Synthesis of Chitosan Oligosaccharide-Loaded Glycyrrhetinic Acid Functionalized Mesoporous Silica Nanoparticles and In Vitro Verification of the Treatment of APAP-Induced Liver Injury

Objective: the study was to find a suitable treatment for acute drug-induced liver injury. The use of nanocarriers can improve the therapeutic effect of natural drugs by targeting hepatocytes and higher loads. Methods: firstly, uniformly dispersed three-dimensional dendritic mesoporous silica nanospheres (MSNs) were synthesized. Glycyrrhetinic acid (GA) was covalently modified on MSN surfaces through amide bond and then loaded with COSM to form drug-loaded nanoparticles (COSM@MSN-NH2-GA). The constructed drug-loaded nano-delivery system was determined by characterization analysis. Finally, the effect of nano-drug particles on cell viability was evaluated and the cell uptake in vitro was observed. Results: GA was successfully modified to obtain the spherical nano-carrier MSN-NH2-GA (≤200 nm). The neutral surface charge improves its biocompatibility. MSN-NH2-GA has high drug loading (28.36% ± 1.00) because of its suitable specific surface area and pore volume. In vitro cell experiments showed that COSM@MSN-NH2-GA significantly enhanced the uptake of liver cells (LO2) and decreased the AST and ALT indexes. Conclusion: this study demonstrated for the first time that formulation and delivery schemes using natural drug COSM and nanocarrier MSN have a protective effect on APAP-induced hepatocyte injury. This result provides a potential nano-delivery scheme for the targeted therapy of acute drug-induced liver injury.


Introduction
Acetaminophen (APAP), which is also known as N-acetyl-p-aminophenol or paracetamol, is among the most frequently used tablets due to its analgesic and antipyretic properties [1,2]. Especially in the era of the COVID-19 virus epidemic, because of its low price and significant effect on fighting fever and muscle soreness, it is often combined with other drugs and is easily overused frequently [3][4][5]. Therefore, the safety of APAP is questionable. Studies have shown that its overdose might lead to hepatotoxicity and acute liver failure (ALF) [6,7]. APAP mediates the formation of N-acetyl-p-benzoquinone imine through cytochrome P450 in the human body, leading to mitochondrial oxidative stress and activation of c-Jun N-terminal kinase, which will lead to nuclear translocation of mitochondrial proteins and induce DNA fragmentation, eventually leading to liver cell necrosis [8]. The drug-induced liver damage (DILI) observed with APAP is the second

Synthesis and Characterization of MSN-NH 2 -GA and COSM@MSN-NH 2 -GA
The nanomedicine, labelled COSM@MSN-NH 2 -GA, was synthesized in several steps (Scheme 1). Briefly, uniformly dispersed three-dimensional dendritic mesoporous silica nanospheres were synthesized by referring to the preparation method by Shen's team [40]. These 3D dendritic MSNs exhibit unique advantages in protein loading and release due to their adjustable large porosity and intelligent layered mesostructure. More importantly, the release rate depends in part on graded biodegradation as 3D dendritic MSNs with larger pore sizes have a faster rate of biological interpretation [41,42]. In this study, GA was selected as the target ligand, and by grafting alkoxysilane, MSNs were externally functionalized and finally anchored by amino reaction with amino-modified GA [43]. COSM was loaded in ethanol by impregnation [44]. The formed glycyrrhetinic acidfunctionalized MSN nanoparticles exhibit the potential to specifically deliver drugs to hepatocytes [42].

Synthesis and Characterization of MSN-NH2-GA and COSM@MSN-NH2-GA
The nanomedicine, labelled COSM@MSN-NH2-GA, was synthesized in several steps (Scheme 1). Briefly, uniformly dispersed three-dimensional dendritic mesoporous silica nanospheres were synthesized by referring to the preparation method by Shen's team [40]. These 3D dendritic MSNs exhibit unique advantages in protein loading and release due to their adjustable large porosity and intelligent layered mesostructure. More importantly, the release rate depends in part on graded biodegradation as 3D dendritic MSNs with larger pore sizes have a faster rate of biological interpretation [41,42]. In this study, GA was selected as the target ligand, and by grafting alkoxysilane, MSNs were externally functionalized and finally anchored by amino reaction with amino-modified GA [43]. COSM was loaded in ethanol by impregnation [44]. The formed glycyrrhetinic acid-functionalized MSN nanoparticles exhibit the potential to specifically deliver drugs to hepatocytes [42]. Scheme 1. Diagram of the synthetic process used to develop our nanomedicine and the simulated cell uptake schematic diagram of COSM@MSN-NH2-GA.
