Background: Intervertebral disc degeneration (IDD) is the most common diagnosis of patients with lower back pain. IDD is the underlying lesion of many spinal degenerative diseases; however, the role of cGAS/Sting/NLRP3 pathway and epigallocatechin gallate (EGCG) in the development of IDD remained unclear. Methods: The expressions of cGAS, Sting and NLRP3 mRNA of intervertebral disc (IVD) samples from IDD patients and controls were detected by RT-PCR. The nucleus pulposus cells (NPCs) were induced by hydrogen peroxide (H 2 O 2 ) and used as an in-vitro model. Both 5 μM and 25 μM EGCG treatment were used to detect the effect of EGCG on the in-vitro model. Cell viability was detected by the MTT method, and cell apoptosis and cell cycle would be detected by flow cytometry. Western blot was used in the detection of the expression of cGAS/Sting/NLRP3 as well as apoptosis-related protein level. ELISA was used in the detection of pro-inflammatory factors, including IL-1β, TNF-α, IL-6 and IL-10. Results: The expressions of cGAS, Sting and NLRP3 mRNA were significantly increased in the IVD samples from IDD patients and NLRP3 was associated with cGAS and Sting. Advanced in-vitro study showed that H 2 O 2 significantly increased the expression of cGAS, Sting and NLRP3 protein levels. Advanced experiments showed that EGCG treatment demonstrated significant protective effects in cell viability, apoptosis, cell cycle arrest and inflammatory status through down-regulation of cGAS/Sting/NLRP3 pathway. Conclusion: It was shown that the cGAS, Sting and NLRP3 up-regulation was associated with the incidence of IDD. Our findings also suggest that EGCG treatment would provide anti-apoptosis, anti-inflammation and promote cell viability in H 2 O 2 treatment-incubated NPCs through inhibiting cGAS/Sting/NLRP3 pathway.
stimuli generate driving forces from the interaction between the micro/nanorobots and aspects of the treatment microenvironment, such as pH, enzymes, and redox potential. [4][5][6][7][8][9] However, the controllability of endogenous power-driven cell robots is limited, considering tumor heterogeneity. In addition, the cell robots may lose driving force when local lesions are cured. In contrast, driving forces generated from externally-applied fields are controllable, and can be output continuously. Micro/ nanorobots for biomedical applications, driven by optical, [9][10][11][12][13] acoustic, [14][15][16][17][18] or magnetic fields, [19][20][21][22][23] have been reported. In particular, micro/nanorobots controlled by magnetic fields have been studied extensively, because magnetic fields can penetrate tissues without attenuation of energy. [23][24][25][26] In general, magneticallycontrolled micro/nanorobot systems can be divided into two components: the magnetic manipulation platform (MMP), and the magnetized micro/nanorobot (MMR). The MMP relies primarily on the characteristics of superimposed magnetic fields, generated by different coils, that can be oriented in any desired direction. [27,28] To be biocompatible, cell membranes, [29] cell derived vesicles, [30] or natural cells [31,32] can be used to camouflage MMRs. [33] Magnetized cell-based robots (MCRs) are particularly effective in targeted treatment of tumors, owing to their homology with the patient, which not only gives the cell carrier excellent biocompatibility, but also takes advantage of the cells' specialized functions. [34,35] MCR fabrication is typically manifested as adhesion of magnetic materials to the cell membrane, or entry of magnetic materials to the cell by means, such as electrostatic adsorption or endocytosis. Examples of the latter strategy include the loading of red blood cells, [36][37][38] macrophages, [32,39] and stem cells [40,41] with iron oxide nanoparticles (NPs) containing drugs, for effective targeting of lesion locations under magnetic drive. However, with this strategy, drug loading is limited, to avoid influencing the activity of cells. An alternative strategy is to wrap the drugs in a membrane, and release them when the cell robots reach the lesion location. For example, liposome or polymer NPs can be loaded into live macrophages thanks to their natural phagocytic function, and the load-drugs can subsequently be released under endogenous or exogenous Injecting micro/nanorobots into the body to kill tumors is one of the ultimate ambitions for medical nanotechnology. However, injecting current micro/ nanorobots based on 3D-printed biocompatible materials directly into blood vessels for targeted therapy is often difficult, and mistakes in targeting can cause serious side effects, such as blood clots, oxidative stress, or inflammation. The natural affinity of macrophages to tumors, and their natural phagocytosis and ability to invade tumors, make them outstanding drug delivery vehicles for targeted tumor therapy. Hence, a mag...
Patients undergoing sacral tumor surgery may be at greater risk for developing wound complications. In this study, it seems that albumin<3.0, operating time >6 hours, and previous surgery may predict those patients that were more prone to developing postoperative wound infection. Using a single surgical team and no instrumentation seems to provide protection against postoperative wound infection in this patient population.
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