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Shoot the Arrow at the Target: Innovative Stimulus-Responsive Smart Nanocarriers for Cancer Therapy

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31 January 2024

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31 January 2024

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Abstract
With the breakthroughs and innovative developments in nanotechnology, research on the application of nanomedicine in cancer therapy has so far seen tremendous expansion and success. Intelligent stimulus-responsive nanocarriers are an emerging field of research and have great interest in cancer therapy owing to the fascinating properties such as excellent targeting function, high drug loading capacity, and targeted on-demand release properties. Responsive nanomaterials can be designed and constructed according to the dosing context and therapeutic needs, at the same time, activated by internal bio-stimuli (pH, redox, and enzymes) and/or external stimuli (ultrasound, light, temperature, and magnetic), respectively. What’s more, smart nanocarriers are also utilized for the precise and controllable release of antitumor drugs from cancer tissues and cells to achieve efficient diagnosis and treatment of tumors. Deeply investigated, responsive nanocarriers have attracted considerable attention due to their ability to release precisely at tumor-specific sites. Herein, we review the recent advances of novel stimuli-responsive nanocarriers in the field of cancer therapy. Finally, the challenges and application prospects of smart nanocarriers are further elaborately discussed.
Keywords: 
Subject: Medicine and Pharmacology  -   Oncology and Oncogenics

1. Introduction

Despite the remarkable advancements in recent years regarding diagnostic procedures and therapeutic techniques, cancer remains one of the most complex diseases affecting the human being health and a primary cause of mortality (around 10 million deaths annually) globally [1-3]. It is considered that around 27 million new cases of cancer would be detected by 2030. The clinical applicability of conventional cancer therapies, such as radiotherapy and chemotherapy, is limited due to their potential for harmful effects on normal cells and broad systemic toxicity [4-6]. In addition, surgery is a popular and successful cancer treatment; however, the broad metastatic lesions typically limit its use in the treatment of metastatic malignancies. The intrinsic limitations of these therapies have led to the progressive development and application of other, safer, and more effective therapeutic modalities. Nanomedicines appear with the tide of clinical requirements. The emphasis of the corresponding research is on the exploitation of nanocarrier-based delivery systems as a mean of overcoming these restrictions [7,8]. These systems have a variety of benefits, such as the capability to extend the circulation time, increase the aqueous solubility, and reduce the side reaction of therapeutic agents via delivering them to specific target positions. With the recent decades seeing a tremendous growth in materials science, nanotechnology, therapeutic methods, and even clinical failures, nanocarriers have emerged as a novel platform for more effective diagnostics, treatment and prevention of a variety of diseases. Furthermore, these nanocarriers can be preferentially accumulated in the leaky vasculature of tumors by passive and active targeting through enhanced permeation and retention (EPR) effects [9-11]. Against the backdrop, more than two dozen nanomedicine formulations have been ratified for applying in clinical settings, and more are undergoing clinical trials. Despite the promising progress, the translation of EPR into the clinic settings remains questionable. For example, most of the conventionally designed nanocarriers have the disadvantage of premature drug release during circulation, which can injure normal tissues and reduce their therapeutic efficacy. Thus, more delivery systems with higher efficiency are needed.
An alternative is the on-demand drug delivery process generally allows for customized release profiles with outstanding spatial, temporal and dosage control. On-demand drug delivery has become possible by adopting stimulus-responsive nanocarriers to recognize and dynamically respond to the specific triggers that mimic the responsiveness of living cells, tissues, or organs. Since stimulus-responsive drug delivery was introduced in the late 1970s [12], researchers have conducted a large number of studies on the applications of stimuli-responsive materials in the field of drug delivery, especially in their design and application as nanocarriers. Specifically, the tumor microenvironment (TME) has utilized as an important target for cancer therapy and exhibits specific physiological properties. With quick tumor growth and vascular anisotropy, intra-tumor blood supply is often inadequate and chronically hypoxic, while cellular metabolism increases the accumulation of lactose and hydrogen ions, resulting in the formation of an acidic TME. In addition, higher redox potential, overexpression of enzymes, and increased metabolic activity are also characteristic of the TME. Together, these changes promote tumor angiogenesis, elevate tumor cell proliferation, migration capacity and immune escape ability, which in turn promote tumor development, and lead to therapeutic resistance and failure. Therefore, exploiting the unique properties of TME to design biomaterial platforms with TME responsiveness has been thought an effective strategy for cancer therapy.
Nanoscale stimuli-responsive carriers may be sensitive to specific triggers, such as internal (pH [13-15], enzyme [16-18], and redox reactions [19,20], etc.) and external (light [21,22], temperature [23-25], magnetic field [26,27], ionizing irradiation [28-30], etc.) triggers, as shown in Figure 1. Upon specific stimuli, these smart nanocarriers will take the place of specific protonation, hydrolytic cleavage, or molecular or supramolecular conformational changes that resulting in the release of the contained drugs. With the unique characteristics of on-demand delivery, stimuli-responsive nanocarriers have greatly facilitated the utilization of nanotechnology in chemotherapy and medical translation. Although these promising tools have generated much interest in drug delivery, there is still a demand of comprehensive reviews that summarize updated achievements in novel stimuli-responsive nanocarriers for cancer therapy.
In this review, we emphasize the recent designs and approaches utilizing smart nanocarriers that can respond to physiological environments and external stimuli to address delivery challenges, such as delivery efficiency, targeting precision and gene silencing. Afterwards, the numerous types of stimuli-responsive nanocarriers employed are summarized and their roles and future potential in organ-restricted delivery are also discussed. In the end, the challenges and application prospects of the smart nanocarriers are elaborately described.

2. Approach to Smart Delivery Strategies

2.1. Internal Stimuli for Drug Delivery Systems

Specific biological factors within the TME or cancer cells, including enzymes, low pH, re dox potential, and high reactive oxygen content, could serve as specific triggers for intranuclear endosome/lysosome escape, controlled release of drug, activation of drug precursors, as well as tumor-specific diagnostics and therapeutics [31-33]. Intrinsic stimuli are those inherent in the TME or within the cancer cells. However, their low specificity and heterogeneous distribution in tumors may compromise the efficacy of nanocarriers that are sensitive to intrinsic stimuli. This section will focus on recent advances in drug delivery systems intrinsically responsive to stimuli substance (mainly pH, redox and enzymes) in cancers diagnosis and therapy.

