Rapid Accessible Fabrication and Engineering of Bilayered Hydrogels: Revisiting the Cross-Linking Effect on Superabsorbent Poly(acrylic acid).

Superabsorbent hydrogels are significant not only in materials science but also in industries and daily life, being used in diapers or soil conditioners as typical examples. The main feature of these materials is their capacity to hold considerable amount of water, which is strongly dependent on the cross-linking density. This study focuses on the preparation of hydrogels by reweighing the effect of cross-linking density on physical properties, which provides green fabrication of bilayered hydrogels that consist of homogeneous structural motifs but show programmed responses via sequential radical polymerization. In particular, when two hydrogel layers containing different cross-linking densities are joined together, an integrated linear bilayer shows heterogeneous deformation triggered by water. We monitor the linear hydrogel bilayer bending into a circle and engineer it by incorporating disperse dyes, changing colors as well as physical properties. In addition, we demonstrate an electric circuit switch using a patterned hydrogel. Anisotropic shape change of the polyelectrolyte switch closes an open circuit and lights a light-emitting diode in red. This proposed fabrication and engineering can be expanded to other superabsorbent systems and create smart responses in cross-linked systems for biomedical or environmental applications.

Introduction

Since poly(2-hydroxyethyl methacrylate) was reported to form a hydrogel in the presence of a cross-linker,[1] a myriad of hydrogels have been widely researched for biomedical and environmental purposes. Among them, superabsorbent hydrogels (SHs) confine considerable amount of water into a three-dimensional, cross-linked network, which is typically greater than hundreds to thousands times their dry weight, and swell while maintaining the original shape.[2−4] Acrylic acid (or acrylate) and acrylamide are extensively used as monomers, along with other monomers such as N-isopropylacrylamide, N,N-diethylacrylamide, and more interestingly, bioextractable sodium 4-hydroxy-2-methylenebutanoate[5] or polymers including poly(vinyl alcohol), which are further cross-linked covalently or noncovalently in situ or ex situ.[2,6] When exposed to aqueous conditions, hydrophilic groups in the polymer network are primarily hydrated by water molecules, and then, the additional water can be absorbed via capillary force and osmotic pressure for filling the space inside the network. Such wet materials essentially possess small yet functionally crucial cross-linking density, which not only leads to water absorbency but also modulates the physical properties of the entire material on demand, for example, elasticity or swelling ratio.

The versatility of SHs has offered privileged, sustainable applications. For instance, from the perspective of polymeric materials, swellable materials have been used as elastomers, watery matrices, containers, supports, and films, which can be further applied in many fields such as soil conditioning, tissue engineering, desalination, catalysis, and health care.[6] In particular, stimuli-responsive SHs have gained notable interest because of the following characteristics:[7−21] (i) bio- and environmental compatibility, (ii) wide range of functional monomers/building blocks including cost-effective natural products (e.g., cellulose, alginate, starch, chitosan, polysaccharides, and proteins), (iii) possible use of water as an eco-friendly ubiquitous stimulus, (iv) use of a broad library of well-established chemistry for synthesis, for example, radical polymerizations, (v) distinguishable volumetric change, and (vi) processability into smart composites integrated with inorganic components that render synergy effects via hybridization. Besides, responsive SHs have been remarkably used as a hydrogel actuator under aqueous conditions. The materials show reconfigurable shape changes in response to pH,[22] temperature,[23−25] salinity,[26] metal ions,[27,28] light,[29] or electric potential,[30,31] taking one step forward to biomimetic responses.

