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Ultrasmall AGuIX theranostic nanoparticles for vascular-targeted interstitial photodynamic therapy of glioblastoma

Authors Thomas E, Colombeau L, Gries M, Peterlini T, Mathieu C, Thomas N , Boura C, Frochot C, Vanderesse R , Lux F, Barberi-Heyob M, Tillement O

Received 11 May 2017

Accepted for publication 1 July 2017

Published 26 September 2017 Volume 2017:12 Pages 7075—7088


Checked for plagiarism Yes

Review by Single anonymous peer review

Peer reviewer comments 2

Editor who approved publication: Dr Thomas Webster

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Eloïse Thomas,1 Ludovic Colombeau,2 Mickaël Gries,3,4 Thibaut Peterlini,3,4 Clélia Mathieu,1 Noémie Thomas,3,4 Cédric Boura,3,4 Céline Frochot,2 Régis Vanderesse,5 François Lux,1 Muriel Barberi-Heyob,3,4 Olivier Tillement1

1Université Lyon, Université Claude Bernard Lyon 1, Centre National de la Recherche Scientifique (CNRS), Institut Lumière Matière, Lyon, 2Laboratoire Réactions et Génie des Procédés, Université de Lorraine-CNRS, Nancy, 3Université de Lorraine, Research Center for Automatic Control of Nancy (CRAN), 4CNRS, CRAN, Vandœuvre-lès-Nancy, 5Laboratoire de Chimie Physique Macromoléculaire, Université de Lorraine-CNRS, Nancy, France

Abstract: Despite combined treatments, glioblastoma outcome remains poor with frequent local recurrences, indicating that a more efficient and local therapy is needed. In this way, vascular-targeted photodynamic therapy (VTP) could help tumor eradication by destroying its neovessels. In this study, we designed a polysiloxane-based nanoparticle (NP) combining a magnetic resonance imaging (MRI) contrast agent, a photosensitizer (PS) and a new ligand peptide motif (KDKPPR) targeting neuropilin-1 (NRP-1), a receptor overexpressed by angiogenic endothelial cells of the tumor vasculature. This structure achieves the detection of the tumor tissue and its proliferating part by MRI analysis, followed by its treatment by VTP. The photophysical properties of the PS and the peptide affinity for NRP-1 recombinant protein were preserved after the functionalization of NPs. Cellular uptake of NPs by human umbilical vein endothelial cells (HUVEC) was increased twice compared to NPs without the KDKPPR peptide moiety or conjugated with a scramble peptide. NPs induced no cytotoxicity without light exposure but conferred a photocytotoxic effect to cells after photodynamic therapy (PDT). The in vivo selectivity, evaluated using a skinfold chamber model in mice, confirms that the functionalized NPs with KDKPPR peptide moiety were localized in the tumor vessel wall.

Keywords: nanoparticles, PDT, vascular targeting strategy, brain tumor, NRP-1, peptide ligand, MRI


Despite multiple treatments, glioblastoma multiforme (GBM) remains the most frequent and malignant brain tumor with an overall survival of only 14.6 months.1 Currently, treatments often combine surgery, radiotherapy and chemotherapy, but a wide majority of GBM recurs locally, upwards of 80% of cases, leading to patient’s death.2 This indicates that a more aggressive local treatment is needed to improve the local control. However, resection can hardly be a complete and curative intervention because of the migration of tumor cells into the healthy brain parenchyma.1 Furthermore, radiotherapy often induces side effects, impacting health and quality of life. In this context, photodynamic therapy (PDT) appears to be an interesting complementary approach in order to prevent GBM local recurrence and to improve local control with minimal side effects.2 PDT is based on the activation of a photosensitizer (PS) by light at an appropriate wavelength to generate reactive oxygen species, especially singlet oxygen.3 Besides, the radius of interaction for singlet oxygen is inferior to 0.2 μm and the half life is short, from 0.03 μs to 0.18 ms, according to the medium, inducing cell damages in close proximity of the activated PS.4 Owing to the localization of the optical fiber into the tumor tissue, an interstitial PDT (iPDT) can be suggested.5 Several clinical trials have highlighted the interest of PDT for GBM.2,68 For Phase II clinical studies, we can mention the one of the Muragaki group on patients with primary malignant brain tumors including 13 GBM cases9 or the one of the Whelan group (NCT01966809) for recurrent high-grade gliomas using intraoperative PDT to eradicate cancer cells after resection as local recurrences in the surgical bed after tumor resection may be due to residual tumor cells.

The choice of the PS molecule is crucial to generate a photodynamic efficiency. Whereas many PSs have been developed, some issues remain and have to be overcome.10 First, numerous PSs are porphyrin derivatives and therefore poorly soluble in water; they can aggregate in physiological media, leading to a drastic decrease in singlet oxygen production and difficulties for intravenous injection. Moreover, they often display a low tumor tissue selectivity in vivo.11,12 During the last few decades, one solution emerged using multifunctional nanoparticles (NPs) for PDT, highlighting several advantages.13 The first one comes from the tumor selectivity. They can indeed specifically accumulate into the tumor tissue due to the enhanced permeability and retention (EPR) effect. Moreover, their surface can be functionalized to target a specific receptor overexpressed by neoplastic or angiogenic endothelial cells.14,15 Their composition can be modulated to protect the PS molecules, increasing their solubility in biological media, optimizing their lifetime in plasma or avoiding enzymatic degradation. Finally, by adding a contrast agent to the NPs, they can also be suggested at the same time for a treatment guided by imaging. It is therefore possible to detect the tumor, to plan the treatment (for instance, an appropriate PDT optical fiber positioned into the tumor volume), to optimize the drug-light interval before irradiation and to follow the tumor response by diffusion MRI.16

