With the advancement of medical imaging, lowering the radiation dose and improving image quality have become focuses of CT innovation. Dual-energy CT (DECT) as an advanced CT technology is now widely used in clinical practice. It can help distinguish between different material compositions by evaluating differences in the attenuation of radiation of two different energies passing through them (1). Moreover, this principle is applied to different algorithms and postprocessing methods, including virtual monoenergetic imaging (VMI), effective atomic number and electron density map, material decomposition [including the virtual non-contrast (VNC) imaging, iodine map (IM), and lung ventilation map], and the material differentiation or labeling (including the urinary stone component analysis, gout imaging, bone removal, pulmonary vascular analysis, and material prominence) (2). Virtual monoenergetic (VM) images—which are reconstructed in the image-domain by the linear combination of two image series; one generated at a high energy level and another generated at a low energy level—can be used as conventional diagnostic images. The VM images show higher iodine contrast at a low energy level and fewer metal artifacts at a high energy level than single-energy CT (SECT) and linearly blended images (3); however, the low penetration ability of low-energy X-ray photons leads to the generation of large noise on VMI reconstructions, thus limiting VMI use. Recently, a reconstruction technique for the third-generation dual-source CT (DSCT)—i.e., noise-optimized virtual monoenergetic imaging (VMI+)—was developed. It uses a frequency-split method to obtain high-contrast image information from low-keV images and high spatial frequencies with the lowest noise information on the optimal-keV images, ultimately combining them to obtain a series of high-contrast and low-noise images (4). The application of the VMI+ technique has significantly resolved the problem of image noise—largely produced at low energy levels—and is a new postprocessing technique for radiological diagnosis. At present, the summary of VMI+ technology is mostly mentioned in the review of the research progress of DECT, and it is only briefly introduced. To acquire better image quality, assist radiologists in applying more appropriate energy levels for reconstruction, and provide more scientific research ideas for VMI+ technology, this review is the first to summarize the results of recent clinical studies for VMI+ technology. The similarity of reconstruction conditions under the same lesion type, such as tumors or vessels, is highlighted. Lastly, all optimal energy levels for VMI+ reconstruction recommended in these studies are summarized to guide clinical applications.
Development of VMI+ reconstructions
In 1973, Hounsfield reported that the estimation of atomic numbers of materials and differentiation of materials with different atomic numbers could be possible using two pictures acquired at different energy levels (5). Subsequently, several researchers performed a preliminary exploration of DECT application (6-11). Until the first DECT (Somatom Definition DS) was produced in 2006, the popularity of SECT was not affected. Unlike the single-source DECT, including rapid kVp switching CT, dual-layer spectral detector CT, and twin-beam CT, the DECT is a DSCT scanner with two independent X-ray tubes and two corresponding detectors; furthermore, the currents and voltages of both tubes are independently regulated (Figure 1). Therefore, radiations of different energies can be generated from the two tubes, and the obtained attenuation information of the material can be utilized to identify the compositions of materials. In addition, the use of both tubes can maximize spectral separation and reduce radiation dose (2,12,13).
Moreover, with both tubes arranged at almost right angles in a plane, DSCT can show improved time resolution compared to SECT. The most advanced DSCT scanner—the third-generation DSCT (Somatom Force)—shows a broader spectrum separation than DSCT scanners of preceding generations, showing the maximum spectrum separation at 70 kVp/150 Sn kVp (tube potential pair). Applying maximum spectrum separation can improve the imaging quality of small body parts, such as the extremities of adults and children, and parts of children’s bodies (2). In addition, the tin filter of the high-energy tube can widen the spectrum separation by blocking the filtration of low-energy photons, thus increasing the effective energy and reducing ineffective radiation simultaneously. Furthermore, the third-generation DSCT scanner widens the scanning field of the low-energy tube to avoid the loss of imaging information of patients with obesity, a concern with DSCT scanners of preceding generations (14).
