An Improved Biocompatible Probe for Photoacoustic Tumor Imaging Based on the Conjugation of Melanin to Bovine Serum Albumin

: A novel, highly biocompatible, well soluble melanin-based probe obtained from the conjugation of melanin macromolecule to bovine serum albumin (BSA) was tested as a contrast agent for photoacoustic tumor imaging. Five soluble conjugates (PheoBSA A-E) were synthesized by oxidation of dopamine (DA) in the presence of variable amounts of BSA. All systems showed the similar size and absorbance spectra, being PheoBSA D (DA:BSA ratio 1:2) the one showing the highest photoacoustic e ﬃ ciency. This system was then selected for the investigations as it showed a marked enhancement of the photoacoustic (PA) contrast in the tumor region upon iv injection. Biodistribution studies conﬁrmed the accumulation of PheoBSA D within the tumor region and showed fast renal elimination, lack of cell toxicity, and good hemocompatibility. A higher PA contrast enhancement was observed in the case of PC3 prostate tumor xenograft when compared to the TS / A breast one, likely reﬂecting di ﬀ erent vascularization / extravasation properties between the two tumor murine models. The improved PA properties shown by PheoBSA D allowed to set up a 3D dynamic contrast-enhanced (DCE) approach that demonstrated a persistent increase of the PA signal in the tumor region for a long period. Overall, the herein reported results demonstrate that PheoBSA D is a promising blood pool contrast agent for in vivo PA imaging, particularly useful for the set-up of 3D DCE-PA approaches to monitor tumor vascular properties.


Introduction
PhotoAcoustic Imaging (PAI) contrast is based on laser-generated ultrasounds [1], featuring concurrently the contrast ability of optical imaging and the high spatial resolution and penetration depth of ultrasounds [2]. Several endogenous molecules (i.e., hemoglobin, melanins, and lipids) have a unique optical absorption spectrum in the NIR region [3] and are exploited in multispectral optoacoustic tomography to detect cancer pathological transformations, for example in the visualization of the tumor-associated changes in blood oxygenation, flow, perfusion, and vascular permeability [4][5][6][7].
Melanin signal has been exploited to assess the metastatic status of the sentinel lymph node in melanoma patients [8].
The contrast enhancement shown by endogenous molecules has inspired the design of exogenous PAI contrast agents (CAs) [9,10]. The PAI-CAs allow to get improved contrast between anatomical structures and provide specific physiological information [11][12][13]. To date, exogenous PAI contrast agents are based on several platforms, including small-molecule dyes like indocyanine green [14][15][16], eventually confined in silica nanoparticles [17,18], carbon nanoparticles [19][20][21], gold nanostructures [22][23][24][25][26], iron-based nanosystems [27], pyrroles [28,29] and biodegradable particles [30]. All these newly developed CAs have been exploited for assessing several properties of the cancer microenvironment [31][32][33][34][35]. As for other medically oriented applications of exogenous nanoparticles, biocompatibility and toxicity issues may hamper the use of nano-sized PAI CAs towards their clinical translation. In fact, although they can be highly specific and provide good contrast, they often show slow renal clearance and may accumulate non-specifically in the mononuclear phagocyte system [36]. Accordingly, the design of less toxic nanoparticles based on endogenous molecules or optically active biodegradable materials attracted much attention in the last few years [10,30].
Melanin is a ubiquitous natural biopolymer found in skin, hair, eyes, and other tissues and it was early recognized as a source of optoacoustic imaging response since it displays a marked absorption over a large spectral region [8,[37][38][39]. Melanins can be classified into four major categories [40] based on involved precursors, their color and distribution, namely (i) black to brown eumelanin derived from S-3,4-dihydroxyphenylalanine (L-dopa) consisting of oligomers of 5,6-dihydroxyindole (DHI) and 5,6-dihydroxyindole-2-carboxylic acid (DHICA) as main constituents; (ii) reddish to light brownish pheomelanin containing benzothiazine and benzothiazole units resulting from the oxidative polymerization of 5-S-cysteinyl-dopa or 2-S-cysteinyl-dopa [41]; (iii) allomelanin (mainly present in fungi and other microorganisms) obtained from the oxidation of catechols and 1,8-dihydroxynaphtalene; (iv) neuromelanin (NM), a complex macromolecular pigment found primarily in dopaminergic neurons of the human substantia nigra (SN) of the central nervous system. Although the precise structure of this biopolymer is not well known, it is thought to be a mixture of eumelanin and pheomelanin obtained by autoxidation of dopamine (DA) by iron to form DA-quinone, with the possible participation of 5-cysteinyl-catechol derivatives [42].