Different kinds of NPs have already been described for PDT.1723 The ones based on polysiloxane are particularly interesting because their size and shape can be controlled, are biocompatible and can be easily functionalized.24 PS molecules can be encapsulated inside pores of mesoporous NPs or grafted on the surface of a polysiloxane core. With this last strategy, singlet oxygen does not need to diffuse out of the NPs and it avoids the aggregation of PS molecules inside the pores. Our group recently described such kinds of NPs for iPDT applied to GBM.25 In this case, 5-(4-carboxyphenyl)-10,15,20-triphenylporphyrin was grafted on the surface of an ultrasmall NP called AGuIX. AGuIX is composed of a polysiloxane core surrounded by [email protected]3+ complexes (DOTA, 1,4,7,10-tetraazacyclododecane-1,4,7,10-tetraacetic acid), enabling detection of NPs by magnetic resonance imaging (MRI). [email protected] NPs were injected intravenously to nude rats bearing U87 intracranial GBM. Their tumor tissue accumulation was followed by MRI, and the optical fiber was precisely inserted into the tumor burden. Using [email protected], iPDT induced a statistically significantly therapeutic effect compared to control groups. It was also possible to determine early predictive markers by proton magnetic resonance (MR) spectroscopy and diffusion MRI to discriminate between nonresponding and responding animals.25

The indirect effects of PDT, including immune response and vascular destruction, are well known to play a major role in photodynamic efficiency.2628 The latter effect may indirectly initiate a privation of nutrients and molecular oxygen into the tumor tissue. To asphyxiate some vascularized tumors, mainly the infiltrating part, a targeting strategy of the tumor vasculature may potentiate this effect. We also previously demonstrated that this effect would play a major role in the destruction of GBM by PDT.11,29 The goal of the present study was to synthesize an ultrasmall theranostic NP, presenting high affinity for neovessels. In addition to a better PDT efficiency, we can also expect to reach longer intra-tumor retention and detection by MRI of the real tumor volume, taking into account the proliferating part of the tumor tissue. Overexpressed receptors specifically located on angiogenic endothelial cells are therefore promising molecular target for PDT. Neuropilin-1 (NRP-1) is one of them; it is a receptor for vascular endothelial growth factor, isoforms A-165 and A-145 (VEGF-A165 and VEGF-A145), and is overexpressed in several cancers.30 The use of a chlorin conjugated to a heptapeptide (ATWLPPR) and their grafting on a NP has already been described for vascular-targeted photodynamic therapy (VTP) and has highlighted very promising in vitro and in vivo results.11,26,29,3133 Recently, we evidenced that new peptides have an improved affinity for NRP-1; DKPPR is one of them.34

This article focuses on the design of a new AGuIX-type nanoplatform for VTP using this DKPPR peptide moiety. For our research approach, a lysine (K) had to be added at the N-terminal side of the DKPPR peptide. Subsequently, the KDKPPR peptide was coupled with a PS, 5-(4-carboxyphenyl)-10,15,20-triphenylporphyrin, to the amine function of the lysine lateral side chain, producing [email protected] This conjugate was then used in the design of this new nanoplatform for VTP by grafting at the surface of AGuIX NPs (producing [email protected]@KDKPPR). After the synthesis and characterization of NPs, their photophysical properties as well as their affinity for NRP-1 recombinant protein, dark cytotoxicity, in vitro and in vivo vascular selectivity and PDT efficiency were evaluated. All the results were compared with the one obtained for a scramble NP (bearing the KRPKPD peptide).

Materials and methods


All reactions involving porphyrin compounds were performed in the dark. Reactions were monitored by thin-layer chromatography (TLC) using aluminum-backed silica gel plates (Macherey-Nagel ALUGRAM® SIL > G/UV254), and ultraviolet light was used to detect TLC spots. Product purifications were performed using Silica Gel 60 (230–400 mesh) for column chromatography and Geduran 60 H Silica Gel (63–200 mesh) for flash column chromatography. Reverse-phase high-performance liquid chromatography (HPLC) was performed on ProStar HPLC (Varian, Agilent Technologies, Santa Clara, CA, USA). Analytical HPLC was done with a Pursuit 5-C18 column (2.5 μm, 4.6×150 mm; Varian) and preparative HPLC with Pursuit 5-C18 column (5 μm, 21.2×150 mm), both using a photodiode array detector (UV–visible detection; Varian) and a fluorescence detector (Varian).


Unless other stated, all chemicals were purchased as the highest purity commercially available and were used without further purifications. 5-(4-carboxyphenyl)-10,15,20-triphenylporphyrin (PS) was purchased from PorphyChem (Dijon, France). The Fmoc-Arg(Pbf)-Wang resin, the Fmoc-Asp(OtBu)-Wang resin, 9-fluorenyl-methoxy-carbonyl (Fmoc)-amino acids and N,N,N′,N′-Tetramethyl-O-(1H-benzotriazol-1-yl)uronium hexafluorophosphate) (HBTU) were purchased from Iris Biotech GmbH (Marktredwitz, Germany). The N-hydroxysuccinimide, N, N′-dicyclohexylcarbodiimide, N-methylmorpholine (NMM), N-methylpyrrolidinone (NMP), N-ε-maleimidocaproic acid, trifluoroacetic acid (TFA) and triisopropylsilane (TIPS) were purchased from Alfa Aesar (Haverhill, MA, USA). Sodium hydroxide (NaOH; 99.99%), hydrochloric acid (HCl; 36.5%-38%), phosphate-buffered saline (PBS; tablet), dimethyl sulfoxide (DMSO; >99.5%) and Fmoc-Lys-OH HCl were purchased from Sigma-Aldrich (St Louis, MO, USA), Traut’s reagent (2-iminothiolane hydrochloride; >97.0%) was purchased from Alfa Aesar. Ellman’s reagent, 5,5-dithio-bis-(2-nitrobenzoic acid) (>98%), was purchased from Thermo Fisher Scientific (Waltham, MA, USA). AGuIX particles were purchased from NH TherAguix (Lyon, France). All products were used without further purification. Only Milli-Q water (ρ>18 MO·cm) was used for the aqueous solution preparation.

