Introduction
Over the last couple of years developments of magnetic resonance imaging (MRI) hardware
and software enabled the acquisition of high-quality images using fast imaging with
steady-state precession (True-FISP) [1]
[2]
[3]. With this technique, a high contrast between blood (hyperintense) and muscle (hypointense,
i. e. myocardium) has been reported. Due to the intrinsic T1/T2 contrast in True-FISP
[2]
[4]
[5], neither exogenous contrast agents nor pre-pulses are needed. Optimal image quality
with reduced artifacts in True-FISP sequences can be achieved using a minimally short
repetition time (TR) during the steady-state of the signal [1]
[3]. In addition to this, the intrinsic flow compensation of True-FISP in all three
spatial coordinates allows for suppression of artifacts originating from constant
flow [5]. Utilizing increased gradient performance as now available on clinical MR-scanners,
short TR and TE became feasible even for high resolution True-FISP sequences. The
high spatial resolution in conjunction with the intrinsic high signal of blood independent
of flow makes True-FISP a potentially favorable imaging sequence for MR-venography.
Furthermore, fast data acquisition in True-FISP sequences might allow for axial slice
orientations with improved delineation of thrombus head configuration in sufficiently
short acquisition times.
Methods
High resolution True-FISP-venography was implemented on a commercial 1.5 T Gyroscan
ACS-NT whole body MR system (Philips Medical Systems, Best, NL) equipped with cardiac
software (INCA2) and a commercially available PowerTrak®6000 gradient system (23 mT/m,
219 µs rise time). For signal acquisition, a commercial 4-element body synergy coil
was positioned at the level of the pelvis and vena cava inferior. Signal from the
lower extremities was obtained using a second (5-element) synergy coil. Using both
coils and a floating table with a step by step technique, data were acquired from
the whole region of interest (crus to infra-renal vena cava) without repositioning
of the patient. All subjects were examined in the supine position.
Scout scanning
For localization of the venous blood stream, a multi stack 2 D True-FISP scout scan
was used (TE 1.2 ms, 128 × 128 matrix, 440 mm field-of-view, 27 slices, slice thickness
10 mm, acquisition time 8 sec).
Imaging sequence for True-FISP MR-venography
MR-venography was acquired using a 2 D True-FISP imaging sequence with a centric ordered
k-space acquisition scheme, a TR of 5.0 ms and a TE of 2.5 ms. A constant excitation
angle of 85° was applied. Because steady state conditions are important for image
quality in True-FISP, 20 start-up cycles preceded the imaging portion of the sequence.
The field-of-view was 440 mm with a 512 × 512 scan matrix, resulting in an in-plane
resolution of 860 × 860 µm2. The slice thickness was 5 mm. For the pelvis two stacks with 20 slices each were
acquired asking the patient to take shallow breaths only to minimize breathing artifacts.
MR-venography of the pelvis and the legs was acquired using multiple stacks and a
floating table with a step-by-step technique. This ensured that the imaging slab was
always in the isocenter of the magnet in order to avoid banding artifacts originating
from field inhomogeneities. Data acquisition time was less than 10 min for a 100 cm
region of interest in craniocaudal orientation.
Subjects
True-FISP MR-venography was investigated in 40 lower extremities in 20 patients (14
- 88 years old). 13 patients suffered from left or right side thrombosis, 5 patient
from bilateral thrombosis, resulting in 23 thromboses in 40 extremities. Two patients
had no thrombosis in the investigated region. The proximal thrombus head was localized
in the vena cava (n = 6), iliac vein (n = 7), superficial/common femoral vein (n =
5) or popliteal vein (n = 4). X-ray phlebography (n = 7), CT (n = 8) or ultrasound
(n = 5, contraindication for X-ray contrast agent or pregnancy) was performed for
comparison [6]
[7].
Data analysis
True-FISP MR-venography was analyzed by two radiologists. The investigators were asked
to identify thrombus localization. Subsequently, data were compared with x-ray phlebography,
CT or ultrasound examination.