Several PAI contrast agents based on melanin-like nanoparticles (MNPs) have been already reported in the literature. These nanosystems were prepared from synthetic melanin granules [43] or from the oxidation of dopamine to yield size-controllable MNPs able to form sufficiently stable suspensions in water and biological media [44][45][46][47][48][49][50][51][52]. A common aspect of all these approaches dealt with the need for introducing chemical modifications aiming at improving their overall hydrophilicity. In this work, we tackled the same task by developing a melanin biopolymer obtained by the autoxidation of DA in the presence of different amounts of bovine serum albumin (BSA). The selected conjugate was tested as a PAI contrast agent for assessing tumor vascularization in mice.

Synthesis of Melanin-BSA Conjugates and PheoBSA-FITC Conjugates
Dopamine hydrochloride, Bovine Serum Albumin (BSA), Potassium phosphate monobasic KH 2 PO4, Dibasic potassium phosphate K 2 HPO4, sodium hydroxide NaOH, Fluorescein isothiocyanate (FITC) were purchased by Sigma-Aldrich (Steinheim, Germany). The melanin-BSA conjugates were prepared by autoxidation of dopamine in the presence of the protein (Figure 1). To obtain water-soluble eumelanin-BSA conjugates (EuBSA), 450 mg of DA and BSA in the amounts necessary to give stoichiometric ratios of 1:2 and 2:1 (w/w) were allowed to react in air in 200 mL of 50 mM phosphate buffer, pH 7.4, at 37 • C while protected from light. The conjugates between pheomelanin and BSA (PheoBSA) were prepared similarly, through the autoxidation of 450 mg of DA in the presence of cysteine (DA:Cys molar ratio 5:1) and BSA in the same proportions as above, DA/BSA = 1:2 and 2:1 (w/w) and in the proportions 1:1 (w/w), in 200 mL of 50 mM phosphate buffer, pH 7.4. These solutions were allowed to react in the air at 37 • C while protected from light. The obtained conjugates were dialyzed for two days using tubing with a 12 kDa cutoff against Milli-Q water that was replaced three times to eliminate unreacted DA and small DAQ (dopaminoquinone) oligomers that were not bound to BSA. The dialyzed conjugates were then lyophilized to obtain brown-black solids. A summary of the various melanin-BSA conjugates that were prepared is given in Table S1 (Supplementary Material). They are named A, B, C, D, E according to the initial ratios of the reagents employed during their preparation and to the reaction time. The lyophilized samples were dissolved in Milli-Q water to make a stock solution of 10 mg/mL. To conjugate FITC to Pheo-BSA-D (PheoBSA-FITC), 8 mg of PheoBSA D was dissolved in a solution of sodium carbonate 0.1 M (pH = 9.4) and then fluorescein isothiocyanate in DMSO (1 µmol, 1 mg/mL, 0.4 mL) was added. The reaction was stirred at room temperature in the dark for 8 h. The solution was dialyzed against water to eliminate unreacted FITC and then lyophilized and stored at 4 • C. The fluorescein bounded to Pheo-BSA D was quantified spectrophotometrically by measuring the absorbance intensity of the PheoBSA-FITC dissolved in water (0.2 mg/mL) at 495 nm against Pheo-BSA D as blank. For the calibration curve, standard solutions of FITC (1 µM to 10 µM) were prepared in water starting from 250 mg/L of fresh solution of FITC in sodium carbonate 0,1 M ( Figure S2). To confirm that the labeling procedure did not affect the fluorescent properties of FITC, excitation and emission spectra of PheoBSA-FITC solution were measured by a high-resolution spectrofluorometer FluoroMax-40 (Horiba Jobin Yvon, New York, NY, USA). The fluorescence emission spectrum was obtained by setting 485 nm as the excitation wavelength and acquiring the fluorescent signal in the range between 495 and 600 nm. The fluorescent excitation spectrum was obtained exciting the sample in the range between 350 and 510 nm and setting 520 nm as emission wavelength ( Figure S3).