Synthesis of PS-NHS: 5-(4-carboxyphenyl succinimide ester)-10,15,20-(triphenyl)porphyrin

In the dark and under inert atmosphere, PS-COOH (1 eq) was dissolved in CH2Cl2 (20–50 mL), and N-hydroxysuccinimide (3 eq) and N, N′-dicyclohexylcarbodiimide (3 eq) were added. The mixture was stirred at 40°C, for 4 h, under argon. Purification of the crude material was performed using a silica gel column with dichloromethane (DCM). PS-NHS was obtained, after recrystallization in DCM/hexane, as a purple solid with a yield of 75%.

Synthesis of Fmoc-Lys(PS)-OH: 2-(9H-fluoren-9-ylmethoxycarbonylamino)-6-[5-(4-carboxyphenyl)-10,15,20- triphenylporphyrin]-hexanoic acid

N-hydroxysuccinimide-activated porphyrin PS-NHS (152.4 mg, 0.20 mmol) and triethylamine (0.21 mmol, 28.3 μL) in 10 mL of CH2Cl2 were added in the dark and under a nitrogen atmosphere to a solution of Fmoc-Lys-OH, HCl (82.8 mg, 0.20 mmol) in a minimum of dimethyl formamide (DMF). After being stirred at ambient temperature for 24 h, the solvent was removed and the crude material was purified by column chromatography on silica gel using EtOH/CH2Cl2, 5/95 (v/v), as the eluent. Solvent was removed in vacuo, and the residue recrystallized using CHCl3/n-hexane. The pure compound was isolated as a purple solid (166.5 mg, 82%).

Synthesis of H-K(PS)DKPPR-OH

The side chains of aspartic acid, lysine and arginine were respectively protected by 2,2,4,6,7-pentamethyldihydrobenzofuran-5-sulfonyl (Pbf), 5-tert-butyl ester (OtBu) and N-tert-butyloxy carbonyl (Boc) groups. H-D(OtBu)K(Boc)PPR(Pbf)-Wang resin was synthesized on a multichannel peptide synthetizer (Intavis AG, Köln, Germany), according to a classical Fmoc/tBu solid phase methodology, using a Fmoc-Arg(Pbf)-Wang resin on a 100 μmol scale. Double coupling was performed using a threefold excess of N-Fmoc-amino acid, activation reagents HBTU (3 eq), NMP (3 eq) and NMM (9 eq) in DMF. The coupling of Fmoc-Lys(PS)-OH (2 eq used) was the only one to be stirred for 5 days. Final Fmoc protection was removed using piperidine. The resin obtained was dried under vacuum and then cleaved using TFA/TIPS/water (92.5/5/2.5%) for 2 h. The acidic resin was filtered and washed with 2 mL of TFA and 50 mL of CH2Cl2. The filtrate was dried under vacuum and lyophilized. The crude product was further purified by preparative HPLC using acetonitrile/water (0.1% TFA; 10:90) to 100% acetonitrile gradient in 25 min, followed by isocratic acetonitrile for 15 min. Rt =17.8 min. Pure product was isolated as a red powder (15.7 mg, 11%).

Synthesis of the [email protected] (maleimido-K(PS)DKPPR-OH)

The side chains of aspartic acid, lysine and arginine were respectively protected by Pbf, OtBu and Boc groups. H-D(OtBu)K(Boc)PPR(Pbf)-Wang resin was synthesized on a fully automated ResPepXL peptide synthesizer (Intavis AG), according to a classical Fmoc/tBu solid phase methodology, using a Fmoc-Arg(Pbf)-Wang resin on a 150 μmol scale. Double coupling was performed using a threefold excess of N-Fmoc-amino acid, activation reagents HBTU (3 eq), NMP (3 eq) and NMM (9 eq) in DMF. After Fmoc deprotection by piperidine, the coupling of Fmoc-Lys(PS)-OH (1.5 eq used) was performed in presence of HBTU (3 eq), NMP (3 eq) and NMM (9 eq) in DMF, and the reaction mixture was stirred for 2 days. Final Fmoc protection was removed using piperidine, and the coupling of N-ε-maleimidocaproic acid (1.2 eq) was realized in the same conditions as in the Fmoc-Lys(PS)-OH coupling. The resin obtained was dried under vacuum and then cleaved using TFA/TIPS/water (92.5/5/2.5%) for 2 h. The acidic resin was filtered and washed with 2 mL of TFA and 50 mL of CH2Cl2. The filtrate was dried under vacuum and lyophilized. The crude product was further purified by preparative HPLC using acetonitrile/water (0.1% TFA; 10:90) to 100% acetonitrile gradient in 15 min, followed by isocratic acetonitrile for 10 min. Rt =17.8 min. Pure product was isolated as a green powder (50 mg, 21%).

[email protected] synthesis and purification

AGuIX NPs (1 mmol of Gd3+) were dispersed in PBS (0.2 M, pH 8, 10 mL, [Gd3+] =100 mM) for 1 h at room temperature (RT). The Traut’s reagent (1 mmol) was dissolved in PBS (Traut’s reagent =50 mg·mL−1) and added slowly to the NPs. The mixture was let under stirring at RT for 1 h. Particles were then purified by tangential filtration trough Vivaspin® membranes (molecular weight cutoff [MWCO] =5 kDa) purchased from Sartorius Stedim Biotech (Aubagne, France). The colloidal solution was introduced into Vivaspin tubes and centrifuged; this step was repeated several times, by filling the tube and centrifuging. The purification process was followed by recording the absorbance spectra of the filtrated solution and stopped when no more signal at 248 nm was detected (signal due to the nonreacted Traut’s reagent, total purification time <1 h). The Gd3+ yield was determined by inductively coupled plasma optical emission spectrometry (ICP-OES) and was of 80%. The Traut yield was determined, thanks to the Ellman’s reagent, and was of 8%.

Thiol quantification

Several samples (V =1 mL) containing the same amount of NPs, n(Gd3+) =0.3 μmol, and an increasing quantity of Ellman’s reagent (0–60 nmol) were prepared in PBS (pH 8). Samples were let in the dark for 15 min to react, and then their absorbance at 412 nm was measured using an UV–visible spectrophotometer (Varian Cary 50) and a Hellma semi micro cell (1 cm light path, 1,400 μL) manufactured from Suprasil quartz (Paris, France).

