# Construction and Performance Research of Reinforced Iron-Based Powder Metallurgy Materials Based on Phyllanthin as Drug Transport Carriers

Authors: Xuehua Feng; Ali Tao; Zurong Song
Journal: Advances in Materials Science and Engineering
 (2022)

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## Abstract

Iron-based powder metallurgy materials are the largest type of powder metallurgy materials, mainly used in structural parts, bearings, and friction materials. Iron-based powder metallurgy materials have a series of advantages such as low cost, good machinability, good weldability, and heat treatment. In recent years, the enhanced iron-based powder metallurgy materials based on lavender elements have become a hot spot in the development of material transportation carriers. In order to study the effects of different hot pressing and sintering temperatures on the density, microstructure, and hardness of the enhanced iron-based powders of caladium, we conducted related studies on the structure core properties of the enhanced iron-based powders of caladium to explore whether it can be used as a drug transport carrier. The research results show that hot pressing sintering can make the powder achieve high densification at lower temperature and shorter cycle, especially in the preparation of difficult-to-form and sintered powder metallurgy materials with unique advantages.


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## Body

## 1. Introduction

Nano-drug carrier refers to a new type of carrier with a particle size of 10–1000 mm, which is usually made of natural or synthetic polymer materials. The advantages of this drug are to improve the absorption and stability of the drug, improve the drug properties and targeting, prolong the drug action time, increase the curative effect, and reduce the side effects. At present, this drug has been preliminarily used in experiments and clinical trials of tumors, diabetes, and vascular diseases, and good results have been achieved. Iron-based powder metallurgy materials are the largest type of powder metallurgy materials, mainly used in structural parts, bearings, and friction materials. Iron-based powder metallurgy materials have a series of advantages such as low cost, good machinability, good weldability, and heat treatment. In recent years, the enhanced iron-based powders of celites have become a hot spot in the research and development of iron-based powder metallurgy materials due to their excellent strength, toughness, hardness, and wear resistance. The particle-reinforced iron-based powder metallurgy material can combine the high hardness and high wear resistance of the reinforcement with the high strength and excellent toughness of the matrix, so it is suitable for use in environments with harsh service conditions (such as high temperature and poor lubricity) It is a relatively ideal new material with great development potential. However, there are relatively few researches on particle-reinforced iron-based powder metallurgy materials, especially the research on the addition of particle-reinforced high-chromium iron-based powder metallurgy materials.In this paper, the construction and properties of phyllanthin as a drug transport carrier using iron-based powder metallurgy reinforcing material were analyzed. The dgnps BTZ nano-drug system was constructed by loading the chemotherapy drug bortezomib on the surface of dopamine nanoparticles by using the catechol group and boric acid to form a reversible boron ester bond. During the experiment, dgnps had the best stability and the least tumor induction, which provided a new idea for drug transport carriers.The nanocarrier, which integrates molecular imaging and therapeutic function, can provide assistance for the customization of treatment scheme and the monitoring of therapeutic effect. At the same time, in addition to utilizing the high permeability and retention effect of nanocarriers, the establishment of active targeting mechanism is an effective way to realize the efficient enrichment of diagnostic and therapeutic reagents in tumor tissues and improve the specificity of treatment. In addition, according to the physiological characteristics of tumor, the establishment of tumor environment responsive chemotherapy drug release mechanism will maximize the therapeutic effect and reduce the toxic and side effects on normal tissues as much as possible.The rapid development of nanotechnology provides new opportunities for molecular imaging diagnosis and targeted therapy of tumors. Shen et al. believe that after cerebral infarction, the regeneration of capillaries plays an important role in recovery. However, the blood-brain barrier (BBB) restricts Rg1 from entering the brain tissue. The transferrin receptor (TfR) is overexpressed in the BBB. They created TfR-targeted nanocarriers (PATRC) to penetrate the BBB to treat cerebral infarction. Although their research is comprehensive, the factors considered are not complete [1]. Sun et al. studied the morphological effects of nano-hydroxyapatite as a drug carrier. They used polyethylene glycol (PEG) as a template to successfully prepare hydroxyapatite/methotrexate (HAp/MTX) hybrids with different forms in situ. They can obtain hybrids with the same phase composition and functional groups in different morphologies (layered, rod-shaped, and spherical) by changing the preparation parameters. They used UV-Vis spectroscopy to identify the drug loading and drug release mechanism of three different hybrids. Although their research has increased the drug load, it lacks a specific experimental program [2]. Agrahari et al. believe that large molecules (proteins/peptides) have the potential to develop new therapies. Due to its specific mechanism of action, large molecules can be administered at lower doses compared with small molecule drugs. They discussed various ways of administration of macromolecules (invasive/noninvasive). They explained the advantages/limitations of the new delivery system and the potential role of nanotechnology in the delivery of macromolecules. Although their research has certain reference value, it lacks experimental data [3].In this paper, the morphology, assembly mechanism, and optical properties of nanoparticles are deeply studied. On this basis, the DGNPs-Btz nanomedicine system was constructed by utilizing the catechol group to form a reversible boronate bond with boronic acid, and placing the chemotherapeutic drug bortezomib on the surface of dopamine-based nanoparticles. The photodynamic activity and drug-responsive release behavior of nano-drug systems were studied, and their anti-tumor effects were evaluated by incubating with tumor cells. The controllable preparation of functional polymer nanoparticles provides a material basis for the development of polymer nanocarriers; the development of new preparation methods and new functional nanocarriers has injected new vitality into nanomedicine delivery. Based on the law of interaction between nanocarriers and biological interfaces, the design and construction of stimulus-responsive and targeting polymer nanocarriers is beneficial to improve the delivery efficiency of nano-drugs.


## 2. Method for Preparing Iron-Based Powder Metallurgy Materials

### 2.1. Preparation of Iron-Based Powder Metallurgy Materials

Particle-reinforced iron-based powder metallurgy materials can combine the high strength, high hardness, wear resistance, and toughness of the matrix and are suitable for use in environments with poor service conditions (such as high use temperature and poor lubricity). This is an ideal new material with great development potential [4]. In this type of material, some strong carbide forming elements, such as chromium, molybdenum, vanadium, and tungsten, are often added to form a large number of carbide strengthening particles in the material structure, which is beneficial to improve the mechanical properties and wear resistance of the material, but at the same time it will also make the material’s pressing performance and sintering performance worse, and it is difficult to densify, thereby reducing the material performance. Gowda et al. highlighted the importance of nanostructure-based drug delivery systems [5]. Serri et al. found that the resulting NPs could be efficiently internalized by mesothelioma cells (MSTO-211H) in the cytoplasmic space, the extent of which was strongly dependent on NP size and polydispersity index, so he further pointed out the importance of NP preparation methods in enhancing their uptake [6]. The infiltration process [5, 6] can effectively improve the density and performance of the material.In this paper, sintering and annealing processes are used to prepare high-strength, high-hardness carbide particle-reinforced iron-based powder metallurgy materials, which are used in the new overhead camshaft structure of high-power engines to directly contact the gap adjustment plate of the cam. The influence of the preparation process parameters on the structure and performance of the material is mainly studied, and the effective way to improve the performance of the material is discussed.