Appl. Sci. 2020, 10, x FOR PEER REVIEW 3 of 13 obtained conjugates were dialyzed for two days using tubing with a 12 kDa cutoff against Milli-Q water that was replaced three times to eliminate unreacted DA and small DAQ (dopaminoquinone) oligomers that were not bound to BSA. The dialyzed conjugates were then lyophilized to obtain brown-black solids. A summary of the various melanin-BSA conjugates that were prepared is given in Table

Cell Line and Animal Models
Murine macrophagic cells (J774A.1) and human prostate cancer cells (PC-3) were supplied by ATCC. Spontaneous breast cancer cell line from a BALB/c mouse (TS/A) was kindly provided by Prof. Federica Cavallo, University of Torino, Torino, Italy. J774A.1 cells were cultured in DMEM high glucose medium, PC-3 cells were cultured in Ham's F-12K, TS/A cells were maintained in RPMI 1640, all media were supplemented with 10% FBS, 2 mM glutamine, 100 IU/mL penicillin, and 100 µg/mL streptomycin. For the preparation of the prostate tumor model, athymic nude mice (aged 6 weeks and weighted 18-22 g) were purchased from Harlan Laboratories. To these mice, a suspension of 5 × 10 6 PC-3 cells in 0.15 mL Phosphate Buffer Solution (PBS) was subcutaneously injected at the right flank of each male mouse. Imaging experiments were carried out approximately 21 days after cell implantation. For the preparation of the TS/A tumor model, 2.5 × 10 5 cells in 0.15 mL PBS were inoculated subcutaneously at the right flank of each wild-type female BALB/c mice, purchased from Charles River Laboratories. All the procedures involving the animals were conducted according to the national and international laws on experimental animals (L.D. 26/2014; Directive 2010/63/EU). For the optical imaging studies, all animals were maintained with VRF1 (P) sterile diet, in pellets (ø 12 mm), by SDS (Special Diets Services Ltd., Witham, England), up to the end of the acclimation period (five days). A special diet aimed at reducing auto-fluorescence, AIN-76a rodent irradiated diet, manufactured by Research Diets (New Brunswick, NJ, USA), was then used until the end of the experiment.

In Vitro Characterization of Melanin-BSA Conjugates
UV/Vis spectra were recorded on Jenway 6715 (Staffordshire, UK) UV/Vis (spectral window: 400-1000 nm). The hydrodynamic sizes of the conjugates were determined by dynamic light scattering (DSL) using a 90 Plus particle size analyzer (Malvern, Zetasizer). The protein content of the BSA conjugate D was obtained by NMR analysis as described by Casella [53]. Shortly, 10 mg of PheoBSA D was added to a solution of 4 mL of 6 M hydrochloric acid for protein hydrolysis. The solution was sealed and heated at 110 • C for 24 h. After cooling, the mixture was evaporated and then dissolved in 1 mL of deuterium oxide and centrifuged to remove the insoluble melanic portion. The supernatant was collected and a standard solution of 0.3 M sucrose in D 2 O was added to achieve a final concentration of 3 mM. The 1H NMR spectra of the hydrolyzed conjugates were recorded on a Bruker (Rheinstetten. Germany) AVANCE 600 spectrometer, accumulating 16 scans.
The photoacoustic signal was evaluated in vitro by a VevoLazr 2100 (Visualsonics, Fujifilm, Toronto, ON, Canada). In the VevoLazr 2100 system, light is generated by a tunable laser (flashlamp-pumped Q-switched Nd:YAG laser with an optical parametric oscillator and second harmonic generator; wavelength range: 680-970 nm; pulse duration 7-10 ns; laser pulse rate 20 Hz) and delivered through fiber optic bundles integrated into a 256-element linear array ultrasonic detector (LZ250 characterized by a broadband ultrasound frequency in the range of 13-24 MHz, center frequency 21 MHz), producing an axial resolution of 75 µm and a lateral resolution of 165 µm. Data acquisition time is 0.2 s/wavelength. Photoacoustic spectra were acquired in the range from 680 nm to 970 nm with a step size of 5 nm, and persistence of 3. The scanning time of the whole spectrum is less than 60 s. To register the photoacoustic spectra the solution was loaded in polyethylene tubes (PE-100) embedded in solidified agar (1% w/v, in milliQ water). An acoustic gel was used as a coupling agent between the ultrasound transducer and the phantom. Agar-based phantoms were used for PAI analysis with the VevoLazr PAI system, with several tubes inserted into each phantom. In each tube different concentrations were used (2.5 mg/mL, 5 mg/mL, 10 mg/mL) of A, B, C, D, and E specimens. Photoacoustic signals at 730 nm were plotted vs. dye concentration to evaluate photoacoustic efficiency and the slopes were compared.

