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Nanomedicine (Lond). 2016 August; 11(15): 1947–1955.
Published online 2016 July 26. doi:  10.2217/nnm-2016-0147
PMCID: PMC4996152

Efficacy and pharmacokinetics of a modified acid-labile docetaxel-PRINT® nanoparticle formulation against non-small-cell lung cancer brain metastases



Particle Replication in Nonwetting Templates (PRINT®) PLGA nanoparticles of docetaxel and acid-labile C2-dimethyl-Si-Docetaxel were evaluated with small molecule docetaxel as treatments for non-small-cell lung cancer brain metastases.

Materials & methods:

Pharmacokinetics, survival, tumor growth and mice weight change were efficacy measures against intracranial A549 tumors in nude mice. Treatments were administered by intravenous injection.


Intracranial tumor concentrations of PRINT-docetaxel and PRINT-C2-docetaxel were 13- and sevenfold greater, respectively, than SM-docetaxel. C2-docetaxel conversion to docetaxel was threefold higher in intracranial tumor as compared with nontumor tissues. PRINT-C2-docetaxel increased median survival by 35% with less toxicity as compared with other treatments.


The decreased toxicity of the PRINT-C2-docetaxel improved treatment efficacy against non-small-cell lung cancer brain metastasis.

Keywords: : acid-labile docetaxel prodrug, blood–brain barrier, Particle Replication in Non-wetting Templates (PRINT)® PLGA nanoparticle

Lung cancer, 80% comprised of non-small-cell lung cancer (NSCLC), is one of the leading causes of cancer worldwide and the USA [1–3]. Lung cancer is the most common primary tumor responsible for brain metastases [19]. Among those diagnosed with NSCLC, 20–50% of patients will develop metastatic brain disease [2], 10% with brain metastases at initial diagnosis [4] and another 30% later in their disease course following standard therapies.

Despite multimodality therapy with combinations of surgery, radiation therapy and chemotherapy, median survival remains less than one year for NSCLC brain metastatic patients [1,2]. NSCLC brain metastases are generally nonresponsive to first-line, single agent platinum-based chemotherapy [2,5]. Docetaxel (Taxotere®) is a standard second line systemic chemotherapy for NSCLC brain metastases [2].

As brain metastasis recurrence is common among patients with advanced NSCLC, optimizing the passage of anticancer agents across the blood–brain barrier, increasing chemotherapeutic concentrations in intracranial and extracranial tumors and decreasing systemic toxicities are important considerations to improve treatment of this disease. Newer delivery techniques, like nanoparticles and carrier-mediated technologies, have illustrated these advantages in the setting of intracranial cancer [6–10]. Clinically, activity of nanoparticle-based systemic therapy has been illustrated in the setting of breast cancer brain metastases, another solid tumor type where brain metastasis recurrence is common [11].

While several studies have shown the superiority of nanoparticle anticancer agents in intracranial malignancies over standard formulations, the mechanism underlying this observation has yet to be fully elucidated [6–12]. The working hypothesis has been that prolonged exposure to anticancer agents afforded by nanoparticle technology may increase passage of small molecules across the ‘blood tumor barrier’, a barrier potentially compromised by the presence of tumor [12].

Particle Replication in Nonwetting Templates (PRINT)® of poly-(lactic acid-co-glycolic acid)-docetaxel

PRINT-poly(lactic acid-co-glycolic acid) (PLGA) nanoparticle formulations of docetaxel have shown superior pharmacokinetic and efficacy profiles over that of standard small molecule docetaxel (SM-docetaxel) in an extracranial NSCLC xenograft model [13]. Given the superior intracranial pharmacokinetic and efficacy profiles for nanoparticle anticancer agents in solid tumors, and the activity of docetaxel in NSCLC, we hypothesized that PRINT PLGA-docetaxel formulations would increase docetaxel concentrations in intracranial tumors and decrease intracranial tumor growth as compared with SM-docetaxel, thereby improving survival. We expected that the acid labile C2-prodrug PRINT® PLGA formulation (PRINT-C2-docetaxel), which should be specifically activated by an acidic tumor microenvironment, would increase efficacy with decreased toxicity over PRINT-PLGA docetaxel (PRINT-docetaxel).

