private Bag 11222, Palmerston North 4442, New Zealand
First published on 29th March 2021
Hydrogels are excellent soft materials to interface with biological systems. Precise control and tunability of dissipative properties of gels are particularly interesting in tissue engineering applications. In this work, we produced hydrogels with tunable dissipative properties by photopolymerizing a second polymer within a preformed cross-linked hydrogel network of poly(acrylamide). We explored second networks made with different structures and capacity to hydrogen bond with the first network, namely linear poly(acrylic acid) and branched poly(tannic acid). Gels incorporating a second network made with poly(tannic acid) exhibited excellent stiffness (0.35 ± 0.035 MPa) and toughness (1.64 ± 0.26 MJ m−3) compared to the poly(acrylic acid) counterparts. We also demonstrate a strategy to fabricate hydrogels where the dissipation (loss modulus) can be tuned independently from the elasticity (storage modulus) suitable for cell culture applications. We anticipate that this modular design approach for producing hydrogels will have applications in tailored substrates for cell culture studies and in load bearing tissue engineering applications.
While many of the elegant approaches adopted either involve chemical functionalization or complex fabrication procedures,24,25 a relatively easier route to produce tough hydrogels is by using the double network (DN) scheme. DN gels consist of two cross-linked polymer networks, where one network is designed to dissipate energy through sacrificial bonds.14 The strategies adopted to achieve dissipation in double network gels fall into two groups. The first group involves introducing a second network with fewer cross-links relative to the first network. In such DN gels, the relatively less cross-linked network dissipates energy and hinders crack propagation of the more cross-linked network. As a result, such gels have been observed to be stiff, yet ductile.15 In the second strategy, non-covalent/supramolecular associations between networks enable the tuning of dissipative properties, leading to stiff and tough hydrogels.26–28 Both strategies have been adopted in various applications such as scaffolds for tissue engineering, drug delivery, and mechanical sensing applications.29 Although significant progress has been made using double network schemes, the spatial modulation of mechanical properties and using the dissipative properties of double network gels to study mechanobiology have not been explored.
In the field of mechanobiology, researchers study how physical forces and mechanical properties of cells and tissues affect cell development and differentiation, and more broadly, physiology and disease. This research field has been primarily motivated by the fabrication of hydrogels with tunable stiffness.5,30 However, in vivo, cells reside in an extracellular matrix with a far more complex mechanical behavior. Recent mechanobiology literature therefore underscores the need for the development of hydrogel substrates with control over both the elastic and viscous components to further the knowledge of the field.31,32
The present study explored the effects of hydrogen bonding in polymeric semi-interpenetrating network gels, to produce materials where both storage and loss moduli can be precisely tuned. Specifically, we have explored the effect of photopolymerizing monomers, with different structures and hydrogen bonding capacity, inside a cross-linked hydrogel network (for schematic, see Fig. 1). This type of semi-interpenetrating network gel enables the tunability of dissipation in the gel. To aid the mechanistic understanding of these gels, we have chosen three different monomers to be polymerized inside a cross-linked poly(acrylamide) (PAAm) hydrogel network, acrylic acid, acrylamide, and tannic acid. Poly(acrylic acid) (PAA) was chosen due to its charged state at physiological pH, and its known ability to form intermolecular complexes with PAAm.33 The carboxylic acid groups of PAA serve as hydrogen bond donors, while the amide groups of PAAm serve as hydrogen bond acceptors.34,35 Tannic acid, a polyphenol capable of UV-polymerization, with multiple hydrogen bonding donor sites, was chosen as the second type of hydrogen bonding network. After polymerization, tannic acid is expected to form short, branched polymers (as compared to the long linear poly(acrylic acid)).36 Polymerization of acrylamide as a second network was chosen as a control, where little or no intermolecular hydrogen bonding interaction between the two acrylamide networks is expected, due to the weak hydrogen bond donor characteristics of PAAm.33
The gels in this study were characterized using rheology, compression testing, and tensile measurements. The gels with hydrogen bonding second networks were found to exhibit higher strength, toughness, and modulus. Furthermore, the use of photo-polymerization of the second network allows for patterning of the second network, which can be used to create gradients or patterns of mechanical properties. This, combined with the temporally stable mechanical properties of the produced gels, is of particular importance for future cell culture studies.
