Article Text


Mechanisms of tissue uptake and retention of paclitaxel-coated balloons: impact on neointimal proliferation and healing
  1. Juan F Granada1,
  2. Mark Stenoien2,
  3. Piotr P Buszman1,
  4. Armando Tellez1,
  5. Dan Langanki2,
  6. Greg L Kaluza1,
  7. Martin B Leon3,
  8. William Gray3,
  9. Michael R Jaff4 and
  10. Robert S Schwartz5
  1. 1Skirball Center for Cardiovascular Research, Cardiovascular Research Foundation, Orangeburg, New York, USA
  2. 2MEDRAD Interventional, Indianola, Pennsylvania, USA
  3. 3Columbia University Medical Center, Center for Interventional Vascular Therapy, New York Presbyterian Hospital, New York, New York, USA
  4. 4Harvard Medical School, Massachusetts General Hospital, Boston, Massachusetts, USA
  5. 5Minneapolis Heart Institute and Foundation, Abbott Northwestern Hospital, Minneapolis, Minnesota, USA
  1. Correspondence to Dr Juan F Granada; jgranada{at}


Background The efficacy of paclitaxel-coated balloons (PCB) for restenosis prevention has been demonstrated in humans. However, the mechanism of action for sustained drug retention and biological efficacy following single-time drug delivery is still unknown.

Methods and results The pharmacokinetic profile and differences in drug concentration (vessel surface vs arterial wall) of two different paclitaxel coating formulations (3 µg/mm2) displaying opposite solubility characteristics (CC=crystalline vs AC=amorphous) were tested in vivo and compared with paclitaxel-eluting stents (PES). Also, the biological effect of both PCB formulations on vascular healing was tested in the porcine coronary injury model. One hour following balloon inflation, both formulations achieved similar arterial paclitaxel levels (CC=310 vs AC=245 ng/mg; p=NS). At 24 h, the CC maintained similar tissue concentrations, whereas the AC tissue levels declined by 99% (p<0.01). At this time point, arterial levels were 20-fold (CC) and 5-fold (AC) times higher compared to the PES group (p<0.05). At 28 days, arterial levels retained were 9.2% (CC) and 0.04% (AC, p<0.01) of the baseline levels. Paclitaxel concentration on the vessel surface was higher in the CC at 1 (CC=36.7% vs AC=13.1%, p<0.05) and 7 days (CC=38.4% vs AC=11%, p<0.05). In addition, the CC induced higher levels of neointimal inhibition, fibrin deposition and delayed healing compared with the AC group.

Conclusions The presence of paclitaxel deposits on the vessel surface driving diffusion into the arterial tissue in a time-dependent fashion supports the mechanism of action of PCB. This specific pharmacokinetic behaviour influences the patterns of neointimal formation and healing.

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Key messages

  • What is already known about this subject?

  • The efficacy of paclitaxel-coated balloons (PCB) for restenosis prevention has been demonstrated in humans. However, the mechanism of action for sustained drug retention and biological efficacy following single-time drug delivery is still unknown.

  • What does this study add?

  • Our data suggest that the observed tissue half-life of paclitaxel delivered by PCB technologies is rate limiting and relates to the slow dissolution of paclitaxel deposits from the vessel surface into arterial tissue in a time-dependent fashion.

  • How might this impact on clinical practice?

  • This experimental study provides better understanding of the processes of paclitaxel local delivery which may implicate in the refinement of currently available and development of new treatment technologies and options for atherosclerotic vascular disease.


Paclitaxel-coated balloons (PCB) have emerged as a viable therapeutic alternative for the interventional treatment of vascular disease.1–5 With the use of this technology, the short-term transfer and long-term retention of paclitaxel to the arterial wall is feasible,1 ,6 thus potentially reducing the untoward effects of the prolonged drug release associated with polymer-based stent technologies7–9 including delayed vessel healing, potentially resulting in stent thrombosis. Experimental data have shown that some paclitaxel formulations are rapidly transferred to the vessel wall following balloon dilation.10 ,11 However, it has been suggested that long-term tissue retention is affected by the drug morphology and resulting solubility attained during the coating process.12

First-generation PCB technologies displayed a high level of crystallinity on the coating surface and were associated with inconsistent drug load and high particulate shedding during balloon inflation. New generations of PCB coatings are under development, displaying more consistent, uniform and less crystalline (CC) coating characteristics. Although these technological changes may potentially affect clinical outcomes, the resulting biological effects on paclitaxel uptake and vessel healing are still unknown.