Methods & materials

Pharmacologic agents

Small molecule docetaxel (SM-docetaxel; Taxotere) was obtained from the University of North Carolina Hospitals Pharmacy. A single step reaction of docetaxel with chlorodimethylethylsilane was performed to generate the C2′ alcohol of taxane, the silyl ether docetaxel prodrug C2, as previously described [13]. PRINT-C2-docetaxel and PRINT-docetaxel nanoparticles were fabricated as previously described, to form the same sized cylindrical particles of PLGA polymer with a diameter of 80 nm and height of 320 nm, with similar drug loading [13,15–18]. Briefly, a thin film of PLGA and Docetaxel or C2-Docetaxel was deposited on a 6″ × 12″ sheet of PET (poly[ethylene terephthalate]) by spreading 150 µl of a 10 mg/ml PLGA and 10 mg/ml docetaxel or C2-docetaxel chloroform solution using a # 5 Mayer Rod (R.D. Specialties). The solvent was evaporated with heat. The PET sheet with the film was then placed in contact with the patterned side of a mold and passed through heated nips (ChemInstruments Hot Roll Laminator) at 130°C and 80 psi. The mold was split from the PET sheet as they both passed through the hot laminator. The patterned side of the mold was then placed in contact with a sheet of PET coated with 2000 g/mol PVOH (poly[vinyl alcohol]). This was then passed through the hot laminator to transfer the particles from the mold to the PET sheet. The mold was then peeled from the PET sheet. The particles were removed by passing the PVOH coated PET sheet through motorized rollers and applying water to dissolve the PVOH to release the particles. To remove excess PVOH, the particles were purified and then concentrated by tangential flow filtration (Spectrum Labs).

A549 intracranial xenograft studies

All animal studies protocols were approved by the University of North Carolina, Chapel Hill Institutional Animal Care and Use Committee, executed by the UNC Animal Studies Core, and performed as previously described [6,13,14]. Briefly, A549-luc-c8, acquired from Caliper Life Sciences (P/N 119266, Perkin Elmer), was propagated in culture in DMEM 10% FBS supplemented with G418 (200 μg/ml). For intracranial injections, cells were harvested in log-phase growth and suspended with 5% methylcellulose in culture media. Eight to ten week Foxn1 nu/nu mice (UNC Animal Studies Core) were implanted with 200,000 cells/5 uls of cell suspension through stereotactic intracranial injection in the right striatum. Animal weights were collected from injection to sacrifice three-times weekly. To determine tumor volumes, mice were anesthetized, injected intraperitoneally with D-Luciferin dissolved in PBS (150 mg/kg; Caliper Life Sciences, MA, USA), then imaged by IVIS Lumina camera (Caliper Life Sciences). Images were analyzed with Living Image 4.0 software (Caliper Life Sciences). All values were corrected for background and recorded as photons/second.

For pharmacokinetic studies, tumors were grown to greater than 2 mm in diameter correlating with bioluminescence signal which occurred between 30 and 40 days post-intracranial injection of tumor cells. The following treatments were given once by IV a) SM-docetaxel at 15 mg/kg, b) PRINT-docetaxel at 30 mg/kg, c) PRINT® C2- docetaxel at 30 mg/kg. These doses were in SM-docetaxel equivalents and below previously determined maximum tolerated doses for nontumor bearing nude mice (nu/nu) [13]. Tumors were collected at n = 3 per time point per treatment, as shown in Figure 1. PBS controls (n = 2) were collected as negative controls for pharmacokinetic analysis. Figures were generated using GraphPad Prism 6.

Figure 1.
Individual and mean concentrations of docetaxel and C2-docetaxel after administration of SM-docetaxel at 15 mg/kg, PRINT-docetaxel at 30 mg/kg, or PRINT-C2-docetaxel at 30 mg/kg docetaxel, by IV × 1 to nu/nu mice bearing intracranial A549 tumors. ...

For efficacy studies, mice were grouped between 21 and 28 days post-injection of tumor cells by intracranial bioluminescence signals, (nu/nu) [13]. Tumor growth by bioluminescence was monitored weekly. Mice weights were collected three-times a week throughout efficacy studies. Two separate efficacy studies were performed and experiments combined, for n > 9/group. Tumor volume change and weight change figures were generated using GraphPad Prism 6, with groups normalized to a baseline value from initial tumor volumes or initial weights at grouping.

