Short Communication - Imaging in Medicine (2018) Volume 10, Issue 3

Clinical applications of diffusion-weighted magnetic resonance imaging

Nguyen Minh Duc1,2*, Huynh Quang Huy1, Mai Tan Lien Bang2, Luc Minh Truong3, Vo Hoang Tri3, Bui Nguyen Canh3, Pham Ngoc Hoa1, Pham Minh Thong4

1Department of Radiology, Pham Ngoc Thach University of Medicine, Ho Chi Minh city, Vietnam

2Department of Radiology, Children’s hospital 2, Ho Chi Minh city, Vietnam

3Department of Radiology, Siemens Healthcare Vietnam, Ho Chi Minh city, Vietnam

4Department of Radiology, Hanoi medical university, Ha Noi, Vietnam

*Corresponding Author:
Nguyen Minh Duc
Department of Radiology Pham Ngoc
Thach University of Medicine Ho Chi Minh city
[email protected]


Based on Brownian motion, diffusion statement of proton hydro inside body is one of the most important variables affected on the diagnosis, treatment planning, and disease response to treatment. There are some different kinds of diffusion-weighted magnetic resonance imaging types such as diffusion-weighted imaging, diffusion tensor imaging, diffusion kurtosis imaging, intravoxel incoherent motion imaging, zoom diffusion imaging, and diffusion spectrum imaging. In this short communication, we aimed to introduce clinical applications of these diffusion-weighted magnetic resonance imaging types.


diffusion-weighted imaging ▪ magnetic resonance imaging ▪ clinical applications


Based on the Brownian motion principle [1,2] (Figure 1), diffusion statement, one of the most essential features of tissue, can be assessed non-ionizingly by means of magnetic resonance imaging (MRI). Currently, we have some demarcating diffusion imaging sequences to achieve diffusion-related variables such as diffusion-weighted imaging (DWI), diffusion tensor imaging (DTI), diffusion kurtosis imaging (DKI), intravoxel incoherent motion imaging (IVIM), zoom diffusion-weighted imaging (Z-DWI), and diffusion spectrum imaging (DSI) [3-12]. In this short communication, we aimed to introduce clinical applications of these diffusion-weighted MRI types.


Figure 1. Brownian motion.


DWI is the most popular form of diffusion MRI based on measuring the Brownian motion of water molecules within tissue voxel. In contrast to free diffusion motion of water in a bottle, diffusion inside one tissue is basically limited by cell membrane margins. The overall diffusion feature of a single voxel represents the combination of water diffusion in different compartments: diffusion within the intracellular space fluid (the cytoplasm and organelles); diffusion within extracellular space fluid (interstitial fluid, intravascular, lymphatic and various biological cavities) and diffusion between intra and extracellular spaces. Therefore, increasing the intensity of cellular tissues, strange substances, heavy particles inside those spaces will result in the limitation of diffusion coefficients [3-6].

Apparent diffusion coefficient (ADC) is a measure of the magnitude of water molecule diffusion within tissue. This assessment can be investigated utilizing dissimilar b-values through modifying gradient amplitude commonly b-values of 0 and 1000 s/mm2. ADC is obtained automatically by the software and then manifested like a parametric map that demonstrates the level of different tissues’ molecule water diffusion. Tissue ADC is introduced in units of mm2/s [3-6].DWI is specifically effective in characterizing tumor (Figure 2) and assessing brain infarction (Figure 3).


Figure 2. Image findings show invasive ductal carcinoma in the left breast (white arrow) with restricted diffusion on DWI (left section) and ADC map (right section) in comparison with reference.


Figure 3. Image findings show an infarction lesion of pons (white arrow) with restricted diffusion on DWI (left section) and color ADC map (right section) in comparison with reference.


Denis Le Bihan first used the term IVIM to demonstrate the microscopic translational movement of water molecules within a voxel [7,8]. In IVIM model, biological tissue consists of 2 apparent compartments: tissues water molecule diffusion considered as true diffusion and microcirculation of blood in the capillary network regarded as perfusion. Hence, Denis Le Bihan introduced that water streaming in capillary intravoxel level imitate a haphazard movement considered as pseudo-diffusion. Likewise to water molecule’s diffusion, the effect of pseudo-diffusion on the signal alleviation Nonetheless, the level of signal alleviation caused by pseudo-diffusion is generally an order of magnitude larger than tissue’s molecular diffusion, therefore its respective addition to the DWI signal becomes important only at a very low b-value generally under b-value of 200 s/mm2, conceding diffusion and perfusion effects to be demarcated. In practice, IVIM was utilized to attain 4 parameters: F (perfusion fraction); D* (pseudodiffusion); D (real-diffusion), and ADC (Figure 4). IVIM is very useful in assessing tumor features and tumor responses to therapy [7-12].


Figure 4. IVIM images show hepatocellular carcinoma (white arrow): (A) D-slow image prior to TACE; (B) D-fast image prior to TACE; (C) f-image prior to TACE; (D) D-slow image after TACE; (E) D-fast image after TACE; (F) f-image after TACE. Figure courtesy of Lin et al. [12].


Conventional DWI when assessing sophisticated structure generally produces not enough spatial resolution. In addition, conventional DWI is very sensitive to body movement and paramagnetic structure led to the geometrical distortion. So as to overcome this problematic condition, Z-DWI is a novel form of conventional DWI combined with high resolution even small field of view which can help clinician to investigate the lesions of sophisticated structure such as hippocampus, spinal cord or early stage of astrocytoma occurred in a small gyrus (Figure 5). Z-DWI is clinically indicated for epilepsy, characterization of hippocampus lesion, spinal cord lesion and assessment of brain tumor [13-15].