[email protected]@KDKPPR synthesis and purification

[email protected] NPs (500 μmol of Gd3+) were diluted in PBS (0.2 M, pH 8, 6 mL), and then, 1.4 mL of DMSO was added and the mixture heated at 40°C. The [email protected] compound was dissolved in DMSO (25 μmol, 15 mg·mL−1) and added to the mixture in five additions, with a spaced out time of 30 min. The additions were made drop by drop in the dark and under stirring. When all the [email protected] compound was added, the solution was let under stirring for 2 more hours ([Gd3+] =50 mM). The solution was then diluted into water to reach a ratio of DMSO/water <4% and purified through tangential filtration as previously described. The particles’ solution was concentrated to approximately [Gd3+] =100 mM, the pH was adjusted to 7.4 and, finally, the solution was sterilized by filtration through a 0.2 μm syringe filter in order to remove the large impurities. It was freeze-dried for storage, using a Christ Alpha 1-2 lyophilizer (Osterode am Harz, Germany). The Gd3+ yield was determined by ICP-OES and was of 45%. The [email protected] yield was determined by absorbance measurements and was of 60%. The same procedure was followed to synthesize [email protected]@scramble.

Affinity to NRP-1

The surface of microplates (Corning Inc., Corning, NY, USA) was coated overnight at RT with NRP-1 at a concentration of 2 μg/mL (R&D Systems, Inc., Minneapolis, MN, USA) in PBS. A solution of PBS containing 0.5% bovine serum albumin (BSA; blocking buffer) was then used to block the plates, to prevent nonspecific interactions, during 1 h at 37°C. In all, 5 ng/mL of biotinylated VEGF-A165 (R&D Systems, Inc.) in blocking buffer containing 2 μg/mL of heparin was used to assess the binding of compounds to NRP-1. Biotinylated VEGF-A165 was added to the coated wells in competition with the different compounds or excess of non-labeled VEGF-A165, as a positive control. The plates were washed after a 2 h incubation at RT, and the amount of bound biotinylated VEGF-A165 was stained with streptavidin horseradish peroxidase conjugate (R&D Systems, Inc.). The reaction was stopped after 20 min at RT by the addition of Stop Solution (R&D Systems, Inc.). Optical densities were measured at 450 nm. Results were expressed as relative absorbance to wells containing only blocking buffer. Three wells per condition were used.

Cellular uptake of NPs

Human umbilical vein endothelial cells (HUVEC) obtained from Merck Millipore (Billerica, MA, USA) were cultivated in the EndoGRO-LS complete medium (Merck Millipore) seeded in 24-well plates at 5×104 cells/well. After 1 day, the medium containing NPs at the concentration of 1 μM was added. After 4 or 24 h, the medium was removed and cells were rinsed twice with cold PBS and trypsinized. After cell counting on a hemocytometer, cells were centrifuged (1,200× g for 5 min) and resuspended in lysis buffer (0.2 N NaOH, 0.5% Triton X-100). Centrifugation (3,500× g for 15 min) was used to remove cell debris. Fluorescence (recorded at 650 nm following excitation at 420 nm) was measured on an M200 Pro spectrofluorometer (Tecan, Männedorf, Switzerland). Results are given as the fluorescence intensity by each cell. Experiments were carried out at least in triplicates.

Dark cytotoxicity

Cell survival after incubation with NPs in the dark was measured using a 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyl tetrazolium bromide (MTT) assay. Briefly, HUVEC were plated at an initial cell density of 5×104 cells/well in 24-well plates and allowed to attach overnight. Wells were rinsed twice with PBS and filled with 500 μL of HUVEC medium containing various concentrations of NPs (from 0.1 to 10 μM). After a 24 h incubation at 37°C, wells were rinsed twice with cold PBS and filled with 200 μL of HUVEC medium. Cell survival was measured by MTT assay as previously described.29 Experiments were carried out in triplicates.


For photocytoxicity, NPs at a final concentration of 1 or 10 μM were added in each well containing HUVEC previously seeded at 5×104 cells/well. HUVEC were cultivated for 4 or 24 h by keeping in darkness. Then, the cells were washed three times with the growth medium to remove the un-internalized NPs. After that, the cells were either exposed to various doses of light (5 or 10 J·cm−2) using a diode laser (Ceralas PDT 652; CeramOptec GmbH, Biolitec, Germany) to assess the photo-induced cytotoxicity of the [email protected] Irradiation was carried out at 652 nm with an irradiance of 4.54 mW/cm2. Finally, cell survival was measured by MTT assay 24 h post irradiation as previously described.29 Each concentration of NPs was tested in sextuplicate.

In vivo experiments: selectivity of NPs in a dorsal skinfold chamber

All in vivo experiments were performed in accordance with the European Community guidelines (2010/63/EU) for the use of experimental animals with respect to the 3 Rs’ requirements for Animal Welfare (the research project nos APAFIS 2368 and 2194 were approved by the French Ministry of Research). Animals were kept under standard conditions (T =21°C±1°C, hygrometry 60%±10%, light on from 6 am to 6 pm) and had free access to standard diet and water.

Stereotactic U87 xenograft implantation was performed as previously described in Toussaint et al.25 MRI acquisitions were performed using a small animal 7 Tesla magnet (BioSpec 70/20 USR; Bruker Optik GmbH, Ettlingen, Germany). The most common MRI sequences and T1-weighted imaging (RARE acquisition; relaxation enhancement TR/TE =400/9 ms; matrix: 256×256) were repeated in axial planes before injection and also at different times after [email protected]@KDKPPR intravenous injection (4 μmol·kg−1, porphyrin equivalent) to visualize the tumor tissue in positive signal. For selectivity of NPs using the dorsal skinfold chamber model, 8–10 weeks old nude female mice were used (Janvier, Le Genest-Saint-Isle, France). U87 xenografts were obtained and implanted in skinfold chambers as previously described in Tylcz et al.35 After 10–14 days following U87 cells implantation, mice were divided into three batches: a batch receiving [email protected]@KDKPPR NPs, another one with [email protected]@scramble and the last one with [email protected] NPs. Visualization of the localization of different NPs into the vasculature (lumen versus vascular column) was performed on anesthetized mice bearing skinfold chambers at 1, 6 and 24 h after injection using the Nikon microscope AZ100 (Nikon Corp., Tokyo, Japan) system equipped with a Digital Light DS-Qi1Mc camera and a confocal device (Revolution DSD; Andor Technology, Belfast, UK).