In this study, we demonstrate a green fabrication method of bilayered hydrogels that show heterogeneous deformation under aqueous conditions by controlling the cross-linking density. The bilayer structure consists of homogeneous chemical species (i.e., cross-linked poly(acrylic acid)) and enables low-cost effort-saving fabrication through sequential radical polymerization in water without the need of ancillary adhesives—eliminating possible interfacial complexity that raises the outbreak of debonding. Instead, only the gap in cross-linking density significantly alters the physical properties of hydrogels, building up programmed responses of the bilayer. Therefore, we evaluate the effect of cross-linking density on superabsorbency, mechanical strength, and thermal stability of hydrogels, which allows a controlled deformation triggered by water. As designed, the bilayered hydrogel curls into a circle when wet; the behavior is dependent on pH. Each layer can be colored with disperse dyes for visual clarity, and the bilayer exhibits material properties emanating from both layers. Furthermore, we prepare a circuit switch using a patterned hydrogel. A small firmly cross-linked hydrogel patch induces enough hydraulic force to bend the loosely cross-linked hydrogel strip, which closes the circuit and switches on a light-emitting diode (LED).

Results and Discussion

Fabrication of a Hydrogel Film from a Glass Template via Radical Polymerization

Figure shows the synthetic procedure of a poly(acrylic acid)-based hydrogel film under aqueous conditions by radical polymerization. First, acrylic acid (14 mL) was added to water (8 mL). Two phases were separated initially, but 80% neutralization with NaOH gave a homogeneous solution with a molar concentration of 8 mM. Then, di(ethylene glycol) acrylate (cross-linker) and potassium persulfate (KPS) (initiator) were added to provide a ready-to-polymerize solution, which was transferred by a syringe to a glass template having a rectangular space inside (11.5 cm × 15 cm × 0.1 cm) for polymerization. The template had a high ratio of surface area to volume and could facilitate efficient heat transfer, which is similar to controlling autoacceleration process in the sheet-type mold. After the displacement, the monomer solution was polymerized on a heating plate at a set temperature of 55 °C for 2 h; the cross-linked hydrogel film was obtained and unloaded from the mold. The soft film was even and transparent without the inclusion of severe cavitation and had a size similar to that of the template. The chemical structure of the hydrogel is shown in the inset of Figure .

Figure 1

Schematic description for the preparation of a poly(acrylic acid)-based hydrogel film. The neutralized monomer was polymerized in a glass template. The transparent hydrogel film obtained and its cross-linked chemical structure are shown in the inset.

Effect of Cross-Linking on the Swelling Properties

A poly(acrylic acid) film dramatically absorbs water and shows a distinct size expansion while maintaining its initial shape. During swelling, the diacrylate cross-linker in the hydrogel films fundamentally affected the superabsorbency. As shown in Figure a, we prepared hydrogel films 1–6 containing different amounts of cross-linker under the same conditions, wet the films with deionized water, and expressed the effect of cross-linker on the absorbency by calculating the degree of swelling (eq ) and cross-linking density (ρ) (eq ) as follows:[32]where X indicates the weight of the wet analyte sample and X0 is the weight of the sample dried under vacuum using a lyophilizer for 48 h.where Vsol indicates the molar volume of water; vp is the equilibrium polymer volume fraction determined from the degree of swelling; and χ is the solvent–polymer interaction parameter of 0.46.[33]

Figure 2

(a) Change in degree of swelling of hydrogel films with regard to the cross-linker ratio after immersing in water for 48 h (sky blue). The as-prepared samples contain a limited amount of water (44–47%) regardless of the ratio (black). (b) Representative volumetric change in film 2 when prepared and freeze-dried. The black square (area, 1 cm × 1 cm) helps to estimate the film size. After immersing in water for 48 h, the swelled film has a side that approximately measures 3.5 cm. (c) SEM images of as-prepared 2 (up) and after swelling in water for 48 h (down). Each sample was freeze-dried for 48 h before the measurement.

