An ideal hydrogel for biomedical engineering should mimic the intrinsic properties of natural tissue, especially high toughness and self-healing ability, in order to withstand cyclic loading and repair skin and muscle damage. In addition, excellent cell affinity and tissue adhesiveness enable integration with the surrounding tissue after implantation. Inspired by the natural mussel adhesive mechanism, we designed a polydopamine–polyacrylamide (PDA–PAM) single network hydrogel by preventing the overoxidation of dopamine to maintain enough free catechol groups in the hydrogel. Therefore, the hydrogel possesses super stretchability, high toughness, stimuli-free self-healing ability, cell affinity and tissue adhesiveness. More remarkably, the current hydrogel can repeatedly be adhered on/stripped from a variety of surfaces for many cycles without loss of adhesion strength. Furthermore, the hydrogel can serve as an excellent platform to host various nano-building blocks, in which multiple functionalities are integrated to achieve versatile potential applications, such as magnetic and electrical therapies.
Hydrogels have a similar structure to biological soft tissues and can be engineered to resemble an extracellular matrix, and therefore have great potential for tissue engineering applications.1, 2, 3, 4 Generally, hydrogels are brittle because of the high water content in the polymer networks, and it is a grand challenge to develop biomimetic hydrogels with superior mechanical properties.5 Several tough hydrogels have been developed, such as interpenetrating network, nanocomposite and double network hydrogels, that generally consist of interpenetrated brittle and ductile networks that can effectively dissipate energy.6, 7, 8, 9 However, most tough hydrogels lack the ability of natural tissue to self-heal after damage because the covalent sacrificial bonds in the hydrogels cannot re-form easily when the hydrogels rupture after experiencing large deformation or cyclic loading.10 To produce highly recoverable, tough hydrogels, researchers have recently replaced sacrificial covalent bonds in the brittle networks with easily re-formable non-covalent bonds, for example, by using ionic-bond crosslinked alginate as the sacrificial network11 or using polyampholytes carrying opposite charges to create electrostatic crosslinked networks.12 The introduction of readily re-formable non-covalent bonds in the network also establishes high self-healing ability in the hydrogels.13
Hydrogels for tissue repair must also be designed with excellent cell affinity that allows cells and tissues to attach so that they can accelerate tissue regeneration after implantation.1, 14 However, most reported tough hydrogels have poor cell affinity and therefore are unfavorable for cell adhesion and growth.15, 16, 17 Moreover, tough hydrogels generally lack tissue adhesion properties and therefore cannot be fixed with the surrounding tissues during surgical operation.1 Mussel-inspired hydrogels have shed new light on the development of hydrogels with good cell affinity and tissue adhesiveness.18, 19, 20 Polydopamine (PDA), which has structural similarity to the adhesive protein of mussels, has high adhesiveness to various surfaces and excellent cell affinity.21, 22 PDA has also been used to prepare self-healable hydrogels because of its highly reactive catechol groups.23, 24 Most previously reported PDA-based hydrogels were formed through metal chelation, but the toxicity of metals might be a concern for biomedical applications.23, 25 In brief, an ideal hydrogel for soft tissue repair should mimic the intrinsic properties of the natural counterpart, especially its high toughness and self-healing ability, in order to withstand cyclic loading and repair skin and muscle damage. In addition, excellent cell affinity and tissue adhesiveness enable integration with surrounding tissue after implantation. However, it is challenging to integrate these characteristics into one hydrogel.
