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This study shows that the synthesis of di‐BCP between amino acid l‐glutamic acid (l‐GluA) and hydrophobic polycaprolactone (PCL) leads to multifunctional and multifaceted capsule formation with different dispersion solvents. Successful synthesis of [(l‐GluA)‐b‐(PCL)] was confirmed by using FTIR and 1H NMR characterizations. For morphological studies, synthesized di‐BCP of [(l‐GluA)‐b‐(PCL)] was dispersed in four different solvents such as acetone, DMSO, IPA, and ethanol and was used for sample preparation for SEM imaging. Interestingly, smooth‐surfaced NPs (defined as type I NPs), rough‐surfaced NPs (type II NPs), porous NPs (type III NPs), and football‐type deep excavation having NPs (defined as type IV NPs). Furthermore, these NPs were characterized through BET, AFM, and DLS for particle size and ζ potential of NPs. LC for types III and IV NPs was calculated to be 1.96% ± 0.01% and 1.92% ± 0.01%, respectively. EE of types III and IV NPs was calculated to be 91% ± 1.5% and 94% ± 1.2%. We used K562 (leukemia blood cancer) and HEK293 (embryonic kidney) cells for in vitro studies. DOX@[(l‐GluA)‐b‐(PCL)] nanoformulation related to types III and IV NPs shows significant early apoptosis that is, 29.17%, which is a remarkable programmed cell death for these porous nanoparticles.
This study shows that the synthesis of di‐BCP between amino acid l‐glutamic acid (l‐GluA) and hydrophobic polycaprolactone (PCL) leads to multifunctional and multifaceted capsule formation with different dispersion solvents. Successful synthesis of [(l‐GluA)‐b‐(PCL)] was confirmed by using FTIR and 1H NMR characterizations. For morphological studies, synthesized di‐BCP of [(l‐GluA)‐b‐(PCL)] was dispersed in four different solvents such as acetone, DMSO, IPA, and ethanol and was used for sample preparation for SEM imaging. Interestingly, smooth‐surfaced NPs (defined as type I NPs), rough‐surfaced NPs (type II NPs), porous NPs (type III NPs), and football‐type deep excavation having NPs (defined as type IV NPs). Furthermore, these NPs were characterized through BET, AFM, and DLS for particle size and ζ potential of NPs. LC for types III and IV NPs was calculated to be 1.96% ± 0.01% and 1.92% ± 0.01%, respectively. EE of types III and IV NPs was calculated to be 91% ± 1.5% and 94% ± 1.2%. We used K562 (leukemia blood cancer) and HEK293 (embryonic kidney) cells for in vitro studies. DOX@[(l‐GluA)‐b‐(PCL)] nanoformulation related to types III and IV NPs shows significant early apoptosis that is, 29.17%, which is a remarkable programmed cell death for these porous nanoparticles.
As an open microfluidic technology with excellent anti‐fouling and energy‐saving properties, liquid gating technology can selectively separate or transfer multiphase fluids, which has shown great application value in the field of biomedical engineering. However, no study has demonstrated that liquid gating technology has the ability to transfer high‐viscosity fluids and biologically active substances, and current liquid gating valves are unable to realize smart‐responsive pulsed‐patterned transfer, which severely limits their application scope. In this paper, liquid gating technology is combined with magnetically responsive materials to prepare a liquid‐based magnetic porous membrane (LMPM) with excellent magnetostatic deformation capability and antifouling properties. On this basis, a magnetic liquid gating valve terminal (MLGVT) with patterning transfer capability is developed, and the feasibility of liquid gating technology for transferring high‐viscosity fluids and hydrogel bioinks is explored. Meanwhile, a flexible MLGVT is prepared and realized for targeted drug delivery. This study expands the potential of liquid gating technology for drug delivery, cellular transport and smart patches.
Ferrofluid droplet has wide applications in bioanalysis manipulation. This study presents a ferrofluid microrobot for manipulation in different workspaces. Based on the deformation character of droplet, the ferrofluid microrobot has the capabilities of climbing the 3D (3-dimensional) surface, splitting in the channel, and transporting large particles. To manipulate in multiple workspaces with the capabilities, the size and magnetic force of ferrofluid are studied for suitable scenes. It shows that the diameter of 0.5 μl ferrofluid is around 980 μm. The manipulation force of different ferrofluid microrobots ranges from micronewton to millinewton. Subsequently, we have verified the manipulation of the ferrofluid microrobot on a 3D chip by permanent magnet. The ferrofluid microrobot can climb the stairs only when the height of the magnetic fluid is higher than twice the height of the stairs. Meanwhile, splitting of ferrofluid microrobot in the microfluidic chip has been successfully demonstrated. It indicates that the splitting influenced by the magnetic field and large magnetic force is easier to split the microrobot. Finally, the transportation of large polystyrene microparticles (150 μm) is confirmed by the ferrofluid microrobot. These capabilities show that the ferrofluid microrobot has the potential application advantage in biomedicine's micro-drug testing.
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