ライフサイエンスコーパス: hydrogel

1 g dictates solute loading and release from a hydrogel.

2 tions, can be generated in a photoresponsive hydrogel.

3 ing bonds with excess hydroxyl groups in the hydrogel.

4 poly(N-isopropylacrylamide) (p-NIPAAm)-based hydrogel.

5 self-assemble in situ into a supramolecular hydrogel.

6 lls (HUVECs) in gelatin methacrylate (GelMA) hydrogel.

7 er gelator (PG) calcium alginate in a hybrid hydrogel.

8 the bacteria was observed in the presence of hydrogel.

9 lithium- and bromine-enriched polyacrylamide hydrogel.

10 signals used to trigger insulin release from hydrogels.

11 singly stable artificial collagen fibers and hydrogels.

12 rved as labile crosslinks within step-growth hydrogels.

13 rization and diminish TGFbeta1 expression in hydrogels.

14 te materials, and 3D porous arrangements for hydrogels.

15 split rings interceded by glucose-responsive hydrogels.

16 synthesis and actuation of CRISPR-responsive hydrogels.

17 ated stiffness and self-healing functions of hydrogels.

18 a of red blood cells under polyvinyl alcohol hydrogels.

19 etention, absorption, and evaporation within hydrogels.

20 ermodynamic partitioning properties of those hydrogels.

21 g from recyclable thermosets to self-healing hydrogels.

22 The topological structure (3 D fiber hydrogel, 3 D GelMA hydrogel, and 2 D culture dish) and

23 hydrogel loadings of 2.5-7.5 g/L, the NaPAA hydrogels achieved ammonium concentrations of 8.3 +/- 0.

24 cularly confined aqueous environments (e.g., hydrogels), affects both the mode and rate of cleavage o

25 an act as transporters to move cargo such as hydrogel alginate capsules containing living cells.

26 These results suggest that simple hydrogels, already built into numerous systems, have a m

27 he design of a novel, intrinsically adhesive hydrogel and its use in developing internal therapeutic

28 ample of a two-component self-assembled LMWG hydrogel and was fully characterized.

29 s and bubble growth kinetics in soft gelatin hydrogel and water.

30 Upon direct peritumoral injection of the hydrogel and with the treatment of 808 nm laser irradiat

31 the local, interior elastic modulus of these hydrogels and both the radial and circumferential failur

32 unaltered cells can be magneto-patterned in hydrogels and cultured to generate heterogeneous tissues

33 Using stimulatory hydrogels and DCs expressing mutant cytoskeletal protein

34 sion has not been achieved between synthetic hydrogels and engineering materials, but is highly desir

35 f-assemble into supramolecular model network hydrogels and facilitate the elucidation of bond lifetim

36 on-based design has already shown promise in hydrogels and highly stretchy nondegradable polymers.

37 y applied delivery systems such as polymeric hydrogels and interstitial spray.

38 Linearly elastic polyacrylamide hydrogels and polydimethylsiloxane (PDMS) elastomers coa

39 mannans, the multiphase architecture of the hydrogels and the aggregative effects amongst hemicellul

40 ure-formed PEDOT:PSS hydrogels (RT-PEDOT:PSS hydrogel) and hydrogel fibers can be used for the develo

41 cal structure (3 D fiber hydrogel, 3 D GelMA hydrogel, and 2 D culture dish) and chemical factors (se

42 electronics including composites, conductive hydrogels, and electrochemical deposition.

43 ulics systems, shape memory polymers (SMPs), hydrogels, and liquid crystalline elastomers (LCEs) and

44 scribe a method that combines microfluidics, hydrogels, and Xenopus laevis egg extract to investigate

45 rmation from nanoparticles to organelle-like hydrogel architecture in living cells.

46 Casein-based hydrogels are biocompatible, biodegradable, renewable, e

47 romote FAK signaling and that stiff D- and N-hydrogels are constrained for vascular morphogenesis.

48 on of natural and synthetic thermoresponsive hydrogels are critically presented.

49 lin delivery and cell replacement therapies, hydrogels are employed to mitigate some of the most long

50 Hydrogels are formed using various triggers, including l

51 Such syringe-injectable hydrogels are highly desirable for minimally invasive bi

52 Albumin-based hydrogels are increasingly attractive in tissue engineer

53 Allyl sulfide hydrogels are used to support the formation of epithelia

54 f using gelatin- and fibrin-based hemostatic hydrogels as a scaffold on pulp regeneration in a minipi

55 of tailored poly(acrylic acid)-based (NaPAA) hydrogels as effective sorbents for ammonium removal fro

56 eports an investigation into organocatalytic hydrogels as prebiotically relevant systems.