Here, we designed a mussel-inspired, highly tough polydopamine–polyacrylamide (PDA–PAM) hydrogel with superior self-healing ability, excellent cell affinity and tissue adhesiveness. The key innovation of our material design is the prevention of overoxidation of PDA during hydrogel synthesis in order to maintain enough free catechol groups in the hydrogel that was inspired by the natural mussel adhesive mechanism. In nature, mussels maintain a high concentration of catechol groups for high adhesiveness by protecting catechol groups via secreting reductive cysteine-rich proteins. Having enough free catechol groups in the PDA–PAM hydrogel was the critical factor to endow unique properties, such as super stretchability, high toughness and repeatable adhesion ability, to the hydrogel. The hydrogel was tough enough to be extended to a large strain of 3300% with a fracture energy as high as 2400 J m−2. The hydrogel could fully self-heal without any external stimuli after rupture. More remarkably, the catechol groups on the PDA chains endowed the hydrogel with exceptional cell affinity and tissue adhesiveness.
Dopamine hydrochloride, acrylamide (AM), ammonium persulfate (APS), N,N’-methylene bisacrylamide (BIS) and tetramethylethylenediamine were purchased from Sigma-Aldrich (St Louis, MO, USA). Epidermal growth factor (EGF) was purchased from Shanghai Primegene Bio-Tech (Shanghai, China). Enzyme-linked immunosorption assay (ELISA) kits were purchased from R&D (Minneapolis, MN, USA). Fetal bovine serum, Dulbecco’s modified Eagle’s medium, 1% penicillin–streptomycin solution and 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) assay were purchased from HyClone (Logan, UT, USA). All other reagents and solvents were of reagent grade.
Preparation of hydrogels
The PDA–PAM hydrogels were synthesized by the following procedures. (1) Dopamine (DA) molecules went through an alkali-induced prepolymerization process to form PDA chains by dissolving DA powder in a beaker containing NaOH aqueous solution (pH=11) and then allowing the DA to self-polymerize for 20 min in air atmosphere under stirring. (2) AM, APS BIS were mixed with the solution of PDA chains in an ice bath under stirring. After 10 min of mixing, the ice bath and stirrer were removed, and AM was polymerized to form PDA–PAM hydrogels. During AM polymerization, DA was also induced by APS to further the polymerization. Hydrogels with different weight ratios of DA/AM were synthesized to investigate the effects of DA on the properties of the hydrogels, as listed in Supplementary Table S1. Note that more APS was needed when DA was present, because DA would also be induced to second polymerization and consume APS.26 In addition, PDA–PAM hydrogel did not form when the weight ratio of DA/AM was higher than 0.8 wt% (Supplementary Figure S1), because the reductive DA molecules affected the activity of the initiator (APS) and thus retarded the polymerization of AM monomers.
Multifunctional hydrogels hosting various nano-building blocks were also synthesized by the same polymerization process as the PDA–PAM hydrogels. Before polymerization, functional nanoparticles (Fe3O4 NPs and carbon black NPs) were added into the DA solution to allow DA polymerization on the nanoparticle (NP) surface. Thus, the PDA-grafted NPs could be well dispersed in the hydrogels after polymerization.
The distribution of PDA in the hydrogel (DA/AM=5 wt%) and possible interaction between PAM and PDA were investigated by time-of-flight secondary ion mass spectrometry (TOF-SIMS V, ION-TOF GmbH, Münster, Germany). The samples were bombarded with Bi3+ primary ions that were accelerated at 25 kV with an average pulsed current of 0.3 pA. The raster area was 200 μm × 200 μm, and the acquisition time for each spectrum was 40 s, corresponding to an ion dose of <4 × 1011 ion cm−2. Three positive and negative spectra were recorded for each specimen at different locations. The spectra were calibrated before extraction of the ion intensity data using the SurfaceLab 6 software (Münster, Germany).
The FT-IR spectra of pure PAM, pure PDA and the PDA–PAM hydrogel (5 wt% DA/AM) were also analyzed to search for possible interactions between PAM and PDA using an FT-IR spectrometer (Nicolet 5700, Thermo, Waltham, MA, USA), and the spectra were recorded between 4000 and 500 cm−1.