At the present time, a potential mechanism of action explaining long-term drug retention yielding sustained biological efficacy following single-time drug delivery has not been described. In this study, we compared the impact of two different coating types on tissue transfer, retention and biological efficacy and propose a mechanism of action explaining the durability of the biological effect following single-time delivery of paclitaxel via balloon delivery.


Device description

PCB angioplasty catheters were prepared having two distinct drug solid-state morphologies using identical balloon platforms and paclitaxel-iopromide coating concentrations applied at a total drug dose of 3 µg/mm2. The solution was precisely metered onto all surfaces of the balloons, including within the folds. As a consequence of the proprietary controlled drying process following balloon coating, the resulting paclitaxel morphologies were either substantially amorphous (AC) or dihydrated CC. The morphological form of the coating was confirmed by surface electron microscopy and Raman spectroscopy (figure 1). The comparison paclitaxel-eluting stent (PES) used in this study was the commercially available balloon-expandable TAXUS Liberté stent system (TS, 3×15 mm, Boston Scientific, Natick, Massachusetts, USA) coated with a durable polymeric coating formulation containing paclitaxel at a concentration of 1 μg/mm2.

Figure 1

Top panel: surface electron microscopy pictures of crystalline (left) and amorphous (right) coatings based on an identical paclitaxel-iopromide combination. Bottom panel: Raman spectroscopy analysis of both coatings.

Study schematic

The study scheme is presented in figure 2. In the first paclitaxel tissue transfer study, abdominal aortas of 44 white rabbits were enrolled. In the following vascular response experiment, 12 domestic swine (DS) were included. The description of each study section is provided below.

Figure 2

Flow chart describing the study's designs including follow-up times. DS, domestic swine; AC, amorphous; CC, crystalline; PCB, paclitaxel-coated balloon; POBA, plain balloon angioplasty; OCT, optical coherence tomography; IVUS, intravascular ultrasound.

Pharmacokinetic studies

All animals received standard care outlined in accordance with the act of animal welfare and the ‘Principles of Care of Laboratory Animals’.13 Abdominal aortas of 44 New Zealand white rabbits, either gender, 3.3–4.5 kg, were treated with a single 3.5×20 PCB each at 1.2–1.3:1.0 overstretch ratio for 60±1 s. An antimicrobial (enrofloxacin, 13.5–17 mg/kg), an antispasmodic (Nifedipine, 30 mg) and aspirin 81 mg were given pre procedure. Induction of anaesthesia was achieved with ketamine/xylazine (42–45.5/8.75–9 mg/kg) followed by 0–5% isoflurane propofol (2–8 mg/kg). Arterial access was obtained using a surgical cut down technique of the carotid artery. Anticoagulation with heparin was achieved during the procedure to maintain an activated clotting time ≥250 s. Treated vessels (four per time point and group) were harvested after 1 h, 24 h, 7 and 28 days. Harvested vessels included the 20 mm treated segment and 10 mm untreated vessel proximal and distal to the treated segment in order to facilitate handling without damaging the treated segment. Taxus stents (3×15 mm) were used for comparison in the same model and treated vessels were harvested at 24 h, 7 and 28 days. The total paclitaxel vessel concentration was calculated as a sum of endoluminal and intramural paclitaxel amount divided by total vessel weight prior scraping. The compartmental concentration was calculated as a paclitaxel amount in the endoluminal and intramural compartment divided by the weight of tissue after scraping.

