Figures
Abstract
Background
Treatment of coronary bifurcation lesions remains challenging, beyond the introduction of drug eluting stents. Dedicated stent systems are available to improve the technical approach to the treatment of these lesions. However dedicated stent systems have so far not reduced the incidence of stent restenosis. The aim of this study was to assess the expansion of the Multi-Link (ML) Frontier™ stent in human and porcine coronary arteries to provide the cardiologist with useful in-vitro information for stent implantation and selection.
Methodology/Principal Findings
Nine ML Frontier™ stents were implanted in seven human autopsy heart samples with known coronary artery disease and five ML Frontier™ stents were implanted in five porcine hearts. Proximal, distal and side branch diameters (PD, DD, SBD, respectively), corresponding opening areas (PA, DA, SBA) and the mean stent length (L) were assessed by micro-computed tomography (micro-CT). PD and PA were significantly smaller in human autopsy heart samples than in porcine heart samples (3.54±0.47 mm vs. 4.04±0.22 mm, p = 0.048; 10.00±2.42 mm2 vs. 12.84±1.38 mm2, p = 0.034, respectively) and than those given by the manufacturer (3.54±0.47 mm vs. 4.03 mm, p = 0.014). L was smaller in human autopsy heart samples than in porcine heart samples, although data did not reach significance (16.66±1.30 mm vs. 17.30±0.51 mm, p = 0.32), and significantly smaller than that given by the manufacturer (16.66±1.30 mm vs. 18 mm, p = 0.015).
Conclusions/Significance
Micro-CT is a feasible tool for exact surveying of dedicated stent systems and could make a contribution to the development of these devices. The proximal diameter and proximal area of the stent system were considerably smaller in human autopsy heart samples than in porcine heart samples and than those given by the manufacturer. Special consideration should be given to the stent deployment procedure (and to the follow-up) of dedicated stent systems, considering final intravascular ultrasound or optical coherence tomography to visualize (and if necessary optimize) stent expansion.
Citation: Kralev S, Haag B, Spannenberger J, Lang S, Brockmann MA, Bartling S, et al. (2011) Expansion of the Multi-Link Frontier™ Coronary Bifurcation Stent: Micro-Computed Tomographic Assessment in Human Autopsy and Porcine Heart Samples. PLoS ONE 6(7): e21778. https://doi.org/10.1371/journal.pone.0021778
Editor: Giuseppe Biondi-Zoccai, University of Modena and Reggio Emilia, Italy
Received: January 22, 2011; Accepted: June 11, 2011; Published: July 21, 2011
Copyright: © 2011 Kralev et al. This is an open-access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.
Funding: The authors have no support or funding to report.
Competing interests: The authors have declared that no competing interests exist.
Introduction
The presence of a bifurcation lesion in patients with coronary artery disease (CAD) is a frequent morphology (8.5%). This incidence was found by a recent study investigating a cohort of 6129 consecutive patients undergoing coronary stent implantation [1]. In most lesion types, drug-eluting stents (DES) have reduced the incidence of revascularization after percutaneous coronary intervention (PCI [2], [3]), but in the case of bifurcation lesions, rates for adverse clinical events still remain high. A recent study investigating bifurcation stenting with sirolimus eluting stents reported in-stent restenosis rates in main vessel and/or side branch of between 6.6% (culotte technique) and 12.1% (crush technique [4]). Before that, main vessel and side branch restenosis rates of >25% were reported [5]–[7], with side branch restenosis considered as a main problem [8].
The existence of an ostial and bifurcation lesion itself is – besides long stents, overlapping stents, suboptimal stent results, stenting of small vessels, existence of multiple lesions, etc – a predictor for late stent thrombosis and restenosis [9], [10]. The high rates of restenosis were one of the reasons for the development of dedicated stent systems (DSS) but according to current guidelines for PCI [11], so far there is no recommendation for the use of DSS. Angiographic success, clinical outcome and development of DSS for coronary bifurcation lesions still remain a challenge and the European Bifurcation Club concluded in a recent state-of-the-art paper that the role of DSS is still the subject of debate, awaiting the “magic” device [12]. Micro-CT has been utilized to investigate oversized postdilation of DES [13], but no micro-CT data are available regarding DSS.