The surface chemical compositions of the PDA, PAM and PDA–PAM hydrogels were measured using XPS (Kratos, Axis Ultra DLD, Manchester, UK). A monochromatic Al Kα X-ray was used as an excitation source (hν=1486.6 eV) running at 15 kV and 150 W. The neutral C1s peak (C–C (H), set at 285.0 eV) was used as a reference for charge correction. Before each measurement, the sample was washed three times in deionized water and ethanol to eliminate reactant residue from the sample and dried in a vacuum chamber at 40 °C for 2 days.
The structures of the bulk PAM hydrogel and the PDA–PAM hydrogel (DA/AM=0.8 wt%) were examined using a scanning electron microscope (SEM, JSM 6390, JEOL, Tokyo, Japan). Before examination, the hydrogels were freeze-dried. Then, the dried hydrogels were cut to expose their inner structures, and the cross-sections were observed.
(1) Tensile tests were performed on a universal testing machine (Instron 5567, Norwood, MA, USA). The loading rate was 100 mm min−1. The specimens had a width of 25 mm and a thickness of 3 mm. The gauge length between the clamps was 5 mm.
(2) Cyclic loading–unloading tests were performed by loading the hydrogels under tension to strains of 1000 and 2000% and then unloading to zero force. A time-dependent tensile–recover–tensile test was conducted to characterize the time-dependent recoverability of the hydrogel. First, the specimens were pulled to achieve an extension ratio of 6 and then unloaded. After storage for different time intervals (10 s, 10 min, 20 min, 30 min and 1 day), the specimens were pulled to 6 times its initial length again.
(3) The fracture energy was determined by the classical single edge notch test on the universal testing machine (Instron 5567). The thickness and width of the specimen were 3 and 25 mm, respectively (Supplementary Figure S10a). During testing, a pair of specimens was pulled: one specimen was unnotched and the other was notched (Supplementary Figure S10b). The fracture energy (Gc, J m−2) was calculated using the method proposed by Greensmith for elastomers.27 Details are provided in the Supplementary Information.
Dynamic rheological tests of the PDA–PAM hydrogels were characterized at room temperature using a Rheometric Scientific HAAKE (MARS, Karlsruhe, Germany) strain-controlled rheometer equipped with 20 mm parallel plates. The storage modulus (G′) and loss tangent (ratio of loss modulus G″ to storage modulus G′) of the hydrogel were determined as the frequency ranging from 0.01 to 10 Hz at 1.0% strain amplitude. Details are provided in the Supplementary Information. All rheological measurements were performed in triplicate.
The stimulus-free self-healing behavior was visually demonstrated by a tear–heal test. The self-healing ability of the hydrogel was then quantitatively evaluated by a tensile–heal–tensile test. The hydrogel was stretched to break on the universal testing machine (Instron 5567), and the crosshead was moved back to bring the two broken pieces into contact, the two hydrogel pieces self-healed after 2 h and the healed specimen was stretched to break again. The self-healing ability was also confirmed by dynamic rheological tests using the two-step procedure.18 Details are provided in the Supplementary Information.
To mimic the adhesiveness of hydrogels to human skin tissues, porcine skin (25 mm × 25 mm) was used for the tensile-adhesion test by the universal testing machine (Instron 5567) under ambient conditions. Adhesion–strip cyclic tests were also conducted to evaluate the repeatable adhesiveness of the hydrogels. The adhesion strength was calculated by the measured maximum load divided by the bonded area. Details are provided in the Supplementary Information.
The PDA–PAM hydrogels with various DA contents (0, 0.2, 0.4, 0.8 wt% to AM) and NIH-3T3 fibroblasts (SCSP-515, Stem Cell Bank, Chinese Academy of Sciences, Shanghai, China) were used to evaluate the cell affinity of the hydrogels. The hydrogels, which had diameters of 7 mm and thicknesses of 2.5 mm, were first sterilized by immersion in 75% alcohol for 24 h. Before cell culture, the PDA–PAM hydrogels were first purified by soaking the hydrogel in deionized water three times, and the deionized water was refreshed every day. The residual amount of acrylamide monomers in the PDA–PAM hydrogel was quantified by gas chromatography. The results demonstrated that nearly no residual AM monomers existed in the PDA–PAM hydrogel after three purification cycles (Supplementary Figures S14 and S15). Then, the hydrogels were immersed in Dulbecco’s modified Eagle’s medium and swelled to equilibrium state for 2 days in a CO2 incubator at 37 °C. The biocompatibility of the hydrogel and cell proliferation were assessed by MTT assay after 3 and 7 days of culture. The morphologies of the cells on the hydrogel surfaces were observed by SEM (JSM 6390) and optical microscopy.
