We hypothesized that a novel three-dimensional virtual semi-transparent annulus plane (3D VSAP) presented on a holographic screen can be used to visualize the prolapsing tissue in degenerative mitral valve disease and furthermore, provide us with geometrical data of the mitral valve apparatus. Phantom and patient studies were designed to demonstrate the feasibility of creating a semi-automatic, semi-transparent mitral annulus plane visualized on a holographic display.
Methods
Ten pipe cleaners mimicking the mitral annulus with different shapes and three types of annuloplasty rings served as phantoms. We obtained 3D transoesophageal examination of the phantoms in a special designed box filled with water. Recordings were converted to the holographic display and a 3D VSAP was created. The ratio of the major and minor axes as well as the non-planar angles were calculated and compared with direct measures of the phantoms. Forty patients with degenerative mitral valve disease were then analyzed with 3D transthoracic echocardiography (TTE) and a 3D VSAP was created on the holographic display. A total of 240 segments were analyzed by two independent observers, one echo expert (observer I), and the other novice with limited echo experience (observer II). The two observers created the 3D VSAP in each patient before suggesting the valve pathology.
Results
The major/minor axes ratio and non-planar angles by 3D VSAP correlated with direct measurements by r = 0.65, p < 0.02 and r = 0.99, p < 0.0001, respectively. The sensitivity and specificity of the 3D VSAP method in patients was 81 and 97 %, respectively (observer I) and for observer II 77 and 96 %, respectively. The accuracy and precisions were 93.9 and 89.4 %, respectively (observer I), 92.3 and 85.1 % (observer II). Mitral valve analysis adding a 3D VSAP was feasible with high accuracy and precision, providing a quick and less subjective method for diagnosing mitral valve prolapse. This novel method may improve preoperative diagnostics and may relieve a better understanding of the pathophysiology of mitral valve disease. Thus, based on the specific findings in each patient, a tailored surgical repair can be planned and hopefully enhance long-term repair patency in the future.
Hinweise
Competing interests
The authors declare that they have no competing interests.
Authors’ contributions
KAD: Carried out the analysis and interpretation of data, drafting the manuscript and final approval of the manuscript submitted. JSK: Carried out the 3D software programming, analysis and interpretation of data and final approval of the manuscript. THV: Carried out the analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval of the manuscript submitted. AEF: Carried out the analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval of the manuscript submitted. RL: Carried out the analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval of the manuscript submitted. SU: Conception and design, analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval manuscript submitted. All authors read and approved the final manuscript.
Background
Degenerative mitral valve disease is a common disorder affecting around 2 % of the population [1]. Valve repair is the optimal treatment and is associated with improved quality of life with less morbidity as well as better long-term survival as opposed to replacement [2‐5]. Intraoperative 2D and real-time 3D transoesophageal echocardiography (TEE) are applied to guide the procedure and confirm a good result [6, 7]. Essentially, the surgical technique involves either resection or chordal replacement, or the combination of both [8‐11] and a prosthetic annuloplasty ring or band [9, 11, 12]. Different surgical repair techniques and annuloplasty rings that either maintain or restore the saddle-shape of mitral annulus are available today [13]. Successful repair depends on correct pre-treatment diagnostics, the repair technique and finally post-repair intra-operative evaluation by TEE. Increased knowledge of the geometry and function of the mitral valve apparatus may reduce the number of repair failures. In recent years, there has been enormous progress in medical imaging technologies and in particular 3D ultrasound [14]. A novel 3D holographic display has been developed and enables 3D visualization of real-time 3D ultrasound data without the need for special glasses [15]. We have recently demonstrated the feasibility of analyzing mitral valve pathology and thereby a potential application of the screen for improved visualization of the mitral valve apparatus [16].
In this proof of concept study, a prototype tool for visualization of a 3D virtual semi-transparent mitral annulus plane (3D VSAP) has been developed on the already existing 3D holographic display thereby increasing the ability to visualize the prolapsing segments of the mitral valve. The rationale of adding a virtual annulus plane is that it may enhance diagnostic accuracy of mitral valve disease, especially prolapses involving anterior leaflet, and furthermore, identify residual prolapses perioperatively, thus avoiding repair failures. We tested the feasibility of creating a virtual mitral annulus plane in a phantom and patient study.
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Methods
Phantom study
Proof of concept was tested with use of pipe cleaners, mimicking the mitral annulus (Fig. 1a and b). We obtained TEE recordings (6 VT, GE Healthcare) in a special designed box filled with water from a total of 10 pipe cleaners with different shapes and non-planar angles and three different mitral annuloplasty rings: Edwards Lifesciences Corporation Physio® I (36 mm), Physio® II (34 mm) and Edwards IMR® ring (30 mm). Data sets were stored as (VolDicom) and exported to a separate workstation connected to a holographic screen (Setred AS) for further analysis. The files containing volumetric ultrasound data needed to be decompressed before being shown on the 3D display. The decompression was done using standard DICOM tool. The full volume dataset was presented in three dimensions (x, y, z) on the display [16].