Ideally, the high- and low-energy radiations from both X-ray tubes should be composed of monochromatic photons. In reality, the X-ray spectrum is polychromatic, which can produce image noise and beam-hardening or metal artifacts because of the difference in the absorption of photons by different materials; that is, materials with high attenuation coefficient absorb more low-energy than high-energy photons. Nevertheless, a series of monochromatic images can be simulated by linearly combining two series of images, each generated at one of the two energy levels of single- or dual-source DECT; this technology is called VMI (1,3,15). Therefore, VMI combines the features of images acquired both at high and low energy levels. At high energy, the VMI reconstruction has the advantages of reduced image noise and metal artifacts (3,14). Although the Compton scattering and the photoelectric effect are both involved in the interaction of X-rays with materials, the photoelectric effect is dominantly involved at low energy levels, and only a few heavy atoms show a strong photoelectric effect. Moreover, the average photon energy is close to the K-edge of iodine at a low energy level. Combining the two effects significantly increases the attenuation and improves the contrast of iodine at low energy (1,2,16). Yu et al. reported that the average attenuation of iodine was 70% higher at 60 keV (about 80 kVp) than at 77 keV (about 120 kVp) (16,17). However, during VMI, the low penetration capability of low-energy X-ray photons is associated with higher imaging noise on DECT compared to SECT scanning. Although the contrast of iodine is increased, it does not necessarily improve the contrast-to-noise ratio (CNR) (3,18).
To reduce image noise and improve the CNR of iodine, Grant et al. (4) improved the VMI technique. They used the frequency-split method to extract the desired frequency information from two sets of images acquired at low and optimal energy levels for VMI reconstructions and subsequently combined them to produce a new series of images of the same frequency showing the characteristics of high-contrast and low-noise. In this study, despite the presence of low-noise which still may affect the image quality at low energy levels for the VMI+ reconstructions, it was demonstrated that CNRs of lesion models were significantly higher than for VMI reconstructions, especially at 40 keV, which is lower than the previously reported energy levels (60–70 keV) associated with the highest CNR for VMI reconstructions. The VMI+ technique helps achieve high contrast with low doses of iodine and without obvious image noise at low energy levels and reduces the beam-hardening and photon starvation artifacts caused by high attenuation materials at high energy levels. It has been a better reconstruction method than has been VMI for radiological diagnosis.
Clinical studies and applications
The VMI+ technique is commonly applied to images of tumors and vessels containing contrast medium, and several studies have demonstrated that VMI+ reconstructions show better quality and more clinical values than VMI and linearly blended reconstructions.
In the studies on contrast-enhanced imaging of tumors, the highest signal-to-noise ratio (SNR) and CNR of most lesions were both observed when 40 keV VMI+ was used; these values were higher than those of VMI+ reconstructions of other energy levels, all VMI series, and linearly blended (M_0.6, M_0.3, and so on) images, and decreased gradually with an increase in energy levels. However, the energy levels required for the best subjective evaluation are approximately 50–60 keV. This was possibly due to the occurrence of the highest image noise at 40 keV and because of its gradual decrease with an increase in energy level. Therefore, although the SNR or CNR of the images is the highest at the lowest energy level, the subjective preference of observers is still affected by image noise, and relatively higher energy levels are preferred for the best subjective evaluation. In all studies, the optimal energy levels for VMI+ reconstructions recommended by researchers for different tumors were typically in the range of 50–60 keV. The optimal energy levels of reconstruction recommended for various cancers/tumors are as follows: 50 keV for cutaneous malignant melanomas and renal cell carcinomas (RCCs) in the corticomedullary-phase of enhancement (19,20); 55 keV for head and neck cancers, lung cancers, and hypervascular liver tumors (21-23); 60 keV for RCCs in the nephrogenic-phase of enhancement, gastrointestinal stromal tumors, and abdominal metastases, and hypo-attenuating liver metastases from colorectal cancers (19,24,25); low energy levels especially 40 and 50 keV for pancreatic adenocarcinomas (26); and 40 keV (a small number of studies) for malignant tumors in the head and neck region, metastatic spinal tumors, and early gastric cancer (27-30). Concerning head and neck malignancies, Albrecht et al. found that 55 keV reconstructions could yield the best subjective image quality (21); however, May et al. recommended 40 keV for optimal image quality (28). The source of this difference may be the subjective inconsistency among different evaluators. Therefore, the optimal energy level for the reconstruction of head and neck malignancy images may be determined through further studies.