### 2.2. Nano-Drug Carrier

Nanomaterials are characterized by small particle size and stable structure. The state of nanomaterials is divided into thermodynamic equilibrium and non-thermodynamic equilibrium, which depends on the material itself. Among them, ultrahigh polymer compounds belong to thermodynamic equilibrium, while crystals composed of different chemical components have non-thermodynamic equilibrium. Nanomaterials can be divided into ultrafine particles and nanosolid materials, among which nanosolid materials are composed of nanometer ultrafine particles. An ideal smart responsive drug carrier should generally have excellent stability, better biocompatibility, strong smart response ability, high drug loading rate, and easy preparation and storage [7]. High-molecular polymers have attracted wide attention because of their good modifiability, simple preparation and purification operations, and easy mass production, and have been widely developed into intelligent responsive nanocarriers. After this, the smart responsive drug carrier is loaded with drugs, it can not only maintain a stable and long-term drug circulation in body fluids or blood but also enrich it near tumor tissues and adjust the drug release rate through the tumor microenvironment or external stimuli. The smart responsive drug carrier improves the utilization of drugs, thereby improving the efficiency of tumor treatment [8].Compared with traditional drug delivery carriers, CNTs have the following advantages:(1)
With a hollow tubular structure and a high specific surface area, it can load a large number of small drug molecules and biological macromolecules such as proteins, nucleic acids, and other substances and protect the drugs or molecules from degradation during the loading process. Or the molecules carry out slow and controlled release [9].(2)
It has strong cell transmembrane ability, can smoothly pass through the cell membrane, deliver drugs or molecules to the inside of different types of cells, and can maintain cell functions and exert drug or molecular curative effects at the same time [10].(3)
The surface has strong adsorption activity and easy functionalization. It can be modified in covalent or noncovalent form, and many different functionalized active groups are attached to its surface to make it multifunctional [11].Nano-drug carrier is the application of nanomaterial in medicine. The small size and large specific surface area of nanomaterials make it possess special physical and chemical properties. It can be used in medicine, biological testing, pharmaceutical industry, and national defense. It can be used as a targeted drug delivery body, small molecule positioning body, tissue engineering material, and single cell processing material. When used as a drug delivery body, these substances are encapsulated in nanoparticles through physical or chemical means. Among them, polymer capsules, liposomes, dendrimers, mesoporous silica, and micelles can all be used as drug delivery bodies [12]. With the continuous in-depth research on the carrier, people have made great improvements in its preparation methods and applications. For example, embedding pesticides in microcapsules can achieve uniform and sustained release of pesticides, reduce environmental pollution of pesticides, and prevent pests from appearing too quickly. The drug delivery body exhibits the characteristics of low toxicity and low biological rejection. For example, the use of nanocarriers for drugs with low solubility can improve its compatibilization, while increasing the utilization of the drug, reducing the negative effects of the drug, saving costs, and improving the pharmacokinetic performance and stability in the physiological environment [13].Real-time tracking, detection, and biological imaging of the carrier can be accomplished by introducing fluorescent probes into the drug controlled release carrier. The surface of silica is hydrophilic, so the silica carrier modified with fluorescent markers has good dispersibility in aqueous solution. Moreover, because the particle size of the silica nanospheres is nanometer-sized and has optical transparency, it will not interfere with the fluorescence emission of the fluorescent agent. A variety of drug carrier delivery systems are widely used in the diagnosis and treatment of targeted drugs and cancer, to achieve the delivery of special tumor sites and enhance the efficacy of the pathological area [14]. The choice of nanomedicine carrier materials depends on the type of drug loading, the biocompatibility of the carrier, and the route of administration, including biodegradable or nondegradable polymers. Nanocarriers optimize their size and shape to improve the effective load rate and solubility of drugs. They can be used as nanomedicine carriers and endow them with molecular and cell labeling, tracking, high-sensitivity detection, drug delivery, and medical imaging functions. Because of its highly branched structure, unique monodispersity, and a large number of soluble functional groups on the surface, this type of carrier has a wide range of applications in nanocomposite materials, drug delivery systems, medicine, and other research fields [15].


### 2.3. Targeting Function of Nanoparticles

Nanomaterials have attracted more and more attention in the field of drug release. By encapsulating drugs in nanocarriers, and modifying them to give the carrier targeting and stimulus responsiveness, the targeted release of drugs in tumor tissues can be achieved. The ideal drug carrier should have the characteristics of stable structure, high drug loading rate, good biocompatibility, low drug leakage and early release, and stimulus-responsive drug release [16]. Its expression is as follows:(1)D=RTN0•13πηd=kB3πηd.In the formula,η is the viscosity of the solvent (dispersion medium) and T is the temperature of the dispersion system. For chains composed of spherical particles, the coercive force is(2)Hcn=μ6Kn−4Lnd3,Kn=∑j=1nn−jnj3,Ln=∑j=11/2n−1<j≤1/2n+1n−2j−1n2j−13.In the formula,n is the number of particles in the ball chain, μ is the particle magnetic moment, and d is the particle spacing.Passive targeting is based on the rapid growth of solid tumors, resulting in characteristics such as leaky tumor vasculature and poor lymphatic drainage. It uses the enhanced penetration and retention effects of NDDS to achieve a strategy to promote drug accumulation in tumor tissues. When the nanoparticles reach the tumor tissue through the EPR effect, they first adhere to the tumor cells or bind to the receptors on the surface and mediate endocytosis. Above the CMC value, the micelles maintain a thermodynamically stable state. When diluted to below the CMC, the micelles will decompose into monomers. The decomposition speed mainly depends on the structure of the amphiphilic polymer and the relationship between the polymer chains. However, polymer micelles usually show a low CMC value, which makes them difficult to change the aggregation state after dilution, which can increase the cycle time [17, 18].


## 2.1. Preparation of Iron-Based Powder Metallurgy Materials

Particle-reinforced iron-based powder metallurgy materials can combine the high strength, high hardness, wear resistance, and toughness of the matrix and are suitable for use in environments with poor service conditions (such as high use temperature and poor lubricity). This is an ideal new material with great development potential [4]. In this type of material, some strong carbide forming elements, such as chromium, molybdenum, vanadium, and tungsten, are often added to form a large number of carbide strengthening particles in the material structure, which is beneficial to improve the mechanical properties and wear resistance of the material, but at the same time it will also make the material’s pressing performance and sintering performance worse, and it is difficult to densify, thereby reducing the material performance. Gowda et al. highlighted the importance of nanostructure-based drug delivery systems [5]. Serri et al. found that the resulting NPs could be efficiently internalized by mesothelioma cells (MSTO-211H) in the cytoplasmic space, the extent of which was strongly dependent on NP size and polydispersity index, so he further pointed out the importance of NP preparation methods in enhancing their uptake [6]. The infiltration process [5, 6] can effectively improve the density and performance of the material.In this paper, sintering and annealing processes are used to prepare high-strength, high-hardness carbide particle-reinforced iron-based powder metallurgy materials, which are used in the new overhead camshaft structure of high-power engines to directly contact the gap adjustment plate of the cam. The influence of the preparation process parameters on the structure and performance of the material is mainly studied, and the effective way to improve the performance of the material is discussed.