Annotation | [Acrylamide] (M) | [Bis-acrylamide] (mM) | [APS] (mM) | [TEMED] (mM) |
---|---|---|---|---|
Low-crosslinking (LC) | 1.688 | 1.945 | 4.38 | 6.67 |
High cross-linking (HC) | 1.125 | 16.215 | 4.38 | 6.67 |
To polymerize the second network inside the PAAm gels (low or high cross-linking), the gels were immersed in a deoxygenated solution (type 1 water or PBS) of monomer (acrylic acid, tannic acid, or acrylamide) and photoinitiator for 24 hours, followed by polymerization by exposure to UV light. A photomask defined by 10% and 20% opacities (Adobe illustrator, USA) was printed on a transparency film using a laser printer (MPC3003, Ricoh, USA). For the acrylic acid polymerized gels, a DCDMS treated quartz glass is placed above the gel over which the printed photomask is placed. For tannic acid polymerized gels, the photomask is placed directly over the top of the gel and tannic acid solution was placed around the gel to avoid drying of the gels. Complete conditions for the second networks can be found in Table 2. In Table 2, PAA, UTA and PTA correspond to poly(acrylic acid), unpolymerized tannic acid and polymerized tannic acid respectively. Following photopolymerization, the hydrogels were then taken out of the molds carefully and swelled as reported for each technique.
Annotation | Monomer | [Monomer] (M) | Photoinitiator | [Photoinitiator] (mM) | Light source | Light exposure time |
---|---|---|---|---|---|---|
PAAmLC-PAA-1 | Acrylic acid | 0.844 | 2-Ketoglutaric acid | 34.2 | 365 nm, 10 mW cm−2, ABM mask aligner | 200 seconds for gels made in PBS, 150 seconds for gels made in H2O |
PAAmLC-PAA-2 | 1.688 | |||||
PAAmLC-PAA-3 | 3.376 | |||||
PAAmHC-PAA-1 | Acrylic acid | 0.56 | 2-Ketoglutaric acid | 34.2 | 350 seconds in both PBS and water | |
PAAmHC-PAA-2 | 1.12 | |||||
PAAmHC-PAA-3 | 2.24 | |||||
PAAmLC-UTA-1 | Tannic acid | 0.044 | n/a | n/a | 254 nm, Boekel Scientific UV cross-linker | n/a for UTA, 3 h for PTA |
PAAmLC-PTA-1 | ||||||
PAAmLC-UTA-2 | 0.088 | |||||
PAAmLC-PTA-2 | ||||||
PAAmLC-UTA-3 | 0.0176 | |||||
PAAmLC-PTA-3 | ||||||
PAAmLC-UTA-1 | Tannic acid | 0.044 | n/a | n/a | n/a for UTA, 3 h for PTA | |
PAAmLC-PTA-1 | ||||||
PAAmLC-UTA-2 | 0.088 | |||||
PAAmLC-PTA-2 | ||||||
PAAmLC-PAAm | Acrylamide | 1.688 | 2-Ketoglutaric acid | 34.2 | 365 nm, 10 mW cm−2, ABM mask aligner | 150 seconds |
Cylindrical hydrogels were made by casting the gels in acrylic molds of 5 mm thickness and 10 mm diameter for the compression tests. The thickness of the gels was measured using a digital Vernier scale before measurements. Compression testing was performed at a constant speed of 1 mm min−1 using either a 50 N or a 1 kN load cell, until fracture. To assess stress-relaxation, the hydrogels were compressed to an equivalent of 1.5% of the gel thickness with a deformation rate of 1 mm min−1. The compressive strain was held constant at this position (for up to 60 min depending on the gel response) while the corresponding stress was monitored. Compressive modulus and stress-relaxation data were both generated on three independent gels for each condition and presented as mean and standard deviations.
The water content in the gels was calculated by:
The data are reported as mean and standard deviations from three separate gels from each condition.
Radical polymerization of acrylamide and bis-acrylamide monomers results in a covalently cross-linked PAAm gel network (Fig. S1 reaction scheme†). The produced single network PAAm gels were swollen for 24 hours in solutions of the monomers for subsequent polymerization and the production of the second networks. For the concentrations used in this work, the pore size of the PAAm gels is expected to be in the range of 100 s of nanometers.38 Since the hydrodynamic size of monomers of acrylic acid (72 Da) and tannic acid (less than 2 nm39) is small compared to the pore size of the gels, we assume complete diffusion of monomers into the PAAm gels.