Full skin wounds repaired by hydrogels
Full skin wounds were created on the dorsal area of rats and treated with the purified PDA–PAM hydrogels. Five male Sprague Dawley rats weighing 180–220 g were used. After being anesthetized with pentobarbital (2 wt%, 2 ml kg−1), the dorsal area of the rat was totally depilated, and four full-thickness circular wounds (5 mm in diameter) were created on the upper back of each mouse by a disposable 5 mm skin biopsy punch (Supplementary Figure S19). The wounds were treated with the PDA–PAM hydrogels (DA/AM=0.8 wt%), EGF-loaded PDA–PAM hydrogels and a blank, respectively. To obtain the EGF-loaded hydrogel, the hydrogel (30 mg) was first sterilized in 75% alcohol, and then EGF (1 μg in 500 μl of phosphate-buffered saline) was absorbed into the hydrogel. After 0, 5 and 15 days post wounding, photographs of the wound closure were taken for each wound with a digital camera, and the percentages of wound closure were calculated. All rats were killed on day 15, and the wound site with the surrounding skin was harvested. Central wound sections were fixed on glass slides and stained with hematoxylin and eosin and Masson’s trichrome to evaluate the wound-healing progress and investigate the skin tissue regeneration and collagen deposition. The experiments were performed in accordance with protocols approved by the local ethical committee and laboratory animal administration rules of China.
Results and discussion
Hydrogel synthesis and characterization
The hydrogel was synthesized by a facile two-step synthetic method (Figure 1a). The first step was an alkali-induced PDA polymerization, in which DA molecules were oxidized to form PDA chains through reaction of the catechol and quinone groups. With the polymerization of PDA, the solution underwent a color change from colorless to pale brown and finally turned to deep brown black over time, which is the typical color of PDA.28 Note that this step was critical to allow the following gel formation process because free DA monomers strongly retarded AM polymerization and thus gelation could not occur (inset photo in Figure 1a). In the second step, acrylamide monomers were added to the above PDA precursor solution and polymerized to form the PDA–PAM hydrogel in the presence of initiator and crosslinker. Importantly, this step prevented further oxidation of PDA by isolating unreacted catechol groups from the outside oxygen environment, and thus enough free catechol groups remained in the hydrogel. PDA–PAM hydrogels with different DA weight ratios were prepared as listed in Supplementary Table S1.