2.1.1. pH-Responsive Nanocarriers

Tumor tissue tends to have lower pH (5.5-6.0) compared to the normal tissue (pH 7.2-7.4), which is typical of solid tumors [13,34]. The main reason for the difference in pH between tumor cells and normal cells is the unrestricted proliferation of tumor cells and their unique metabolic changes (Warburg effect), which allow the cells to take up more glucose [35,36]. However, the level of oxidative phosphorylation within cancer cells is insufficient. As the dominant energy supply mode of tumor cells, glycolysis produces a plentiful of lactic acid, giving rise to a large accumulation of lactic acid in tumor tissues. In addition, the incomplete vascular system of tumor tissues and the absence of lymphatic system accelerate the acidic microenvironment of tumors [35,37,38]. One area of research that shows promise in responsive nanocarriers is exploiting the micro-acidity of tumor cells to control drug delivery and release. The release of drugs can be triggered by changes in internal pH levels. Nanoparticles have various gatekeeper molecules on their surface, which can be labeled using pH unstable groups like ester, hydrazine, and acetal bonds. These bonds are cleaved under acidic conditions. The transition from a neutral to an acidic environment leads to significant changes in the physical properties of substances' activity. For example, Zhang et al. designed and constructed a dihydralazine (HDZ)-pH-responsive delivery system based on a cyclic RGD (cRGD) peptide-modified dextran-hydrazone-doxorubicin (cRGD-Dex-DOX) precursor drug (Figure 2A) [39]. This nanosystem not only improved active targeting ability through cRGD peptide introduction but also exhibited pH-responsive drug release characteristics for targeting tumor stromal microenvironments (TSMs). In addition, co-loading HDZ and doxorubicin injections into the nanosystem resulted in sustained normalization of tumor vasculature, enhancing penetration into deep tumor sites. After four rounds of injections, it significantly dilated tumor vasculature while down-regulation of hypoxia-inducible factor 1α (HIF-1α), α-smooth muscle actin (α-SMA), and fibronectin expression and so forth. These alterations within TSMs not only enhanced the NPs enrichment and infiltration but also facilitated activated T cells infiltration into the tumors, which indicated that implementing such a system could potentially offer an effective "multifunctional therapy" by enhancing the effectiveness of chemotherapy and boosting the immune response against tumors. In vivo experiments conducted in 4T1 mice confirmed that this therapy has the most prominent anti-tumor effect with the fewest side effects than all other control regimens tested. The low drug-carrying capacity of nanocarrier carriers has been one of the major challenges encountered in smart nanomedicine systems and has largely limited the development of nanocarrier technology. Zhang and his co-workers constructed a 2D ultra-thin lamellar double hydroxide (LDH) nanosheet P-LDH with great drug loading capacity, outstanding colloidal stability, and extended blood circulation for cancer therapy (Figure 2B) [40]. P-LDH, synthesized by a biocompatible polymer-assisted bottom-up approach, has an ultra-thin two-dimensional lamellar structure with a large number of internal cargo-anchored sites available for drug loading, thus achieving a super drug loading capacity of 734% (doxorubicin/nanoparticle mass ratio). Under physiological pH conditions, P-LDH-delivered doxorubicin remained stable on the nanosheet carriers while exhibiting continued release in the TME and intracellular environment, suggesting on-demand drug release due to pH-responsive nanosheet biodegradation. In both in vitro and in vivo 4T1 models, based on an ultra-high-loading system, P-LDH exhibited improved efficacy in enhancing tumor cell uptake efficiency, prolonging drug circulation, improving therapeutic efficacy and reducing systemic toxicity compared to a multilayered high-loading system based on lactate dehydrogenase. The successful construction of this nanosystem also provides the possibility for the rapid development of nano-loading technology.

2.1.2. Redox-Responsive Nanocarriers

Reactive oxygen species termed ROS are known to be by-products of biological aerobic metabolism, containing oxygen ions, peroxides, and oxygen-containing free radicals, which play an essential role in various normal biological and pathological processes [41,42]. Scientific studies have shown that under normal physiological conditions, ROS are maintained at a very low equilibrium level in living organisms, but during the development of various diseases, including inflammation, cardiovascular diseases, sarcoidosis, and tumors, ROS level in local tissue mitochondria is much higher than that in normal ones [43,44]. Numerous studies have confirmed that the abnormal physiological behaviour of tumor tissues enable them to produce large amounts of ROS, the concentration of which is increased by more than ten times than that of normal tissues [45]. Therefore, by utilizing the differences in ROS levels in and out of tumor tissues and cells, ROS-responsive smart nanomedicine carriers constructed with ROS-sensitive materials are a prerequisite for controlling the targeted release of drug molecules for drug delivery in tumor cells [46,47]. The ROS-sensitive chemical groups in the design skeletons of current ROS-responsive drug carriers mainly contain characteristic groups such as borate, thione, sulfide, selenium and ferrocene groups [19,48]. Recently, Dey et al. developed SPP@2ME, a cascade-amplified polymer precursor drug loaded with 2-methoxy-β-estradiol (2ME) [49]. In this study, selective activation of SPP@2ME by rich ROS in cancer cells triggers the progressive decomposition of spontaneous polymerization pre-drugs (SPPs) in tumor cells and the production of a large number of quinones and their analogs (QMs), which deplete glutathione (GSH). Meanwhile, SPP degradation leads to the rapid release of 2ME into cellular plasma, increasing ROS levels in cancer cells through a domino-like cascade amplification feedback mechanism (Figure 3A). What's more, the synergistic effect of SPP and 2ME remarkably exacerbated the oxidative stress and destroyed redox equilibrium of cancer cells. The in vivo and ex vivo experiments confirmed the great potential of SPP@2ME in anti-tumor therapy and also provided important insights for innovative and precise nanomedicine.
There are significant redox potential differences between tumor tissues and normal physiological tissues as well as inside and outside tumor cells. The abnormal metabolism in tumor tissues leads to the generation of a more intense reducing environment [50]. The concentration of GSH is about 2-20 μM in normal tissues, and the concentration of GSH in tumor tissues is usually two times that in normal tissues. The intracellular GSH concentration is about 0.5-10 mM, which is more than 100 times the extracellular concentration (2-20 μM) [19,51]. In addition to the reducing substance GSH, tumor cells contain small amounts of divalent iron ions (Fe2+), cysteine (Cys), thioredoxin reductase and lysosomal thiol reductase [52]. Therefore, this difference in the content of reduced substances inside and outside tumor cells (especially GSH) provides new possibilities for designing reduction-responsive nanodrug carriers to achieve reduction-responsive drug release inside the tumor cells. Reduction-sensitive chemical groups, such as disulfide bonds and diselenide bonds [19,53], are able to undergo rupture, thus causing changes in the structure of the drug carrier and achieving rapid drug release. For example, Li et al. reported a dihydroartemisinin (DHA) dimerized nanoprecursor drug (DHA2-SS) with disulfide bonds as connecting bonds [51]. The nanoprecursor drug exhibited stability with high drug loads (up to 90.6 wt%). It demonstrated sensitivity to changes in redox levels within the TME, resulting in efficient release of DHA for chemotherapy (Figure 3B). Notably, in vitro and in vivo therapeutic experiments revealed that these prepared SS NPs displayed strong endocytosis capabilities, intense cytotoxicity, and improved anti-tumor effects compared to free DHA. Simultaneously, RNA sequencing and bioinformatic analysis indicated that it could not only induced apoptosis through the intrinsic mitochondrial apoptotic pathway, but also inhibited glycolysis via the PI3K/AKT/HIF-1α signaling pathway, presenting a novel target for treating hepatocellular carcinoma. Consequently, this study provided valuable insights into designing responsive precursor drug nanoparticles while encouraging further research on traditional Chinese medicine and related natural active ingredients.

