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Comparative computed flow dynamic analysis of different optimization techniques in left main either provisional or culotte stenting

  • Gianluca Rigatelli EMAIL logo , Fabio Dell’Avvocata , Marco Zuin , Sara Giatti , Khanh Duong , Trung Pham , Nguyen Si Tuan , Dobrin Vassiliev , Ramesh Daggubati and Thach Nguyen
Published/Copyright: December 29, 2017
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Journal of Translational Internal Medicine
From the journal Journal of Translational Internal Medicine Volume 5 Issue 4

Abstract

Background and Objectives

Provisional and culotte are the most commonly used techniques in left main (LM) stenting. The impact of different post-dilation techniques on fluid dynamic of LM bifurcation has not been yet investigated. The aim of this study is to evaluate, by means of computational fluid dynamic analysis (CFD), the impact of different post-dilation techniques including proximal optimization technique (POT), kissing balloon (KB), POT-Side-POT and POT–KB-POT, 2-steps Kissing (2SK) and Snuggle Kissing balloon (SKB) on flow dynamic profile after LM provisional or culotte stenting.

Methods

We considered an LM-LCA-LCX bifurcation reconstructed after reviewing 100 consecutive patients (mean age 71.4 ± 9.3 years, 49 males) with LM distal disease. The diameters of LAD and LCX were modelled according to the Finnet’s law as following: LM 4.5 mm, LAD 3.5 mm, LCX 2.75 mm, with bifurcation angle set up at 55°. Xience third-generation stent (Abbot Inc., USA) was reconstructed and virtually implanted in provisional/cross-over and culotte fashion. POT, KB, POT-side-POT, POT-KB-POT, 2SK and SKB were virtually applied and analyzed in terms of the wall shear stress (WSS).

Results

Analyzing the provisional stenting, the 2SK and KB techniques had a statistically significant lower impact on the WSS at the carina, while POT seemed to obtain a neutral effect. In the wall opposite to the carina, the more physiological profile has been obtained by KB and POT with higher WSS value and smaller surface area of the lower WSS. In culotte stenting, at the carina, POT-KB-POT and 2SK had a very physiological profile; while at the wall opposite to the carina, 2SK and POT–KB-POT decreased significantly the surface area of the lower WSS compared to the other techniques.

Conclusion

From the fluid dynamic point of view in LM provisional stenting, POT, 2SK and KB showed a similar beneficial impact on the bifurcation rheology, while in LM culotte stenting, POT-KB-POT and 2SK performed slightly better than the other techniques, probably reflecting a better strut apposition.

Key words: left main stenting; stenting techniques; computational fluid dynamic analysis

Introduction

During crossover/provisional left main (LM) stenting, final kissing balloon inflation (KBI), with simultaneous inflation of the main vessel (MV) and side branch (SB) balloons, has been thought to be most effective in order to secure SB patency, reduce SB stenosis and remove jailed struts. [1]

The advantage of KBI over non-KBI treatment in terms of major adverse cardiac events (MACE), has not been proven despite lower SB diameter stenosis at a six to 12-month follow-up.[2-3] On the other hand, proximal optimization technique (POT), which is a dilation of the MV proximal to the carina, has been proved to correct the proximal MV malapposition and optimize SB ostium strut opening for proper wire re-crossing in the distal cell.[4] Modifications of both techniques have been proposed in order to achieve a bigger SB ostium with low MV distortion and malapposition. These new techniques include the sequential POT-side-POT as alternative to KB,[5] the POT-KB-POT,[6] the 2-step kissing (2SK)[7] and the snuggle KB (SKB) or T-ballooning.[8]

The exact hemodynamic value of these new techniques has not been investigated in the standard coronary artery bifurcation. Which is the ideal technique in the LM bifurcation scenario independent of the provisional or dual stenting techniques? As designing a randomized trial evaluating the outcomes of such different techniques in a homogeneous population of LM disease is conceptually impossible and economically expensive, computational fluid dynamic (CFD) analysis,[9] which has been applied in many fields of cardiovascular medicine, may give at least a suggestion on the impact of such techniques on flow physiology and may represent the basis for further in-vivo investigation. The aim of the study is to evaluate by CFD the impact of provisional single-stenting or culotte dual-stenting on flow dynamic of LM bifurcation and LAD/LCX ostia.