The initial as-prepared samples had similar values for degree of swelling (44–47%), irrespective of the amount of cross-linker, because the films were consistently prepared from 0.8 M monomer solutions in water. However, after drying and re-swelling in water for 48 h, the hydrogel films showed different swelling ratios, which hinged on the cross-linking density. Film 2 (0.34 wt % of cross-linker) swelled for a maximum of 200 times, and then, the value decreased as more cross-linkers were involved. Figure b shows an isotropic dimensional change in 2. The initial film had a side of 1.15 cm, which decreased by 26% when lyophilized, but exposure to water increased the side 4.1×. The black square behind the hydrogel film indicates the transparency of the film and supports the size estimation. As expected, the cross-linking density obtained from eq revealed the inverse proportion against the swelling ratio of the films, except for the case of 1, which has the least amount of cross-linker. We reason that the partially soluble loose network of 1 hindered the capillary force for water absorption.[34] In Figure c, the example porous network of 2 was observed using scanning electron microscopy (SEM), which was developed after swelling in water. The pore size ranges from 3 to 20 μm. All experimental values of the obtained hydrogels are summarized in Table .

Table 1

Degree of Swelling and Cross-Linking Density of Hydrogel Films 1–6

hydrogel film	cross-linker (wt %)	degree of swelling (%)	cross-linking density (mmol L–1)
1	0.20	15 912	0.71
2	0.34	20 164	0.47
3	0.42	16 287	0.68
4	0.50	10 011	1.55
5	0.63	7509	2.54
6	0.80	7140	2.77

In addition, we measured the actual change in the temperature of the polymerizing solution during radical polymerization. Therefore, a flexible thermocouple probe was inserted into the polymerizing solution of 2, which was cast inside the template on a heating plate (set temperature, 55 °C), and the temperature was tracked by a digital thermometer, as shown in Figure a. The temperature exponentially increased for the initial 20 min and then slightly elevated more for 15 min, indicating an accelerated polymerization (Figure b). In general, Trommsdorff effect aggravates undesirable properties in polymeric materials, such as cavitation or unevenness, during polymerization.[35,36] However, the cast solution of 2 exhibited only a weak exothermic process, from which the regular hydrogel film 2 was produced. The maximum temperature was found to be 50.4 °C; thereafter, the temperature of the film was stabilized at 48 °C until the end of the reaction.

Figure 3

(a) Photograph of measuring temperature of the polymerizing solution of 2 in the glass template on a heating plate using a digital thermometer. (b) Change in the temperature of the solution during radical polymerization.

Effect of Cross-Linking on the Mechanical Strength of Hydrogels

Chemical cross-linking provides an effective approach to control the mechanical strength of polymeric materials. Herein, we measured the stress–strain curves of the resulting films, as shown in Figure . Figure a shows the representative curves for hydrogel samples 1–6, from which we can anticipate the effect of cross-linking density. As described in Figure b, toughness values increased until the amount of cross-linker increased from 0.20 (film 1) to 0.34 wt % (film 2) and then decreased in inverse proportion to the amount of cross-linker. A similar tendency was observed for elongation at fracture. As an example, at 0.34 wt %, the toughness of film 2 was found to be 0.28 MJ m–3 with 300% elongation at fracture. On the other hand, Young’s modulus only fluctuated within a narrow range of 0.12–0.15 MPa. Presumably, small change in cross-linker concentration would manipulate microstructures or induce microdeformation in hydrogels, leading to a change in ductility of materials rather than stiffness. We also changed the initiator concentration, which can control the molecular weight between the cross-links (Mc), another factor affecting the cross-linking density, during polymerization.[37,38] Thus, we polymerized film 2 using different initiator concentrations. Toughness increased in proportion to the amount of initiator until 0.56 wt % of KPS was incorporated (a maximum toughness, 0.40 MJ m–3) and then decreased; in contrast, elongation at fracture decreased above 0.43 wt % (Figure S1). Although the total changes were much smaller than the results from the cross-linker concentration, a detailed future investigation would elaborate complementary effects of both factors on the mechanical properties of the hydrogel materials.

Figure 4

Mechanical properties of hydrogels 1–6. (a) Representative tensile stress–strain curves from the hydrogels that contain different concentrations of cross-linker when polymerized with 0.25 wt % KPS. (b) Change in toughness (blue), elongation at fracture (black), and Young’s modulus (orange, inset) of the hydrogels with respect to the concentration of cross-linker. The data points were obtained in quintuplicate from five independent experiments.