## 2.2. Nano-Drug Carrier

Nanomaterials are characterized by small particle size and stable structure. The state of nanomaterials is divided into thermodynamic equilibrium and non-thermodynamic equilibrium, which depends on the material itself. Among them, ultrahigh polymer compounds belong to thermodynamic equilibrium, while crystals composed of different chemical components have non-thermodynamic equilibrium. Nanomaterials can be divided into ultrafine particles and nanosolid materials, among which nanosolid materials are composed of nanometer ultrafine particles. An ideal smart responsive drug carrier should generally have excellent stability, better biocompatibility, strong smart response ability, high drug loading rate, and easy preparation and storage [7]. High-molecular polymers have attracted wide attention because of their good modifiability, simple preparation and purification operations, and easy mass production, and have been widely developed into intelligent responsive nanocarriers. After this, the smart responsive drug carrier is loaded with drugs, it can not only maintain a stable and long-term drug circulation in body fluids or blood but also enrich it near tumor tissues and adjust the drug release rate through the tumor microenvironment or external stimuli. The smart responsive drug carrier improves the utilization of drugs, thereby improving the efficiency of tumor treatment [8].Compared with traditional drug delivery carriers, CNTs have the following advantages:(1)
With a hollow tubular structure and a high specific surface area, it can load a large number of small drug molecules and biological macromolecules such as proteins, nucleic acids, and other substances and protect the drugs or molecules from degradation during the loading process. Or the molecules carry out slow and controlled release [9].(2)
It has strong cell transmembrane ability, can smoothly pass through the cell membrane, deliver drugs or molecules to the inside of different types of cells, and can maintain cell functions and exert drug or molecular curative effects at the same time [10].(3)
The surface has strong adsorption activity and easy functionalization. It can be modified in covalent or noncovalent form, and many different functionalized active groups are attached to its surface to make it multifunctional [11].Nano-drug carrier is the application of nanomaterial in medicine. The small size and large specific surface area of nanomaterials make it possess special physical and chemical properties. It can be used in medicine, biological testing, pharmaceutical industry, and national defense. It can be used as a targeted drug delivery body, small molecule positioning body, tissue engineering material, and single cell processing material. When used as a drug delivery body, these substances are encapsulated in nanoparticles through physical or chemical means. Among them, polymer capsules, liposomes, dendrimers, mesoporous silica, and micelles can all be used as drug delivery bodies [12]. With the continuous in-depth research on the carrier, people have made great improvements in its preparation methods and applications. For example, embedding pesticides in microcapsules can achieve uniform and sustained release of pesticides, reduce environmental pollution of pesticides, and prevent pests from appearing too quickly. The drug delivery body exhibits the characteristics of low toxicity and low biological rejection. For example, the use of nanocarriers for drugs with low solubility can improve its compatibilization, while increasing the utilization of the drug, reducing the negative effects of the drug, saving costs, and improving the pharmacokinetic performance and stability in the physiological environment [13].Real-time tracking, detection, and biological imaging of the carrier can be accomplished by introducing fluorescent probes into the drug controlled release carrier. The surface of silica is hydrophilic, so the silica carrier modified with fluorescent markers has good dispersibility in aqueous solution. Moreover, because the particle size of the silica nanospheres is nanometer-sized and has optical transparency, it will not interfere with the fluorescence emission of the fluorescent agent. A variety of drug carrier delivery systems are widely used in the diagnosis and treatment of targeted drugs and cancer, to achieve the delivery of special tumor sites and enhance the efficacy of the pathological area [14]. The choice of nanomedicine carrier materials depends on the type of drug loading, the biocompatibility of the carrier, and the route of administration, including biodegradable or nondegradable polymers. Nanocarriers optimize their size and shape to improve the effective load rate and solubility of drugs. They can be used as nanomedicine carriers and endow them with molecular and cell labeling, tracking, high-sensitivity detection, drug delivery, and medical imaging functions. Because of its highly branched structure, unique monodispersity, and a large number of soluble functional groups on the surface, this type of carrier has a wide range of applications in nanocomposite materials, drug delivery systems, medicine, and other research fields [15].


## 2.3. Targeting Function of Nanoparticles

Nanomaterials have attracted more and more attention in the field of drug release. By encapsulating drugs in nanocarriers, and modifying them to give the carrier targeting and stimulus responsiveness, the targeted release of drugs in tumor tissues can be achieved. The ideal drug carrier should have the characteristics of stable structure, high drug loading rate, good biocompatibility, low drug leakage and early release, and stimulus-responsive drug release [16]. Its expression is as follows:(1)D=RTN0•13πηd=kB3πηd.In the formula,η is the viscosity of the solvent (dispersion medium) and T is the temperature of the dispersion system. For chains composed of spherical particles, the coercive force is(2)Hcn=μ6Kn−4Lnd3,Kn=∑j=1nn−jnj3,Ln=∑j=11/2n−1<j≤1/2n+1n−2j−1n2j−13.In the formula,n is the number of particles in the ball chain, μ is the particle magnetic moment, and d is the particle spacing.Passive targeting is based on the rapid growth of solid tumors, resulting in characteristics such as leaky tumor vasculature and poor lymphatic drainage. It uses the enhanced penetration and retention effects of NDDS to achieve a strategy to promote drug accumulation in tumor tissues. When the nanoparticles reach the tumor tissue through the EPR effect, they first adhere to the tumor cells or bind to the receptors on the surface and mediate endocytosis. Above the CMC value, the micelles maintain a thermodynamically stable state. When diluted to below the CMC, the micelles will decompose into monomers. The decomposition speed mainly depends on the structure of the amphiphilic polymer and the relationship between the polymer chains. However, polymer micelles usually show a low CMC value, which makes them difficult to change the aggregation state after dilution, which can increase the cycle time [17, 18].


## 3. Nano-Drug Carrier Construction

### 3.1. Equipment and Reagents

The main instruments used in the experiment are rotary evaporator, freeze dryer, vacuum drying oven, magnetic stirrer, water bath constant temperature oscillator, wide-angle laser light scattering instrument, centrifuge, transmission electron microscope, superconducting nuclear magnetic resonance (NMR), etc. [19].The main reagents used in the experiment are lavender, cetyltrimethoxyammonium bromide, citric acid, ethyl orthosilicate (TEOS), aminopropyltrimethoxysilane (APTES), doxorubicin (Dox), oxidized glutathione (GSSG), reduced glutathione (GSH), hyaluronic acid (HA), hyaluronidase (Hyal-1), N-hydroxysuccinimide (NHS), etc. All the above reagents are used directly [20].


### 3.2. Extraction and Separation of Phylocene

The extraction method was alcohol extraction. The gold powder was extracted with petroleum ether 3 times, 24 hours each time. The petroleum ether extract was obtained after concentration. Euphorbia tomentosa was extracted with 95% industrial ethanol 3 times, 24 hours each time. After three times of ethanol filtrate combination, the extract solution was concentrated to extract form under reduced pressure to obtain ethanol extract. After adding proper amount of water, the ethanol extract was extracted with equal amount of ethyl acetate and n-butanol 3-4 times. The petroleum ether extract was extracted with 80% ethanol to obtain 80% ethanol extract. The ethanol extract was 111.19 g, the ethyl acetate fraction was 18.18 g, and the n-butanol part was 24.83 g [21].