Statistical analysis

All results were given as mean ± standard error of the mean (SEM). Nonparametric Mann–Whitney U test was used to determine the statistical significance with a limit set to P<0.05 using GraphPad Prism 5 (GraphPad Software, Inc., La Jolla, CA, USA) versus [email protected]@scramble.


The syntheses of AGuIX and AGuIX functionalized with 5-(4-carboxyphenyl)-10,15,20-triphenylporphyrin ([email protected]) NPs have already been described in the literature.25,36 In the present study and in order to maintain the affinity of the DKPPR peptide for NRP-1 recombinant protein, a new functionalization approach has been suggested. It consisted of the conjugation of the KDKPPR peptide moiety to the PS molecules, followed by the grafting of this new [email protected] conjugate to the surface of the AGuIX NPs through a maleimido–thiol reaction. It produced [email protected]@KDKPPR NP. The same protocol was also used with a scramble peptide containing the same amino acids ([email protected], [email protected]) to check the targeting selectivity of this new nanoplatform.

Synthesis and characterization of peptide derivatives

[email protected] and [email protected] compounds were synthesized by Fmoc/tBu solid-phase strategy (Figure 1). It is known that the lysine side chain provides a convenient handle to link a PS. For the synthesis of the [email protected] and [email protected], we choose to link first in liquid phase the 5-(4-carbonylphenyl)-10,15,20-triphenyl-porphyrin succidinyl ester (PS-NHS) already described by our team37 to the amine function of the lysine lateral side chain to form the Fmoc-Lys(PS)-OH (Figure 1). The coupling of Fmoc-Lys(PS)-OH and N-ε-maleimidocaproic acid was achieved on a H-peptide-Wang resin. During the coupling of Fmoc-Lys(PS)-OH and all the next steps, light exposure was minimized to limit unwanted side reactions by sealing the vessel in aluminum foil. The [email protected] and [email protected] peptides were cleaved from the resin with a mixture of TFA, TIPS and water (92.5/2.5/5). The [email protected] and [email protected] compounds were purified by preparative reversed-phase (RP)-HPLC. Characterizations of the compounds were confirmed by high-resolution mass spectrometry (HRMS) and 1H NMR experiments (Supplementary materials). As shown in Figure 2A, the photophysical properties of PS are preserved during the [email protected] compound synthesis; indeed, the singlet oxygen and the fluorescence quantum yields remain almost identical. The affinity of the peptide for the NRP-1 receptor was estimated as EC50 values (ie, the concentration of competitor that displaced 50% of biotinylated VEGF-A165 binding, using the medium effect method). It was found to be almost as good as one of KDKPPR alone (Figure 2B). Indeed, we found an EC50 value of 2 μM for KDKPPR, 1 μM for [email protected] and 81 μM for [email protected]

Figure 1 PS synthesis.
Notes: (A) Preparation of Fmoc-Lys(PS)-OH: (a) DCC, NHS, CH2Cl2, 40°C, 4 h and (b) Fmoc-Lys-OH HCl, Et3N, DCM, DMF, 0°C to RT, 24 h. (B) Solid phase synthesis of the [email protected] compound: (a) N-deprotection: 20% piperidine in DMF, (b) coupling: HBTU/NMM/NMP and (c) cleaving: TFA/TIPS/H2O.
Abbreviations: PS, photosensitizer; DCM, dichloromethane; RT, room temperature; NMM, N-methylmorpholine; NMP, N-methylpyrrolidinone; TFA, trifluoroacetic acid; TIPS, triisopropylsilane; DCC, N,N′-dicyclohexylcarbodiimide; DMF, dimethyl formamide; NHS, N-Hydroxysuccinimide; HBTU, N,N,N′,N′-Tetramethyl-O-(1H-benzotriazol-1-yl)uronium hexafluorophosphate.

Figure 2 PS characterizations.
Notes: (A) Absorption coefficient, fluorescence and singlet oxygen quantum yields of PS, [email protected], [email protected], [email protected] (B) Binding of the DKPPR peptide, the KDKPPR peptide, the [email protected] and the [email protected] to recombinant NRP-1 protein. Binding of biotinylated VEGF (5 ng/mL; 110 pM) to NRP-1 in the presence of 2 μg/mL heparin was evaluated when increasing concentrations of compounds (6.5–200 μM) were added (data points show the mean ± SD, n=3). The values found for EC50 are 46 μM for DKPPR, 2 μM for KDKPPR, 1 μM for [email protected] and 81 μM for [email protected]
Abbreviations: PS, photosensitizer; DMSO, dimethyl sulfoxide; EC50, concentration of competitor that displaced 50% of biotinylated VEGF-A165 binding.

Synthesis and characterization of the NPs for VTP

To introduce thiol group on the NP, a cyclic imido ester, the Traut’s reagent, was incubated with AGuIX NPs for 1 h at RT and at pH 8 (Figure 3A). It reacted with the primary amines present at the surface of the particles in a ring-opening reaction, resulting in a free sulfhydryl.38 The obtained [email protected] particles were then purified by tangential filtration over a 5 kDa cutoff membrane. Thanks to the absorbance of Traut’s reagent at 248 nm, the purification was followed by UV–visible spectroscopy. In order to quantify the number of thiols per particle, the Ellman’s reagent was used.39 In slightly basic conditions, it can react with sulfhydryl groups and release the 5-thio-2-nitrobenzoic acid, presenting a strong absorbance at 412 nm (Figure 3B). Briefly, the quantification is based on the addition of an increasing quantity of Ellman’s reagent to [email protected] particles. First, an increase in absorbance at 412 nm can be observed because of the reaction of thiol with Ellman’s reagent. When all the thiol functions have reacted, a plateau is reached. The results give approximately one thiol for 10 Gd3+ (corresponding to about one per particle).

