Optimizing Dacarbazine Therapy: Design of a Laser-Triggered Delivery System Based on β-Cyclodextrin and Plasmonic Gold Nanoparticles

Abstract

Dacarbazine (DB) is an antineoplastic drug extensively used in cancer therapy. However, present limitations on its performance are related to its low solubility, instability, and non-specificity. To overcome these drawbacks, DB was included in β-cyclodextrin (βCD), which increased its aqueous solubility and stability. This new βCD@DB complex has been associated with plasmonic gold nanoparticles (AuNPs), and polyethylene glycol (PEG) has been added in the process to increase the colloidal stability and biocompatibility. Different techniques revealed that DB allows for a dynamic inclusion into βCD, with an association constant of 80 M⁻¹ and a degree of solubilization of 0.023, where βCD showed a loading capacity of 16%. The partial exposure of the NH₂ group in the included DB allows its interaction with AuNPs, with a loading efficiency of 99%. The PEG-AuNPs-βCD@DB nanosystem exhibits an optical plasmonic absorption at 525 nm, a surface charge of −29 mV, and an average size of 12 nm. Finally, laser irradiation assays showed that DB can be released from this platform in a controlled manner over time, reaching a concentration of 56 μg/mL (43% of the initially loaded amount), which, added to the previous data, validates its potential for drug delivery applications. Therefore, the novel nanosystem based on βCD, AuNPs, and PEG is a promising candidate as a new nanocarrier for DB.

1. Introduction

Aging and exposure to pollutants make cancer one of the leading causes of death in the world, with 10 million deaths occurring in 2020 and projected to reach 28 million until 2040 [1,2]. Antineoplastic drugs have mechanisms of action based on interrupting cell growth or destroying them; they affect both cancerous and healthy cells [3,4]. Dacarbazine (DB) is an alkylating agent used in the treatment of several types of cancer, such as Hodking’s lymphoma, melanoma, pancreatic islet carcinoma, and sarcomas [4,5,6,7]. It has an aggressive and non-selective behavior and is classified among the antitumor drugs for which there is no exposure range considered safe; nevertheless, its consumption has increased by around 12% annually since 2004 [8,9]. The drug is highly unstable, degrading to carbene and aryl radicals, which are species involved in DNA damage, and inside the human body it produces reactive and highly toxic oxygen species. These species are also suspected to be responsible for the pain experienced by patients and for the incidence of carcinogenic, teratogenic, and mutagenic effects [10,11]. This antineoplastic has a 5-h half-life in the body and a 40% intact excretion rate in urine. Even from an ecological point of view, after biodegradation processes in wastewater treatment plants, 98.2% remains, generating a concentration of 0.1 ng/L in riverbeds, which is a serious environmental problem. [12,13]. Therefore, it is necessary to further advance the application of this drug, for example, by improving its aqueous solubility, stability, and specificity for an intelligent therapy at the site of action, ideally reducing the administered dose. In this sense, cyclodextrins (CD) and gold nanoparticles (AuNPs) have emerged as promising tools for the development of novel drug delivery nanosystems [2,14,15,16,17].

CDs are nontoxic cyclic oligosaccharides formed from 6, 7, or 8 glucopyranose units bonded via α(1−4) bonds as a truncated cone, approved by the Food and Drug Administration (FDA) for a wide range of pharmaceutical, food product, and cosmetic applications [18,19,20]. They are characterized by a hydrophilic exterior and a hydrophobic interior, working as a pocket or host for poorly soluble or reactive organic molecules, forming inclusion complexes [21,22]. The βCD, composed of 7 glucose units, is highlighted due to its appropriate dimensions to include aromatic cycle species. Hence, it has been widely studied to optimize the performance of drugs by preventing decomposition and increasing aqueous solubility [23,24]. Considering the molecular dimensions of DB and its hydrophobic regions, this drug could be included inside the non-polar internal cavity of βCD, forming a new inclusion complex [25,26]. Interestingly, some inclusion complexes present an arrangement that exposes suitable drug functional groups to interact with other materials, such as AuNPs, to add characteristics and properties that continue to contribute to the optimization of the drug in therapy [27,28,29,30,31].