Cell Viability Assay
To evaluate the cytotoxic effect of PheoBSA D, a CellTiter-Blue Cell Viability Assay (Promega Corporation, Durham, NC, USA) was performed. J774 (10 × 10 3 ) cells were plated in 96-well culture plates and treated with different concentration of PheoBSA D (ranging from 0.5 mg/mL to 10 mg/mL) for 24 h. Then, cells were washed with PBS, and CellTiter-Blue reagent was added to each well following manufacturer instructions. Fluorescence was measured at 560Ex/590Em using a 96-well plate reader. Each assay was repeated at least three times. Data are presented as the percentage of viable cells normalized to their respective controls.

PheoBSA-FITC In Vivo Biodistribution Test
PheoBSA-FITC (300 µL/mouse of 2 mg/mL solution) was administered intravenously (IV) to PC-3 tumor-bearing animals when the tumors reached approximately 150-200 mm 3 . Mice were anesthetized under 3-4% Sevoflurane gas anesthesia (O 2 97.0-96.0%) and euthanized by cervical dislocation 4 h (n = 3) and 24 h (n = 3) after injection. Tumors and main organs (liver, brain, kidneys, spleen, heart, lungs, and muscle) were then excised for ex-vivo fluorescent signal measurement. The optical imaging experiments were performed on an IVIS Instrument SPECTRUM (Perkin Elmer Italia S.p.A.), equipped with a CCD camera and irradiated with filtered light of wavelength 500 nm (bandwidth of 30 nm) and light of emission intensity was collected at 540 nm (bandwidth of 20 nm). ROIs corresponding to the entire organ were selected by an operator over harvested tissues. The signal intensity within the ROIs were determined automatically by the software and tissue biodistribution was evaluated.

Synthesis and Characterization of Melanin-BSA Conjugates
The spontaneous oxidation of DA yields an untreatable, insoluble polymeric material (synthetic melanin or eumelanin). When DA oxidation is carried out in the presence of enough BSA equivalents, water-soluble melanin-BSA conjugates could be obtained. Melanin-BSA was prepared according to a modified version of a reported procedure [53], through the autoxidation of dopamine (Figure 1). The quinone compounds formed by the oxidation of DA react with the nucleophilic groups present in the protein (cysteine, histidine, lysine) and the growing melanic oligomers remain covalently linked to the protein, generating eumelanin-type conjugates (EuBSA). PheoBSA-type conjugates were prepared under the same conditions from dopamine and L-cysteine (DA:Cys molar ratio of 5:1). Different melaninBSA conjugates were prepared by varying the ratio DA/BSA w/w (2:1; 1:1; 1:2) and the time of reaction as reported in Table S1 (Supplementary Material). After dialysis and lyophilization, the solubility of the conjugates was tested by adding 10 mg of solid powder to 1 mL of water. The solubility of the conjugates depends on the ratio between the melanic and protein contents, which reflect the used ratio of DA/BSA w/w reagents and the applied reaction time. Conjugates A, B, C, D, E resulted to be well soluble at the tested concentration of 10 mg/mL. Most of them were prepared in the presence of cysteine, and hence are classified as Pheo-BSA conjugates, with smaller DA oligomers bound to the protein.