Quantification of paclitaxel surface deposition

The vessel segment was blotted dry of blood, weighed, carefully incised longitudinally and pinned open, and stents, if present, carefully removed. The vessel surface (endoluminal) paclitaxel was removed together with the entire intimal and endothelial layer from the underlying muscular and adventitial layers of the vessel segment (intramural) by gentle scraping with a blunt plastic pipette. The intima and pipette tip were transferred to a labelled cryovial. The remaining vessel was weighed again and transferred to another labelled cryovial. The cryovials were flash frozen and stored at −70°C prior to analysis for paclitaxel content. Paclitaxel concentrations in the intimal and underlying tissues were determined separately by an independent laboratory using validated liquid chromatography-mass spectrometry (LC-MS)/MS methods. Tissues were sectioned into small pieces and weighed. Samples were then homogenised in phosphate buffered homogenisation solution. The homogenate was labelled with an internal standard, extracted with methyl tert-butyl ether and evaporated to dryness. The reconstituted sample was analysed by reverse-phase high-performance LC with MS/MS detection. The total paclitaxel vessel concentration was calculated as a sum of endoluminal and intramural paclitaxel amount divided by total vessel weight prior scraping. The compartmental concentration was calculated as a paclitaxel amount in the endoluminal and intramural compartment divided by the weight of tissue after scraping. Drug elimination (kelimin) was calculated based on the following formula kelim=[ln(Cpeak)–ln(Ctrough)]/tinterval. Second, paclitaxel half-life was calculated t½=0.693/kelim.

Coronary porcine study

All animals received standard care outlined in accordance with the act of animal welfare and the ‘Principles of Care of Laboratory Animals’.13 A total of 12 castrated male DS (mean body weight 40.5±2.4 kg) were included and maintained on a standard chow diet until completion of the study. One intramuscular muscarinic anticholinergic dose (glycopyrrolate 0.005–0.02 mg/kg) was given pre procedure. Induction of anaesthesia was achieved with a rapid acting general anaesthetic (Tiletamine+Zolazepam, Telazol 2–5 mg/kg) followed by endotracheal intubation with a continuous inhalation of 1–3% isoflurane. Arterial access was obtained using a surgical cut down technique of the carotid artery. All animals received 75 mg aspirin and 75 mg clopidogrel 3 days before the procedure and continued until completion of the study. Anticoagulation with heparin was achieved during the procedure (3000–10 000 U) to maintain a coagulation time ≥250 s. Following baseline angiography, a total of 32 coronary arteries were analysed using intravascular ultrasound to determine the diameters of the coronary target sites. Coronary predilation was performed using a regular angioplasty balloon before stent implantation. Then, balloon-expandable bare metal stents (Orbus X, Bavaria Medizin Technologie GmBH 3 and 3.5×15 mm) were deployed at a 1.25:1 overstretch ratio for 30±3 s. Finally, stents were dilated with one of the PCB formulations (CC or AC) or a bare balloon was used to postdilate the stents for 30±3 s ensuring at 1:1 PCB ratio. At 28 days follow-up, all animals underwent terminal angiography and optical coherence tomography (OCT) imaging analysis. Quantitative coronary angiography was performed offline by a single operator blinded to the study group utilising QAngio XA Software V. (Medis Medical Imaging Systems, Leiden, The Netherlands).

OCT imaging

OCT images were recorded using the M4 OCT imaging system (ImageWire, LightLab Imaging, Inc, Westford, Massachusetts, USA). Integrated OCT image analysis software developed by LightLab Imaging was used for all measurements. System calibration of the z-offset was performed on each image wire before every single imaging procedure. OCT imaging pullbacks were performed at a rate of 10 mm/s using continuous non-occlusive contrast-saline mixture as a flush. All images were acquired at 100 frames/s and stored on the system hard drive for off-line analysis. Morphometric analysis was performed by two operators blinded to the study groups. Each individual pullback analysis was divided into proximal reference vessel, stent segment and distal reference vessel. Instent analysis was divided into 7–8 equal cross sections.