In the PDA–PAM hydrogel, PDA chains were linked to the PAM network through interactions between the catechol groups of the PDA chains and the amino groups of the PAM network (Figure 1b). The PDA chains intertwined to form recoverable non-covalent bonds, including π–π stacking and hydrogen bonds,26, 28, 29 dispersed in the PAM network. Thus, the PAM network was hybrid crosslinked by covalent bonds and reversible non-covalent bonds from PDA. In addition, the interaction between PDA chains and the PAM network led to load sharing between the ductile PAM network and the non-covalent bonds in the crosslinked PDA chains. Consequently, the PAM network could significantly extend to sustain large deformations and maintain the elasticity of the hydrogel. The reversible bonds from the PDA chains linked to the PAM network could dissipate energy efficiently through breakage of the non-covalent bonds to prevent crack propagation during stretching, therefore enhancing the toughness and increasing the extension ratio as well as endowing the hydrogel with excellent self-healing ability.13
The interaction between PDA and PAM in the PDA–PAM hydrogel was confirmed by TOF-SIMS, FT-IR, proton nuclear magnetic resonance and XPS (Figure 2b and Supplementary Figures S2–S5). The chemical maps of TOF-SIMS indicated a homogenous dispersion of PDA in the PAM network (Figure 2a). The secondary ions C3H6NO+ (m/z 72) and C8H7NO2+ (m/z 149) were chosen to represent PAM and PDA, respectively. These two ions were uniformly distributed over the whole cross-section area, suggesting the uniform distribution of PAM and PDA components in the hydrogel. A peak at m/z 261 was observed in the positive spectrum of the PDA–PAM hydrogel, but it did not appear in either the PAM spectrum or the PDA spectrum (Supplementary Figures S2a and b). This suggests that the peak at m/z 261 originates from the reaction between PAM and PDA. It has been reported that the catechol/quinone groups on PDA could crosslink with nucleophilic amine groups via a Schiff base reaction.28, 30, 31 In agreement with this notion, the tentative assignment of the peak at m/z 261 is C13H14N2O4+ (see the inset of Figure 2b) that results from interactions between the amine groups of PAM and the catechol groups of PDA. This reaction connects the PDA chains to the PAM networks. In addition, the FT-IR spectrum of the PDA–PAM hydrogel showed a new peak at 1258 cm−1, corresponding to C–N stretching in phenyl amines, in comparison with pure PAM and PDA (Supplementary Figure S3). The presence of this peak also indicated interactions between the -NH2 groups of PAM and the catechol groups of PDA, as shown in the black square in Figure 1b(1). Proton nuclear magnetic resonance analysis was also used to investigate the interactions of DA and AM (Supplementary Figure S4). After AM was mixed with DA to form AM–DA complexes, the broad band of the catechol groups in DA (8.87 p.p.m.) split into two sharp peaks (8.85 and 8.88 p.p.m.). In addition, the active hydrogen in DA shifted from 7.99 to 7.8 p.p.m. These results demonstrated that there were interactions between the oligomers of DA and AM. XPS analysis also confirmed the presence of free catechol groups in the PDA–PAM hydrogel (Supplementary Figure S5). SEM micrographs showed that the PDA–PAM hydrogels displayed microfibril structures, whereas the pure PAM hydrogel had a smooth surface (Figure 2c and Supplementary Figure S6). The microfibrils in the hydrogel may be caused by the complexation of PDA and PAM chains that led to interweaved three-dimensional structures.
Stretchability, toughness and fatigue resistance
The PDA–PAM hydrogel exhibited super stretchability and high toughness. The hydrogel was stretched 30 times beyond its initial length, as shown in the typical tensile stress–strain curves (Figures 3a and b). Note that the stress–strain curves showed the nonlinear inelastic mechanical behavior of the hydrogel, and the Young’s modulus (E) decreased during extension, and this is the widely encountered softening phenomenon of highly stretchable hydrogels.7 Increasing the content of DA remarkably enhanced the stretchability of the hydrogels (Figure 3c). The tensile loading–unloading tests showed pronounced hysteresis, indicating energy dissipation from bond breakage. In addition, during tensile loading–unloading tests, the residual strain was very small, even when the hydrogel was stretched to a strain of 2000% (Figure 3d). After removal of the load, the hydrogel automatically recovered its original shape (Supplementary Figure S8). However, if the second loading was applied immediately (10 s), the strength of the hydrogel was slightly weaker. After sufficient storage duration (1 day), when stretched again, the hydrogel showed almost full self-recovery. In contrast, the pure PAM hydrogel ruptured, rather than recovered, during the second tensile test (Supplementary Figure S9). These results indicated that the internal damage of the hydrogel showed fatigue resistance and could withstand cyclic loading after the addition of DA, although the recovery process took time.