As shown in Figure 1a,b, SEM revealed that the MSN nanoparticles are spherical and exhibit a uniform particle size distribution. TEM showed that the MSN nanoparticles are spherical with clear and uniform mesoporous channels on the surface and a uniform particle size, which is consistent with the SEM results. After targeted modification, MSN-NH2-GA nanoparticles with a uniform particle size and complete morphology were obtained. The particle size distributions of MSN and MSN-NH2-GA nanoparticles are (156.7 ± 61.7) nm and (190.7 ± 78.1) nm, respectively (Figure 1c). The particle size of the nanoparticles gradually increases with the modification process. The nanoparticles are dispersed in different solvents, and the measured particle size is also inconsistent because the DLS measurement conditions are in aqueous solution. Therefore, the DLS results are slightly larger than the TEM particle size results. The zeta potential of the nanoparticles also reflects the macroscopic changes in the surface modification of the nanoparticles. Figure 1d shows that the zeta potential of the blank MSN was −40.42 ± 22.11 mV due to the presence of silanol groups on the MSN surface and its negative charge. After amino modification occurred, the amino group (positively charged) replaced silanol (which is negatively charged), so the zeta potential changed from negative to positive, and the zeta potential of MSN-NH2 was 58.62 ± 4.479 mV. When glycyrrhetinic acid was docked, part of the amino group was consumed and covered so that the positive charge decreased, and the zeta potential of MSN-NH2-GA became (7.013 ± 4.132) mV. Scheme 1. Diagram of the synthetic process used to develop our nanomedicine and the simulated cell uptake schematic diagram of COSM@MSN-NH 2 -GA.
As shown in Figure 1a,b, SEM revealed that the MSN nanoparticles are spherical and exhibit a uniform particle size distribution. TEM showed that the MSN nanoparticles are spherical with clear and uniform mesoporous channels on the surface and a uniform particle size, which is consistent with the SEM results. After targeted modification, MSN-NH 2 -GA nanoparticles with a uniform particle size and complete morphology were obtained. The particle size distributions of MSN and MSN-NH 2 -GA nanoparticles are (156.7 ± 61.7) nm and (190.7 ± 78.1) nm, respectively (Figure 1c). The particle size of the nanoparticles gradually increases with the modification process. The nanoparticles are dispersed in different solvents, and the measured particle size is also inconsistent because the DLS measurement conditions are in aqueous solution. Therefore, the DLS results are slightly larger than the TEM particle size results. The zeta potential of the nanoparticles also reflects the macroscopic changes in the surface modification of the nanoparticles. Figure 1d shows that the zeta potential of the blank MSN was −40.42 ± 22.11 mV due to the presence of silanol groups on the MSN surface and its negative charge. After amino modification occurred, the amino group (positively charged) replaced silanol (which is negatively charged), so the zeta potential changed from negative to positive, and the zeta potential of MSN-NH 2 was 58.62 ± 4.479 mV. When glycyrrhetinic acid was docked, part of the amino group was consumed and covered so that the positive charge decreased, and the zeta potential of MSN-NH 2 -GA became (7.013 ± 4.132) mV. ure 2 shows that all samples show the skeleton absorption peaks of silicon-based materials, namely, the Si-O-Si symmetrical stretching vibration peak (800 cm −1 ), the Si-O-Si asymmetric stretching vibration peak (1085 cm −1 ), and the Si-OH stretching vibration peak (960 cm −1 ). The infrared spectra peaks of MSN-NH2 are located at 2922 cm −1 and 2855 cm −1 , which are the C-H stretching vibrations of APTES, indicating that the amino group was correctly modified. The amide II band at 1445 cm −1 and the C=C stretching vibration of GA at 1545 cm −1 indicate that the GA molecule is modified to MSN by amide bonds.  To decide the chemical grafting of exceptional practical groups, MSN, MSN-NH 2 and MSN-NH 2 -GA were characterised using distinct methods and after every reaction step. Using FTIR spectroscopy, we can see the functionalization manner of nanoparticles. Figure 2 shows that all samples show the skeleton absorption peaks of silicon-based materials, namely, the Si-O-Si symmetrical stretching vibration peak (800 cm −1 ), the Si-O-Si asymmetric stretching vibration peak (1085 cm −1 ), and the Si-OH stretching vibration peak (960 cm −1 ). The infrared spectra peaks of MSN-NH 2 are located at 2922 cm −1 and 2855 cm −1 , which are the C-H stretching vibrations of APTES, indicating that the amino group was correctly modified. The amide II band at 1445 cm −1 and the C=C stretching vibration of GA at 1545 cm −1 indicate that the GA molecule is modified to MSN by amide bonds.