Histology protocol

Hearts were removed immediately following termination and arteries were flushed with Ringer's lactate for 15 min (1 L). After all the blood was washed out, pressure perfusion fixation was performed for 20 min with 10% neutral buffered formalin. The fixated heart was immersed in a formalin filled container for at least 24 h to continue further fixation. Coronary arteries were removed from the myocardium and then dehydrated, embedded in plastic and finally sectioned at proximal, mid and distal locations of the stented segment. Each segment was sectioned for staining. One set of sections was stained with H&E and a second set with elastin trichrome stain. Using Spot Advanced V.4.1.1 Software (Spot Imaging Solutions, Sterling Heights, Michigan, USA), digital vessel images were captured and histomorphometry was performed using NOVA PRIME V.6.70.10 software (Bioquant Image Analysis Corp., Nashville, Tennessee, USA). The Morphometric characteristics that were evaluated were lumen (L) area (mm2), internal elastic lamina (IEL) area (mm2), external elastic lamina area (mm2), medial area (mm2), per cent area stenosis and neointimal thickness. Neointimal area was defined as IEL minus L. Percentage area of stenosis was calculated as [(IEL−L)/IEL]×100. A semiqualitative score was used to determine loss of endothelialisation (0=≥90% of luminal surface covered, 1=75–90% of luminal surface covered and 2=≤75% of luminal surface covered), inflammation (0=none, 1=mild and 2=severe), medial smooth muscle cell (SMC) loss (0=none, 1=1–25%, 2=26–50%, 3=51–75%, 4=76–100%) and IEL disruption (0=none, 1=1–25% and 2=26–50%).

Statistical analysis

Quantitative data were normally expressed as mean value±SD. For a skewed distribution, data were expressed as median and IQR. Qualitative data were presented as number and percentage. The Shapiro-Wilk test was used for testing normality. Quantitative data were compared either with the Student t test or one-way analysis of variance (ANOVA) for normal distribution data or the Mann-Whitney U test, otherwise. Holm Sidak post-ANOVA tests were used to test for differences in variables between stent types. When either equal variance test or normality test failed, a Kruskal-Wallis test (with Dunn's method for post hoc group comparison) was conducted; p values of ≤0.05 were considered statistically significant. Areas under the curve (AUCs) were calculated with the trapezoidal rule and compared utilising methodology by Hanley and McNeil.14 SigmaStat V.3.11 (Systat Software) and MedCalc V.10.2 (Mariakierke, Belgium) were utilised for the statistical analyses.


Tissue pharmacokinetics study

Abdominal aortic tissue was harvested at different time points following either PCB dilation or TS implantation. The arterial tissue pharmacokinetic profile of all tested groups is shown in figure 3. The overall vessel size was comparable among all groups and the paclitaxel tissue concentrations were normalised by total tissue weight (data not shown). Following PCB dilation, the 1 h total paclitaxel tissue concentrations were comparable with CC and AC. At 24 h, CC sustained similar concentrations, whereas levels declined by 99% in AC group (p<0.01). In addition, at the same time point, both the CC (20-fold) and AC (5-fold) formulations displayed higher total paclitaxel tissue concentrations compared with the TS group (p<0.05). Within 7 days, there was a significant decline (CC=88.6% and AC=99.9%) in the total paclitaxel tissue concentrations compared with original 1 h concentration. In comparison, in the TS group there was an almost sixfold increase in the total paclitaxel tissue concentration at the same time point. In all groups, paclitaxel tissue levels remained detectable up to 28 days. The CC group resulted in tissue concentrations threefold higher than the TS group. Conversely, the AC group yielded paclitaxel tissue concentrations significantly lower and barely detectable when compared with the CC and the TS groups. Area under the pharmacokinetic curve was significantly higher in the CC group as compared with AC and PES (2422.7 vs 138.4 vs 102.45; p<0.05). The calculated tissue half-life for paclitaxel delivered by the CC and the AC was 7.5 and 3.4 days, respectively.

Figure 3

Graphic representation of the 28-day paclitaxel tissue levels of both paclitaxel-coated balloon coatings in comparison with the Taxus stent (PES). AC, amorphous; CC, crystalline; PES, paclitaxel-eluting stent.