Pharmacokinetics analysis

After sacrifice, plasma, contralateral brain, intracranial tumor and the peritumor brain tissue consisting of the 2 mm perimeter surrounding intracranial tumor were collected and snap frozen in liquid nitrogen. The associations between injected agents (SM-docetaxel, PRINT-docetaxel and PRINT-C2-docetaxel) and downstream pharmacokinetic analytes (docetaxel and C2-docetaxel) are summarized in Table 1. Docetaxel was measured in all samples after administration of SM-docetaxel, PRINT-docetaxel and PRINT-C2-docetaxel, as previously described [13]. The analysis of docetaxel in PRINT-docetaxel samples measured nanoparticle-encapsulated + released docetaxel. The analysis of docetaxel from PRINT-C2-docetaxel samples measured converted C2-docetaxel, released from nanoparticle-encapsulation [13]. C2-docetaxel was measured in all samples after administration of PRINT-C2-docetaxel, representative of nanoparticle-encapsulated + released C2-docetaxel prodrug. All samples were analyzed using liquid chromatography tandem mass spectroscopy (LC-MS/MS), as previously described [13].

Table 1.
Pharmacokinetic analytes of injected agents.

Data analysis & statistical methods

Generally, all data analysis and statistical methods were performed as previously described [6,13,14,17].

Pharmacokinetic analysis

Pharmacokinetic data were analyzed by noncompartmental methods using WinNonLin Professional Edition version 6.1 (Pharsight Corp, NC, USA). The area under the concentration curve (AUC) versus time was calculated from 0 to tlast. The conversion of PRINT-C2-docetaxel prodrug to active docetaxel was calculated from the PRINT-C2-docetaxel AUCs as follows: [AUC_doctaxel/(AUC_C2-docetaxel+AUC_docetaxel)]*100 [13].


The Kaplan–Meier method and Log rank test were used to estimate and compare median survival between treatment groups. Median survivals, along with their 95% confidence intervals, and Log-rank test p-values were reported.

Tumor volume changes & mouse weight change analysis

Both fold change in tumor volumes and mice weight over time were determined relative to treatment start date. Linear mixed models, with a random intercept and slope, were used to evaluate changes over time, overall and between groups. SAS statistical software, v9.3, was used for these analyses (NC, USA).


Pharmacokinetics of SM-docetaxel, PRINT-docetaxel & PRINT-C2-docetaxel in intracranial NSCLC tumor-bearing nude mice

To demonstrate that PRINT-docetaxel and PRINT-C2-docetaxel formulations can increase intracranial tissue exposure to docetaxel, a pharmacokinetic study was performed using the A549 human non-small-cell lung cancer (NSCLC) brain metastases xenograft murine model with administration of SM-docetaxel, PRINT-docetaxel and PRINT-C2-docetaxel. This KRAS-activated NSCLC background was shown to be responsive to both PRINT-docetaxel formulations in a subcutaneous tumor model [13].

Table 1 summarizes the association of analytes (docetaxel or C2-docetaxel) with chemotherapeutic agents injected (SM-docetaxel, PRINT-docetaxel, PRINT-C2-docetaxel). Figure 1 shows the pharmacokinetic profile of docetaxel after single dose administration of SM-docetaxel, PRINT-docetaxel, PRINT-C2-docetaxel, in plasma, contralateral brain, peritumoral brain and intracranial tumor.

In each tissue analyzed, the nanoparticle formulations achieved higher exposures of drug in tumors compared with SM-docetaxel. Both PRINT-docetaxel and PRINT-C2-docetaxel formulations, measured by docetaxel and C2-docetaxel respectively, were detected 24 h or later after administration in plasma and contralateral brain. Docetaxel from SM-docetaxel or converted C2-docetaxel prodrug were detectable for 6 h after administration of SM-docetaxel or PRINT-C2-docetaxel in plasma and undetectable 2 h after administration in contralateral brain. In peritumoral brain, docetaxel from PRINT-docetaxel was present at 24 h after administration, as compared with SM-docetaxel, C2-docetaxel from PRINT-C2-docetaxel, or docetaxel from converted C2-docetaxel, all undetected beyond 6 h after administration. Docetaxel from the converted C2- prodrug was detected in intracranial tumors for up to 24 h, as compared with SM-docetaxel, C2-docetaxel prodrug from PRINT-C2-docetaxel, or docetaxel from PRINT-docetaxel, all undetectable after 6 h.

While AUCs were similar in contralateral brain, peritumoral brain and intracranial tumor, the Cmax for the docetaxel converted from PRINT-C2-docetaxel prodrug was three- to fourfold lower than SM-docetaxel in these intracranial tissues tested. These data are summarized in Table 2. These data also show a greater than threefold increased conversion of the released C2-docetaxel prodrug in intracranial tumor (10.9%) as compared with plasma, contralateral brain or peritumoral brain (3% or less). These data demonstrate that docetaxel from both PRINT-docetaxel formulations cross the blood–brain barrier and accumulate in intracranial tumors.

