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Temporally Targeted Imaging Method Applied to ECG-Gated Computed Tomography

Rationale and Objectives

Existing cardiac imaging methods do not allow for improved temporal resolution when considering a targeted region of interest (ROI). The imaging method presented here enables improved temporal resolution for ROI imaging (namely, a reconstruction volume smaller than the complete field of view). Clinically, temporally targeted reconstruction would not change the primary means of reconstructing and evaluating images, but rather would enable the adjunct technique of ROI imaging, with improved temporal resolution compared with standard reconstruction (∼20% smaller temporal scan window). In gated cardiac computed tomography (CT) scans improved temporal resolution directly translates into a reduction in motion artifacts for rapidly moving objects such as the coronary arteries.

Materials and Methods

Retrospectively electrocardiogram gated coronary angiography data from a 64-slice CT system were used. A motion phantom simulating the motion profile of a coronary artery was constructed and scanned. Additionally, an in vivo study was performed using a porcine model. Comparisons between the new reconstruction technique and the standard reconstruction are given for an ROI centered on the right coronary artery, and a pulmonary ROI.

Results

In both a well-controlled motion model and a porcine model results show a decrease in motion induced artifacts including motion blur and streak artifacts from contrast enhanced vessels within the targeted ROIs, as assessed through both qualitative and quantitative observations.

Conclusion

Temporally targeted reconstruction techniques demonstrate the potential to reduce motion artifacts in coronary CT. Further study is warranted to demonstrate the conditions under which this technique will offer direct clinical utility. Improvement in temporal resolution for gated cardiac scans has implications for improving: contrast enhanced CT angiography, calcium scoring, and assessment of the pulmonary anatomy.

The use of electrocardiogram (ECG)-gated computed tomography (CT) in the assessment of coronary artery disease has been rapidly escalating in recent years, and is increasingly recognized as an accurate, noninvasive means to detect obstructive coronary artery disease ( ). The utility of cardiac CT has been demonstrated in both calcium scoring and contrast enhanced coronary angiography ( ). It has been recommended that calcium scoring be applied to the asymptomatic population for risk assessment; while CT angiography may serve as an alternative or adjunct to invasive coronary catheterizations for a subset of symptomatic patients ( ). Scanning with state-of-the-art 64-slice multidetector (MD)CT scanners has demonstrated a high negative predictive value for the identification of significant lesions (ie, those stenoses that are greater than 50%) ( ), thereby demonstrating significant clinical utility of 64-slice MDCT scanners. To lower the heart rate, β-blocker medication is routinely prescribed to the patient before scanning. However, because of the intrinsic requirement for mechanical rotation of both the source and detector in MDCT scanners, motion blurring can still occur in the reconstructed coronary angiography images. In a recent study using a state-of-the-art 64-slice scanner, some motion artifacts were present in approximately half of the examined coronary segments, and moderate motion artifacts were present in 14% of the examined coronary segments ( ). To combat these artifacts, one vendor recently released a dual source scanner ( ) that offers significant gains in temporal resolution. However, because there is a large installation base of single source scanners the task of improving image quality on these scanners is of significant consequence. Therefore a need remains to improve on the current image reconstruction techniques for single source CT scanners. The technique proposed in this work enables improved temporal resolution for regions of interest (ROIs).

Standard clinical reconstruction of the entire field of view (FOV) requires projection data acquired over an angular range of 180° plus the angle covered by the fan beam (“fan angle”) ( ). Current state-of-the-art cardiac imaging methods do not allow for improved temporal resolution when considering a targeted ROI. Recently, it has been shown that reconstruction of an ROI is possible with a reduced angular scan range ( ). By reducing the angular range required to reconstruct ROI images, the temporal resolution is improved and motion artifacts are reduced. Thus, we refer to this technique as spatially and temporally targeted reconstruction (STTaR).

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Materials and methods

Controlled Motion Phantom

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Figure 1, The digitized velocity profile prescribed to simulate vessel motion during the cardiac cycle. The units on the ordinate have been converted from voltage to velocity by the constant factor prescribed to the servo driver. The letters labeling different positions in the cardiac cycle will be used as reference for the subsequent reconstruction results.