### 3.3. Preparation of Nanoparticles

HCPT nanoparticles (MPEG DGN/hcptnps) were prepared by precipitation method. 20 mgmpeg-dgn coupling compound was dissolved in 3.5 mlpbs buffer solution, and 10 mg HCPT was dissolved in 0.5 ml anhydrous dimethyl sulfoxide DMSO solvent. The DMSO dissolved in the drug was dropwise into the precursor drug aqueous solution under intense stirring. After continuous stirring at 25°C for 20 min, the mixture was transferred to the dialysis bag of mwco3500 after 10 min of ultrasound and then dialyzed with PBS buffer solution (100 ml). The dialysate was changed every 3 h. MPEG DGN/hcptnps were obtained after 3 days of dialysis [22].


### 3.4. Spectral Performance Detection

(1)
Absorption spectrum measurement: Set the scanning wavelength range to 400–900 nm, the scanning interval is 1 nm, and perform baseline scanning with the solvent of the above solution respectively, and then scan the sample, read the absorption wavelength and absorbance value, and save the scan data.(2)
Measurement of emission spectrum: Set the excitation light source to xenon lamp and the detector to NIRRMI. The excitation and emission slits are both 5 nm, the excitation wavelength is the maximum absorption wavelength, and the scanning wavelength range is set to (Ex + 20) − 1200 nm. Put the working solution into the sample cell to scan, read the emission wavelength and fluorescence intensity, and save the scan data [23].


### 3.5. Determination of Drug Loading Efficiency

The drug loading efficiency (DLE) of HCPT was analyzed by VYDAC214TP54 column high performance liquid chromatography (Agilent1200). When determining the drug loading, HCPT was dissolved in 50 mL of acetonitrile and diluted to 5 different concentrations. The mobile phase is acetonitrile/water solution (28/72,v/v), and the flow rate is 1.0 mL/min. The column temperature was 25°C, and the absorbance of HCPT was measured at 266 nm. The standard curve of HCPT was obtained. The pretreatment of mPEG-DGN/HCPTNPs is the same as that of pure HCPT. Dissolve 1 mg of mPEG-DGN/HCPTNPs in 1 mL of acetonitrile, take 20 μL of the sample, and inject it into a high performance liquid chromatograph for detection, and the obtained spectrum is calculated according to the standard curve to calculate the corresponding drug loading quality [24, 25].


### 3.6. In Vitro Cytotoxicity Test

Inoculate HepG2 and COS7 cells in a 96-well plate. After the cell growth is stable, discard the original medium, and add medium containing different concentrations of free DOX and DOX@MSN-ss-CD/mPEG (DOX concentration is 0.100, 0.500, 1.00, 2.00, and 4.00μg/mL), and set up 6 samples with different concentrations. After 48 h of culture, the survival rate of the cells was measured by MTT method, and the untreated cells were used as blank control. Among them, the ultraviolet radiation group was incubated with DOX@MSN-ss-CD/mPEG for 5 minutes and then subjected to ultraviolet radiation for 5 minutes, and then placed in dark conditions, and only the cells subjected to ultraviolet radiation were used as a blank control [26].


### 3.7. Drug Loading and Release

The antitumor drug DOX can be loaded into the nano-drug through electrostatic adsorption with the negatively charged PAA layer. By thoroughly mixing DOX with the aqueous solution of UCNPs@PAA-b-PEG and stirring for 24 hours at room temperature, the material can be adsorbed on DOX. After the completion of the culture, the supernatant of the mixed solution was collected for the characterization of DOX carrying efficiency. In order to detect the release of DOX, the DOX-UCNPs@PAA-b-PEG sample was immersed in phosphate buffer (pH = 7.4 and 5.0) and shaken at 37°C for a certain period of time. Then, the supernatant of the buffer solution was collected, and the amount of DOX in the solution was tested and recorded by absorption spectrum [27].Five microliters of PBS solution (pH = 7.4) containing 5 mg of sample psio2 GSSG CdS/HA was injected into the treated dialysis bag. The dialysis bag was immersed in the release solution under the above different conditions in turn and was shaken in a shaker at 36.8°C. After each fixed time interval, 2 ml of the release medium was taken out, and its absorbance was measured at 480 nm. The same amount of fresh release liquid was added in time to keep the total volume of the release solution constant. The release experiment of each group was performed three times in parallel.


### 3.8. Analysis of Particle Size and Zeta Potential

The particle size of CNTs is related to the distribution of nano-layers and the stability of nanostructures and the encapsulation rate of drug-loading, which is an absolute factor affecting the dispersibility of CNTs. In addition, it also determines the drug release rate of CNTs into the tissue and the bioavailability of the absorbed part. Therefore, controlling the particle size of CNTs helps to improve the uniformity of CNTs dispersion and nuclear biocompatibility. Zeta potential is to investigate the potential difference between the CNTs solution and the dispersion medium, and its charge determines its physical stability. Take a small amount of dry powder of SWCNTs, SWCNTs-COOH, SWCNTs-PEG, SWCNTs-PEG/PEI, SWCNTs-PEG/PEI-FA, and SWCNTs-PEG/PEI-FA-CS , dissolve them in ultrapure water, and dilute to a certain amount and place it on an Nano-S9 laser particle size analyzer and Nano-ZSP laser potentiometer to analyze its particle size and zeta potential [28].


## 3.1. Equipment and Reagents

The main instruments used in the experiment are rotary evaporator, freeze dryer, vacuum drying oven, magnetic stirrer, water bath constant temperature oscillator, wide-angle laser light scattering instrument, centrifuge, transmission electron microscope, superconducting nuclear magnetic resonance (NMR), etc. [19].The main reagents used in the experiment are lavender, cetyltrimethoxyammonium bromide, citric acid, ethyl orthosilicate (TEOS), aminopropyltrimethoxysilane (APTES), doxorubicin (Dox), oxidized glutathione (GSSG), reduced glutathione (GSH), hyaluronic acid (HA), hyaluronidase (Hyal-1), N-hydroxysuccinimide (NHS), etc. All the above reagents are used directly [20].


## 3.2. Extraction and Separation of Phylocene

The extraction method was alcohol extraction. The gold powder was extracted with petroleum ether 3 times, 24 hours each time. The petroleum ether extract was obtained after concentration. Euphorbia tomentosa was extracted with 95% industrial ethanol 3 times, 24 hours each time. After three times of ethanol filtrate combination, the extract solution was concentrated to extract form under reduced pressure to obtain ethanol extract. After adding proper amount of water, the ethanol extract was extracted with equal amount of ethyl acetate and n-butanol 3-4 times. The petroleum ether extract was extracted with 80% ethanol to obtain 80% ethanol extract. The ethanol extract was 111.19 g, the ethyl acetate fraction was 18.18 g, and the n-butanol part was 24.83 g [21].