2.1.3. Enzyme-Responsive Nanocarriers

Enzymes, as macromolecular biocatalysts, act a crucial role in systemic metabolism and cellular regulation and are important parameters in the diagnosis of various diseases. Studies have shown that dysregulated expression of certain enzymes leads to increased enzyme concentrations at the tumor site, such as matrix metalloproteinases 2 (MMP2), glycosidase, cathepsin B, secretory phospholipase A2 (sPLA2), hyaluronidase (HAdase), and others (sPLA2), hyaluronidase (HAdase), etc [54,55]. Therefore, based on the differences in enzyme expression between normal tissues and tumor sites, enzyme recognition and degradation nanosystems that can specifically recognize the differences in enzyme over-expression inside and outside the cell can be designed and constructed to achieve specific enzyme-responsive drug release at tumor sites [55]. In addition, enzymes as triggers have many unique advantages, such as the mildness of the enzymatic reaction conditions and good enzyme selectivity of substrates. Therefore, the design of enzyme-responsive drug-release nanomedicines based on tumor-specific highly expressed enzymes can obtain highly specific controlled release functions and thus reduce side effects of drugs. A great number of studies have reported that matrix metalloproteinases (MMPs) are currently commonly used triggers for enzyme-responsive drug delivery in antitumor therapy [56-58]. For example, Cao et al. constructed the Nap-FFGPLGLARKRK, a surfactant-like peptide for cancer-targeted drug delivery [58]. This peptide consisted of three functional components: a Nap-FF-aromatic motif that facilitated it self-assembly, an enzyme-responsive cleavable -GPLGLA-segment, and a positively charged -RKRK-segment that balanced the molecule's amphiphilicity while promoted interactions with cell membranes, which self-assembled into elongated fibers with a hydrophobic core capable of encapsulating significant amounts of the anticancer drug DOX (Figure 4A). Targeted drug delivery and selective anticancer therapy are achieved through tumor overexpression of matrix metalloproteinase-7 (MMP7) at the tumor site, which is degraded into finer fibers that precipitate out and slow the release of DOX. In vivo antitumor experiments in mice confirmed that this enzyme-responsive peptide drug carrier could effectively inhibited tumor growth and metastasis, while greatly reducing adverse reactions. This investigation demonstrated it’s desirable to utilize enzyme-sensitive peptide nanostructures in practical targeted drug delivery, which had significant prospects in biomedical cancer therapy. In addition, Wan et al. constructed dual enzyme-responsive micelles for the first time by physically loading enzyme-responsive substances into the micelles via π-π stacking, and obtained DOX micelles consisting of intra- and extracellular enzyme-responsive TPD&FPD&D micelles by dialysis preparation [59]. Two of the enzyme-responsive substances were D-α-tocopherol polyethylene glycol 3350 succinate (TPGS3350)-Gly-Pro-Leu-Gly-Val-Arg (GPLGVR)-DOX (TPD) precursors specifically responding to the overexpression of MMP-9 in the TME, and FA-Asp-Glu-Val-Asp (DEVD)-DOX (FPD) precursors responding to the caspase-3, respectively (Figure 4B). In addition, the micellar matrix material TPGS3350 was obtained by esterifying and synthesizing PEG3350 with vitamin E succinate to extend the circulation time of TPD&FPD&D micelles in the bloodstream in vivo and to utilize the EPR effect for passive targeting enrichment in tumor tissues. In the presence of MMP-9 enzyme over-expressed in tumor tissues, the GPLGVR peptide in the micelles could be cleaved, thereby shedding the outer layer of TPGS3350 and exposing folate as itstargeting molecule. Subsequently, the micelles could enter the tumor cells through folate receptor-mediated endocytosis pathway. At the same time, free DOX was released is released from the micelles, inducing 4T1 apoptosis in tumor cells, activating the apoptotic protease caspase-3, which further cracked the peptide (DEVD) and increased the release of DOX, thus markedly enhancing the cytotoxicity of the intracellular drug and improving the antitumor effect. This study demonstrated that micelles, activated by a bi-enzymatic reaction, had the advantages of long cycle time, good stability, penetration, high drug loading, targeting, high biosafety, and rapid intracellular uptake, which provided an effective tumor inhibition and reduced systemic toxicity in 4T1 hormonal mice.

2.2. External Stimuli for Drug Delivery Systems

External stimuli can influence the state of nanocarriers in biosystems, mainly including light, ultrasound, magnetism and temperature. The enrichment of nanocarriers in a desired region is facilitated by external stimuli, such as magnetic fields, controlled release, intracellular drug delivery, and activation of imaging and therapeutics. Applying external stimulation for drug delivery are with multiple facilitations: (1) the timing, location, and intensity of external stimuli (e.g., magnetic field, laser irradiation) can be precisely controlled by artificial intelligence; (2) external stimuli can be attach or eliminated according to the therapeutic needs; (3) multifunctional, multimodal tumor diagnosis and treatment can be achieved through the superposition of multiple external stimuli; (4) it can be more easily implemented for multiple times or consecutively (e.g., for hours or days) drug delivery and therapeutic stimulation; and (5) injury to normal tissues and organs can be minimized by more perfect control of external stimulation. In addition, the external stimulus response system allows for interconversion between different stimuli, such as localized release of drugs under near-infrared irradiation with localized heat generation in tissues (thermal response). In this chapter, we will discuss the development of drug delivery systems utilizing external stimuli, including light, ultrasound, magnetic field, temperature changes, and their specific applications in tumor diagnosis and therapy.