While the PAAm gels (single and semi-interpenetrating network) are transparent and colorless, the hydrogels made with second networks of poly(acrylic acid) and poly(tannic acid) are both opaque(Fig. 1C), assumingly due to the associative interactions between the two networks.35 The slight brown color exhibited by PAAm-poly(tannic acid) (PAAm-PTA) gel is due to the concentration of tannic acid used in this work. The visible color change of the gel is a strong indication of the successful incorporation of the second network into the gels. To further confirm the presence of the second network in the gels, FTIR spectra were recorded of PAAmLC, PAAmLC-PAA-2, PAAmLC-UTA-2 and PAAmLC-PTA-2 gels (as per Tables 1 and 2) as well as of pure PAA polymer and pure tannic acid. For the pure PAAm FTIR spectra, the peaks at 1603 cm−1 and 1645 cm−1 were assigned to the N–H bending and CO stretching of the amide group.35 In the PAA spectrum, the peaks at 1234 cm−1 and 1695 cm−1 were attributed to the C–O stretch and CO stretch of the carboxylic acid group.35 The FTIR spectrum of PAAmLC-PAA-2 showed signatures of both the PAA and PAAm, which confirmed the incorporation of PAA inside the PAAm gel (Fig. 2A).
For the PAAmLC-UTA-2 and PAAmLC-PTA-2 gels, the FTIR spectra displayed peaks attributed to the presence of aromatic rings in the tannic acid,40 indicating the presence of tannic acid in both gels (refer Table S1 for detailed assignment of peaks†).
The inclusion of the second network may increase or decrease the swelling ratio and water content depending on the interactions between the first and second networks. In this case, the swelling studies revealed that PAA and PTA incorporated gels swelled significantly less than pure PAAm gels. It was further observed that the gels with polymerized tannic acid swelled less than the gels where the tannic acid was not polymerized (Fig. 2C). The fact that the tannic acid is polymerized allows the hydrogen bonding to couple the two networks over longer length scales (that of the polymerized tannic acid vs. monomeric tannic acid in the unpolymerized case). The same trend was observed for the corresponding PAAmHC gels as well (Fig. S5B†). In the case of PAAm incorporated gels, the swelling ratio was found to be slightly higher than that of PAAmLC gels and significantly higher when compared to those of PAA and PTA incorporated gels, which can be attributed to the absence of interactions between the first and the second networks.
To further affirm the polymerization of tannic acid, UV-Vis was performed on the solutions of unpolymerized and polymerized tannic acid (Fig. 2D). It has been suggested that a UV-Vis peak observed at 350 nm is correlated with the quinone formation which is an indication of polymerization of phenolic compounds.36 The appearance of a distinct 350 nm peak for the PTA when compared to the UTA clearly confirms the presence of polymeric species (Fig. 2D).
Finally, we performed dynamic light scattering (DLS) on the solution mixtures of PAAm and PAA, unpolymerized tannic acid (UTA) or PTA to analyze the size of the hydrogen bonded aggregates (Fig. S1B†). DLS of PAAm-PAA showed a wide size distribution of aggregates, which may be attributed to the random radical polymerization of the monomers. However, the DLS of PAAm-UTA and PAAm-PTA exhibited more narrow size distributions and a lower polydispersity. Specifically, the size of the aggregates in the PAAm-PTA mixture (∼330 nm) was found to be larger than those in the PAAm-UTA mixture (∼210 nm). The narrower size distribution for PAA-PTA compared to the PAA counterpart may be attributed to that the polymerization of tannic acid results in shorter polymers.