AuNPs have been extensively studied in therapy and the diagnosis of cancer [2,32,33,34]. The extensive study on chemical synthesis methods allowed a high degree of control over the size and shape of the nanosystem obtained, resulting in simple, reproducible, and scalable methodologies [35,36,37]. These nanoparticles demonstrate excellent biocompatibility, interesting optoelectronic properties, and an easily functionalized surface, which leads to a promising platform for drug delivery [38,39,40,41]. The use of polymers and proteins, such as polyethylene glycol (PEG) and bovine serum albumin (BSA), are used to increase their stability and avoid opsonization of AuNPs, thus increasing their circulation time in the organism [42,43]. Due to their size and the size of blood vessels in fenestrated tissue, AuNPs accumulate preferentially in tumors due to passive targeting enabled by the enhanced permeation and retention effect (EPR) [44,45,46]. In this way, antineoplastic agents can be targeted to their specific site of action, minimizing damage to healthy tissue. Furthermore, drugs can be released in a controlled process utilizing the photothermal effect, which is the generation of local heat on the surface of the plasmonic AuNP due to their interaction with light at wavelengths close to the optical absorption maximum [47,48,49,50]. Currently, AuNPs are independently used as a therapeutic agent by triggering hyperthermia to destroy tumor cells [51]. Thus, the vectorization of DB on AuNPs could optimize its toxic profile and synergize at the therapeutic level, while the solubility and stability in water could be increased by formulating it in βCD, which allows the formation of a new nanosystem for site-specific and controlled release [51,52,53,54].

This is the first study of the inclusion of DB in βCD in a solid state, and its subsequent functionalization with AuNPs. Considering the exclusive use of biocompatible agents, PEG was incorporated into the colloidal solution, forming the new PEG-AuNPs-βCD@DB nanosystem. The understanding of the complex formation was performed using techniques including powder X-ray diffraction, NMR of 1 and 2 dimensions, scanning electron microscopy, and molecular docking. The development of the nanosystem was characterized using UV-Visible spectroscopy, DLS, Zeta potential measurements, Raman and SERS spectroscopy, and transmission electron microscopy. Validation of this nanosystem as a new nanocarrier candidate was performed by obtaining relevant pharmaceutical parameters such as the association constant, loading capacity and efficiency, and size and surface charge of functionalized nanoparticles. As a proof of concept, the release of DB was demonstrated by laser irradiation assays. Figure 1 shows a scheme of the different stages of the nanosystem’s development and its proof of concept.

We believe that the synergistic incorporation of βCD, AuNPs, and PEG could improve the formulation of DB-optimized anticancer therapy by increasing the aqueous solubility, stability, and local concentration of the drug, in addition to triggering its release at the site of action by laser irradiation.

2. Materials and Methods

2.1. Materials

Dacarbazine (C₆H₁₀N₆O) ≥ 99%, molar weight: 182.18 g/mol; β-cyclodextrin (C₄₂H₇₀O₃₅) ≥ 97%, molar weight: 1134.98 g/mol; tetrachloroauric acid (HAuCl₄*3H₂O) ≥ 99.9%, molar weight: 393.83 g/mol; sodium citrate (Na₃C₆H₅O₇) ≥ 99%, molar weight: 294.10 g/mol; and nitric acid (HNO₃) 70%, molar weight: 63.01 g/mol were provided by Sigma Aldrich (Saint Louis, MO, USA). Hydrochloric acid (HCl) 37%, molar weight: 36.46 g/mol; ethanol (C₂H₅OH) ≥ 99.9%, molar weight: 46.07 g/mol; hexane (C₆H₁₄) ≥ 99.7%, molar weight: 86.18 g/mol; and water (nanopure) were provided by Merck (Darmstadt, Germany). Methoxy PEG Thiol (CH₃O-PEG5000-SH) ≥ 95%, molar weight: 5 kDa was provided by JenKem Technology (Plano, TX, USA).