## 3.3. Preparation of Nanoparticles

HCPT nanoparticles (MPEG DGN/hcptnps) were prepared by precipitation method. 20 mgmpeg-dgn coupling compound was dissolved in 3.5 mlpbs buffer solution, and 10 mg HCPT was dissolved in 0.5 ml anhydrous dimethyl sulfoxide DMSO solvent. The DMSO dissolved in the drug was dropwise into the precursor drug aqueous solution under intense stirring. After continuous stirring at 25°C for 20 min, the mixture was transferred to the dialysis bag of mwco3500 after 10 min of ultrasound and then dialyzed with PBS buffer solution (100 ml). The dialysate was changed every 3 h. MPEG DGN/hcptnps were obtained after 3 days of dialysis [22].


## 3.4. Spectral Performance Detection

(1)
Absorption spectrum measurement: Set the scanning wavelength range to 400–900 nm, the scanning interval is 1 nm, and perform baseline scanning with the solvent of the above solution respectively, and then scan the sample, read the absorption wavelength and absorbance value, and save the scan data.(2)
Measurement of emission spectrum: Set the excitation light source to xenon lamp and the detector to NIRRMI. The excitation and emission slits are both 5 nm, the excitation wavelength is the maximum absorption wavelength, and the scanning wavelength range is set to (Ex + 20) − 1200 nm. Put the working solution into the sample cell to scan, read the emission wavelength and fluorescence intensity, and save the scan data [23].


## 3.5. Determination of Drug Loading Efficiency

The drug loading efficiency (DLE) of HCPT was analyzed by VYDAC214TP54 column high performance liquid chromatography (Agilent1200). When determining the drug loading, HCPT was dissolved in 50 mL of acetonitrile and diluted to 5 different concentrations. The mobile phase is acetonitrile/water solution (28/72,v/v), and the flow rate is 1.0 mL/min. The column temperature was 25°C, and the absorbance of HCPT was measured at 266 nm. The standard curve of HCPT was obtained. The pretreatment of mPEG-DGN/HCPTNPs is the same as that of pure HCPT. Dissolve 1 mg of mPEG-DGN/HCPTNPs in 1 mL of acetonitrile, take 20 μL of the sample, and inject it into a high performance liquid chromatograph for detection, and the obtained spectrum is calculated according to the standard curve to calculate the corresponding drug loading quality [24, 25].


## 3.6. In Vitro Cytotoxicity Test

Inoculate HepG2 and COS7 cells in a 96-well plate. After the cell growth is stable, discard the original medium, and add medium containing different concentrations of free DOX and DOX@MSN-ss-CD/mPEG (DOX concentration is 0.100, 0.500, 1.00, 2.00, and 4.00μg/mL), and set up 6 samples with different concentrations. After 48 h of culture, the survival rate of the cells was measured by MTT method, and the untreated cells were used as blank control. Among them, the ultraviolet radiation group was incubated with DOX@MSN-ss-CD/mPEG for 5 minutes and then subjected to ultraviolet radiation for 5 minutes, and then placed in dark conditions, and only the cells subjected to ultraviolet radiation were used as a blank control [26].


## 3.7. Drug Loading and Release

The antitumor drug DOX can be loaded into the nano-drug through electrostatic adsorption with the negatively charged PAA layer. By thoroughly mixing DOX with the aqueous solution of UCNPs@PAA-b-PEG and stirring for 24 hours at room temperature, the material can be adsorbed on DOX. After the completion of the culture, the supernatant of the mixed solution was collected for the characterization of DOX carrying efficiency. In order to detect the release of DOX, the DOX-UCNPs@PAA-b-PEG sample was immersed in phosphate buffer (pH = 7.4 and 5.0) and shaken at 37°C for a certain period of time. Then, the supernatant of the buffer solution was collected, and the amount of DOX in the solution was tested and recorded by absorption spectrum [27].Five microliters of PBS solution (pH = 7.4) containing 5 mg of sample psio2 GSSG CdS/HA was injected into the treated dialysis bag. The dialysis bag was immersed in the release solution under the above different conditions in turn and was shaken in a shaker at 36.8°C. After each fixed time interval, 2 ml of the release medium was taken out, and its absorbance was measured at 480 nm. The same amount of fresh release liquid was added in time to keep the total volume of the release solution constant. The release experiment of each group was performed three times in parallel.


## 3.8. Analysis of Particle Size and Zeta Potential

The particle size of CNTs is related to the distribution of nano-layers and the stability of nanostructures and the encapsulation rate of drug-loading, which is an absolute factor affecting the dispersibility of CNTs. In addition, it also determines the drug release rate of CNTs into the tissue and the bioavailability of the absorbed part. Therefore, controlling the particle size of CNTs helps to improve the uniformity of CNTs dispersion and nuclear biocompatibility. Zeta potential is to investigate the potential difference between the CNTs solution and the dispersion medium, and its charge determines its physical stability. Take a small amount of dry powder of SWCNTs, SWCNTs-COOH, SWCNTs-PEG, SWCNTs-PEG/PEI, SWCNTs-PEG/PEI-FA, and SWCNTs-PEG/PEI-FA-CS , dissolve them in ultrapure water, and dilute to a certain amount and place it on an Nano-S9 laser particle size analyzer and Nano-ZSP laser potentiometer to analyze its particle size and zeta potential [28].


## 4. Construction Results of Nano-Drug Carrier

The main methods to prepare nanoparticles are emulsion polymerization, natural polymer polymerization, molecular self-assembly, etc. In this paper, a small amount of soluble metal salts are impregnated into semiconductor powder by analyzing the doping of transition metal particles in the self-assembly method and then baked. Proper doping of transition metal ions can introduce lattice defects into semiconductor crystals to form more photocatalytic active sites, but excessive doping will increase the number of carrier recombination centers on the surface of the catalyst, reduce the activity, and finally make drug nanoparticles.


### 4.1. Analysis of Phylocene

The 24 h cell survival rate of HeLa cells treated with different concentrations ofEuphorbia extract is shown in Table 1 and Figure 1. The logarithmic phase cells on 96 well plate were treated with drug. The OD value was detected by CCK-8 method after 24 hours. The results showed that all of the five fractions inhibited the proliferation of HeLa cells, and it was related to the drug concentration. With the increase of drug concentration, the survival rate of HeLa cells gradually decreased. When the concentration increased to a certain level, all the cells would be killed. The inhibitory effect of QJZ-E3 and QJZ-E4 samples was much greater than that of QJZ-E samples, and the activities of QJZ-E1 and QJZ-E2 samples were not strong, which indicated that the anti-cervical cancer active components of Euphorbia tomentosa were mainly concentrated in the alcohol extracts with higher polarity. It can be seen from the figure that the cell morphology changed significantly before and after administration. After treatment with QJZ-E, QJZ-E3, and QJZ-E4, the cell volume was significantly reduced, the connection between the cells disappeared and isolated from the surrounding cells, and the cells were suspended in the medium with a large number of apoptosis. However, after treatment with QJZ-E1 and QJZ-E2, the coexistence of living cells and dead cells was observed, and the cell survival rate was about 50%.Table 1
Cell survival rate.
Concentration00.511.522.53QJZ-E0.830.710.690.750.860.560.47QJZ-E10.750.660.810.620.590.570.79QJZ-E20.550.640.710.630.880.760.66QJZ-E30.340.250.570.610.710.490.53QJZ-E40.840.750.590.680.490.410.27Figure 1
Cell survival rate.The results of TEM show that the hydrophobicity and aggregate size of the brush increase with the decrease in the number of side chains. With the further increase of hydrophobicity, the morphology of aggregates also changed from micelles to vesicles. The results of SEM are consistent with those of TEM. In addition, the test results of cryo TEM and FF-TEM are larger than those of ordinary TEM and SEM, which is mainly due to the dehydration and shrinkage of aggregates in the drying process of TEM and SEM. When the hydrophilicity of amphiphilic random copolymers is strong and the molecular chain is long, it tends to form single molecular micelles; when the hydrophobicity is increased and the molecular chain is short, it tends to form multi molecular aggregates.


