Theranostics 2014; 4(2):134-141. doi:10.7150/thno.7217 This issue
1. Institute of Functional Nano & Soft Materials (FUNSOM), Soochow University, Suzhou, Jiangsu 215123, China
2. Laboratory of Molecular Imaging and Nanomedicine (LOMIN), National Institute of Biomedical Imaging and Bioengineering (NIBIB), National Institutes of Health (NIH), Bethesda, Maryland 20892, United States
3. Center for Molecular Imaging and Translational Medicine School of Public Health, Xiamen University, Xiamen 361005, China
† These authors contributed equally to this work
Herein, we for the first time report a novel activatable photoacoustic (PA) imaging nano-probe for in vivo detection of cancer-related matrix metalloproteinases (MMPs). A black hole quencher 3 (BHQ3) which absorbs red light is conjugated to near-infrared (NIR)-absorbing copper sulfide (CuS) nanoparticles via a MMP-cleavable peptide linker. The obtained CuS-peptide-BHQ3 (CPQ) nano-probe exhibits two distinctive absorption peaks at 630 nm and 930 nm. Inside the tumor microenviorment where MMPs present, the MMP-sensitive peptide would be cleaved, releasing BHQ3 from the CuS nanoparticles, the former of which as a small molecule is then rapidly cleared out from the tumor, whereas the latter of which as large nanoparticles would retain inside the tumor for a much longer period of time. As the result, the PA signal at 680 nm which is contributed by BHQ3 would be quickly diminished while that at 930 nm would be largely retained. The PA signal ratio of 680 nm / 930 nm could thus serve as an in vivo indicator of MMPs activity inside the tumor. Our work presents a novel strategy of in vivo sensing of MMPs based on PA imaging, which should offer remarkably improved detection depth compared with traditional optical imaging techniques.
Keywords: Peptide, Photoacoustic imaging, Enzyme cleavage, Copper sulfide, MMPs detection.
Matrix metalloproteinases (MMPs) are a family of zinc-dependent endopeptides that degrade proteins in the extracellular matrix (ECM) and play an important role in the development of various diseases including cancer, inflammatory, neurological and cardiovascular diseases [1, 2]. As for cancer, MMPs not only have distinct roles in tumor angiogenesis, but also affect multiple signaling pathways to control the balance between growth and antigrowth signals in the tumor microenvironment . Developing a noninvasive imaging tool to assess MMP activity in vivo would help to understand the roles of MMPs in tumor microenvironments. Recently, various proteases activatable optical probes have been developed for in vivo MMP imaging. These probes usually consist a near-infrared fluorescence dye and a quencher at the opposite ends of an MMP substrate (peptide), and are in their dark quenched state in the absence of MMPs [4-6]. Upon exposure to MMPs, the activatable peptide is cleaved by MMPs, releasing the free fluorescent dye which provides the recovered fluorescence to be detected [7-11]. According to the literatures, many groups have reported that optical imaging, especially fluorescence imaging, can be used to detect the MMP activities in vivo [6, 7, 12]. However, the optical imaging has some limitation such as tissue autofluorescence, limited light penetration depth and poor spatial resolution, which may affect the precise of the results.
Photoacoustic (PA) imaging detects ultrasound waves generated by photothermal expansion of light-absorbing tissues or contrast probes under pulsed laser irradiation. As a recently developed imaging technology, PA imaging offers significantly improved in vivo imaging depth and resolution limit compared with traditional in vivo optical imaging [13-15]. While traditional fluorescence imaging usually can only detect signals no deeper than a few millimeters, PA imaging exhibits dramatically enhanced tissue penetration (up to about 7 centimeters so far) and is thus a more clinically relevant imaging technique. Moreover, without the tissue-scattering issue during signal collection, which largely limits the spatial resolution of in vivo fluorescence imaging (e.g. scattering of emitting light by biological tissues), in vivo PA imaging is able offer much better imaging resolution. Nowadays, various organic or inorganic nanoparticles, including porphyrin shell , gold nanoparticles [17, 18], carbon nanotubes [19-21] and nano-graphene [22, 23], all with high near-infrared (NIR) absorbance, have widely explored for in vivo PA imaging. However, the use of photoacoustic imaging for detection of the in vivo MMPs activity has not yet been reported to our best knowledge.