As seen in Figure 3a,b, the adsorption isotherm conforms to the Langmuir IV isotherm, and the nanomaterial exhibits a mesoporous structure. It can be seen that, when the relative pressure P/P 0 < 0.35, N 2 is present on the surface of the material channel. With single molecule and multimolecular layer adsorption, the amount of adsorption slowly increases. Under a relative pressure of 0.35 < P/P 0 < 0.8, an obvious capillary condensation step can be observed, and the adsorption amount increases, indicating that the pore size distribution is wide. When 0.8 < P/P 0 < 0.9, the nitrogen adsorption and the outer surface curve are gentle. When P/P 0 > 0.9, there is a hysteresis loop. At this time, nitrogen adsorption occurs in the gap between the particles, the adsorption capacity increases, and the curve shows an additional large jump. The postgrafting method was used to modify the targeting group so that group modification would also occur in the pores of the nanoparticles. Figure 3b shows that the modification of amino and glycyrrhetinic acids exhibited a certain covering effect on the nanoparticles. As seen in Figure 4a As seen in Figure 3a,b, the adsorption isotherm conforms to the Langmuir IV isotherm, and the nanomaterial exhibits a mesoporous structure. It can be seen that, when the relative pressure P/P0 < 0.35, N2 is present on the surface of the material channel. With single molecule and multimolecular layer adsorption, the amount of adsorption slowly increases. Under a relative pressure of 0.35 < P/P0 < 0.8, an obvious capillary condensation step can be observed, and the adsorption amount increases, indicating that the pore size distribution is wide. When 0.8 < P/P0 < 0.9, the nitrogen adsorption and the outer surface curve are gentle. When P/P0 > 0.9, there is a hysteresis loop. At this time, nitrogen adsorption occurs in the gap between the particles, the adsorption capacity increases, and the curve shows an additional large jump. The postgrafting method was used to modify the targeting group so that group modification would also occur in the pores of the nanoparticles. Figure 3b shows that the modification of amino and glycyrrhetinic acids exhibited a certain covering effect on the nanoparticles. As seen in Figure 4a,b, the MSNs had specific surfaces of 565.27 m 2 /g, contained pores with a size of 6.15 nm, and a volume of 1.18 cm 3 /g. MSN-NH2-GA had specific surface areas of 245.83 m 2 /g, showed pores with a size of 6.04 nm, and a volume of 0.69 cm 3 /g. Therefore, the specific surface area, pore volume and pore size of MSN-NH2-GA decreased accordingly.