Furthermore, we took 1, 3, and 6 and measured their tensile strengths at 80 °C to investigate a thermal effect. At 80 °C, the films stiffened more—toughness and elastic modulus increased and elongation reduced—as compared to the measurement at 25 °C (Figure a–c). The total exposure time to heat during testing was less than 2 min. The fractured specimen from 3 (0.42 wt %) was hard and brittle, as shown in Figure S2b. To examine the effect of thermal treatment on hydrogels, we incubated film 3 at 40, 60, and 80 °C for 3 and 10 min and tested their mechanical strengths at the same temperatures (Figure d). The longer the exposure time at a higher temperature, the more rapidly did the Young’s modulus increase, which indicates that the film hardened by thermal drying. On the other hand, potential thermal annealing would occur together inasmuch as the modulus gradually increased even at 40 °C less than the polymerizing temperature.[39]

Figure 5

Young’s modulus (a), elongation at fracture (b), and toughness (c) of hydrogel films 1, 3, and 6, measured at 80 °C (red). The results from 25 °C (black) are shown for comparison. (d) Change in Young’s modulus of 3 after exposure to different temperatures (40 °C, blue; 60 °C, sky blue; and 80 °C, red). The data points were obtained in quintuplicate from five independent experiments.

Fabrication of Responsive Hydrogel Bilayers

A minor modification in the chemical structure (i.e., cross-linking density) alters the macroscopic physical properties of polymeric materials, highly encouraging us to develop responsive hydrogels capable of showing designed behaviors in water. In particular, when two adjacent parts with different cross-linking densities are joined together, the interface in between gives rise to heterogeneous deformation of the entire material, taking advantage of the different swelling ratios in an aqueous medium. Hence, we have designed and fabricated bilayered hydrogels by sequential radical polymerization (Figure a). In a glass template, we prepared the first layer containing 0.34 wt % cross-linker (film 2). On top, we directly deposited the second polymerizing solution containing 0.80 wt % cross-linker (film 5) and polymerized under the same conditions in the presence of 0.25 wt % KPS. Each polymerizing solution was dyed with navy blue and red disperse dyes for differentiation before conducting polymerization. Therefore, in situ polymerization provided a bilayered structure of hydrogel in which the thickness of the first (navy blue) and second (red) layers measured 1.2 and 0.8 mm, respectively. The hydrogel layers adhered tightly to one another because of the probable interpenetration that would occur at the interface during the second polymerization reaction. After unloading from the glass mold, the bilayer was obtained, which had a volume of 2.8 cm × 0.2 cm × 0.3 cm and displayed an anisotropic shape change.

Figure 6

(a) Fabrication of the bilayered hydrogel via sequential polymerization. The first and second layers are prepared from 2 and 5 dyed in navy blue and red, respectively. (b) Change in the degree of swelling of each colored layer. Swelling behaviors of pristine 2 and 5 are shown for comparison, and the expanded view of the initial linear region is shown in the inset. (c) Change in elongation at fracture (black) and Young’s modulus (orange) of hydrogels when dyed and integrated.

Figure b shows the change in the degree of swelling of each layer in deionized water, similarly determined by eq . Incorporated with the hydrophobic disperse dyes, the navy blue 2 and red 5 hydrogels exhibited a total degree of swelling that decreased in half when fully swelled, compared to 2 and 5 before dying. The insoluble dyes also affected the swelling rates of both hydrogel layers, which reduced from 193 to 177% min–1 for 2 and from 161 to 96% min–1 for 5 after dying, calculated from the linear slopes of the initial region (inset in Figure b). We further swapped the dyes in the layers, which yielded red 2 and navy blue 5 films. However, both samples showed less difference in the swelling ratios, meaning that the bilayer from navy blue 2 and red 5 can better induce the reconfiguration (Figure S3). Inclusion of the dyes also altered the mechanical strength of the hydrogel bilayer (Figure c). The hydrophobic dyes enhanced the elongation at fracture of 2 and 5, which could sustain cross-linked structures during the elongation under tensile stress.[40] However, the bilayer displayed an average elongation at fracture of both hydrogels as expected, whereas the Young’s modulus did not change much. Representative stress–strain curves are shown in Figure S4, and the measured values are listed in Table S5.