Some studies reported interesting findings. Martin et al. (19) analyzed the reconstruction images of RCC during the corticomedullary and nephrogenic phases of enhancement and recommended energy levels for each of the phases. Shi et al. (29) found that the proportion of focal enhanced lesions of early gastric cancer in the portal phase displayed in VMI+ reconstructions was 16.1% higher than that in mixed 120 kV polyenergetic images (PEIs). Moreover, in VMI+ reconstructions, the superficial- and excavated-type lesions, which were not visible in the PEIs, could be found, and consequently, observers can stage early gastric cancer more correctly. It was believed that the application of 40 keV VMI+ technology plays a key role in selecting treatment methods because it is associated with a decrease in false staging rate. By simulating liver and hypervascular tumors containing iodine in vitro, Marin et al. (23) found that the tumor-liver CNR was the highest in VMI+ reconstruction regardless of the diameter of the liver and the surrounding fat-mimicking rings. Furthermore, in small, medium, and large models, the highest CNRs of VMI+ reconstructions were 64%, 55%, and 69% higher than those of VMI reconstructions, respectively. Therefore, it was considered that the use of the VMI+ technique could eliminate the need for considering the body size and simplification of the workflow of reconstructions. Although Lukas et al. (25) recommended 60 keV as the optimal energy level of reconstruction for hypo-attenuating liver metastases from colorectal cancer, they believed that the 40 keV VMI+ could provide additional information on lesions with poor contrast and unclear outline. Interestingly, May et al. (28) compared the application of third-generation dual-source DECT and single-source DECT to detect head and neck cancers. They found that dual-source DECT yielded a higher cancer contrast, clearer margin, and superior subjective image quality than single-source DECT.
When the most appropriate energy level is selected, VMI+ reconstructions of tumors during enhancement can show less noise, higher SNR and CNR, and better subjective image quality along with clearer lesions than VMI reconstructions and linearly blended images can (Figure 2); furthermore, selection of the most appropriate energy level may help reduce the impact of patient‘s body size on image quality and play a key role in the diagnosis and treatment.
VMI+ has often used for the reconstruction of CT angiography (CTA) images.
Cerebral and cervical CTA
Leithner et al. (31) reported that the VMI+ and VMI reconstruction techniques at an optimal energy level (40 keV and 60 keV, respectively) and the conventional linearly blended (M_0.6) reconstruction techniques did not show differences in the subjective detection and grading of stenosis at the bifurcation of the common carotid arteries (CCA) and the siphon of the internal carotid arteries (ICA). However, researchers believed that additional VMI+ reconstructions could help improve the quality of unclear head and neck CTA images because all vessels show the highest CNRs on these reconstructions. Riffel et al. (32) also reported that ultra-low keV VMI+ reconstruction could improve the basilar arteries and ICA image quality. Concerning the standard mixed images (similar to the acquisition at 120 kVp), Zhao et al. (33) found that the attenuations of cerebral and cervical arteries in the 40 keV VMI+ reconstructions of the low-concentration contrast-medium group were all significantly higher than those in the high-concentration contrast-medium group; however, the CNRs were similar between the groups. Therefore, it was proposed that a low concentration of contrast medium can be selected before the application of VMI+ technology for the reconstruction of cerebral or cervical CTA images.