57 plants and could expand the potential use of hydrogels as sensors, soft robots, and actuators.

58 ontact lenses and more specifically silicone hydrogels, as a previously overlooked source of plastic

59 sitive peptide that self-assembles to form a hydrogel at neutral pH.

60 Mice injected subcutaneously with 1,4-DPCA/hydrogel at the onset of periodontitis resolution displa

61 ylene glycol (600) diacrylate (PEG (600) DA) hydrogels at E(p) = 2, 5, 12 uJ.

62 r radiation at lambda = 532 nm within fibrin hydrogels at pulse energies of E(p) = 12, 18 uJ and with

63 ds indicate that rAAV-FLAG-hsox9/PEO-PPO-PEO hydrogel-augmented microfracture significantly improves

64 ization of aster movement away from V-shaped hydrogel barriers provided additional evidence for a MT-

65 Most importantly, the hydrogel based on 3 catalyzed the prebiotically relevant

66 In detail, an injectable and thermosensitive hydrogel based on poly(ethylene oxide) (PEO)-poly(propyl

67 test this relationship, we developed several hydrogel-based approaches to alter blastomere geometry i

68 and modularization to fabricate and assemble hydrogel-based microreactor assemblies comprising millio

69 a super-soft and super-elastic magnetic DNA hydrogel-based soft robot (DNA robot), which presents a

70 As a result, the hydrogel-based solar evaporator can extract water from a

71 capacities for generating higher-resolution hydrogel-based structures without necessarily having to

72 to measure endothelial permeability in a 3D hydrogel-based vascular model was developed that replace

73 or the development of soft and self-healable hydrogel bioelectronic devices.

74 an in-depth critical analysis on the use of hydrogel bioinks for printing microvascularized construc

75 demonstrated to develop injectable PEDOT:PSS hydrogels by taking advantage of the room-temperature ge

76 Water inside the hydrogel can quickly evaporate to dissipate the waste he

77 rrence mouse model suggest that this prodrug hydrogel can release cancer therapeutics into brain pare

78 ed anisotropic polyvinyl alcohol/polyaniline hydrogel can work as a stretching/compressing/bending el

79 s, and functional additives, and discuss how hydrogels can be employed as precursors and templates fo

80 Here, we show that cell-laden hydrogels can be patterned with algorithmically generate

81 h aliquots of fuel and removal of waste, the hydrogels can be re-programmed time after time.

82 The heterogeneous hydrogels can be structurally fused by interfacial cross

83 These composite hydrogels can be therefore envisioned as models of secon

84 In conclusion, we showed that AM hydrogels can be used as a potential carrier for ADSCs,

85 release surfactants only when placed in the hydrogel capsules.

86 ivity in liquid, vapor, and semisolid (e.g., hydrogels, cheese) phases.

87 Our method enables fatigue-resistant hydrogel coatings on diverse engineering materials with

88 optimized MCLW chip was formed from a total hydrogel concentration of 40% v/v of PEGMEA-PEGDA (M(n)

89 Hydrogels consist of a cross-linked polymer matrix imbib

90 The advantages of the nanoparticle and hydrogel constituents can be synergistically combined, e

91 ) p(HEMA-co-EGMA) was used to render complex hydrogel constructs through microlithographic fabricatio

92 purely relying on post-printing treatment of hydrogel constructs.

93 inexpensive, and nontoxic poly(acrylic acid) hydrogels containing calcium acetate.

94 ion and longer residence time than Poloxamer hydrogels currently being investigated clinically for he

95 sphinate at 1 x 10(-3) m), leads to complete hydrogel degradation in less than 15 s.

96 al of this work was to develop an injectable hydrogel delivery system that can allow localized releas

97 issue, polymer, agar, bone, spider silk, and hydrogel demonstrate that the developed model is superio

98 r results indicate that gelatin-SH/PEGDA IPN hydrogels demonstrated biocompatibility and mechanical p

99 ersion, while a freeze-drying can retain the hydrogel derived three-dimensionally (3D) porous structu

100 l types, and enhance mechanical stability in hydrogels derived from them.