Paclitaxel vessel surface deposition analysis

A compartmental vessel analysis (vessel surface vs arterial wall) was performed by scraping the vessel surface of the treated segments. In the CC group, paclitaxel concentrations were higher on the vessel surface when compared with arterial wall concentrations at 24 h, 7 and 28 days (figure 4A). Furthermore, AUC for vessel surface paclitaxel concentration was significantly higher than the arterial wall level curve (AUC surface: 7118.8 vs intra-arterial: 1948.1, p=0.03). Conversely, in the AC group, the vessel surface and the arterial wall concentrations were similar at 1 and 24 h (figure 4B). After 24 h, the vessel surface concentration declined further in comparison with the arterial wall levels (figure 4B). The AUCs for paclitaxel concentration were similar for both compartments in this group (AUC surface: 127.5 vs intra-arterial: 190.2; p=0.2). Additionally, at 1 h, the total vessel surface paclitaxel presence appeared similar. However, at 24 h and at 7 days, the CC group retained a higher percentage of the initial paclitaxel uptake when compared with the AC group. A paclitaxel deposits distribution analysis is shown in figure 5. This analysis demonstrated that approximately 27% of the total amount of drug delivered via balloon dilation remained on the surface of the vessel regardless of the coating type. At 24 h, 36.7% of the total paclitaxel recovered remained on the vessel surface in the CC group, compared with 13.1% in the AC group (p<0.01). In the CC, the vessel surface deposits of paclitaxel remained stable up to 7 days, while these deposits further decreased in the AC group (38.4% vs 11%; p=0.07). At 28 days, the percentage of paclitaxel vessel surface deposits appeared to equalise between both groups. The calculated paclitaxel half-life for both compartments was similar in the AC group (2.5 days for vessel surface and intra-arterial). By contrast, in the CC group, the calculated vessel surface half-life was higher (11.5 days) compared with arterial wall (7.5 days).

Figure 4

Compartmental analysis displaying the paclitaxel concentrations on the inner layer (endoluminal) and intra-arterial over time (crystalline (A) and amorphous (B) coatings).

Figure 5

Paclitaxel endoluminal amount over time expressed as percentage of total vessel amount. AC, amorphous; CC, crystalline.

Tissue effects coronary study

A summary of the imaging results is presented in table 1. At baseline, the reference vessel diameter and the stent:artery ratios were comparable between groups. The final minimal lumen diameter following stent implantation was also similar between groups. At 28-day follow-up, the CC group displayed larger minimal lumen diameters and lower percentage diameter stenosis compared with the AC and the bare balloon control groups. In the OCT in vivo evaluation, the CC group displayed larger lumen areas (increase=63.8% vs AC and 45.9% vs plain balloon angioplasty (POBA); p=0.03) and lower per cent area stenosis (decrease=23.9% vs AC and 25% vs POBA; p=0.03, table 2). In addition, OCT analysis showed that the distribution of neointima in the AC group was similar to that in the POBA control group (figure 6). Conversely, the CC group displayed a pattern of neointimal distribution that was heterogeneously distributed. A summary of the histological findings is shown in table 2 and representative stent cross sections in figure 7. Similar to the OCT findings, morphometric evaluation showed that the CC had 23.7% and 22.2% decrease in per cent area stenosis when compared with the AC and the POBA control group, respectively. The CC group displayed signs of drug effect such as slightly lower endothelialisation scores, less mature neointima and higher degrees of fibrin deposition in comparison to the AC and the POBA control groups.

Table 1

Intravascular and angiographic imaging analyses at baseline and at 28-day follow-up following PCB delivery in porcine coronary arteries

Table 2

Histomorphometric and vascular healing response analysis of stents according to the PCB formulation used at 28 days

Figure 6

Neointimal distribution along the treated arterial segments by optical coherence tomography at 28 days in the tissue effects arm of the study. PCB, paclitaxel-coated balloon; POBA, plain balloon angioplasty.

Figure 7

Representative histological pictures of CC (A) and AC (B) at 28 days in porcine coronary arteries following paclitaxel-coated balloon delivery.