In this work, copper sulfide (CuS) nanoparticles, which exhibit strong NIR absorbance and have been widely used as a photothermal agent for cancer ablation therapy [24-26], are conjugated with a red-light-absorbing organic dye, BHQ3, via a MMPs cleavable peptide. The obtained CuS-peptide-BHQ3 (CPQ) nano-probe exhibits strong photoacoustic signal at the wavelengths of 680 nm and 930 nm before enzyme cleavage, owing to the absorption of BHQ3 and CuS nanoparticles, respectively. In the presence of MMPs expressed inside the tumor, our CPQ nano-probe is recognized by the protease, releasing free BHQ3 which as a small molecule could be rapidly washed out from the tumor area, leaving bare CuS nanoparticles which would retain inside the tumor for a much longer period of time (Fig. 1). The PA signal ratios recorded at two different wavelengths, 680 nm / 930 nm, is then significantly decreased. Therefore, this novel nano-probe allows us for the first time using PA imaging to investigate the in vivo MMP activity in the animal tumor model.
A schematic illustration of the CPQ nano-probe that can be activated by MMPs. In this nano-probe, BHQ3 is conjugated to CuS nanoparticles through a MMP-cleavable peptide linker, and thus could be released from nanoparticles upon exposure to MMPs.
Copper sulfide (CuS) nanoparticles were synthesized in the aqueous phase. In brief, 14 mg of copper (II) chloride (CuCl2) and 20 mg of sodium citrate were dissolved in 100 ml of ultra pure water upon stirring at room temperature. After 5 min, 7.8 mg of sodium sulfide was added into the solution. The mixture was reacted at room temperature over night. The citrate-coated CuS nanoparticles were obtained and washed with water by centrifugation at 15,000 rpm to remove excess reagents. The product was stored in 4 oC for next experiments.
MMP-sensitive substrate peptide was synthesized as previously reported. Briefly, the side chain protected MMP substrate, GPLGVRGKGG, was synthesized manually on 2-Cl-Trt resin at 0.1 mmol scale using the standard Fmoc (N-(9-fluorenyl) methoxycarbonyl) protocol and (benzotriazol-1-yloxy) tripyrrolidinophosphonium hexafluorophosphate (PyBOP) activation. The MMP substrate is recognized and cleaved between Gly and Val as indicated by bold italics. After being released from the resin by Dichloromethane (DCM) containing 1% trifluoroacetic acid (TFA), the peptide was purified by RP-HPLC on a C18 semi-preparative column using a linear gradient of 10% to 55% acetonitrile/water (0.1% TFA) for 30 min at a 10 ml/min flow rate, and then lyophilized. Next, the side-chain protected MMP substrate was reacted with a black hole quencher-3 (BHQ-3) in DMF solution containing 2 % of DIPEA for 2 hours. After purification, BHQ-3 conjugated MMP substrate (peptide-BHQ3, PQ) was precipitated in cold ether. The pellet was collected by centrifuge and dissolved in TFA cocktail for 2 hours to remove the side chain protection group. After that, free amine on Lysine was exposed for conjugation with CuS. All the final products were confirmed by analytical reversed-phase high performance liquid chromatography (RP-HPLC, DIONEX, CA), using 5% to 65% acetonitrile containing 0.1% TFA versus distilled water containing 0.1 % TFA over 30 min at a flow rate of 1 ml/min (C18 column, 5 μm, 120Ao, 250 × 4.6 mm) and LC-mass spectroscopy. The purity of the product is > 95%. The obtained peptide-BHQ3 (PQ) probe was dissolved in dimethyl sulphoxide (DMSO) solution and stored in -20 oC
~ 1 mg of N-(3-dimethylaminopro-pylN'-ethylcarbodiimide) hydrochloride (EDC, Sigma-Aldrich) and ~1 mg of Sulfo-NHS was firstly added to the solution of CuS solution (0.8 mg/ml, 200 μl) at pH 7.4 to activate the carboxyl group of CuS nanoparticles. After 20 min, 10 ml of PQ (20 mg/ml) with amino groups was added into the solution and reacted over night at room temperature by avoiding light. Excess PQ was removed by centrifugation at 15,000 rpm and washed away with ultra pure water for two times.