101 SS (0.0, 0.1, and 0.5 wt%) manufactured into hydrogel disks using the two methods were shown to yield

102 We also show that non-dynamic (N) hydrogels do not promote FAK signaling and that stiff D-

103 e zinc ion sensor based on optical fiber and hydrogel doped with the fluorescent zinc ion probe molec

104 entangled link-augmented stretchable tissue-hydrogel (ELAST), a technology that transforms tissues i

105 e unique interconnected porous structures of hydrogels enable fast charge/mass transport while offeri

106 The double porosity of the alginate hydrogel enhanced the surface area of the polyaniline co

107 polyvinyl alcohol networks, building hybrid hydrogel evaporators in a cost-effective fashion ($14.9

108 Phenylboronic acid-hydrogels exhibit volumetric and dielectric variations i

109 rge-scale production of injectable PEDOT:PSS hydrogel fibers at room temperature.

110 OT:PSS hydrogels (RT-PEDOT:PSS hydrogel) and hydrogel fibers can be used for the development of soft

111 capsulation system based on calcium alginate hydrogels filled with cumin essential oil has been inves

112 e this type of substrate buried under a thin hydrogel film.

113 present a promising route to integrate those hydrogels films in electronic platforms for cell culture

114 d using mainstream ammonium removal by NaPAA hydrogels followed by biological assimilation from the g

115 is an increasing need to develop conducting hydrogels for bioelectronic applications.

116 Hydrogels for biomedical applications such as controlled

117 of the design and development of biopolymer hydrogels for biomedical applications, with an emphasis

118 summarize recent developments in the use of hydrogels for both insulin delivery and insulin-producin

119 wth enable the unique potential of this SAPD hydrogels for clinical translation as an adjunct therapy

120 challenges in the design of thermoresponsive hydrogels for CNS therapy are reviewed.

121 art insulin delivery, pH sensitive polymeric hydrogels for oral insulin delivery, and other physioche

122 st outline perspectives in glucose sensitive hydrogels for smart insulin delivery, pH sensitive polym

123 These PEDOT:PSS hydrogels form spontaneously after syringe injection of

124 The hydrogels form under ambient conditions within minutes u

125 nes the in vitro formulation development for hydrogel-forming microneedle arrays containing esketamin

126 Hydrogel-forming microneedle arrays were fully character

127 tion, we tested the ability of an injectable hydrogel-formulated PHD inhibitor, 1,4-dihydrophenonthro

128 We identified a PEG hydrogel formulation that uses thiol-vinyl sulfone Micha

129 Based on this injectable hydrogel formulation, we designed an affinity-based prot

130 In the present study, we developed hydrogels from amnion tissue as a delivery system for AD

131 such as optical transparency, porosity, and hydrogel functionalization by a well-controlled reactive

132 able properties that significantly influence hydrogel functions, including resorption and molecular d

133 vidin immobilized on functionalized acrylate hydrogel, generating a binding signal of (12.379 +/- 0.4

134 roup in vivo as compared to that in the core hydrogel group and the vehicle group.

135 rmore, more BMSCs survived in the core-shell hydrogel group in vivo as compared to that in the core h

136 The majority of research on albumin hydrogels has focused on bovine serum albumin (BSA), lea

137 use of extracellular matrix based injectable hydrogels has gained increased attention due to their un

138 These electrostatic hydrogels have a high affinity for a wide range of organ

139 However, injectable PEDOT:PSS hydrogels have been rarely reported.

140 Integrin-specific hydrogels have diverse pleiotropic effects on hMSC repar

141 Modified NaPAA hydrogels having 60% ionization and 4.8 mol % N',N'-meth

142 SA is the easiest method of synthesizing HSA hydrogels however hydrogel opacity and poor cell attachm

143 ine to yield hetero-ladder electroconductive hydrogels, iii) the development of a multi-analyte physi

144 tion (i.e., immunoprobing) in a large-format hydrogel immunoassay.

145 Hydrogel implantation in mouse and porcine models of hin

146 act directly with the benzaldehyde to form a hydrogel in situ based on Schiff base 2 as a low-molecul

147 onstrate its capability to form a reversible hydrogel in vitro containing amyloid-like fibrils.

148 zation potential comparable to bulk cellular hydrogels in this pilot study.

149 In vivo, PEG hydrogels induce local immune responses comparable to bi

150 A phenylboronic acid-based, hydrogel-interlayer Radio-Frequency (RF) resonator is de

151 ight the highly tunable synthesis of various hydrogels, involving key synthetic elements such as mono

152 p dip-coating process is described to enable hydrogel ionotronics of diverse configurations.

153 of fabrication expands the design space for hydrogel ionotronics.