The concept of developing a balloon-based drug delivery system to prevent arterial restenosis was based on the hypothesis that a durable effect on neointimal proliferation could be achieved following the single-time delivery of paclitaxel into the vessel wall.1 ,2 ,6 ,15 This early hypothesis contradicted previous experimental16 and clinical17 data suggesting that sustained tissue exposure to paclitaxel was necessary to effectively decrease restenosis. Owing to its unique delivery mechanism and proposed pharmacokinetic profile, the early promising clinical results of PCB technologies were originally challenged.18

Early experimental data confirmed that paclitaxel transfer into the vessel wall occurs rapidly following balloon inflation.6 ,19 In addition, tissue pharmacokinetic studies10 showed that short-term tissue levels of paclitaxel following balloon delivery were higher by several orders of magnitude compared with drug-eluting stents20 ,21 and that therapeutic concentrations of paclitaxel were found beyond 28 days following initial drug delivery.5 Also, several publications demonstrated that the long-term vessel healing profile appears to be similar to commercially available drug eluting stent technologies.22 However, despite its documented clinical efficacy in selected clinical scenarios, a potential mechanism of action explaining long-term drug retention and sustained biological effect has not been proposed for PCB technologies. In these series of experimental studies, we propose a working hypothesis for the mechanism of action of PCB by comparing the pharmacokinetic behaviour of two different coatings displaying opposite solubility profiles with a commercially available PES.

Paclitaxel transfer and retention

In the present study, paclitaxel tissue levels shown in the TS group followed a typical pattern of drug release from a polymer reservoir and the levels progressively increased from 24 h to 28 days (6-fold and 18-fold increase in tissue levels at 7 and 28 days, respectively). Data reported from a similar study in rabbit iliac arteries using TS23 demonstrated that paclitaxel tissue concentration increased from 0% at implant to approximately 5% at 30 days, and then decreased slowly through 180 days. Therefore, we chose 1, 7 and 28 days to model TS tissue paclitaxel increase to peak concentration. In contrast, paclitaxel transferred to the vessel wall via both PCB formulations was ∼20 orders of magnitude higher compared with the early TS tissue levels (figure 3). At 24 h, the tissue levels achieved by PCB using the CC remained stable. Conversely, in the AC group, there was a sharp decline in paclitaxel tissue levels achieving values comparable to the TS group. In the AC group, tissue paclitaxel levels continued to decline over time and fell below the TS curve at 28 days. Conversely, although CC tissue levels steadily continued to decline, the 28-day tissue levels achieved were comparable to the TS group. This finding may explain the lack of efficacy of some PCB technologies in early clinical trials.24 Our data also suggest that acute drug transfer and long-term tissue retention are independent of each other as both PCB formulations achieved comparable acute transfer levels but very different long-term tissue retention levels. In our study, the calculated tissue elimination half-life of total paclitaxel in treated arteries was several orders of magnitude higher (3.4 for AC and 7.5 for CC) compared with previous experimental pharmacokinetic studies of paclitaxel delivered via balloon in which tissue elimination half-life is reported to be on the order of hours.12 ,25–28 This prolonged elimination half-life of paclitaxel suggests an additional mechanism for long-term retention through the development of compartments or deposits from which drug releases over time into the tissue.

Vessel surface paclitaxel deposits and tissue retention

In this study, we also demonstrated that following PCB dilation, a proportion of the paclitaxel is retained on the vessel surface and is not acutely dissolved into the tissue. In the CC group, sustained paclitaxel vessel surface levels were maintained, while in the AC group, the surface concentrations rapidly decreased over time. It seemed apparent that arterial wall levels of paclitaxel were driven by the sustained retention of drug on the surface of the vessel wall, thereby maintaining a positive concentration gradient from the vessel surface into the arterial wall. By 24 h the differences in paclitaxel vessel surface levels were striking between both PCB groups. However, by 7 days arterial tissue concentrations began to equalise the vessel surface levels providing an explanation about the lack of tissue toxic effects seen in experimental studies despite the apparent supratherapeutic tissue levels found immediately after PCB use.5 ,6 ,11 ,29 At 30 days, the arterial tissue levels of paclitaxel seen in the CC group were comparable to the levels seen in the TS group and within the inhibitory concentration range of SMC proliferation.30 In addition, the concentration of paclitaxel found on the vessel surface in the CC group at the same time point was threefold higher than the arterial wall levels of the drug. These results seem to be consistent with previous reports showing that specific binding to intracellular proteins occurs primarily in the subintimal space and determines arterial transport properties and microtubule binding of paclitaxel.31 ,32