2.2.1. Light-Responsive Nanocarriers

The tunability and real-time manipulation of the intensity and wavelength of light, good spatio-temporal precision, mini-invasiveness, higher confidence, and orthogonality to the intracellular light environment have led to the widespread use of photosensitized nanocarriers in biomedical fields [60,61]. Effective therapeutic methods of photostimulation include photothermal drugs and photosensitive drugs. The study of photosensitized drug release is, firstly, through light stimulation of microenvironmental changes, the carrier molecular structure changes to make the drug release; secondly, while irradiating the photosensitizer to produce therapeutic effects, the intermediates indirectly act on the chemical bond to make the drug release. The light source, which is the central element of photostimulation, can be ultraviolet-visible (UV-vis) or near-infrared (NIR) [62,63]. However, UV-vis light has the disadvantage of poor penetration ability, cannot penetrate deep into tissues and easily causing harm to the human body, while the maximum permeability of skin to light appears in the NIR window of 650-900 nm with a penetration depth of up to 2 cm. What’s more, the longer the wavelength, the greater the ability to penetrate into tissues in the NIR wavelength region [64]. As a result, NIR light offers considerable advantages compared to UV and visible light in phototherapy and optical imaging of deep tissues [65]. Therefore, NIR light is more suitable as a source of stimulating light for the construction of light-triggered drug delivery systems [66].
In general, various strategies have been proposed in designing light-stimulated drug release systems for tumor therapy: (1) absorption of light dissociating the prodrug into its active form; (2) absorption of light by a photosensitive molecule, which triggers a physical change that releases the encapsulated drug [67,68]. The former commonly involves functionalizing the chemotherapeutic drug to obtain a prodrug with reduced cytotoxicity. Under light exposure at the target site, these precursor drugs undergo photolysis giving rise to the release of the chemotherapeutic drug and the realization of precision therapy. The latter usually employs light-responsive organic molecules such as azobenzene derivatives grafted onto the surface of functionalized nanoparticles. These photoresponsive moieties undergo isomerization (e.g., trans-cis-isomerization) in response to light, leading to conformational or molecular changes that result in the release of the encapsulated drug [67,69]. In addition to photo-responsive DDSs designed for chemotherapy, photosensitive nanomaterials have been applied for cancer diagnosis and treatment in other forms, such as photodynamic therapy (PDT), photothermal therapy (PTT), and photoacoustic (PA) imaging [70-72]. A successful construction of an intelligently designed and controlled synthesis of psar-modified gold nanovesicles (PSGVs) (Figure 5A) was first reported by Lv et al [68]. By synthesizing a battery of lipoic acid-capped polysaccharide-b polycaprolactone block copolymers (PSar-b-PCL) and systematically investigating the self-assembly behavior of 26 nm gold nanoparticles mediated by block copolymer, the construction of NIR-light-responsive psar-modified gold nanovesicles (PSGVs) was enhanced to highly efficient photo-thermal conversion efficiency (up to 34.6%). Next, the anti-tumor drug DOX was efficiently loaded in the PSGV cavity, and the high loading capacity (up to 20.6%) and stability of DOX were realized. The encapsulated DOX was targeted for rapid release by 808 nm laser irradiation to achieve controlled drug delivery and tumor therapy. Impressively, DOX-loaded PSGV (DOX-PSGV) showed increased cellular uptake efficiency and higher tumor inhibition than DOX-loaded polyethylene glycol (PEG)-encapsulated gold nanovesicles (DOX-PEGV). Both in vitro and in vivo anti-tumor trials indicated that DOX-PSGV was equipped with favorable photothermal/chemotherapeutic synergistic therapeutic effects under 808 nm laser irradiation.
However, in practical clinical applications, the targeting properties and sustained drug release ability of nanostructures may be restricted by their irreversible and uncontrolled destruction. To address this challenge, Deng and his collaborators designed and prepared X-ray responsive biomimetic nanocapsules PETAzo@ZnS-A with reversible and tunable permeability by crosslinking poly(thymine) and photoisomerized poly(azobenzene) (PETAzo) with adenine-modified ZnS (ZnS-A) nanoparticles (NPs) (Figure 5B). The ZnS-A nano particles efficiently converted X-ray into UV-visible light and induced isomerization of azobenzene groups, thus allowing the active load to diffuse controllably through the bilayer membrane for accurate drug delivery [73]. In contrast to the conventional method of regulating the permeability of nanostructures by destroying the structure of nanocapsules, which was an irreversible process, PETAzo@ZnS-A remotely controlled bilayer permeability of nanocapsules allows for adjustable permeability while maintaining structural integrity, with long retention time, remotely controlled drug release, improved targeted aggregation, and potent anti-tumor effects. The outcomes of in vivo and ex vivo experiments proved that the X-ray-triggered nanocapsules can control the drug release to meet the complex sensitivities of various tumor cells and patients, enabling precision tumor therapy.

2.2.2. Ultrasound-Responsive Nanocarriers

Ultrasound, as a non-invasive method, belong to one of the most frequently used exogenous stimuli strategies in tumor therapy [74,75]. Furthermore, the inimitable benefits of ultrasound responsiveness are safer and deeper tissue penetration [28,76]. In drug delivery systems, the pressure waves of ultrasound are 20 kHz or higher, which is a crucial factor in local stimulation involving both site-specific and spatial release control, giving rise to a growing awareness of cancer therapy [77-79]. Wang et al. established an ultrasound-responsive nanoprodrug named CPT-t-R-PEG2000@BaTiO3 (CRB), which encapsulated piezoelectric nanomaterials barium titanate nanoparticle (BaTiO3) in amphiphilic prodrug molecules. The ROS-responsive thioketal bond (t) in this prodrug linked chemotherapy drug camptothecin (CPT) to NO-donor L-arginine (R) (Figure 6A) [80]. BaTiO3, as a piezoelectric material, is triggered by ultrasound in the complicated hypoxic environment of tumors and water cleavage to continuously generate ROS through piezoelectric catalysis, which induces a cascade reaction process. Then due to breakage of thione bond, CPT is released and L-arginine (R) is oxidized to produce NO molecules, accomplishing timed and targeted delivery of NO and CPT at the tumor site. What's more, NO could modulate the matrix of the TME, promoting the deep tumor penetration of the nanoparticles and the release of CPT, further improving the chemotherapeutic effect on tumors. In vivo animal experiments confirmed that CRB significantly enhanced the anti-tumor effect by inhibiting resistance to chemotherapy in mice. This precursor drug delivery strategy was shown to have the great advantages of safer and better targeting, which might be a viable avenue for treatment of pancreatic cancer, inspiring further studies of drug deeper tumor infiltration.
Sun and his group members developed a peptide nanogel that can undergo stiffness transformation by external ultrasound stimulation by using genipin crosslinked with polylysine, simultaneously, introducing a targeted drug (ICAM-1 antibody) and a chemotherapeutic drug (epirubicin) to obtain the gel prodrug GenPLPFT/EPI [29]. By regulating the external ultrasound stimulation, its deformation ability and stiffness were achieved to reach deep penetration into the tumor and prolong blood circulation, further enabling it to effectively treat triple-negative breast cancer (TNBC) (Figure 6B, C). In both in vitro and in vivo TNBC models, GenPLPFT/EPI was able to balance blood circulation and deep tumor infiltration to exert highly effective anti-cancer effects, which the investigators attributed likely to the active targeting and ultrasound-triggered deformability of GenPLPFT. In contrast, unsonicated GenPLPFT represented only a low level of tumor penetration. Overall, ultrasound-responsive peptide nanogels were an effective cancer drug treatment that could effectively balance the conflicting needs of deep tumor penetration and extended blood circulation.