154 The acrylate-based hydrogel is a synthetic polymer, so properties such as o

155 The data demonstrated that this core-shell hydrogel is an effective strategy for promoting transpla

156 generates in pure water and that in gelatin hydrogel is considered.

157 The hydrogel is cytocompatible and supports 2D/3D cell growt

158 The hydrogel is demonstrated to low down the operating tempe

159 ion and Au nanoparticle hybrid (DNA-UCNP-Au) hydrogel is developed.

160 The hydrogel is expected to be widely adopted in current sem

161 Here, an allyl sulfide photodegradable hydrogel is presented, achieving rapid degradation throu

162 ntrol of cell orientation within 3D collagen hydrogels is developed to dynamically create various tai

163 Here, a new method for forming hydrogels is introduced: ultrasound-triggered enzymatic

164 incorporated into an injectable alginate-RGD hydrogel laden with endothelial cells (ECs) for further

165 nt stabilized by an outer stimuli-responsive hydrogel layer (thickness of ~150 nm) that yields the mi

166 ggered unlocking of the outer, pH-responsive hydrogel layer and to the release of insulin.

167 drogel layer to Zn(2+)-ions and/or the outer hydrogel layer to acidic pH or crown ether leads to the

168 Subjecting the inner hydrogel layer to Zn(2+)-ions and/or the outer hydrogel

169 The hydrogel layers exist in a higher stiffness state that p

170 This results in the hydrogel layers of lower stiffness allowing either the m

171 ridging units associated with the respective hydrogel layers.

172 degradation, we designed concentric cylinder hydrogels loaded with different cargoes (e.g., model pro

173 consisted of a dissociative thermoresponsive hydrogel-loaded clip unit where the sandwich-type immuno

174 At hydrogel loadings of 2.5-7.5 g/L, the NaPAA hydrogels ac

175 sms and transform the current development of hydrogel materials into sustainable energy and water tec

176 ices, and immunoassay scaffolds that utilize hydrogel materials is informed by an understanding of th

177 c matrices such as basement membrane extract hydrogels (Matrigel) that allows us to measure contracti

178 e embedding of fresh frozen specimens into a hydrogel matrix composed of hydroxypropyl methylcellulos

179 ng clusters" (THBCs) as side groups into the hydrogel matrix.

180 immobilization of the bioreceptor within the hydrogel matrix.

181 echanical deformation of the 3D cross-linked hydrogel matrix.

182 Perfusable dendritic networks in cell-laden hydrogels may help sustain thick and densely cellularize

183 ation, as exemplified by an enzyme-resistant hydrogel, may thus be developed.

184 Furthermore, hydrogel membrane resistances extracted from equivalent

185 ines cell-free extracts with photo-patterned hydrogel micro-enclosures as a means to investigate micr

186 Here, a dual-function nanoparticle-loaded hydrogel microcapsule is developed that enables graft re

187 lar arrays on a flexible film and conductive hydrogel micropatterns including polyethylene glycol (PE

188 wo-photon polymerization 3D microprinting of hydrogel microrobots with ample functionalization: tunab

189 be converted into highly conductive and soft hydrogel microstructures.

190 In this work, we used gelatin to prepare hydrogel nanoparticles and studied whether gelatin nanop

191 CG can be entrapped in the crosslinked HD/Se hydrogel network and long lasting photothermal efficacie

192 on of energy mediated by the 3D cross-linked hydrogel network facilitates pairwise interactions betwe

193 geneously distributed throughout a tissue or hydrogel network.

194 ted mesoporous, cubic ferritin crystals with hydrogel networks, resulting in hybrid materials (polyme

195 talline frameworks or uniform nanostructured hydrogels of spherical, vesicular, or cylindrical morpho

196 ion from 0.01 to 1.00 wt% PEDOT:PSS produced hydrogels of varying and tunable electrical and electroc

197 which is fabricated by electrodeposition of hydrogel on a microdisk electrode, immobilizes the elect

198 ordered nanocrystalline domains of synthetic hydrogels on engineering materials can give a fatigue-re

199 method of synthesizing HSA hydrogels however hydrogel opacity and poor cell attachment limit their us

200 lity of bioorthogonal catalysis and physical hydrogels opens up new opportunities to administer and m

201 lized mass spectrometry enhanced by affinity hydrogel particles (analytical sensitivity = 2.5 pg/mL)

202 ynthesizing uniform, deformable and tuneable hydrogel particles, which can also be easily derivatized

203 we conclude that our Coa-embedded composite hydrogel platform could effectively augment osteochondra

204 l epithelial stem/progenitor cells on fibrin hydrogels pre-incubated with LN-511-E8 resulted in multi

205 e magnetic susceptibility of the surrounding hydrogel precursor solution is enhanced.