From Fig. 3 it can be observed that PAAmLC-UTA gels exhibited only a modest increase in strength, stiffness, and toughness compared to PAAmLC. This change in material properties is likely due to hydrogen bonding interactions between the parent network and tannic acid, a branched molecule with multiple hydroxyl groups capable of hydrogen bonding with the amides in PAAm.42 This observation is in agreement with a recent study that showed such enhancement of stiffness and toughness for PAAm gels immersed in tannic acid of different concentrations.43 A much more significant increase in strength, stiffness, and toughness was observed for the PAAmLC-PTA gels. This may be due to the fact that the polymerization of tannic acid is able to interact with the first network across longer length scales (that of the polymerized tannic acid). It is clear from the tensile curves that the yield strength is particularly high for PAAmLC-PTA-1. However, due to large variation in that data, this does not correlate with a significantly higher stiffness (Young's modulus) of this sample compared to PAAmLC-PTA-2 or 3. For these higher concentrations of PTA, the gels exhibited a clear yield point after which they enter a non-linear and stiffening regime, resulting in stronger and tougher gels. It is important to note that the stiffness in this case was derived from an area of low strain in the elastic region. For clarity, the individual tensile stress–strain curve for PAAmLC-PTA-2 has been annotated with the individual sections as defined in this work (Fig. S6A†). When the concentration of PTA is increased even more in the gel (PAAmLC-PTA-3), the gel exhibited lower tensile strength, modulus, and toughness when compared to PAAmLC-PTA-2 (Fig. 3A and E). The lowering of tensile properties with an increase in concentration may be correlated with the phase separation of the polymers at higher loading, the change in the network structure or a suboptimal ratio between hydrogen bond donors and acceptors. A recent study made using poly(acrylic acid) hydrogel with incorporated poly(vinyl alcohol) showed a similar decrease in tensile properties of gels above a certain concentration threshold, which was attributed to a change in the network structure of the gels.44
Of the tannic acid incorporated gels discussed thus far, PAAmLC-PTA-2 was the strongest and toughest with a tensile strength of 0.35 ± 0.035 MPa, a toughness of 1.64 ± 0.26 MJ m−3 and an average tensile strain at break of 1200%. We also characterized the fracture energy of hydrogels using the tear test for the PAAmLC-PTA-2 hydrogels using the procedure described in Sun et al.45 The fracture energy using the tear test was calculated to be 2372 ± 244 J m−2 (details in the ESI, Fig. S11†). The fracture energy obtained was comparable to polydopamine incorporated PAAm gels reported in the literature.46
The literature values for a similar concentration of the first network (10–15%) made with gelatin methacrylate and unpolymerized tannic acid as the second network show a tensile strength of between 0.1 and 0.2 MPa and tensile strain% in the range of 200–250%.47 Like PAAm in our case, gelatin has functional groups that can form hydrogen bonds with tannic acid. In the gelatin case, the hydrogen bonding may be more complex due to the available functional groups in protein materials. In that case, a much higher concentration of tannic acid was also used 100% (w/v) compared to 15% (w/v) in our case. Thus, while the studies have differences in the concentrations used, it appears that the polymerization of tannic acid in our case resulted in the production of stiff and tough hydrogels by simple one-step polymerization.
A similar trend, but at a different magnitude, can be observed for the PAAmLC-PAA gels. Fig. 3B, D and F clearly show an increase in strength, toughness and stiffness for PAAmLC-PAA gels compared to PAAmLC. Also, here, a concentration dependence is observed, with the highest tensile properties observed for PAAmLC-PAA-2. Specifically, the tensile strength, Young's modulus, and toughness for PAAmLC-PAA-2 were found to be 78.4 ± 7.1 kPa, 15.17 ± 2.6 kPa, and 0.46 ± 0.04 MJ m−3 respectively. The enhanced tensile properties may be attributed to the ratio of hydrogen bond donors to acceptors being optimal for the PAAmLC-PAA-2 composition which has also been reported in other studies.26,48 The PAAmLC-PTA and PAAmLC-PAA gels also showed enhancement in mechanical properties in compression testing measurements (Fig. 4). The PAAmLC-UTA-1 and PAAmLC-PTA-1 gels did not exhibit any significant change in differences in compressive properties compared to PAAmLC. PAAmLC-UTA-2 and PAAmLC-PTA-2 both displayed increased compressive strength, toughness and stiffness. The highest values were obtained for PAAmLC-PTA-2 with a compressive strength of 25.7 ± 0.6 MPa along with a toughness of 1.63 ± 0.2 MJ m−3 and compressive modulus of 0.07 ± 0.018 MPa. These values are comparable to those of stiff and tough composite hydrogels made with gelatin,49,50 although in the gelatin case, the second network was ionically cross-linked. It is remarkable to observe that such high tensile and compressive properties can still be achieved for PTA hydrogels purely based on hydrogen bonding interactions, without crosslinking the second network.