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Porcine Model

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Figure 2, (a) The central image slice full field of view reconstruction to demonstrate the porcine coronary anatomy. As an example in this work, we demonstrate the concept of temporally targeted reconstruction spatially and temporally targeted reconstruction for the region of interest (ROI) given by the dashed line. (b) The right coronary artery and the sinoatrial nodal artery (SAN) are contained within this ROI.

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Scan Parameters

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Image Reconstruction

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Figure 3, The required angular scan range for the short scan and the temporally targeted scan are shown in (a) . For this sample, region of interest analytic reconstruction supported using the data highlighted by the dashed line, whereas for reconstruction of the entire field of view the angular range is given by the solid line. The time required to obtain the projection data is shown with respect to a hypothetical electrocardiogram signal and a schematic motion profile (b) . The wider (light) region corresponds to the full field of view reconstruction, whereas the central (dark) region corresponds to the temporal window for the temporally targeted reconstruction.

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Results

Controlled Motion Phantom

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Figure 4, A comparison between the spatially and temporally targeted reconstruction phantom reconstructions (top row) and the standard reconstructions (bottom row). Each image corresponds to a different gating window (a–e) in which the gating windows have been represented pictorially in Fig 1 a-e.

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Figure 5, The contour plots corresponding to the reconstructed images given in Fig 4 a–d. The top row results are contours from spatially and temporally targeted reconstruction and the bottom row are contours from the standard reconstruction results. The outermost contour corresponds to −419 Hounsfield units (HU) and each additional inner contour corresponds to an additional 16 HU.

Figure 6, The eccentricity values of fits to the contours at −419 Hounsfield units from reconstructions conducted with a gating window centered on the plotted positions in the simulated cycle. The standard reconstruction is represented by asterisk, whereas the spatially and temporally targeted reconstruction results are plotted with circles.

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Porcine Model

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Table 1

The Temporal Parameters of the Projection Data Used for the Temporally Targeted and the Standard Short Scan Reconstruction

Temporally Targeted Short Scan Angular range 180° 235° Cardiac window (% RR) 27 36 Acquisition time 200 ms 261 ms

Note that the cardiac window is heart-rate dependent (ie, if the heart rate was reduced this ratio of the data acquisition period to the time between R waves would be reduced).

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Coronary ROI

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Figure 7, A comparison of single axial slice images with and without temporal targeting. (a) The axial slice of the short scan with the right coronary artery region of interest (ROI) highlighted. (b) The standard spatially targeted ROI reconstruction. (c) The spatially and temporally targeted axial slice of the ROI. Display window (−1000 Hounsfield units to 1000 Hounsfield units).

Figure 8, Comparison of the maximum intensity projection images through the coronary region of interest (ROI) in the z (SI) direction: (a) through the full field of view (0 Hounsfield units [HU] to 900 HU), (b) through the coronary ROI (dashed line) without temporal targeting (−590 HU to 780 HU), and (c) through the coronary ROI with temporal targeting (−590 HU 780 HU). Additionally, in (a) the pulmonary ROI used is denoted by the solid line.

Figure 9, Maximum intensity projection images through the region of interest in the x (anteroposterior) direction. (a) Without temporal targeted reconstruction. (b) With temporal targeted reconstruction. Display window (–590 Hounsfield units to 780 Hounsfield units).

Figure 10, A comparison of the isosurface rendering results: (a) without temporal targeting and (b) with temporal targeting.

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Pulmonary Region of Interest

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Figure 11, Comparison maximum intensity projection images through the pulmonary region of interest: (a) without temporal targeting, and (b) with temporal targeting. Display window (−660 Hounsfield units 650 Hounsfield units).

![Figure 12, Minimum intensity projections through: the entire field of view −50 Hounsfield units [HU] to 650 HU), the pulmonary region of interest without temporal targeting (−920 HU to −400 HU) and the pulmonary ROI with temporal targeting (−920 HU to −400 HU).

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Discussion

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Acknowledgments

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Appendix

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Figure 13, The parameterization of the acquisition geometry for the equi-angular detector used in this study. Each collected data point is parameterized by three parameters: the view angle parameter ( t ), the fan angle (λ) and the height in the detector plane ( v ). The radius of the trajectory is given by R and the distance from the source to detector is given by D (distance measured along the incident x-ray direction for v = 0).

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