Figure 3 [email protected] NPs synthesis and characterizations.
Notes: (A) Reaction of the amino group with the Traut’s reagent (PBS, pH =8, [Gd3+] =80 mM, RT, one Traut’s reagent for one Gd). (B) Thiol quantification on [email protected] using the Ellman’s reagent and absorbance measurements, n(Gd3+) =0.3 μmol in PBS (pH =8), 15 min, RT. The change of slope indicates that there are ~30 nmol of thiol in the solution (one SH for one particle).
Abbreviations: NP, nanoparticle; PBS, phosphate-buffered saline; RT, room temperature.

In the second step, as shown in Figure 4A, [email protected] was functionalized with the [email protected] compound by creating a stable thioester bond. To obtain solubility of both NPs and porphyrin derivatives, the [email protected] was gradually added to the NPs in a mixture of PBS and DMSO at 40°C. Then, the colloidal suspension was purified by tangential filtration over a 5 kDa cutoff membrane and by filtration over a 0.2 μm filter. As presented in Figure 4B, the resulting [email protected]@KDKPPR NPs have hydrodynamic diameter of ~10 nm, which is suitable for renal elimination. Besides, magnetic properties are consistent with their use as a positive contrast agent in MRI (r1 =16.1 s−1·mM−1 per Gd3+, r2/r1 =1.6 at 37°C and 1.4 T). No modification in the [email protected] absorbance spectra was detected after grafting (Supplementary materials). Calibration curves indicate that one [email protected] compound is present for 15 Gd3+ (corresponding to one to two particles). However, the fluorescence spectrum was found to be modified (refer Supplementary materials for the emission spectra after an excitation at 420 nm). Because of the poor solubility of PS in water, its fluorescence (ΦF) and singlet oxygen (ΦΔ) quantum yield as well as the one for [email protected] compound cannot be determined in water. As presented in Figure 4B, this is no more the case when [email protected] is grafted on AGuIX (ΦF =10% and ΦΔ =28%), highlighting the fact that AGuIX enables the solubility of PS in water. Besides, these yields are similar to the only PS or [email protected] in DMSO (ΦF =15 and 13% or ΦΔ =24 and 20% respectively). The NPs conjugated with the scramble peptide, [email protected]@scramble ([email protected]@KRPKPD), present similar characteristics.

Figure 4 Synthesis and characterizations of [email protected]@KDKPPR NPs.
Notes: (A) Grafting of the [email protected] compound on [email protected] NPs, DMSO/PBS (pH =8), 40°C, 4 h, [Gd3+] =50 mM, one PS for two SHs. After purification, approximately one PS molecule has been conjugated to one to two NPs. For [email protected]@scramble NPs, the same procedure was followed and similar results were obtained. (B) Size and magnetic properties of AGuIX, [email protected], [email protected]@KDKPPR and [email protected]@KDKPPR NPs. All NPs described a mean hydrodynamic diameter < or ~10 nm and magnetic properties consistent with their real interest as a positive contrast agent for MRI analysis. [email protected]@KDKPPR and [email protected]@scramble NPs describe similar fluorescence quantum yields (ΦF) and singlet oxygen quantum yields (ΦΔ) in D2O. (C) T1 coronal MRI images obtained before [email protected]@KDKPPR NPs intravenous injection and 1, 6 and 24 h after intravenous injection. Proton density weighted MRI (TR/TE: 5000/33 ms, NEX: 2, FOV: 4×4 cm, matrix: 256×256, SI: 1 mm). Maximal MRI signal intensity after injection was observed 1 h post injection.
Abbreviations: PS, photosensitizer; NP, nanoparticle; DMSO, dimethyl sulfoxide; PBS, phosphate-buffered saline; MRI, magnetic resonance imaging.

After intravenous injection of KDKPPR-targeted NPs, the positive contrast enhancement by MRI allowed us to visualize the tumor tissue (Figure 4C). Owing to these multifunctional NPs, we optimized the position of the optical fiber into the tumor tissue and selected an optimal drug-light interval between the nanoplatforms injection and the photodynamic treatment, validating the concept of iPDT guided in real time by MRI analysis.

NPs affinity to NRP-1 protein

For measurements of the binding affinities of NPs for recombinant NRP-1 protein, a competitive binding test using biotinylated VEGF-A165 was performed. As biotinylated VEGF-A165 binding to this receptor is heparin dependent, the competitive binding experiments were always carried out in the presence of heparin. As shown in Figure 5, [email protected]@KDKPPR displaces the binding of biotinylated VEGF-A165 to NRP-1 (EC50 =19 μM) more effectively than [email protected] and [email protected]@scramble (81 and 176 μM, respectively).

Figure 5 Binding of [email protected], [email protected]@scramble and [email protected]@KDKPPR NPs to recombinant NRP-1 protein.
Notes: (A) Binding of biotinylated VEGF165 (5 ng/mL; 110 pM) to NRP-1 in the presence of 2 μg/mL heparin was evaluated when increasing concentrations of peptide (6.5–200 μM) were added (data points show the mean ± SD, n=3). (B) [email protected]@KDKPPR NPs lead to a relevant affinity toward NRP-1 protein compared to [email protected] or [email protected]@scramble.
Abbreviations: PS, photosensitizer; NP, nanoparticle; EC50, concentration of competitor that displaced 50% of biotinylated VEGF-A165 binding.

In vitro dark cytotoxicity

An MTT test was used to evaluate the dark cytotoxicity of NPs for PS concentration, ranging from 1 to 10 μM in HUVEC. In the absence of light exposure and after 24 h incubation with 10 μM of [email protected], NPs exhibited no cytotoxicity (Supplementary materials).