The aim of this study was to assess the expansion of the DSS Multi-Link (ML) Frontier™ (Abbott Vascular, Santa Clara, CA, USA) in human and porcine coronary arteries to provide the cardiologist with useful in-vitro information for stent implantation and selection, contributing to the development of these devices and the treatment of coronary bifurcation lesions.
Methods
The study was performed in accordance with federal laws and regulations, international accreditation standards, institutional policies and the local ethics committee (Medical Ethic Commission II, Faculty of Medicine Mannheim, University of Heidelberg). Written informed consent was obtained from all patients by the Department of Anatomy, University of Heidelberg, and data were analyzed anonymously.
Investigation background
In this in vitro study, seven autopsy heart samples from human subjects with known CAD and five porcine heart samples were appropriated. Human and porcine heart samples were immediately preserved with static cold flush with crystalloid solution [14]. Nine stents were implanted in human non-stenotic bifurcations 24–48 h after explantation and five stents were implanted in fresh vascular porcine bifurcation tissue 24 h after excisement (Figure 1). All heart samples were routinely processed for cardiac catheterization with standard 5, 6 or 7F guiding catheters and 0.014-inch floppy guide wires. Because of anonymization no detailed information about the CAD status was available.
Immediately after excisement the ML Frontier™ stents were implanted in fresh vascular bifurcation tissue in the porcine heart samples.
Stent implantation
In total, 14 ML Frontier™ stents with a nominal size of 3.0 mm×18 mm were successfully implanted in appropriate bifurcations under fluoroscopic control. Coronary intervention was performed each time using high-pressure stent deployment as recommended by the manufacturer (14 atm, duration 30–35 s). Angiography was then performed and the coronary perfusion was graded according to the Thrombolysis in Myocardial Trial (TIMI) classification [15]. The proximal and distal reference luminal diameters of the main vessels and the side branches were assessed before stent implantation by quantitative coronary angiography (QCA) and the stent/artery ratios were calculated.
Micro-CT
The stented segments were each prepared in a conical 50 ml polypropylene tube (BD Falcon™ Tube, Becton Dickinson, Franklin Lakes). Micro-CT was performed using an industrial micro-CT system (Yxlon Y.Fox, Yxlon International GmbH, Hamburg, Germany). A total of 1200 projections were acquired within 40 s of scan time (2×2 binning of the detector; 944×704 pixel; 360° rotation; 90 µA; 160 kV). Proprietary scanner control software was used to monitor the scanning process, and to save projection data. Standard cone-beam CT reconstruction was performed using a filtered back-projection algorithm (Reconstruction Studio Version 1.2, Comet GmbH, Garbsen, Germany) with Shepp-Logan filter applied. The reconstructed volumes (512 Matrix) were reviewed in multiplanar reformation (MPR) as well as in a 3D volume rendering mode using OsiriX-software (v3.5.1). Data sets were reviewed in MPR (OsiriX) and 3D volume rendering using standard radiological equipment (I-View 3D 1.0.2.3, TeraRecon Inc., San Mateo, USA). After that, devices were surveyed and proximal and distal stent diameters (PD, DD), side branch diameters (SBD), mean stent length (L), as well as the corresponding opening areas (PA, DA, SBA) were measured. The measurements were carried out in MPR-mode. The stent length (Figure 2, panel A), stent diameters and sidebranch diameters (Figure 3, panel A and B) were measured aligning the z-axis with the centreline of the stent looking exactly perpendicular into the stent lumen. In the real world stent opening is not always exactly circular, consequently the stent expansion cannot always be assessed by measuring a diameter, and two orthogonal angiographic views or IVUS (intravascular ultrasound, visualizing vessel lumen and stent opening area) are recommended for evaluation of stent expansion. As with IVUS, micro-CT also offers the possibility of visualizing the stent opening area. Therefore, in this study, in all cases both the diameters and the opening areas were measured and compared with the data given by the manufacturer. The compliance chart of the manufacturer contains the diameters of the stent, so the corresponding opening areas were calculated by applying the circle area formula Area = πr2 with r describing the radius of the circle, conforming to 1/2 the diameter. All opening areas were first manually traced by the observer and then determined by the software (Figure 3, panel C, sidebranch opening area).
