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Multisection (Multidetector) CT — Detailed Overview
Multisection CT is synonymous with multidetector CT (MDCT) — a CT architecture in which multiple parallel rows of detectors simultaneously acquire several cross-sectional images per gantry rotation, replacing the single-row detectors of conventional and early spiral CT.
1. Historical Development
| Era | Technology | Key Limitation |
|---|
| Pre-1990 | Sequential (step-and-shoot) single-slice CT | Inter-slice gaps; patient must hold breath for each slice |
| ~1990 | Spiral (helical) single-slice CT | Volumetric acquisition possible but slow; thick slices |
| 1998 | 4-slice MDCT introduced by multiple manufacturers | Began the MDCT era |
| 2000s | 16- → 64-slice MDCT | Near-isotropic voxels; single breath-hold chest |
| Present | 128-, 256-, 320-detector-row systems; dual-source | Temporal resolution <100 ms; whole-organ coverage in one rotation |
The introduction of 64-channel MDCT was a watershed: at this configuration, the incident x-ray beam width remains constant regardless of collimation setting, so geometric efficiency is high with little dose penalty.
"In 1998 several CT manufacturers introduced multidetector systems, which provided considerable improvement in acquisition speed, coverage, and temporal and spatial resolution."
— Grainger & Allison's Diagnostic Radiology
2. Core Technical Principles
2.1 Detector Array and Simultaneous Section Acquisition
- A multirow detector array replaces the single detector row. Each row independently acquires a slice, so N rows → N simultaneous slices per rotation.
- Pitch = table speed ÷ gantry rotation speed. A higher pitch increases z-axis coverage per unit time but can reduce signal-to-noise ratio.
- Section collimation (beam width per detector element) and reconstruction thickness are now independently controllable — the raw data can be retrospectively reconstructed at any thickness from the archived dataset.
2.2 Isotropic Voxels
A defining feature of modern MDCT is true isotropic imaging: each voxel has equal dimensions in x, y, and z axes. This enables:
- Reformation in any arbitrary plane (axial, coronal, sagittal, oblique) with no loss of resolution
- Accurate 3D post-processing and volumetric measurements
- Computer-aided detection (CAD) of pulmonary nodules and emboli
2.3 Gantry Rotation Speed
Current systems rotate at as low as 0.33 s per rotation. Combined with multi-row acquisition, this provides:
- Single breath-hold chest coverage — feasible even in tachypnoeic patients
- Reduced motion artefact
- In paediatrics, reduced need for sedation
2.4 Novel Technologies for Further Improvement
| Technology | Mechanism | Benefit |
|---|
| Dual-source CT | Two x-ray tubes at 90° to each other | Temporal resolution ~75 ms; dual-energy capability |
| Flying focal spot | Alternates focal spot position rapidly | Converts 128-row → virtual 256-row array; improved z-resolution |
| Wide-area detector (320-row) | 16 cm z-axis coverage per rotation | Entire heart or organ imaged in a single rotation |
3. Dose Profile and Geometric Efficiency
Fig. — Geometry and Dose Profile for Spiral, 4-, 16-, and 64-Slice CT. The umbral region (U, solid blue) contributes to image reconstruction. The penumbral region (P, shaded) is discarded as "wasted" dose. As section count increases from 4 to 64, the penumbral fraction progressively diminishes.
The collimated dose profile is trapezoidal in the z-direction:
- Umbral (plateau) region: the entire focal spot illuminates the detector → uniform signal → used for reconstruction
- Penumbral regions (beam edges): partial focal spot illumination → non-uniform signal → discarded by post-patient collimator
This discarded penumbral dose is the primary reason MDCT carries a higher radiation burden than single-slice CT. The relative penumbral fraction:
- Decreases as section width increases (wider beam → penumbra is a smaller fraction)
- Decreases as the number of simultaneous sections increases (4→16 MDCT: significant waste; 64-MDCT: penumbra is minimal)
A secondary source of geometric inefficiency is inter-detector gaps — photons incident on gaps between detector elements are lost. The number of gaps increases with detector row count.
4. Image Reconstruction
4.1 Reconstruction Kernels (Algorithms/Filters)
| Algorithm type | Effect | Clinical use |
|---|
| Low spatial frequency (smooth) | Reduces noise; lower spatial resolution | Soft tissue, vascular structures, mediastinum |
| High spatial frequency (sharp/lung) | Enhances fine detail; increases noise | Lung parenchyma, airways, bone, HRCT |
Thin-section raw data can be retrospectively reconstructed with sharp kernels even from a standard protocol — making dedicated HRCT acquisitions no longer mandatory with MDCT.
4.2 Section Thickness Flexibility
From a single raw acquisition, MDCT allows reconstruction of:
- 0.6–1.25 mm thin sections — high spatial resolution, 3D post-processing, pulmonary nodule characterisation, interstitial lung disease, pulmonary embolism
- 2.5–5 mm thick sections — better contrast resolution, faster review; adequate for mediastinal masses, lung cancer staging
4.3 Iterative Reconstruction
New model-based iterative reconstruction algorithms decouple tube current from image noise, enabling marked dose reduction while preserving image quality. Particularly validated for cardiac CT.