Therapeutic window of PCB delivery

Our data suggest that the observed tissue half-life of paclitaxel delivered by PCB technologies is rate limiting and relates to the slow dissolution of paclitaxel deposits from the vessel surface into arterial tissue in a time-dependent fashion. Once paclitaxel is transferred into the vessel wall, the mechanisms of intra-arterial transfer follow well-described patterns of pharmacokinetics.33 In any case, the resulting tissue levels of paclitaxel at 28 days are above the reported IC50 values for human SMC (1.4–2 ng/g)30 and endothelial cell proliferation (1.7–6.8 ng/g).34 Thus, the proposed mechanism of action reconciles the apparent contradiction between the observed short-term supratherapeutic tissue levels seen right after balloon delivery and the resulting vessel healing profiles seen at the experimental level. The ‘total’ paclitaxel levels measured in pharmacokinetic tissues are likely magnified due to the higher concentrations of non-soluble paclitaxel deposits remaining on the surface. These deposits, important as a reservoir to maintain long-term tissue levels, appear to get washed off into the blood stream within the first 7 days following initial drug delivery. Then, the resulting levels of intra-arterial paclitaxel appear to be within the therapeutic range for inhibition of smooth muscle proliferation and below cytotoxic concentrations, which is consistent with experimental and clinical data, both for peripheral and coronary territory, on safety and efficacy reported to date.1–4 ,15

Biological response to paclitaxel transfer

The differences in paclitaxel tissue retention found in both PCB groups resulted in significant differences in the degrees of neointimal formation between both groups. In general, the pattern of drug release and retention displayed by the CC group resulted in higher total vessel luminal areas, heterogeneity of neointimal formation, SMC loss and fibrin deposits. In addition, in vivo OCT analysis demonstrated a more heterogeneous pattern of neointimal formation in the CC group. In conclusion, in these series of studies, we demonstrated that the type of paclitaxel coating impacts the degree of drug transfer and retention. Long-term paclitaxel retention appears to depend on surface deposits that serve as delivery mechanism occurring over time.

Study limitations

The main limitation of this study derives from its experimental nature and the analytical methods used. First, the normal rabbit aorta lacks the biological components seen in atherosclerotic vascular disease. Therefore, the pharmacokinetic results found in our studies may not correlate with the levels potentially found in humans. It is well known that there is a significant amount of variability seen in pharmacokinetic studies using animal models. In addition, since efficiency of removal of insoluble drug by the surface wipe technique is not perfect, the obtained values may introduce analytical errors and may not reflect accurate values for the percentage of total drug in the surface deposition study. However, all studies were performed following identical protocols and procedures introducing the same systematic errors, if any. Finally, the stent study used a different animal species (porcine) and slightly higher balloon to artery ratio than commonly performed in the experimental setting. Although this approach was used in order to increase the biological response to drug delivery and healing, it is known that this method may introduce significant variability of the resulting data. Importantly, since each PCB uses different manufacturing methods2 ,3 ,6 ,10 ,15 ,16 resulting in different coating characteristics, the results of the present study may not be directly representative of all PCB technologies.

  • Received March 3, 2014.
  • Revision received May 5, 2014.
  • Accepted May 28, 2014.
View Abstract


  • Contributors JFG contributed to the concept, planning, conducting and manuscript drafting, and he is the guarantor. MS contributed to the concept and planning. PPB was involved in planning, data analysis and interpretation, statistics and manuscript drafting. AT was involved in conducting, data and pathological analysis. DL was involved in planning. GLK was involved in planning and study management. MBL was involved in planning and scientific supervision. WG and MRJ were involved in data interpretation and manuscript revision. RSS was involved in scientific supervision, concept and planning.

  • Funding MEDRAD Interventional (Indianola, PA) provided financial support and materials for this study.

  • Competing interests At the time of experiment, MS and DL were full time employees of Medrad Interventional.

  • Ethics approval The Institutional Animal Care and Use Committee approved the study.

  • Provenance and peer review Not commissioned; externally peer reviewed.

  • Data sharing statement No additional data are available.

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