Fig. 1
Pipe cleaner number 2 mimicking mitral annulus seen from front (a) and profile view (b). c Profile of the same pipe cleaner with 3D VSAP as presented on the holographic screen. AL-PM anterolateral-posteromedial. AP anteroposterior
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The virtual plane on the holographic screen was derived by manually tracking the pipe cleaners along the “anteroposterior” cropping plane. This tracking consists of consecutively clicking out points along the circumference of the pipe cleaners, thus defining the external boundary of the virtual plane. Before tracking, a virtual line was drawn by clicking out points from “commissure to commissure “along the curvature of the phantoms to ensure the saddle shape of the annulus plane. The plane was finally made using a “Delaunay triangulation process” on all the points (Fig. 2) and was visualized as a three-dimensional semi-transparent blue surface. Typically, 20–25 points were needed to generate the 3D virtual plane. The signal intensity was adjusted leaving only the semi-transparent mitral annulus plane visible on the screen. Since we were not able to perform direct measurements on the 3D display, the annulus plane was projected into a 2D image showing the annulus plane in a front view (surgeon view) and side view (cropping plane perpendicular to the “anteroposterior” cropping plane) (Fig. 1c). The 2D images were stored in Paint (Microsoft®) and the ratio of the projected anterolateral-posteromedial and anteroposterior diameters (AL-PM/AP) as well as the non-planar angles for each pipe cleaner and annuloplasty ring were measured (Image J) (Fig. 3). Direct measurements of the phantoms (Image J) where obtained from photos of all pipe cleaners and annuloplasty rings (front and profile view similar to the projections from the 3D display).
Fig. 2
Shematic illustration of a phantom mimicking the mitral valve (Surgeon view) after labeling the circumference by mouse clicking (circular blue points) in a cropping plane perpendicular to the virtual plane. A line was drawn by clicking out points from “commissure to commissure“ (PMC to ALC) along the curvature of the phantoms to ensure the saddle shape of the annulus plane. A series of small triangles (Delaunay Triangulation) between the points generated the 3D surface that was made semitransparent (blue) to better appreciate the prolapsing tissue crossing the blue surface. ALC: Anterolateral commissure PMC: Posteromedial commissure
Fig. 3
Mitral valve and its corresponding measurements front view (a) and profile (b). AL-PM anterolateral-posteromedial. AP anteroposterior. Ao aorta
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Patient study
Study population
Patients with mitral valve regurgitation were prospectively recruited from the outpatient cardiac clinic at Oslo University Hospital, Rikshospitalet. Criteria for enrollment were degenerative mitral valve disease including patients with Barlow disease scheduled for valve surgery. Patients with arrhythmia were excluded. All patients gave written informed consent. The study protocol was approved by the regional Committees on Biomedical Research Ethics. A total of 40 patients were included, of these 6 patients with Barlow disease.
Echocardiography
Echocardiographic examinations were obtained at the Department of Cardiology, Oslo University Hospital, Rikshospitalet. Two dimensional transthoracic and transoesophageal echocardiographic recordings were obtained by a Vivid E9 (GE Healthcare, Horten, Norway). Blinded to the 2D recordings, real time 3D echo acquisition of the mitral valve apparatus was obtained using a 3D volumetric transducer (4 V, GE Healthcare). A full-volume scan was acquired from an apical approach (frame rate of 27.2 ± 8.1 frames per second and number of heart cycles obtained 3.9 ± 0.76). The patient was tilted approximately 45 towards a left lateral decubitus position. Data sets were stored digitally in raw data format (VolDicom) and exported to the holographic screen.
The full volume dataset was presented in three dimensions (x,y,z) on the 3D display. In addition, a dynamic presentation was feasible, adding the fourth dimension (time) to the analysis. The cine loop covered a complete heart cycle and the loop was manually stopped at a time frame in systole when the prolapse was most prominent for further analysis. A similar approach as used for the phantom study was applied when generating the 3D virtual plane in patients. The cropping plane, however, was approximately perpendicular to the AP-diameter, and we tracked the mitral annulus by moving the cropping plane along the AL-PM axis. As for the phantoms, 20–25 points were used to generate the virtual plane. The description of valve pathology was in accordance with Carpentier’s classification [17].
A total of 240 mitral valve segments from 40 patients were analyzed by two independent observers. One observer was experienced echocardiographer (Observer I), the other novice with limited echocardiographic training (Observer II). Findings were compared with visual inspection during surgery in 35 patients and from 2D TEE in 5 patients.