In vitro and in vivo selectivity

The cellular uptake of NPs was examined using HUVEC, in the dark, at a PS non-cytotoxic concentration of 1 μM. As shown in Figure 6A, after 4 h of NPs’ incubation with HUVEC cells, the [email protected]@KDKPPR uptake was found to be twice higher than [email protected] or [email protected]@scramble NPs in relation with the grafting of DKPPR peptide. Indeed, the fluorescence per cell is 7.85±1.89×10−3, 3.83±0.75×10−3 and 3.25±0.42×10−3, respectively. However, no statistically relevant difference in cellular uptake was observed after 24 h of incubation for [email protected] and [email protected]@KDKPPR (fluorescence per cell of 2.52±0.55×10−2 and 2.58±0.29×10−2, respectively).

Figure 6 In vitro and in vivo selectivity followed by the photodynamic efficiency of functionalized NPs on HUVEC.
Notes: (A) In vitro selectivity: uptake in HUVEC after 4 and 24 h of incubation with functionalized NPs ([PS] =1 μM). The fluorescence measured before injection is related to the tissue autofluorescence (measured before administration of NPs). (B) In vivo selectivity: selectivity of NPs using a dorsal skinfold chamber model, before and 1, 6 and 24 h after intravenous injection of [email protected], [email protected]@scramble and [email protected]@KDKPPR ([PS] =6 μmol/kg). Blood vessels are represented in black and PS fluorescence in red. On the contrary to [email protected] or [email protected]@scramble, thanks to the targeting peptide, [email protected]@KDKPPR NPs were fixed to the vessel walls of the tumor tissue. All pictures have been taken with the same magnification, scale bar represents 100 μm. (C) Influence of light dose on cell viability after PDT (5 or 10 J·cm−2), following exposure of NPs ([PS] =1 μM and exposition time of 4 h). For in vitro experiments, n=3 or n=6. *P<0.05 and **P<0.01 versus [email protected]@scramble. A statistically significant photocytotoxicity was obtained with [email protected]@KDKPPR.
Abbreviations: NP, nanoparticle; HUVEC, human umbilical vein endothelial cells; PS, photosensitizer; au, atomic unit.

The vascular distribution of the NPs was performed by intravital microscopy in U87 xenograft tumors implanted in nude mice skinfold chambers. In vivo, distribution of [email protected] and [email protected]@scramble describes the same profile (Figure 6B). They were found free in the blood vessels at 1 h but disappeared from them at 6 h. [email protected]@KDKPPR NPs were recognized by the tumor endothelium and seem to be bound to the vessels walls of the tumor from 1 h postintravenous injection. The binding remains visible by fluorescence until 24 h. These results look very promising in the context of VTP.

In vitro PDT efficiency

Figure 6C illustrates in vitro results concerning photocytotoxicity on HUVEC and light dose efficiency. As expected, increasing light dose leads to a decrease in cell viability. Indeed, the cell viability (%) for an irradiation at 5 J·cm−2 was 100±6, 84±3, 72±5 and 53±3 for the control, [email protected], [email protected]@scramble and [email protected]@KDKPPR NPs, respectively. At 10 J·cm−2, it was 100±3, 60±2, 42±1 and 2±1 for the control, [email protected], [email protected]@scramble and [email protected]@KDKPPR, respectively. The best results were obtained with [email protected]@KDKPPR compared to other NPs, illustrating the real interest of the DKPPR-targeting peptide for PDT. The effect of incubation time or concentration (of porphyrin) was also studied (Supplementary materials). As expected by the results of HUVEC cellular uptake, it was found that after 4 h of incubation time, a relevant photocytotoxic effect was obtained with [email protected]@KDKPPR compared with AGuIX or [email protected]


Many studies have shown that tumor vasculature targeting is effective in enhancing the therapeutic efficacy of PDT. Several strategies exist as the use of antibodies or small synthetic peptides have the advantages of being easier to prepare and handle.40,41 For example, Ichikawa et al42 have synthesized liposomes bearing a pentapeptide (APRPG) and a PS (benzoporphyrin derivative) for the targeting of angiogenic endothelial cells. They showed that peptide-conjugated liposomal PS exhibited strong suppression of tumor growth compared to those targeted with NPs without APRPG. Besides, there is a growing interest in the development of particles for VTP and imaging. Kopelman et al43 were the first to describe the synthesis of a nonbiodegradable NP for the diagnosis and treatment of brain cancer. These nanosystems were composed of polyacrylamide, MRI contrast agents (for imaging), PSs (for PDT), PEG chains (for a better solubility and biodistribution) and an RGD peptide moiety (for the targeting of neovasculature). In vivo experiments on rats bearing intracerebral 9L tumors showed that the MRI contrast agent provided real-time tumor kill measurement.

The goal of our study was to design and to evaluate a new nanoplatform consisting of a surface-localized tumor vasculature targeting NRP-1 and displaying photodynamic and imaging agents for iPDT of GBM guided by interventional MRI. An NP called AGuIX was used; it is composed of gadolinium chelates, DOTAGA, 2,2′,2″-(10-(2,6-dioxotetrahydro-2H-pyran-3-yl)-1,4,7,10-tetraazacyclododecane-1,4,7-triyl)triacetic acid, covalently grafted to a polysiloxane core; its synthesis and properties have already been presented in the literature.36,4448 A PS, a tetraphenylporphyrin (TPP) and a peptide (KDKPPR) targeting the NRP-1 receptor overexpressed by tumor angiogenic vessels were then grafted on the surface of this particle. The choice of the AGuIX NPs was driven by several points. First, they display a hydrodynamic diameter <10 nm, even after functionalization, which is small enough to provide exclusive renal excretion and well adapted for further clinical development. They can also accumulate in the tumor by the EPR effect. So far, no toxicity has been noticed during regulatory toxicity tests on rodents and monkeys, and AGuIX has been recently accepted for a Phase I clinical assay (EudraCT no: 2015-004259-30). The presence of gadolinium enables the NPs to be used as a positive MRI contrast agent; it will therefore be possible to detect the tumor tissue, to determine an accurate position for the PDT fiber and to follow up by noninvasive imaging photodynamic efficiency.