### 4.2. Performance Analysis of Nano-Drug Carrier

The UV-visible absorption spectra of PMSNs, DOX, and PMSNs@DOX are shown in Table2 and Figure 2. Free doxorubicin (DOX) has a strong UV-Vis absorption peak at 480 nm, while PMSNs have no characteristic absorption peak at this wavelength. After DOX is loaded, the absorption of PMSNs@DOX at 480 nm is significantly enhanced, indicating that DOX has been successfully loaded on PMSNs. In addition, the zeta potentials of PMSNs and PMSNs@DOX are -17.41 ± 0.38 mV and −8.08 ± 0.18 mV, respectively. The change of zeta potential also indirectly proves the existence of DOX. At the same time, the UV-Vis absorption spectrum of the nanocomposite obtained after PMSNs@DOX was modified by FA was also measured, and the results showed that there were both the characteristic peak of folic acid at 280 nm and the characteristic peak of DOX at 480 nm, indicating the success of FA modified on the surface of PMSNs@DOX. In addition, the absorption spectrum of CCPEB is just the composite spectrum of PFN and ONB, so there is a large spectral overlap with the emission of UCNP, which provides a prerequisite for triggering CCPEB under near-infrared light excitation conditions to achieve photodynamic therapy and siRNA release. In the presence of singlet oxygen, the intensity of the absorption spectrum of ADMA will decrease. Therefore, the production efficiency of singlet oxygen can be detected indirectly by detecting the change in the absorption spectrum of ADMA. The material is irradiated with 808 nm light, and ADMA is detected every 10 minutes. Absorption spectrum, the absorption curve of ADMA, can be obtained by using the absorption of ADMA at 260 nm and the irradiation time. The obvious change in the potential indicates that the amination modification is successful and the alginic acid is successfully coated on the surface of MSN. Since the surface of protamine sulfate is rich in amino acids that dissociate in the solution with positive potential, the nanoparticle potential becomes +13.2 mV. The obvious change of surface potential indicates that the amination modification is successful and the alginic acid is successfully coated on the MSN surface, and the cationic polypeptide protamine sulfate is successfully modified.Table 2
Ultraviolet visible light absorption spectrum.
Normalized absorbance1234567PMSNs0.340.511.350.520.410.660.75DOX0.412.221.490.520.690.710.34PMSNs@DOX1.230.490.680.510.490.570.61Figure 2
Ultraviolet visible light absorption spectrum.


### 4.3. Assembly Mechanism of Nanoparticles

The size of nanoparticles was further characterized by dynamic light scattering (DLS). It was confirmed that the size of nanoparticles dispersed in aqueous solution was about 110 nm, which was consistent with SEM and TEM images. The nanoparticles were dispersed in DMEM to study the stability of nanoparticles. The size of nanoparticles was measured on the first day, the third day, and the fifth day. It was found that the size of nanoparticles remained stable after 5 days storage in DMEM. Compared with the nanoparticles in aqueous solution, the hydration diameter of nanoparticles in DMEM is higher than that in water. The aqueous solution, dgnps solution, and MB solution containing the same amount of Abda were irradiated with 635 nm laser. The absorbance of the solution was measured every 2 minutes. The photodegradation curve of the solution is shown in Figure3. The absorption peak of Abda was almost unaffected by laser irradiation alone. However, with the addition of dgnps, the absorbance of the solution at 378 nm decreased gradually with the laser irradiation at 635 nm, indicating that dgnps can produce singlet oxygen under red light irradiation.Figure 3
Photodegradation curve of solution.As shown in Figure3, the abnormal condition of Abda reached the peak value of 1.2 at 4 minutes of the experiment. After 4 minutes, the condition of the sheep farm decreased but remained stable at the later time. Among the three experimental variables, the value of dgnps is the least abnormal and the most stable, and the frequency of tumor induction is the least. When the MB reaches 8 minutes, the abnormal situation intensifies and rises steadily. When the nanoparticles are captured by the endosomes, the PAA layer carrying DOX is protonated in the weakly acidic microenvironment of the tumor cells, resulting in the release of DOX. The released DOX can directly enter the nucleus, thereby inducing tumor cell apoptosis. This data proves that in the treatment of U87MG cells, RGD-mediated tumor cells play a key role in the endocytosis of materials. MTT experimental data show that this well-designed composite nano-drug with pH-responsive drug release ability and specifically targeting tumor cells has a good tumor treatment effect and shows a wide range of application prospects in practical applications. The apoptotic rate of 4T1 and Hela cells treated with UF at high concentrations is extremely low, indicating that UF nanoparticles have low cytotoxicity. Cells treated with RB or 808 nm light also have a higher survival rate. This is due to the high biological safety of RB and 808 nm radiation at low concentration and low power density. But for other treatment groups, the survival rate of cells showed a drug concentration-dependent. With the increase of material concentration, cells treated with pure DOX showed slight apoptosis. The poor therapeutic effect of this small molecule chemotherapeutic drug may be caused by the low concentration of DOX, and it is related to the active efflux effect of tumor cells and small molecule drugs after a long time incubation. Most importantly, as an oxygen-containing and dual-drug system, URODF + has extremely high cytotoxicity to both mouse and human tumor cells. Compared with the URDF + treatment group, this significantly enhanced tumor suppression effect indicates that the oxygen contained in the URODF nanoplatform has a key role in synergistic therapy.