2.2.3. Magnetic-Responsive Nanocarriers

In recent years, magnetically responsive nanosystems, owing to their unique and outstanding physical and chemical characteristics, have shown promising applications in many fields of biology and medicine, including tumor targeting and imaging. It is particularly worth mentioning for their roles in providing diversified delivery routes for drug delivery [81]. Compared with endogenous stimulus-responsive nanosystems, magnetic-responsive nanosystems have the following advantages: with intrinsic magnetotactic properties, magnetic fields can be applied in vivo by remote operation to increase the enrichment of drugs in tumors and target tumors; local high temperatures will be produced in an applied alternating magnetic field, which can kill tumor cells through targeted thermotherapy; through the action of an applied high-frequency magnetic field, different tissues of the organism radiate energy to the surroundings, which generates different resonance signals [82-84]. By applying high-frequency magnetic field, different tissues of the organism will radiate energy to the surrounding environment, thus generating different resonance signals and realizing magnetic resonance imaging (MRI), cellular imaging and tumor detection, as well as real-time dynamic tracking and evaluation of tumor diagnosis and treatment and therapeutic effect after drug administration [85]. To date, a variety of magnetoresponsive nanocarriers have been studied and widely used, including magnetoresponsive nanoparticles, superparamagnetic iron oxide nanoparticles (SPIONs), magnetic nanogels and polymer micelles, etc [86-89]. Recently, Guo et al. designed and prepared a magnetically responsive immunostimulatory nanoparticles (MINPs) based on SPIOs loaded with cytosine-phosphate-guanine oligodeoxynucleotides (CpG odn), which could be used not only as a contrast agent for photoacoustic/magnetic resonance (PA/MR) dual-modal imaging, but also a magnetically-targeted therapeutic agent for photothermal-triggered immunotherapy [90]. Under the action of an external magnetic field, MINPs exhibited good magnetic targeting, which can lead to large number of photo-absorbents (SPIOs) and immuno-adjuvants (CpG ODNs) to accumulate within the tumor, achieving precise dual-modality imaging guidance. What's more, through near-infrared irradiation, MINPs have a good photothermal conversion effect, which can effectively photothermally destroy primary tumors, release tumor-associated antigens, and exhibit a function similar to that of an "autologous tumor vaccine", thus activating a force fulimmune response to fight against tumor and generating a synergistic photothermal/immunotherapy effect on both primaryand distant tumors (Figure 7A). The successful construction of this strategy provided a platform to achieve a synergistic photothermal/immunotherapy effect and a new option for the precise individualized diagnosis and treatment of various tumors and metastases. Similarly, Jia et al. developed a versatilenanoplatform (CoFe2O4 nanoparticles@dopamine@DOX) for magnetically responsive on-demand thermotherapy and chemotherapy synergistic diagnosis of tumors based on magnetic CoFe2O4 MNPs [91]. The nanoplatform had excellent magnetically triggered thermotherapy efficacy, magnetically responsive drug delivery capability, and strengthened MRI T2-weighted signals. What's more, in vivo experiments showed that CoFe2O4 nanoparticles@dopamine@DOX nanomedicine could achieve magnetically-responsive on-demand thermotherapy and DOX release, which significantly inhibited the growth of cancer cells and led to significant tumor regression with good safety (Figure 7B). This multifunctional nanoplatform featured simple fabrication, green environmental protection, magnetically triggered high thermotherapy efficacy rate, magnetically responsive tumor on-demand therapy, and non-invasive imaging modalities, which offered great advantages over traditional single-drug therapeutic technologies, and provided an option for precise clinical treatment of tumors.

2.2.4. Temperature-Responsive Nanocarriers

Nowadays, temperature-sensitive drug delivery systems are much researched stimulus response strategies, which have been widely used in oncology therapy due to their advantages of flexible design, adjustable phase change temperature, multi-pathway stimulation (internal stimulation, including tumor, inflammation, and infection; and external stimulation, including light irradiation, triggered by magnetic or electric fields or external heating), and strong passive targeting ability [24]. In addition, it has been reported that local thermal stimulation at 42.5-43.5°C in tumors benefits drugs to avoid cancer cells. On the other hand, thermal stimulation has a vasodilating effect and alters the permeability of tumor cell membranes, thus facilitating the delivery of antitumor drugs and local drug concentration, and enhancing the antitumor effect. Heat-sensitive materials are usually temperature-controlled by a temperature-sensitive material in a nanosystem, which triggers a change in the nanosystem upon warming, triggering drug release [92,93]. Typically, thermosensitive nanosystems remain stable at 37°C and can trigger rapid drug delivery after reaching 40-42°C, minimizing drug leakage due to blood circulation and metabolism at the tumor site [31]. Polymeric micelles [94-96], hydrogel [97,98], liposomes [92,99,100], and poly(N-isopropylacrylamide) [101] have all been used as carriers for thermoresponsive systems because they exhibit low critical dissolution temperatures. Temperature-sensitive liposomes are one of the most widely used thermoresponsive nanosystems, which can induce phase transitions in lipids and conformational changes in lipid bilayers under temperature changes (~40-50°C). A representative example was the recent construction of a multifunctional "smart" liposome diagnostic platform (liposomes L1) by Zhu et al., which consisted of the chemical structure of an M-PEGylated peptide programmed into the peptide M-PEG "comb" 1, which was equipped with an 19F MRI/fluorescence dual imaging and temperature-sensitive "add-on" modules, and were obtained by self-aggregation with the anticancer drug adriamycin (doxorubicin) and lecithin (Figure 8A). Moreover, as a chemically accurate monodisperse peptide, it perfectly avoided the heterogeneity problem of polydisperse biomaterials. In addition, it could be precisely programmed during solid-phase peptide synthesis, enabling fine on-demand tuning of physicochemical and biological properties. And the 19F MRI/fluorescence dual imaging technology provides ex vivo and in vivo drug imaging and tumor imaging, which truly enabled visual dynamic imaging and efficacy tracking of therapy (Figure 8B). What's more, this intelligent lipid diagnostic platform had the characteristics of long in vivo half-life, good monodispersity, biodegradability, low toxicity and high tumor accumulation. The successful construction of this platform provided a new reference for the design of multifunctional "add-on" modular lipid nanodrug delivery systems for tumors, as well as the quick and facile development of various "smart" diagnostics.