A designed behavior of bilayer is presented in Figure . Here, we investigated the bending of the bilayer in various pHs, which can affect the actuation of polyelectrolyte materials. Figure a shows the bilayer bending in a neutral pH 7 buffer. As soon as immersed in the buffer, the linear material bent in a round shape in 15 min, as the navy blue layer (2, 0.34 wt % cross-linker) that positioned outside swelled more than the red layer (5, 0.80 wt % cross-linker) inside. A longer exposure to the medium only increased the whole size of the bilayer to a small extent but did not unfold the shape (Figure S6). In addition, we investigated the effect of pH on the behavior of the hydrogel in aqueous media. Figure b reveals the change in the curvature of the deformed hydrogels when exposed to various pHs of 3, 7, and 10. The curvature of hydrogels autonomously increased as time elapsed. The curvature increased slightly faster (the rate of folding was found to be 28.1 m–1 s–1, calculated from the initial linear region) at pH 3 than that at pH 7 (26.7 m–1 s–1), but the final curvature was slightly lower than the value resulted from pH 7, accompanying less folding. Interestingly, the curvature increased most rapidly at pH 10 (rate, 33.6 m–1 s–1; 1.3 times faster than that at pH 7), and the final curvature reached 224 m–1—the theoretical curvature of a circle that has 2.8 cm circumference—in 9 min, as shown in the inset of Figure b. We assume that protonation of carboxylates at pH 3 could hinder a complete folding of the bilayer as decreasing hydrophilicity and water absorbency as well. However, the remaining acid groups would be deprotonated at pH 10, which could promote water absorbency and the following folding behavior while hydrophilicity increased. Time-lapsed photographs of the bending behavior are presented in Figures S5, S7, and S8. Furthermore, we tested the reversible shape change of the bilayer that was pre-exposed to pH 10 for 10 min. As expected, the curled bilayer recovered its original shape after taking away from water and drying under air for 1 h at 70 °C but bent again when rewet for 10 min at pH 10. During five drying–rewetting cycles, the bilayer iterated the programmed response without structural degeneration (Figure c).

Figure 7

(a) Bending motion of the hydrogel in a pH 7 buffer solution at 25 °C. The linear bilayer curls into a round shape within 15 min. (b) Change in the curvature of the bilayer over time while exposed to buffer solutions of various pHs (pH 3, orange; pH 7, black; and pH 10, sky blue). A magnified image of the bilayer folding completely after immersed at pH 10 for 9 min is shown in the inset. (c) Change in the curvature of the bilayer during drying–rewetting cycles. Photographs of the bilayer taken at the third drying–rewetting cycle were presented.

In addition, we have engineered the hydrogel bilayer through patterning with glass masks (Figure a). The small glasses masked the first layer (navy blue 2; size, 3 cm × 0.5 cm × 1.3 mm) during the second polymerization, leaving a small red patch (red 5; size, 0.5 cm × 0.5 cm × 0.7 mm) on the bottom layer. The small patch caused the bending of the entire hydrogel in deionized water. We positioned the patterned hydrogel between two parallel copper plates, and the hydrogel was held onto the bottom plate with a crocodile clip. The copper plates were connected to an LED bulb and a dry cell battery, resulting in an open electronic circuit (Figure b). As designed, the hydrogel bending in deionized water touched the other copper plate 1 cm distant, closing the circuit. We could see a dim red light before deformation because the hydrogel contains charged ions, which would diffuse into deionized water. However, the underwater actuation lit the LED bulb in bright red in 2 min (Figure c).