2.2. Formation of the Inclusion Complex

To form the βCD@DB complex, the saturated solutions of method [55] were used with minor modifications. A total of 96 mg of DB were dissolved in a 1:2 water ethanol solution with constant stirring at 25 °C for 1 h. In addition, 400 mg of βCD were dissolved in water with constant stirring for 2 h at room temperature. Then, both solutions were mixed with gentle and constant stirring for 1.5 h. The mixture was covered and kept motionless under a hood for 2 weeks. Crystals precipitated at the bottom of the solution and were extracted, washed, and dried before the complete evaporation of the solvents.

2.3. Loading Capacity of β-Cyclodextrin

Loading capacity was calculated from the weights of βCD and drug obtained, using Equation (1) [56].

$$Loading capacity=\frac{Weight of DB in \beta CD}{Weight of \beta CD}\times 100$$

(1)

2.4. Association Constant of β-Cyclodextrin@dacarbazine

For the βCD@DB complex, the association constant was obtained following the Higuchi and Connors method [57]. The βCD concentration versus the loaded DB concentration (calculated by the Beer–Lambert law) was plotted. The value of the slope of the graphs related the amount of βCD added to the amount of solubilized drug, indicating the degree of solubilization (DS). DS was used in Equations (2) and (3) to finally calculate the association constant (Ka_1:1) and complexation efficiency (CE) of the βCD@DB.

$$K{a}_{\left(1:1\right)}=\frac{\mathrm{DS}}{\left[\mathrm{Co}\right]\left(1-\mathrm{DS}\right)}$$

(2)

$$\mathrm{CE}=K{a}_{\left(1:1\right)}\left[\mathrm{Co}\right]=\frac{\mathrm{DS}}{\left(1-\mathrm{DS}\right)}$$

(3)

[Co] corresponds to the concentration of the free drug in absence of βCD.

2.5. Stability and Modeling of β-Cyclodextrin@dacarbazine

Conformational searches were calculated by Autodock Vina 1.1.2 software (2014) [58] (Lo Jolla, CA, USA) with the Lamarckian Genetic Algorithm (LGA), using βCD as the receptor and DB as the ligand. The structure of βCD was extracted from the crystallographic data reported in the Cambridge Crystallographic Database Nº 210,892 [59]. The parameters used for the global search were consistent with previous similar works [27,60,61], where an initial 300 individuals, 2000 maximum energy evaluations, and 10,000 maximum generations were used as a final criterion. An elitism value of 1 mutation rate of 0.02 and a crossover rate of 0.8 were used. The vacuum permittivity was set up. The amine groups were considered rotable, thus producing the flexible docking scheme. The modeling grid measures were 4 × 4 × 4 nm to cover the entire surface of βCD, which calculated the most favorable complexation positions for the system. The obtained structures of the βCD@DB complex were employed to rationalize the experimental results.

2.6. Synthesis of Gold Nanoparticles

A synthesis of plasmonic AuNPs was performed using the Turkevich method [62]. All glassware were carefully washed with aqua regia before use. A reflux system was used, and 100 mL of HAuCl₄*3H₂O 1.0 mM was added. An amount of 114.1 mg of sodium citrate was dissolved in 10 mL of water and heated at 60 °C for approximately 5 min. When reflux was achieved, a citrate solution (at 60 °C) was added under constant agitation (72 g) over 30 min. Later, the solution was cooled slowly to room temperature. The obtained AuNPs were filtered and stored at 4 °C. The concentration of AuNPs was obtained using the reported molar extinction coefficient and the Beer–Lambert equation [63,64].

2.7. Functionalization of Gold Nanoparticle with the Complex

AuNPs were functionalized with the βCD@DB complex via the exchange of citrate, which was the original stabilizer. In addition, thiolated polyethylene glycol (CH₃O-PEG-SH) was incorporated. For this, 2 mL of a 20 mg/mL aqueous solution of βCD@DB were mixed with 2.5 mL of a 9 nM aqueous solution of AuNPs and agitated for 10 min at room temperature, completely protected from light sources. Subsequently, 500 μL of a 0.420 mM aqueous solution of CH₃O-PEG-SH were added and agitated for 1 h under the same conditions. The PEG-AuNPs-βCD@DB solution that formed was dialyzed to facilitate the removal of excess citrate. For this purpose, a Spectrum™ brand cellulose exchange membrane with a pore size of 5000 d and solutions of decreasing citrate concentration down to pure water were used. The process took 2 days. Finally, the resulting colloidal solution was centrifuged at 3200 rpm and resuspended in water fixed at pH 6.5. The AuNPs-βCD@DB-PEG solution was stored at 4 °C.