Figure 5. Z-DWI image shows the asymmetrical gyrus of left hippocampus (white arrow) in comparison with normal gyrus of right hippocampus.


DTI is an expansion of DWI that permits data contouring depended on tissue tract specifically white-matter extent direction. The axon architecture in parallel bundles with outside myelin armor eases the water molecule’s diffusion along the same main direction (Figure 6) [16-19]. Fiber-tracking, also known as tractography, bases on the DTI to track fibers along their whole direction. Beginning from a region of interest, generally defined manually, the fiber-tracking algorithm looks forward to adjacent voxels whose main diffusion direction is in the continuity of the previous one. The most common tracked fiber bundle is the corticospinal tract. In addition, DTI also produces two parameters: ADC and fractional anisotropy (FA) also known as diffusion anisotropy (Figure 7). In practice, the application of DTI is for brain such as tract-specific localization of white matter lesions, localization of tumors in relation to the white matter tracts, localization of the main white matter tracts for neurosurgical planning and assessment of the white matter maturation; nevertheless, today DTI can be applied to some other organs such as kidney, uterus, muscle and heart[16-19].


Figure 6. DTI images show white-matter bundles: (A) Axial plane, (B) Coronal plane, (C) Sagittal plane.


Figure 7. DTI image shows the tractography of cortical-spinal bundles, FA and ADC.


DKI is an advanced method which is an extension of DTI by measuring the skewed distribution, also known as kurtosis of water diffusion relied upon a distribution function capability. The kurtosis is a common, dimensionless statistic for quantifying nongaussian motion based on the dissimilarity from a normal distribution and abnormal distribution [20,21]. It generates a high order diffusion of water distribution and analysis. Furthermore, DKI can quantify the diffusion restriction more accuracy than DTI (Figure 8). DKI protocols are different from DTI-protocols in utilizing at least 3 b-values in comparison with 2 b-values for DTI and at least 30 independent diffusion gradient directions in comparison with 6 for DTI. DTI protocols for brain need 0, 1000, 2000 s/mm2 b-values with diffusion extensions. Post-processing image necessitates the use of specialized algorithms. DKI is commonly used for assessing stroke and brain tumor. With the organs outside the brain, there are some previous studies manifested the efficacy of DKI [20,21].


Figure 8. DTI (left section) and DKI (right section) tractographies manifested on a normal brain are provided as an example to demonstrate the dissimilarity in sensitivity for the detection of tiny crossing fibers between DTI and DKI fiber-tracking techniques. Figure courtesy of Paydar et al. [18].


The DTI model revealed that there is an exclusive intravoxel direction of each fiber symbolized by the main eigenvector. However, it is concluded that in case of crossing fiber commonly representing the areas in which the fibers’ direction is not similar, i.e. when the fibers are interdigitating, caressing, curving, or bending each other, DTI is not valid (Figure 9) [22-24]. Recently, more robust models of the diffusion process have been proposed that focus to overcome the disadvantage of the DTI model. Among others, DSI is one of best solutions. DSI improves the accuracy in case of crossing fiber and also produces a high resolution and deep detail of fiber bundles in comparison with DTI (Figure 10) [22-24].


Figure 9. DTI (A) and DSI (B) images show the tractographies of crossing fiber bundles (white arrow).


Figure 10. DSI image shows whole full and detailed white-matter bundles.

Advantage and disadvantage

The biggest benefit of DWI sequences is the value of quantitative parameters reflected the velocity of proton’s movement and the shape of proton’s motion inside the tissue. With the current innovative techniques, IVIM also reflects partially the perfusion feature of tissues [7,8]. In addition to DTI, DKI and DSI can improve the precise rate in investigating the nerve, muscle and even tissue bundles thereby reducing the false positive and negative of diagnosis [18-24].

To resolve the low temporal resolution, Z-DWI is essential to assess the sophisticated structure like small gyrus, hippocampus and prostate [13-15]. All of these techniques are free gadolinium exposure hence it can duplicate without possibility of kidney damage or gadolinium retention. These techniques are very helpful in children, older patients, renal impairment disease and patients with high risk of gadolinium allergy. Nonetheless, DWI techniques are launched better in the MRI of at least 1.5 Tesla with corresponding analysis softwares [4-6]. Furthermore, DSI is tended to be more excellent on MRI of at least 3 Tesla and DKI needs to be evaluated with mathlab correlative with bi-exponential, tri-exponential or complex model [22-24]. In terms of investigation on the physiological and biological features of tissue, innovative DWI techniques are more prosperous and rigorous than conventional DWI in manufacturing more information for managing confidential diagnosis, appropriate treatment and lesions' response to therapeutic methods.


Diffusion magnetic resonance imaging has dissimilar types which can facilitate and produce helpful information for clinicians to optimize diagnosis and treatment strategy. In addition to conventional DWI and DTI, new methods such as IVIM, Z-DWI, DKI and DSI are developed to improve the precision of diagnosis and therapeutic treatment strategies, which therefore should be investigated carefully.

Disclosure statement

Luc Minh Truong, Vo Hoang Tri and Bui Nguyen Canh are employees of Siemens. Nevertheless, the scientific guarantor of this publication is Dr. Nguyen Minh Duc and Dr Huynh Quang Huy, Department of Radiology, Pham Ngoc Thach University of Medicine. Nguyen Minh Duc and Huynh Quang Huy contributed equally to this article. All authors read and approved manuscript. The authors of this manuscript report no conflict of interest.


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