To identify the COSM API, nanocarriers (MSN-NH2-GA), physically mixed groups, and nanopharmaceutical groups, differential scanning calorimetry (DSC) was performed. The results are shown in Figure 5. The black (A), red (B), blue (C), and green (D) curves represent the COSM, nanocarrier (MSN-NH2-GA), physical mixing, and nanomedicine (COSM@MSN-NH2-GA) groups, respectively. COSM exhibits an obvious single-melting endothermic peak at approximately 200 °C, while the nanocarrier (MSN-NH2-GA) group shows an obvious dehydration peak at approximately 100 °C. The DSC analysis of the physically mixed group contains characteristic absorption peaks of the carriers and COSM, which was because the drug and the carriers were simply mixed. In the DSC analysis of the nanodrug group, the characteristic absorption peak of the main drug (COSM) disappeared, indicating that COSM was present in an amorphous form in the nanodrug group and was no longer present in a crystalline state. These observations indicate that COSM was successfully incorporated into the mesoporous channels of MSN-NH2-GA.  According to the previous experiments, the feasibility of using 3,5-dinitrosalicylic acid (DNS) as a method for the determination of COSM content was determined, and the specific determination conditions were finally optimized and screened out [45,46]. In the drug loading experiment, the dosage ratio of COSM and MSN-NH2-GA is 1:2, and the drug loading time is 12 h, which is the best drug loading condition. The encapsulation efficiency (EE%) was 28.36% and the load capacity (LC%) was 56.72%.  According to the previous experiments, the feasibility of using 3,5-dinitrosalicylic acid (DNS) as a method for the determination of COSM content was determined, and the specific determination conditions were finally optimized and screened out [45,46]. In the drug loading experiment, the dosage ratio of COSM and MSN-NH2-GA is 1:2, and the drug loading time is 12 h, which is the best drug loading condition. The encapsulation efficiency (EE%) was 28.36% and the load capacity (LC%) was 56.72%. To identify the COSM API, nanocarriers (MSN-NH 2 -GA), physically mixed groups, and nanopharmaceutical groups, differential scanning calorimetry (DSC) was performed. The results are shown in Figure 5. The black (A), red (B), blue (C), and green (D) curves represent the COSM, nanocarrier (MSN-NH 2 -GA), physical mixing, and nanomedicine (COSM@MSN-NH 2 -GA) groups, respectively. COSM exhibits an obvious single-melting endothermic peak at approximately 200 • C, while the nanocarrier (MSN-NH 2 -GA) group shows an obvious dehydration peak at approximately 100 • C. The DSC analysis of the physically mixed group contains characteristic absorption peaks of the carriers and COSM, which was because the drug and the carriers were simply mixed. In the DSC analysis of the nanodrug group, the characteristic absorption peak of the main drug (COSM) disappeared, indicating that COSM was present in an amorphous form in the nanodrug group and was no longer present in a crystalline state. These observations indicate that COSM was successfully incorporated into the mesoporous channels of MSN-NH 2 -GA. According to the previous experiments, the feasibility of using 3,5-dinitrosalicylic acid (DNS) as a method for the determination of COSM content was determined, and the specific determination conditions were finally optimized and screened out [45,46]. In the drug loading experiment, the dosage ratio of COSM and MSN-NH2-GA is 1:2, and the drug loading time is 12 h, which is the best drug loading condition. The encapsulation efficiency (EE%) was 28.36% and the load capacity (LC%) was 56.72%.  According to the previous experiments, the feasibility of using 3,5-dinitrosalicylic acid (DNS) as a method for the determination of COSM content was determined, and the specific determination conditions were finally optimized and screened out [45,46]. In the drug loading experiment, the dosage ratio of COSM and MSN-NH2-GA is 1:2, and the drug loading time is 12 h, which is the best drug loading condition. The encapsulation efficiency (EE%) was 28.36% and the load capacity (LC%) was 56.72%.

In Vitro Biological Evaluation
LO2 was cultivated, 8000-10,000 cells per well in a 96-well plate were seeded, the cell state with a microscope was observed after about 10-12 h of culture; APAP modelling groups were set at 0, 2, 4, 6, 8, 10, 12, 14, 16 mM. APAP was given to each group according to the preset setting, and the culture was continued for 3, 6, 12, and 24 h; the cell survival rate was measured by CCK-8 method, and the optimal concentration and time for modelling were determined. According to the results of nanomedicine cytotoxicity, the dosage of COSM@MSN-NH 2 -GA group was low dose (200 µg/mL), medium dose (400 µg/mL), high dose (800 µg/mL); in total, there was a group of six duplicate holes. The drug loading of COSM@MSN-NH2-GA is 28.36% ± 1.00%. By equivalent conversion, the dosage of the free drug COSM was low dose (56 µg/mL), medium dose (113 µg/mL), high dose (226 µg/mL); in total, eight duplicate wells were in each group, and they continued to culture for 12 h after adding the COSM drug. The experiment and results of this part are shown in the annex.