Material and methods

Left main model

For the computational domain analysis, we considered a LM-LCA-LCX bifurcation reconstructed after analyzing 100 consecutive patients (mean age 71.4 ± 9.3 years, 49 males) with LM distal disease, who underwent percutaneous coronary intervention (PCI) between January 1st, 2016 and January 1st, 2017. The mean diameter of the proximal LM, LAD and LCX by quantitative coronary analysis (QCA) was 4.62 ± 0.86 mm, 3.31 ± 0.92 mm, and 2.74 ± 0.93 mm, respectively. The mean LAD-LCX bifurcation angle, measured after the diagnostic angiography using an electronic goniometer was 53.6° ± 12.3°, whereas the mean length of LM was 19.4 ± 4.1 mm (Figure 1). The mean diameter stenosis by QCA was 82% ± 7.6%. The diameter of the ascending aorta at the origin of the left coronary artery was 28 ± 4.7 mm. The diameters of LAD and LCX were modelled according to the Finnet’s law[10] resembling the in-vivo measurements, as following: LM 4.5 mm, LAD 3.5 mm, LCX 2.75 mm, with bifurcation angle set up at 55°. The LM was divided into three sections including ostium, mid-shaft and distal portion. A plaque inducing a stenosis of 90% was placed at the mid-shaft/distal position (Figure 1). The model was constructed using Rhinoceros v. 4.0 Evaluation (McNeel & Associates, Indianapolis, IN). Pressure was assumed to be stable at 120/80 mmHg.

Figure 1 Left main coronary artery bifurcation model: A) model diameter and length; B) Appearance of the virtual implantation of Xience in provisional stenting fashion; C) Appearance of the virtual implantation of Xience in culotte fashion; D) Xience design and reconstruction.
Figure 1

Left main coronary artery bifurcation model: A) model diameter and length; B) Appearance of the virtual implantation of Xience in provisional stenting fashion; C) Appearance of the virtual implantation of Xience in culotte fashion; D) Xience design and reconstruction.

Stent simulation

For the stent simulation, we reconstructed the strut design and linkage pattern of a third-generation, everolimuseluting stent ( Xience, Abbot Corp, USA), used in our institution. Computer Aided Design (CAD) software was used to reproduce the stented geometry as accurately as possible (SolidWorks 2009, SolidWorks Corp, Concord, MA). At first, we created the solid model of the coronary artery bifurcation and then the expanded stent geometry (Figure 1). For this purpose, a hollow tube with outer diameter equal to both the nominal expanded diameter and thickness of the stent was created. Then, a 2-dimensional sketch with the stent’s strut was propagated and wrapped around the tube. Through a cut-out, the obtained ring of the stent was propagated axially to create a full-length, expanded model.

Interventional protocols adopted in the simulation

Cross-over/provisional stenting: 1) Predilation of MV 1:1 with non-compliant balloon; and 2) Stenting of MV with stent diameter according to the distal MV reference diameter as currently recommended.[11]

Culotte stenting: 1) Predilation of both branches 1:1 with non-compliant balloon; 2) Stenting of MV to SB; 3) Opening the stent cell with small 2.0 × 15 mm balloon; and 4) Stenting MB proximal to distal.

Steps for different post-dilation techniques are reported in Table 1. Only POT was not considered in the analysis of culotte stenting because it is not used in clinical practice in dual stenting.

Table 1

Steps for each technique included in the computational analysis

Steps
Techniques123
POTInflation of SC balloon 4.5 × 6 mm at 20 atm
KBInflation of the SB with SC balloon 2.0 × 15 mm at 16 atmSimultaneous inflation of 3.5 × 15 (LM to LAD) e 2.75 × 15 mm (LM to LCX) SC balloons at 18 atm
POT -Side-POTInflation of SC balloon 4.5 × 6 mm at 20 atmInflation of 2.75 × 15 mm (LM to LCX) NC balloon at 18 atmInflation of SC 4.5 × 6 mm balloon at 20 atm
POT-KB-POTInflation of SC balloon 4.5 × 6 mm at 20 atmSimultaneous inflation of 3.5 × 15 (LM to LAD) e 2.75 × 15 mm (LM to LCX) SC balloons × 6 mm at 20 atm at 18 atmInflation of SC balloon 4.5
2SKInflation of the SB with SC balloon 2.0 × 15 mm at 16 atmInflation of 3.5 × 15 (LM to LAD) SC balloon at 18 atmInflation of 2.75 × 15 mm (LM to LCX) SC balloon at 18 atm
SKBSimultaneous inflation of 3.5 × 15 (LM to LAD) e 2.75 × 15 mm (LM to LCX) SC balloons at 18 atm with the marker of the SB balloon at the middle of the MB balloon

  1. LAD: left anterior descending coronary artery; LCX: left circumflex coronary artery; LM: left main; KB: kissing balloon; POT: proximal optimization technique; SKB: snuggle kissing balloon; 2SK: 2-step sequential kissing balloon; atm: atmosphere

Virtual Implantation

After the stent model was placed in the correct position as per the different stenting techniques, material removal was applied depending on the considered techniques. Subsequently, using the Boolean operation, the modified solid model was subtracted from the bifurcation model to obtain the final geometry. Specifically, we assumed that after stent deployment and implantation, both in the main and side branch, there were no residual stenosis.