The activity of the CPQ nano-probe was investigated by incubating the probe (0.8 mg/ml) in the reaction buffer (50 mM Tris•HCl, 10 mM CaCl2•2H2O, 0.15 M NaCl, 0.05% Brij35; pH 7.8 TCNB buffer) containing 40 nM of catalytic domain of MMP-13. The UV-vis-NIR spectrums of the samples were measured using a spectrofluorometer (F-7000 Fluorescence Spectrophotometer, Hitach, Tokyo, Japan) at indicated time at 37 °C for 6 h. Each time before samples were measured, cleaved BHQ3 containing fragment was removed by centrifuge. Three independent experiments were conducted in parallel.
All cell culture related reagents were purchased from Gibico. SCC7 breast cancer cells were cultured in RPMI-1640 cell medium supplemented with 10% FBS and 1% penicillin-streptomycin. Athymic nude mice were obtained from Harlan laboratories (Frederick, USA) under protocols approved by National Institutes of Health Clinical Center Animal Care and Use Committee (CC/ACUCC). The SCC7 tumor models were generated by subcutaneous injection of 1×106 cells in 60 μl PBS into the right backside of nude mice. The mice were used for treatment when the tumor volume reached ~100 mm3.
For PA imaging, nude mice bearing SCC7 tumors were intratumorally injected with CPQ (100 µl, 0.8 mg/ml) and imaged at different time points post injection by a Vevo 2100 LAZR system (VisualSonics Inc.) at wavelength at 680 nm and 930 nm which are contributed by BHQ3 and CuS nanoparticles, respectively. For quantitative calculation, the regions of interest (ROI) were drawn over tumor, with the averaged PA signals measured.
We prepared CuS nanoparticles in the aqueous solution following a literature protocol . In brief, copper chloride (CuCl2) was reacted with sodium sulfide (Na2S) in the present of sodium citrate upon stirring overnight. The citrate-coated CuS nanoparticles were obtained and washed by centrifugation at 15,000 rpm to remove excess reagents . Transmission electron microscopy (TEM) image showed that the size of CuS nanoparticles was about 20 nm (Fig. 2a). UV-vis-NIR spectrum of CuS nanoparticles revealed a high NIR absorbance band (Fig. 2b). The citrate-coated CuS nanoparticles were very stable in different physiological solutions including phosphate buffer (PBS), fetal bovine serum (FBS) and cell medium (Fig. 2b). In order to study the cytotoxicity of CuS, the standard methyl thiazolyltetrazolium (MTT) assay was carried out to determine relative viabilities of SCC7 breast cancer cells after being incubated with various concentrations of CuS nanoparticles for 24 h. No obvious toxicity of those nanoparticles to cells was observed even at high concentrations up to 100 µg/ml (Supplementary Material: Figure S1).
The enzyme sensitive probe, peptide-BHQ3 (PQ) (BHQ3-Gly-Pro-Leu-GLy-Val-Arg-Gly-Lys-Gly-Gly-(amide)) was synthesized, purified by high performance liquid chromatography (HPLC), and characterized by LC-mass spectroscopy, as previously reported[4-6] (Supplementary Material: Figure S2). In order to synthesize the MMP-activatable PA imaging nano-probe, the carboxyl groups on the citrate-coated CuS nanoparticles (0.8 mg/ml, 200 μl) were firstly activated by N-(3-dimethylaminopropyl - N'-ethylcarbodiimide) hydrochloride (EDC) and N-Hydroxysulfosuccinimide (Sulfo-NHS). After 20 min, PQ (10 ml, 20 mg/ ml) was added into the CuS solution and reacted overnight avoiding light. The obtained product was purified by centrifugation at 15,000 rpm and washed with ultra pure water twice. UV-VIS-NIR spectra uncovered a strong absorption peak at 630 nm, which was attributed to the attachment of BHQ3 on CuS nanoparticles (Fig. 2c). Control experiments evidenced that the PQ was covalently conjugated to CuS nanoparticles instead of physical adsorption (Supplementary Material: Figure S3). A loading efficiency at 12.5% (PQ: CuS weight ratio) was achieved in this system.