While the standard deviation for the strength and toughness of the PAAmLC-PAA gels makes conclusions challenging, a similar trend to those observed in tensile testing can be observed. The compressive modulus shows the same increase for the intermediate concentration. Compression testing was also possible for the PAAmLC-PAAm control, and the compressive properties of those gels were similar to those of PAAmLC hydrogels (1.95 ± 1.1 MPa strength, 0.032 ± 0.01 MJ m−3 toughness, 20.3 ± 0.6 kPa modulus for PAAmLC gels and 1.63 ± 0.29 MPa strength, 0.017 ± 0.005 MJ m−3 toughness, 20.16 ± 4.6 kPa modulus for PAAmLC-PAAm gels). To investigate the influence of the crosslinking of the first network on the mechanical properties of the semi-interpenetrating network gels, a first network with a higher cross-linking ratio (PAAmHC, cross-linking ratio 69:1) was prepared. It is to be noted that a lower concentration of acrylamide monomers was used for the highly cross-linked gels compared to the loosely cross-linked gels (1.12 M vs. 1.69 M). This lower concentration was used since gels with the same high cross-linking ratio and the same monomer concentration as the PAAmLC were found to be too brittle to handle and test, in particular as semi-interpenetrating network gels. As expected from a more cross-linked gel, PAAmHC was found to be stiffer than PAAmLC, with higher Young's and compressive moduli of 19.6 ± 5 kPa and 52.9 ± 4.7 kPa respectively (Fig. S6 and S7†), compared to 2.23 ± 0.6 kPa and 20.3 ± 0.6 kPa for PAAmLC (Fig. 3 and 4).
A significant increase in tensile strength, toughness, and modulus was observed for PAAmHC-PTA, compared to both PAAmHC and PAAmHC-UTA (Fig. 5A and S6A†). However, no significant change in compressive properties was seen compared to PAAmHC (Fig. 5C and S6C†). In the case of PAA incorporated gels, a significant enhancement of both tensile and compressive properties was observed for PAAmHC-PAA-2 and 3 (Fig. 5B, D, S6B and D†).
It has previously been demonstrated that both monomer and cross-linking concentrations of the first network significantly affect the tensile properties of double network gels.51 A direct comparison of properties between both crosslinking ratios in our case is not possible as we used different concentrations of monomers for the two different crosslinking ratios. However, the results clarify that irrespective of the cross-linking ratio of the first network, the PAA and PTA incorporated gels exhibit enhanced mechanical properties.
The single network PAAmLC gels did not exhibit stress relaxation (Fig. S8A†), in line with elastic materials. In fact, of the loosely cross-linked gels, only PAAmLC-PAA-2 and 3 exhibited significant stress relaxation (Fig. S8C†). For the highly cross-linked first network, none of the gels displayed significant stress relaxation (Fig. S8B†).
The average relaxation times of PAAmLC-PAA-2 and PAAmLC-PAA-3 gels were found to be around 1000 seconds after one day of swelling (Fig. S8C†). The relaxation behavior observed in these gels is attributed to the breaking of hydrogen bonds between PAAm and PAA in response to applied stress. Long polymer chains with ionic cross-links exhibit substantial stress relaxation due to the breaking of ionic cross-links with applied stress.55 The fact that polymerized tannic acid gels (PAAmLC-PTA-1 and PAAmLC-PTA-2) did not exhibit this type of relaxation behavior may be an additional indication that polymerization of tannic acid did not yield long chain polymer networks.
In order to produce gels with stable mechanical properties under cell culture conditions, all gels were prepared under physiological conditions by replacing water with PBS. Fig. S9A† demonstrates the change in mechanical properties due to the osmotic swelling for gels prepared using water. Frequency sweep rheology of tannic acid polymerized gels made with two different opacities of transparent masks (10% and 20%) exhibited similar storage moduli but different loss moduli in the low frequency regime (Fig. 6A). Since tannic acid is expected to polymerize into short polymer species that could diffuse out of the gel, these hydrogels were characterized after equilibration for 24 hours in PBS. A frequency of 0.16 Hz was chosen to compare the gels' mechanical properties, as it has been suggested that cells probe the mechanical properties of substrates close to 0.16 Hz.32 Compared to the loosely cross-linked single network PAAm gels (PAAmLC), the semi-interpenetrating network gels with polymerized tannic acid exhibited a small increase in storage modulus and a noticeable increase in loss modulus (Fig. 6B). The controls in this case, were the PAAmLC gels with unpolymerized tannic acid (PAAmLC-UTA in Fig. 6B), which showed only a slight increase in loss modulus (G′′ average −105 Pa, compared to polymerized tannic acid gels with G′′ average – 706 Pa and 370 Pa for 10% and 20% masks respectively). However, for the highly cross-linked first network (PAAmHC gels), a significant difference in loss modulus was not observed using the photomask approach (data not shown).