Coronary blood vessel
Arendt et al. (34) found that images of the coronary arteries showed the best subjective and objective quality, including subjective vascular contrast and contour of calcified plaques, at 40 keV. Symons et al. (35) analyzed both calcified and non-calcified coronary plaques and found that the CNR of coronary plaques can be improved at low energy levels (40–70 keV); however, they indicated that accurate measurement of the absolute volume of coronary plaques might be difficult at 40 keV. Therefore, re-calibration software and observers with abundant diagnostic experience are required when using 40 keV reconstruction. In coronary stent imaging, the presence of beam-hardening artifacts and partial volume effects can cause the underestimation of stent lumen diameter by observers (36). Mangold et al. (37) analyzed coronary stents, but the imaging was in vitro. Their findings were as follows: the highest CNR of in-stent iodine was observed at 120 keV, while the maximum in-stent diameter could be measured at 130 keV, especially for a diameter of ≤3 mm. However, coronary CTA (CCTA) was not generally recommended for evaluating coronary stents in the guidelines (38), and the application of the above finding could expand the usefulness of CCTA for the evaluation of stents, including small stents. Moreover, their study found that the radiation dose of DECT was 49% lower than that of 120 kV SECT. In addition, De Santis et al. (39) reported that a combination of low iodine delivery rate (0.4–1.0 gI/s) and 40–70 keV VMI+ reconstructions could help achieve diagnostic attenuation (300 HU) of coronary blood vessels. The possibility of applying low radiation dose using DECT and advantages of using low-concentration contrast agent with low-energy VMI+ reconstruction for obtaining diagnostic images facilitate the wide usage of a combination of DECT and VMI+ for evaluating coronary arteries. In addition to coronary arteries, coronary veins often play an important role in treating heart disease. However, Kim et al. (40) found that the objective and subjective image quality of the conventional linearly blended (M_0.6) reconstruction was better than that of VMI+ reconstruction for coronary veins.
As indicated in the preceding section, Beeres et al. (41) reported that the SNR and CNR of aorta CTA in VMI+ reconstructions were higher than those in VMI reconstructions, especially at low energy levels. In addition, Martin et al. (42) analyzed the left ventricular blood pool, infrarenal aorta, iliac and femoral arteries and obtained similar results. Nevertheless, by combining the subjective evaluation of image quality and ability to obtain relevant measurements of the transcatheter aortic valve replacement (TAVR), the researchers recommended 50–60 keV VMI+ as the reconstruction technique for the aorta CTA before TAVR.
Concerning pulmonary angiography, Meier et al. observed the highest SNR and CNR of images and the highest subjective image quality score at 40 keV (43); these findings were in contrast with those reported by Martin et al. concerning the aorta (42). Meyer et al. (44) analyzed pulmonary angiography images of patients with suspected pulmonary embolism (PE); they observed the highest CNR of main pulmonary arteries at 50 keV and peripheral pulmonary arteries at 40 keV extremely high sensitivity, specificity, and accuracy. In addition, 40–50 keV is found to be ideal for image reconstruction when low-dose iodine was used to reduce the risk of renal damage. In addition, PE could be incidentally found when evaluating tumors in portal-venous phase CT (CTpv) images. According to a study by Weiss et al. (45), low-keV reconstruction can significantly increase the contrast of pulmonary arteries and improve the visibility of occasional pulmonary emboli in CTpv. Their subsequent study, they (46) found volumes of small emboli being occasionally over-amplified at 40 keV; this could limit the detection of actual-sized emboli, not being fully compensated for through window-setting adjustment. However, this study was based on reconstruction at only two energy levels, 40 and 55 keV; therefore, 55 keV reconstruction, which yields better results, is recommended. After selecting the appropriate reconstruction level, D’Angelo et al. (47) considered that image quality degradation owing to improper window settings might affect inexperienced observers’ ability to interpret images. They recommended 40 keV as the optimal energy level and 1,070/380 as the optimization parameters of window settings for pulmonary angiography.
Because bronchial arteries are close to the esophagus in the mediastinum, they may be injured during surgery for esophageal cancer, which may cause bleeding. Therefore, Nomura et al. (48) evaluated the image quality of bronchial arteries on VMI, VMI+, and composite (about 105 kVp) reconstructions. They found that 40–50 keV VMI may be more suitable for visualizing bronchial arteries and surrounding tissue. The results were considered due to the subjective evaluation affected by the higher CT attenuation on VMI than VMI+ at low voltages. It is suggested that VMI+ may be poor in the display of fine vessels.