### 4.4. Simulation Release Results of Nanomedicine

The ideal polymer drug carrier must have the property of effective release at the target. In order to improve the targeting release ability of DOX, we used acylhydrazone bond to connect it to the polymer skeleton to achieve the effect of targeted control release in acidic environment. The in vitro drug simulation experiments under different pH conditions proved this characteristic. The cytotoxicity test results of different concentrations of polymer precursors are shown in Figure4. When PCP-DOX was cultured at pH 7.4 for 65 hours, the drug release rate was only 6.4%, which proved that PCP-DOX had good stability in normal body fluid environment. However, under the condition of pH 5.0, the release rate of DOX was 32.8% in 24 hours and 60.0% in 65 hours. The release process of DOX continued and was positively correlated with the hydrolysis rate of acylhydrazone bond. In terms of release performance of polymer prodrug, pmema hyd DOX was consistent with PCP-DOX. In addition, the anticancer effect of PCP-DOX was further verified by celltier blue cytotoxicity test.Figure 4
Cytotoxicity test results.MCF-7, HepG2, and A549  hours later were cultured with PCP DOX of different concentrations. The culture medium was replaced with fresh serum-free DMEM for 47 hours, and then the cytotoxicity was detected. It can be seen from the data in the figure that PCP-DOX prodrug has enhanced therapeutic effect in three different cell lines, which is mainly attributed to the high efficiency of cell internalization and effective intracellular controlled release of PCP-DOX. When the concentration of DOX increased to 0.5μg/ml, the cytotoxicity of all materials increased significantly in different cell lines. Dox was selected as a drug model to study the drug controlled release performance of psio2-cs-cdha carrier. The drug release mechanism of DOX is that the hydroxy-1 in tumor microenvironment will decompose HA molecules on CDHA, resulting in CDHA falling off, and some pores on the surface of the carrier are exposed, resulting in drug release; meanwhile, the lower pH in the release solution will cause the change of chitosan molecular chain structure on the surface of the carrier, and the carrier pore channel will be exposed, The drug was released. The release experiment showed that the drug release rate was less than 20% under the normal physiological conditions of pH = 7.4, and reached 40% after 8 hours of release at pH = 5.6. Compared with the drug release under the response of hyal-1, the release rate of the carrier in acidic condition is slightly lower, and the time to reach the release equilibrium is longer. The reason may be that CDHA does not separate from the carrier under acidic conditions, and the drug molecules are hindered by CDHA in the process of diffusion outside the pore channel. As a nanoparticle plugging agent, CDHA is more effective in plugging the pores on the surface of the carrier than CS molecules.


## 4.1. Analysis of Phylocene

The 24 h cell survival rate of HeLa cells treated with different concentrations ofEuphorbia extract is shown in Table 1 and Figure 1. The logarithmic phase cells on 96 well plate were treated with drug. The OD value was detected by CCK-8 method after 24 hours. The results showed that all of the five fractions inhibited the proliferation of HeLa cells, and it was related to the drug concentration. With the increase of drug concentration, the survival rate of HeLa cells gradually decreased. When the concentration increased to a certain level, all the cells would be killed. The inhibitory effect of QJZ-E3 and QJZ-E4 samples was much greater than that of QJZ-E samples, and the activities of QJZ-E1 and QJZ-E2 samples were not strong, which indicated that the anti-cervical cancer active components of Euphorbia tomentosa were mainly concentrated in the alcohol extracts with higher polarity. It can be seen from the figure that the cell morphology changed significantly before and after administration. After treatment with QJZ-E, QJZ-E3, and QJZ-E4, the cell volume was significantly reduced, the connection between the cells disappeared and isolated from the surrounding cells, and the cells were suspended in the medium with a large number of apoptosis. However, after treatment with QJZ-E1 and QJZ-E2, the coexistence of living cells and dead cells was observed, and the cell survival rate was about 50%.Table 1
Cell survival rate.
Concentration00.511.522.53QJZ-E0.830.710.690.750.860.560.47QJZ-E10.750.660.810.620.590.570.79QJZ-E20.550.640.710.630.880.760.66QJZ-E30.340.250.570.610.710.490.53QJZ-E40.840.750.590.680.490.410.27Figure 1
Cell survival rate.The results of TEM show that the hydrophobicity and aggregate size of the brush increase with the decrease in the number of side chains. With the further increase of hydrophobicity, the morphology of aggregates also changed from micelles to vesicles. The results of SEM are consistent with those of TEM. In addition, the test results of cryo TEM and FF-TEM are larger than those of ordinary TEM and SEM, which is mainly due to the dehydration and shrinkage of aggregates in the drying process of TEM and SEM. When the hydrophilicity of amphiphilic random copolymers is strong and the molecular chain is long, it tends to form single molecular micelles; when the hydrophobicity is increased and the molecular chain is short, it tends to form multi molecular aggregates.


## 4.2. Performance Analysis of Nano-Drug Carrier

The UV-visible absorption spectra of PMSNs, DOX, and PMSNs@DOX are shown in Table2 and Figure 2. Free doxorubicin (DOX) has a strong UV-Vis absorption peak at 480 nm, while PMSNs have no characteristic absorption peak at this wavelength. After DOX is loaded, the absorption of PMSNs@DOX at 480 nm is significantly enhanced, indicating that DOX has been successfully loaded on PMSNs. In addition, the zeta potentials of PMSNs and PMSNs@DOX are -17.41 ± 0.38 mV and −8.08 ± 0.18 mV, respectively. The change of zeta potential also indirectly proves the existence of DOX. At the same time, the UV-Vis absorption spectrum of the nanocomposite obtained after PMSNs@DOX was modified by FA was also measured, and the results showed that there were both the characteristic peak of folic acid at 280 nm and the characteristic peak of DOX at 480 nm, indicating the success of FA modified on the surface of PMSNs@DOX. In addition, the absorption spectrum of CCPEB is just the composite spectrum of PFN and ONB, so there is a large spectral overlap with the emission of UCNP, which provides a prerequisite for triggering CCPEB under near-infrared light excitation conditions to achieve photodynamic therapy and siRNA release. In the presence of singlet oxygen, the intensity of the absorption spectrum of ADMA will decrease. Therefore, the production efficiency of singlet oxygen can be detected indirectly by detecting the change in the absorption spectrum of ADMA. The material is irradiated with 808 nm light, and ADMA is detected every 10 minutes. Absorption spectrum, the absorption curve of ADMA, can be obtained by using the absorption of ADMA at 260 nm and the irradiation time. The obvious change in the potential indicates that the amination modification is successful and the alginic acid is successfully coated on the surface of MSN. Since the surface of protamine sulfate is rich in amino acids that dissociate in the solution with positive potential, the nanoparticle potential becomes +13.2 mV. The obvious change of surface potential indicates that the amination modification is successful and the alginic acid is successfully coated on the MSN surface, and the cationic polypeptide protamine sulfate is successfully modified.Table 2
Ultraviolet visible light absorption spectrum.
Normalized absorbance1234567PMSNs0.340.511.350.520.410.660.75DOX0.412.221.490.520.690.710.34PMSNs@DOX1.230.490.680.510.490.570.61Figure 2
Ultraviolet visible light absorption spectrum.