LO2 hepatocytes were treated with APAP for 12 h and then treated with COSM, MSN-NH 2 -GA, and COSM@MSN-NH 2 -GA for 12 h. Then, the growth state of the cells were observed under the microscope. As shown in Figure 6 proved that the nanoparticles were a safe and non-toxic nanocarrier. In the free drug group, the cell state of the COSM (L) group was close to that of the APAP model group, the normal hepatocytes in the COSM (M) and COSM (H) groups increased, the cell morphology was more normal, and the number of dead cells decreased. Each group treated with the nanodrug showed a decrease in the number of dead cells, but the middle-dose group and the high-dose group displayed the most pronounced effects of cell treatment due to the more normalized cell morphology and lower number of dead cells in these groups. The model group generally showed a substantially higher number of dead cells and significantly fewer normal liver cells than the normal control group. In addition, the appearance of many dead cells changed, displaying abnormal forms and decreased cell activity.   The contents of ALT and AST in the medium were determined by collecting the culture medium, and the therapeutic effect of each administration group on APAP-induced LO2 hepatocyte injury was detected by CCK-8 method. As shown in Table 1, COSM@MSN-NH 2 -GA (M) and COSM@MSN-NH 2 -GA (H) treatment groups significantly increased hepatocyte survival and inhibited hepatocyte injury. In addition, compared with the APAP model group, the nanomedicine treatment could significantly reduce the contents of ALT and AST in the culture medium, as shown in Figure 7. In the high-dose group, compared to the free COSM, the nano-drug COSM@MSN-NH 2 -GA showed a more significant decrease in the indexes of ALT and AST. It can be speculated that the glycyrrhetinic acid receptor (GAR), as the most commonly used targeting effect, is overexpressed in hepatocytes [47,48]. MSN-NH 2 -GA uses a receptor-mediated strategy to improve delivery efficiency and achieve better therapeutic effect. Taken together, the results indicated that COSM@MSN-NH 2 -GA could treat APAP-induced hepatocyte injury. Therefore, the combined use of COSM and MSN-NH 2 -GA can improve the vitality of hepatocytes and provide great hope for the treatment of APAP-induced hepatocyte injury.    In this experiment, fluorescence microscopy was used to observe the cellular uptake behaviour of nanoparticles. As shown in Figure 8, at 5 min, no fluorescence could be observed in the C 6 -NP group, but blue nuclei stained with DAPI could be clearly observed. After 1 h, fluorescence was observed in the cytoplasm of the cells. The fluorescence intensity of the C 6 -NP group was significantly enhanced, indicating that the targeted nanoparticles showed higher cell uptake ability. At 2 h, the fluorescence intensity of the C 6 -NP groups confirmed an increasing trend. In the C 6 -NP group, the Merge diagram showed mixed blue and green light, and the cytoplasm and nucleus of the cells exhibited much fluorescence. This result may be due to the above-mentioned specific GA-receptor-mediated endocytosis mechanism, and a large number of C6-NPs nanoparticles are internalized by LO2 cells [29,30].
In this experiment, flow cytometry was performed to analyse the cell uptake behaviour of nanoparticles (Figure 9). At 5 min, the fluorescence intensity of the free coumarin group (938.6 ± 115.7) was not considerably longer than that of the C 6 -NP group (923.8 ± 27.4). At 1 h, the cell fluorescence intensity of the nanoparticle group was maintained at a high level (11378.07 ± 2692.05), which was appreciably different from that of the free drug group (3082.83 ± 220.94). With increases in the reaction time, the fluorescence intensity of the nanoparticle group reached 12991.77 ± 2303.26 at 2 h, whereas the fluorescence intensity of the free drug group was 4746. 3 ± 1990.77. This finding shows that compared with free drugs, targeted modified nanoparticles exhibit a stronger drug transport ability and are more easily taken up by cells. 27.4). At 1 h, the cell fluorescence intensity of the nanoparticle group was maintained at a high level (11378.07 ± 2692.05), which was appreciably different from that of the free drug group (3082.83 ± 220.94). With increases in the reaction time, the fluorescence intensity of the nanoparticle group reached 12991.77 ± 2303.26 at 2 h, whereas the fluorescence intensity of the free drug group was 4746. 3 ± 1990.77. This finding shows that compared with free drugs, targeted modified nanoparticles exhibit a stronger drug transport ability and are more easily taken up by cells. Overall, the uptake of glycyrrhetinic-acid-modified nanomedicines by cells was better. The results of fluorescence microscopy and flow cytometry showed that the glycyrrhetinic-acid-modified nanoparticles exhibited a higher fluorescence intensity than that of the free C6 group at the same time and showed stronger fluorescence intensity faster, indicating that the treatment can significantly increase the uptake of nanomedicines by LO2 cells.