Each melanin-BSA conjugates displayed the typical absorption profile of melanin extending from the UV to the visible range (Figure 2A). Their sizes (diameter) were as follows: 18.8 ± 0.5 nm (conjugate A); 2.3 ± 0.5 nm (conjugate B); 5.3 ± 0.5 nm (conjugate C); 5.2 ± 0.5 nm (conjugate D); 4.6 ± 0.5 nm (conjugate E) ( Figure S1). The smallest sizes were observed for the Pheo-BSA conjugates, as expected based on a lower DA polymerization in the presence of cysteine. The quantification of BSA in the PheoBSA D was estimated after complete hydrolysis of the protein by NMR, according to a reported procedure [53]. The method is based on the quantification of the aromatic protons of tyrosine (20 residues in BSA) and the methyl groups of threonine (33 residues in BSA) that give easily recognizable 1 H NMR signals, using sucrose as standard. The result suggested an averaged ratio of 20% of the protein (w/w).
Appl. Sci. 2020, 10, x FOR PEER REVIEW 6 of 13 reported procedure [53]. The method is based on the quantification of the aromatic protons of tyrosine (20 residues in BSA) and the methyl groups of threonine (33 residues in BSA) that give easily recognizable 1 H NMR signals, using sucrose as standard. The result suggested an averaged ratio of 20% of the protein (w/w). FITC was conjugated with PheoBSA D for in vivo biodistribution studies. A FITC calibration curve was used for the quantification of FITC conjugated to PheoBSA D using PheoBSA D as a blank at the same concentration in mg/mL. We calculated an amount of 2 μmol of FITC per g of PheoBSA D.
Photoacoustic measurements of the conjugates showed broad absorption spectra, typical of natural melanin ( Figure 2B). PheoBSA D showed the highest PA contrast properties at a concentration of 2.5 mg/mL. Despite PheoBSA C displayed comparable absorbance properties to PheoBSA D, a lower PA emission efficiency was observed, likely reflecting different PA efficiency due to a different polymerization degree when compared to PheoBSA D. Photoacoustic emission showed a linear dependence with the concentration for all the investigated systems ( Figure 2C). When compared with a previously reported system, melanin free acid (MFA-PEG) [47], it was found that PheoBSA D displayed almost a two-fold increase in PA contrast capability ( Figure 2D).

PheoBSA Conjugate D in Vivo Biodistribution and Tumor Detection
The toxicity of PheoBSA D was evaluated by incubating J774A.1 cells in presence of several concentrations of the melanin/BSA conjugate. As can be seen from the graph ( Figure 3A), after three days, no cell toxicity was detected. The vitality of the J774A.1 cells was completely unaffected by the presence of the PheoBSA conjugate up to the concentration of 2.5 mg/mL, whereas at higher concentrations, a moderate toxicity was measured, although any side effects in any of the injected animal was observed. The PheoBSA D showed also high stability in serum for several hours and titrated at different pH ( Figure 3B). FITC was conjugated with PheoBSA D for in vivo biodistribution studies. A FITC calibration curve was used for the quantification of FITC conjugated to PheoBSA D using PheoBSA D as a blank at the same concentration in mg/mL. We calculated an amount of 2 µmol of FITC per g of PheoBSA D.
Photoacoustic measurements of the conjugates showed broad absorption spectra, typical of natural melanin ( Figure 2B). PheoBSA D showed the highest PA contrast properties at a concentration of 2.5 mg/mL. Despite PheoBSA C displayed comparable absorbance properties to PheoBSA D, a lower PA emission efficiency was observed, likely reflecting different PA efficiency due to a different polymerization degree when compared to PheoBSA D. Photoacoustic emission showed a linear dependence with the concentration for all the investigated systems ( Figure 2C). When compared with a previously reported system, melanin free acid (MFA-PEG) [47], it was found that PheoBSA D displayed almost a two-fold increase in PA contrast capability ( Figure 2D).