2D measurement (panel A) and 3D visualization (panel B) of stent length by micro-CT.
Diameters were measured by aligning the z-axis with the centreline of the stent looking exactly perpendicular into the stent lumen (panel A, panel B). Panel C depicts the measurement of the side branch opening area (SBA). Measurements were performed in multiplanar reformation (MPR) mode.
Statistical analysis
Deviations from values given by the manufacturer were evaluated by the one sample t test. Data are presented as mean ± standard deviation (SD). Values of p<0.05 (two-tailed) were considered statistically significant. The calculations were performed using SPSS-Software (SPSS-Software GmbH, München, Germany).
Results
All DSS showed a successful angiographic result with a TIMI 3 flow. Detailed measurements of opening areas, corresponding diameters, stent lengths, reference luminal diameters and stent-to-artery ratios are presented in Table 1. The proximal stent diameters assessed in human autopsy heart samples were significantly smaller than in porcine heart samples (PD: 3.54±0.47 mm human vs. 4.04±0.22 mm porcine, p = 0.048) and than those given by the manufacturer (PD: 3.54±0.47 mm human vs. 4.03 mm manufacturer, p = 0.014). The mean stent length assessed in human autopsy heart samples was smaller than in porcine heart samples (L: 16.66±1.30 mm human vs. 17.30±0.51 mm porcine, p = 0.32) and significantly smaller than that given by the manufacturer (L: 16.66±1.30 mm human vs. 18 mm manufacturer, p = 0.015). Measured values of the distal stent diameter (DD: 3.24±0.41 mm human vs. 3.26 mm porcine, p = 0.91) and side branch diameter (SBD: 2.15±0.44 mm human vs. 2.2 mm porcine, p = 0.75) showed no significant difference between human autopsy heart samples, porcine heart samples and data given by the manufacturer (Figure 4).
Proximal stent diameters (PD) were significantly smaller in human autopsy heart samples than in porcine heart samples (P = 0.048) and than those given by the manufacturer (P = 0.014). The mean stent length was smaller in human autopsy hearts than in porcine heart samples (P = 0.32), and also significantly smaller than that given by the manufacturer (P = 0.015). Side branch diameters (SBD) and distal stent diameters (DD) did not differ significantly.
Correspondingly, the proximal stent opening area was significantly smaller than the area measured in porcine heart samples (PA: 10.00±2.42 mm2 human vs. 12.84±1.38 mm2 porcine, p = 0.034) and the area given by the manufacturer (PA: 10.00±2.42 mm2 human vs. 12.76 mm2 manufacturer, p = 0.009, calculated with the proximal diameter of the compliance chart). The distal stent opening area (DA: 8.39±2.06 mm2 human vs. 8.35 mm2 porcine, p = 0.96) and the side branch opening area (SBA: 3.77±1.40 mm2 human vs. 3.80 mm2 porcine, p = 0.94) did not differ significantly from areas measured in porcine heart samples or data given by the manufacturer (Figure 5).
Proximal stent opening areas (PA) were significantly smaller in autopsy human heart samples than in porcine heart samples and than those given by the manufacturer. Side branch opening areas (SBA) and distal stent opening areas (DA) did not differ significantly.
Exact 2D measurement and 3D visualization of the stent length is depicted in Figure 2, panels A and B. Adequate expansion of the distal opening and the side branch opening is depicted in Figure 6, panel A; inadequate expansion of the proximal opening is shown in Figure 6, panel B.
Adequate expansion of distal opening (panel A) and inadequate expansion of the proximal stent opening (panel B).