The characterization of CuS nanoparticles and CPQ nano-probe. (a) A TEM image of CuS nanoparticles showing the average particle size at ~ 20 nm. (b) UV-vis-NIR spectral of CuS nanoparticles in water solution. Inset: the photos of CuS solution (0.8 mg/ml) in different solutions including water, PBS, FBS and cell medium. (c) UV-vis-NIR spectral of CuS nanoparticles before and after conjugation of peptide-BHQ3. (d)The size and Zeta potential distribution of CuS nanoparticles, CPQ nano-probe, and the CPQ after enzyme cleavage. Conjugation of peptide-BHQ3 resulted in the significant increase of the nanoparticle zeta potential, which decreased again after enzyme cleavage.
UV-vis-NIR spectra of CPQ nano-probe before and after enzyme cleavage. (a&b) UV-vis-NIR absorbance spectra of CPQ with (a) or without (b) MMP-13 addition measured at different time points. (c) UV-vis-NIR absorbance spectra of CPQ added with both MMP-13 and MMPI-III, the latter of which could inhibit the MMP-activity. (d) The relative absorbance ratio change of 630 and 930 nm in (a-c). We normalized the relative absorbance ratio (630 nm : 930 nm) at the beginning of our experiment to be 1. Error bars were based on standard deviations of three parallel samples.
In order to demonstrate the response of our nano-probe to MMPs, CPQ (0.8 mg/ml, 100 μl) was incubated with recombinant human MMP-13 enzyme (100 μl, 40 nM) in the absence or presence of the MMP inhibitor III (MMPI-III, 10 μl, 50 nM), a broad spectrum MMP inhibitor that could inhibit the activities of many MMPs including MMP-13, at 37oC in the TCNB buffer solution (50 mM Tris•HCl, 10 mM CaCl2•2H2O, 0.15 M NaCl, 0.05% Brij35; pH 7.8). At different time intervals, portions of the solutions were collected and centrifuged at 15,000 rpm for 5 min to remove supernatant. The sediment was then re-dissolved in water and recorded by UV-vis-NIR spectrometer. An obvious decrease of the absorption peak at 630 nm was observed for CPQ added with MMP-13 within 2 hours, owing to the protease induced peptide cleavage that released free BHQ3 (Fig 3a). In marked contrast, no significant change in the UV-VIS-NIR spectra of CPQ without adding MMP-13, or the mixture of CPQ and MMP-13 but with addition of protease inhibitor MMPI-III, was noticed, suggesting our CPQ nano-probe was stable in the absence of MMP-13 activity (Fig 3b&c). Based on the change of absorbance ratio at 630 nm, we can then use this nano-probe to determine MMPs activity (Fig. 3d).
Before using photoacoustic imaging to detect the activity of MMPs in vivo, we first measure the PA signals of free BHQ3 (0.1 mg/ml), free CuS nanoparticles (0.8 mg/ml), and CPQ (0.8 mg/ml) before and after enzyme cleavage in solutions. Because the wavelength range of the laser in our PA instrument was 680-970 nm, we chose 680 nm instead of the peaked absorbance wavelength (630 nm) for BHQ3 imaging. While the PA signals of free BHQ3 were rather strong at 680 nm but barely detectable at 930 nm, CuS nanoparticles offered much stronger PA signals at 930 nm than that at 680 nm (Fig 4a). As expected, CPQ nano-probe showed strong PA signals at both 680 nm and 930 nm prior to enzyme cleavage (Fig. 4a). However, after being treated with MMP-13 and purification to remove detached dye molecules, the PA signal of CPQ at 680 nm was significantly decreased, while that at 930 nm had little change (Fig. 4a), consistent to the absorbance data (Fig. 2a).
Nanoparticles with large sizes usually would show much longer retention in the tumor compared to small molecules, which are easily washed out and excreted after administration. This is the basic assumption of our MMP-responsive PA imaging nano-probe. To verify our speculation, mice bearing SCC7 tumors were intratumorally injected with free BHQ3 (0.1 mg/ml, 100 μl) and free CuS nanoparticles (0.8 mg/ml, 100 μl), and imaged by a Vevo 2100 LAZR system (Visual Sonics Inc.). Right after injection, BHQ3 treated mice exhibited very strong 680 nm PA signals, which was rapidly diminished in just 2 hours (Fig 4 b&c). In contrast, CuS nanoparticles injected tumors exhibited high 930 nm PA signals, which retained almost at constant level over 24 hours (Fig 4 b&c).