2.8. Loading Efficiency of Gold Nanoparticles

Loading efficiency is the maximum amount of drug that the nanosystem can carry. To calculate it, the amount of DB detected in the supernatant after functionalizing the AuNPs with the βCD@DB complex was subtracted from the amount of DB initially available, using Equation (4) [56].

$$Loading efficiency=\frac{Weight of DB in \beta CD@DB loaded to the AuNP}{Weight of DB in \beta CD@DB added}\times 100$$

(4)

2.9. Equipment and Methodology for the Characterization

A crystallographic analysis was performed by the powder X-ray diffraction technique (PXRD) using a Siemens D-5000 diffractometer (Munich, Germany) with graphite-monochromated Cu K-α radiation at 40 kV and 30 mA with a wavelength of 1.540598 Å.

SEM micrographs were obtained using a LEO 1420 VP (Oberkochen, Germany) with a coupled energy dispersive analysis instrument, model Oxford 7424, at an accelerating voltage of 25 kV. For FE-SEM imaging, a Zeiss Leo Supra 35-VP model (Oberkochen, Germany) was used with accelerating voltages of 15 kV and 20 kV. A coating with gold using magnetron sputtering in high vacuum was necessary to improve the conductivity of the samples and avoid their polarization. For βCD and DB, 100s of metallization were performed and for βCD@DB, 20s of metallization were performed.

Nuclear magnetic resonance of 1 and 2 dimensions (¹H and ROESY, respectively) was performed using Bruker Advance 400 MHz equipment (Billerica, MA, USA) at 300 K, with TMS as the internal reference and DMSO-d₆ as solvent. Specifically, the ROESY technique was performed using the pulsed field selected gradient method for 24 h. The processing of the data obtained was performed using the MestRec software (Santiago de Compostela, Spain).

For UV-visible spectrophotometry measurements, PerkinElmer Lambda 25 UV equipment (Waltham, MA, USA) was used with 1-cm-diameter quartz cuvettes in a wavelength range between 200 and 800 nm.

To determine the average particle size and its distribution, high-resolution transmission electron microscopy (HRTEM) was performed using a JEOL 2000FX TEM microscope (Akishima, Tokyo, Japan) at 200 kV, and transmission electron microscopy (TEM) was performed using a JEOL JEM 1200 EX (Akishima, Tokyo, Japan) with an accelerating voltage of 80 kV. The samples were prepared by depositing 10 μL of solution on a copper grid with a continuous formvar film and were slowly dried by exposure from an IR lamp.

Dynamic light scattering (DLS) and Zeta potential techniques were performed using Malvern ZetaSizer Nano ZS equipment (Malvern, Malvern, United Kingdom) with a capillary cell with gold electrodes.

Raman spectra were obtained from the direct measurement of the samples in the solid and aqueous states, using a Renishaw Ramanscope 1000 (Wotton-under-Edge, United Kingdom), excited with a 632.8 nm He-Ne laser. IR spectra were obtained using a Perkin Elmer 2000 (Waltham, MA, USA) with KBr pills. To interpret the results of the IR and Raman spectra, calculations with the PhEA molecule were performed using Gaussian 09, revision D.01 [65], using density functional theory at the B3LYP/6- 311 + G(d,p) level of theory in the gaseous state. Geometry optimization and frequency calculations, including Raman activity, were requested.

2.10. Drug Release Studies Using Laser Irradiation

The laser used was provided by Power Technology, Inc. The wavelength was 532 nm, with a beam diameter of 1 mm and 45 mW of power. In a quartz cuvette, an aqueous phase and an organic phase were disposed of, adding 300 μL of hexane and 300 μL of the PEG-AuNPs-βCD@DB nanosystem in water, isolated from external light sources. First, the passive diffusion of the drug from the nanosystem into the organic phase was studied. Then, the aqueous phase is irradiated for 15, 30, 45, and 60 min, measuring the absorbance of DB in hexane at each interval. After calculating of the molar extinction coefficient (ε = 10.93 mM·cm⁻¹ at 237 nm), the maximum absorbance obtained in the characteristic region of DB in an organic medium in each assay was converted into mass by using the Lambert–Beer law. The mass released by diffusion was subtracted from the total loaded mass to obtain the mass susceptible to being released by laser irradiation.