Table 2.
Pharmacokinetic parameters.

PRINT-C2-docetaxel increases survival as compared with docetaxel & PRINT-docetaxel in an intracranial model of NSCLC

The efficacy of PRINT-docetaxel formulations as compared with SM-docetaxel were evaluated in the NSCLC brain metastases model A549 (Figure 2). Analysis of tumor growth rates by bioluminescence is summarized in Figure 2A. The growth rate of vehicle-control treated tumors was significantly higher from all treatment groups from start of treatment (day 21) through day 60 (p < 0.0001); there were no differences in tumor growth rate between all other treatment groups (p > 0.7).

Figure 2.
All docetaxel therapies decrease tumor burden, but PRINT-C2-docetaxel improves survival.

Comparison of median survivals by treatment (Figure 2B) demonstrated that the PRINT-C2-docetaxel significantly improved survival by greater than 35% as compared with other treatment arms. Median survival in response to PRINT-C2-docetaxel was 90 days (95% CI: 70–103) as compared with vehicle control (61 days (95% CI: 50–68), SM-docetaxel (66.5 days (95% CI: 57–86), and PRINT-docetaxel (58 days [95% CI: 37–79], overall p-value: p = 0.1556). These data illustrate that while all treatments decreased tumor burden and slowed tumor growth rates, only treatment with the PRINT-C2-docetaxel prodrug improved survival.

Figure 3 demonstrates that mice treated with PRINT-C2-docetaxel therapy exhibited stable weight during the first 6 weeks of therapy. Mice in the other treatment or control groups exhibited weight loss during the first 6 weeks of therapy, significantly different than that of PRINT-C2-docetaxel (p < 0.003). The weight loss in the PBS group followed closely with tumor burden as expected. However, in SM-docetaxel and PRINT-docetaxel groups, weight loss did not correspond with tumor burden and steadily decreased with treatment number. This demonstrates that PRINT-C2-docetaxel was effective in reducing intracranial tumor burden without significant toxicity during the first 6 weeks of treatment resulting in improved overall survival.

Figure 3.
PRINT-C2-Docetaxel minimizes docetaxel toxicity as measured by average weight change.


Brain metastases, increasing in frequency as therapeutics for advanced extracranial cancer progress and evolve, require novel therapeutic approaches. Therapies for brain metastases should effectively target tumor tissue in the brain at concentrations high enough to induce tumor cell death and/or stabilize disease, while minimizing normal intracranial and extracranial toxicities, thereby increasing survival and quality of life.

This work shows that intravenous injections of PRINT PLGA nanoparticle formulations of docetaxel and the prodrug C2-docetaxel deliver docetaxel to intracranial tumors and exhibit antitumor activity against an orthotopic model of KRAS-NSCLC brain metastases. AUC analysis illustrates that delivery of released docetaxel from PRINT-docetaxel or the C2-docetaxel prodrug via PRINT-C2-docetaxel nanoparticles was higher than that of SM-docetaxel in intracranial tumors, 13-fold for PRINT-docetaxel and sevenfold for PRINT-C2-docetaxel (Table 2). Moreover, nanoparticles were detected in plasma for up to 72 h (Figure 1). In comparison to prior studies with PRINT-docetaxel formulations, the AUC of the intracranial tumor for each treatment were at lower levels than those described in the A549 tumor flank model (4885 vs 60,858 for PRINT-docetaxel; 2634 vs 26,799 for PRINT-C2-docetaxel; 372 vs 73,222 for SM-docetaxel), although plasma AUCs for all treatments were higher in this study as compared with the flank study (326,352 vs 79,192 for PRINT-docetaxel; 360,281 vs 227,735 for PRINT-C2-docetaxel; 4742 vs 1227 for SM-docetaxel) for similar dosing concentrations [13]. As compared with flank studies [13], intracranial tumor AUCs were an order of magnitude lower for each treatment observed, suggesting a drug delivery issue, likely related to the blood–brain barrier [12,20].