CFD analysis

To analyze the spatially resolved velocity, pressure and wall shear stress (WSS), we used CFD simulations. In particular, we modelled blood as a non-Newtonian, viscous and incompressible fluid. Density was defined as 1060 kg/m3, according to the standard values cited in the literature. Blood was represented by the Navier-Stokes equation:

V⋅∇=−∇⋅τ−∇P(12)

and continuity equation:

∇⋅V=0(12)

where v is the 3D velocity vector, P pressure, r density and τ the shear stress term. Instead, Carreau model was adopted for viscosity:

μ=μ∞+(μ0−μ∞)[1+(λγ˙)2](n−12),whereλ=3.313s,n=0.3568,μ0=0.56Pandμ∞=0.0345P(13)

Given that coronary artery perfusion is primarily diastolic, at the inlet we considered a steady blood flow velocity (0.18 m/s) and pressure (10,665 Pa equivalent to 80 mmHg).[12, 14] The hemodynamic parameters that were assessed at stented LM bifurcation were static pressure (Pa), WSS (Pa) and area of lower WSS (cm2) through the carina, which is one of the most sensible site for restenosis/thrombosis in coronary bifurcation.[15] The numeric grid was created from the geometry using ANSYS Meshing 14.0 (Ansys, Inc., Canonsburg, PA), while the simulations were conducted using the commercial software ANSYS FLUENT 14.0 (Ansys, Inc., Canonsburg, PA).

Fluid parameters

Static and dynamic pressure in the vessel was evaluated in Pascal. Practically, low static pressure is generally related to an increased vessel wall thickness. [16] In particular, dynamic pressure has been defined as:

q≡12v2

Wall shear stress (Pa) has been defined as the force that is tangentially acting to the surface due to friction. As it is well known, low wall shear stress is related to the development of greater plaque and necrotic core progression with a constrictive remodeling, whereas high wall shear stress segment develops greater necrotic core and calcium progression with expansive remodeling.[17-18]

Results

Provisional stenting analysis

The 2SK and KB techniques resulted in a statistically significant lower impact on the WSS at both LAD/LCX ostia and a surface area with lower WSS at the carina. These results were very similar to the physiologic model (233 and 254 mm2, respectively vs. 202 mm2, P = 0.03 and P = 0.001), while POT resulted in a neutral effect. On the contrary, POT-side-POT, POT-KB-POT and SKB had the worst physiologic profile (Table 2, Figure 2).

Table 2

Fluid dynamic profile in Left main provisional/cross-over stenting.

Pressure at the carina (mmHg)WSS LAD (Pa)WSS LCX (Pa)WSS carina (Pa)Area of lower WSS at carina (mm2)WSS opposite to the carina (Pa)Area of lower WSS opposite to the carina (mm2)
Physiological Model80[a]10.624[a], [b]12.803[a]3.266[a]201[a], [b], [c]2.28[a], [b]186[a], [b]
POT-Side-POT79.29.21010.6572.740508[b]2.96[b]304[b]
KB only80.810.40712.063.1002543.02214
POT-KB-POT79.3[a]8.415[a]9.729[a]2.503[a]489[a]2.44[a]288[a]
POT only79.59.60811.122.8602782.52201
2SK79.49.66511.993.0252332.19218
SKB79.38.897[b]9.554[b]2.478[b]471[c]3.58265

  1. KB: kissing balloon; POT: proximal optimization technique; 2SK: 2-step kissing; SKB: snuggle kissing balloon; Clear values: P > 0.5

Figure 2 Computed flow dynamic representation of area of lower Wall Shear Stress forces at the carina site using the different post-dilation techniques in Provisional stenting: the area of Wall Shear Stress forces results smaller in kissing balloon and 2-step kissing balloon compared to the others.
Figure 2

Computed flow dynamic representation of area of lower Wall Shear Stress forces at the carina site using the different post-dilation techniques in Provisional stenting: the area of Wall Shear Stress forces results smaller in kissing balloon and 2-step kissing balloon compared to the others.