Gels with poly(acrylic acid) as the second network also displayed marked differences in loss modulus between hydrogels produced with 10% and 20% opacity photomasks, both in the case of low and high cross-linking of the first PAAm network (Fig. 6C and D). While the PAAmHC gels displayed a constant storage modulus after polymerization of the second network, in the case of PAAmLC gels, a noticeable change of the storage modulus was observed. This may be attributed to the higher swelling of the gel with the lower cross-linking, leading to a larger uptake of acrylic acid. Such a noticeable change in storage modulus was not observed for PAA incorporated PAAmHC gels when compared with PAAmHC gels. While the obtained loss modulus for the PAAmHC-PAA gels was low compared to the PAAmLC-PAA gels (G′′ average – 398 Pa and 221 Pa for 10% and 20% mask, Fig. 7D), it is evident that gels with a similar storage modulus and different loss moduli can be fabricated, irrespective of the first network crosslinking ratio.
UV-Vis of the PBS solution used for swelling the gels was performed to evaluate the amount of tannic acid that gets leached out of the PAAmLC-UTA and PAAmLC-PTA gels (Fig. S10A† shows the calibration curve of tannic acid in PBS). Both unpolymerized and polymerized tannic acid gels leached out similar amounts of tannic acid after one day and the leachate did not show any traces of polymeric species in the case of polymerized tannic acid gels (Fig. S10B†). Therefore, we assume that all polymerized tannic acid species remain in the gel.
Temperature-controlled UV-Vis spectroscopy was performed to determine the transition temperature of the gels. Hydrogen bonds or electrostatic interactions between polymers result in a transition temperature, similar to the so-called upper critical solution temperature (UCST), above which, the components in a mixture are miscible in all proportions. Here, we attribute this temperature transition to the breaking of associative interactions at high temperatures.56 We define our upper phase transition temperature, as the temperature during the heating ramp at which the transmission reaches 50%. From the UV-Vis, we found the upper phase transition temperature to be close to 37 °C for the PAAmLC-PAA gels made in PBS (compared to 31 °C for the gels made in water) (Fig. 7A). Previous studies have shown that the UCST for hydrogels made by random copolymerization of PAAm and PAA was affected by hydrogen bonding and that it was proportional to the amount of poly(acrylic acid) and cross-linking.57 The presence of ions is well known to affect polymer transition temperatures.56 The tannic acid containing PAAmLC-UTA gels exhibit a much broader transition with a transition temperature of around 49 °C for water made gels and 45 °C for PBS made gels (Fig. 7B). The polymerized tannic acid PAAmLC hydrogels exhibit an even more complex behavior (Fig. S10C†), emphasizing the complexity of the processes involved when the associative interactions break at high temperature which warrants further investigation.
As the UCST of PAAmLC-PAA gels was close to that of cell culture conditions, the mechanical properties of the gels after swelling in PBS at 37 °C for 24 hours were tested (Fig. 7C). The frequency sweep rheology revealed that the mechanical properties of the gels did not change significantly when compared to the mechanical properties of gels obtained at room temperature after 4 hours of swelling in PBS. Hence, it can be concluded that both PAA incorporated and tannic acid hydrogels hold promise as cell culture substrates.