The fracture energy of the PDA–PAM hydrogel (2400 J m−2) is much higher than that of the pure PAM hydrogel (650 J m−2) (Figure 3e) and human cartilage (~1000 J m−2),11 as measured by single-edge notched tests (Supplementary Figure S10). In particular, during the experiment, in contrast to the notch-sensitive pure PAM hydrogels, where the notch quickly turned into a running crack during stretching, the PDA–PAM hydrogels were insensitive to the notch and could be stretched to a large fracture strain of 26 (Supplementary Videos S1 and S2). The PDA–PAM hydrogel was also tough enough to bear stretching after being knotted (Figure 3f) and recovered its original shape even when subjected to compression strains of up to 85% (Figure 3g). However, the addition of DA decreased the tensile strength (Supplementary Figure S7). These phenomena could be ascribed to the increase in the viscosity of the hydrogels after DA addition (Supplementary Figure S11), as evidenced by dynamic rheological tests, in which the loss tangent (G″/G′) increased with DA content. The crosslinker (BIS) content affected the mechanical properties of the hydrogels (Supplementary Tables S2 and S3).
Stimuli-free self-healing properties
The PDA–PAM hydrogel had self-healing ability in the ambient environment without any metal-chelation agents and/or other external stimuli that was ascribed to catechol-mediated interfacial hydrogen bonds and π–π stacking (Figure 1b). As shown in Figure 4a, when we tore the hydrogel into two separate pieces and then brought them into contact, they automatically rejoined after 2 h in the ambient environment. The fracture line could not be identified when the healed hydrogel was further stretched. To quantitatively evaluate the self-healing property, we performed a tensile–heal–tensile test (Figure 4b). The healed hydrogel could once again sustain a large strain after a healing duration of 2 h at room temperature. No large differences were observed between the two tensile stress–extension ratio curves, indicating that the hydrogel had fully recovered (Figure 4c). The self-healing property was further confirmed by dynamic rheological tests (details in the Supplementary Information). A 100% strain through a strain amplitude sweep was first applied to break the hydrogels, and subsequently a low strain (0.01%) amplitude and low frequency (f=1 Hz) was applied to allow the hydrogel to recover. As shown in Figure 4d, the storage modulus G’ (2869 Pa) of the recovered PDA–PAM hydrogel nearly recovered its initial value (2707 Pa) within 30 s after stopping the large strain, whereas the pure PAM hydrogel did not recover its initial G′ value (Figure 4e). Note that the hydrogel could perfectly self-heal if two freshly cut surfaces were maintained in contact for 2 h. In contrast, if two uncut surfaces were brought together, they could adhere to each other and be separated by pulling (Supplementary Figure S12c). This is because the freshly cut surfaces have many active catechol groups that lead to strong self-healing, whereas the catechol groups on uncut surfaces can lead to adhesion that is different from previous self-healing hydrogels based on host–guest interactions.32 These results thereby confirm the reversible nature of the non-covalent bonds between PDA chains that can re-form after breakage and therefore impart self-healing properties to the PDA–PAM hydrogel.13
The PDA–PAM hydrogel possessed exceptional tissue adhesiveness that provided universal soft tissue adhesion with no skin tissue irritation or inflammatory response. As shown in Figure 5a, the hydrogel tightly adhered on the author’s skin and could support a tube full of water. The hydrogel could be easily peeled off without leaving any residue on the skin when no longer in use (Figure 5a). The adhesiveness of the hydrogel herein allowed it to conform readily to dynamic skin surfaces. As shown in Figure 5b, the hydrogel still was firmly attached on the author’s skin when it was stretched and followed the movement of the joint as the wrist was bent or twisted. The hydrogel had repeatable and superior adhesiveness even after six cycles of adhere strip, and the skin was not hurt during the adhere–strip cycle (Figure 5b and Supplementary Video S3). The adhesive strength of the hydrogel to porcine skin increased with DA content and reached a maximum of 15.2 KPa when the DA/AM ratio was 0.8 wt%. Almost no loss of adhesive strength was measured during the adhesion–strip cyclic test (Figure 5c) that revealed that the adhesion was reversible, thereby benefiting the removal of the hydrogel when it was no longer needed. The free catechol groups in PDA could interact with amine or thiol groups to form cation–π or π–π interactions with various contact surfaces1, 33 that were responsible for the adhesion properties. Note that more BIS reduced the adhesion strength (Supplementary Figure S13), because the increase in crosslinking density of the hydrogel restricted the mobility of the polymer chains.34 Consequently, the viscosity of the hydrogel decreased, and the polymer chains were not easily diffused into the tissue surface to form intimate contact with the tissue surfaces.