Schabel et al. (49) found that the SNR, CNR, and visibility were the highest at 40 keV on VMI+ reconstructions of hepatic veins and that these values were higher than those of VMI reconstructions and conventional linearly blended (M_0.6) images. Furthermore, Albrecht et al. (50) found that low-keV VMI+ reconstructions show high image quality for hepatic, splenic, superior mesenteric, and renal arteries. In their subsequent study, they (51) increased the number of target arteries of the thorax and abdomen. Their study suggested 70 keV as the optimal energy level for VMI+ reconstruction of thoracoabdominal CTA images and indicated that additional 40 keV or 50 keV VMI+ reconstructions may be necessary when poor vascular contrast or requirements for clearer small vessel images are noted. Martin et al. (52) found that the 40 keV VMI+ reconstruction improved the diagnostic accuracy of active arterial abdominal hemorrhage and recommended 40 keV as the energy level for image reconstruction when abdominal or pelvic vascular hemorrhage is suspected. In addition, Caruso et al. (53) recommended 40 keV as the energy level of reconstruction for obtaining the best CNR and 1,350/430 as the window width and level for obtaining the best quality images of the abdominal aorta and bilateral common iliac and femoral arteries. The window settings were wider and higher than those recommended by D’Angelo et al. (47) for pulmonary angiography.
Lower extremity CTA
Wichmann et al. (54) analyzed the lower extremity arteries and found that objective image quality, including intravascular contrast attenuation and CNR, was the highest for 40 keV and 50 keV VMI+; furthermore, they found that the sensitivity of VMI+ reconstructions for the detection of vascular stenosis was >50% higher than that of VMI reconstructions and conventional linearly blended (M_0.6) images. However, their study recommended 50 keV VMI+ for reconstruction due to the higher image noise level at 40 keV.
Endoleaks after endovascular aneurysm repair (EVAR)
Endoleak, a common complication occurring after EVAR, can increase the rupture of an enlarged aneurysm, with early detection associated with an improved prognosis (55). Martin et al. (56) recommended 40 keV as the best energy level for image reconstruction when concurrent endoleaks are suspected after EVAR surgery.
Venous thromboembolism, including PE and deep vein thrombosis (DET), gradually increases with the progression of age (57), with CT venography being the preferred diagnostic method. However, because the attenuation of thrombotic substances changes with age, it is difficult to detect thrombosis when its attenuation is close to that of the contrast medium in vessels (58-60). VMI+ reconstruction can help distinguish thrombosis from iodine by enhancing the contrast of the latter. Through in vitro study, Bongers et al. (61) reported that high contrast and CNR of clots in blood samples showing high and intermediate attenuations were observed in 40 keV VMI+ reconstructions, and those in blood samples showing low attenuations were observed in 190 keV VMI+ reconstructions. A low energy level can increase iodine contrast, while a high energy level can reduce iodine contrast; therefore, the contrast difference between blood and clots can be achieved.
As in the case of tumors, SNR or CNR of vessels with iodine contrast was the highest at 40 keV in the VMI+ reconstructions. Nevertheless, based on the subjective evaluation, the recommended energy levels of enhanced vessel reconstruction—which were mostly in the range of 40–50 keV—were slightly lower than those for tumors. (The reconstruction images of cervical CTA are shown in Figure 3). This may be due to two reasons: a higher concentration of contrast medium in vessels than tumors and high absorption of low-energy X-rays at low energy levels, making the vascular attenuation of thrombosis more obvious than tumors. Nonetheless, at 40 keV, the absolute volume of coronary plaques or PE could vary; therefore, either an appropriate correction or using other energy levels are necessary. Moreover, the contrast difference between blood and thrombosis could be changed by adjusting the energy level to facilitate the appropriate visualization of thrombosis. In addition to the intravascular conditions, a low-keV condition of VMI+ reconstruction could facilitate the visualization of vascular bleeding. Furthermore, studies confirmed that low concentrations of contrast medium or low iodine injection rates could also maintain diagnostic requirements of low-keV VMI+ reconstructions. Except for the applications of VMI+ reconstructions at low energy levels, those at the high energy level were proven to be more valuable for the imaging of small coronary stents. After selecting the appropriate energy level for reconstruction, several studies recommend selecting appropriate window width and window level for image observation. A previous study on coronary arteries showed that the radiation dose used for DECT was lower than that for SECT.
Through quantitative analysis of image quality, including grey and white matter SNR, grey-white matter CNR, and posterior fossa artifact index, as well as through qualitative analysis of overall subjective image quality, supratentorial image noise, grey matter, and white matter differentiation, and posterior fossa artifacts, Park et al. (62) found that except for the least posterior fossa artifacts or the lowest artifact index observed at 70 keV, the other objective and subjective evaluations were optimal at 60 keV.