## 4.3. Assembly Mechanism of Nanoparticles

The size of nanoparticles was further characterized by dynamic light scattering (DLS). It was confirmed that the size of nanoparticles dispersed in aqueous solution was about 110 nm, which was consistent with SEM and TEM images. The nanoparticles were dispersed in DMEM to study the stability of nanoparticles. The size of nanoparticles was measured on the first day, the third day, and the fifth day. It was found that the size of nanoparticles remained stable after 5 days storage in DMEM. Compared with the nanoparticles in aqueous solution, the hydration diameter of nanoparticles in DMEM is higher than that in water. The aqueous solution, dgnps solution, and MB solution containing the same amount of Abda were irradiated with 635 nm laser. The absorbance of the solution was measured every 2 minutes. The photodegradation curve of the solution is shown in Figure3. The absorption peak of Abda was almost unaffected by laser irradiation alone. However, with the addition of dgnps, the absorbance of the solution at 378 nm decreased gradually with the laser irradiation at 635 nm, indicating that dgnps can produce singlet oxygen under red light irradiation.Figure 3
Photodegradation curve of solution.As shown in Figure3, the abnormal condition of Abda reached the peak value of 1.2 at 4 minutes of the experiment. After 4 minutes, the condition of the sheep farm decreased but remained stable at the later time. Among the three experimental variables, the value of dgnps is the least abnormal and the most stable, and the frequency of tumor induction is the least. When the MB reaches 8 minutes, the abnormal situation intensifies and rises steadily. When the nanoparticles are captured by the endosomes, the PAA layer carrying DOX is protonated in the weakly acidic microenvironment of the tumor cells, resulting in the release of DOX. The released DOX can directly enter the nucleus, thereby inducing tumor cell apoptosis. This data proves that in the treatment of U87MG cells, RGD-mediated tumor cells play a key role in the endocytosis of materials. MTT experimental data show that this well-designed composite nano-drug with pH-responsive drug release ability and specifically targeting tumor cells has a good tumor treatment effect and shows a wide range of application prospects in practical applications. The apoptotic rate of 4T1 and Hela cells treated with UF at high concentrations is extremely low, indicating that UF nanoparticles have low cytotoxicity. Cells treated with RB or 808 nm light also have a higher survival rate. This is due to the high biological safety of RB and 808 nm radiation at low concentration and low power density. But for other treatment groups, the survival rate of cells showed a drug concentration-dependent. With the increase of material concentration, cells treated with pure DOX showed slight apoptosis. The poor therapeutic effect of this small molecule chemotherapeutic drug may be caused by the low concentration of DOX, and it is related to the active efflux effect of tumor cells and small molecule drugs after a long time incubation. Most importantly, as an oxygen-containing and dual-drug system, URODF + has extremely high cytotoxicity to both mouse and human tumor cells. Compared with the URDF + treatment group, this significantly enhanced tumor suppression effect indicates that the oxygen contained in the URODF nanoplatform has a key role in synergistic therapy.


## 4.4. Simulation Release Results of Nanomedicine

The ideal polymer drug carrier must have the property of effective release at the target. In order to improve the targeting release ability of DOX, we used acylhydrazone bond to connect it to the polymer skeleton to achieve the effect of targeted control release in acidic environment. The in vitro drug simulation experiments under different pH conditions proved this characteristic. The cytotoxicity test results of different concentrations of polymer precursors are shown in Figure4. When PCP-DOX was cultured at pH 7.4 for 65 hours, the drug release rate was only 6.4%, which proved that PCP-DOX had good stability in normal body fluid environment. However, under the condition of pH 5.0, the release rate of DOX was 32.8% in 24 hours and 60.0% in 65 hours. The release process of DOX continued and was positively correlated with the hydrolysis rate of acylhydrazone bond. In terms of release performance of polymer prodrug, pmema hyd DOX was consistent with PCP-DOX. In addition, the anticancer effect of PCP-DOX was further verified by celltier blue cytotoxicity test.Figure 4
Cytotoxicity test results.MCF-7, HepG2, and A549  hours later were cultured with PCP DOX of different concentrations. The culture medium was replaced with fresh serum-free DMEM for 47 hours, and then the cytotoxicity was detected. It can be seen from the data in the figure that PCP-DOX prodrug has enhanced therapeutic effect in three different cell lines, which is mainly attributed to the high efficiency of cell internalization and effective intracellular controlled release of PCP-DOX. When the concentration of DOX increased to 0.5μg/ml, the cytotoxicity of all materials increased significantly in different cell lines. Dox was selected as a drug model to study the drug controlled release performance of psio2-cs-cdha carrier. The drug release mechanism of DOX is that the hydroxy-1 in tumor microenvironment will decompose HA molecules on CDHA, resulting in CDHA falling off, and some pores on the surface of the carrier are exposed, resulting in drug release; meanwhile, the lower pH in the release solution will cause the change of chitosan molecular chain structure on the surface of the carrier, and the carrier pore channel will be exposed, The drug was released. The release experiment showed that the drug release rate was less than 20% under the normal physiological conditions of pH = 7.4, and reached 40% after 8 hours of release at pH = 5.6. Compared with the drug release under the response of hyal-1, the release rate of the carrier in acidic condition is slightly lower, and the time to reach the release equilibrium is longer. The reason may be that CDHA does not separate from the carrier under acidic conditions, and the drug molecules are hindered by CDHA in the process of diffusion outside the pore channel. As a nanoparticle plugging agent, CDHA is more effective in plugging the pores on the surface of the carrier than CS molecules.


## 5. Conclusions

This paper mainly studies the construction and properties of nano-drug carrier based onEuphorbia. It was found that GST inhibitor (NDB CL) could significantly reverse the resistance of resistant population to cyhalothrin. The GST activity of resistant population was significantly higher than that of sensitive population. Therefore, the resistance of TCGD16 population to cyhalothrin was related to the enhancement of GST activity. The commonly used photosensitive group nitrobenzyl was alternately introduced into the main chain of the polymer based on phenylacetylene benzene, and then the side chain was linked with polyethylene glycol through esterification reaction to obtain amphiphilic structure. It can self-assemble into nano-aggregates in water and can realize two-photon excitation photodegradation under 800 nm light excitation.The killing effect of different functionalized SWCNTs drug-loaded complexes on cells is mainly related to the loaded DOX. Targeted MTT experiments, cell uptake experiments, and phagocytosis experiments all confirmed that the drug-loaded complexes can actively recognize MCF-7 cells, thereby achieving the purpose of targeted therapy. Compared with a single molecule, these copolymer nano-aggregates have a larger two-photon absorption cross section, and the aggregation state of the nano-aggregates makes it easier for the energy transfer process between phenylalin and nitrobenzyl to occur. Due to the large two-photon absorption cross-section and effective energy transfer process, these nano-aggregates can be rapidly degraded under near-infrared light excitation conditions and release the coated hydrophobic drugs, so they can be effectively used for photodegradable nano-drug carrier.In this paper, by loading the dye in liposomes, and with the help of click chemistry, the dye CyBI7 is rapidly enriched in the tumor site to realize the early diagnosis of tumor and precise photothermal and photodynamic therapy. It solves the many shortcomings of the integrated diagnosis and treatment system in the traditional sense, provides new methods and new ideas for the targeted diagnosis and treatment of tumors and biological research, and is of great significance to the early diagnosis and treatment of various tumors. Cyclodextrin shell and mPEG shell can effectively encapsulate DOX in the mesoporous pores of MSN. Under the dual stimulation, the double shell gradually separates, the mesoporous pores are exposed, and the carrier exhibits a controllable release behavior. The results of cell experiments show that nanoparticles have good biocompatibility, and the combination of light stimulation and internal reduction stimulation makes the carrier have better therapeutic selectivity.



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*Source: 8528074-2022-08-29.xml*