PheoBSA Conjugate D In Vivo Biodistribution and Tumor Detection
The toxicity of PheoBSA D was evaluated by incubating J774A.1 cells in presence of several concentrations of the melanin/BSA conjugate. As can be seen from the graph ( Figure 3A), after three days, no cell toxicity was detected. The vitality of the J774A.1 cells was completely unaffected by the presence of the PheoBSA conjugate up to the concentration of 2.5 mg/mL, whereas at higher concentrations, a moderate toxicity was measured, although any side effects in any of the injected animal was observed. The PheoBSA D showed also high stability in serum for several hours and titrated at different pH ( Figure 3B). The distribution of PheoBSA-FITC (300 μL/mouse of a 2 mg/mL solution) after IV administration was investigated in male Athymic nude mice (n = 6) which were subcutaneously inoculated with human prostate PC-3 cancer cells. Ex vivo optical imaging experiments on excised organs, i.e., tumor, liver, brain, kidneys, spleen, heart, lungs, and muscle were performed at 4 h and 24 h post-injection ( Figure 3C,D). Images recorded 4 h after the injection showed an intense signal at kidneys and in the tumor regions whereas very weak signals were detected for liver, muscle, and lungs. No signal could be detected from the brain, heart, and spleen. After 24 h post-injection, the signal decreased although it remained still detectable in tumor and kidneys. All the other organs showed a signal comparable with the fluorescence observed in not treated animals (data not show).
The capability of PheoBSA D for tumor imaging was further assessed by acquiring PA images in HER2 positive breast TS/A tumor models. The acquisitions were carried out either on VevoLazr 2100 (Visualsonic) and LOIS 3D (Tomowave) systems (Figures 4 and 5). A net tumor contrast enhancement during the first 30 min from the administration of the CA was observed on both scanners. The VevoLazr photoacoustic imager generates a lower tumor enhancement compared to those obtained with the LOIS 3D, as reported in Figures 4 and 5. The distribution of PheoBSA-FITC (300 µL/mouse of a 2 mg/mL solution) after IV administration was investigated in male Athymic nude mice (n = 6) which were subcutaneously inoculated with human prostate PC-3 cancer cells. Ex vivo optical imaging experiments on excised organs, i.e., tumor, liver, brain, kidneys, spleen, heart, lungs, and muscle were performed at 4 h and 24 h post-injection ( Figure 3C,D). Images recorded 4 h after the injection showed an intense signal at kidneys and in the tumor regions whereas very weak signals were detected for liver, muscle, and lungs. No signal could be detected from the brain, heart, and spleen. After 24 h post-injection, the signal decreased although it remained still detectable in tumor and kidneys. All the other organs showed a signal comparable with the fluorescence observed in not treated animals (data not show).
The capability of PheoBSA D for tumor imaging was further assessed by acquiring PA images in HER2 positive breast TS/A tumor models. The acquisitions were carried out either on VevoLazr 2100 (Visualsonic) and LOIS 3D (Tomowave) systems (Figures 4 and 5). A net tumor contrast enhancement during the first 30 min from the administration of the CA was observed on both scanners. The VevoLazr photoacoustic imager generates a lower tumor enhancement compared to those obtained with the LOIS 3D, as reported in Figures 4 and 5.  A possible reason for the observed findings appears related to the different instrument configuration that allows one to acquire a 3D image with the LOIS and 2D with the Vevo with different penetration depth [54,55]. Photoacoustic signal is partly limited to the epithelial tumor zone by Vevo, so the enhancement is calculated from about one-third to one-half of the entire ROI drawn on the tumor ( Figure 4B). However, the VevoLazr is closer to a clinical setup with a handheld probe.
Upon comparing the results obtained using the LOIS 3D system it was found that PheoBSA D photoacoustic enhancement in the prostate tumor model roughly doubled the signal enhancement observed for the TS/A tumor model. This observation may be accounted for in terms of a larger   A possible reason for the observed findings appears related to the different instrument configuration that allows one to acquire a 3D image with the LOIS and 2D with the Vevo with different penetration depth [54,55]. Photoacoustic signal is partly limited to the epithelial tumor zone by Vevo, so the enhancement is calculated from about one-third to one-half of the entire ROI drawn on the tumor ( Figure 4B). However, the VevoLazr is closer to a clinical setup with a handheld probe.
Upon comparing the results obtained using the LOIS 3D system it was found that PheoBSA D photoacoustic enhancement in the prostate tumor model roughly doubled the signal enhancement observed for the TS/A tumor model. This observation may be accounted for in terms of a larger A possible reason for the observed findings appears related to the different instrument configuration that allows one to acquire a 3D image with the LOIS and 2D with the Vevo with different penetration depth [54,55]. Photoacoustic signal is partly limited to the epithelial tumor zone by Vevo, so the enhancement is calculated from about one-third to one-half of the entire ROI drawn on the tumor ( Figure 4B). However, the VevoLazr is closer to a clinical setup with a handheld probe.