Synthesis of MSN-NH2-GA Nanoparticles
The following substances were purchased from industrial suppliers and used as received. Triethanolamine (TEA), N-hydroxysuccinimide (NHS), dicyclohexylcarbodiimide (DCC), glycyrrhetinic acid (GA), dimethyl sulfoxide (DMSO), and diethyl ether were al biochemically obtained from MACKLIN Technology Co., Ltd. (Shanghai, China). Cyclohexane, absolute ethanol, and methanol were all provided by Tianjin Damao Reagent Factory (Tianjin, China). Cetyltrimethylammonium chloride (CTAC), tetraethyl orthosilicate (TEOS), 3-aminopropyltriethoxysilane (APTES), and 1-octadecene (ODE) were purchased from Sigma-Aldrich Trading Co., Ltd. (Shanghai, China). Unless otherwise indicated, al Overall, the uptake of glycyrrhetinic-acid-modified nanomedicines by cells was better. The results of fluorescence microscopy and flow cytometry showed that the glycyrrhetinicacid-modified nanoparticles exhibited a higher fluorescence intensity than that of the free C 6 group at the same time and showed stronger fluorescence intensity faster, indicating that the treatment can significantly increase the uptake of nanomedicines by LO2 cells.

Synthesis of MSN-NH 2 -GA Nanoparticles
The following substances were purchased from industrial suppliers and used as received. Triethanolamine (

Preparation Characterization
FTIR spectra were obtained using an FTIR spectrophotometer (VERTEX 70v, Bruker GmbH, Bremen, Germany) to determine the profitable synthesis of MSN-NH 2 and MSN-GA. The dimension distribution and zeta potential of the pattern nanoparticles were explored using a laser particle dimension analyser (Delsa, Beckman Technology Co., Ltd., Durahm, NC, USA). The morphologies of MSN and MSN-NH 2 -GA were observed by TEM (Tecnai G2 F20, Thermo Fisher Scientific, Waltham, MA, USA) and scanning electron microscopy (SEM) (XFlash 6130, Carl Zeiss, Oberkochen, Germany). The unique structures and pore dimension distribution traits of MSN and MSN-NH 2 -GA were determined by nitrogen adsorption (ASAP2460, American Mack Instruments Co., Ltd., Colonial Heights, VA, USA).

Encapsulation of COSM in MSN-NH 2 -GA (COSM@MSN-NH 2 -GA)
Chitosan oligosaccharide (COSM) was purchased from Shandong Aokang Biotechnology Co., Ltd., with batch number of 200409C, degree of deacetylation (DD) of 90.2%, and molecular weight of 1000 Da. To study the loading ability of COSM on the prepared nanoparticles, 10 mg of nanocarrier MSN-NH 2 -GA was placed into 10 mL of ethanol solution at room temperature and ultrasonically dispersed for approximately 10 min. Then, 10 mg of COSM was added and stirred slowly on a magnetic stirrer for 12 h. Finally, a highspeed centrifuge was used for centrifugation to collect the lower drug-loaded nanoparticles, which were freeze-dried for storage. Differential scanning calorimetry (DSC) curves were obtained using a synchronous thermal analyser (STA449, Netzsch, Selb, Germany) with a temperature range of 20 • C to 300 • C and a heating rate of 10 • C/min. The determination method of COSM content was established by DNS method, and the absorbance of COSM was determined by multifunctional enzyme-labeled instrument (MAXM4, Meigu Molecular Instruments Co., Ltd., Shanghai, China), and the standard curve of COSM was drawn ( Figure S3). The amounts of COSM in the nanoparticles were measured.
The encapsulation efficiency (EE%) of COSM in the nanoparticles was calculated using the following formula: The cell line was purchased from the Cell Bank of the Chinese Academy of Sciences and was cryopreserved at the Institute of Traditional Chinese Medicine, Guangdong Pharmaceutical University, with the human foetal hepatocyte LO2 mobile line. The cells were cultured in RPMI-1640 medium containing 10% foetal bovine serum and 1% FBS in a humidified incubator with a 5% carbon dioxide atmosphere. This protocol was reviewed and approved by the Institutional Review Board of Guangdong Pharmaceutical University.