5. Window Settings
Because MDCT generates a continuous Hounsfield unit scale, window settings must be tailored:
- Window centre ≈ midpoint between the density of the structure of interest and surrounding tissue
- Wide windows (e.g., −600/1600 HU) → lung parenchyma
- Narrow windows (e.g., 40/400 HU) → mediastinum, soft tissue
6. Postprocessing Techniques
MDCT's isotropic volumetric data enables the following 2D/3D techniques:
| Technique | Method | Key Application |
|---|
| MPR / CMPR (multiplanar/curved MPR) | 1-voxel-thick tomographic sections in any plane | Pulmonary emboli, airways evaluation |
| MIP (maximum intensity projection) | Only highest-attenuation voxels rendered | Vascular imaging, micronodular disease distribution |
| MinIP (minimum intensity projection) | Only lowest-attenuation voxels rendered | Emphysema, air trapping (augments air-trapping conspicuity) |
| Shaded surface display (SSD) | Threshold-based surface rendering | Large airway/vessel overview |
| Volume rendering (VR) | All voxels, opacity assigned by HU | Surgical planning, complex anatomy |
| Virtual bronchoscopy | Fly-through of airway lumen | Airway stenosis evaluation |
7. Contrast Medium Protocols
MDCT's faster acquisition requires redesigned contrast injection protocols:
- Faster peak enhancement → need higher iodine delivery rate (faster injection rate + higher iodine concentration)
- Typical 64-slice thoracic MDCT: 60–120 mL of 320–400 mg/mL iodine at 3.5–5 mL/s, followed by 20–40 mL saline chaser
- Biphasic (dual-bolus) protocols are standard: the saline chaser dilutes contrast density in brachiocephalic veins, eliminating streak/beam-hardening artefacts and providing more homogeneous enhancement
- Triphasic protocols (contrast → contrast:saline mix → saline) used for "triple rule-out" CT (simultaneous coronary, pulmonary, and aortic evaluation)
- Bolus tracking / automated triggering (rather than fixed delays) is preferred given the narrow acquisition windows
8. Cardiac MDCT (ECG Gating)
MDCT enables non-invasive coronary imaging via ECG synchronisation:
| Mode | Mechanism | Radiation dose | Use |
|---|
| Prospective gating | Scan triggered at fixed interval after R-wave; pauses between beats | Low (<1 mSv achievable) | Calcium scoring, coronary CTA at stable HR |
| Retrospective gating | Continuous acquisition throughout cardiac cycle; retrospective phase selection (0–90% R-R at 10% intervals) | High (~10× prospective) | Functional assessment (ejection fraction, wall motion) |
Optimal image quality requires:
- Heart rate ≤60 bpm (β-blockade preparation) — ensures R-R interval >1000 ms
- End-diastole selected for final reconstruction (period of least cardiac motion)
Dual-source and 320-detector systems have further reduced effective temporal resolution to <100 ms, enabling diagnostic-quality coronary imaging even at higher heart rates.
9. Dual-Energy CT (DECT)
Current MDCT platforms offer DECT capability via:
- Dual-source: two tubes operating simultaneously at different kVp (e.g., 80 and 140 kVp)
- Rapid kVp switching: single tube alternates between energies
- Dual-layer ("sandwich") detector: separate detector layers absorb different energy spectra
Clinical value: material-specific image sets from a single acquisition:
- Virtual unenhanced images — eliminates need for a separate pre-contrast scan → dose reduction
- Iodine maps → pulmonary blood volume maps (perfusion assessment in pulmonary embolism, comparable to scintigraphy)
- Nodule characterisation by differential iodine uptake
10. Dose Reduction Strategies
(Grainger & Allison's Diagnostic Radiology, Table 1.3)
| Category | Strategies |
|---|
| Tube current | AEC; weight/size-based modulation; ECG gating; low-dose protocols (40–70 mAs for chest) |
| Tube voltage | Reduced kVp (especially in thin patients or paediatrics) |
| Beam shaping | Bowtie filters |
| Acquisition | Higher pitch; shorter z-coverage; faster rotation; wider collimation |
| Reconstruction | Iterative reconstruction (especially model-based); high-sensitivity detectors |
| Protocol | Patient shielding; restrict FOV to area of interest |
A 50% reduction in tube current halves effective dose, provided acceptable image noise is maintained.
Summary
Multisection (multidetector) CT is the foundation of modern cross-sectional imaging. Its principal advances over single-slice CT are:
- Simultaneous multi-section acquisition → dramatically reduced scan time
- Isotropic voxels → unrestricted multiplanar and 3D reformatting
- Flexible retrospective reconstruction → single acquisition, multiple slice thicknesses and kernels
- ECG gating → non-invasive cardiac and coronary imaging
- Dual-energy capability → material decomposition, virtual unenhanced, perfusion maps
The ongoing trade-off between image quality, temporal resolution, and radiation dose drives iterative hardware and software innovation — from flying focal spots and 320-row detectors to AI-assisted iterative reconstruction.
Sources: Grainger & Allison's Diagnostic Radiology (7e); Fuster and Hurst's The Heart (15e)