Suitable tube potential settings for different abdominal sizes
After inserting cylinders in torso-shaped water phantoms of different diameters in a vitro study, Michalak et al. (63) found that there was no increase in image noise due to iodine at 40 keV using a tube potential pair of 70 kVp/150 Sn kVp in phantoms with a diameter of ≤35 cm. Moreover, 40 keV can still be used for reconstructing iodine imaging, but the tube potential pair of 80 kVp/150 Sn kVp should be set, and when the diameter is 35–40 cm, 50 keV should be used if artifacts are generated. Furthermore, for a 40–45 cm diameter, the corresponding tube potential should be set at 90 kVp/150 Sn kVp, and the energy level should be set at no less than 60 keV. In addition, for a diameter of >45 cm, the corresponding tube potential, and energy level should be set at 90 kVp/150 Sn kVp and no less than 70 keV, respectively.
Hyper- and hypo-attenuating liver lesions
Husarik et al. (64) analyzed the hyper- and hypo-attenuating liver lesions with different concentrations of iodine using phantoms of four different sizes and reported that 40 keV and 190 keV should be the energy levels of reconstructions for hyper-attenuating and hypo-attenuating lesions, respectively; however, they recommended that SECT be selected for imaging lesions in a very obese patient. Interestingly, Caruso et al. (65) analyzed the hypo-enhancing lesions with a diameter of >1 cm in the portal phase and found that although subjective image quality and preference were superior at 50 keV, the CNR of lesions was the highest at 40 keV, which is contrary to the results reported by Husarik et al. (64), potentially because their liver models (64) contained no iodine. In fact, the iodine content of liver parenchyma is significantly higher than that of the hypo-attenuating lesions in enhanced CT scans; with a decrease in energy level, the degree of increase in liver attenuation is always higher than that of the hypo-attenuating lesions, resulting in the continuous increase of CNR. Furthermore, De Cecco et al. (66) found that 50 keV VMI+ provided superior image quality and diagnostic accuracy for the detection of hypervascular liver lesions, especially those with a diameter of <1 cm, but the sensitivity and specificity for the detection of lesions with a diameter of ≥1 cm were not significantly higher than those of VMI and linearly blended (M_0.6) reconstructions. Sample DECT reconstruction images of hypo- and hyper-attenuating liver lesions are shown in Figure 4.
Optimum window settings for liver imaging
De Cecco et al. (67) found that the application of optimal window settings yielded high diagnostic accuracy. They selected 50 keV VMI+, 70 keV VMI, and linearly blended (about 120 kVp) reconstruction techniques based on prior studies to analyze images of the hepatic arterial and portal phases; they found that the attenuation was the highest at 50 keV VMI+ and that both the optimal window width and level were 429.3±44.5 and 129.4±9.7 HU, respectively, in the arterial phase and 376.1±14.6 HU and 146.6±7.1 HU, respectively, in the portal phase. In addition, for detecting the lesions using 50 keV VMI+, sensitivity was 100% and 96% in the arterial and portal phase, respectively.
Sugrue et al. (68) examined pancreatic laceration and found the highest CNR and injury-to-normal parenchyma contrast and improved injury conspicuity and diagnostic confidence in 40 keV VMI+ reconstructions. Timely and accurate identification of pancreatic laceration is very important for the treatment and prognosis of patients. Coincidentally, a study using a second-generation DSCT scan followed by VMI+ reconstruction for images of hepatic and splenic lacerations found that the highest CNR also appeared at 40 keV (69).
Lumbar internal fixation
The effect of using the VMI+ technique on reducing metal artifacts generated by lumbar internal fixation was analyzed for the first time by Zeng et al. (70), who found that the 130 keV VMI+ reconstruction for the region surrounding internal fixation could improve the clarity of the metal-bone interface and decrease the number of artifacts and facilitate superior diagnostic assessment of the surrounding soft tissue, abdominal aorta, and inferior vena cava. Furthermore, 120 keV VMI+ reconstruction was reportedly appropriate for spinal canal imaging.