206 The formation of hydrogel prevents the aggregation of graphene oxide and

207 Three-dimensional (3D) hydrogel printing enables production of volumetric archi

208 Furthermore, D-hydrogels promote hECFC microvessel formation and angiog

209 e also allowing systematic variations to the hydrogel properties tailored for the organoid of interes

210 ration in the determination of nanocomposite hydrogel properties.

211 exist; these account for differences in the hydrogel properties.

212 release microspheres with a thermoresponsive hydrogel provides flexibility for encapsulating therapeu

213 f compartmentalized microscale objects in 3D hydrogels provides a step towards the modular assembly o

214 osheets captured within agarose and alginate hydrogels, providing a biodegradable catalytic framework

215 ctors in mice using a platform of injectable hydrogels readily modified to present interfaces with di

216 els as the result of phase transition of the hydrogels, realizing multiplexed thermal image- and dist

217 pai-conjugated polymers (CPs) in conductive hydrogels remains challenging due to the water-insoluble

218 In addition, the NaPAA hydrogels removed 25-51% ammonium in 10 min from synthet

219 Self-assembled peptide hydrogels represent the realization of peptide nanotechn

220 esis and testing of either PEG-DNA or PA-DNA hydrogels require 3-4 d of laboratory time.

221 e immobilization of TD-NTs in size-exclusive hydrogel resins simultaneously adsorbs septic molecules,

222 f neurotrophin-3 from peptide-conjugated PEG hydrogels resulting from the reversible interaction betw

223 s-laden microcarriers loaded into injectable hydrogels revealed their capability of tunneling formati

224 nd tendons, robust antifouling coatings, and hydrogel robots.

225 that these room-temperature-formed PEDOT:PSS hydrogels (RT-PEDOT:PSS hydrogel) and hydrogel fibers ca

226 ecules, and live cell encapsulation within a hydrogel scaffold.

227 A highly specific DNA-functionalized hydrogel sensing layer was integrated with the diffusive

228 tion of Oenococcus oeni into SiO(2)-alginate hydrogel (Si-ALG) and the addition of lysozyme in wines

229 patterns including polyethylene glycol (PEG) hydrogel, silver nanowires (AgNW), and reduced graphene

230 (sVEGFR1), a VEGF receptor antagonist, in a hydrogel skewed differentiation of MF-activated SSCs tow

231 Bioprinting uses hydrogel solutions called bioinks as both cell carriers

232 res and photopolymerized to yield continuous hydrogel structures.

233 ing temperature-responsive or non-responsive hydrogels, structures that undergo reversible curling we

234 is and fabrication of different nanoparticle-hydrogel superstructures are discussed, followed by an o

235 Each component of these nanoparticle-hydrogel superstructures can be easily modified, resulti

236 When we implant hydrogel supplemented with endothelial cells (ECs) on th

237 Our results showed that AM hydrogels supported cell viability, proliferation, and s

238 dwiching antibody probe solution against the hydrogel surface yields spatially nonuniform dilution.

239 ropic proteins are superior to other organo-/hydrogel systems.

240 n (CPT)-based self-assembling prodrug (SAPD) hydrogel that can be used as an adjunct therapy for loca

241 ed poly(ethylene) glycol diacrylate (PEG-DA) hydrogel that was cast-molded into a circular shape.

242 t poly(2-hydroxylethyl methacrylate) (pHEMA) hydrogel that was resistant to leaching in ultrapure H(2

243 r technique, we generated a multi-responsive hydrogel that, at one temperature, could be moved throug

244 dived in suspensions or emulsions and macro hydrogels that are gel colloid type.

245 ssues and organs, including the use of smart hydrogels that can be modified to enhance organization a

246 to compartmentalize organisms into polymeric hydrogels that control the final consortium composition

247 Biohybrid hydrogels that mimic the form and function of natural ma

248 Responsive hydrogels that undergo controlled shape changes in respo

249 etic cryogels, an advanced type of polymeric hydrogel, that are syringe-deliverable through hypodermi

250 ther than magnetizing the objects within the hydrogel, the magnetic susceptibility of the surrounding

251 enzyme catalyzes the formation of fibrinogen hydrogels through covalent intermolecular crosslinking.