Polymer gels consisting of two cross-linked polymer networks have been shown to exhibit excellent toughness and stiffness.43,49,58,59 However, the influence of using uncross-linked polymers with different structures as second networks has not previously been studied in depth. We systematically studied poly(acrylamide) gels with the incorporation of three different second networks: linear polymers that can hydrogen bond with the first network (PAA, molecular weight 3.43 × 106 g mol−1 obtained by using a viscometer with k and a values obtained from the literature,60 see Fig. S4†), linear polymers that do not form hydrogen bonds with the first network (PAAm), and short branched polymers that can hydrogen bond with the first network (PTA). We found that hydrogen bonding gels exhibited higher stiffness and toughness, in agreement with expectations. An optimum concentration of the hydrogen bonding second network was also observed (PAAmLC-PAA-2, PAAmLC-PTA-2) where the highest values of stiffness and toughness were achieved. When compared to the single network PAAmLC gels, the PAAmLC-PTA-2 hydrogels exhibited a 19 times tensile strength enhancement, and a 55 times increase in toughness. Similarly, when compared to the unpolymerized tannic acid incorporated gels (PAAmLC-UTA-2), PTA gels showed a 6.3 times increase in tensile strength and a 9 times increase in toughness. When compared to PAAmLC-PAA-2 gels, a 4.3 times increase in strength and a 3.6 times enhancement in toughness were observed. Finally, Young's modulus was calculated to be 0.12 ± 0.02 MPa which is about 20 times higher than that of UTA gels and 50 times higher than that of the parent gels. In addition to that, the water content of PAAmLC-PTA-2 gels (average of 75%, Fig. S5A†) was found to be slightly higher than those of previously reported hydrogels with similar compression properties.49 From the tensile properties of polymerized tannic acid gels, it is clear that the gels exhibit high stiffness and toughness. The yielding behavior and subsequent energy dissipation observed in these gels are attributed to the breaking of weak hydrogen bonded aggregates between PAAm and polymerized tannic acid. Double networks composed of poly(methacrylic acid) and poly(dimethacrylamide) have previously been found to exhibit high stiffness and toughness, which was attributed to the varied sizes of the hydrogen bonded aggregates.26 Indeed, the DLS revealed that polymerized tannic acid produced larger aggregates with poly(acrylamide) when compared to the poly(acrylic acid) (Fig. S1B†) which might in part explain the increased stiffness and toughness of PAAmLC-PTA-2 gels when compared to PAAmLC-PAA-2 gels. The incorporation of polymerized tannic acid into PAAm gels results in increased hydrogen bonding density.
Polymerized tannic acid incorporated inside PAAm gels is similar to self-polymerized dopamine incorporated inside PAAm gels.46 However, for polydopamine incorporated gels, though an enhancement of toughness was observed, the stiffness was found to decrease when compared with the control gels without polydopamine. In contrast, in our case, we observed that incorporation of polymeric tannic acid enhances both stiffness and toughness. A recent study by Cui et al.61 showed that oligomeric lignin, hydrogen bonding elastomers, showed a similar enhancement of stiffness and toughness. The authors argue that the enhancement is ascribed to the rigidity and network forming ability of the oligomeric lignin species. We believe that polymerized tannic acid incorporated inside PAAm gels enhances the stiffness and toughness through a similar mechanism, although further structural characterization, such as small angle X-ray and neutron scattering, is needed to confirm this hypothesis.
Furthermore, we also speculate that the structure of the polymerized polyphenol results in more entanglement within the first network. However, the exact mechanism of how the polymerized polyphenol's structure contributes to the mechanical properties is still not clear at this point. Our results further suggest that for the rational design of hydrogels for specific applications, the structure of second networks should also be considered in addition to the cross-linker concentration and the density of hydrogen bonds.
In summary, we have demonstrated a simple, yet versatile, strategy to produce hydrogels with tunable dissipation. By careful selection of the second network, this study addresses the critical gap in the literature in adopting semi-interpenetrating network gels for cell culture studies, which are mainly hindered by swelling. While the current study focused on understanding the effect of an uncross-linked second network with different structures using a variety of mechanical characterization techniques, the simplicity of this approach enables easy adaptability of such gels to various cellular mechanotransduction studies. Furthermore, we found that the polymerization of polyphenols, which results in short polymers, yields a remarkable increase in stiffness and toughness. Finally, to the best of our knowledge, we report for the first time that it is possible to achieve tunable dissipation properties using UV polymerization of polyphenols.
Footnotes |
† Electronic supplementary information (ESI) available. See DOI: 10.1039/d1na00103e |
‡ Present address: Department of Neuroscience and Biomedical Engineering, Aalto University, Espoo, 0076, Finland. |
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