Discussion
Micro-CT is an independent method capable of measuring stent cells with high precision [13], [16]. This is the first study that has investigated a DSS by micro-CT, visualizing the deployment behaviour and assessing expansion in different tissue models. Proximal diameters of the devices implanted in human autopsy hearts were significantly smaller than in porcine heart samples and than the predicted diameter from the manufacturer's compliance chart. In comparison to the porcine heart samples, as in real world stenting conditions, the human heart samples had atherosclerosis. Atherosclerosis is associated with a higher vessel wall resistance and this might have led to a suboptimal expansion of the stent in comparison to the porcine heart samples and in comparison with the data given by the compliance chart. Proximal vessel diameters are generally larger than distal vessel diameters, which should ideally also be factored in the stent-balloon design. But conical ballons (proximal balloon ending larger than distal ballon ending) are not available, so this might be a reason why suboptimal stent expansion was observed mainly in the proximal stent part. Similar, it must be taken in account that coronary arteries are not linear so that vessel wall resistance in the curved part and/or shear forces of the coronary arteries due to atherosclerosis might hinder complete length expansion. Our results reflect findings of a previous study in which intravascular ultrasound (IVUS) was used to investigate four different stents demonstrating that the minimal stent diameters measured by IVUS were significantly smaller than those predicted by the manufacturers [17]. Regarding clinical data relating to the ML Frontier™, the FRONTIER stent registry [18] reported an initial device success of 91%. At 6 month follow-up, the MACE rate was 17.1% with a main branch in-stent restenosis (ISR) of 25.3%. Newer data evaluating the ML Frontier™ [19] reported a device success of 95% (postprocedural main vessel stenosis 19%) with a follow-up ISR rate of 29% (in-stent late lumen loss 0.52±0.44 mm). The results of the present study might contribute to a better understanding of these clinical trials, suggesting that in human heart samples with CAD the proximal part of the ML Frontier™ shows a smaller expansion characteristic than in porcine heart samples or in a water bath.
Our results are in accordance with the results of another study, reporting an incomplete apposition also at the proximal edge of the DSS AXXESS in two of 139 cases [20]. Although there is a case report of the ML Frontier™, showing an adequate proximal stent apposition documented by IVUS [21]. On balance, we agree with Bhalla et al., recommending careful stent deployment [22] and propose special consideration of balloon inflation pressure and duration, postdilation of the proximal stent part and final kissing balloon technique, respecting the individual lesion type of the patient to avoid stent malapposition.
Stent malapposition and its pathophysiological role in both ISR and stent thrombosis is of major importance. One of the leading sources of ISR is local vascular healing response associated with intimal hyperplasia [23]. Main predictors of ISR are final minimal luminal diameter, stent length and structural deformation of the stents with suboptimal vessel wall coverage [24], [25]. Insufficiently enlarged stent cells may also cause thrombus formation [26], [27]. Several important studies have demonstrated that stent underexpansion/malapposition is one of the major reasons for stent thrombosis [26], [28]–[31]. Focusing on data for bifurcation stenting, fewer data are available but similar mechanisms are thought to be implicated. Good positioning of the stent struts against the vessel wall, adequate stent openings and the stent length are – in addition to other factors such as delta angle, etc – crucial factors for successful bifurcation stenting [27], [32]–[34]. The results of the present study suggest that in human autopsy hearts with CAD the stent length might be slightly smaller than expected. More micro-CT studies with newer stent devices are needed to clarify this point. We agree with Mortier et al. who recommend careful selection of stent devices [16], and want to draw special attention also to the stent length. Therefore, after complex PCI with heavy calcification, need for multiple balloon inflation, etc, critical observation of the angiographic result in two orthogonal perspectives should be performed. In some cases IVUS, optical coherence tomography (OCT) or X-ray visual enhancement [35] might provide additional useful information, enabling optimization of the stent deployment.
Another conclusion of this study is that micro-CT is a feasible tool to visualize and survey expansion of dedicated stent systems in vitro. So far, only few data about micro-CT are available, but micro-CT has already been described as an adequate tool for the assessment of single wires, lumen, endo-luminal plaques, cell sizes of stents [16], [36], [37], as well as for the assessment of complex stenting strategies on silicone bifurcated vessel models [38]. Importantly, this study provides data on autopsy heart samples from human subjects with CAD. Performing this investigation strictly in accordance with the guidelines of the local ethics committee, data were anonymized and no information about the CAD status was (and is) available. Nevertheless, in the real world clinical setting there is also often no information available on the CAD status and decisions regarding the interventional approach are made after the first angiographic projections. In the porcine heart samples no CAD was expected or detected. Therefore we do not think that the absence of information regarding CAD status will have significantly influenced our results. The findings of the present study are of practical interest in the context of the interventional treatment of coronary bifurcation lesions, the stent selection and the follow-up investigations in patients already having undergone Multi-Link Frontier stent implantation.