Statistics
Summary values are expressed as mean with standard deviation. Agreement between readers was measured using Cohen’s Kappa (Douglas G. Altman et al. Practical Statistics for Medical Research Chapman & Hall/CRC, 1991 pp 403–409). Grading of Kappa values was set at poor for 0–0.2; fair for 0.21–0.41; moderate for 0.41–0.6; good for 0.61–0.8 and very good for 0.81–1.0. Accuracy and precision was calculated according to the International vocabulary of metrology (JCGM 200:2008 International vocabulary of metrology - Basic and general concepts and associated terms (VIM)) according to the formula: Accuracy = (number of true positives + true negatives)/(number of true positives + true negatives + false negatives + true negatives) and precicion = number of true positives/(number of true positives + false positives). The AL-PM/AP ratio and non-planar angle measurements by the two methods (3D VSAP and direct measurements) were compared by use of the method of Bland and Altman [18] and by regression analysis with a least-squares method. We considered results significant at a value of p < 0.05.
Results
Phantom study
Table 1 shows the individual measurements of the pipe cleaners and annuloplasty rings (AL-PM/AP ratio and the non-planar angle) obtained by 3D VSAP method and direct measurements. The non-planar angles and AL-PM/AP ratios by 3D VSAP correlated with direct measurements by y = 0.97x + 5.5265, r = 0.99, p < 0.0001 and y = 0.7776x + 0.2944, r = 0.65, p < 0.02, respectively (Figs. 4 and 5). The Bland-Altman plots in Figs. 6 and 7 show the agreements between the non-planar angles and AL-PM/AP ratios, respectively.
Table 1
Ratio of major/minor axes (AL-PM/AP) and non-planar angles by 3D VSAP and direct measurements in pipe cleaners and the mitral annuloplasty rings
Correlation between non-planar angle in pipe cleaners and annuloplasty rings determined by 3D VSAP and direct measurements. y = 0.97x + 5.5265, r = 0.99, p < 0.0001
Fig. 5
Correlation between AL-PM/AP ratio in pipe cleaners and annuloplasty rings determined by 3D VSAP and direct measurements. y = 0.7776x + 0.2944, r = 0.65, p < 0.02
Fig. 6
Agreement between non-planar angle by 3D VSAP and direct measurements. Mean difference between methods and ± 2 SD are indicated
Fig. 7
Agreement between AL-PM/AP ratio by 3D VSAP and direct measurements. Mean difference between methods and ± 2 SD are indicated
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Patient study
Table 2 shows the basic echocardiographic findings in all patients. We were able to obtain an annulus plane in all subjects. Table 3 summarizes the results from mitral valve segment analysis by visual inspection during surgery and with 3D VSAP method by both observers. A
Table 2
Haemodynamic parameters
Age (years)
57 ± 15
Male (%)
72
Heart rate (bpm)
70 ± 12
LVIDd (mm)
63.3 ± 6.9
LVIDd indexed (mm/m2)
33.4 ± 3.8
LVIDs (mm)
40.3 ± 5.4
LVIDs indexed (mm/m2)
21.3 ± 3.2
LV EDV (ml)
211.3 ± 48.0
LV EDV indexed (ml/m2)
111.1 ± 22.5
LV ESV (ml)
80.4 ± 25.3
LV ESV indexed (ml/m2)
42.5 ± 12.2
LV Stroke volume (ml)
68.7 ± 16.9
LV Cardiac output (l/min)
4.7 ± 0.94
LV EF (%)
62 ± 4.8
LA area (mm2)
27.7 ± 6.4
MAD (AP) (mm)
3.95 ± 0.4
Regurgitant volume (ml/beat)
62.2 ± 26.7
Bpm, beats per minute, LVIDd, left ventricular internal dimension diastole, LVIDs, left ventricular internal dimension systole, LV SV, left ventricular stroke volume, LV EF, left ventricular ejection fraction, LV EDV, left ventricular end-diastolic volume, LV ESV, left ventricular end-systolic volume, LA, left atrium, MAD (AP), mitral annulus diameter (antero-posterior)
Table 3
Prolapsing segments suggested by the two observers (number of correct segments in parenthesis)
Prolapsing segments
Surgical findings
Observer I
Observer II
A1
1
0
0
A2
8
8(7)
5(5)
A3
6
5(4)
7(4)
P1
2
1(0)
1(0)
P2
31
31(30)
30(29)
P3
5
2(2)
5(2)
Number
53
47
48
Sensitivity
0.81
0.77
Specificity
0.97
0.96
total of 240 segments were analyzed and visual inspection during surgery revealed a total of 16 prolapsing segments. Both observers spent 2–6 min to complete the virtual annulus plane and describe the valve pathology. Figures 8a and 9a show representative recordings of different mitral valve pathology (surgeon view) and demonstrates where the prolapsing segments crosses the visualized plane. The sensitivity and specificity of the 3D VSAP method was 81 and 97 %, respectively (observer I) and for observer II 77 and 96 %, respectively. The accuracy and precisions were 93.9 and 89.4 %, respectively (observer I), 92.3 and 85.1 % (observer II). The inter-observer agreement was 0.96 with Cohen’s Kappa 0.86.