At the wall opposite to the carina, a more physiological profile was obtained only by KB and POT with higher WSS and smaller area of lower WSS, respectively. At the same time, POT-KB-POT, POT-side-POT and SKB, again obtained a worst profile (Table 2, Figure 3).

Figure 3 Histograms representation of the comparison of Wall Shear Stress forces value (Panel A) and area of lower Wall Shear Stress forces at the wall opposite to the carina (Panel B) between Provisional (blue bars) and Culotte stenting (orange bars) techniques. *P < 0.05, **P < 0.001.
Figure 3

Histograms representation of the comparison of Wall Shear Stress forces value (Panel A) and area of lower Wall Shear Stress forces at the wall opposite to the carina (Panel B) between Provisional (blue bars) and Culotte stenting (orange bars) techniques. *P < 0.05, **P < 0.001.

Culotte stenting analysis

At the carina, only POT-KB-POT and 2SK resulted in a good profile compared to the physiological model with a smaller surface area of lower WSS at the carina (220 mm2vs. 202 mm2 (P < 0.03), while the KB and POT-Side-POT techniques provided slightly worse results particularly at the carina and ostium of LCX (Table 3, Figure 4).

Figure 4 Computed flow dynamic representation of area of lower Wall Shear Stress forces at the carina site using the different post-dilation techniques in Culotte stenting: the area of Wall Shear Stress forces results smaller in POT-kissing balloon-POT and 2-steps kissing balloon compared to the others.
Figure 4

Computed flow dynamic representation of area of lower Wall Shear Stress forces at the carina site using the different post-dilation techniques in Culotte stenting: the area of Wall Shear Stress forces results smaller in POT-kissing balloon-POT and 2-steps kissing balloon compared to the others.

Table 3

Fluid dynamic profile in Left main Culotte stenting

Pressure at the carina (mmHg)WSS LAD (Pa)WSS LCX (Pa)WSS carina (Pa)Area of lower WSS at carina (mm2)WSS opposite to the carina (Pa)Area of lower WSS opposite to the carina (mm2)
Physiological Model80.010.624[a], [b]12.800[a], [b]3.266[a], [b]208[a], [b]2.28186
POT-Side-POT80.210.15012.324[a]3.102249[b]2.11221
KB only80.210.20412.4773.189236[a]2.16214
POT-KB-POT79.910.76912.6983.403[a]2202.45205
2SK79.810.125[a]12.3553.2792282.14219
SKB79.89.995[b]12.239[b]3.104c2092.35198

  1. KB: kissing balloon; POT: proximal optimization technique; 2SK: 2-step kissing; SKB: snuggle kissing balloon.

At the wall opposite to the carina, the SKB, 2SK, and POT–KB-POT techniques provide the best performance in terms of rheology with a very small area of low WSS and high WSS value in general, while the KB and POT-side-POT techniques resulted again as the worst performers (Table 3, Figure 3).

Discussion

Our study suggested that from a fluid dynamic point of view, for LM provisional stenting, the POT, KB and 2SK techniques showed similar beneficial impacts on the bifurcation rheology, which were of higher WSS at the opposite wall and smaller surface area of low WSS at the carina, In LM culotte stenting, the POT-KB-POT and 2SK techniques provided slightly better results than the other techniques.

The single stent-provisional and dual stent-culotte techniques are the most widely used techniques to treat LM bifurcation in the real world. These techniques showed good long-term outcomes in both past and recent trials.[19-20] How to perform and which is the ideal post-dilating technique is still being hotly debated. In the past, the classic final KB inflation constituted the “mantra” of the interventional cardiologist in the optimization of LM stenting. More recently, the POT and its modified techniques such as the POT-Side-POT, 2SK and SKB showed high potential of correcting the KB drawbacks, while achieving a great ostial opening for the SB. Many bench and clinical studies showed that KB restores the MV stent volume, area, and symmetry loss after SB dilation in the bifurcation segment at the cost of some zones of struts malapposition due to the effect and a certain proximal elliptical deformation.[21] On the contrary, POT promoted full proximal stent apposition and conferred a more natural circular shape to the proximal segment of the MV.[6] POT also increased the size of opening of the SB ostium and by that, facilitated a distal wire re-crossing, independent of which stent type was used.[22]

Intriguingly in our study, neither POT (only in provisional stenting) nor KB (only in dual stenting) were able to increase significantly the WSS at both carina and the wall opposite to the carina, compared to the novel techniques. In provisional stenting, KB and its modifications, the 2SK, performed better than POT at the carina site, while at the wall opposite to the carina, POT provided smaller area of lower WSS compared to all the other techniques. On the other hand, after culotte stenting, POT modifications, the so-called POT-KB-POT and 2SK, performed better than the classical KB, particularly at the carina and wall opposite to the carina, where the WSS were much lower with KB only or with POT-side-POT.