At last, we used our CPQ nano-probe for in vivo MMPs detection by PA imaging. The SCC7 tumor modal, which has been extensively documented to show high levels of MMP-13 expression [4-7, 12, 27], was chosen in our experiments. After intratumoral injection of CPQ (0.8 mg/ml), PA images were taken using 680 nm and 930 nm excitations. Right after injection, strong PA signals at both 680 nm and 930 nm showed up in the SCC7 tumor. Interestingly, the PA signals at 680 nm remarkably decreased over time due to MMP-induced peptide cleavage that released BHQ3 (Fig 4b), while that at 930 nm showed little change within 24 h (Fig 4b&d). Note that since the MMP-induced cleavage of the CPQ probe as well as the washing out of released BHQ3 molecules from the tumor all took time, the PA signals at 680 nm showed no significant changes in the first 2 hours but dramatically decreased at later time points. In order to confirm this phenomenon was due to MMPs induced specific cleavage, MMP inhibitor-III was injected into the tumor 30 min prior to the administration of CPQ nano-probe to inhibit MMP-activity. In this case, no significant change of PA signals at both 680 nm and 930 nm was observed within 24 hours post injection, suggesting that the MMP inhibitor could inhibit the MMPs enzyme activity in vivo and prevent enzyme-induced cleavage of the MMP-specific peptide (Fig 4b&d).
In vivo MMP-sensing by photocoustic imaging. (a) Solution PA images of BHQ3 (0.1 mg/ml), CuS (0.8 mg/ml), CPQ nano-probe (0.8 mg/ml), and CPQ + MMP-13. (b) In vivo PA imaging of mice with tumors injected with free BHQ3, free CuS, CPQ nano-probe, and CPQ with MMPI-III co-injection. The images were taken at different time post injection. (c) The change of tumor PA signals of the control groups including free BHQ3 at 680 nm and free CuS nanoparticles at 930 nm. (d) The PA signal ratios (680 nm/ 930 nm) of the CPQ group and CPQ + MMPI-III group measured at different time post injection. The background PA signal before injection was subtracted in the above values. Error bars were based on standard deviations of 3-4 mice per group. The 680 nm/ 930 nm PA signal ratio at the tumor after injection of CPQ nano-probe could be used to detect MMP-activities in vivo.
In order to accurately calculate the PA signal at 680 nm and 930 nm, we drew up the region-of-interest (ROI) in the PA images to count the PA signals, with the background PA signals (before injection of CPQ nano-probe) subtracted. The PA signal ratio of 680 nm: 930 nm was calculated. It was found that in tumors injected with the CPQ probe, this ratio showed a remarkable decrease, which was not observed if MMPI-III was pre-injected to inhibit the MMP-activity inside the tumor (Fig. 4d). Therefore, we could use this nano-probe to detect the in vivo MMP-activity by PA imaging.
We have demonstrated a MMP enzyme-sensitive nano-probe with CuS nanoparticles and BHQ3 molecules conjugated together though a MMP-cleavable peptide linker for in vivo MMP detection under PA imaging. While showing strong PA signals at both 680 nm and 930 nm wavelengths owing to the optical absorbance of BHQ3 and CuS nanoparticles, respectively, the CPQ nano-probe in the presence of MMPs can be tailored to discard BHQ3, resulting in remarkably decreased PA signals at 680 nm in comparison to that at 930 nm. Such a simple and straightforward strategy allows us for the first time to use PA imaging for in vivo detection of a specific enzyme activity. Compared with traditional optical imaging (e.g. fluorescence imaging) used in MMP detection, PA imaging would exhibit dramatically enhanced tissue penetration, and is expected to offer markedly improved in vivo spatial resolution during imaging owing to its unique mechanism[15, 17]. Our results would encourage further exploration of smart imaging probes for in vivo detection of other classes of important functional biological molecules based on PA imaging.
Fig.S1 - Fig.S3.
This work was partially supported by the National "973" Program of China (2011CB911002, 2012CB932601, 2013CB733802, 2014CB744503), the National Natural Science Foundation of China (51002100, 51072126, 51373144, 81371596), and the Intramural Research Program (IRP) of the National Institute of Biomedical Imaging and Bioengineering (NIBIB), NCI), National Institutes of Health (NIH). Kai Yang was supported by a scholarship from the China scholarship Council (CSC).
The authors have declared that no competing interest exists.
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Corresponding authors: shawn.chengov (X. Chen) or zliuedu.cn (Zhuang Liu).