Fig. 8
Surgeon view of the mitral valve from a patient with P2 prolapse as presented on the holographic screen. 3D VSAP is visible as a semi-transparent blue plane showing clearly the prolapsing segment that crosses the surface (a). b The same patient without 3D VSAP. Ao aorta, RV right ventricle, P2 indicating prolapse of mid segment posterior leaflet
Fig. 9
Surgeon view of the mitral valve from a patient with A3/P3 prolapse as presented on the holographic screen. 3D VSAP is visible as a semi-transparent blue plane showing clearly the prolapsing segments that crosses the surface (a). b The same patient without 3D VSAP. Ao aorta, RV right ventricle, A3 and P3 indicating prolapse of the posteromedial segments of the mitral leaflets
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Discussion
The introduction of 3D echocardiography opens for improved diagnostics and treatment of valvular heart disease. Still, the exact extension of prolapsing tissue in degenerative mitral valve disease may be challenging, particularly in Barlow’s disease, and the use of a virtual annulus plane may be beneficial. Perioperative 3D VSAP may improve the diagnostic accuracy of on-table quality control after mitral valve repair.
The present study demonstrates proof of concept and shows good agreement between the 3D VSAP presented on the holographic screen and the configuration of the phantoms (pipe cleaners and annuloplasty rings). Furthermore, we showed in patients that the semitransparent annulus plane could easily visualize which part of the leaflets that was crossing the plane (Figs. 8 and 9) in good agreement with the findings during surgery. More important, a very good inter-observer agreement was demonstrated, indicating that a novice with limited echocardiographic experience can perform advanced segment analysis similar to the expert.
The importance of analyzing the annulus plane in mitral regurgitation has been addressed in several studies the recent years [19‐24]. Both animal studies and simulations have shown the effect of different annuloplasty rings on mitral leaflet dynamic motion [24] and leaflet strains [20]. The present 3D VSAP method may enable better and rapidly mitral annular assessment, ensuring appropriate annuloplasty selection and perioperative assessment of the valve repair We demonstrated the feasibility of creating an “annulus plane” in phantoms (pipe cleaners and annuloplasty rings) and the measured non-planar angles and dimensions (ratios) correlated well with direct measurements. This could open for a more robust estimation of the annulus plane after implantation of the ring perioperatively, and may expose small residual prolapses that need to be addressed on-table.
When proven robust, the method can be applied in multicenter studies to demonstrate whether use of a virtual annulus plane provides better short- and long-term repair patency.
The patient study was obtained with 3D TTE. The reason for using TTE recordings, was that 3D TEE files were too large to be transferred to the holographic screen. This will be solved in the near future and the segmentation of the mitral annulus is expected to be easier with better acoustic windows. Furthermore, the virtual plane is only visible in one time frame, therefore tracking algorithms will be developed to show the plane moving throughout the heart cycle providing dynamic information about the deformity and rigidity of the mitral annulus.
Conclusion
The presentation of a semi-transparent annulus plane was feasible, and the estimated non-planar angle in phantoms correlated well with direct measurements. In patients, we were able to obtain the virtual mitral plane in all, visualizing the prolapsing segments with a good accuracy and precision by both observers. A potential application of this method is more precise localization and quantification of prolapsing leaflet tissue in mitral valve disease.
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Acknowledgement
We would like to thank Jan Otto Beitnes, MD, PhD for his contribution to the statistical section.
Funding sources
S. Urheim is recipient of research grants from The Research Council of Norway.
Edwards Lifesciences Corporation® provided the PHYSIO, IMR ETLOGIX and the PHYSIO II annuloplasty rings used in the study.
The funding sources had no role in the design or the conduct of the study.
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Disclosures
Stig Urheim has accepted fees from GE Vingmed to speak at their invitations.
Jørn Skaarud Karlsen receives a fee from Setred through Kalkulo AS for computer programming.
This article is published under license to BioMed Central Ltd. This is an Open Access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/4.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly credited. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.
Competing interests
The authors declare that they have no competing interests.
Authors’ contributions
KAD: Carried out the analysis and interpretation of data, drafting the manuscript and final approval of the manuscript submitted. JSK: Carried out the 3D software programming, analysis and interpretation of data and final approval of the manuscript. THV: Carried out the analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval of the manuscript submitted. AEF: Carried out the analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval of the manuscript submitted. RL: Carried out the analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval of the manuscript submitted. SU: Conception and design, analysis and interpretation of data, revising the manuscript critically for important intellectual content and final approval manuscript submitted. All authors read and approved the final manuscript.
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