Signal-to-noise ratios of the venous blood pool at the level of the iliac, femoral
and popliteal veins and thrombus-blood-pool contrast-to-noise ratios [12] were calculated from regions of interest drawn in the venous blood pool and the
thrombus (maximal fitting circle). Noise was defined as the standard deviation in
a region of air in frequency encoding direction.
Results
MR studies were completed in all subjects without complications. Data acquisition
time was less than 10 minutes. On all the acquired True-FISP MR-venography images,
signal-to-noise ratio and contrast-to-noise ratio could be evaluated. Veins and arteries
were successfully differentiated including main calf veins using adjacent slices.
Fig. [1 a] shows representative images of a patient without thrombosis. External iliac veins
are displayed with a bright signal. In contrast, veins occluded by thrombus demonstrated
a signal loss and an enlarged vessel diameter (Fig. [2]). The proximal thrombus head of an acute deep venous thrombosis (Fig. [3]) is clearly delineated demonstrating a dark signal and a high contrast to the surrounding
bright venous blood stream. In all cases the thrombus head could be correctly localized
on the True-FISP MR-venography.
Although the aim of this study was to investigate the feasibility of True-FISP MR-venography,
in two patients with insufficient ultrasound examination conditions but contraindication
to X-ray phlebography, True-FISP-venography could demonstrate important additional
findings like common iliac vein or inferior vena cava thrombosis (Fig. [4]). In two further cases, unknown contralateral thrombosis was seen with True-FISP
MR-venography. Two tumor masses with venous compression syndrome and one vena cava
compression due to pregnancy (Fig. [2 c]) were found on the True-FISP MR-venography images.
Objective analysis of the pelvic and deep leg veins demonstrated a mean signal-to-noise
ratio of the blood-pool of 54 ± 19 and a high mean thrombus-blood-pool contrast-to-noise
ratio of 46 ± 16.
Discussion
Detection of acute deep vein thrombosis is of crucial importance due to potentially
severe complications including acute or chronic pulmonary embolism [8]. X-ray phlebography and ultrasound are well established for diagnosis of deep vein
thrombosis. But there are contraindications for X-ray phlebography like pregnancy,
hyperthyreosis or renal failure. Furthermore, contrast venography is semi-invasive
and may fail to depict some segments of the venous system in up to 10 - 20 % [7]. Ultrasound venography has been established as a non-invasive tool for deep vein
thrombosis detection with the limitation of low sensitivity for iliac veins, vena
cava inferior or calf veins thromboses. Furthermore, ultrasound is examiner dependent
and time-consuming. Thus, a non-invasive MR-technique for fast visualization of the
venous system may be a useful clinical tool. To obtain sufficient visualization of
small veins or thrombi in MR imaging, high spatial resolution is needed with a high
contrast-to-noise ratio. Therefore, we sought to investigate the potential of a fast
high resolution True-FISP sequence for MR-venography, which may allow for a high-contrast
MR-venography without costly contrast agent.
Technical considerations of MR-venography using high resolution True-FISP
True-FISP sequences demonstrate a T1/T2 contrast due to data acquisition in a steady
state condition of the transverse magnetization [9]. Therefore, the long T2 of blood allows for high signal intensities of the blood
pool. These signal properties are well known from functional cardiac studies [1]
[3]
[9]. However, in such lower resolution cardiac images, fat is nicely suppressed if a
low number of excitations and centric k-space sampling is used [10]. In contrast to this, in our high resolution True-FISP approach with a 512 × 512
matrix, enhanced excitations are used which might explain the bright signal of fat
in the presented True-FISP MR-venography images. The lack of fat suppression in our
sequence did not limit vessel depiction, because a typical black rim surrounding the
vessels allowed for sharp delineation of the vessel lumen even in small veins (Fig.
[1]). This black rim is probably due to the echo time of 2.5 ms yielding a near out-of-phase
situation for fat and water protons [9]. In our series, all thrombus demonstrated a hypointense signal when compared to
the venous blood pool, which may be explained by the relatively short T2 of clots
[11]. However, further investigations including clots of various ages are needed to fully
understand the contrast in MR-venography using True-FISP sequences.