Biocompatibility and wound repair
Both the in vitro cell culture and in vivo animal experiments demonstrated that the PDA–PAM hydrogel was biocompatible. The hydrogel had high affinity to cells because the catechol groups can form strong interactions with functional groups in the cell membrane, such as thiols and imidazoles.1 As shown in Figure 6a and Supplementary Figure S16, a large number of fibroblasts adhered to and spread well on the surfaces of the PDA–PAM hydrogels. Increasing the DA content in the hydrogels enhanced adhesion and promoted the proliferation of fibroblasts (Figure 6b).
In vivo implantation demonstrated that the PDA–PAM hydrogels could accelerate skin tissue regeneration (Figures 6c–f). Surgery details are provided in the Supplementary Figure S19. The wounds treated with PDA–PAM hydrogels were covered by complete and thick epidermis (Figures 6e). The regenerated new skin tissue integrated well with the PDA–PAM hydrogels (Figure 6f), and they were mature, as evidenced by well-organized and aligned collagen fibers in the wound area (Figure 6f). After EGF was loaded in the PDA–PAM hydrogel, the wound was completely repaired with hair coverage (Figure 6e). The interface between the newly regenerated skin tissue and the hydrogel was diffused (Figure 6f), and more mature and compact collagen fibers were present (Figure 6f).
These in vivo wound-healing results indicated that the PDA–PAM hydrogel facilitated a quicker wound-healing process than the blank groups. The good wound-healing ability of the PDA–PAM hydrogel was attributed to four reasons. First, the high tissue adhesiveness of the PDA–PAM hydrogel guaranteed intimate contact of the hydrogel to the surrounding tissue and protected the wound sites from infection during the entire healing period. Second, the excellent cell affinity of the hydrogel facilitated cell adhesion, attachment and migration. Third, the hydrogel had good affinity to extracellular matrix proteins (Supplementary Figure S17), and protein adsorption could further improve cell attachment,35 that established a positive feedback loop to finally create suitable extracellular matrix microenvironments for cell adhesion.36 Finally, the hydrogel stably immobilized EGF and preserved the bioactivity of EGF (Supplementary Figure S18) that enhanced the migration of fibroblasts to the wound area and promoted complete skin regeneration for the superior treatment of dermal wounds. The excellent wound-healing performance of the hydrogel shows great potential for clinic applications.
In addition to the high stretchability, stimuli-free self-healing ability and adhesiveness, the PDA–PAM hydrogel could serve as an excellent platform for tuning with multifunctionalities by hosting various nano-building blocks, because the PDA component in the hydrogel can facilitate the uniform distribution of functional NPs in the hydrogel by PDA grafting on the surface of the NPs (Supplementary Figure S22). The grafted NPs then interacted with the PAM network, and thus multifunctional hydrogels were obtained (Figure 7a). As examples, magnetic and conductive hydrogels were formed from the inclusion and dispersion of magnetic Fe3O4 and carbon black NPs into the hydrogels, respectively. In both cases, after PDA grafting, the NPs were well distributed in the water (Figures 7b and c), and the hydrogel incorporated with NPs displayed a homogeneous morphology at the microscopic level, as observed by SEM, suggesting that the NPs were well dispersed into the polymeric matrix and covered with PDA microfibrils (Supplementary Figures S20 and S21, similar to the structure presented in the pure PDA–PAM hydrogel (Figure 2c).