The silyl ether C2′ alcohol of docetaxel was generated to produce an acid labile docetaxel prodrug that could specifically target the acidic environments of cancer cells. The applicability of the acid labile chemistry of silyl ethers as anticancer prodrugs was previously demonstrated with gemcitabine [23]. In this case, lower pH increased both prodrug release and conversion from the PRINT nanoparticle. Consistent with the model, PRINT-C2-docetaxel had an increased conversion of 10.9% in intracranial tumors, as compared with 2.1, 1.8 and 3.0% in plasma, contralateral and peritumor environments, respectively. The C2-docetaxel conversion rate in intracranial tumors is lower than in the flank model (32.5 vs 10.9%), but at a similar conversion value as described for liver [13], and is within the range of other clinically relevant prodrug strategies. We did not determine a mechanism for the decrease in prodrug conversion in the intracranial tumors, which could include mass action effects due to lower concentrations of C2-docetaxel in intracranial versus extracranial tumors or a difference in tumor biology based on the contributing brain tissue environment.

While all treatment arms decreased tumor burden and slowed intracranial growth rates by bioluminescence imaging, the PRINT-C2-docetaxel increased median survival, by greater than 35%, as compared with all other treatment arms. We hypothesize that the efficacy of the PRINT-C2-docetaxel is due to decreases in toxicity [13]. This is supported by the following evidence: 1) Pharmacodynamics from previous studies show that PRINT-C2-docetaxel has slower release kinetics as compared with PRINT-docetaxel due to the increased lipophilicity of C2-docetaxel as compared with docetaxel; 50% of the PRINT-C2-docetaxel is released at 24 h as compared with less than 6 h with PRINT-docetaxel cargo. Additionally, C2-docetaxel has an 8 h half-life for conversion to docetaxel in PBS [13]. This demonstrates that the longer retention of C2-docetaxel in the nanoparticle, with an added conversion rate to docetaxel, delays active drug release, minimizing toxicity. 2) In this study, the docetaxel from the release and conversion of the PRINT encapsulated C2-docetaxel has a lower Cmax in plasma than the SM-docetaxel, although converted docetaxel from PRINT-C2-docetaxel was found 24 h after injection in contrast to SM-docetaxel or PRINT-docetaxel in intracranial tumor. This supports previous pharmacodynamics analysis [13] and is consistent with the hypothesis that PRINT-C2-docetaxel would be less toxic than SM-docetaxel in these studies. 3) While all docetaxel treatments decreased tumor burden (Figure 2A), only the PRINT-C2-docetaxel increased median survival as compared with all other treatment arms (Figure 2B). 4) Docetaxel treatment is consistently associated with neutropenia, which may be minimized by PRINT-C2-docetaxel. In previous studies [13], 4 days after the sixth intravenous dose of 20 mg/kg, animals treated with PRINT-C2-docetaxel had PBS control levels of white blood cells, and twice the white blood cell levels as SM-docetaxel treated animals, at equimolar dosing. 5) With regards to median survival and the 60 days post-intracranial injection with six doses of treatment, the SM-docetaxel, PRINT-docetaxel and PBS control groups showed weight decline that correlated to time of death. However, tumor burden in SM-docetaxel and PRINT-docetaxel was significantly decreased as compared with PBS controls, supporting treatment-specific toxicity. Mice treated with the PRINT-C2-docetaxel showed no change in weight during this timeframe and decreased tumor burden. This was also consistent with previous studies [13].

Targeting drug to tumors through nanoparticle delivery methodologies is a promising strategy to increase tumor cytotoxicity and decrease drug-associated toxicities. Encapsulated cargo has a different pharmacodynamic profile than free drug and takes on the pharmacokinetics of its carrier. This results in increased systemic half-life of the drug, changes in the drug tissue distribution and increased drug-tumor exposure with less systemic toxicity [6,9,13,17]. In this manner, nanoparticle encapsulation generates a prodrug of the free drug cargo [6]. However, in this study, simply changing drug distribution and increasing target dosing by encapsulating free chemotherapeutic drug (i.e., docetaxel) did not balance decreased systemic toxicity to support extended survival. The mechanism supporting decreased PRINT-C2-docetaxel toxicity may include the longer half-life of cargo release as compared with PRINT-docetaxel (24 h vs <6 h at pH 7.4), as well as the timing and specificity of the target tissue activation [13].

Target tissue activation of the C2-docetaxel prodrug is modeled to occur through ethyl-dimethyl-silyl-ether docetaxel protonation and hydrolysis, resulting in docetaxel release. This reaction proceeds in acidic environments like tumors, without enzymatic activity [13]. Cancer cells’ dependency for anaerobic metabolism generates an acidic extracellular microenvironment and intracellular endocytic and lysosomal vesicular network. This increases activation of acid-labile molecules for anticancer therapy with some tumor specificity. This strategy is being vigorously tested in the context of acid labile nanoparticles, targeting agents and prodrugs like C2-docetaxel [21,22]. This study introduces the application of the acid labile chemistry of silyl ethers tagged chemotherapeutics as a targeting agent for intracranial tumors.