Figure 8

(a) Depiction for fabrication of the patterned hydrogel. The glass masks are placed on the first layer in situ before casting the second polymerizing solution. The first and second layers are prepared from the same solutions as those used in Figure . (b,c) Circuit switch based on the patched hydrogel (b, open circuit). In deionized water, the bending hydrogel connects two plates, switching on the LED in red (c, closed circuit).

Conclusions

Bilayered hydrogels capable of showing programmed responses have been demonstrated. The hydrogels are made by cross-linking superabsorbent poly(acrylic acid), where cross-linking density plays a crucial role in manipulating the swelling behavior as well as mechanical strength. In particular, engineering cross-linking density provides heterogeneous deformation when two SHs containing different cross-linking densities are consolidated via sequential in situ polymerization. Through the rapid accessible fabrication, we were able to prepare bilayered hydrogels and colored each layer with disperse dyes. The concomitant physical changes were investigated. The linear hydrogel bilayer revealed a pH-dependent folding behavior and showed remarkably fast complete deformation at pH 10. Furthermore, patterning on the hydrogel brought about a polyelectrolyte switch that closed the circuit and lit an LED bulb in red. This fabrication method can be expanded to other superabsorbent systems using biocompatible monomers, and a merger with diverse functionalities would expedite the development of cross-linked polymeric systems that feature smart responses for many biomedical or eco-friendly applications, for example, microlenses that show a controlled release or functional membranes that remove specific pollutants (e.g., microplastics) in the ocean.

Experimental Section

Materials

Acrylic acid, di(ethylene glycol)diacrylate, and KPS were obtained from Sigma-Aldrich. Disperse dyes such as Synolon N/Blue S-GLS (navy blue color) and Synolon Rubine S-GEL (red color) were purchased from Kimco. Acrylic acid was distilled under reduced pressure at 50 °C before use. Deionized water was prepared using a water purification system (Pure Power I+, DAIHAN Scientific). All other reagents and solvents used were purchased commercially and were used as received unless otherwise noted.

Analytical Methods

For nuclear magnetic resonance (NMR) measurement, hydrogel sample 2 was prepared in an NMR tube using D2O instead of water. 1H NMR spectrum was recorded using a Bruker 300 MHz NMR spectrometer at 25 °C. Proton chemical shifts are expressed in parts per million (ppm, δ scale) and are referenced to tetramethylsilane ((CH3)4Si, δ 0.00 ppm) or to residual protium in the solvent (D2O, δ 4.70 ppm). Data are represented as follows: chemical shift, multiplicity (s = singlet, d = doublet, t = triplet, q = quartet, m = multiplet and/or multiple resonances, and br = broad peak), integration. Carbon nuclear magnetic resonance (13C NMR) was recorded using a Bruker 500 MHz NMR spectrometer at 25 °C. Carbon chemical shifts are expressed in parts per million (ppm, δ scale) and are referenced to tetramethylsilane ((CH3)4Si, δ 0.00 ppm). For the tensile test, the as-prepared hydrogel films were cut using a laser cutter. The films were glued between two PMMA clamps with a superglue. The resulting specimens have a size of 10 mm × 10 mm × 1 mm (length × width × thickness). Uniaxial tensile tests were performed using an Instron 5543 universal testing machine with a 1000 N load cell at 25 °C in air. The specimens were stretched at a rate of 5 mm/min until the samples were broken. The elastic modulus and toughness were calculated from the initial slope (strain range of 10–30%) and the area under the stress–strain curve, respectively. Each film type was tested in quintuplicate; the average and standard deviations from this set were plotted. Micromorphology of the dried hydrogel film was observed using a Carl Zeiss SUPRA 55VP scanning electron microscope at an accelerating voltage of 2 kV. Before the measurement, the sample was dried using a lyophilizer for 3 d and coated with a thin platinum layer. Attenuated total reflection Fourier transform infrared spectroscopy measurements were performed using a Nicolet-6700 instrument (Thermo Scientific) at room temperature. The spectrum was obtained by averaging 32 scans over the range of 4000 to 400 cm–1.