3. Results and Discussion

3.1. Dacarbazine Loading into β-Cyclodextrin Forming the New β-Cyclodextrin@dacarbazine Complex

The drug loading in native βCD was performed using the saturated solutions method, obtaining a precipitate that corresponds to the βCD@DB complex, which was characterized using PXRD and SEM. Figure 2 shows the diffractograms and micrograph for βCD, DB, βCD@DB, and the diffractogram of the physical mixture between βCD and DB.

Peaks at 4°, 6°, 8°, 9°, 13°, and 20° (2θ) of βCD associated with a P-type monoclinic conformation [66], and peaks at 11°, 17°, 22°, 26°, and 27° (2θ) of DB associated with a monoclinic structure of a P2_1/n group [67,68], disappeared when the βCD@DB complex was formed. Instead, in the diffractogram of the βCD@DB system appear new peaks, specifically at 10°, 15°, 19°, 23°, and 25° (2θ), that are characteristics of aromatic rings included in βCD matrices [69,70]. The permanence of other peaks corresponding to βCD, in the diffractogram of βCD@DB, reveal the influence of this matrix on the crystalline packing of the complex, while the defined peaks of the DB pattern that disappear in the complex reveal the effective inclusion of the drug. Therefore, crystalline packing arrangement of the complex was different compared to the pure species and represents a new crystalline phase. The physical mixture corresponds to a superposition between the traces of the pure species, confirming that this procedure does not generate interactions that disturb the crystal lattice of any of them (more details in Figure S1, in Supplementary Materials, Section S1).

Different morphologies of βCD, DB, and βCD@DB were observed in SEM micrographs, which reveal that the inclusion phenomenon generates a new crystalline arrangement of the βCD units when the drug is housed in its cavity. Considering that SEM imaging requires the metallization of organic compounds, the complex was covered by gold for 20 s, being a substrate with a higher affinity for this metal than the pure species, which require 100 s of metal deposition. Added to the above, the crystal length analyses show that the βCD@DB complex formation method allows obtaining solid structures that are 13 and 10 times larger compared to the sizes of pure βCD and DB, respectively (additional SEM micrographs, together with size analyses, are detailed in Figure S2 and Table S1 in the Supplementary Materials, Section S1).

Subsequently, a study about the host-guest interactions and stoichiometric ratio of the βCD@DB complex in solution was performed using proton nuclear magnetic resonance (NMR) spectroscopy.

Table 1. Proton assignments and ¹H-NMR chemical shifts of βCD, DB, and βCD@DB.

Proton	δβCD (ppm)	δβCD@DB (ppm)	Δδ (ppm)	Proton	δDB (ppm)	δβCD@DB (ppm)	Δδ (ppm)
-H3	3.648	3.657	0.009	-NH	12.617	12.591	−0.026
-H5	3.555	3.561	0.006	-CH3′	3.518	3.504	−0.014
-H6	3.617	3.623	0.006	-CH3′’	3.131	3.126	−0.005
-OH2	5.735	5.711	−0.024	-CH	7.527	7.520	−0.007
-OH3	5.680	5.662	−0.018	-NH2a,b	7.451	7.416	−0.035
-OH6	4.479	4.436	−0.043		7.307	7.294	−0.013

shows the chemical shifts of βCD and DB protons resulting from the inclusion process. ¹H-NMR spectra of all species, along with proton assignment, are shown in Figure S3 in the Section S2 of the Supplementary Material.