In addition to enhanced vessels and tumors, VMI+ has been used in the imaging of children’s heads, other liver lesions, pancreatic lacerations, and in reducing metal artifacts. Furthermore, choosing both suitable window settings and a combination of tube voltage according to different abdominal sizes will also improve diagnostic accuracy. The above results, summarized in Table 1, show the optimal energy levels for different lesions to guide clinical application.
Current limitations and future challenges
The VMI+ technique has been extensively proven to show significantly higher contrast of lesions or vessels containing iodine, lower image noise, and higher image quality than have been VMI and linearly blended reconstructions and SECT images. Moreover, on the premise of using the VMI+ reconstruction, the contrast medium concentrations can be decreased to reduce the incidence of contrast-induced nephropathy. However, the VMI+ images are still affected by noise at low energy levels, especially while imaging tumor lesions with relatively low iodine concentrations. Although the CNR of both tumors and vessels is the highest at 40 keV, the subjective selection of best quality images is associated with the energy level of 50–60 keV. In addition, the VMI+ reconstructions need to be generated on the postprocessing workstation, which is labor-intensive and time-consuming, thus being easily overlooked. Future research should mainly focus on the problem of noise impact on image observation at low energy levels. Because the VMI+ technology involves the reconstruction of two sets of images generated using the high and low energy levels of DECT, the primary breakthrough in reducing the noise of VMI+ images is to reduce the possibility of noise generation by DECT. Because of the unique orthogonal geometry of the two tube-detectors on dual-source DECT, the scattered radiations of the tubes easily affect each other, thus reducing spectral separation and increasing image noise; therefore, a better scatter correction algorithm is needed (1,2,12). In addition, technicians should know the optimal energy level of reconstruction either for the target organs or lesions to improve postprocessing efficiency. Because the VMI+ technology on DECT is a postprocessing technology of the imaging domain, unlike the image processing technology of the projection domain, the VMI+ images can be retrospectively processed after scanning. Therefore, in addition to enhancing tumors, vessels, and organs (brain and liver), other lesions or organs can also be studied. For example, the strong photoelectric effect principle of heavy atoms at low energy could be used to distinguish gallbladder stones containing a small amount of calcium salt from polyps without calcium salt. In solving image quality problems, the image quality can also be further optimized by changing the tube voltage and combining the optimal energy level of VMI+ reconstruction. Additional studies will provide more favorable information regarding imaging diagnosis.
The use of DSCT has been steadily increasing. As the postprocessing technology of the third generation DSCT, VMI+ has been widely recognized for reducing image noise, improving image quality, and increasing iodine contrast. Knowing the best energy levels for imaging different lesions is the basis—and even the key—of the VMI+ technique. The reconstructed images, combined with the optimal window settings, provide more accurate information regarding image diagnosis. In addition, the application of VMI+ allows the use of a low concentration of contrast medium and reduces the incidence risk of contrast-induced nephropathy. As a new postprocessing technique, the VMI+ should be explored for applications beyond the reconstructions of vascular or tumor images in the future.
Funding: This study was supported by National Natural Science Foundation of China (No. 81971598, 82071456), Shanghai Shuguang Program (No. 19SG06), Shanghai Municipal Commission of Science and Technology (No. 19411951200). What is more, thanks for the images of renal carcinoma (Figure 2) and liver lesions (Figure 4) with the patients’ consent provided by the Department of Radiology, Second Xiangya Hospital, Central South University.
Conflicts of Interest: All authors have completed the ICMJE uniform disclosure form (available at https://dx.doi.org/10.21037/qims-20-1196). The authors have no conflicts of interest to declare.
Ethical Statement: The authors are accountable for all aspects of the work in ensuring that questions related to the accuracy or integrity of any part of the work are appropriately investigated and resolved. The informed consent was obtained from the patients for the publication of this manuscript and any accompanying images.
Open Access Statement: This is an Open Access article distributed in accordance with the Creative Commons Attribution-NonCommercial-NoDerivs 4.0 International License (CC BY-NC-ND 4.0), which permits the non-commercial replication and distribution of the article with the strict proviso that no changes or edits are made and the original work is properly cited (including links to both the formal publication through the relevant DOI and the license). See: https://creativecommons.org/licenses/by-nc-nd/4.0/.
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