Synthesis of a Poly(acrylic acid)-Based Hydrogel

Hydrogel films were prepared via typical free-radical polymerization. A representative example of hydrogel 2 was prepared as follows: To a solution of acrylic acid (14.7 g, 0.204 mol, 1490 equiv) in water (8 mL), sodium hydroxide (6.6 g, 0.165 mol, 1190 equiv) was added dropwise in water (16 mL), resulting in 80% neutralization of acrylic acid. The monomer solution was degassed by vigorous N2 bubbling for 1 h. After adding KPS (37 mg, 0.14 mmol, 1.0 equiv, 0.25 wt %) and di(ethylene glycol) diacrylate (50 mg, 0.23 mmol, 1.7 equiv, 0.34 wt %), the reaction mixture was transferred to a glass template having a size of 11.5 cm × 15 cm × 0.1 cm (width × length × thickness) and placed on a heating plate having a set temperature of 55 °C for 2 h. A freestanding hydrogel film was obtained after unloading from the mold in a quantitative yield. IR (cm–1): 3361, 2932, 2852, 1685.8, 1552, 1405, 1294; 1H NMR (300 MHz, D2O): δ 1.82 (br s, methine protons), 1.23 (br s, methylene protons); 13C NMR (125 MHz, D2O): δ 183.6, 44.8, 37.3, 36.1. The obtained NMR spectra are shown in Figures S9 and S10. The amounts of initiator and cross-linker were varied from 0.05 to 0.75 and from 0.20 to 0.80 wt %, respectively, with reference to the amount of acrylic acid monomer. For investigating the cross-linker effect (Figure ), the amount of initiator was set at 0.25 wt %; for the initiator effect (Figure S1), 0.34 wt % cross-linker was used, as shown in Table .

Table 2

Compositions of Cross-Linker and Initiator Incorporated in Hydrogel Films for Tensile Testing

for cross-linker effect		for initiator effect
cross-linker (wt %)	initiator (wt %)	cross-linker (wt %)	initiator (wt %)	control variables
0.20	0.25	0.34	0.05
0.34			0.17
0.42			0.25	acrylic acid
0.50			0.43	NaOH water
0.63			0.56
0.80			0.75

Preparation of Bilayered Hydrogels

Bilayered hydrogels were prepared by sequential radical polymerization. Di(ethylene glycol)diacrylate (50 mg, 0.233 mmol, 1.7 equiv, 0.34 wt %), KPS (37 mg, 0.14 mmol, 1.0 equiv, 0.25 wt %), and a navy blue dye (10 mg) were added to 80%-neutralized acrylic acid (14.7 g, 0.204 mol, 1490 equiv) solution. The first polymerizing solution was poured into a glass template (11.5 cm × 15 cm × 0.1 cm), which was covered with a glass lid, and heated at 55 °C for 2 h to afford the first layer. The second layer was synthesized onto the first layer in a similar manner. After the fabrication of the first layer inside the glass template, additional glass slides (thickness, 0.1 cm) were placed as a spacer. In this step, the first layer was masked with glass pieces when preparing the patterned bilayer. The second polymerizing solution was prepared by adding di(ethylene glycol)diacrylate (119 mg, 0.556 mmol, 4.1 equiv, 0.80 wt %), KPS (37 mg, 0.14 mmol, 1.0 equiv, 0.25 wt %), and a red dye (10 mg) to the 80%-neutralized acrylic acid solution. The second solution was carefully injected into the gap between the first layer and glass lid and then heated at 55 °C for 2 h. The freestanding bilayer hydrogel was obtained in a quantitative yield after unloading from the mold and cut into pieces of desired sizes by using a laser cutter or razor.