Upon comparing the results obtained using the LOIS 3D system it was found that PheoBSA D photoacoustic enhancement in the prostate tumor model roughly doubled the signal enhancement observed for the TS/A tumor model. This observation may be accounted for in terms of a larger vascularization of prostate cancer and consequently the major distribution of the blood pool agent. As a proof of concept for a DCE-PA imaging experiment that exploits the altered permeability of tumor vasculature, the photoacoustic signal was acquired every 72 s and the uptake of the melanin-based contrast agent PheoBSA D over time was assessed in the tumor region ( Figure 6). This result demonstrated a slow but steady increase of the PA signal with a peak at about 15-25 min after the injection of PheoBSA D, that one may assume as the time needed for the extravasation and accumulation of the nano-sized agent in the tumor region. More quantitative analysis for DCE-PA imaging has also been proposed for taking into account the different compartments and laser fluence [56,57]. In the last years, similar dynamic contrast enhancement photoacoustic 3D PA studies using ICG as contrast agent have been performed [58][59][60][61]. However, ICG applications are limited by their rapid clearance, low photostability, low water solubility, and tendency to form aggregates. Herein we propose a melanin-based nanoparticle endowed with a longer circulation time compared to ICG-albumin adduct that allows for prolonged DCE experiments.
Appl. Sci. 2020, 10, x FOR PEER REVIEW 9 of 13 vascularization of prostate cancer and consequently the major distribution of the blood pool agent. As a proof of concept for a DCE-PA imaging experiment that exploits the altered permeability of tumor vasculature, the photoacoustic signal was acquired every 72 s and the uptake of the melaninbased contrast agent PheoBSA D over time was assessed in the tumor region ( Figure 6). This result demonstrated a slow but steady increase of the PA signal with a peak at about 15-25 min after the injection of PheoBSA D, that one may assume as the time needed for the extravasation and accumulation of the nano-sized agent in the tumor region. More quantitative analysis for DCE-PA imaging has also been proposed for taking into account the different compartments and laser fluence [56,57]. In the last years, similar dynamic contrast enhancement photoacoustic 3D PA studies using ICG as contrast agent have been performed [58][59][60][61]. However, ICG applications are limited by their rapid clearance, low photostability, low water solubility, and tendency to form aggregates. Herein we propose a melanin-based nanoparticle endowed with a longer circulation time compared to ICGalbumin adduct that allows for prolonged DCE experiments.

Conclusions
The herein reported results show that PheoBSA D is a promising melanin-based contrast agent for photoacoustic imaging. This nanosystem represents the prototype of a class of PAI-CAs based on the melanin-albumin conjugates, characterized by a relatively small size, improved photoacoustic properties, and excellent biocompatibility. The in vivo tumor uptake was evaluated by two different optoacoustic scanners which showed the capability of this nanosystem to report on tumor vascularity in two murine tumor models. Further studies are needed to evaluate the PAI properties of these compounds in comparison to FDA approved dyes such as indocyanine green.
Supplementary Materials: The following are available online at www.mdpi.com/xxx/s1, Figure S1: Hydrodynamic sizes of the conjugates determined by dynamic light scattering (DSL) using a 90 Plus particle size analyzer (Malvern, Zetasizer). Figure S2: Calibration curve for FITC quantification. Figure S3: Excitation and emission spectra of PheoBSA-FITC. Table S1: Summary of the several prepared melanin-BSA conjugates.

Conclusions
The herein reported results show that PheoBSA D is a promising melanin-based contrast agent for photoacoustic imaging. This nanosystem represents the prototype of a class of PAI-CAs based on the melanin-albumin conjugates, characterized by a relatively small size, improved photoacoustic properties, and excellent biocompatibility. The in vivo tumor uptake was evaluated by two different optoacoustic scanners which showed the capability of this nanosystem to report on tumor vascularity in two murine tumor models. Further studies are needed to evaluate the PAI properties of these compounds in comparison to FDA approved dyes such as indocyanine green.