2.3. Dual and Multiple Stimuli Responsiveness

To further optimize the delivery of antitumor agents, there is an increasing interest in designing stimuli-responsive nanocarrier delivery systems. However, as tumor cells exhibit significant heterogeneity, most mono-responsive nanosystems possess limited performance of sluggish and inadequate drug release at target site, resulting in the reduction of therapeutic efficacy [102,103]. In comparison, multiple stimuli-responsive nanoparticles are more popular for dealing with the heterogeneity and complexity of the bio-microenvironment to achieve adequate site-specific delivery [53,104]. For example, in solid tumors, the abnormal metabolic patterns and levels of tumor tissues and tumor cells, which can co-exist with pH gradients and oxidative environments, are ideal combinations of intracellular stimulators for the construction of stimuli-responsive nanodrugs. Zhang et al. designed a self-assembled pH/ROS-responsive micellar drug delivery system (PPT/D(DMA)@DOX) loading adriamycin (DOX) [105]. The system featured charge reversal and self-amplified drug release. Charge reversal occurs when the negatively charged surface micelles are exposed to acidic conditions (pH<6.8), generating good cell membrane penetration and enhancing tumor cell uptake. In addition, thioether molecules undergo oxidative decomposition and deliver drugs to tumor cells, exerting antitumor activity by increasing tumor ROS levels and inducing apoptosis. More importantly, the exposed α-tocopheryl succinate (TOS) fragments lead to increased intracellular ROS concentration, self-amplified breakdown of micelles, and accelerated release of DOX, resulting in potent tumor-killing capabilities (Figure 9A). In conclusion, this pH/ROS-responsive micellar drug delivery system has the unique advantages of desirable cellular uptake, triggered targeted release, and charge reversal system, showing significant prospects for improved treatment outcomes in tumor therapy.
Jia et al. reported an innovative intra-tumor dual redox/enzyme-responsive NO-releasing nanomedicine platform (QM-NPQ@PDHNs) by encapsulating NO-precursor drugs NPQ and AIEgen QM-2 in hybrid micelles doped with silicon disulfide [106]. The nanoplatform exhibited efficient passive tumor-targeting ability, which allowed the encapsulated NPQ to be efficiently carried into the targeted tissue. The over-expression of GSH in the tumor would induce disulfide bond breaking and NPQ release. With high concentrations of GSTπ and GSH at the tumor site, NPQ was catalyzed to release large amounts of NO to kill tumor cells. Compared to free NPQ drugs, QM-NPQ@PDHN was more target-specific and had higher safety for normal tissues (Figure 9B). This dual redox/enzyme-responsive nanomedicine provided a new way to increase the specificity of chemotherapeutic drugs, efficient anti-tumor therapy, and safe treatment.
Additionally, researchers have also dual expanded stimulus-responsive nanomaterials with pH and enzyme sensitivity for specific drug delivery. Considering that the barrier impermeability of solid tumors might limit the co-delivery of protein-based drugs and chemotherapeutic agents, Shen et al. established a novel pH/enzyme dual-activated ZIF-DOX/RA@DG nanosystem that carry ribonuclease a (RA) and DOX in the core of a zeolite-type imidazolium salt framework (ZIF-8) [107]. External encapsulation with dextran coating (DG) using microfluidics was used to stabilize the polymer reactivity of the encapsulated drugs, the structure and biological activity of ZIF-8. In addition, the nanosystem exhibited dual reactivity owing to γ-glutamyl transpeptidase (GGT)-activated cationization and degradation arouse by the acidic microenvironment (Figure 9C). Due to the surface charge of the DG layer from a slightly negative charge to a positive charge, the penetration ability of ZIF@DG NPs into solid tumors upon GGT activation was enhanced. Indeed, the pH-responsive DG coating inhibited circulating guest proteins and small-molecule drugs leaking prematurely from the ZIF-8 nanoparticles, thus achieving the targeted release of cargo molecules within the tumor. The results of in vivo experiments confirmed the synergistic anticancer therapeutic effect of ZIF-DOX/RA@DG nanosystems with multiple drug-carrying capacity, tumor-selective permeability to deeper, and less easily penetrated lesion sites. This multidrug delivery system based on smart response design and microfluidic-assisted synthesis method offered prospects for clinical tumor therapy.
Apart from the synchronized internal dual response described above, there are external stimulus and internal stimulus synergistic, external and internal stimulus synergistic responses, and multi-response nanocarrier systems. For example, Chen et al. recently constructed a NIR light and pH dual-response multimodal synergistic diagnosis and treatment platform (PCN-DOX@PDA) [108]. This platform could achieve tumor diagnosis and treatment through a triple synergistic strategy, which included: (1) using porous metal-organic framework (MOF) material PCN-600 as a carrier carrying antitumor agents and polydopamine (PDA), the ligand tetracarboxyphenylporphyrin (TCPP) in PCN600 as a photosensitizer generated monolinear oxygen (1O2) to kill tumor cells with an excitation of 633 nm, while PDA served as a photothermal agent to achieve photothermal treatment of tumors; (2) PCN-DOX@PDA achieved smart release of the anticancer drug DOX by responding to the weak acidic TME and thermal stimulation generated by near-infrared irradiation; (3) due to the presence of Fe3+ in the center of the PCN, PCN-DOX@PDA could mediate tumor chemotherapy through magnetic resonance imaging and photothermal and photodynamic synergistic therapy to achieve diagnosis and treatment of tumors (Figure 10A). In vivo experimental results verified that PCN-DOX@PDA had good biocompatibility and anti-tumor ability, indicating that the dual-response multifunctional integrated diagnostic platform of NIR and pH had an unlimited potential in oncology precision therapy and diverse biomedical applications.
Nanocatalysts is one of nanomaterials with endogenous enzyme-like activity, which have been widely studied for tumor catalytic therapy recently. However, there is still a challenge for the construction of nanocatalysts with favorable enzyme catalytic activity and biocompatibility for tumor therapy. Recently, Zhu et al. constructed a TME/light-responsive, biodegradable, multimodal imaging-guided nanocatalyst, CuxMnySz (PCMS), for oncology diagnosis and treatment [109]. PCMS possessed multi-enzymatic (CAT-like and OXD-like activities) properties, and was capable of catalyzing the endogenous hydrogen peroxide in the TME (H2O2) to oxygen (O2) via a catalase-like activity cascade, and superoxide radicals through an oxidase-like activity cascade, resulting in excellent catalytic therapeutic effects. Meanwhile, PCMS depleted endogenous GSH in tumor cells through GSHOX-like activity, which effectively inhibited antioxidant defense and amplified the level of oxidative stress to ROS in tumor cells. In addition, under laser irradiation, PCMS exhibited excellent photothermal performance (up to ƞ = 56.7%) with an excitation at NIR-II 1064 nm, which significantly enhanced the therapeutic efficacy of tumor treatment. Notably, PCMS exhibited multimodal imaging (PAI, MRI, and ITI) performance in vivo to effectively detect tumors and track nanocatalyst distribution and metabolism (Figure 10B). This feature enabled PCMS to achieve optimal performance in the most efficient time window. In a hormonal mouse model, PCMS effectively inhibited tumor development, and significantly improved the therapeutic effect with few side effects. In summary, the present study provides an innovative strategy to efficiently generate ROS and consume ROS scavenging system through a cascade reaction, and rationally design a highly efficient nanocatalator for tumor catalytic therapy.
A large number of triple stimulus-responsive nanodrug delivery systems have been reported for tumor treatment in the TME, showing superior specificity, targeting, controllability and safety [33], for example, pH/redox/NIR triple-responsive ZnO quantum dots-conjugated hollow mesoporous carbon nanoplatform [110], light and dual-redox triple-responsive core-crosslinked micelles [111], hypoxia/temperature/pH triple-responsive block copolymers [112], and so forth. Recently, Wu et al. reported a pH/thermal/glutathione triple-responsive smart supramolecular nanomedicine (FUS/ICG@PEDD) which was constructed by utilizing particular and kinetic hydrogen bonding interactions [112]. The supramolecular polymeric micelles were co-loaded with α, ω-functionalized symmetric hydrogen bonding precursor drug 5-fluorouracil acetate -SS-5-fluorouracil acetate (FUS) and dual photothermal/photodynamic agent (indocyanine green, ICG). It also featured increased drug loading, cross-linking for robustness, pH-responsive charge reversal and intelligent drug delivery, and was perfectly synergistic with CT/PTT/PDT for tumor diagnosis and treatment (Figure 11). For supramolecular micelle construction, the investigators designed a novel amphiphilic diblock copolymer PEG-b-P(DAPA-co-DEAEMA) (denoted as PEDD) as a drug delivery vehicle, in which hydrophilic PEG [poly(ethylene glycol)] and hydrophobic P(DAPA-co-DEAEMA) [poly(diaminopyridylacrylamide-co-2-(diethylamino)ethyl methacrylate] were equipped with dual functional groups: pH-responsive charge reversal DEAEMA motifs and H-bonded DAP motifs. In vitro and in vivo experiments revealed significant antitumor activity. Overall, the successful construction of this hydrogen-bonded nanomedicine provided new ideas and references to advancing intelligent nanomedicines and multimodal cancer therapy.

