Currently, there is a growing use of superparamagnetic iron oxide nanoparticles (SPION) coated with a biocompatible shell in the eld of personalized medicine, namely for the detection and therapy of certain cancerous conditions. The real-time monitoring of therapy may be facilitated by the use of superparamagnetic iron oxide nanoparticles. This can be achieved by mixing SPION with various medications and afterward observing the alterations in T1 or T2 relaxation parameters [49]. In addi­tion, MNPs possess several advantageous characteristics that render them highly suitable for various disease treatments. These benets include a substantial surface area-to-volume ratio, optimal pore size, functionalized surfaces, multiple interac­tion or binding sites, and little mass transfer resistance [47]. The researchers Ngen et al. devised a magnetic nanoparticle with a particular afnity for the prostate­specic membrane antigen (PSMA). This nanoparticle was subsequently assessed in a mouse model utilizing T2-weighted magnetic resonance imaging after intrave­nous injection of 50mg/kg of the nanoparticle at the dose necessary for thermo­therapy. The study found that nanoparticles had a higher tendency to collect toward the outer edges of tumors, specically in comparison to tumors that lacked prostate­specic membrane antigen. Additionally, tumors that expressed PSMA showed noticeable elevation in contrast at both 24 and 48h after nanoparticle delivery [50]. While some magnetic nanoparticles and superparamagnetic iron oxide nanoparti­cles have received FDA approval, excessive quantities of these substances may pose risks to human health. These risks include adverse effects on several organs such as the liver, brain, skin, gastrointestinal function, and potential neurological impair­ment [35]. Hence, in the context of clinical investigations, it is imperative to take into account the physicochemical characteristics and potential toxicity of MNPs. Moreover, to ensure their safe and effective use in treatment, it is essential to imple­ment appropriate control measures and functionalize their surfaces by the incorpo­ration of diverse inorganic or organic chemicals, leading to the attainment of passivated surfaces [47].

[60]. The highly branching three-dimensional structure and presence of several functional groups in invitro cancer diagnostics contribute to an increased capture density per unit area and improved capacity to bind cancer markers. Regarding in vivo cancer diagnostics, the excellent biocompatibility and low viscosity of nanoparticles serve as the fundamental factors for their potential use in invivo set­tings [61].

The manufacture of PSMA-targeted polyamidoamine (PAMAM) dendrimer nanocarriers was described by Lesniak etal. in their study [1547]. One of the meth­ods used was a straightforward single-step synthesis to produce dendritic nanopar­ticles that were electrically neutral, had a limited variation in particle size, and possessed a diameter of around 5nm. The ndings from positron emission tomog­raphy (PET) and biodistribution studies using 64Cu-labeled dendrimer nanocarri­ers, both in vitro and invivo, demonstrated a signicant accumulation of these nanocarriers in PSMA+PC3 PIP tumors within 24hours post-injection. This obser­vation further substantiated the specic uptake of dendrimer nanocarriers by PSMA+ tumors [62]. Signicant advancements have been achieved so far in the application of dendritic polymers in the eld of therapeutic diagnostics. Nevertheless, the use of dendritic macromolecules in clinical practice is hindered by factors such as possible toxicity, bio-elimination, and long-term impacts, which are attributed to the intricate production process [63]. Nonetheless, ongoing endeavors are being made to advance the translation of dendritic polymer nanosystem-based diagnostic therapeutics from the experimental stage to practical use in clinical settings. These efforts primarily focus on enhancing the design of synthetic methods, rening pro­cedures, and implementing precise characterization processes.

phagocyte systems (MPS) [67]. The encapsulation of medicine inside a polymeric micelle fraction has the potential to signicantly enhance the drug’s water solubil­ity. This increase in solubility may range from ten-fold to 500-fold, therefore enabling the intravenous delivery of hydrophobic drugs that are encased within micelles. For instance, the water solubility of paclitaxel, a medication that is typi­cally insoluble in water, may be signicantly increased by its encapsulation inside micelles [68].