In the past, other studies could explain these findings and at least partially confirmed the bench study results.[5, 6] POT had the maximum impact only on the proximal part of the MV and opened the struts of the SB, while at the wall of the SB opposite to the carina, POT increased the apposition of struts but not at the carina itself.

In our study, the technique implying simultaneous or sequential dilation of MV and SB increased WSS at the carina and at the wall opposite to the carina as well. However, in dual stenting, the sequential technique was not beneficial as much as when it was associated with POT. Indeed, KB only induced a bottleneck effect with lower WSS at the carina and this problem could only be corrected with a second POT. These observations suggest that a better strut apposition rather than a more complete coverage induced a smaller area of lower WSS, which produced a beneficial effect in respect to restenosis and more importantly thrombosis. As matter of fact, narrow strut spacing leads to larger areas of adverse low WSS, an effect which in part could be mitigated by reducing the struts thickness and size.[23] In our study, the conclusion could be made that the beneficial mechanism of POT, 2SK and KB were more likely due to better strut apposition rather than homogenous strut coverage.

Limitations

Some confounders would be different and multiple including the particular stenting technique considered in our study, obviously different from DK-crush or T-stent, the pressure of inflation and deployment, the angle of the carina that is a mean angle driven from the anatomical findings of our standard population, the diameter of the model that again reflects the mean vessel diameters of our population. Moreover, our study takes into account an ideal left main model. The artery has been considered non-compliant, straight and stationary. However, coronary artery perfusion is mainly diastolic and previous studies have already demonstrated that myocardial motion has a negligible effect on blood flow distribution on the arterial tree. Our model considered an optimal stent deployment without residual stenosis despite use in daily clinical practice, the different angles, the amount and circumferential extent of the calcium, the length of the respective lesion, and many other parameters have an obvious impact on the implantation technique and outcomes. Moreover, imposed hemodynamic conditions assume that the patient was hemodynamically stable. Other limitations of the study are that we did not evaluate the time averaged wall shear stress (TAWWS), oscillatory index (OSI) and the relative residence time, which had a recognized role in the treatment of coronary artery stenosis.

Conclusions

Different post-dilation techniques analyzed by CFD have a different impact on rheolysis of LM bifurcation with a more significant effect after provisional stenting, as compared to culotte stenting.

Although not transferrable to clinical practice, our study substantially confirmed and enhanced the clinical value of recently proposed modification of POT and KB in LM stenting such as 2SK in provisional and POT–KB-POT in culotte stenting, suggesting a good strut apposition as the basis of maintaining a beneficial bifurcation rheology. The apparent negative or neutral impact on bifurcation rheology by the other techniques should probably be viewed in the light of the positive effects on stent apposition and geometry using these two stenting techniques. Whether these findings would be confirmed using other stenting techniques and in anatomical scenario different from LM, should be tested in further studies. However, clinical trials, although difficult to conceive, are needed to assess the real contribution of all these techniques on the long-term outcomes of LM stenting.

Dr. Gianluca Rigatelli, MD, PhD, EBIR, FACP, FACC, FESC, FSCAI, Cardiovascular Diagnosis and Endoluminal Interventions, Rovigo General Hospital, Rovigo 45100, Italy.

  1. Conflict of Interest: None of the other authors have identified a conflict of interest.

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Published Online: 2017-12-29

© 2017 Gianluca Rigatelli, Fabio Dell’Avvocata, Marco Zuin, Sara Giatti, Khanh Duong, Trung Pham, Nguyen Si Tuan, Dobrin Vassiliev, Ramesh Daggubati, Thach Nguyen

This article is distributed under the terms of the Creative Commons Attribution Non-Commercial License, which permits unrestricted non-commercial use, distribution, and reproduction in any medium, provided the original work is properly cited.

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https://doi.org/10.1515/jtim-2017-0035
Keywords for this article
left main stenting; stenting techniques; computational fluid dynamic analysis
Creative Commons
BY-NC-ND 3.0

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