Protons that are oriented towards the interior of the βCD cavity (H3, H5, and H6) and those close to its openings (OH2, OH3, and OH6) can present chemical shifts due to the inclusion phenomenon [21,71]. Shifts towards lower fields of the H3, H5, and H6 proton signals were observed due to interactions with the highly electronegative atoms of DB. In turn, shifts towards higher fields of the proton signals present in all the hydroxyl groups were observed, probably due to the shielding effect produced by the inclusion of the drug. On the other hand, the shift of the DB proton signals towards higher fields is due to an increase in nearby electron density. This confirms the effective inclusion of the drug in βCD [17,27,28,29]. The stoichiometry of the complex was obtained by comparing the integrals for H1 of βCD regarding CH₃′, CH₃′′, CH, and NH of DB, obtaining a stoichiometric ratio of 1:1 (see the details in Figure S4 and Table S2 in the Supplementary Materials, Section S3).

Rotational Overhauser Enhancement Spectroscopy (ROESY) complemented with theoretical molecular docking were used to study the interactions and geometry of DB loading [72]. Zoom sections of the two-dimensional spectrum of the βCD@DB complex (a and b) and the most stable conformation obtained by docking (c and d) are shown in Figure 3 (full spectrum in Figure S5 in the Section S4, Supplementary Materials).

Figure 3a–c reflects the interactions between the protons of DB with the internal protons (H3, H5, and H6) and with the protons of the secondary hydroxyls (OH2 and OH3) of βCD. Crossed peaks between CH₃′ and CH₃′′ with H5 and H6, together with crossed peaks between NH₂ and CH with H5 mainly, corroborate the effective inclusion of the drug. The orientation of the guest molecule could be elucidated by the interactions observed between CH and the secondary hydroxyl groups, which would indicate that the region of the imidazole ring is included and oriented towards the wider opening; therefore, the region of the primary amide and methyl groups are oriented toward the narrower opening of βCD. In this sense, molecular modeling is frequently used to support the structural elucidation of inclusion complexes [61,73]. Figure 3d,e corresponds to a theoretical arrangement of DB in the matrix; here the complete inclusion of the drug was observed, with specific interactions between the protons of the CH₃ groups with H5 and H6, and the protons of the CH groups with H3, H5, and secondary hydroxyl groups, confirming a dynamic inclusion of DB, which is oriented towards the narrower opening of βCD.

Finally, to determine the pharmaceutical parameters of relevance, DS, CE, and Ka, the phase solubility method was used [57]. The solubility graph indicates that the formation kinetics correspond to an AL type diagram, confirming a 1:1 stoichiometry inclusion compound, which represents a βCD loading capacity of 16% for DB (see the details in Figures S6 and S7 in the Supplementary Materials, Section S5). An increase in the aqueous solubility of the drug was observed with increasing concentrations of βCD. The DS value for the complex was 0.023; the CE was 0.024; and Ka was 80 M⁻¹. These data constitute the basis for evaluating the feasibility of a future pharmaceutical formulation. In general, values greater than 2000 M⁻¹ indicate a limitation in the pharmaceutical formulation, such as poor pharmacokinetics, since the drug release rates can be affected. Meanwhile, Ka with lower values of 50 M⁻¹ also present limitations since they have low stability and do not release the drug at its site of action [74]. In this sense, to ensure the permanence of the drug in the transport system, the use of AuNPs becomes relevant. It has previously been reported that the presence of AuNPs interacting with the βCD-drug complex can decrease the degree of dissociation of the drug in solution, controlling its release by means of a stimulus such as laser irradiation [29].

It is known that AuNPs can absorb the energy emitted by an external source, such as a laser, which is subsequently released in the form of heat together with the molecules that are close to its surface as another consequence of this photothermal effect [34,75,76]. Notably, this has been demonstrated for a drug included in AuNPs- and βCD-based systems using laser irradiation [29,31]. Therefore, in addition to generating localized hyperthermia, AuNPs are therapeutic agents, especially in cancer, where they also act as nanocarriers for the antitumor drug, which can be released if localized energy is irradiated.