A multifunctional conductive, stretchable, self-healable hydrogel was obtained after the incorporation of CB NPs (Supplementary Tables S4 and S5). The hydrogel showed good conductivity (∼0.4 S cm−1), as measured by the two-probe method (Supplementary Figure S20). The integration of multiple functions was well demonstrated in a battery-powered circuit with a light-emitting diode (LED) (Figure 7b). The hydrogel worked as a conductor to connect the circuit to brightly light the LED. Then, the hydrogel was stretched, and the LED emission gradually weakened during this process. The resistance of the hydrogel under tension was measured that increased with an increase in extension ratio (Supplementary Figure S20e). The hydrogel was stretched to break, and the LED turned off. The fractured two parts of the hydrogel were brought into contact to self-heal for 2 h, and the LED was brightly lit again. The healed hydrogel could once again bear large stretching.
A multifunctional magnetic, stretchable, adhesive hydrogel was obtained after the incorporation of Fe3O4 NPs. The magnetization curves showed that the hydrogel was a typical superparamagnetic material (Supplementary Figure S21c). To prove the integration of these hydrogel properties, hydrogel blocks with (black) and without (brown) Fe3O4 NPs were brought into contact and self-healed to form a hydrogel rope (Figure 7c). Then, the hydrogel rope was adhered to nails and hung near a magnet. It was observed that the magnetic hydrogel regions (black part) were attracted by the magnet, and the hydrogel rope bent into a ‘S’ shape.
The hydrogel was obtained by introducing reversible bonds homogeneously distributed inside a single covalent polymer (PAM) network. The PDA chains in the PAM network achieved a good balance between non-covalent bonds and covalent bonds in the hydrogel, the main reason for the toughness and self-healing properties. These results demonstrated that even a single network could achieve a tough hydrogel similar to previously reported double network and interpenetration hydrogels. This approach of designing hydrogels based on the hybrid crosslinking of a single polymer network with non-covalent bonds, such as hydrogen bonds, π–π stacking, hydrophobic interactions and so on, could be generalized to produce a wide range of tough hydrogels with multiple characteristics.
In summary, we developed a novel but general design strategy to produce tough hydrogels, simultaneously showing the features of self-healing and tissue adhesiveness. The super stretchability and high fracture energy of this hydrogel were comparable with those of soft tissues. The self-healing ability rendered it particularly suitable for repairing fatigue-damaged tissues. The high cell affinity and tissue adhesiveness guaranteed it to fix to the surrounding tissues, thus promoting tissue regeneration. In addition, the hydrogel could serve as a universal platform to incorporate many types of functional NPs, resulting in hydrogels with multiple functionalities, such as magnetic and conductive response properties. The successful fabrication of conductive and magnetic hydrogels suggested that the PDA–PAM platform can be further extended to host other guest NPs with various therapeutic effects, such as drug- and growth factor-encapsulated polymeric or bioceramic NPs, greatly extending the range of applications of current hydrogels.
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This work was financially supported by the National Key Research and Development Program of China (2016YFB0700802), the 863 Program (2015AA034202), the NSFC (81671824), the Open Fund of Key Lab of Advanced Technologies of Materials (MOE), the Fundamental Research Funds for the Central Universities (2682016CX075), the Start-up Funding of the South University of Science and Technology of China (F Ren), the 2015 Doctoral Innovation Funds of Southwest Jiaotong University, and Sichuan Province Youth Science and Technology Innovation Team (2016TD0026).
The authors declare no conflict of interest.
Supplementary Information accompanies the paper on the NPG Asia Materials website
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Han, L., Yan, L., Wang, K. et al. Tough, self-healable and tissue-adhesive hydrogel with tunable multifunctionality. NPG Asia Mater 9, e372 (2017). https://doi.org/10.1038/am.2017.33
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