Meanwhile, new DSS with promising first-in-human experiences [39], [40] are available (Abbott Frontier™, Petal™, AST SLK-View™, BIGUARD™, Devax Axxess Plus™, Y-Med SideKick™, Stentys™, Capella Sideguard™, Invatec Twin-Rail™, Minvasys Nile Croco™, Tryton™ and TriReme Antares SAS™). The Asian Bifurcation Club designed a new DSS (BIGUIDE™) and initiated an ongoing phase 1 preclinical study [5]. The European Bifurcation Club outlined in a consensus report the importance of stent design, maximal stent cell size and final kissing balloon inflation [41]. The present study may give rise to further micro-CT investigations, yielding more data about the expansion behaviour of DSS and thereby contributing to the development of these devices.
Limitations
Postmortem vessel wall resistance and the limited number of available autopsy heart samples (consequently limited number of investigated stents) might have influenced our data. Second, stent openings in real life are not always truly circular, so in these cases comparison with the data given by the manufacturer was made by assessing stent opening areas.
Conclusions
Micro-CT is able to provide useful information for the evaluation and should be taken into account for the development of DSS. In real life, the proximal part and the stent length of the ML Frontier™ stent might show smaller expansion characteristics than in porcine heart models or water bath. Therefore, special consideration should be given to the stent deployment procedure of DSS, considering final IVUS or OCT to visualize (and if necessary optimize) stent expansion.
Author Contributions
Conceived and designed the experiments: SK TS. Performed the experiments: SK TS BH JS MAB. Analyzed the data: SK TS K-KH MB. Contributed reagents/materials/analysis tools: SL MAB SB AM. Wrote the paper: SK. All authors revised the manuscript and provided approval of the finished paper.
References
- 1. Daemen J, van Twisk PH, Kukreja N, van Domburg RT, Boersma E, et al. (2009) The relative safety and efficacy of bare-metal and drug-eluting stents in low and high-risk patient subsets. An epidemiological analysis of three sequential cohorts of consecutive all comers (n = 6129). EuroIntervention 4(4): 464–474.
- 2. Lee CW, Park DW, Lee BK, Kim YH, Hong MK, et al. (2006) Predictors of restenosis after placement of drug eluting stents in one or more coronary arteries. Am J Cardiol 97(4): 506–511.
- 3. Morice MC, Serruys PW, Sousa JE, Fajadet J, Ban Hayashi E, et al. (2002) A randomized comparison of a sirolimus-eluting stent with a standard stent for coronary revascularization. N Engl J Med 346(23): 1773–1780.
- 4. Erglis A, Kumsars I, Niemelä M, Kervinen K, Maeng M, et al. (2009) Nordic PCI Study Group. Randomized comparison of coronary bifurcation stenting with the crush versus the culotte technique using sirolimus eluting stents: the Nordic stent technique study. Circ Cardiovasc Intervent 2: 27–34.
- 5. Chen SL, Louvard Y, Runlin G (2009) Perspective on bifurcation PCI. J Interv Cardiol 22(2): 99–109.Review.
- 6. Ikeno F, Kim YH, Luna J, Condado JA, Colombo A, et al. (2006) Acute and long-term outcomes of the novel side access (SLK-View) stent for bifurcation coronary lesions: a multicenter nonrandomized feasibility study. Catheter Cardiovasc Interv 67(2): 198–206.
- 7. Ge L, Airoldi F, Iakovou I, Cosgrave J, Michev I, et al. (2005) Clinical and angiographic outcome after implantation of drug eluting stents in bifurcation lesions with the crush stent technique: importance of final kissing balloon post-dilation. J Am Coll Cardiol 46(4): 613–620.
- 8. Colombo A, Moses JW, Morice MC, Ludwig J, Holmes DR Jr, et al. (2004) Randomized study to evaluate sirolimus-eluting stents implanted at coronary bifurcation lesions. Circulation 109(10): 1244–1249.