First, LO2 cells were cultured and observed by microscope. Then, according to the previous experimental results (see attachment: Figure S2, Tables S1 and S2), the administration components were divided into high, medium, and low (H, M, L) COSM, (H, M, L) MSN-NH 2 -GA nanoparticles and (H, M, L) COSM@MSN-NH 2 -GA nanomedicine, with 8 replicate wells in each group. APAP was added at the modelling concentration for 12 h, the model group was treated with APAP only, the clean group was treated with an identical amount of medium, and the experimental group was treated with free drug COSM, nanoparticles MSN-NH 2 -GA, and the nanodrug COSM@MSN-NH 2 -GA and cultured for 12 h.
The cytopathological state was observed to evaluate the therapeutic effect. In this study, the optimal concentration and time of APAP for modeling were screened (see attachment: Figure S4), and the cell viability was measured by CCK-8 method as the evaluation index. First, the cell culture medium was collected and centrifuged, and the contents of AST (C010-3-1, Nanjing Jiancheng Biological Co., Ltd., Nanjing, China) and ALT (C009-3-1, Nanjing Jiancheng Biological Co., Ltd., Nanjing, China) were measured according to the kit instructions. The survival state of adherent cells was detected by the CCK-8 method.
3.5. In Vitro Cellular Uptake 3.5.1. Fluorescence Microscopy (CLSM) Coumarin-6 (C 6 ) is a liposoluble dye with strong fluorescence. It is commonly used in cellular uptake studies with nanoformulations [49,50]. LO2 hepatocytes with cell viability meeting the experimental requirements were inoculated into a 24-well plate and incubated for more than 12 h until 80% of the cells adhered to the wall. The C 6 solution and C 6 -NP nanosolution were diluted with serum-free medium so that both groups of C 6 concentrations were 800 ng/mL and were washed 3 times with PBS. After culturing for 30 min, 1 h, and 2 h, the original medium was discarded, subjected to three 5 min washes with PBS, incubated with 4% paraformaldehyde for 15 min, and washed 4 times with PBS after fixation. In a dark environment, the anti-fluorescence-quenching suspension-containing DAPI was dropped on the glass slide, and then the cell slide was placed upside down on the glass slide to complete the suspension. A fluorescence microscope was used for observation and analysis.

Flow Cytometry (FCM)
LO2 cells were seeded in a 6-well plate at 20 w cells/well and incubated for more than 12 h, and cell adherence was observed. When more than 80% of the cells adhered, the coumarin solution and coumarin-labelled C 6 -NPs were diluted with minimal medium so that the fluorescein concentration was 800 ng/mL. Time gradients were set as 5 min, 1 h, and 2 h. After incubation for corresponding time in each group, cells were collected by centrifugation. The cells were resuspended with 300 µL PBS and detected by flow cytometry.

Conclusions
In this study, a multifunctional drug delivery carrier based on glycyrrhetinic acid embedded in silica nanoparticles was successfully synthesized. Not only does MSN-NH 2 -GA show satisfactory loading ability, but also it enhances its biocompatibility. The successful synthesis of MSN-NH 2 -GA was verified by FTIR, SEM and zeta potential measurement. In vitro studies show that this kind of nontoxic nanoparticles can significantly enhance the uptake of cells. The COSM drug has a protective effect on liver cell injury induced by APAP. In particular, the delivery of COSM through MSN-NH 2 -GA can greatly improve the therapeutic effect on LO2 cells. In summary, COSM@MSN-NH 2 -GA is a non-toxic, stable and efficient nano-therapeutic drug for acute liver injury. The results of this study provide a potential nanodelivery platform for the targeted therapy of acute liver injury.
Supplementary Materials: The following supporting information can be downloaded at: https://www.mdpi.com/article/10.3390/molecules28104147/s1, Figure S1: The synthetic route of MSN-NH 2 (A), the synthetic route of GA-NHS (B) and the synthetic route of MSN-NH 2 -GA (C); Figure S2: Effect of different MSN and MSN-NH 2 -GA concentrations on cell viability rate; Figure S3: Standard curve of GluNH 2 with glucosamine as standard; Figure S4: Effect of different modeling concentrations (APAP) and time on cell viability rate (A) and IC 50 curve (B); Table S1: Investigation of different drug/carrier ratio; Table S2: Investigation of different drug/carrier ratio.