Due to the intrinsic flow-compensation of True-FISP in all three spatial coordinates,
flow-artifacts are totally suppressed if slow constant flow is present [5]. In contrast to True-FISP MR-angiography, which requires data acquisition during
diastole to avoid artifacts from systolic aortic pulse [12], imaging of slow more constant venous blood may be possible without k-space segmentation
and therefore with more stable steady-state conditions. With the presented True-FISP
imaging sequence, the venous blood stream of the lower extremities including the pelvic
veins and infrarenal vena cava could be visualized without motion artifacts. However,
the impact of venous flow on True-FISP images remains to be investigated.
Clinical considerations of MR-venography using high resolution True-FISP
In our series, True-FISP MR-venography allowed for clear visualization of the thrombus
in all cases even in the main veins of the crus (Fig. [3 a, b]). The presented technique is a fast (< 10 min) imaging tool for routine diagnosis
of deep vein thrombosis, even with transaxial slice orientation and high spatial resolution.
First MR-venography techniques have used pedal contrast media administration and coronal
3 D gradient-echo sequences as known from MR-angiography, resulting in excellent MR-venograms
[13]. However, this approach is still semi-invasive, needs costly contrast agents and
acquires coronal slices. Axial imaging planes and high spatial resolution as used
in the presented approach may have the potential of better visualization of thrombus
head configuration with respect to the surrounding blood pool and contact to the vessel
wall when compared to coronal orientations due to lesser partial volume effect in
perpendicular to the vessel orientations. Although axial slice orientation requires
much more images than coronal slice orientation in order to cover the same field-of-view,
with the presented fast imaging True-FISP MR-venography approach, limitations due
to long acquisition times for large examined regions of interest are no longer present.
In our first True-FISP MR venography study using True-FISP imaging, 23 of 23 deep
venous thromboses were successfully visualized. Furthermore, in this first feasibility
study in two cases unsuspected bilateral thrombosis were found on True-FISP MR-venography.
In one further case, True-FISP MR-venography could clearly show a large floating thrombus
head in the inferior vena cava (Fig. [4]), a highly important finding for therapy. In two other patients, tumor masses causing
venous compression were diagnosed on the MR-images. This shows the potential of MRI
for examination of both legs and the pelvis including the soft tissue, which is automatically
performed with our transaxial True-FISP MR-venography approach.
MR-venography might be the technique of choice in case of pregnancy or for patients
with contraindication to contrast media administration. In pregnancy, initial clots
are often located in the iliac veins. Exclusion of vena cava inferior thrombosis,
which is essential for therapy strategy often is not achievable by ultrasound. Due
to potential vena cava compression in pregnant women and in order to minimize patient
discomfort, a fast MR-venography is needed, which can be easily performed with True-FISP
MR-venography (Fig. [2]).
Recently, new MR-approaches have been introduced allowing for fast detection of pulmonary
embolism [14]
[15]. Combined with fast MR-venography and without the need for additional contrast agent
application, a complete diagnosis can be achieved in one session and with only minor
prolongation of measurement time. The presented True-FISP MR-venography seems to be
a powerful and efficient tool for that purpose.
Although correct diagnosis of deep vein thrombosis was successfully established in
this first feasibility study, there are some limitations of this technique. In the
presented True-FISP MR-venography, arteries and veins are displayed with a bright
signal, which makes MIP reconstruction not useful. However, the bright arteries may
be used as landmarks, especially if veins are occluded. For validation of the clinical
usefulness of this new technique, further studies involving more patients and only
one gold standard for comparison are needed. Furthermore, the superiority of True-FISP
MR-venography when compared to other non-invasive tools like ultrasound remains to
be investigated.
Conclusions
The presented MR-venography using high resolution True-FISP allows for fast high-resolution
and high-contrast visualization of deep vein thrombosis.