3. Conclusions and Perspectives

In summary, this paper reviews and assessments the strategies for the application of smart stimulus-responsive nanosystems in tumor therapy. Nowadays, stimuli-responsive nanomaterials have gained great attention in anti-tumor therapy investigation. Compared with traditional therapeutic methods, smart nanocarriers can change the carrier structure by endogenous or exogenous stimuli, which will release the encapsulated drug. It increased the biosafety and release rate of the drug, ensured it releasing at the desired point, and realized the targeted drug therapy. It also significantly improved the development of multi-drug resistance in tumors. Moreover, multifarious of stimuli-responsive nanocarriers have made significant progress in practical applications. Among them, stimulus-responsive nanocarriers such as pH, redox, enzyme, light, ultrasound, magnetism and temperature have been extensively researched in the fields of drug delivery and tumor therapy.
Generally, in intelligent stimulus-response nanosystems, different types of stimuli have different characteristics. For instance, pH stimulus-responsive nanocarriers have high sensitivity and a wide pH adjustment range. However, the complexity, heterogeneity, and uncertainty of tumorigenesis and development lead to different tumor pH values, which affect the mode of action and effect of pH stimulus-responsive nanocarriers. Of course, this difference in stimulus response factors is a common and generic problem with stimulus-responsive nanocarriers. Redox-stimulated responsive nanocarrier reactions are fastly being used for therapeutic applications such as antioxidants and tumors. Although they possess a well-defined chemical bonding reaction mechanism, the complexity of the material preparation process and its incomplete biodegradability in vivo are great challenges for such materials. Besides, enzyme-stimulated responsive polymer nanos with high selectivity and sensitivity are an excellent strategy for tumor therapy. Nevertheless, enzyme instability and the widely distributed nature of enzymes, the carrier drug may be released prematurely. Alternatively, temperature stimulus responsive nanocarriers with a wide temperature response range are not effective for single stimulus application and are suitable to be combined with other stimuli or therapies for optimal performance. Particularly, optical stimulus responsive nanocarriers have favorable selectivity and chargeability, but as mentioned earlier UV light has high energy but weak penetration, while NIR light is contrary, requiring prolonged light irradiation to achieve the targeted therapeutic effect. Consequently, light-responsive nanocarriers are suitable for the therapy of epidermal or superficial tumors, such as skin cancer.
Furthermore, despite the promising progress of smart nanomaterials in the field of tumor therapy, there are still many challenges away from practical applications.
(1) Biocompatibility and selectivity: this remains the most significant challenge. The majority of intelligent nanosystems continue to face challenges regarding their biocompatibility (toxicity associated with the materials used) as well as their limited selectivity, and thus novel/multiple approaches are imperative to adhere to the rigorous requirements in clinical environments.
(2) Mechanism clarity: most evaluations of the merits of materials have focused on their anti-tumor effects, but their anti-tumor biological mechanisms still need to be studied in greater depth, which will help to advance the understanding of tumor-anti-tumor drug-agent interactions, and to rationally develop novel and enhanced oncology agents.
(3) Pharmacogenetic and pharmacokinetic analyses: the therapeutic effects of smart nanomaterials in vivo, including selectivity and efficiency targets, biodistribution, biodegradation, and immune responses at the organ and system levels, still need to be studied in more depth.
(4) Animal experimental models: though in vitro bio-experiments could provide intelligent nanomaterials with rapid and prominent antitumor effect, and the in vitro results do not directly reflect the real situation.
(5) Clinical translational research: the establishment and advancement of various oncology smart nano-formulations are usually targeted to realize practical clinical applications, which involves the cooperation of experts from multi-disciplines.
Finally, the rapid development and explosive growth in the use of Artificial Intelligence (AI) is providing invaluable assistance in constructing predictive models of nanobio-interactions, hierarchical targeting and drug delivery efficiencies, modes of action, as well as nanomedicine safety and efficacy. Although it is still in its infancy, these tools and methods will revolutionize cancer nanomedicine in near future, at the same time, which also offering tremendous potential for improving cancer therapy.

Author Contributions

X.L.: initial draft writing, conceptualization, validation, visualization, and revision. F.H.: initial draft writing, conceptualization, validation, visualization, and revision. M.L.: conceptualization, final draft review, funding. All authors have read and agreed to the published version of the manuscript.

Funding

This work was supported by the Natural Science Foundation of Hunan Province (No. 2021JJ41008), the Scientific Research Project of Health Commission of Hunan Province (No. B202313057213, No. W20243230), the Key Project of Changsha Science and Technology Plan (No. kh2201059), and the Youth Science Foundation of Xiangya Hospital (No. 2022Q16).

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

Not applicable.

Conflicts of Interest

The authors declare no conflicts of interest.