We conclude that PRINT nanoparticles of docetaxel can enter and inhibit growth of human intracranial tumors in a murine xenograft model of NSCLC. We show that intravenous administrations of PRINT-C2-docetaxel prodrug are more efficacious than either free docetaxel or PRINT-docetaxel against a brain metastasis model of NSCLC. We conclude that PRINT-C2-docetaxel increases survival by decreasing systemic toxicities, through slower chemotherapeutic release and the targeted conversion of the prodrug in the intracranial tumor environment. We confirm that decreasing the systemic toxicity of chemotherapeutics is an important adjunct treatment strategy against intracranial cancers.

Executive summary


  • Nanoparticle formulations of PRINT-docetaxel and PRINT acid labile C2-docetaxel prodrug have been shown to be more effective than free drug against the A549 NSCLC subcutaneous xenograft model.


  • Given at similar molar doses, docetaxel and C2-prodrug docetaxel from PRINT-nanoparticle formulations were found in intracranial tumor and brain tissues at greater than sevenfold higher concentrations than SM-docetaxel at all time points.
  • The AUCs for docetaxel from converted C2 prodrug and SM-docetaxel were similar in intracranial tissues tested; the Cmax for C2 prodrug was three- to fourfold lower than SM- docetaxel.
  • Conversion of the acid-labile C2 prodrug to docetaxel was highest in intracranial tumor tissue, 10.9% as compared with 2.1% in plasma, 1.8% in contralateral brain and 3.0% in peritumoral brain.
  • All docetaxel treatments significantly decreased tumor burden as compared with control during the first 6 weeks of treatment (p < 0.0001).
  • The PRINT C2-docetaxel prodrug formulation treatment increased median survival to 90 days, as compared with 61 days for control, 58.5 days with PRINT-docetaxel and 66.5 days with SM-docetaxel.
  • PRINT C2-docetacel was less toxic by measures of weight change during the first 6 weeks of treatment.


  • Acid-labile PRINT C2-prodrug nanoparticle, because of improved tumor specificity resulting in decreased systemic toxicity, had a superior efficacy as compared with SM-docetaxel and PRINT-docetaxel against a NSCLC brain metastases model.
  • The combination of PRINT PLGA nanoparticle technology with a tumor activated agent may be a useful anticancer therapeutic for intracranial tumors.


C Bowerman is currently a research associate for Moderna Therapeutics (MA, USA). K Chu is currently a research associate for GSK Pharmaceuticals, Research Triangle Park (NC, USA). O Karginova is currently a research associate in the Department of Hematology and Oncology, University of Chicago (IL, USA). Additionally, the authors would like to thank Liquidia Technologies for providing PRINT® molds used in the fabrication of nanoparticles.



The content is solely the responsibility of the authors and does not necessarily represent the official views of the National Cancer Institute or the National Institutes of Health.

Financial & competing interests disclosure

The authors of this manuscript receive uncompensated research funding from Novartis, Sanofi, toBBB, GERON, Angiochem, Merrimack, PUMA, Lily, Merck, Oncothyreon. CK Anders serves in an uncompensated advisory role for Novartis, Sanofi, toBBB, GERON, angiochem, Merrimack, Lily, Genentech, Nektar, Kadmon. The project described was supported by grant number K23CA157728 (CK Anders) from the National Cancer Institute. Research was supported by the 2010 Breast Cancer Research Foundation-AACR Grant for Translational Breast Cancer Research, grant number 10-60-26-ANDE (CK Anders). CK Anders is a Damon Runyon Clinical Investigator, supported (in part) by the Damon Runyon Cancer Research Foundation (CI-64-12). Funding also came from the Lineberger Comprehensive Cancer Center University of North Carolina SPORE Career Development Award, 5P50CA058223 (SPORE; CK Anders), University Cancer Research Fund and the Carolina Center for Cancer Nanotechnology Excellence (U54CA151652; JC Luft, C Bowerman, K Chu, JM DeSimone). 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.

No writing assistance was utilized in the production of this manuscript.

Ethical conduct of research

The authors state that they have obtained appropriate institutional review board approval or have followed the principles outlined in the Declaration of Helsinki for all human or animal experimental investigations. In addition, for investigations involving human subjects, informed consent has been obtained from the participants involved.


Papers of special note have been highlighted as: • of interest; •• of considerable interest

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