252 d density results in strong adhesions of the hydrogel to a range of surfaces, including glass, plasti

253 ing a temperature-responsive, shear-thinning hydrogel to compartmentalize organisms into polymeric hy

254 established using a hyaluronic acid-gelatin hydrogel to culture a mixture of GBM and MG and evaluate

255 We investigated the potential of amnion hydrogel to maintain ADSC functions, the synergistic eff

256 ochannel networks are generated in a gelatin hydrogel to overcome the diffusion limit of nutrients an

257 e, which was then encapsulated into the core hydrogel to support the BMSC growth and differentiation.

258 aper-based devices that use Cas12a-sensitive hydrogels to convert DNA inputs into a variety of visual

259 ircumvent this restriction, we have utilized hydrogels to cover such surfaces and maintain a more phy

260 hnology that transforms tissues into elastic hydrogels to enhance macromolecular accessibility and me

261 Here, we exploit photostiffening hydrogels to manipulate nuclear mechanosensing in human

262 thography protocols necessary to shape these hydrogels to match the dimensions and density of in vivo

263 sochoric, and reversible switching from soft hydrogels to rigid plastics at elevated temperature is r

264 nonthrolin-4-one-3-carboxylic acid (1,4-DPCA/hydrogel), to promote regeneration of alveolar bone lost

265 Hydrogel touch pads are adhered to curved or flat insula

266 -responsive poly(acrylamide-co-acrylic acid) hydrogel transduces optical energy into mechanical defor

267 omaterial was capable of transforming into a hydrogel upon introduction to a hydrated environment.

268 nherently conductive polymers with bioactive hydrogels using bi-functional monomers such as poly(pyrr

269 can tune the stiffness of covalent adaptable hydrogels using different wavelengths of visible light.

270 The hydrogel was expected not to interfere with standard tis

271 ectable nanoparticle encapsulated core-shell hydrogel was fabricated for simultaneous iron overload c

272 lantation with high-molecular-weight keratin hydrogel was selected as the inner core.

273 The resulting bio-inert hydrogel was then subjected to air plasma treatment whic

274 ermeability of endothelial cells cultured on hydrogels was electrochemically measured after being sub

275 BSA) analyte molecules, indicating that the hydrogel waveguide film is highly porous to both sizes o

276 Using engineered hydrogels, we demonstrate that the mechanical properties

277 cose test strips from MGCN-chitin-AcOH based hydrogel were reported and verified for semi-quantitativ

278 Stable and translucent HSA hydrogels were created by controlled thermal gelation an

279 In vivo studies in which the hydrogels were formed in situ over stromal keratectomy w

280 e selected as the therapeutic agents and the hydrogels were formulated based on the increasing concen

281 -D printed lines of varying wt% of PEDOT:PSS hydrogels were shown to alter the cutoff frequency of th

282 In conclusion, the hydrogels were successfully developed and proven to have

283 ferent physicochemical states, e.g. particle hydrogels, which can be dived in suspensions or emulsion

284 oth RF read-out and phenylboronic acid-based hydrogels will enable biosensors capable of long-term, r

285 chelator-loaded low-molecular-weight keratin hydrogel with quick degradation property was selected as

286 However, the emergence of conducting polymer hydrogels with a desirable network structure cannot be r

287 Hydrogels with adhesive properties have potential for nu

288 ased protein release system by modifying PEG hydrogels with affinity peptides specific to neurotrophi

289 Our work demonstrates that the 3D-printed hydrogels with angiogenic cells hold great promise for p

290 ed with a pendant bisphosphonate to generate hydrogels with enhanced mechanical properties and preser

291 functionalisation of inert heat-derived HSA hydrogels with extracellular matrix proteins and these m

292 This injectable formulation provides elastic hydrogels with higher mechanical rigidity, better bio-ad

293 olution temperature, we were able to develop hydrogels with highly tunable volumetric expansion.

294 Here, we develop hydrogels with identical polymer components but differen

295 sufficient concentrations, these tapes form hydrogels with reduced storage moduli but retain the she

296 cience is demonstrated by the fabrication of hydrogels with specific architectures, photo-immobilizat

297 s on early stages of vasculogenesis by using hydrogels with tunable stiffness and stress relaxation.

298 Using a common polyacrylic acid hydrogel, with divalent cations and acid as representati

299 ponses comparable to biocompatible Poloxamer hydrogels, yet they released payloads at a ~5-fold slowe

300 The incorporation of nanoparticles into hydrogels yields novel superstructures that have become