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Figure 1. Schematic of stimulus-responsive smart nanocarriers for cancer therapy.
Figure 1. Schematic of stimulus-responsive smart nanocarriers for cancer therapy.
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Figure 2. (A) Schematic illustration of pH-responsive cRGD-Dex-DOX/HDZ nanoparticles. Reprinted with permission from [39], Copyright 2023, Wiley. (B) Schematic of the P-LDH nanosheet-based ultra-high drug delivery system. a) synthetic route of P-LDH-DOX and b) long blood circulation, intracellular delivery, and pH-responsive DOX release through P-LDH nanosheets. Reprinted with permission from [40], Copyright 2022, Wiley.
Figure 2. (A) Schematic illustration of pH-responsive cRGD-Dex-DOX/HDZ nanoparticles. Reprinted with permission from [39], Copyright 2023, Wiley. (B) Schematic of the P-LDH nanosheet-based ultra-high drug delivery system. a) synthetic route of P-LDH-DOX and b) long blood circulation, intracellular delivery, and pH-responsive DOX release through P-LDH nanosheets. Reprinted with permission from [40], Copyright 2022, Wiley.
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Figure 3. (A) Schematic representation of the preparation and disruption of redox homeostasis of a cascade-amplified self-immolating polymer prodrug (SPP@2ME) for cancer therapy. Reprinted with permission from [49], Copyright 2023, Elsevier. (B) Schematic illustration of (a) construction of dihydroartemisinin dimeric precursor drug nanoparticles (SS NPs) bridged by disulfide bond linkers and (b) and application in antitumor therapy. Reprinted with permission from [51], Copyright 2021, Springer.
Figure 3. (A) Schematic representation of the preparation and disruption of redox homeostasis of a cascade-amplified self-immolating polymer prodrug (SPP@2ME) for cancer therapy. Reprinted with permission from [49], Copyright 2023, Elsevier. (B) Schematic illustration of (a) construction of dihydroartemisinin dimeric precursor drug nanoparticles (SS NPs) bridged by disulfide bond linkers and (b) and application in antitumor therapy. Reprinted with permission from [51], Copyright 2021, Springer.
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Figure 4. (A) Schematic representation of the molecular structure and self-assembly of MMP7-sensitive peptides into nanostructures, drug loading and enzyme release processes, and use for cancer therapy. Reprinted with permission from [58], Copyright 2019, American Chemical Society. (B) Schematic representation of the preparation and in vivo administration of intracellular and extracellular enzyme-activated micelles. Reprinted with permission from [59], Copyright 2022, Springer.
Figure 4. (A) Schematic representation of the molecular structure and self-assembly of MMP7-sensitive peptides into nanostructures, drug loading and enzyme release processes, and use for cancer therapy. Reprinted with permission from [58], Copyright 2019, American Chemical Society. (B) Schematic representation of the preparation and in vivo administration of intracellular and extracellular enzyme-activated micelles. Reprinted with permission from [59], Copyright 2022, Springer.
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Figure 5. (A) Illustration for the preparation of DOX-PSGV by PSar-b-PCL block copolymers-induced self-assembly of gold NPs and the NIR light controlled drug release mechanism in vivo. Reprinted with permission from [68], Copyright 2022, Springer. (B) Schematic preparation of self-assembled X-ray responsive biomimetic nanocapsules of poly(ethylene glycol)-b-poly(thymine) -b-poly(azobenzene) (PETAzo) triblock polymer and used for cancer therapy. Reprinted with permission from [73], Copyright 2019, Wiley.
Figure 5. (A) Illustration for the preparation of DOX-PSGV by PSar-b-PCL block copolymers-induced self-assembly of gold NPs and the NIR light controlled drug release mechanism in vivo. Reprinted with permission from [68], Copyright 2022, Springer. (B) Schematic preparation of self-assembled X-ray responsive biomimetic nanocapsules of poly(ethylene glycol)-b-poly(thymine) -b-poly(azobenzene) (PETAzo) triblock polymer and used for cancer therapy. Reprinted with permission from [73], Copyright 2019, Wiley.
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Figure 6. (A) Schematic of the effective chemotherapy by inhibiting stroma and enhancing CPT penetration through US-triggered piezocatalysis and nanoprodrug strategy. Reprinted with permission from [80], Copyright 2023, American Chemical Society. (B) Schematic of stiffness-tunable GenPLPFT/EPI for deep tumor delivery, where external sonication induced a switch in GenPLPFT to a softer and larger nanogel vio pulse-triggered pluronic F127 shedding. (C) Upon sonication at tumor site, GenPLPFT/EPI transformed to a softer and larger nanogel with improved deformability for achieving deep tumor penetration. Reprinted with permission from [29], Copyright 2022, American Chemical Society.
Figure 6. (A) Schematic of the effective chemotherapy by inhibiting stroma and enhancing CPT penetration through US-triggered piezocatalysis and nanoprodrug strategy. Reprinted with permission from [80], Copyright 2023, American Chemical Society. (B) Schematic of stiffness-tunable GenPLPFT/EPI for deep tumor delivery, where external sonication induced a switch in GenPLPFT to a softer and larger nanogel vio pulse-triggered pluronic F127 shedding. (C) Upon sonication at tumor site, GenPLPFT/EPI transformed to a softer and larger nanogel with improved deformability for achieving deep tumor penetration. Reprinted with permission from [29], Copyright 2022, American Chemical Society.
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Figure 7. (A) Schematic illustration of the imaging-guided photothermally triggered immunotherapy using magnetic-responsive immunostimulatory nanoagents (MINPs) targeting both primary treated and distant untreated tumors. Reprinted with permission from [90], Copyright 2019, Elsevier. (B) Schematic illustration of the MNPs@dopamine@DOX theranostic nanoplatform for magnetic-responsive on-demand synergistic thermal-chemo therapy. Reprinted with permission from [91], Copyright 2021, Springer.
Figure 7. (A) Schematic illustration of the imaging-guided photothermally triggered immunotherapy using magnetic-responsive immunostimulatory nanoagents (MINPs) targeting both primary treated and distant untreated tumors. Reprinted with permission from [90], Copyright 2019, Elsevier. (B) Schematic illustration of the MNPs@dopamine@DOX theranostic nanoplatform for magnetic-responsive on-demand synergistic thermal-chemo therapy. Reprinted with permission from [91], Copyright 2021, Springer.
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Figure 8. (A) The design of peptidic M-PEG “comb” 1 as “add-on” module for liposomal theranostics. (B) The multifunctional theranostics liposomes L1 performed image-guided tumor treatment on the nude mouse xenograft model. Reprinted with permission from [92], Copyright 2019, Wiley.
Figure 8. (A) The design of peptidic M-PEG “comb” 1 as “add-on” module for liposomal theranostics. (B) The multifunctional theranostics liposomes L1 performed image-guided tumor treatment on the nude mouse xenograft model. Reprinted with permission from [92], Copyright 2019, Wiley.
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Figure 9. (A) Schematic illustration of the successive behaviors of the multifunctional micelle of the charge reversal PPT/D(DMA)@DOX system with self-amplifiable drug release for tumor therapy. Reprinted with permission from [105], Copyright 2020, Springer. (B) Schematic illustration of QM-NPQ@PDHNs fabrication and therapeutic mechanisms in liver cancer with overexpression of GSH and GSTπ. Reprinted with permission from [106], Copyright 2018, Wiley. (C) Schematic representation of pH/enzymatic dual-activated ZIF@Polymer nanosystems construction and their application in co-delivery of proteins and chemotherapeutic agents to improve deep tumor penetration. Reprinted with permission from [107], Copyright 2022, Wiley.
Figure 9. (A) Schematic illustration of the successive behaviors of the multifunctional micelle of the charge reversal PPT/D(DMA)@DOX system with self-amplifiable drug release for tumor therapy. Reprinted with permission from [105], Copyright 2020, Springer. (B) Schematic illustration of QM-NPQ@PDHNs fabrication and therapeutic mechanisms in liver cancer with overexpression of GSH and GSTπ. Reprinted with permission from [106], Copyright 2018, Wiley. (C) Schematic representation of pH/enzymatic dual-activated ZIF@Polymer nanosystems construction and their application in co-delivery of proteins and chemotherapeutic agents to improve deep tumor penetration. Reprinted with permission from [107], Copyright 2022, Wiley.
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Figure 10. (A) Schematic of the design of PCN-DOX@PDA and the modeling of the lethal mechanism against tumor cells. Reprinted with permission from [108], Copyright 2023, American Chemical Society. (B) Schematic illustration of the mechanism of PCMS for photothermal-enhanced cascade catalytic therapy. Reprinted with permission from [109], Copyright 2023, Wiley.
Figure 10. (A) Schematic of the design of PCN-DOX@PDA and the modeling of the lethal mechanism against tumor cells. Reprinted with permission from [108], Copyright 2023, American Chemical Society. (B) Schematic illustration of the mechanism of PCMS for photothermal-enhanced cascade catalytic therapy. Reprinted with permission from [109], Copyright 2023, Wiley.
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Figure 11. Schematic of the design of PCN-DOX@PDA and the modeling of the lethal mechanism against tumor cells. Reprinted with permission from [113], Copyright 2023, American Chemical Society.
Figure 11. Schematic of the design of PCN-DOX@PDA and the modeling of the lethal mechanism against tumor cells. Reprinted with permission from [113], Copyright 2023, American Chemical Society.
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