- 9. Grines CL, Bonow RO, Casey DE Jr, Gardner TJ, Lockhart PB, et al. (2007) Prevention of premature discontinuation of dual antiplatelet therapy in patients with coronary artery stents: a science advisory from the American Heart Association, American College of Cardiology, Society for Cardiovascular Angiography and Interventions, American College of Surgeons, and American Dental Association, with representation from the American College of Physicians. J Am Coll Cardiol 49(6): 734–739.
- 10. Lüscher TF, Steffel J, Eberli FR, Joner M, Nakazawa G, et al. (2007) Drug-eluting stent and coronary thrombosis: biological mechanisms and clinical implications. Circulation 115(8): 1051–1058.
- 11. King SB 3rd, Smith SC Jr, Hirshfeld JW Jr, et al. (2008) 2007 Focused Update of the ACC/AHA/SCAI 2005 Guideline Update for the Percutaneous Coronary Intervention: A Report of the American College of Cardiology/American Heart Association Task Force on Practice Guidelines (2008). Circulation 117: 261–295.
- 12. Legrand V, Thomas M, Zelisko M, De Bruyne B, Reifart N, et al. (2007) Percutaneous coronary intervention of bifurcation lesions: state-of-the-art. Insights from the second meeting of the European Bifurcation Club. EuroIntervention 3(1): 44–49.
- 13. Basalus MW, van Houwelingen KG, Ankone MK, Feijen J, von Birgelen C (2010) Micro-computed tomographic assessment following extremely oversized partial postdilation of drug-eluting stents. EuroIntervention 6: 141–148.
- 14. Jacobs S, Rega F, Meyns B (2010) Current preservation technology and future prospects of thoracic organs. Part 2: heart. Curr Opin Organ Transplant 15: 156–159.
- 15. The TIMI Group (1985) Thrombolysis in Myocardial Infarction (TIMI) trial: phase I findings. N Engl J Med 312: 932–936.
- 16. Mortier P, Van Loo D, De Beule M, Segers P, Taeymans Y, et al. (2008) Comparison of drug-eluting stent cell size using micro-CT: important data for bifurcation stent selection. EuroIntervention 4(3): 391–396.
- 17. De Ribamar Costa J Jr, Mintz GS, Carlier SG, Costa RA, Fujii K, et al. (2005) Intravascular ultrasonic assessment of stent diameters derived from manufacturer's compliance charts. Am J Cardiol 96(1): 74–78.
- 18. Lefèvre T, Ormiston J, Guagliumi G, Schultheiss HP, Quilliet L, et al. (2005) The Frontier stent registry: safety and feasibility of a novel dedicated stent for the treatment of bifurcation coronary artery lesions. J Am Coll Cardiol 46(4): 592–598.
- 19. Radke PW, Jain D, Conrad A, Thomsen C, Remmel M, et al. (2008) Evaluation of the dedicated Frontier coronary bifurcation stent: A matched pair analysis with drug-eluting and bare metal stents. Clin Res Cardiol 97(4): 260–265.
- 20. Miyazawa A, Ako J, Hassan A, et al. (2007) Analysis of bifurcation lesions treated with novel drug-eluting dedicated bifurcation stent system: intravascular ultrasound results of the AXXESS PLUS trial. Catheter Cardiovasc Interv 70(7): 952–957.
- 21. Amador Gil C, Delgado Espinosa A, Medina Fernández-Aceytuno A (2008) Ultrasound findings in a coronary bifurcation lesion treated using the frontier dedicated stent system. Rev Esp Cardiol 61(7): 765.
- 22. Bhalla KS, Anderson HV (2009) Drug-eluting stents: careful deployment required. JACC Cardiovasc Interv 2(5): 435–436.
- 23. Hoffmann R, Mintz GS, Dussaillant GR, Popma JJ, Pichard AD, et al. (1996) Patterns and mechanisms of in-stent restenosis. A serial intravascular ultrasound study. Circulation 94(6): 1247–1254.
- 24. El-Omar MM, Dangas G, Iakovou I, Mehran R (2001) Update on In-stent Restenosis. Curr Interv Cardiol Rep 3(4): 296–305.