In this study, it was decided not to graft separately the PS and the targeting peptide on the particle but to graft directly the compound [email protected] The major interest is to improve the synthesis reproducibility by performing only one conjugation step on the particle, to conserve a good homogeneity for the functionalized particles and, finally, to quantify easily the number of targeting peptides on the particle, thanks to the strong absorbance of the PS. AGuIX particles present primary amines on their surface, and our group has recently published a study in which these groups were used to graft a TPP molecule on AGuIX.25 In that case, the porphyrin used presented an NHS ester function that could react with an amino group to form a covalent amide bond. In the present study, a new functionalization approach had to be developed in order to maintain the affinity of the KDKPPR peptide for NRP-1 receptor. First, a thiol function was added to the surface of the particles and reacted in a second step with the [email protected] compound to form a stable thioether bond. Maleimide reactions are specific for thiols at the used pH of 7.5.38 With this strategy, we can easily modulate the number of [email protected] per particle; in our case, one compound was added for 15 Gd3+ (corresponding to approximately one PS for one or two NPs). With this ratio, a good solubility and colloidal stability in aqueous solutions were maintained and an appropriate PDT efficiency was obtained. Besides, the magnetic properties of the functionalized particles (r2/r1 =1.6 s−1·mM−1 at 37°C and 60 MHz) are consistent with their use as a positive contrast agent in MRI to guide and follow PDT treatment. The same process was used for the coupling of a scramble peptide (KRPKPD) coupled to the PS.

In vitro, in the absence of light irradiation, the functionalized NPs showed no cytotoxicity for the concentration of PS <10 μM using HUVEC overexpressing NRP-1 receptor. The singlet oxygen quantum yield was not altered by the grafting on the NPs, showing that the PS molecules could be photoactivated to yield photocytotoxic effects in vitro and in vivo (ΦΔ =20% for [email protected] in DMSO and ΦΔ =28% for [email protected]@KDKPPR in water). This is consistent with previous studies on this kind of NPs bearing chlorin or porphyrin PSs.11,25,29 The way by which the PS is added in or on the NP is really crucial because it can have an impact on its photophysical properties and therefore on its photocytotoxic effect. Chu et al designed silica-based NPs encapsulating methylene blue. They showed that the singlet oxygen formation with the particle was lower than with the methylene blue alone probably because of dimer’s formation inside the particle.49 A comparative study was also performed by Tang et al50 to evaluate the encapsulation of methylene blue in two types of silica-based NPs. One was prepared using tetraethoxysilane and the other one using methyltrimethoxysilane and phenyltrimethoxysilane as precursors. If the PS loading was higher with the Stöber process, the kinetic of singlet oxygen formation was lower. Our strategy describes different advantages for the PS photophysical properties. As the PS is grafted on the surface of the particle, the singlet oxygen does not need to diffuse in and out of the particles and the grafting prevents the PS aggregation. The photocytotoxic effect was confirmed in vitro on HUVEC. Indeed, we observed that the presence of the peptide units (KDKPPR) onto the [email protected] increased its PDT effect, probably due to an improved cellular uptake.

Molecular affinity was investigated for functionalized particles. Even after grafting on NPs, the KDKPPR peptide was still able to bind NRP-1 protein. Indeed, [email protected]@KDKPPR showed a relevant molecular affinity of 19 μM, whereas the [email protected] demonstrated a molecular recognition for NRP-1 protein of 81 μM (four times higher) and the scramble particles, [email protected]@scramble, had one of 176 μM (~10 times higher).

The affinity was also evaluated in vivo, thanks to dorsal skinfold chamber studies performed after intravenous injection of NPs in mice bearing U87 xenografts tumors. [email protected] and [email protected]@scramble NPs were located in the blood vessels at 1 h post injection but disappeared from them at 6 h, due to the fenestration of the tumor vasculature. On the contrary, [email protected]@KDKPPR particles were located onto the vessel walls of the tumor 1 h after intravenous injection and were still present 24 h after the administration. These qualitative fluorescence images support the important characteristics of our NPs; nevertheless, it will be helpful to complete them by quantitative data. [email protected]@KDKPPR particles seem therefore really promising to detect the proliferating part of the tumor by MRI and in the context of VTP. The long-term targeting of the neovasculature seems an important asset for a further fractionated treatment.


In this study, we designed a new AGuIX NP for MRI-guided VTP of GBM. It combines MRI contrast agents, a PS for the photodynamic effect and a new peptide targeting NRP-1 receptor overexpressed by the tumor vasculature. It was shown that the photophysical properties of the PS and the peptide affinity for NRP-1 protein were preserved after the grafting onto AGuIX. The cellular uptake of NPs by HUVEC was increased twice compared to those without peptide or with a scramble peptide. The in vivo selectivity, evaluated using a skinfold chamber model in mice, confirmed that the KDKPPR-conjugated NPs were localized on the tumor vessel walls, highlighting their potential for VTP. Other experiments are in progress to fully describe the biodistribution of these NPs and to follow the VTP efficiency. T1-weighted imaging after intravenous injection of the targeted NPs will allow us to define the real tumor volume, taking into account the proliferating part of the tumor tissues. Besides, the drug-light interval will be optimized in real time according to the MRI signal intensity. Finally, the optimal irradiation scheme for iPDT will be developed as part of efficiency, inflammation and vascular responses.


This work was supported by the research funds of the French Ligue Nationale Contre le Cancer and EURONANOMED II “PhotoBrain” project (no ANR-14-ENM2-0001-01). The authors thankfully acknowledge Kevin Lemoine for his help in the synthesis of NPs. F Lux and O Tillement have one patent to disclose: WO2011135101. This patent protects some of the NPs described in this publication: AGuIX.


The authors have no other relevant affiliations or financial involvement with any organization or entity with a financial interest in or financial conflict with the subject matter or materials discussed in the manuscript apart from those disclosed. The authors report no other conflicts of interest in this work.



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