3.2. Functionalization of Gold Nanoparticle Surface with β-Cyclodextrin@dacarbazine Complex

To form the nanocarrier based on AuNPs, they were synthesized following the Turkevich method [62], and then, the citrate ligand was exchanged for the βCD@DB complex. To increase the colloidal stability of the system, CH₃O-PEG₍₅₀₀₀₎-SH molecules were incorporated, forming the new PEG-AuNPs-βCD@DB nanosystem. The AuNPs obtained and functionalized in their different stages were characterized by UV-vis spectroscopy, dynamic light scattering (DLS), Zeta potential, and transmission electron microscopy (TEM). Figure 4 shows the UV-VIS spectra of AuNPs-citrate, AuNPs-βCD@DB, and PEG-AuNPs-βCD@DB, and HR-TEM micrographs of AuNPs stabilized with PEG and βCD@DB system. In addition,

Table 2. Wavelengths of the maximum absorbance (λ_max), hydrodynamic diameter (D_H), polydispersity index (PDI), surface charge, and diameter according to TEM for AuNPs with different stabilizers.

Nanosystem	λmax (nm)	DH (nm)	PDI	Surface Charge (mV)	TEM Diameter (nm)
AuNPs-citrate	523	45 ± 11	0.33	−43 ± 4	12 ± 4
PEG-AuNPs-βCD@DB	525	65 ± 25	0.41	−29 ± 4	12 ± 3

shows the results obtained from the different techniques used in these nanosystems.

A bathochromic displacement at 525 nm of the plasmon of the AuNPs was observed when citrate was replaced by the PEG-complex as stabilizer due to the new interaction of the electrons of the nanoparticles with functional groups SH (from PEG) and NH₂ (from DB in βCD), as has been reported [28,45,77]. In addition, an increase in hydrodynamic diameter from 45 to 65 nm and PDI from 0.3 to 0.4 for the PEG-AuNPs-βCD@DB system comparing to AuNPs-citrate was observed using DLS. This increase in the solvation sphere was attributed to the replacement of citrate by PEG and βCD@DB, which have greater size and mass. In this sense, the change in surface charge from −43 mV to −29 mV corroborates the effective exchange of the stabilizer. HR-TEM images of the PEG-AuNPs-βCD@DB nanosystem show the spherical shape of the nanoparticles with an average diameter of 12 nm, which is the same as for the as-synthesized AuNPs using citrate. These results confirm that the plasmonic and superficial properties’ changes can be attributed to the replacement of the stabilizer without a process of aggregation or interparticle coupling occurring (see the details in Supplementary Materials, Section S6). After the PEG-AuNPs-βCD@DB purification process, the drug content of the extracted supernatant was analyzed to evaluate the loading efficiency of the AuNPs. According to this, 99% of the initial mass of DB remains in the βCD@DB complex loaded to the nanosystem. This reaffirms that the drug, previously included in βCD, is interacting with the surface gold atoms of the nanoparticles (see Table S3 in Supplementary Materials, Section S6).

The inclusion phenomenon of DB in βCD and its interaction with AuNPs generate changes in the vibrational modes of the constituting molecules, which are associated with modifications in the intensity or spectral position of their signals in the Raman spectrum. Next, the Raman and SERS techniques were used to study the disposition and interaction of the drug loaded in the nanosystem. Figure 5 shows the Raman spectra of DB, βCD, βCD@DB, and PEG-AuNPs-βCD@DB. The DB vibrational mode assignments in the Raman spectra are attached in Table S4 in Section S7, Supplementary Materials.

In the DB spectrum, signals at 325, 540, 1210, 1547, and 1592 cm⁻¹ associated with vibrational modes of azide and amide can be observed. These signals were also observed in βCD@DB spectra. The signal at 1372 cm⁻¹ in the DB spectra, associated with the imidazole bending and azide stretching, shows a splitting in βCD@DB spectra, suggesting that the chemical environment was different for both sections, probably because the imidazole was found interacting with the βCD interior while the azide was arranged outward. The loss of the remaining DB signals in the βCD@DB spectrum was due to the vibrational restraint caused by the inclusion phenomenon. This effect was also supported by the IR spectroscopy analysis (see the details in Figure S12 in Section S7, Supplementary Materials).