- 25. Ino Y, Toyoda Y, Tanaka A, Ishii S, Kusuyama Y, et al. (2009) Predictors and prognosis of stent fracture after sirolimus-eluting stent implantation. Circ J 73(11): 2036–2041.
- 26. Costa RA, Mintz GS, Carlier SG, Lansky AJ, Moussa I, et al. (2005) Bifurcation coronary lesions treated with the “crush” technique: an intravascular ultrasound analysis. J Am Coll Cardiol 46(4): 599–605.
- 27. Ormiston JA, Webster MW, Ruygrok PN, Stewart JT, White HD, et al. (1999) Stent deformation following simulated side-branch dilatation: a comparison of five stent designs. Catheter Cardiovasc Interv 47(2): 258–264.
- 28. Takebayashi H, Kobayashi Y, Dangas G, Fujii K, Mintz GS, et al. (2003) Restenosis due to underexpansion of sirolimus-eluting stent in a bifurcation lesion. Catheter Cardiovasc Interv 60(4): 496–499.
- 29. Liu X, Doi H, Maehara A, Mintz GS, Costa JdeR Jr, et al. (2009) A volumetric intravascular ultrasound comparison of early drug-eluting stent thrombosis versus restenosis. JACC Cardiovasc Interv 2(5): 428–434.
- 30. Hassan AK, Bergheanu SC, Stijnen T, van der Hoeven BL, Snoep JD, et al. (2009) Late stent malapposition risk is higher after drug-eluting stent compared with bare-metal stent implantation and associates with late stent thrombosis. Eur Heart J 31(10): 1172–80.
- 31. Min SY, Kim YH, Park SJ (2009) Very late stent thrombosis of sirolimus-eluting stent combined with late stent malapposition and aneurysm formation. J Invasive Cardiol 9: E175–177.
- 32. Louvard Y, Lefèvre T, Morice MC (2004) Percutaneous coronary intervention for bifurcation coronary disease. Heart 90(6): 713–722.
- 33. Ormiston JA, Webster MW, El Jack S, Ruygrok PN, Stewart JT, Scott D, et al. (2006) Drug-eluting stents for coronary bifurcations: bench testing of provisional side-branch strategies. Catheter Cardiovasc Interv 67(1): 49–55.
- 34. Colombo A, Moses JW, Morice MC, Ludwig J, Holmes DR Jr, et al. (2004) Randomized study to evaluate sirolimus-eluting stents implanted at coronary bifurcation lesions. Circulation 109(10): 1244–1249.
- 35. Agostoni P, Verheye S (2007) Bifurcation stenting with a dedicated biolimus-eluting stent: X-ray visual enhancement of the final angiographic result with “StentBoost Subtract”. Catheter Cardiovasc Interv 70(2): 233–236.
- 36. Murasato Y, Hikichi Y, Horiuchi M (2009) Examination of stent deformation and gap formation after complex stenting of left main coronary artery bifurcations using microfocus computed tomography. J Interv Cardiol 22(2): 135–144.
- 37. Stiller W, Kobayashi M, Koike K, Stampfl U, Richter GM, et al. (2007) Initial experience with a novel low-dose micro-ct system. Rofo 179(7): 669–675.
- 38. Hikichi Y, Inoue T, Node K (2009) Benefits and limitations of cypher stent-based bifurcation approaches: in vitro evaluation using micro-focus CT scan. J Interv Cardiol 22(2): 128–134.
- 39. Verheye S, Grube E, Ramcharitar S, Schofer JJ, Witzenbichler B, et al. (2009) First-in-man (FIM) study of the Stentys bifurcation stent - 30 days results. EuroIntervention 4(5): 566–571.
- 40. Sheiban I, Omedé P, Biondi-Zoccai G, Moretti C, Sciuto F, et al. (2009) Update on dedicated bifurcation stents. J Interv Cardiol 22(2): 150–155.
- 41. Stankovic G, Darremont O, Ferenc M, Hildick-Smith D, Louvard Y, et al. (2009) Percutaneous coronary intervention for bifurcation lesions: 2008 consensus document from the fourth meeting of the European Bifurcation Club. EuroIntervention 5: 39–49.