On the other hand, in the SERS spectrum of PEG-AuNPs-βCD@DB, amplified signals of DB were observed at 713 and 754 cm⁻¹, associated with N-C-O scissoring and C-N azide in-plane bending, as well as signals at 1286 and 1314 cm⁻¹, associated with imidazole in-plane vibrations. In particular, the C=O stretching signal at 1712 cm⁻¹ appears in PEG-AuNPs-βCD@DB but not in the DB spectrum. The decrease of signals at 1372, 1492, and 1527 cm⁻¹, associated mainly with imidazole, azide, and N-(CH₃)₂ out-of-plane vibrations regarding DB spectra, was observed in conjunction with the loss of signals at 1210 and 1592 cm⁻¹, associated principally with NH₂. These changes suggest that the dynamic inclusion of DB in βCD, discussed in ROESY and docking, allows its mobility and orientation to suit its interaction with the gold surface. A perpendicular arrangement regarding the molecular plane of DB on the AuNPs’ surface through its interaction via the NH₂ group was proposed [17,78]. Notably, the signal in the 130 cm⁻¹ sector suggests the formation of the thiol-gold bond of the PEG used as a stabilizer [79,80].

3.3. Dacarbazine Controlled Release Using Laser Irradiation

The photothermal effect of AuNPs has been widely studied for controlled drug release and to produce hyperthermia, which effectively and locally kills cancer cells [29,31,32,47,81,82]. This effect can be generated by the application of energy from an external light source with a suitable wavelength and intensity, such as a laser. As a proof of concept, the controlled release of DB triggered by laser irradiation onto AuNPs present in the nanosystem was tested. Figure 6 shows the amount of DB mass released at different time intervals and the total using a continuous laser at 532 nm.

A two-phase system consisting of an aqueous phase with PEG-AuNPs-βCD@DB and an organic phase was developed. In the latter, the drug is expected to diffuse almost freely after its release from the nanosystem due to its mainly non-polar character. First, a passive diffusion of 2 μg was observed. This was subtracted from the total to highlight only the stimulated release. Then, laser irradiation triggers the release of DB from the nanosystem, reaching 3.4 μg after 15 min. A tendency to increase the amount of DB released as a function of time was established, achieving a maximum release of 4.8 μg from 45 to 60 min of laser irradiation. Subsequently, a total release of 16.7 ± 3.9 μg was obtained after 60 min of irradiation, which corresponds to 42.9 ± 4.1% of the total DB loaded in the nanosystem; this represents a concentration of 55.7 μg/mL (see the details in Table S5 in Section S8, Supplementary Materials). The release profile and the times involved were equivalent to previous reports on molecules released from systems based on cyclodextrins and AuNPs [29,31]. Considering the cytotoxicity of DB expressed in terms of IC50 (the drug concentration required for killing 50% of the B16F1 mouse melanoma cancer cell line), the value that has been reported is 0.48 mg/mL [83], hence the amount released from the nanosystem may be adequate. Accordingly, the laser-triggered controlled release of DB from the PEG-AuNPs-βCD@DB nanosystem could reach optimized concentrations at the site of action compared to free DB. Thus, it is proposed that the PEG-AuNPs-βCD@DB system may be a promising candidate for use in cancer therapy.

4. Conclusions

The new inclusion complex between DB and βCD in a solid-state was successfully obtained. DB presents a dynamic inclusion into βCD, remaining stable in solution in a 1:1 ratio. Notably, βCD shows a loading capacity of 16% with a suitable association constant and an increase in its aqueous solubility. These pharmaceutical parameters facilitate its projection and comparison with other possible complexations of DB.

In turn, citrate-coated AuNPs with an average diameter of 12 nm were obtained, which are suitable for applications in biological systems. Subsequently, the citrate molecules were effectively exchanged by the βCD@DB complexes and PEG, resulting in a new nanosystem that was stable over time and had a high loading efficiency.

Laser irradiation assays showed that the PEG-AuNPs-βCD@DB nanosystem is able to release drug in a controlled manner through the excitation caused by an incident electromagnetic wave, confirming the generation of the surface plasmon resonance effect and having a total average release amount corresponding to 43% with respect to the mass of DB contained in the nanosystem. According to the above, it is understood that the DB loading in this new nanocarrier based on βCD and AuNPs has the potential to be tested in biological systems as an alternative improvement to current cancer treatments. Studies of DB loaded to the new nanosystem, such as evaluation of cytotoxicity, membrane permeability, and therapeutic potential in in vitro and in vivo cancer models, are considered necessary to continue with the validation of this strategy for drug delivery applications.